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Nanotube membranes for chemical and biochemical sensing and separation

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Title:
Nanotube membranes for chemical and biochemical sensing and separation
Creator:
Trofin, Lacramioara
Publication Date:
Language:
English
Physical Description:
xv, 109 leaves : ill. ; 29 cm.

Subjects

Subjects / Keywords:
Aluminum ( jstor )
Antibodies ( jstor )
Cell membranes ( jstor )
Chemicals ( jstor )
Diameters ( jstor )
Electrodes ( jstor )
Fluorescence ( jstor )
Ion currents ( jstor )
Molecules ( jstor )
Nanotubes ( jstor )
Chemistry thesis, Ph. D ( lcsh )
Dissertations, Academic -- Chemistry -- UF ( lcsh )

Notes

Thesis:
Thesis (Ph. D.)--University of Florida, 2005.
Bibliography:
Includes bibliographical references.
General Note:
Printout.
General Note:
Vita.
Statement of Responsibility:
by Lacramioara Trofin.

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University of Florida
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University of Florida
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Copyright [name of dissertation author]. Permission granted to the University of Florida to digitize, archive and distribute this item for non-profit research and educational purposes. Any reuse of this item in excess of fair use or other copyright exemptions requires permission of the copyright holder.
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726715280 ( OCLC )

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NANOTUBE MEMBRANES FOR CHEMICAL AND BIOCHEMICAL
SENSING AND SEPARATION














By

LACRAMIOARA TROFIN


A DISSERTATION PRESENTED TO THE GRADUATE SCHOOL
OF THE UNIVERSITY OF FLORIDA IN PARTIAL FULFILLMENT
OF THE REQUIREMENTS FOR THE DEGREE OF
DOCTOR OF PHILOSOPHY

UNIVERSITY OF FLORIDA































Copyright 2004

by

Lacramioara Trofin






























This dissertation is dedicated to my parents, Lucia and Nicolae Darie.












ACKNOWLEDGMENTS

I think if any of us honestly reflects on who we are, and how we got here, we

discover a debt to others that spans nearly our whole lives.


The work and support of some people made my life easier everyday.


Some people


have directly shaped my life and my work.

I would like to acknowledge the inspiration and guidance that I received from my


Ph.D. advisor, Dr. Charles R. Martin.


He encouraged and supported my work.


He also


taught me how to effectively communicate science and successfully write scientific


papers.


I am grateful for the many suggestions and comments that I received from the


members of the Martin group. I have been fortunate to be a member of such a diverse,

team-oriented research group. Many colleagues contributed directly to my research

projects with their ideas and energies. David T. Mitchell introduced me to the field of


He taught me how to make alumina membranes, silica nanotubes and he


gave me excellent training in electron microscopy.


advice on the microbattery project.

impedance spectroscopy. I am gra


SangBok Lee gave me insightful


Marc Wirtz taught me the fundamentals of


teful to Punit Kohli for his help in the protein


separation project and for his contagious enthusiasm for science.

chatting with Zuzanna Siwy have led to fruitful developments. S

with her knowledge and energy to my scientific development. I


The many hours I spent


The contributed directly

would like to thank


nanomaterials.






Elizabeth Heins, David Mitchell, Shufang Yu, Punit Kohli, Marc Wirtz gave me ideas


and helped me in preparing the talks that I presented during graduate school. I am very

grateful to Myungchan Kang, who helped me with the microarrays project. He taught me


about plasma etching technique and fluorescence spectroscopy.


I am indebted to Miguel


O. Mota, who did his best to improve on my best. Miguel spent many hours making


alumina membranes and solutions necessary for my projects.


I also want to thank


Heather Hillebrenner who has shared her needs and experiences with me.


I have had the


wonderful experience to truly believe that in some small way I helped her; that means so

very much to me. I am also grateful to Zuzanna Siwy and Lane Baker who proofread this

dissertation and, by their feedback, they helped me structure better the dissertation.

My life during the graduate school would have been much less interesting without

my friends Isabela and Calin Briciu, Zuzanna Siwy, Cristina Cosma, Nathalie Kohli, and


Violeta Bacanu.


I would like to specially thank my boyfriend, Hermann Schulte auf'm


Erley, for his love and continuous support during my last years of graduate school.

I would like to thank to my chemistry high school teacher, Ion Dumbrava, and my

mentor, Dr. Gheorghe Ivan from CERELAST-Bucharest, for their untiring support and

seemingly unlimited belief in me.

Special gratitude is reserved to my parents, Lucia and Nicolae Darie, who have

encouraged me in so many ways to pursue my life dreams.















TABLE OF CONTENTS
Page


ACKNOW LEDGM ENTS...... ... ............... ........ ...................................... v


LIST OF TABLES..... ............ ... ........ ..... ... a.. e..... .. ... ..... .. .......... ........... ix


LIST OF FIGURES... ................. ....... .... ...... .... .......... .. ......... ..x


AB STR A C T .................................................... ...... ... .. ......... .......... X V


CHAPTER


INTRODUCTION AND BACKGROUND .............. ........................ ..........1


Introduction............


B background ..... ..... ...... .....................
Membrane-Based Template Synthesis..
Membrane templates .................
Electroless deposition................


. .. m m
C tees tee c.


* m .. m m .


. .. .. ...3
. ... 3
. .... ..3


Applications of gold nanotube membranes
Porous Alumina Membranes......................
Two-step anodization method..............
M mechanism ...................................


* me .... ... S .. .....
.. .. ..............aacc. *...c e. .c me.
a ac. ... C5 .. .. .. ..t *m c e .e S *. e a....


....14


Applications of alumina membranes ....... ..... ........................... .. ....16
Sol-Gel Chemistry ................. ................................. ...... .. ..... 19
Silane Chemistry ......... ............... ........... ... ................................20
Carrier Facilitated Transport ............................................................23
Single Pore Polymeric Membranes ...................................................27
Irradiation with heavy ions.............. ....................... ....................29
Ion track etching ....... ........ ..... .... .... ............ ..... ................. 30
Dissertation Overview .................. ...... ......... ..a........... ...................... 32


ION CHANNEL MIMETIC SENSOR WITH AN ON-BOARD


MICROBATTERY ...........


* e e c cm C C J k ll C C 3 C Jft Ck cc .m e, ... at 5 m C C S tt /.35


Introduction .. ... ....... ..... ..e... ... .... ... .. ..... 35
FxYnerimnPntnl .


..5







Microbattery Fabrication ...........SE .......... ....... ..... ... .. 37
Scanning Electron Microscopy (SEM) ...................................... ........38
Cell Assembly and Battery Discharge Measurements............... .............38
Results and Discussions...................................... ................................. 39
Characterization of the Electrode Films .......................................... .. 39
Battery Iischarge Experiments......................................................... 41
Effect of Surfactant Concentration on the Response Time.........................46
Investigations of Alkyl Chain Length on the Response Time ......................47
Conclusions.. ........ ........ ......... ............ ... .. ........ ......... ... .... ... 48

HIGHLY SELECTIVE ANTIBODY-BASED NANOTUBE MEMBRANES FOR
PROTEIN SEPARATION



M aterials ........................... .. ............................ *.....S. .. ........ .. *...... ... 51

Fabrication of the Nanoporous Alumina Membranes.................................51


Antibody Immobilization...
Transport Experiments......
Results and Discussions .........
Effect of Antibody Affinity
Effect of the Feed Solution
Coefficient ...................
Effect of the Pore Diameter
Conclusions... ................


* C** ttt C..1q1 ec sss, qq.uss
baatcs C 11S1u1t cCC mu ... C*5 Ca


* t q c a
eq. ..


*9S95t:


on Selectivity Coefficient...................
Concentration on the Flux and Selectivity


on the Flux and Selectivity Coefficient.


. 52
. ... 53

...........54


... ..........57

... .. ..61


3-D POROUS ALUMINA-BASED PROTEIN MICROARRAYS.....................63

Introduction. ................. ................... ..... ........... .. .. .... ..... .. .. .. .63
Experimental. e....... ... ...... ..s.. ..... ..ss c...... .. ... ... ...... .... .64
M ateri als... .... ...................... ............................................ ... 64
Fabrication of Porous Alumina Microarrays.......................................67


M ethod 1.............
M ethod 2 .............
Membrane Modification
Microarray Modification
Results and Discussions.......


Microarrays
Microarrays
Effect of the
Sensitivity..
Selectivity..


s .. q s .e c e c s s e e.. .. ...6 7
for Sensitivity Studies ......... ...........................71
for Selectivity Studies .... ... ........ ...... ........ .....72
t..., q gs s. *. ,..,. c. a .. *,*., ., ... 73


Fabricated by Method 1............. ..... ............ ......... .......73
Made by Method 2 .. ..... ............. ..... .... .................. .74
Silica on the Sensitivity Measurements.............................75
........................ .. ... ...... C .. .76
c....... .q.q. q ..s. ......... ..t.. .. .. ,. .. .... .... ..... ...... ,7 7


C conclusions ...... ................... ... .. ........ ........... ......... .. ............... .. ..80







Introduction........ .................. .... ...... ............ .. ...... .. .. .. ... .. ..... .. ..82


Experim mental ........ ........ ..... ....... .... ... ...... .. ...
M aterials..........................c. .......... ................ .
Electroless Plating of PET Membranes........... .......
Proteins ...... .. .... e. ... ....... ........


.m. .m.. ... .. ..... .. 84
S...................... 84
.. ...... ....... .. ... .85
........ .. ... .... ..... 85


ExpCerimental Set e...... .......... ... ................. .......... ...... ................85
Results and Discussions ................ ........................................................86


......... e e c .94


6 C(ONC1LUS(IONSJ.(S..............g ...........g.g.. ..........g.c.ccg.......

LIST OF REFERENCES.........g.......................Ceeg*eam .e e aec*..e. ec........

BIOGRAPHICAL SKETCH..................................... ............... .............109


Conclusiotls.













LIST OF TABLES


Table

2-1

2-2

2-3


page

Effect of DBS concentration on the response time................................ 42

Effect ofDTA concentration on the response time............ .................... .43

Effect of alkyl chain length in alkyl trimethylammonium surfactants on the
response time .................. ................. .................... ........... 44













LIST OF FIGURES


Figure


page


Scanning electron micrographs of the surfaces of the (A) alumina and (B)


polycarbonate membranes......


S S 8 SS**


Electrochemical cell setup for alumina growth........................................10

Variation of the pore diameter with the voltage applied..............................11

Variation of the pore diameter with the concentration of the electrolyte


solution..


Scanning electron micrographs of the (A) solution side and (B) barrier side of an
alumina membrane formed at 50 V in 5% oxalic acid.................................1


Scanning electron micrographs of the (A) surface and (B) cross-section of an


alumina membrane obtained at 50 V in 5% oxalic acid...


S ** S ** 9.*..**11


. .... ..13


1-8.

1-9.

1-10.

1-11.

1-12.

1-13.

2-1.

2-2.

2-3.


Scanning electron micrographs of the (A) surface and (B) cross-section of a
commercial alumina membrane (Whatman) with pore diameter of 200 nm. .....14

Schematic representation of the pore formation in the porous alumina film...... 15

Steps involved in the silane chemistry.. .......... ....... .................. ........23

Typical nonlinear flux pattern for carrier-mediated diffusion. .....................25

Schematic representation of how the facilitated transport works...................26

Chemical formula of the PET (A) and Kapton (B). .................................30

Schematic representation of a conductivity cell used for chemical etching.......30

Schematic representation of the microbattery fabrication.........................38

Schematic representation of a U-tube permeation cell...............................39

Cross-sectional (upper) and surface (lower) SEM images of the battery electrode






EDS spectra of the membrane surface after deposition of Ag (A) and after


conversion of the Ag surface to AgCl (B).


EDS spectrum of the opposite


membrane surface that had been coated with Zn (C). ................................41


Current-vs.-time response for the transmembrane microbattery applied to an
alumina membrane that was not rendered hydrophobic by silane functionalization
(A). Analogous current-vs.-time response for the hydrophobic C18-modified
m em brane (B ) .......................... ........... .... ..... .. .... .. .... .. ............. .... .... 43


Current-vs.-time response for a hydrophobic membrane before and after injection


........45


Scanning electron micrograph of a porous alumina membrane with pores of 50
nm in diameter and pore density of- 1010


pores/cm2......................


Modification steps involved in antibody
immobilization..............................


S... .. 53


Transport plots of GFP-Hevein and RFP through ENA 11 His (A), 1 C2 (B) and


1A4 (C) nanotube membranes ...................................
Effect of the antibody immobilized on the selectivity .......
Plot of fluxes of GFP-Hevein and RFP versus feed solution


concentration ..........................


C *C C. C.55


C p


. ..57


Transport plots of GFP-Hevein and RFP through a 1A4 antibody-modified
membrane when using 5 nM (A), 20 nM (B), 50 nM (C) and 100 nM (D) feed


solution concentration................


*SSSS SSCC 55S* *S.*S SW CS*S e*S* ** ** CS* Se m... C CC .5


Variation of the selectivity coefficient with feed solution
concentration....................................................


Transport plots obtained when used membranes with pores of 50 nm (A), 70 nm
(B) and 100 nm (C) in diameter ...................................... ................. .60
Selectivity coefficient variation with the pore


diameter..


. ..... .. ... ...61


Schematic representation of the microarray fabrication by method 1...............66

Schematic representation of the microarray fabrication by method 2...............68

Electrochemical cell setup for silver electrodeposition: A, Ag wire counter and
reference electrode; B, Ag plating solution; C, Cu foil; D, Au-Pd modified
alumina membrane as working electrode; E, stainless steel plate; F, teflon tape; G,
O -ring seal .... ....... .................... .......... .......... ... .... ... ...... ... ...69


Modification steps for sensitivity studies .................................................71


Scanning electron micrographs of the porous alumina microarrays fabricated by
method 1 at a low (A) and higher (B) magnification.............. ...................72


...52


of DBS surfactant solution ................... .........,......., .....


..59






4-7.


4-8.


4-9.


4-10.


4-11.


Fluorescence spectra for a rhodamine B-APTES-alumina sample with (green) and
w without (red) silica ....... ............................ ...................... ...............76

Relative fluorescence coefficient for rhodamine B-modified membranes of
different thicknesses...... ................. .................................................77

Optical (left) and fluorescence (right) image of a 350 pm x 350 pm area of the
microarrays after immobilization of the target proteins.............................78

Excitation with 495 nm light: A, 2D fluorescence image; B. 3D fluorescence
image; C, fluorescence intensity profile ........... ........... ......... .............79


Excitation with 590 nm light: A, 2D fluorescence image; B. 3D fluorescence
image; C, fluorescence intensity profile................. ......................


.80


Sensing lysozyme with a single conical gold nanotube. (A) Current-voltage
characteristic of the Au nanotube before (red points) and after modification with
thiolated biotin (blue points). The diameters of the pore opening are 5 nm and 0.6
p-m, respectively. (B) Ion current versus time through the Au nanotube modified
with biotin recorded at 1 M KC1, pH 7. (C) Ion current versus time as in (B) at
presence of 100 nM lysozyme in contact with the small opening of the pore....87


Sensing streptavidin with a single conical gold nanotul
characteristics of a single conical Au tube modified wi
180 pM streptavidin added on the small side of the con
current in time through a single Au nanotube modified
M KCI, pH 4.5, recorded at -1000 mV. (C) Ion current
presence of 180 pM streptavidin...........................


Blockage time vs.


be. (A) Current-voltage
th SH-biotin at presence of
lical nanotube. (B) Ion
with biotin, recorded at 1
in time as in (B), at


. ....... 88


-log of the molar streptavidin concentration ...................90


Chemical modifications of a
dimensional nanoimmunoass
interactions with protein G.
modifications of a single Au
1 M KC1, pH 7, performed a
modifications has diameters


single Au tube leading to preparations of 3
say for detection of IgGs and probing their
(A) Schematic representation of the subsequent
tube. (B) Current-voltage characteristics recorded at
after each modification step. The gold tube after
of-I15 nm and 0.6 pm, respectively..................91


L


Sensing of cat IgG with a single conical Au nanotube modified with protein G as
shown in Fig. 4. (A) Current-voltage characteristic of a single Au tube recorded at
1 M KC1, pH 8.7. Ion current in time recorded at 500 mV transmembrane
potential before (B) and after (C) adding 100 nM cat IgG. The gold tube after
modifications has diameters of-15 nm and 0.6 pm, respectively..................92


Sensing of horse IgG with a single conical Au nanotube modified with protein G
4 a a^ t aj 4 4 P, fl4 a**r .*j 4 4* .






5-7. I-V curves for the ricin sensor in the presence of no protein (x), 100 nM BSA( ),
and -100 nM ricin (e). ............. 94.................. ...............94












Abstract of Dissertation Presented to the Graduate School
of the University of Florida in Partial Fulfillment of the
Requirements for the Degree of Doctor of Philosophy

NANOTUBE MEMBRANES FOR CHEMICAL AND BIOCHEMICAL SENSING
AND SEPARATION

By

Lacramioara Trofin


May 2005


Chair:


Charles R. Martin


Major Department:


Chemistry


The discovery of novel materials, processes, and phenomena at the nanoscale, as

well as the development of new experimental and theoretical techniques for research,

provide fresh opportunities for the development of innovative nanodevices and


nanostructured materials.


Nanostructured materials can be made with unique


nanostructures and properties, and finding various and unique applications of these is a


continuous challenge for researchers in this field.


As part of this emerging research, the


work presented here is focused on development of new nanostructures based on

nanoporous membranes, and investigation of their applications as sensors and separation


devices.


A template synthesis method is used to produce nanotubes inside the pores of


both aluminum oxide and polymeric membranes.


After an introduction in the template


synthesis method and the processes of fabrication of the porous membranes, the

dissertation is centered on investigating new applications of these nanotube membranes.






There are three applications of the nanotube alumina membranes, and one application of

the single nanotube polymeric membranes that are explored.

Porous alumina is used to mimic the function of the ligand-gated ion channel by

applying a porous battery cathode film to one face of the hydrophobic membrane and a


porous battery anode film to the other face.


Hence, in analogy to the naturally occurring


channel case, we have a membrane with a built in electrochemical potential difference

across the membrane.

The application of silica nanotube membranes in selective separation of proteins is


presented

analyte.


i.


The membranes were modified with antibodies that selectively bind one


These nanotube systems lead to the transport at much higher rates of the analyte


which binds to the membrane.

Another application studied is the fabrication of the protein microarrays which

features a three dimensional substrate based on porous aluminum oxide membranes.

These membranes represent distinct microfeatures on a robust platform, and they have


cylindrical pores with monodisperse nanoscopic diameters.


The advantages of using this


substrate and its application in antibody specificity screening are presented.

Finally, a new family of protein biosensors based on a single conical nanotube


membrane is described.


Three different protein systems were investigated: (i)


biotin/streptavidin, (ii) protein-G/immunoglobulins, and (iii) anti-ricin/ricin.











CHAPTER 1
INTRODUCTION AND BACKGROUND

Introduction

Nanotechnology refers to technologies in which matter is manipulated on the


atomic and molecular level to create new materials and observe new processes.


It is not


just the study of the very small; it is also the practical application of that knowledge.


Nanotechnology is a truly interdisciplinary field.


Materials scientists, electronic and


mechanical engineers, as well as medical researchers are working together with


biologists, physicists and chemists.


Research at the nanoscale is unified by the need to


share the knowledge and expertise required to work at the atomic and molecular level.

Powerful new concepts and capabilities, such as atomic-scale imaging and manipulation,

self-assembly and biological structure-function relationship, together with increasingly

powerful computing tools are rapidly converging from different research areas.


Nanotechnology is not a new area, though.


Mother Nature serves as a model for having


many materials and processes that functions at the nanoscale (1); small molecular

building blocks are joined together to produce nanostructures with defined geometries


and functions.


The top-down approach becomes increasingly difficult, as the final


products approach the nanometer levels.


It has become evident that Nature's bottom-up


approach can be emulated to produce new materials with nanosized dimensions and

engineered properties.

KT t a, .. a a4 n 1 n-^ n j (,j / ) \ n \ n 4 r. .' a:,, 4. .L I La a I a a a a c







silver particles.


More recently, a wider variety of nanoparticles have been synthesized;


for example, commercially available magnetic beads are used for cell preparation (6,7),

quantum dots are used for long-term fluorescence assay in cells (8), and colloidal gold


has been used for gene therapy (9).


Since the discovery of carbon nanotubes in 1991


(10), the synthesis and functionalization of the nanotubular materials has become one of


the most highly energized research areas (11).


Nanotubes have numerous potential


commercial and technological applications, including their use in nanoelectronics

(12,13,14,15), catalysis (16,17,18), hydrogen storage (19), scanning probe microscopy

(20), biosensors (21,22) and drug delivery systems (23).

Research in the field of nanotube membranes will have a great impact on


membrane technology.


Membranes are utilized to perform separations for a wide range


of applications such as water and wastewater treatment, electrodialysis, gas separation,


and fuel cell development (24).


The use of membranes and biological tools are important


in the development of biomedical and biotechnological applications (25).


Recently,


membranes have been gaining attention as options for biological sensors (26).


However,


modem biotechnology and separation science have presented new challenges to

membrane technology, including the requirement of pores with diameters similar to those


of molecules under study, therefore as small as several nanometers.


Nanometer scale


pores are necessary in achieving optimal control of the flow of biomolecules as well as in


developing sensors for their detection (27-30).


Another challenge is the development and


characterization of membranes possessing well-controlled, stable, and uniform nanometer

dimension pores capable of the separation and sensing of molecules in a restricted




3


In light of these challenges, Martin's group has pioneered a bottom-up method for


the production of nanotube membranes, called template synthesis (31). This method

involves synthesizing nanotubes inside of a porous membrane (template). This chapter


provides background information on the following: membrane-based template synthesis,

fabrication and applications of porous alumina (one type of membrane template), sol-gel

and silane chemistry, carrier facilitated transport, and single pore polymeric membranes.


An overview of the dissertation is also presented.


This information will be used in the


next chapters.

Background

Membrane-Based Template Synthesis

In recent years, the Martin group has been investigating a versatile method to


produce nanomaterials, called template synthesis (31).


In this approach, a membrane


with uniform dispersed, micro or nanometer diameter pores acts as a template.


When


material is deposited into the cylindrical pores of the membranes, it adopts their shape.

the template is dissolved, the material can retain the high aspect ratio of the pores,


yielding wires or tubes with nanometer diameters.

the type of materials that can be prepared. For ins


The method is versatile with regard to


stance, track-etched polymeric


membranes have been used to prepared nanostructures composed of metals (32,33),

insulating polymers (34) or conductive polymers (35,36).

Membrane templates

Two types of template are most often used for this approach: polycarbonate and


alumina membranes.


Polycarbonate membranes are prepared by the "track-etch" method







pore densities approaching 109 pores/cm2

electrochemically from aluminum foils (38

International), or can be prepared in the lab


Alumina membranes are prepared

). They are commercially available (Whatman

oratory. The process of making alumina


membranes and their applications will be discussed in detail in the following section.


Figure 1-1. Scanning electro micrographs of the 3 pim pore diameter polycarbonate (A)




5


Figure 1-1 shows scanning electron micrographs of the surfaces of the


polycarbonate and alumina membranes, respectively.


Templates with diamond shapes


pore in mica have also been reported (39).

The sensing and transport properties of the gold nanotube membranes prepared by

the electroless deposition method (40) were investigated extensively in the Martin group

(40-47).

Electroless deposition

Electroless deposition involves a chemical reducing agent which is used to plate a


metal from a solution onto a surface.

be summarized as follows. The men


solution of SnCl2.


The method for electroless deposition of gold can


ibrane is first "sensitized" by exposing it to a


This results in deposition of Sn" onto the membrane surfaces and the


pore walls. After the sensitization, the membrane is immersed into an ammonia silver

nitrate solution. A surface redox reaction occurs (Equation 1-1) and Ag' is reduced by


, which results in absorbtion of Ag nanoscopic particles on the membrane surfaces.


Sn~ + 2Agf01


- SnV + 2Ag>


The subscripts "surf" and "sol" denote species absorbed to the membrane surfaces


and species in solution, respectively.


plating solution at 40C.


Then, the membrane is immersed into a gold


A second redox reaction occurs, and Auo displaces the Ag


particle, yielding the membrane surfaces to be coated with Au particles (Equation 1-2).


Au' + Ago,


(1-2)


-> Auo + Ag\o


These Au particles are excellent autocatalysts for the reduction of Au' to Au,




6


Applications of gold nanotube membranes

Gold nanotube membranes are a new class of molecular filters, capable of sensing


and transporting both small and large molecules.


excess


Jiraje et al. took advantage of the


charge density present on the inner walls of the gold nanotubes and showed the


regulation of ion transport through the membranes (40).


They showed the fluxes of


anionic and cationic permeates changed with the potential applied to the gold nanotube


membranes. The tubes transport ions which have the opposite charge as the gold

nanotubes (40). Because the inner diameter of the gold tubes can be of molecular


dimensions (<1 nm), nanotube membranes have also been used to separate small


molecules on the basis of molecular size (41).


In these experiments, a large molecule, (a


tris-bipyridal complex of Ru(In Ru(bpy)32+), and a small molecule (methyl viologen


MV2+), were used.


A selectivity coefficient was defined as the ratio between the fluxes


of MV2+


Ru(bpy)32+ through the membranes.


They report a selectivity coefficient


of 50 when the inner diameter of the gold tubes was 5.5 nm.


They have also showed that


as the inner diameter decreases, the selectivity coefficient increases, reaching a value of


fora


nm inner diameter (41).


The gold nanotube membranes were also used to


study the DNA transport, both by diffusion and electrophoretically.


The flux of the


single-stranded homooligonucleotides made of thymidine bases (poly(Tn) where n

represents the number of bases decreased as the size (base number) of the poly(Tn)

increased (42).

Another way of introducing chemical and biochemical transport selectivity is by


adsorbing thiols on the gold nanotubes (43.44.451.


Hvdronhobic thiols vield membranes








gold tubes was used to make pH-switchable ion transport membranes.


Depending on the


solution pH, the membrane can have excess positive charge (low pH), no net charge


(isoelectric point ), or excess negative charge (high pH ).


As a result, these membranes


can be switched between cation-, non-ion-permselective, and anion-transporting states


(45).


By controlling the inner diameter of the gold tubes, these membranes can also show


good selectivity for transport of proteins on the basis of molecular size (46).


In this work,


chemisorbtion of a PEG-thiol prevented the non-specific adsorbtion of the protein on the


gold tubes.


A transmembrane pressure was applied to the feed solution to force the


solution through the membrane.


The effect of nanotube diameter on the flux and


selectivity for lysozyme, bovine serum albumin and P-lactoglobulin A was investigated


(46).


Recently, through the immobilization of molecular recognition elements, gold


nanotube membranes were used to obtain


selectivity (47).


DNA single base mismatch transport


Single-stranded DNA molecules with a thiol at one end were


chemisorbed on the inner walls of the tubes.


These DNA functionalized tubes selectively


recognize and transport the DNA sequences which are complementary to the DNA on the

tubes, relative to the uncomplementary DNA sequences.

Porous Alumina Membranes

Electrochemical oxidation (anodization) of aluminum surfaces under controlled

conditions can produce aluminum oxide or alumina with a structure of essentially


cylindrical, parallel pores (48).


Anodic porous alumina membranes can be made with


pore diameters varying between few nanometers to 200 nm, with lengths up to 300 urm


I_.flX. -1L: r.-. ,-d2ln1


r(-1.. LI-.~- L~ l*f..L,,,: 3',


/ Af \




8


solutions (e.g. phosphoric acid (49), oxalic acid (50) and sulfuric acid) are used as

electrolyte (51).

In recent years, there has been a growing interest in preparing alumina membranes

with a perfect pore array architecture, having a high aspect ratio at the nanometer scale.

This interest was drawn by the possibility of applying these membranes as hosts or

templates for the fabrication of the nanodevices.

There are two reported methods for the fabrication of highly ordered anodic porous


alumina membranes.


One is the two-step anodization method which will be discussed in


detail in the next section; this is the method that is used in our laboratory to make the


alumina membranes (52,53).


In the other method, the layout of the initiation sites for


hole development in anodic alumina is achieved by a process based on nanoindentation


of the aluminum substrate.


In this process, an array of shallow depressions is formed on


aluminum by indentation, and these depressions serve as initiation sites for hole


generation at the initial stage of generation.


Masuda et al. (54) used a SiC mold to form


an array of concave features with the desired arrangement (square, triangular) on


aluminum.


In addition, Mikulskas et al. (55) showed that the nanoindentation twice with


commercially available optical grating rotated by an angle of 600 to each other, can create


pre-structures with rombohedral ridges on aluminum.


The advantage of this patterning is


that it eliminates the high cost of the mold, which requires electron beam lithography to


produce it.


Masuda et al. (56) reported another patterning method, by using a


nanoindentation apparatus attached to a scanning probe microscope.

Twn-sten anodization method







Polishing of aluminum foils. In order to obtain a high quality alumina film, the

starting material, aluminum, must be very smooth. High purity aluminum foils (99.99 %)


are first mechanically polished with a slurry of alumina particles.


Larger particles


(>10pam) are used to remove material fast, and polishing is continued with slurries of


progressively smaller particles of submicron size.


If the aluminum foils have severe


scratches, mechanically polishing with fine sand paper is applied until the scratches


disappear.


This mechanical polishing is followed by an electrochemical one.


In this


process, a potential difference of 15 V is applied between the aluminum foil (which


serves as the anode) and a lead plate which serves as the cathode.


The polishing solution


(95% concentrated phosphoric acid, 5% concentrated sulfuric acid and 20 g/L chromic


oxide) is heated to 700C.


This process is analogous with that of alumina film formation,


but the electrolyte, being a very concentrated acidic solution at high temperature, favors


immediate dissolution of alumina.


The electropolishing step (usually 5 minutes) is


repeated as many times as it is necessary, until the aluminum foil has a mirror-like

surface.


Anodization steps.


Electropolished aluminum is electrochemically oxidized into a


first step at a constant voltage, using an electrochemical cell setup like the one presented

in figure 1-2.

In the process of forming the alumina film referred in the literature as the growth


process, the aluminum is the anode and a stainless steal plate is used as the cathode.

anode and cathode are immersed into an electrolyte solution and a voltage is applied


jicino a rn,-^r ciinnlrl


Both


Th ftemnnratlire /(lrol/llx; hehl xin (Y sanl 1 0 \ i rnntmnllrl ilcinoa




10

strongly on experimental conditions, such as temperature, voltage applied, type of


electrolyte and concentration of the electrolyte (57-59).


Smaller pore sizes require lower


applied voltages and therefore more conductive electrolytes (such as sulfuric acid) (48).
Larger pores need larger voltages, which causes a high rate of dissolution in highly
conductive electrolytes (62).


Anode


Power
supply


Cathode


Alumin


,/Porous
Alumina


Electrolyte


Stirring
bar


Figure 1-2. Electrochemical cell setup for alumina growth.
Thus, the formation of large pores will require lower conductivity electrolytes, such as


oxalic acid.


The pore diameter in the grown alumina films varies in direct proportion to


the voltage applied and the concentration of the electrolyte.


Figure 1-3 shows the


dependence of the pore diameter on the voltage applied, when using 5% oxalic acid as





1


electrolyte solution, when 50 V was applied.


1


The thickness of the formed alumina film


depends on the anodization time; longer anodization times yield thicker membranes.

After the first anodization, alumina film is removed in a solution which is 0.4 M in


phosphoric acid and 0.2 M in chromic oxide at 600C.


The removal of alumina film leaves


behind aluminum with a hexagonal scalloped pattern, due to the self-organizing into a


hexagonal arrays of the pores during the anodization (50).


That is, the removal of the


alumina leaves indentations, or pits, in the aluminum that correspond to each pore.


1 2 3 4 5
Oxalic Acid Concentration, %


Figure 1-3.


Variation of pore diameter with applied voltage.


140 -
120
100 -
80
60
40
20





12


To obtain this pattern on aluminum, the duration of the anodization process must at

least 12 hours.

The pre-pattemed aluminum is then re-anodized in exactly the same conditions,


which were used in the first anodization step. The por

already highly ordered and monodisperse (52). The se

out for a length of time, depending on the thickness of


es nucleate in the pits which are

cond anodization step is carried


alumina membranes desired.


our laboratory, we obtained alumina membranes of thicknesses between 0.3 and 150 p.m.

Detaching. After the second anodization step, alumina can be detached from the


unoxidized aluminum by two methods.

a saturated solution of HgC12. One sid<


One method utilizes dissolving the aluminum in


e of the formed alumina membrane, which faced


during the growth the electrolyte solution has open pores while pores on the other side


are closed (60).


The two sides are called "solution" and "barrier" side, respectively.


Figure 1-5 shows the scanning electron micrographs of the solution side and barrier side

of an alumina membrane obtained in our laboratory.


4r- J J f 4 -r 6 t 4 f




13


This barrier layer can be removed by etching of alumina films for very short time in


dilute acid or basic solutions.


The second method for detaching the alumina films is


known as the "voltage reduction process" (61).


This process uses a progressive reduction


of the applied voltage until it reaches 4-5% from the initial value.


Because the pore


diameter is directly proportional to the voltage applied, the resulting pores branch down


to smaller sizes.


The anodization is then stopped and the aluminum/alumina system is


placed into an etching solution, which can be a dilute acidic or basic solution.


The thin


barrier layer and the small pores dissolve faster, resulting in detachment of the alumina

from the aluminum.

In our laboratory, using two-step anodization method, we obtained highly ordered,

porous alumina membranes. The pores are very uniform throughout the whole thickness

of the membrane, as can be seen in Figure 1-6.




.. .l... .


******** e* ...:. ---







Figure 1-6. Scanning electron micrographs of (A) surface and (B) cross-section of an
alumina membrane obtained at 50 V in 5% oxalic acid.

Alumina membranes with pore diameters of 200 nm are commercially available


frrnm Whntman Tnternmtinnnl


PnreA nf 1 Oi nm nnd 90 nrm in rliameter arp alAn nvnilahle




14


on one side the pores have these diameters on a length of 200 nm; on the other side the

membranes have pore with 200 nm in diameter. Figure 1-7 shows scanning electron

micrographs of the (A) surface and (B) cross-section of a commercially available alumina

membrane with a pore diameter of 200 nm. Compared to the home-grown membranes

(Figure 1-6), these membranes have pores which are not uniformly distributed throughout

the membrane and are characterized by much more heterogeneous diameter.


rfe


Figure 1-7. Scanning electron micrographs of (A) surface and (B) cross-section of a
commercial alumina membrane (Whatman) with pore diameter of 200 nm.

Mechanism

The formation of a highly ordered pore array in the alumina membranes is the

result of two competing processes: 1) the pore initiation process due to a geometric

effect, which is called "field assisted dissolution process" (52) and 2) the self-

organization of the pores which is thought to be driven by mechanical stress at the

alumina/aluminum interface (62).

In the pore initiation process, the alumina film developed at the metal-film-

electrolyte interface, at preferred sites (small pits or defects), undergoes dissolution,







outer film surface, which are the precursors of the pores.

effectively polarizes the Al-O bonds, allowing more A13


of the field.


Field-assisted dissolution

dissolution than in the absence


As a consequence of the pore development, the electric field and the ionic


current become concentrated in the barrier layer beneath the major pores.


This implies


continued migration of the 02/0H' ions from the electrolyte to form a solid film at the


metal-film interface and corresponding A13+

as well as field-assisted dissolution of A13 i


ejection at the pore base-electrolyte interface

ons (59). This mechanism of pore nucleation


is illustrated schematically in Figure 1-8.


AIO


f/nt


Figure 1-8. Schematic representation of the pore formation in the porous alumina film.

The pore initiation process is followed by a steady-state film formation. In this

state, there is a dynamic equilibrium between film growth at the metal-film interface and

field-assisted dissolution at the pore base-electrolyte. The mechanical stress, a possible

origin of repulsive forces between neighboring pores, is associated with the expansion of

the aluminum during oxide formation (62). This leads to the self-organization of the




16


Applications of alumina membranes

Due to the packed array of columnar hexagonal cells with cylindrical, uniformly

sized pores, porous alumina membranes have been used to fabricate many types of


nanocomposites using the template synthesis method.


For instance, template pores were


filled with metals or semiconductors used for the preparation of magnetic recording

media (63,64), optical devices (65), functional electrodes (66,67), electrochromic (68),


and electroluminescence display devices (69,70).


The outside diameter of the


nanocomposites is determined by the pore diameter of the membranes, and the length of


the nanocomposites is controlled by the thickness of the membranes.


Natan and co-


workers synthesized submicrometer metallic barcodes by alternating Au and Ag


segments along the length of a nanowire (71).


For sensing and nanoelectrode


applications, the nanowires can remain in the template and function as an array.


single-nanowire applications, removing the template produces individual nanowires that


can be isolated.


Porous alumina has also been used as a template to make Au, Ni and Si


nanoring arrays by a sputtering redeposition method (72).

The channels of alumina membranes were used to produce a new kind of artificial


lipid membrane system.


In this system, lipid bilayers were immobilized on the surface


(73) and inside of the pores of the membranes (74), creating a platform with potential

applications for biosensing.

Porous alumina membranes were also used as a support to incorporate metal


clusters, or colloid particles (75).


This opens the way to new applications, such as


chemical complexation inside the membranes of radioactive organo-metallic compounds







Lahav et. al. reported a procedure to make metal "nanoparticles nanotubes" that

combines nanotube geometry with nanoparticle morphology and properties (76).

When the alumina membranes are used as templates to make nanotubes, an


important issue is controlling the inside diameter of the formed nanotubes.


This problem


has been approached


by the layer-by-layer film deposition process.


In this method, films


of materials are deposited layer-by-layer on the pore walls of the membranes to make


nanotubes.


The resulting inner diameter of the nanotubes is dictated by the thickness and


the number of film layers deposited.


polyelectrolytes (77).


Using this method, Ai, et al. deposited layers of


Kovtyukhova et al. have also used a method based on alternate


SiC14/H20 deposition cycles to make silica nanotubes (78), and Hou, et al. used

Mallouk's alternating a,wo-diorganophosphonate/Zr chemistry (79) to prepare nanotubes

within the pores of alumina template membranes (80).

Highly selective silica nanotube membranes can be used as both sensors and as


molecular filters (81,82,83).

nanotube membranes (84).


A sol-gel template method was used to prepare the silica

In the next section, a detailed review of the chemistry


involved is presented.

Two applications of the silica nanotube membranes are their use for biological


extraction and for biocatalysis.


In this procedure, silica nanotubes were removed from


the membrane by dissolving the template, and collected by filtration.


They were


functionalized with octadecyl silane on the inside, resulting into a hydrophobic nanotube

interior, while the outside was left unfunctionalized, giving an hydrophilic nanotube


extenor.


These hvdrophilic/hvdroohobic nanotubes were used successfully to extract




18


solution of 7,8-benzoquinoline, a lipophilic compound that preferentially entered the


hydrophobic interior of the tubes.

removed from the solution (81).


In this way, more than 90% of the compound was

In the same work, Mitchell et al. showed that


enantiomers of a drug can be separated using a suspension of nanotubes (81).


In this case


the nanotubes were functionalized with an antibody that binds the RS isomer of the drug


over the SR isomer.


These nanotubes successfully extracted 75% of the RS isomer from


a 20 ptM racemic mixture, and all of the RS isomer from a 10pM racemic mixture.

Another application of the silica nanotube membranes is their use in bioseparation.

Lee and co-workers also looked at the separation of RS and SR enantiomers of a drug


(82).


In this case, the membrane was not removed, and the silica nanotube membranes


were modified again with an antibody that selectively binds the RS isomer.


They found


that these membranes facilitate the transport of the RS enantiomer, as the RS flux was


twice the SR flux, for nanotubes with an inner diameter of 35 nm.


It was also shown that


the binding affinity of RS over SR could be tuned by addition of DMSO to the protein

buffer solution, leading to an optimal DMSO concentration that maximized the


selectivity.


The selectivity could be further enhanced by decreasing the silica nanotube


diameter, yielding a selectivity of 4.5 when the nanotube diameter was 20 nm.

Yamaguchi and co-workers have reported a method to form a hybrid membrane

composed of silica-surfactant nanocomposites inside a porous alumina membrane, which


functions as a nanometer-order size-exclusive separation (83).


In this work, they added a


precursor solution of TEOS (tetraethoxyortosilicate) and CTAB

(netvltrimethvlnmmnniuim hrnmide' tn the aluminn memhrann raevltino in the




19


were able to separate two small protein molecules, myoglobin and bovine serum albumin,

(diameter > 4 nm) from two other smaller molecules, rhodamine B and vitamin B12,


(diameter


< 2.4 nm).


Nanorods made in alumina membranes were used as gene delivery systems (85).

Leong and co-workers fabricated nickel-gold nanorods by template electrodeposition in


alumina membranes. Transferrin, an iron transport protein, was bound to the Au

segments by a thiol linkage. They served to promote cellular uptake of the rods by a

receptor mediated pathway. The Ni portions were functionalized with DNA plasmid that

contained a fluorescent reporter gene. They showed that the nanorods were internalized

by the cell, but they did not enter to the nucleus. These nanorods have two functions, one

to target the cells and to deliver the DNA. In the nucleus, green fluorescence was


observed, indicating the delivery of the reporter gene into the nucleus.

Porous alumina membranes in a tubular shape were made when the aluminum to be


oxidized was purchased in the form of wires or cylinders.


were used in studies of catalysis (86),


These porous alumina tubes


and as drug delivery systems (87).


Sol-Gel Chemistry

Sol-gel chemistry is a powerful method to generate inorganic materials. It

originated in the 1970's, as scientists attempted to find low temperature routes to glass


synthesis (88,89).


The high temperatures (1300 to 20000C) needed to form glass are a


result of the need to destroy the crystallinity of the precursors; that is, even the glass is an


amorphous material, it is generally made from crystalline oxide precursors.


method to use noncrystalline precursors was searched for.


As a result, a


It was found that liquid







R3Si-O-R+H20 R'Si-O-H +R-OH


(1-3)


The silanols than can undergo further polymerization reactions with another

silanols or other alkoxysilanes:


RSi-O-H+H-O-SiR


- R3Si- O -SiR3


+H20


(1-4)


RSi-O-H+R-O-SiR3


-- R3Si- O SiR3+R-OH


(1-5)


In both cases, the result is formation of a three-dimensional siloxane network.


the start of the polymerization, many small siloxanes particles are formed.


well dispersed in the liquid phase and form colloids.


They are very


When the particles are well isolated


from each other, the density of the suspension resembles that of the solvent.


stage, the colloidal form is called a "sol"


At this


. As polymerization continues, the particles


increase in size and the viscosity of the solution increases.


The particles develop a three-


dimensional network throughout the solution, which is named a "gel" (90).


Temperature,


solution pH, water concentration and the type of the alkyl group are parameters that


influence the rate of hydrolysis and polymerization (91).


with the temperature.


The rate of gelation increases


The hydrolysis reaction is very slow and entails the replacement of


alkoxy groups with hydroxyl groups.


or base catalyzed (92).


It is much faster when the reactions are either acid


A larger, more sterically bulky alkyl group slows down the


reaction rate (92).


There are two ways of converting gels to silica. In the first method, the gel is

heated or placed under vacuum to remove the solvent phase. The open three-dimensional


structure collapses, condensing it into a dense phase called a xerogel (91).


In the second








material, called an aerogel (93).


The maximum temperature for both processes can be


kept below 1000C.

Silane Chemistry

Siliceous surfaces (e.g. silicates and aluminates) can be derivatized with a large


variety of different functional groups using silane chemistry.


covalent bonding with these surfaces (94).


Organosilanes form


The general formula of an organosilane is


RnSiX(4-n), where X is a hydrolyzable group capable of forming strong covalent bonds


with the hydroxyl groups on silica surfaces such as halogen, alkoxy or aciloxy.

group is a nonhydrolyzable group that may posses a desired functionality (95).

most used types of organosilanes for surface modification are chlorosilanes and


alkoxysilanes.


The R

The two


The attachment chemistry of both types is equivalent because when the


chlorosilanes are dissolved in alcohol, they react with the alcohol to form alkoxysilanes:


R3Si-Cl+R-O-H


-R3Si-O-R+HCI


(1-6)


The extent of this reaction can be monitored by measuring the pH. Alkoxysilane


chemistry is analogous to the sol-gel formation chemistry. Silanes with one hydrolyzable

group can be utilized to produce monolayers on the surfaces. Because there is only one

reactive group, the silanes can either bind to the surface or dimerize. Dimers cannot bind


further and can be washed away.

hydrophobic surfaces (95). Whe


The silanes with one hydrolyzable group yield to


;n surfaces with a higher degree of coverage are desired,


silanes with two or three hydrolyzable groups are used.


These are first allowed to


oligomerize in a slightly aqueous alcohol solution (water content is typically 5% vol/vol)








alkoxysilanes (94).


The surface to be modified is than added to this solution and the


oligomers bind to the surface through the surface hydroxyl groups (coupling step).


Figure 1-9 shows the reactions involved in the hydrolysis and coupling steps.


modification by this route requires only a few minutes of immersion.


Surface


If a 2% of


trialcoxy- or trichlorosilane solution is used, the resulting modified surface is normally 3-

8 monolayers thick (95).

The silanized surfaces must be cured usually at 1200C for 30 minutes, or for 24

hours at room temperature.

Chlorosilanes can also be deposited from aprotic solvents, such as toluene and


tetrahydrofuran (94).


If these solvents are anhydrous (and the surface is free of water),


then no alkoxysilane can be formed, and no polymerization of the silanes can take place.

The reaction must proceed by the nucleophilic attack from surface hydroxyl sites, and as


a result, only one monolayer can be formed (94).


Surface modification in these cases


takes longer time, usually 12-24 hours.







Step 1. Hydrolysis


y/\V\S -OR
\OR


+ 3H20


y/VSiLOH
\OH


+ 3ROH


Step 2. Coupling


Si Si O Si Glass surface


Si -O- Si-O-Si


I I
0 H OH


O
H

HOJAPH
*
Ho(I)


%44%


A?


Figure 1-9 Steps involved in the silane chemistry.

Carrier Facilitated Transport

In biological systems, the simplest mechanism by which molecules pass through a


plasma membrane is passive diffusion (116).


During the passive diffusion, a molecule


simply dissolves in the lipid bilayer, diffuses across it and passes to the other side of the


membrane.


Larger, uncharged, polar molecules, such as glucose, and charged molecules


of any size, like small ions K Na


passive diffusion.


, Cr, are unable to cross the plasma membrane by


Their passage through the membrane is mediated by proteins that


enable the transport of molecules and ions through the plasma membrane without







Carrier proteins bind specific some molecules that are transported.


They then undergo


conformational change that allows molecules to pass to the other side of the membrane.

Channel proteins form open pores through the membrane, allowing free diffusion of any


molecule of the appropriate size and charge.


In biological systems, this phenomenon is


called facilitated diffusion.

By the 1950's, scientists started to develop synthetic analogs of natural systems that


function on the base of facilitated transport concept.


Facilitated transport that uses a


chemical completing agent immobilized into a synthetic membrane has been the subject


of numerous articles (96-104).


Facilitated transport was accomplished in liquid


membranes, in which two aqueous phases were separated by an organic solvent


containing carrier molecules, such as crown ethers.


Diffusion of metal ions in liquid


membranes is governed by the complex formation with the carrier at the aqueous/organic


interface and the selectivities are generally very high.


The fluxes in the membranes are


very low because they are limited by the convection of the carrier in the organic phase


(104).


The biggest disadvantages of using liquid membranes are the low fluxes, the


leaching of the carrier and the poor physical stability.


These problems have prevented


wide-scale application of liquid membranes in industrial separations.

Polymeric facilitated transport has been applied more recently to eliminate liquid

loss. Tsuchida and co-workers have published results based on various metalloporphyrins

cast into polymer films for selective 02 transport (105,106) and N2 transport (107).

Yoshikawa et al. described CO2 transport in these fixed site carrier membranes (108).


Polymeric facilitated membranes have been applied also to ion separations.


For instance,







potassium from sodium and rubidium (97), and potassium from lithium (101).


Facilitated


transport of metal ions resulted in good selectivity with marked improvement in


membrane stability as compared to liquid membranes.


Some other applications include


transport and separation of ethane and ethane through Nafion membranes (109), olefin

(110) and small carbohydrate separation (111).

The first facilitated transport-based system described was that of Scholander (112),

who showed that oxygen diffusion through a filter paper membrane containing a


hemoglobin solution was enhanced.


Oxygen diffusion through a membrane that has been


soaked in methemoglobin, which has no carrier-oxygen binding capacity, showed the

same low diffusion rate that would be expected for simple diffusion of oxygen through


water.


However, in the presence of hemoglobin an additional amount of oxygen is


carried through the membrane due to the hemoglobin-oxygen complex formed in the


The increase in oxygen transport due to the action of hemoglobin as a


carrier is termed the "facilitation effect" (114). Figui

flux pattern for carrier-mediated facilitated diffusion.



Enhanced diffusior


Fl ux


re 1-10 shows a typical nonlinear


1


Facilitation


Effect


Passive diffusion


ria


membrane (113).




26


As can be seen in Figure 1-10, facilitated diffusion occurs at low concentration of


feed solution. Facilitation effect reaches a maxi

carrier molecules which binds the analyte (115).


mum value due to the saturation of


The basic mechanism for this enhanced


transport is a reversible reaction (see equation 1-7) between an analyte molecule A,

which can enter the membrane phase, with a carrier B, which is immobilized on the

membrane (114).


A+B <=AB


(1-7)


In this process, both the chemical reaction and diffusion occur simultaneously in

the system, resulting in an accelerating transport of the permeate species, A, through the

membrane.


Membrane Cross-


Section


Concentration gradient in the
case of facilitated diffusion


Concentration gradient in the
case of passive diffusion


Length


Figure 1-11. Schematic representation of how facilitated transport works.

A schematic explanation of how facilitated transport works is shown in Figure 1-





27


concentration of the immobilized carrier and CAp is the concentration of the permeant A


in the permeate side. According to Fick's


first law of diffusion, the flux of a permeate


molecule across a membrane is directly proportional to the concentration gradient across


the membrane.


One-dimensional representation of the Fick's law (see equation 1-8) has


the following form:


aC
-Dx
3x


(1-8)


aC
In equation 1-8, J represents the flux, D is diffusion coefficient and represents
ax

concentration gradient of a permeate molecule across the membrane. Inside the

membrane the concentration of the immobilized carrier is higher than the concentration


of the permeate molecule in the feed side.


Due to that the concentration gradient for the


permeate molecule that react with the carrier is higher than the concentration gradient of

a permeate molecule that does not interact with the carrier and is transported by passive


diffusion.


This results in an enhanced flux of molecules that interact with the carrier,


compared with those that do not interact.

Single Pore Polymeric Membranes

Ion channels and pores are crucial for functioning of a living organism (116,117).

Channels and pores are the principal nanodevices mediating the communication of a cell

with other cells where ion channels serve as extremely sensitive electromechanical

devices that regulate electric potential, ionic flow, and molecular transport across cellular


membranes (116).


Emulating the function and structure of these natural nanodevices





28


It has been shown that a protein nanopore (e.g.,the a-hemolysin channel), which

is embedded into a lipid bilayer membrane, can function as a biosensor for biomolecules,


for example, DNA (118).


The sensing procedure is based on directing the biomolecule to


the pore by means of an electric field.


When passing through the pore, a biomolecule


brings about its temporary blockage, which is observed as a change in the ion current


signal.


The ion current blockade depends on the structure and chemistry of the


biomolecule (e.g., the DNA sequence) (118), which is the basis of its detection.


biological pore is however quite fragile.


This


A more realistic approach to applying this idea


on an industrial scale would involve replacing the protein channel with a durable,


synthetic nanopore.


Recent research has shown that a single conical-shaped pore


generated in a polymeric foil presents similar transport properties to those of natural


biological channels (119-123).


In these studies, they have prepared model nanoporous


systems of known geometry and chemistry to study the relationship between the structure

and transport properties of nanopores, as well as, creating abiotic analogues of biological


channels.


Such an approach enables one to focus on the basic physical and chemical


phenomena underlying biochannels function.


A special emphasize was given to the family of voltage-gated channels.


current rectification and the dependence of ion current fluctuations on voltage across the


membrane are fingerprints of this type of channel (117).


were prepared by the track-etch technique.


The synthetic pores studied


This technique is based on irradiation a


polymer foil with swift heavy ions and subsequent chemical development of the latent


--







penetrates the foil and produces one latent track (37). Subsequently, one latent track after

chemical development results in the formation of one pore. Counting the number of ions,


which penetrate the foil gives a possibility to prepare membranes with a designed number


of pores.


Controlling the irradiation down to one ion enables preparing a macroscopic


sample containing just one pore.


The Department of Materials Research, GSI


Darmstadt, possesses a unique world wide facility suitable for single-ion irradiation (37).

A membrane with a single pore creates an optimal system for fundamental studies of ion

transport through nanopores, because averaging effects resulting from ion transport

through many pores can be avoided.

To prepare voltage-gated nanopores, an asymmetric pore geometry has been used,

because it was found that biological voltage-gated channels are asymmetric (124-126).

The conically shaped nanopores in polymer membranes were shown to rectify ion current

and exhibit ion current fluctuations of similar statistical properties as the ion current

through biological voltage-gated channels (119,121).

The application of a single conical gold tube membrane to protein biosensing will


be presented in chapter


The steps involved in preparing these membranes are


presented here, and are as follows:

Irradiation with heavy ions

Polyethylene terephthalate (PET) (Hostaphan RN12, Hoechst) and polyimide

(Kapton HN50, Du Pont) foils, having a thickness of 12 jm are irradiated with single


swift heavy ions at normal incidence.


Figure 1-12 shows the chemical formula of PET


anti ltr ntnrn









H
.C-0O--C
II
0 H


H
-C-o-
H


Figure 1-12. Chemical formula of the PET (A) and Kapton (B).

Gold, xenon and uranium ions of energy 11.4 MeV per nucleon are used at the


linear accelerator UNILAC (GSI, Darmstadt).


At this energy the penetration range of


ions in PET foil is larger than the thickness of foils and the energy loss of ions along the

track is well above the energy threshold, which assures a homogeneous etching (127).

Single ion irradiation is performed by defocusing the ion beam and placing a metal mask


with an aperture of 0.3 mm in front of the polymer foils.


The ions pass through the


aperture in a discrete way and as soon as one ion reaches the detector placed behind the

sample, the beam is switched off by a beam chopper within several microseconds.

Ion track etching

Chemical etching of single-ion irradiated foils is performed in a conductivity cell,

connected to a voltage source and picoamperometer (see Figure 1-13).


FI i!-


etchant


stopping
solution







To obtain conical pores, etching is performed only from one side.


The other side


of the membrane is protected against etching by a stopping medium, which neutralizes


the etchant (121,122,128,129).


For etching of PET, 9 M NaOH has been used, therefore


an acidic solution plays the role of a stopping medium.


Ion tracks in Kapton were


developed in sodium hypochlorite with 13 % active chlorine content.


A stopping


medium of 1 M potassium iodide was used, which serves to reduce the OC1"


in etching, to Cf (122,129).


ions, active


The chemical stopping is supported by an electrical one.


The platinum two electrode system is configured in a way that the anode is placed on the


etching side, and the cathode is placed within the neutralizing side (128).


At the very


beginning of the etching process the two halves of the conductivity cell are not connected


with each other and the ion current measured is zero.


When the pore is etched through,


the ion current increases gradually, indicating increase of the pore diameter.


The etching


process is stopped by washing the pore with a stopping medium and water.

The big opening of the pore, D, has been determined by scanning electron


microscopy.


For conical pores in PET, D


- 600 nm and for pores in Kapton D


2 pm.


The difference in D values results from difference in non-specific etching of the two

polymers, the so-called bulk etch rate, which determines the big opening of the pores


(129).


The small opening of the conical pores is below scanning electron microscopy


resolution and its diameter d was estimated by measuring a current-voltage characteristic


of a single nanopore in a standard solution of 1 M KC1.


Assuming an ideal conical shape


of the pore its small opening can be calculated using the following equation (128,122):


4LI


/r 41 <"




32


where L is the length of the pore, K stands for the specific conductivity of the

electrolyte, U denotes the voltage applied across the membrane and I is the ion current


measured.


This etching process gives the possibility of producing pores with an effective


diameter d as small as 2 nm.

Gold electroless plating

The single conical tube membranes are obtained using a template synthesis


method.


Single pore membranes are electroless plated with gold (40), as described


before in this chapter.

Dissertation Overview

The aims of the research presented in this dissertation are to investigate potential

applications of the nanotube membranes in chemical and biochemical sensing and

transport.

Chapter 1 provides background information on the template synthesis method and

two types of templates (porous alumina and polymeric membranes) that are used in this

research.


Chapter


presents the preparation of a biomimetic ligand-gated ion channel


membrane, based on a microbattery/nanoporous system.


This membrane turns on the


battery and attendant ion current in the presence of a targeted chemical stimulus (a


surfactant in this case).


This microbattery was prepared by depositing anode and cathode


materials on either side of a nanoporous alumina membrane.


The pores in the membrane


were made hydrophobic by reaction with an 18-carbon (C18) alkyl silane.


When placed


between two salt solutions, the pores in the Cls-modified membrane are not wetted by




33


membrane causing the biomimetic gate to open, which results in a high flux of ions


through the nanoporous membrane, and consequently, the microbattery turns "on"


Once


"on", the microbattery discharges and the discharging current is collected in an external

circuit.

Chapter 3 presents silica nanotube membranes are used to prepare highly selective


membranes for protein separation.


Two antibodies with different affinities for hevein


have been immobilized on highly ordered porous alumina membranes.


labeled with green fluorescence protein (GFP).


red fluorescence protein (RFP)


monitored.


Hevein was


The transport of both GFP-Hevein and


- which was used as a control analyte- has been


The transport of both proteins has been recorded simultaneously at two


different emission/excitation wavelengths.


As a control experiment, we used membranes


with an immobilized antibody that does not have any affinity towards GFP-Hevein or

RFP. The alumina membranes were prepared by two step anodization method, having


pore diameters between 50 and 100 nm and thickness from 40 to 200 mm.


Both the


influence of pore diameter and the membrane thickness on the transport of GFP-Hevein


and RFP were studied.


These membranes selectively transport the protein (GFP-Hevein)


that binds to the antibody, relative to the other protein (RFP) that has no affinity for the

antibody.

Chapter 4 explores another application of the porous alumina membranes, in this


case, serving as protein microarrays.

microarrays are presented. The first

pre-patterned aluminum surface. In


Two methods of preparing alumina-based


method implies growing alumina membranes on a

the other approach, commercial alumina membranes




34


thickness of the membranes on the fluorescence intensity, and also the capability of these

microarrays to selectively recognize different analytes were studied.


Chapter 5 deals with a new class of artificial ion channels based on a


membrane that contains a single conically shaped nanotube.


synthetic


These nanotube-based


abiotic ion channels exhibit transport properties analogues to voltage-gated biological


channels.


The ion current through a single nanotube fluctuates in time in a voltage-


dependent manner as well as it is rectified. The membrane with a single conically shaped

gold nanotube was prepared by the template method. The nanotube has a large-diameter

opening of- 600 nm and a small-diameter opening of 2 5 nm. In the biosensing


application, the nanotube-containing membrane is placed between the two chambers of a


conductivity cell filled with an electrolyte.


Electrodes present in each half-cell solution


are used to apply a transmembrane potential and measure the resulting ion current


through the nanotube.


The internal surfaces of the nanotube are modified with a specific


biochemical molecular-recognition agent (the "capture" agent, e.g., an antibody) which

interacts specifically with a given biomolecule (the analyte) present in one of the


contacting solution phases.


The binding interaction between the nanotube-bound capture


agent and the solution-phase analyte is transduced as a change in the ion current that


flows through the nanotube.


This new biosensing technology was demonstrated using


both biotin as the capture agent and streptavidin as the analyte, and protein G as the


capture agent and IgG as the analyte.


The detection of a biological warfare agent (ricin)


is also presented.

The results and conclusions of this dissertation are summarized in Chanter 6.












CHAPTER 2
ION CHANNEL MIMETIC SENSOR WITH AN ON-BOARD MICROBATTERY

Introduction

Ion channels are the heart of many biological processes including nerve activity and


muscle contraction.


Channels operate by being either open or closed.


There are several


aspects of the channel environment which affect the channel opening (gating) such as


voltage, a molecular ligand, phosphorylation, or mechanical stimulus (116).


Mimicking


the principles of such natural sensor system is of great importance in sensor development


(130,131).


One example of a natural ligand-gated ion channel is the acetylcholine-gated


ion channel (132), which is closed ("off" state) in the absence of acetylcholine but opens


(and supports an ion current,


"on" state) when acetylcholine binds to the channel.


This


concept of ion-channel mimetic sensing, originally proposed by Umezawa's group (133),


has been of considerable interest in analytical chemistry (134-136).


In the biological


channel there are no electrodes, and the ion current is driven by an electrochemical


potential difference across the cell membrane (137).


That is, the cell membrane has its


own built-in transmembrane power supply that drives the ion current when the channel


opens.


Whether this power supply can be utilized in this way depends on whether the


channel is open or closed.

We describe here the preparation of a biomimetic ligand-gated ion channel


membrane, based on a microbattery/nanoporous system.


To explore this concept we




36


thin-film battery anode onto one face, and a thin-film battery cathode onto the opposite


face, of the membrane.


Hence, in analogy to the naturally occurring channel case, we


have an ion-channel mimetic membrane with a built in electrochemical potential


difference across the membrane.


We show here that in the absence of the ligand (again, a


hydrophobic ionic surfactant), the membrane is in its "off" state, and the electrochemical


potential difference cannot be utilized to drive a transmembrane ion current.


when the ligand is detected, the membrane switches to its "on"


In contrast,


state and the


transmembrane battery discharges producing a corresponding transmembrane ion current.

Experimental

Materials

Octadecyltrimethoxysilane was obtained from Aldrich.

Dodecyltrimethylammonium chloride, hexadecyltrimethylammonium chloride,

dodecylbenzenesulfonic acid, and the nonionic surfactant Triton X-100 were obtained


from Acros Chemicals.


Octyltrimethylammonium bromide was obtained from from


Fluka and N-Dodecyl-N,N-dimethyl-3-ammonio-1-propanesulfonate from Sigma.


Silver


powder 99.9% was obtained from Strem Chemicals and zinc powder (99.33%) from


Fisher Chemicals.


All chemicals were used as received.


MiliQ 18-Mq water was used


for preparing all aqueous solutions.


Commercial porous alumina membranes (-200 nm-


diameter pores, 60 |xm thick) were obtained from Whatman Inc.

Silanization of the Alumina Membranes

A solution that was 5% (v/v) in octadecyltrimethoxysilane (Cis-silane) was

nrenared in ethanol: to this solution was added acetate hbuffer (50mM. nH=5.1 to make




37


from the solution and rinsed with ethanol. The membrane was sonicated for 10 minutes in

ethanol to remove the physisorbed silanes from the surface. The modified membrane was

cured at 1500C in air for 20 min. The performance of the coating was assessed by

measuring a contact angle of 1300 (+80).

Microbattery Fabrication

As shown schematically in Figure 2-1, the anode and cathode of the battery were


deposited as thin films coating the faces of the Cis-modified membrane.


These films


were deposited by thermal evaporation of either Zn (anode material) or Ag (precursor to


cathode material) from a tungsten boat.


depositor was used.


A Denton Vacuum DV-502 vapor-phase


The pressure inside the deposition chamber was -10-5 Torr.


Deposition time was 10 minutes for both the silver and zinc films.


The Ag film was


deposited first, and then a portion at the surface of this film was converted to AgC1,


which acted as the cathode for the microbattery.


This was accomplished by immersing


the silver-coated membrane in an aqueous solution that was 0.1M in FeC13 and 0.3M in


HC1.


The Zn film was then deposited on the opposite face of the membrane.


important to point out that these films are porous and are thus permeable to ions and

molecule present in solution phases that contact the membrane videe infra).















erzmial
evaporation


0.1 MFeCI
0.3 MH-C


evapomation


Cq-ndified alunina


Ag/Cl-ndiified
alurmina


OAAgC 8-lnmdified
alumina


AgClAg/Cqs-mxified
Alurina/Zn


Figure 2-1. Schematic representation of the microbattery fabrication.

Scanning Electron Microscopy (SEM)

SEM was used to study the surface morphology of the anode and cathode films.


Data were obtained using a JEOL 6400 microscope.


Elemental compositions for the


films were obtained using an Oxford energy dispersive spectrometer (EDS) attached to

the JEOL microscope.

Cell Assembly and Battery Discharge Measurements

After deposition of the electrode films, the membrane was sandwiched between


two pieces of Scotch tape that had 0.47 cm diameter holes punched through them.

holes defined the area of the membrane exposed to the contacting solution phases.


These

In


addition, the tape was used to attach a Pt foil lead to the surface of each battery electrode


film in order to make electrical contact with the electrodes.


The membrane was then


mounted between the two halves of a U-tube permeation cell (31,40,43).


Figure


shows a schematic representation of a U-tube permeation cell. The electrolyte solution


I -1 1 "fi 11 fl t *E T /r1A 1 1 fl 1 -


... 1.




39


This was accomplished by injecting the desired volume of a stock surfactant solution into


the 0.1 M NaCI in both half-cells.


The surfactant solutions were also 0.1 M in NaCI.


battery discharge current was monitored using a potentiostat (EG&G model 273)

interfaced to a PC running CorrView and CorrWare software packages (Scribner

Associates, Inc., Southern Pines, North Carolina).


Glass U-cell


Fe
solu





Membrane


ed


tion


Perm eate
solution


Stirring bars


0-rings


Figure


Schematic representation of a U-tube permeation cell.


Results and Discussions

Characterization of the Electrode Films

Surface and cross-sectional SEM images (Figure 2-3) show that both the Ag/AgCl


and the Zn thin films are porous.


particles.


This porosity results because the films are deposited as


The cross-sectional images indicate that these particulate films are -500 nm


thick, and that deposition does not propagate down into the pores.


(The particles seen in


the pores in the cross-sectional images were dislodged from the surface films during







EDS spectra for the Ag, Ag/AgC1 and Zn films are shown in Figure 2-4.


The Ag


film (Figure 2-4 A) shows prominent peaks for Ag and Au; the Au peak results because


the surface of the film was sputtered with Au prior to taking the SEM image.


Much


weaker signals are observed for Cu (from the Cu foil tape used to attach the sample to the


SEM stub) and Al and O (from the underlying alumina membrane).


The upper surface of


the Ag film was chemically oxidized to AgC1, which served as the cathode for the

transmembrane microbattery.


Ag/AgCl film


Zn film


Cross-section


Cross-section


Top view


Figure


Top view


Cross-sectional (upper) and surface (lower) SEM images of the battery


electrode films that coat the faces of the alumina membrane.

After oxidation a prominent Cl peak is observed in the EDS spectrum (Figure 2-4

fn \ rT^ .- ',7 r .. i r*_ I1. A 1 1 A r i._ n


;l~x
ri."$








rue UUCU S *flyrt


LS ^*^|*t ,^;,^ &^


2 ... 4 -'.1 E 8 10 12
*~~~~~ ~ ~ i f i ihi kk AA Jw^f V


I~ *..i ..,
-6 *.t-=i -.


I IIIIIIII ..yr:I..lllllL 461111 5!1~(~1'1 a':.11'11.'. : 8 2
.. .. ] 1.~ :I B :2
r -


Figure 2-4. EDS spectra of the membrane surface after deposition ofAg (A) and after
conversion of the Ag surface to AgCl (B). EDS spectrum of the opposite
membrane surface that had been coated with Zn (C).


Battery Discharge Experiments


Control experiments were first conducted with membranes that were not modified


with the hydrophobic Cis-silane.


As described above, a Zn anode film was applied to one


face of the membrane and a Ag/AgCl cathode film was applied to the opposite face.


membrane was mounted in the U-tube cell, and the electrode films were connected to the


leads of the potentiostat.


However, the half-cells were initially devoid of electrolyte


solution, and as a result, there was no ironically conductive pathway through the


r_ Jr- C "- ....
O~~ ~ ~~~~~~~~ ~ .': 2 ,jf .;i"li~ ":i I:







NaC1) was added to both half-cells.


Because the untreated alumina membrane is so


hydrophilic, electrolyte immediately flooded the pores, allowing for ionic conduction


between the anode and cathode films.


This allowed the transmembrane microbattery to


discharges via the following discharging half-reactions:


Zn -- Zn2+

2AgCl+ 2e


= 0.763 V

= 0.222 V


-> 2Ag+2C1-


(2-1)

(2-2)


As indicated by Eo values, this battery delivers almost 1 V


As shown in Figure


A the current raises immediately to a peak value of -250 pIA and then decays away with


time.


Before this experiment, the face of the membrane coated with the AgCI cathode


film was dark purple in color due to the AgC1.


After this experiment this face of the


membrane was white, indicating that all of the AgCl had been reduced during the battery


discharge.


This explains why the current ultimately decays to zero (Figure


An analogous experiment was conducted with a C1i-modified membrane that had


the Zn anode and AgCl cathode films on its surfaces (Figure


electrolyte was added to the half-cells at t


In this case,


However, the current obtained is at the


noise level of the potentiostat, indicating that battery discharge is prevented.


As shown in


our prior work, this is because the hydrophobic pores are not water wetted (138), and as a


result there is, again, no ionic-conduction pathway through the membrane.


These results


show that when the hydrophobic microbattery membrane is exposed to NaCl solution, the

membrane is in its "off" state, and transmembrane battery discharge is prevented.










0 0003


0 0002


E 00001


0


-0 0001


A



C-





! i i -.


-5e-10


Tune (Sec)


[.iI lIE lhl hl liUllUIMIIII




S000 3000
1000 2000 3000


Time (Sec)


Figure


Current-vs.-time response for the transmembrane microbattery applied to an
alumina membrane that was not rendered hydrophobic by silane


functionalization (A).


Analogous current-vs.-time response for the


hydrophobic C18-modified membrane (B).

Figure 2-6 shows current-vs.-time data for the C18-modified membrane before and


after injection of dodecylbenzene sulfonate (DBS) into the half-cell solutions.


injection of DBS, t


Prior to


< 200 s, the membrane was again in its "off" state, and battery


discharge was prevented.


=200


s, DBS was injected to make the DBS concentration


in both half-cells 1 mM.


After injection there was an induction period followed by a


time region in which a low-level discharge current (-1.5 gA) was observed (inset Figure


2-6).


This low-level discharge current flowed for 1300 s, after which a burst of current,


at a much higher level was observed.


Analogues results were obtained for C18


membranes upon exposure to the cationic surfactant dodecyltrimethylammonium (DTA).

These results are in many ways similar to results obtained in our prior

investigations of the effect of DBS on the ionic resistance of the C18-modified alumina


membrane (138).


First, when 0.1 M KCI was present in both half-cells, without added


..




44


membrane resistance to decrease, but still the resistance remained high (> 20 MO).

When the DBS concentration reached 10 jiM a precipitous 4-order of magnitude drop in


resistance was observed.


The key point is that two "on" states were observed a high-


resistance "on" state at low concentrations of DBS followed by a sharp transition to a

low-resistance "on" state at higher concentrations of DBS.

We showed that the sharp transition from the high-resistance "on" state to the low

resistance "on" state is associated with flooding of the pores with the electrolyte solution


(138).


That is, at some critical solution-phase concentration of DBS, the quantity of DBS


partitioned into the membrane is sufficiently high that the pores are no longer


hydrophobic, and water cannot be prevented from entering the pores.


In this flooded


state charge is carried through the membrane by migration of ions in the solution-filled


pores.


At lower DBS concentrations, the ionic current is presumably carried by surface


migration of the DBS and attendant counterion along the pore walls in pores that are


devoid of water (138).


This accounts for the high resistance of this "on" state.


In the transmembrane microbattery experiments described here, after injection of

DBS into the electrolyte solutions, DBS must diffuse through the porous electrode films


videe infra) and then into the hydrophobic pores.


The two "on" states observed


previously (138) are analogous to the two current-levels observed here.


The low current


"on" state (e.g., inset Figure 2-6) is associated with surface migration in pores devoid of

water, and the sharp transition to the higher current "on" state is associated with flooding


of the pores with water and electrolyte. As be:

some critical level of DBS into the membrane.


fore, flooding occurs when diffusion brings

Finally, the induction period prior to the





45


in the membrane such that a discharge current above the detection limit for the

potentiostat can be supported.


0.0005


0.0004


0.0003


0.0002


0.0001


0


-0.0001


1000 2000 3000


Time (Se


Figure 2-6.


Current-vs.-time response for a hydrophobic membrane before and after


injection of DBS surfactant solution.

After injection, the DBS concentration in both half-cells was 1 mM. The timescale

of this induction process, however, seemed long; e.g., in Figure 2-6 it takes in excess of


1300


s before the critical membrane level of DBS is achieved.


This suggests that there is


some barrier to transport of DBS into the membrane.


The most likely source of this


barrier is diffusion of DBS through the battery electrode films on the surfaces of the


membrane.


To explore this issue we attempted to make thinner electrode films; however,


because of the particulate nature of these films, the lateral electronic resistance of these

thinner films was too high, and battery discharge was not observed.







used above) were then thermally evaporated onto these Au films. In essence, the Au

films act as current-collectors for the overlying battery electrode films. We found that


the induction times for these thinner battery electrode films were shorter than for thicker


films.


For example, with the 1 mM DTA solution a membrane with the thinner battery


electrode films showed a response time of 400


s as opposed to 1000


s for the membrane


with the thicker films.


These results show that transport of surfactant through the battery


electrode films is a kinetic barrier in this system.

Effect of Surfactant Concentration on the Response Time

The response time of this device is defined as the induction time period between

injection of surfactant into the half-cell solutions and observation of the low current "on"


state.


Over the concentration range 0.01 mM to 1 mM, the response time is inversely


proportional to the solution-phase DBS concentration (Table 2-1).


This result is


consistent with our model that the response time is associated with transport of DBS


through the electrode films and into the pores of the membrane.


Higher DBS


concentrations yield higher concentrations at the membrane solution interface and thus


higher net fluxes into the membrane.


As a result, the time required to achieve a


concentration of DBS in the membrane sufficient to support the low current "on" state

decreases with increasing solution-phase DBS concentration.


Table 2-1.


Effect of DBS concentration on the response time.


DBS Concentration (mM) [ Response time (s)
2 350
1 1.5
0.1 52
0.01 70








Table


2-2 shows that analogous results are obtained for the cationic surfactant


DTA; however, at both the 0.01 and 0.001 mM levels the response times for DTA are


about a factor of three times higher than for DBS.


These results also fit our diffusional-


transport model because the diameter of the DTA head group is larger than the diameter


of the DBS head group -3.7 nm vs.


The larger diameter for the DTA


head group makes the surface diffusion coefficient smaller, and as a result the diffusional

transport time longer.


Table


Effect of DTA concentration on the response time.


When the solution-phase DBS concentration is increased to


mM the response


time goes up again, indeed, to a value higher than is observed for the lowest DBS


concentration (Table 2-1).


While analogous results are obtained for DTA, the


concentration producing the longest response time (1 mM, Table 2-2) is lower than for


DBS.


Our initial hypothesis was that these longer response times at the highest surfactant


concentrations were in some way associated with micelle formation; however, the critical

micelle concentrations (CMCs) for DBS and DTA are 1.1 mM (140) and 4.4 mM (141),


respectively.


Hence, while the concentration that yields the longest response time for


DBS (2 mM) is above the CMC, the concentration that yields the longest response time


for DTA (1 mM) is below the CMC.


It is not yet fully understood why the response time


II i i i i -


DTA Concentration (mM) Response time (s)
1 1000
0.1 140
0.01 216
0.001 600


-2.0nm(13 9).




48


Investigations of Alkyl Chain Length on the Response Time

During the investigations of hydrophobic alkyl thiol-modified gold nanotube

membranes it was shown that the transmembrane flux increases with the hydrophobicity


of the permeate molecule (44).


This is because the flux is directly proportional to the


partition coefficient for the permeate molecule at the membrane/feed-solution interface


(Equation


in reference 44).


The same principle should apply for flux of hydrophobic


surfactant molecules into the C18-modified alumina membranes studied here. As a result,

response time should decrease with increasing hydrophobicity of the surfactant. To


explore this issue we investigated response times for three alkyl trimethylammonium


surfactants (Table 2-3).


In agreement with the above analysis, response decreases with


increasing hydrophobicity alkyll chain length) of the surfactant.


Table


Effect of alkyl chain length in alkyl trimethylammonium surfactants on the
response time. Concentration in all cases = 1 mM. These results were


obtained using the C18-modified membrane with thinner battery electrode
films.
Number of carbons in alkyl chain Response time (s)
8 >3600
12 400
16 5


Conclusions

It has been shown in this work that a microbattery /nanoporous membrane acts as a

biomimetic "smart membrane" in the sense of emulating the function of ligand-gated ion

channels; i.e., they can be switched from an "off" state to an "on" state in response to the

presence of a targeted chemical stimulus. Modifying the aluminum oxide with long chain


alkylsilanes makes the membrane pores hydrophobic and the microbattery


is "off'


. In the




49


response time of the system: the hydrophobicity of the analyte (shorter response time for

more hydrophobic analytes), the nature of the polar head group of the analyte (anionic

surfactants are sensed faster than the cationic ones) and the concentration of the analyte

(shorter response time for lower concentration). This concept could ultimately lead to a

remote sensing technology where the battery discharge current is use to drive a device

(e.g., a buzzer) that signals to the outside world that the ligand has been detected.













CHAPTER 3
HIGHLY SELECTIVE ANTIBODY-BASED NANOTUBE MEMBRANES FOR
PROTEIN SEPARATION

Introduction

Many technically challenging and commercially attractive separation problems can

not be solved with existing membranes because the typically achieved separations of


complex mixtures are only fractionation into substance groups (142).


Membranes with


high selectivities for example for chiral drugs, toxins or complex biomolecules are


required.


The aim of current membrane development is preparing "tailored" membranes


with high selectivity and/or high flux of the analytes of interest across the membranes;

this can be achieved by developing membranes modified with molecular recognition


elements, with high pore density and a narrow pore size distribution.


Active research is


devoted to highly specific membrane separations based on molecular recognition inside

the nanoporous membranes (47,82,152).

We report here a protein separation method based on facilitated transport

selectivity, that utilizes immobilized molecular recognition elements in a porous alumina


membrane.


We found that by modifying the walls of the alumina membrane pores with


antibodies, proteins that have an affinity towards these antibodies are transported at a


higher rate than proteins that do not interact with the antibodies.


We used two Fab


fragments (1C2 and 1A4) of antibodies that were grown against the protein hevein; 1A4


- ~ -~ -..




51


Hevea Brasiliensis involved in the inhibition of several chitin-containing fungi (144,145).

Hevein was produced as a green fluorescence protein (GFP) fusion protein (GFP-Hevein)


in insect cells (

spectroscopy.


143).


In this way GFP-Hevein can be detected by fluorescence


Red fluorescence protein (RFP) was used as a control protein because it


does not have any affinity towards any of the antibodies. Because their excitation and

emission spectra do not overlap (XexGFp=395 nm, XemGFP=510 nm, hexRFp=563 nm,

,emRFp=582 nm), GFP and RFP are very well suited for dual-label experiments (146).

Experimental

Materials

The antibodies ENA 11 His, 1A4 and 1C2 Fab fragments were provided by VTT

Biotechnology, Finland. Red fluorescence protein (rDsRed2 protein) was purchased from


BD Biosciences Clontech.


High purity aluminum foils 100 mm x 500 mm x 0.2 mm,


purity 99.9998%) were obtained from Alfa Aesar, tetraethyl orthosilicate (TEOS) from

Sigma Aldrich and triethoxysilylaldehyde from Gelest.

Fabrication of the Nanoporous Alumina Membranes

We used a two-step anodization method (52,53) to fabricate the porous alumina


membranes.


Briefly, the aluminum foils were first electropolished at 15 V in a solution


with the following composition: 95 wt. % H3PO4, 5 wt. % H2S04 and 20 g/L CrO3.


solution was heated at 70 OC.


The polished aluminum foil was anodized at 40, 50 and 70


V to obtain membranes having 50, 70 and 100 nm pore diameter, respectively.


We used


5% oxalic acid as the electrolyte solution and the anodization experiments have been


done at 0 C.


The first film of the membrane was dissolved away in an aqueous solution







highly ordered nanoporous alumina membranes.

was dissolved into a saturated HgCl2 solution. 1


The aluminum that was not oxidized


'hen the barrier layer of the alumina


membranes was removed in 5% H3P04 solution.

Scanning electron microscopy was used to measure the pore diameters and the


thicknesses of the alumina membranes prepared.


A JEOL FE-SEM 6438 was used.


Alumina nanoporous membranes (Figure 3-1) were used as templates for immobilization

of the antibodies.


Figure 3-1. Scanning electron micrograph of a porous alumina membrane with pores of
50 nm in diameter and pore density of- 1010 pores/cm2.


Antibody Immobilization

Figure 3-2 shows a schematic representation of the modification steps involved in


antibody immobilization.


Silica nanotubes were deposited inside the pores of the


alumina membranes using a sol-gel method (81.84).


Briefly. a sol-gel silica precursor








was allowed to hydrolyze for 30 minutes.


Alumina membranes were than immersed into


the sol-gel for 1 minute under sonication, after which they were air dried for 10 minutes


at room temperature and cured in the oven for 12 hours at 1500C.


Triethoxysilylaldehyde


has been used to attach aldehyde terminal groups onto the pores of the membranes.


free amino sites of the antibody Fab fragments react with the aldehyde groups via a


Schiff base chemistry (147,176,177).


The aldehyde-modified silica nanotube membranes


were incubated for 12 hours at 4 OC in a solution containing 0.2 mg/ml antibody Fab


fragments solutions.


All solutions of the antibody Fab fragments, GFP-Hevein and RFP


were made in phosphate buffer saline (PBS) solution having pH=7.4.


After washing


them with PBS, the antibody-modified membranes were incubated for 3 hours in a

blocking solution containing 1% bovine serum albumin (BSA) and 1% Tween-20 in PBS.

Blocking solution was used to block both the unreacted aldehyde groups and nonspecific


adsorbtion.


The membranes were washed copiously with PBS afterwards and stored in


PBS at 40C until used in transport experiments.


--OH
- OH
--OH
--OH


OMe


-d


H

Si H


Surface of the
silica nanotube
membrane




54


Transport Experiments

The antibody-modified silica nanotube membranes were sandwiched between two


pieces of Scotch tape that had 0.314 cm2 area holes punched through them.

defined the area of the membrane in contact with the solution phases. The


These holes


membranes


were then mounted between two halves of a U-tube permeation cell (40,43,44,148). The

feed solutions had equal concentrations in GFP-Hevein and RFP. A volume of 3 ml PBS

was used on both halves of the permeation cell. The rate of transport (flux) was

determined by periodically measuring the fluorescence intensity of the permeate solution


using a Varian Cary Eclipse spectrofluorometer.


GFP-Hevein and RFP were detected


simultaneously.

Results and Discussions

Effect of Antibody Affinity on Selectivity Coefficient

Transport plots in Figure 3-3 show the number of picomoles of GFP-Hevein and


RFP transported through the nanotube membranes versus the permeation time.


A single


membrane was cut into three pieces and they were modified with ENA 11 His Fab

fragments (Figure 3-3A), 1C2 Fab fragments (Figure 3-3B) and 1A4 Fab fragments


(Figure 3-3C) respectively. The membrane used for these experiments had pores 70 nm

in diameter and a thickness of 90 upm. A concentration of 10 nM in both GFP-Hevein


and RFP in PBS was used in feed side, with PBS only in the permeate side.


Due to the


fact that ENA 11 His does not have affinity for either GFP-Hevein or RFP, membranes


modified with this antibody were used for control experiments.


As can be seen from


Figure 3-3A RFP is transported by passive diffusion at a higher rate than GFP-Hevein,









28,000 Da (149,150) and Hevein has a molecular weight of 4,000 Da (151).


When the


antibody having an affinity towards Hevein (1A4 or 1C2 Fab fragments) was


immobilized, the membranes transported GFP-Hevein at a much higher rate (Figure 3-3A


and 3-3B) than they transported RFP.


SGFP-Hevein
---RED


0 500


1000


1500


Time, min


---GFP-Hevein
-U-RED


0 500


1000


Time, min


KU-RED


-~--------x--------V


1000


Time, mn.


1




56


Because 1A4 and 1C2 Fab fragments bind hevein, these data suggest that

immobilization of these antibodies facilitates the transport of GFP-Hevein versus RFP.

The transport of GFP-Hevein through the membranes is not linear in time because the

concentration gradient decays with time, so the driving force for diffusion decays as well.

Due to that, the fluxes of GFP-Hevein and RFP through the membranes were calculated


with respect to the linear part of the transport plots (the first two points of the plots).


defined a selectivity coefficient for a membrane, s, as the ratio between the flux of GFP-


Hevein and the flux of RFP.


Figure 3-4 shows the influence of the type of the antibody


immobilized on the selectivity coefficient.


21.5


.-~*.* 1*,
*I..
.---


ENA


1A4 ...


*C~i'iiU
A.'~;I~~


Figure 3-4. Effect of the antibody immobilized on the selectivity coefficient.

As can been observed from Figure 3-4, immobilization of an antibody with higher


affinity towards the analyte yields a higher selectivity coefficient.


Immobilization of an


antibody of high binding affinity towards an analyte, results in increase of the analyte


*^*




57


Effect of the Feed Solution Concentration on the Flux and Selectivity Coefficient

An important parameter in characterizing facilitated transport of the molecules

through membranes is the feed solution concentration. A plot of flux versus feed


concentration should have a "Langmuirian" shape (47,82,152).


We investigated the effect


of the feed solution concentration on fluxes of GFP-Hevein and RFP (Figure 3-5). In

these experiments the membranes were modified with 1A4 Fab fragments and they had

pores of 70 nm in diameter and 90 mrn thickness.


55 60 65 70 75 80 85 90 95 100


Feed Concentration, nM


Figure


Plot of fluxes of GFP-Hevein and RFP versus feed solution concentration.


The plot showed in Figure 3-5 has a Langmuirian shape for GFP-Hevein.


It can be


observed that at high feed concentration the membrane transports RFP at higher rates


than GFP-Hevein.


At high feed concentration (100 nM), passive diffusion is


predominant. Facilitated transport theory also predicts that the highest selectivity


'^'~~^"""""~'~~l~l""""""~~~~~ 1"11~~-'~""'~~~~




58


plots of GFP-Hevein and RFP through a 1A4 antibody-modified membrane when using


nM (A), 20 nM (B),


0 nM (C) and 100 nM (D) feed solution concentration.


--Fi


8


-p-


TnU% nsi
~1GOD0
Trmmn


Tnt nin


D




I--FD
II!


flUw
TrIP 11*1


Tm uu nit


Figure 3-6.


Transport plots of GFP-Hevein and RFP through a 1A4 antibody-modified


membrane when using


nM (A), 20 nM (B),


50 nM (C) and 100 nM (D) feed


solution concentration.

These transport plots were used to calculate the selectivity coefficient (Figure 3-7).


Indeed the selectivity coefficient decreases as the feed solution increases.


nM feed


solution concentration a selectivity coefficient of 30.6 is obtained, and for 100 nM feed

solution concentration we obtained a value of 0.7 of the selectivity coefficient, which

corresponds to massive diffusion of the proteins.


B


C

















10
5
0

50
30

Feed Concentration, nM


Figure


Variation of the selectivity coefficient with feed solution concentration.


Effect of the Pore Diameter on the Flux and Selectivity Coefficient

The diameter of the pores of the alumina membranes is another important

parameter that influences the flux of the proteins and selectivity coefficient of a


membrane.


Figure 3-8 shows the transport plots obtained when membranes with pores of


50 nm (Figure 3-8A), 70 nm (Figure 3-8B) and 100 nm (Figure 3-8C) in diameter were


used.


The membranes with pores of 50 nm and 70 nm in diameter had thickness of 80


jtm and 90 am respectively, and were modified with 1C2 Fab fragments.


The membrane


with pores of 100 nm in diameter had a thickness of 50 pm and was modified with 1A4


Fab fragments.

RFP has been us

(Figure 3-9). Th


In all cases a feed solution concentration of 10 nM in GFP-Hevein and

;ed. The selectivity coefficient decreases as the pore diameter increases

re increase in selectivity coefficient is obtained at the cost of lowering the




60


means that when using membranes with this pore diameter, facilitated transport is not

predominant; only passive diffusion is observed at high pore diameters.


A



I -CGFP-He'\ei


Time, min


B


-4-GFP-He\ein
-u-RED


Time, min.


--GFP-Hewin
---RED


0


1500


Time, min











18
16
14
12
10


r
I.!--


50 nm 70 nm 100


Figure 3-9. Selectivity coefficient variation with the pore diameter.



Conclusions

Highly selective nanotube membranes for protein separations have been prepared.

The separation is based on molecular recognition inside the nanopores of alumina


membranes.


We have used antibody Fab fragments which as molecular recognition


elements selectively bind and transport proteins.


There are important parameters that


should be taken into account in obtaining a desired protein separation with certain fluxes


and selectivity coefficients.


These parameters are: binding affinity between the antibody


and the antigen, feed solution concentration, pore diameter of the membrane and


membrane thickness.


A higher binding affinity is desired because it leads to a higher


selectivity; although a very high binding affinity is not appropriate because the analyte


should be released from the antibody and transported through the membrane.


Higher


selectivity coefficients are obtained at lower feed solution concentration and when using




62

however, lower fluxes are obtained. High fluxes are important in separation processes;

higher fluxes can possibly be obtained by decreasing the membrane thickness, by

applying pressure (153) or by applying an electric field across the membrane (154).












CHAPTER 4
3-D POROUS ALUMINA-BASED MICROARRAYS

Introduction

Microarray technology is an emerging technology which is having a considerable


impact in proteomic research.


Protein microarrays allow the identification and


quantification of a large number of target proteins using a small amount of sample within


one single experiment (155 ).


assays.


This technology requires rapid, high throughput protein


Recent studies showed that protein microarrays can be used to screen for protein-


protein interaction (156,157), antibody specificity profiling (158,159 ), immune profiling

(160), and protein-small molecule interactions (161).

Significant challenges exist for protein microarrays which do not exist for gene


arrays (155,162,163,164).


The initial challenge is developing a system capable of


detecting a broad range of concentrations; proteins can exist in a very broad dynamic


range (up to 1010) in any cell.


The second challenge is detecting very low abundance


proteins; for DNA, PCR methods exists for amplification, while for proteins no


amplification method is available yet.


DNA is a very uniform and stable molecule (it


does not lose its activity when stored dry), with a well defined activity prediction based


on primary nucleotide sequence.


These factors are different for proteins.


Proteins exhibit


very diverse individual tertiary molecular structures; further, their 3D structure is

important for their activity, they should always be kept wet to avoid denaturation.







hydrogen bonds, hydrophobic or Van der Waals interactions.


In addition proteins may


have multiple binding sites and can possibly interact with different molecules in the same

time.


Because of these challenges, substrate requirements are more demanding for


protein microarray technology.


Various types of substrate have been explored (165,166)


and the search for new supports with superior performances is still a challenge. There

have been reports on the spotting of protein microarrays using a variety of surfaces and

immobilization chemistries, including but not limited to agarose (167), polyvinylidene


difluoride (168), and polyacrylamide gel pads (169).


Proteins arrays on glass surfaces


coated with aldehyde (161), poly-L-lysine, and gold surfaces derivatized with SAMs


(170) have been reported also.


Application ofnanoporous silicon as support for protein


microarrays has been recently reported (171).


Three dimensional porous surfaces offer


several advantages over the flat surfaces, including higher sensitivity due to the higher

sample loading capacity, broader dynamic range of concentrations and a 3-D

environment that preserves protein activity and accessibility.

Here we report two methods of fabrication of 3-D porous alumina-based


microarrays and show their applications in antibody specificity screening.


Besides the


advantages offered by a 3-D support for microarrays, alumina membranes present a very

well defined morphology, which is important for uniform immobilization of the proteins

and providing reproducible detection of the ligand-binding events.

Experimental


Materials





65


Chemical Technologies, and triethoxysilylbutyl aldehyde from Gelest. Triton X-100,

tetraethylorthosilicate (TEOS), rhodamine B isothiocyanate, human and mouse IgG, anti-

human IgG labeled with Alexa 488 and anti-mouse IgG labeled with Alexa 594 were


purchased from Sigma Aldrich.


Surface coating polymer FSC-M was obtained from


Shipley and polymer remover (remover 1165, Shipley) was purchased from MicroChem.


All the materials were used as received. The TEM copper grids (400 mesh, PELCO) that

were used as masks were purchased from Ted Pella. The porous alumina membranes that


were used for the second method were bought from Whatman, and they had a nominal


pore diameter of 200 nm.


(Cranston, RI).


Silver plating solution (Ag 1025) was purchased from Technic


Silver wire (2 mm thick) were purchased from Alfa Aesar (Ward Hill,


MA).

Fabrication of porous alumina microarrays

Method 1


High purity aluminum foil was first glued to a glass by using an epoxy glue.


Then


the Al foil/glass plate was electropolished into a solution composed of 95 wt. % H3P04,


wt. % H2S04 and 20 g/L Cr03, heated at 70 OC.


Al foil/glass was washed with distilled


water and dried under vacuum at room temperature.

Figure 4-1 shows a schematic representation of the first method of fabrication of


the porous alumina microarrays.


There are four steps involved in this procedure and they


are as follow:


Step 1.


The electropolished Al foil/glass was first spin-coated with a surface


cnatinp nnlvmer (FSC-MV


From the SEM measurements we found that the thickness of







The polymer/Al foil was then inserted into a reactive ion etching apparatus


(Samco Plasma Ion Etching System, model RIE-1C). The pc

for 5 seconds in order to make the surface hydrophilic. This

oxygen plasma with radio frequency (13.56 MHz) of 140 W.

20 Pa oxygen and oxygen flow rate was 30 seem. Copper gr


)lymer surface was etched

was accomplished using

The plasma pressure was


ids (400 mesh) were placed


on top of the polymer with a dilute Triton X solution, which is a wetting agent, and

ensures the copper grid was stick flat to the surface after drying.


Step 3.


The plate with copper grids was etched for 4.5 minutes and then the copper


grids were blown away.


In this way, we obtained Al surfaces patterned with the coated


polymer.


Cu grid
Polymer
Al foil
glass


02 plasma etching


Cu grid removing


Electrochemical
anodization of Al


Step 2.







Step 4.


The patterned Al/glass system was electrochemically oxidized to form


porous alumina films, only in the areas where the Al was exposed.


The anodization was


carried out in 5% oxalic acid as electrolyte, at 00C, under a constant voltage of 50 V.

In a similar way, patterning of anodic alumina into aluminum was reported (172).

In this case, the aluminum was patterned with silica either by a sol-gel process or by


dielectric evaporation.


In the first case they reported the presence of cracks at the


interface between aluminum and alumina, and in the second case they observed the

growth of tilted pores underneath the silica layer.

Method 2

Figure 4-2 shows a schematic representation of the steps involved in fabrication of


the alumina microarrays by method


A thin Au-Pd layer (approximately 90 nm in


thickness) was sputtered on one side of the alumina membrane.

performed using a Denton Vacuum Desk II Cold Sputter. The


seed layer for electroplating.


Au-Pd sputtering was


Au-Pd layer was used as a


Commercial alumina membranes having 60 atm in


thickness and 200 nm pore diameter were used.

Au-Pd sputtered alumina membrane. Another


A copper TEM grid was placed on top of


mask (aluminum foil) was placed on top


of the copper grid just to have enough Au-Pd material for making the electrical contact.

This assembly was then inserted into the center of the vacuum chamber of a reactive ion

etching apparatus (Samco Plasma Ion Etching System, model RIE-1C) and Ar plasma


was used to etch the Au-Pd seed layer.


The Ar plasma parameters were as follows: 10


mmins, 13.56 MHz, 140 W, 10 Pa Ar, Ar flow rate = 12 sccm.


After etching, an Au-Pd


replica of copper grid was transferred to the membrane.








1Agon etchng


' F 1!


Polymer
spin coating


Cu grid

Au-Pd layer

Alumina membrane


~:~" x~ "4"" E":; <0'""
0*:": *" ::
A>r -
0x" 0"
~a,,.,~: ~0 -42E:pr


Silver
electrodeposition


Polymer
removing


Figure 4-2. Schematic representation of the microarray fabrication by method


Electroplating was accomplished using a EG&G PAR Model 273


galvanostat/potentiostat which was controlled using a CorrWare software package


(Scribner Associates, Inc., Southern Pines, North Carolina).


Electrochemical cells were


prepared from a Teflon cell (17 mm inner diameter) and stainless still plate, which were


held together using screws and o-rings (see Figure 4-3).


To electrodeposit


Ag into the


membrane, the membrane was placed on Teflon tape, Au-Pd sputtered layer side up.


Electrical contact was made to the membrane using copper adhesive tape.


A silver wire


was used as the counter electrode.


Ag was then deposited at


-2 mA cm-


for 8 minutes,


Silver
electrodeposition
.
.', "* ^ *




69


layer to prevent the leakage of plating solution through the membrane and suppress the


lateral growth of the electrodeposits.

electrochemical cell again. In this c;

the open pores faced up. Additional


for 90 minutes.


The spin-coated membrane was place into the


ise, the Ag electroplated layer was side down so that


Ag was then plated into the membrane at -0.50 mA


After electroplating, the membrane was immersed into spin coating


polymer remover for 10 minutes, rinsed with ethanol, and dried at room temperature.


Figure 4-3.


Electrochemical cell setup for silver electrodeposition: A, Ag wire counter


and reference electrode; B, Ag plating solution; C, Cu foil; D, Au-Pd modified
alumina membrane as working electrode; E, stainless steel plate; F, teflon
tape; G, O-ring seal.

Membrane modification for sensitivity studies

For sensitivity experiments, five membranes with 0.5, 1.2, 50, 60 and 90 pm


thickness have been prepared.


They were prepared by electrochemically oxidation of


aluminum, using the two step anodization method (52).


Briefly, high purity (99.9998%)


aluminum foils were electropolished at 15 V in a solution with the following







oxalic acid as the electrolyte.


The anodization was conducted at 00C, for 15 hours.


first film of the membrane was dissolved away in an aqueous solution that was 0.2 M in


CrO3 and 0.4 M in H3PO4, at 60-70 OC.


The second anodization step was carried out in


exactly the same conditions (referring to the voltage applied and the electrolyte solution


used) as the first step.


The time of the anodization in the second step varied for the five


membranes from 20 minutes to 16 hours, resulting in formation of highly ordered

nanoporous alumina membranes having pore diameter of 75 nm and thicknesses between


0.5 and 90 jrm.


The aluminum that was not oxidized was dissolved into a saturated


HgC12 solution, except for the case of 0.5 and 1.2 jpm thick membranes due to their more

susceptibility to fragment into the small pieces.

A sol-gel template synthesis method was used to deposit silica nanotubes (with a


wall thickness


- 3 nm) within the pores of the alumina films (173,174 ).


First, a sol-gel


silica precursor was prepared by mixing absolute ethanol, TEOS and 1 M HCI (50:50:1).


This solution was allowed to hydrolyze for 30 minutes.


Alumina template membranes


were than immersed into the sol-gel for 1 minute under sonication, after which they were

air dried for 10 minutes at room temperature and cured in the oven for 12 hours at 1500C.

The inside walls of the silica nanotubes were reacted then with APTES, a silane with an


amino terminal group.


The silica nanotube membranes were immersed into an ethanol-


based solution which contained 6% APTES and 6% pH 5.1 acetate buffer solution.


membranes were kept in solution for 10 minutes under vacuum followed by 20 minutes


in ambient air at room temperature.


They were dried under nitrogen and cured at 120-


~. A -~ -~ -- -








The amino modified silica nanotube membranes were immersed in a solution of 1 %


(wt) rhodamine B isothiocyanate in DMF for 16 hours in the vacuum, under nitrogen.

The rhodamine B modified membranes were washed in DMF, chloroform and ethanol.

The washing was performed for 10 minutes under sonication in each solvent.


APTES
3-aminopropyltrimethoxysilane


H2N




H3CH2CO -S-
H3CH2CO/ >OCH2CH3


RHODAMINE B
ISOTHIOCYANATE
, = 570 nm X = 595 nm


CHCH N


CH2CH3


+ CH CH
N


CH2CH


--OH
-OH
-OH
-OH


--NH2


Silica Nanotube
Membrane


--4


_-Os
r-CT


NHC/
I
S


Figure 4-4. Modification steps for sensitivity studies.

As a control experiment we modified a piece of glass with rhodamine B in the same


conditions as the alumina membranes.


The glass was initially cleaned in a piranha


solution (3:1 H2SO4:30% H202) at 900C and washed copiously with deionized water.

Fluorescence spectra of the alumina membranes and glass modified with

rhodamine B were taken using a Zeiss fluorescence microscope. The Rhodamine B dye

was excited using 570 nm light and the emission was monitored using a 590 nm band


pass filter.


The dye was excited while simultaneously monitoring the emission with a


I


bH





72


Microarray modification for selectivity studies

The alumina microarrays made by method 2 were used to investigate their


selectivity, in terms of screening for antibody specificity.


Again, a silica thin film was


deposited on the pore walls of alumina membrane-based microarrays.


These were


immersed into a ethanolic solution that was 5% in an aqueous acetate buffer with a pH of


5.1, and 5% in triethoxysilylbutyl aldehyde.


The aldehyde groups react readily with the


primary amines on the proteins to form a Schiffs base linkage (176,177).


This approach


was used to covalently attach the capture proteins, which in this case were human and

mouse IgG's.

The proteins were spotted on the alumina microarrays using a 10 X microscope


connected to a monitor, and a manual microinjection system (Brinkman,


A volume of 10 jiL of protein solution (0.2 mg/ml in PBS pH=


Westbury, NY).


.4) was back loaded into


a femtotip (Fisher Scientific, Pittsburgh, PA) and a compensation pressure of 50 psi


applied.


The tip was positioned using a micromanipulator until the tip touches the


alumina surface.


Due to the porous nature of the alumina, the dye is pulled into the


islands through capillary action without the need for addition pressures.


Once the surface


was saturated with protein solution the tip was reposition to another spot and filled in a


similar manner.


After 12 hours incubation at 40C, the arrays were immersed into a


blocking PBS buffer solution that contained 1% BSA and 0.1 % Tween-20 for 3 hours.

This step is necessary not only for blocking the unreacted aldehyde groups, but also for


reducing the non-specific adsorption of the proteins (161).


After washing thoroughly


tta+1, Df ld V~nr rln ni-nrn'd : ,r ,.nraltn ;nn *k~O n~nn~ n nalun an nnn~nrnn a~~n +b +nca nr







Alexa 594 dye, both having a concentration of img/ml in PBS).


After 12 hours of


incubation, the arrays were washed three times with PBS and then twice with deionized

water.

Fluorescence microscope imaging was performed in order to evaluate the


selectivity of the alumina-based microarrays.


The Alexa 488 dye was excited with 495


nm light and the emission monitored using 515 nm band pass filter.


The Alexa 594 dye


was excited using 590 nm light and the emission monitored using a 590 nm band pass


filter. After individual image acquisition, the fluorescence images for each dye were

overlaid. Also an optical image of the surface was acquired using reflected light from the


surface.

Results and Discussions

Microarrays fabricated by method 1

Figure 4-5 shows scanning electron micrographs (SEM) of the porous alumina


microarrays fabricated by method 1 at a low (A) and higher (B) magnification.


As can be


seen in the SEM image, the porous alumina films are very distinct areas on the


polymer/Al surface.


The pores of the alumina film are not highly ordered in this case,


due to the fact that the anodization process took place only in one step and for a very


short period of time (20 minutes).


Uniformly cylindrically pores can be obtained by


using a two-step anodization method (52).




















Figure 4-5. Scanning electron micrographs of the porous alumina microarrays
fabricated by method 1 at a low (A) and higher (B) magnification.

Microarrays made by method 2


Figure 4-6 A shows the SEM image of the silver patterned porous membrane.


silver metal was not electrodeposited throughout the whole length of the membrane; it

was deposited only along on a distance that represents 5% of the membrane thickness


(see Figure 4-6 B).


The possibility of using commercially available alumina membranes


presents an advantage of this method.


For quantitative studies, however, because of poor


homogeneity of the pores diameter in these alumina membranes, one will have to use


membranes prepared in house with highly ordered pores.


These membranes will have to


be patterned by method
























Figure 4-6. Scanning electron micrographs of the porous alumina microarrays fabricated


by method


A, Ag patterned on porous alumina and B, Ag rods after


dissolving the membrane

Effect of the silica on the sensitivity measurements

Although silanes can be attached directly on the alumina surfaces, we found that

the fluorescence signal is enhanced if a thin film of silica is deposited primarily on the


pore walls of the membrane (Figure 4-7).


The silica film introduces a higher density of


hydroxyl groups on the surfaces, which provides a higher reactive surface area for further


modification.


The fluorescence spectra in Figure 4-7 show that for samples modified


with silica, the fluorescence signal is approximately 7 times higher than for samples

modified initially only with the silanes.










60000



40000



20000



0


600 700


Wavelength (nm)


Figure 4-7


. Fluorescence spectra for a rhodamine B-APTES-alumina sample with (green)


and without (red) silica.

Sensitivity

The graph in Figure 4-8 shows the relative fluorescence coefficient for rhodamine


B-modified membranes of 0.5, 1.2, 50, 60 and 90 am thickness.


defined the relative


fluorescence coefficient, a, as the ratio between the fluorescence intensity of the dye


modified membrane and the glass slide modified in the same way.


As we expected, the


3D structure of the alumina membranes leads to a higher sample loading capacity,

yielding an enhanced signal. Depending on the thickness of the membrane, the signal can

be enhanced as much as 416 times for a 90 um thick membrane.




















glass 0.5 1.2 50 60 90


Membrane thickness, pm

Figure 4-8. Relative fluorescence coefficient for rhodamine B-modified membranes of
different thicknes.

Selectivity

As an application for the porous alumina-based microarrays we have screened the


arrays for antibody specificity.


After capture proteins were immobilized (human and


mouse IgG's), the arrays were probed with a mixture of the target proteins (anti-human


IgG-Alexa 488 and anti-mouse IgG-Alexa 594).


The left side image of Figure 4-9


represents an optical image of a 350 jtm x 350 jim section of the microarrays showing the

spots where we immobilized the capture proteins, and the right side image shows the


fluorescence image acquired after the mobilization of the target proteins.


It can be seen


from these images only the spots containing the capture proteins were highly fluorescent,

indicating that the proteins were immobilized and able to retain their functional properties


on the porous surfaces.


The spots where no capture proteins were immobilized are


lightly visible, indicating some nonspecific binding on the alumina surface.








Human IgG


Mouse
IgG



Mouse
IgG^


Mouse
SIgG



Mouse
9IgG


Human IgG


Figure 4-9: Optical (left) and fluorescence (right) image of a 350 upm


x 350 am area of


the microarrays after immobilization of the target proteins.

Investigations of the fluorescence intensity profile (Figures 4-10 and 4-11) denoted

cross-reactivity between the human and anti-mouse IgG, and mouse and anti-human IgG


respectively.


The uneven peaks in the intensity profile graphs are the results of both an


inhomogeneous delivery of capture proteins using the manual injection system and the


disordered structure of porous alumina.


These drawbacks can easily be overcome by


using a automatic injection system and a very highly ordered pore alumina support. That

is, high uniformity of the porous support is one general demand for quantitative protein

immobilization; both geometry (pore size) and morphology (pore shape, level of

branching) affect the physical properties of the protein microarrays and thus their

performances and characteristics (171).

One important feature of our microarrays is that the arrays are very well defined on


the platform.


They are separated from each other by either Al (method 1) or Ag (method


This eliminates the tendency of the samples to spread out, which is a main issue in







































-150 -100 -50 0 50 100 150


X Axis (m)





Figure 4-10. Excitation with 495 nm light: A, 2D fluorescence image; B. 3D fluorescence
image; C, fluorescence intensity profile.






























S -150 -100 -50 0 50 100 150 2



30 -150 -100 -50 0 50 100 150 2'


X Axis (pm)

Figure 4-11. Excitation with 590 nm light: A, 2D fluorescence image; B. 3D fluorescence
image; C, fluorescence intensity profile.

Conclusions

In summary, we report here two methods of fabrication of 3-D porous alumina-


based microarrays.


showed the advantages of using these arrays in terms of


sensitivity and the importance of using silica nanotubes for signal enhancement.


application of these microarrays in antibody specificity screening has been shown also.


The arrays obtained by method


being opened at both sides, can be incorporated into


microfluidic devices. The electrodeposited Ag rods confer to the membrane a greater

mechanical stability.

J J4 4 4 4* 1- 4 4 44 > 4 4.1-n







samples can be spotted on the same surface.


Furthermore, the sample loading capacity


can be controlled by varying the thickness and the pore diameter of the alumina


membranes.


The uniformity of the spot intensity profile can be improved by using


alumina membranes with very highly ordered pore diameter distribution.

The ability to make protein arrays on a surface with very well defined features and

morphology should increase the capabilities of researchers to study protein interactions

on a whole proteome scale using the array technology.












CHAPTER


PROTEIN SENSING WITH SINGLE NANOPORE MEMBRANES

Introduction

There has been a big interest in constructing single molecule sensors based on


nanopores.


The principle of the sensor operation is based on the nanometer opening of


the pore which is comparable to the size of molecules to be detected (178).


When a


molecule enters the pore, the pore is temporarily blocked, which can be observed as a


significant temporary reduction in the ion current passing through the pore.

operates therefore as a Coulter counter on a single molecule level (178). T]


The device


his type of


sensor has been constructed on the basis of a protein a-hemolysin and its functioning was


demonstrated for DNA analysis (118,179, 180).


The nanopore sensor enabled


determination of the length distribution as well as chemical composition of DNA strands

in a solution, which built hopes for single-nanopore super fast DNA sequencing


(181,182).


A further major advance was made in the group of Hagan Bayley in


engineering a biosensor that is capable of identifying individual DNA strands with single-


base resolution.


Each biosensor element consists of an individual DNA oligonucleotide


covalently attached within the lumen of the a-hemolysin pore to form a "DNA-


nanopore"


. The other single strand the analyte is in the electrolyte solution.


This


system could distinguish between complementary and non-complementary DNA strands,


making it specific for a given DNA sequence.


This biological pore-bilayer system is




83


industrial scale would involve replacing the protein channel with a durable, robust,


synthetic nanopore.


Detecting single DNA molecules and characterizing their


distribution was demonstrated with several types of solid state nanopores but none of

them was equipped with recognition sites specific for a given biomolecule (183-187).

Here we present a 3-dimensional nano-immunoassay based on a single pore


system, capable of probing protein-protein interactions and detecting warfare agents.


principle of operation of this device is very simple and based on an intuitive and checked

experimentally fact that transport properties of a nanopore depend very strongly on the


pore walls surface characteristic (119, 188,189).


If an analyte to be detected binds to the


recognition sites placed on the pore walls and the pore has an opening of several

nanometers, the transport characteristic of a nanopore, expressed for example in a form of


current-voltage (I-V) characteristic, will be significantly changed.


Basing the detection


signal on I-V curves rather than time series will significantly simplify the recording as


well as data analysis process.


I-V curve represents average transport properties and as


such is much less demanding concerning the noise-free environment for recording than

time series, which is the main detecting signal for Coulter counter based devices (178).

As a base for the 3-dimensional nano-immunoassay we chose polymeric


membranes covered electrolessly with gold.


Gold surface enables easy modification of


chemistry of the pore walls by application of a thiol chemistry (44,190).


The pores in


polymer membranes were prepared by the track etching technique, which is based on

irradiation of polymer films with heavy ions and subsequent development of the latent


tracks by chemical etching (37).


The technique gives amazing freedom in preparation of




84


our 3-dimensional nano-immunoassay we chose asymmetric, conical shape of the pore


(120-128).


A conical pore has a much lower resistance than an equivalent cylindrical


pore of the same limiting diameter.


Additional advantage of using asymmetric pores is


that we limit the interactions zone in the pore, which makes the sensor's response faster


and is expected to lower the detection limit.


The pores were subsequently covered


electrolessly with gold (40), which resulted in formation of gold tubes (123).


principles of the nanodevice operation were shown first with the system biotin-

streptavidin, which is known to have a very high binding constant, and the binding is


regarded as practically irreversible (191).


We also checked applicability of the device for


sensing protein-protein interactions on the example of protein G modified Au tubes.

Protein G is a cell surface-associated protein isolated from Goward Group G Streptococci


and binds with high affinity immunoglobulins (IgG's) (192,193).


In our experiments we


have used cat IgG which has no affinity for protein G, and horse IgG which has a strong


affinity to the protein G (194,195).


It is also shown the potential of this nanopore system


in building sensors for warfare agents, on the example of ricin.

Experimental

Materials

We used 12 jam thick polyethylene terephthalate (Hostaphan RN 12, Hoechst) foils,


irradiated with single swift heavy ions (

(UNILAC, GSI Darmstadt). To obtain


Au, Xe, U) (196) of 2.2 GeV kinetic energy


conical pores, the single ion irradiated polymer


foils were mounted between two chambers of a conductivity cell and etched from one


side in 9 M NaOH, as described elsewhere (120,122,128). The chemical etching was








resulted in increase of the pore diameter.


The diameter of the large pore opening was


estimated on the basis of the so called bulk etch rate, which for PET at 9 M NaOH and


room temperature is 2.13 nm/min (120).


For example,


2 hours etching results in 520 nm


pore diameter.


The diameter of the small opening was obtained on the basis of


conductivity measurements assuming a conical shape of the pore (37).


prepared had a diameter of-40 nm.


The pores we


Plating the nanopores with gold resulted in final


diameters varying between 5 and 20 nm, function of the gold deposition time.


The big


diameter of the pores did not change significantly.

Electroless plating of PET membranes

The electroless plating was performed according to the procedure described


elsewhere (40).


The plating process was performed at 3.6 OC, and pH 9.9.


Tipically,


after 2.5 hours of plating, the gold layer has an approximative thickness of 4 nm.

Proteins


Lysozyme, streptavidin, bovine serum albumin (BSA), protein G


cat IgG and horse IgG were purchased from Sigma Aldrich.


- biotin labeled,


EZ-Link Biotin-HPDP or


(N-(6-(Biotinamido)hexyl)-3'-(2'-pyridyldithio)-propionamide was bought from Pierce.

Ricin Toxoid and Biotinylated Anti-Ricin IgG were bought from Toxin Technology, Inc.,


Sarasota, FL.


Ricin Toxoid has been toxoided using glutaraldehyde crosslinking and has


less than 1% of the original toxicity.

Experimental Setup

The single conical-Au-nanotube membrane was mounted between two halves of a

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Full Text

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NANOTUBE MEMBRANES FOR CHEMICAL AND BIOCHEMICAL SENSING AND SEPARATION By LACRAMIOARA TROFIN A DISSERTATION PRESENTED TO THE GRADUATE SCHOOL OF THE UNNERSITY OF FLORIDA IN PARTIAL FULFILLMENT OF THE REQUIREMENTS FOR THE DEGREE OF DOCTOR OF PHILOSOPHY UNNERSITY OF FLORIDA 2005

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Copyright 2004 by Lacramioara Trofin

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This dissertation is dedicated to my parents Lucia and Nicolae Darie.

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ACKNOWLEDGMENTS I think if any of us honestly reflects on who we are, and how we got here, we discover a debt to others that spans nearly our whole lives. The work and support of some people made my life easier everyday. Some people have directly shaped my life and my work. I would like to acknowledge the inspiration and guidance that I received from my Ph.D. advisor, Dr. C harl es R. Martin. He encouraged and supported my work. He also taught me how to effectively communicate science and successfully write scientific papers I am grateful for the many suggestions and comments that I received from the members of the Martin group. I have been fortunate to be a member of such a diverse, team-oriented research group Many colleagues contributed directly to my research projects with their ideas and energies. David T. Mitchell introduced me to the field of nanomaterials. He taught me how to make alumina membranes, silica nanotubes and he gave me excellent training in e l ectron microscopy. SangBok Lee gave me insightful advice on the microbattery project. Marc Wirtz taught me the fundamentals of impedance spectroscopy. I am grateful to Punit Kohli for his help in the protein separation project and for his contagious enthusiasm for science. The many hours I spent chatting with Zuzanna Siwy have led to fruitful developments. She contributed directly with her knowledge and energy to my scientific development. I would like to thank David T. Mitchell and Eli z abeth Heins for the endless hours they spent teaching me English For that I am especially gratefu l to them. Damian Odom Scott Miller lV

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Elizabeth Heins, David Mitchell, Shufang Yu, Punit Kohli, Marc Wirt z gave me id e as and helped me in preparing the talks that I presented during graduate school. I am ve ry grateful to Myungchan Kang who helped me with the microarrays project. He taught me about plasma etching technique and fluorescence spectroscopy. I am indebted to Miguel 0. Mota, who did his best to improve on my best. Miguel spent many hours makin g alumina membranes and solutions necessary for my projects I also want to thank Heather Hillebrenner who has shared her needs and experiences with me I ha ve had th e wonderful experience to truly believe that in some small way I helped her; that means so ery much to me I am also grateful to Zuzanna Siwy and Lane Baker who proofread this dissertation and, by their feedback, they helped me structure better the dissertation My life during the graduate school would have been much less interestin g without my friends Isabela and Calin Briciu Zu z anna Siwy Cristina Cosma Nathalie Kohli and Violeta Bacanu. I would like to specially thank my boyfriend Hermann Schulte aufm Erley for his love and continuous support during my last years of graduate school. I would like to thank to my chemistry high school teacher Ion Dumbra v a and m y mentor Dr. Gheorghe Ivan from CERELAST-Bucharest for their untirin g support and seemingly unlimited belief in me. Special gratitude is reserved to my parents Lucia and Nicolae Darie w ho ha v e encoura ge d me in so many ways to pursue my life dreams V

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TABLE OF CONTENTS P a g e ACKNOWLEDGMENTS .. . .. . ... .. ... .. .. .. .. ... . . . . .. ... .... ... .. ...... . . .... ... .i v LIST OF TABLES .. ........... ... . . .. ... .. .. . .... .. .. .. ... .. . ... .. . . ... . .. .. . .. . ... .i x LIST OF FIGURES .... .. . .. ...... .... ..... . . ... .. .. ... . . .. .. ......................... .. x ABSTRACT .... .. .... ..... . . .... ... .. .... ... ... ... .. ... .. ... .. .. .. . ...... . ....... .. .... xi v CHAPTER 1 INTRODUCTION AND BACKGROUND . .. .. . .. . .. .... .. ... .. . .. .. . .... ... 1 Introduction ...... ... ... .. .. . . .... ... .... ..... .. .. .... .... . ... .. .... ........ ... ..... .. ... ............... 1 Background ....... ... ... .. . ...... ... ...... ... . ....... .. ... . .. .. ... . ... ........ ... . 3 Membrane-Based Template Synthesis .. ... .. . .... . .... .. .... .... .. ... .. . ... .. 3 M e mbran e templates ... ........ . ... . ...... .. .. ... .... .... ... ..... ... ........ 3 Electro less deposition . ... .. ... .. ........ ..... . . .. ... ... .. . .... . .. .. . ... .. 5 Applications of gold nanotube membranes . ... ... .. .. ... .. ... .. ... ....... .. ... 6 Porous Alumina Membranes . .. .. ........ .. .. ... .. .... ... ... ........ .. ..... .. ... .. 7 T wo-step anodi z ation method . . ... . .. . . .. .. .. . .... .. .. .. . . ... .. ......... 8 Mechanism ... .. . .............. .. ......... .. .... . .. .. ... ............. .. . ... 1 4 Applications of alumina membranes . . .. ....... . .. ..... . ... . . ........... 1 6 Sol Gel Chemistry ........ . .. .. . .. .. . . .. ..... .... ... .. .. .. .. .. .. . .... ... . . .. .. 1 9 Silane C hen1istry .... . .. .... .. ........ .. . . ...... .. . ...... .. . .... . . . .. . ........ 20 Carrier Facilitated Transport .... ... ...... ................ . .. ............ ..... ... 23 Sin g l e Pore Polym e ric M e mbran es ..... . ... ... .. . . .. .. .. . . ...... . .. . .. .... 27 Irradiation with heavy ions .. .... ...... . . ... ... .. . .... .. ... .... ... . .... .. .. .. 29 Ion track e tchin g ........ .. .. .... ... .. ... ... ....... .. . .. . .. .... .. . . .... . . 30 Dissertation O ve rview . . . .. .. .. .. ... . .. .. ... . ... . .. .. ...... . ... ...... ............ 3 2 2 ION C HANNEL MIM E TI C SENSOR WITH AN ON BOARD MI C ROBATT E RY ... .. .... .... .. . . . .. ....... .. ..... ... . ............................ 35 Introduction .. . ... ... .. . .. .. ..... .... . .. .. ... ......... ............... .. . .. .. .. . 3 5 Ex p e rim e ntal ... ... ... ....... . ... . . ........... .. .... ................................ 36 Mat e rials . ... ..... ... . .. .. ... .. ... .. ....... .. ...... . . ... .. .. . . ... . .. .. .. 36 Silani z ation of th e Alumin a M e mb ra n e s .. .... . ..... .. .. .. ... ....... ...... 36 V l

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Microbattery Fabrication ...... .... . ..... .. .. .. ....... .. .. .. .. . ..... . .. .. .. . .. .. 37 Scanning E l ectro n Microscopy (SEM) ... .. ....... .. . .......................... .. .. 38 Cell Assemb l y an d Battery Discharge Measu r ements ... .. .. ..... ... .. ... .. ... .... 38 Results and Discussions ...... ................ . ............. ....... ... .. . .. .. ............. 39 C har acterizat ion of the E l ec trod e Films ...... .... .. ......... ...... .. ... ...... ... .... 39 Battery Discharge Experiments ......... ... .. ... ... .. .. ........... ... ... .. ......... . .41 Effect of Surfactant Concentration on the Response Time . ... ...... .. . ...... .46 Investigations of Alkyl C h ai n Length on the Response Time ....... .. . . ..... .. 47 Co n c lusions .... .... ..... .. .... ..... ..... ................... ... .. ........ .... ... ... ......... ... 48 3 HIGHLY SELECTIVE ANTIBODY-BASED NANOTUBE MEMBRANES FOR PROTEIN SEPARATION Introduction ... ..... ......... ... ..... ... . ... ................ .. ......... . ... . . . .. ... 50 Experime nt a l ................. .. ........... ......... .......... . .... .. ... ..... ... ........ . 51 Materials .. .... .. . .. ..... ... . ..... .. .. ... ... .... ... . ... .... ... . ... .... . ...... .. 51 Fa bric at ion of the Nanoporous A lumin a Mem b ranes .. ...... .. ..... .. ... .... . ... 51 Antibody Immobili za tion ...... ... . .. .... ... . .............................. .... . .. 52 Transport Expe rim ents .... ..... ............. .. .. ..... ........ .. ..... .......... ..... 53 R es ult s and Discussions .. ...... .. ... ... ..... ..... . ... .................................... 54 Effect of Antibody Affinity on Selectivity Coefficient. ...... ..... ... .. ... .. . .. 54 Effect of th e Feed Solution Concentration on th e Flux and Selectivity Coefficie nt. ...... ...... .. .. ............ . ..... ........... ... ...... . ... ..... .... . .... 57 Effect of the Pore Diam eter on the Flux and Selectivity Coefficient. .. .. .... .. 59 Conc lu s ions ... ........... ............. . ...................... ....... ..... ......... .... ........ 6 1 4. 3D POROUS ALUMINA-BASED PROTEIN MICROARRA YS ...... ... ........ .... 63 Introduction . .. .... .. . ... . . .. .. .... . ................... . ......... ..... . . .... ... 63 Experimenta l . . ....... ... ..... ... . ........ ....... .. . .... ... .. .... ... .. ... .. ..... .... .. .. 64 Materials ..... .. .. ..... ... .... ... .. ... ........... .. ... ... .......................... 6 4 Fabricatio n of Porous A lum ina Microarrays ........ ..... ..... ... . .. .. ..... ....... 67 Method 1 ...... ..... . . .. . . . ....... .. ...... .. ... . ... . ....................... 67 Method 2 . .. ......... .. ...... .. .... .. .. ...... .... ..... .. ........ .. .......... ... .... 69 Membra n e Mod ific atio n for Sensitivity Studies .. .... .. ....... .. ....... .. ... . .... 71 Microarray Mod ifi cation for Selectivity Studies .... . . .. .. .................. .... 72 Results and Discussions ... . ... .. .... ..... .. .. ... .............. . .. .... ... .. ..... ... ...... 73 Microarrays Fab ri cated by Method 1 .. .... ..... .. .. ............... .......... .. .. .. 73 Microarrays Made by Met hod 2 .......... .. ......... ..... ... .. ... ... ............... 74 Effect of the Silica on the Sensitivity Measurements .. .. .. . ....... ... ....... .. .. 75 Sensitiv it y . .... ........................... .... ....... .. . ... .. .......................... 76 Selectivity .......... ... .... ......... . ..... ..... .. .... ..... ..... . ..................... 77 Conc lu sions ............ .. ... ... .. ... ....... .. ... .. ... . ... ...... .. ........ ..... .. ....... .. 80 5 PROTEIN SENSING WITH SINGLE NANOTUBE MEMBRANES .. ........... ... 82 Vil

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Introduction ............. ..... .. .......... ... ... ... ............. ............. .............. 82 Experimental . .. .. . ............... ... ........... ............ .. ..... ...... ...... ... .... .... . 84 Materials. . . . . . . . . . . . . . . .. .......... .... ... ..................... .. ......... 84 Electro less Plating of PET Membranes .. ... ... ... ......... ... .. .. .. .. .. ..... .. .... 85 Proteins .... ....... ........ ....................... . ... .......... .... .. .... ..... .. .. ..... 85 Experimental Setup ........ .. ................... .. ... ... .. ....... ..... ... ... ... ........ ... 85 Results and Discussions .. . .. ...... . .. ... .. ........ .. .... ... .. . ............ .. ... ... .. .. 86 Conclusions ..... ..... ....... .. .. ... .......... ... .......... .... . ..... . . ... ..... .. .. .... . 94 6 CONCLUSIONS ..... ... ........ .. ... ......... .... ... ...... .. ........ .. . ......... ... ... ... 95 LIST OF REFERENCES ... ... .. .... .. ....... .. . ........... .. .. .. .. . . .................. .. 98 BIOGRAPHICAL SKETCH . . .. .... .. ....... . .. .. ... .... ............ .. .... ... . ...... .... ... 109 V lll

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LIST OF TABLES Table 2-1 Effect of DBS concentration on the response time .. . ...... ........................ .42 2 2 Effect ofDTA concentration on the response time ..... .. ...... .. . .. .. .. .... .. 43 2 -3 Effect of alkyl chain length in alkyl trimeth y lammonium surfactants on the r e sponse time .... ... .... ... .. .. .... . ... .. ... .. . ........... . .. ... ... .. ... ..... .... 44 l X

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LIST OF FIGURES Figure 1-1 Scanning electron micro graphs of the surfaces of the (A) alumina and (B) polycarbonate membranes . ..... . ... ........... .. ... .... ..... ... ..... ... ............ .4 1-2 Electrochemical cell setup for alumina growth .. .. ...... .. .. .......................... 10 1-3 Variation of the pore diameter with the voltage applied ........... .. .. ... ... .. .. ... 11 1-4. Variation of the pore diameter with the concentration of the electrolyte solution .. ... ........ ............................. ..... ......... ....... ........... .......... 11 1-5 Scanning electron micro graphs of the (A) solution side and (B) barrier side of an alumina membrane formed at 50 V in 5% oxalic acid ................................ 12 1-6 Scanning electron micro graphs of the (A) surface and (B) cross-section of an alumina membrane obtained at 50 V in 5 % oxalic acid ... ..... .. .. ................. .. 13 17. Scanning electron micro graphs of the (A) surface and (B) cross-section of a commercial alumina membrane (Whatman) with pore diameter of200 nm . ... 14 1-8 Schematic representation of the pore formation in the porous alumina film .. . .. 15 1-9 Steps involved in the silane chemistry ....... .. .. ..... ........ ........ ...... ............ 23 1-10 Typical nonlinear flux pattern for carrier-mediated diffusion ... ... ..... ... .. .. .. 25 1-11 Schematic representation of how the facilitated transport works .. ... . ... ... .... 26 1 1 2. Chemical formula of th e PET (A) and Kapton (B) ..... .. .......... .... .............. 30 1 1 3 Schematic representation of a conductivity cell used for chemical etching ... .. 30 2-1. Schematic representation of the micro battery fabrication . .................. . . .. 38 2-2. Schematic representation of a U tube permeation cell. ................. .. . ... .. ... 39 2-3. Cross-sectiona l (upper) and surface (lower) SEM ima ges of the battery e lectrode films that coat th e fac es of the alumina m e mbran e . ... .... ........ ... ... ......... .40 X

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2-4. EDS spectra of t h e membrane surface after deposition of Ag (A) and after conversion of the Ag surface to AgCl (B). EDS spectrum of the opposite membrane surface that had been coated with Zn (C) .......... .. . ....... . ... .. .41 2-5. Current-vs.-time response for the transmembrane microbattery applied to an a lumin a membrane that was not rendered hydrophobic by silane functionali z ation (A) Ana lo gous current-vs.-time response for the hydrophobic Cl8-modified membrane (B) ........... . .. .. ..... ..... ........ ............ ... .. .. ......... . . ..... 43 2-6. Current-vs.-time response for a hydrophobic membrane before and after injection of DBS surfactant solution ...... .... .. ...... .... . ...... .. .... ... .... . .. ... .. . . .45 3 -1 Scanning electron micrograph of a porous alumina membrane with pores of 50 nm in diameter and pore density of ~ 10 1 0 pores / cm2 .. . ... .. ... .. . ..... . .. .. .... ........... .. ........ .. . ..... ... ........ .. 52 3 2. Modification steps involved in antibody immobili z ation ..... .......... .... ............ .... . ...... ....... ... ... ... .. . ... .. .... 53 3-3. Transport plots of GFP-Hevein and RFP through ENA l lHis (A) 1 C2 (B) and 1A4 (C) nanotube membranes .... .... .. ... .. .. .... . .. .. ... . .. ... ... . . .. .. .... 55 3-4. Effect of the antibody immobilized on the selectivity ... .......... ..... ........ ... .. 56 3-5. Plot of fluxes of GFP-Hevein and RFP ve r sus feed so lu tion concentration ... ... . ... . . . .. ... ... . ..... ... ... ........... ....... ... .. .. . ......... 5 7 3-6. Transport plots of GFP-Hevein and RFP through a 1 A4 antibody-modified membrane when using 5 nM (A) 20 nM (B) 50 nM (C) and l 00 nM (D) feed so lu tion concentration . .. . . .... ... ... .. ... . ... .... ...... .. ....... .. ....... .... . . 58 3-7. Variation of the se l ectivity coefficient with feed solution concentration .. ..... . .. .. ............ ..... . ....... ......... . ... ... ... .... ...... . 5 9 3-8. Transport plots obtained when used membranes with pores of 50 nm (A) 70 nm (B) and 100 nm (C) in diameter. ... ... . .. ..... ... .. . . ..... .... ..... . .. .. ... ....... 60 3-9. Se l ectivity coefficient variation with the pore diameter. .. .. ...... .... . .. .... .. .. .... ..... .. .. ... .. .. .... .... . ..... .. ... ........... 61 4-1. Schemat i c representation of the microarray fabrication by method l . . . ... ... ... 66 4 2 Schematic representation of the microarray fabrication by method 2 .. ... .. ...... 68 4-3. E l ectrochemical cell setup for si l ver electrodepos i tion : A Ag wir e counter and reference electrode ; B Ag plating solution ; C Cu foil ; D Au-Pd modifi e d a lumin a membrane as working electrode; E stain l ess steel plate; F teflon tap e; G O-ring seal ........ . .... .... ... . ...... ... . ..... ... .. ... .. ... ...... ......... .... ..... 6 9 4-4. Modification steps for sensitivity studies . . ........ . .. .. .... .. ... .. .. .. .. .... .. . 7 1 4-5 S c annin g el e ctron micro graphs of the porous alumina microarrays fa bri ca t e d b y method 1 at a l ow (A) and higher (B) magnification .. ... .. .. ........... ... ..... .. 7 4 4 6 Scannin g e l ectron micro graphs of th e porous alumina microarra y s fabri ca t e d b y m e thod 2 : A Ag pattern e d on porous alumina and B A g rods a ft e r dissol v in g th e membrane ... .... . ... .. ...... .... . .... .... ... .. ... ... ... ..... .. .. . .. ...... ... .... 7 5 X I

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4-7. Fluorescence spectra for a rhodamine B-APTES-alumina sample with (green) and without (red) silica ... ... .................. ............... . ....... ........... .. .. .. .. 76 4-8. Relative fluorescence coefficient for rhodamine B-modified membranes of different thicknesses ............. ... . ........... . ....... .. .. ...... .. .. .. ... . ... .. 77 4-9. Optical (left) and fluorescence (right) image of a 350 m x 350 m area of the microarrays after immobilization of the target proteins ... .... ... .... ... .. . .. .. .. 78 4-10. Excitation with 495 nm light: A 2D fluorescence image; B. 3D fluorescence image; C fluorescence intensity profile ..... .. .. .. ... . .. ...... ..... ... . ......... 7 9 4-11 Excitation with 590 nm light: A, 2D fluorescence image ; B. 3D fluorescence image; C, fluorescence intensity profile... . .. .. .. ... . ...... ... ... ...... . . ... .80 5-1. Sensing lysozyme with a single conical gold nanotube. (A) Currentv ol t age characteristic of the Au nanotube before (red points) and after modification with thiolated biotin (blue points). The diameters of the pore opening are 5 nm and 0 6 respectively. (B) Ion current versus time through the Au nanotube mod i fied with biotin recorded at 1 M KCl pH 7. (C) Ion current versus time as in (B) at presence of 100 nM lysozyrne in contact with the small opening of the pore ... 8 7 5-2. Sensing streptavidin with a single conical gold nanotube. (A ) Current-voltage characteristics of a single conical Au tube modified with SH-biotin at presence of 180 pM streptavidin added on the small side of the conical nano tube. (B ) Ion current in time through a single Au nanotube modified with biotin, recorded at 1 M KCl pH 4.5 recorded at -1000 m V. (C) Ion current in time as in ( B) at presence of 180 pM streptavidin . ... . ... ... .. ..... . .. ... .. . .... . .. . ... .. ... .. ... 88 5-3 Blockage time vs. log of the molar streptavidin concentration .... . .... . .. .. ... 90 5-4. Chemical modifications of a single Au tube leading to preparations of 3 dimensional nanoimmunoassay for detection oflgGs and probing their interactions with protein G (A) Schematic representation of the subsequent modifications of a single Au tube (B) Current-voltage charac t eristics recorded at 1 M KCl, pH 7 performed after each modification step. The gold tub e aft e r modifications has diameters of ~ 15 nm and 0 6 respectively .. .. . .. ........ 91 5-5 Sensing of cat IgG with a single conical Au nanotube modified with protein Gas shown in Fi g. 4. (A) Curr e nt-volta g e charact e ristic of a sin g le Au tub e recorded at 1 M KC! pH 8 7 Ion current in time r e corded at 500 mV transm e mbran e potential before (B) and after (C) addin g 100 nM cat IgG The g old tube aft e r modifications ha s diam e t e rs of ~ 15 nm and 0 6 m respe c ti v el y ..... .. .. .. . . .. 92 5-6 Sensing of horse I g G with a single conical Au nano tube modified with prot e in G as shown in Fig 4. (A) Current-volta g e characteristics o f a singl e g old tub e recorded at pH 4.4 1 M KC! before (x) and after() adding 10 nM hors e I g G .. . 9 3 X II

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5-7. I-V curves for the ricin sensor in the presence of no protein (x), 100 nM and ~ 100 nM ricin ( ) .... .... ................ .. . . ............... ..... .... . ........... 94 X lll

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Abstract of Dissertation Presented to the Graduate School of the University of Florida in Partial Fulfillment of the Requirements for the Degree of Doctor of Philosophy NANOTUBE MEMBRANES FOR CHEMICAL AND BIOCHEMICAL SENSING AND SEPARATION By Lacramioara Trofin May 2005 Chair : Charles R. Martin Major Department: Chemistry The discovery of novel materials, processes, and phenomena at the nanoscale, as well as the development of new experimental and theoretical techniques for research provide fresh opportunities for the development of innovative nanodevices and nanostructured materials. Nanostructured materials can be made with unique nanostructures and properties, and finding various and unique applications of these is a continuous challenge for researchers in this field. As part of this emerging research, the work presented here is focused on development of new nanostructures based on nanoporous membranes and investigation of their applications as sensors and separation devices. A template synthesis method is used to produce nanotubes inside the pores of both aluminum oxide and polymeric membranes. After an introduction in the template synthesis method and the processes of fabrication of the porous membranes the dissertation is centered on investigating new applications of these nanotube membranes. XIV

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There are three applications of the nanotube alumina membranes and one application of the single nanotube po l ymeric membranes that are explored. Porous alumina is used to mimic the function of the ligand-gated ion channel by app l ying a porous battery cathode film to one face of the hydrophobic membrane and a porous battery anode film to the other face. Hence, in analogy to the naturally occurring channel case, we have a membrane with a built in electrochemjcal potential difference across the membrane. The application of silica nano tube membranes in se l ective separation of proteins is presented The membranes were modified with antibodies that selectively bind one analyte. These nanotube systems lead to the transport at much higher rates of the analyte which binds to the membrane. Another application studied is the fabrication of the protein microarrays which features a three dimensional substrate based on porous aluminum oxide membranes. These membranes represent distinct microfeatures on a robust platform and they have cylindrical pores with monodisperse nanoscopic diameters The advantages of using this substrate and its application in antibody specificity screening are presented. Finally a new family of protein biosensors based on a single conical nano tube membrane is described. Three different protein systems were investigated: (i) biotin/streptavidin (ii) protein-G /i rnmunoglobulins, and (iii) anti-ricin/ricin. xv

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CHAPTER 1 INTRODUCTION AND BACKGROUND Int r o du ction Nanotechnology refers to technologies in which matter is manipulated on the atomic and molecular l evel to create new materials and observe new processes. It is not just the study of the very small ; it is also the practical application of that knowledge. Nanotechnology is a truly interdiscip l inary field Materia l s scientists, electronic and mechanical engineers, as well as medica l researchers are working together with biologists, physicists and chemists. Research at the nanoscale i s unified by the need to share the knowledge and expertise required to work at the atomic and molecular level. Powerfu l new concepts and capabilities, such as atomic-sca l e imaging and manipulation self-assembly and biologica l structure-function relationship, together with increasingly powerful computing tools are rapidly converging from different research areas. Nanotechno l ogy is not a new area, though. Mother Nature serves as a model for having many materia l s and processes that functions at the nanoscale (1); small mo l ecular building blocks are joined together to produce nanostructures with defined geometries and functions. The top-down approach becomes increasingly difficult, as the final products approach the nanometer l evels It has become evident that Nature s bottom-up approach can be emulated to produce new materials with nanosi z ed dimensions and engineered properties. Nanoparticles (2 3) and nano tubes ( 4 5) are the two principal branches of nanostructured materia l s. Historically nanopartic l es were mainly restricted to gold and 1

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2 silver particles. More recently a wider variety of nanoparticles have been synthesi ze d ; for examp l e, commercially available magnetic beads are used for cell preparation (6,7), quantum dots are used for long-t erm fluorescence assay in cells (8), and colloidal gold has been used for gene therapy (9) Since the discovery of carbon nanotubes in 1991 ( 10) the synthesis and functionalization of the nano tubular materials has become one of the most highly energized r esearch areas (11 ) Nano t ubes have numerous potential commercial and technological applications, including their use in nanoelectronics (12, 13 14, 15) catalysis (16, 17 18) hydrogen storage (19), scanning probe microscopy (20), biosensors (2 1 22) and drug delivery systems (23). Research in the field of nanotube membranes will have a great impact on membrane technology. Membranes are utili ze d to perform separations for a wide range of applications such as water and wastewater treatment electrodialysis, gas separation, and fuel cell development (24). The use of membranes and biological tools are important in the d evelopment of biomedical and biotechnological applications (25). Recently membranes have been gaining attention as options for biological sensors (26). However, modem biotechnology and separation science have presented new challenges to membrane technology, including the requirement of pores with diameters similar to those of molecules under study, therefore as small as several nanometers Nanometer scale pores are necessary in achjeving optimal contro l of the flow of biomolecules as well as in developing sensors for their detection (27 -3 0). Another challenge is the development and characteri za tion of membranes possessing well-controlled, stable, and uniform nanom eter dimension pores capab l e of the separation and sensing of molecules in a restricted manner.

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3 In light of these challenges, Martin's group has pioneered a bottom-up method for the production of nanotube membranes, called template synthesis (3 1 ). This method involves synthesizing nanotubes inside of a porous membrane (template). This chapter provides background information on the following : membrane-based template synthesis, fabrication and applications of porous alumina ( one type of membrane template), sol-gel and silane chemistry, carrier facilitated transport, and single pore polymeric membranes. An overview of the dissertation is also presented This information will be used in the next chapters. Background Membrane-Based Template Synthesis In recent years the Martin group has been investigating a versatile method to produce nanomaterials, called template synthesis (31). In this approach, a membrane with uniform dispersed micro or nanometer diameter pores acts as a template. When material is deposited into the cylindrical pores of the membranes, it adopts their shape. If the template is dissolved, the material can retain the high aspect ratio of the pores, yielding wires or tubes with nanometer diameters. The method is versatile with regard to the type of materials that can be prepared. For instance, track-etched polymeric membranes have been used to prepared nanostructures composed of metals (32 33) insulating polymers (34) or conductive polymers (35,36). Membrane templates Two types of template are most often used for this approach: polycarbonate and alumina membranes Polycarbonate membranes are prepared by the "track-etch method (3 7 ) and have been commerciali z ed by companies lik e Nucleopore and Osmonics Poretics These membranes have pores with diameters between 10 nm and 10 and

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4 pore densities approaching 10 9 pores / cm 2 Alumina membranes are prepared electrochemically from aluminum foils (38). They are commercially available (W h atman International), or can be prepared in the laboratory. The process of making alumina membranes and their applications will be discussed in detail in the following section. Figure 1 1 Scannin g electro micro graphs of the 3 rn pore diameter polycarbonate (A) and 200 nm por e diameter alumina (B) membrane surfaces.

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5 Figure 1-1 shows scanning electron micro graphs of the surfaces of the polycarbonate and alumina membranes, respectively. Templates with diamond shapes pore in mica have also been reported (39). The sensing and transport properties of the go ld nanotube membranes prepared by the electro less deposition method ( 40) were in vestigated extensively in the Martin group (40-47) Electroless deposition Electroless deposition involves a chemical reducing agent which is used to plate a metal from a solution onto a surface. The method for electro less deposition of gold can be summarized as follows. The membrane is first "sens iti zed" by exposing it to a solution of SnC]i. This results in deposition of Sn 11 onto the membrane surfaces and the pore walls. After the sensitization the membrane is immersed into an ammonia silver njtrate solution A surface redox reaction occurs (Equation 1-1) and Ag 1 is reduced by Sn 11 which results in absorbtion of Ag nanoscopic particles on the membrane surfaces. S 11 +2A I s I V +2A 0 n s urf g sol n s u rf g s u r f ( 1-1 ) The subscripts "surf and "sol" denote species absorbed to the membrane surfaces and species in solution respectively. Then, the membrane is immersed into a gold plating so lution at 4 C A second redox reaction occurs and Au 0 displaces the Ag particle yielding the membrane surfaces to be coated with Au particles ( Equation 1-2 ). (1-2 ) These Au 0 particles are exce ll ent autocatalysts for the reduction of Au 1 to Au 0 using forma ld ehyde as reducing agent. As a result the Au deposition begins at the pore walls formin g Au nanotubes or nanowires depending on the plating time (33)

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6 Applications of gold nanotube membranes Gold nano tube membranes are a new class of molecular filters, capable of sensing and transporting both sma ll and l arge molecules. Jiraje et al. took advantage of the excess charge density present on the inner walls of the gold nanotubes and showed the regulation of ion transport through the membranes ( 40). They showed the fluxes of anionic and cationic permeates changed with the potential applied to the gold nanotube membranes. The tubes transport ions which have the opposite charge as the gold nanotubes (40). Because the inner diameter of the gold tubes can be of molecular dimensions ( < 1 nm) nanotube membranes have also been used to separate small molecules on the basis of molecular size ( 41 ). In these experiments, a large molecule, ( a tris-bipyridal complex of Ru (ll) Ru(bpy) ?J, and a small molecule (methyl vio l ogen MV 2 J, were used. A se l ectivity coefficient was defined as the ratio between the fluxes of MV 2 + and Ru(bpy) / + through the membranes. They report a se l ectivity coefficient of 50 when the inner diameter of the gold tubes was 5.5 nm. They have also showed that as the inner diameter decreases the selectivity coefficient increases reaching a va lu e of 172 for a 2 nm inner diameter (4 1 ). The gold nanotube membranes were also used to study the DNA transport both by diffusion and electrophoretically. The flux of the single-stranded homooligonucleotides made of thymidine bases (po l y(T n) where n represents the number of bases decreased as the si ze (base number) of the po l y(Tn) increased ( 42). Another way of introducing chemical and biochemical transport selectivity is by adsorbing thiols on the go ld nano tubes ( 43 44,45). Hydrophobic thiols yield membranes that preferentially transport hydrophobic species and hydrophilic thiols form tubes that preferentia ll y transport hydrophilic species ( 43 44). The a bsorbtion of L-cysteine on the

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7 gold tubes was used to make pH-switchable ion transport membranes Dependin g on the solution pH, the membrane can have excess positive charge (low pH), no net charge (isoelectric point) or excess n ega tive charge (high pH). As a result, these membranes can be switched between cation, non-ion-permselecti ve, and anion-transporting states ( 45). By controlling the inner diameter of the gold tubes, these membranes can also show good selectivity for transport of proteins on the basis of molecular size ( 46). In this work chemisorbtion of a PEG-thiol prevented the non-specific adsorbtion of the protein on the gold tubes A transmembrane pressure was applied to the feed solution to force the solution through the membrane The effect of nanotube diameter on the flux and selectivity for lyso zyme, bovine serum albumin and ~-lactoglobulin A was investigated ( 46). Recently through the immobilization of molecular recognition elements gold nanotube membranes were used to obtain DNA single base mismatch transport selectivity ( 4 7). Single-stranded DNA molecules with a thiol at one end were chemisorbed on the inner walls of the tubes. These DNA functionalized tubes selectively recognize and transport the DNA sequences which are complementary to the DNA on the tubes relative to the uncomplementar y DNA sequences Porous Alumina Membranes E l ectrochem ic al oxidation (anodi za tion) of aluminum surfaces under controlled conditions can produce aluminum oxide or a lumina with a structure of essentially cylindrical, parallel pores ( 48). Anodic porous a lumin a membranes can be made with pore diameters varying between few nanometers to 200 nm with lengths up to 3 00 m (49) Pore densities can range from 10 9 10 12 pores / cm 2 Solutions of dilute acidic

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8 solutions (e.g. phosphoric acid (49) oxalic acid (50) and sulfuric acid) are used as e l ectrolyte (51). In recent years, there has been a growing interest in preparing alumina membranes with a perfect pore array archjtecture, having a high aspect ratio at the nanometer scale. This jnterest was drawn by the possibility of applying these membranes as hosts or templates for the fabrication of the nanodevices. There are two reported methods for the fabrication of highly ordered anodic porous alumina membranes One is the two-step anodization method which will be discussed in detail in the next section; this is the method that is used in our laboratory to make the alumina membranes (52,53). In the other method, the layout of the initiation sites for hole development in anodic alumina is achieved by a process based on nanoindentation of the aluminum substrate. In this process, an array of shallow depressions is formed on aluminum by indentation, and these depressions serve as initiation sites for hole ge neration at the initial stage of generation. Masuda et al. (54) used a SiC mold to form an array of concave features with the desired arrangement (square, triangular) on aluminum In addition, Mikulskas et al. (55) showed that the nanoindentation twice with commercially available optical grating rotated by an angle of 60 to each other can create pre-structures with rombohedral ridges on aluminum. The advantage of this patterning is that it eliminates the high cost of the mold which requires electron beam lithography to produce it. Masuda et al. (56) reported another patt erning method by using a nanoindentation a pparatus attached to a scanrung probe microscop e. Two-step anodization method This method involves two successive steps of anodization of an aluminum foil in order to obtain very highly ordered porous alumina membranes.

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9 Polishing of aluminum foils. In order to obtain a high quality alumina film, the starting material, aluminum must be very smooth. High purity aluminum foils (99.99 % ) are first mechanically polished with a slurry of alumina particles. Larger particles ( > 1 0m) are used to remove material fast and polishing is continued with slurries of progressively smaller particles of submicron size. If the aluminum foils have severe scratches, mechanically polishing with fine sand paper is applied until the scratches disappear. This mechanical polishing is followed b y an electrochemical one. In this process a potential difference of 15 V is applied between the aluminum foil (which serves as the anode) and a l ead plate which serves as the cathode. The polishing solution (95 % concentrated phosphoric acid 5% concentrated sulfuric acid and 20 g/L chromic oxide) is heated to 70 C. This process is analogous with that of alumina film formation but the electro lyte being a very concentrated acidic solution at high temperature favors immediate dissolution of alumina. The electropolishing step (usually 5 minutes) is repeated as many times as it is n ecessary, until the a lum i num foil has a mirror-like surface Anodization steps. E l ectropolished aluminum is e l ectrochemically oxidi z ed into a first step at a constant voltage using an electrochemica l ce ll setup like the one presented in figure 1-2. In the process of forming the alumina film referred in the literature as the growth process the aluminum is the anode and a stainless steal plate is us e d as the cathod e Both anode and cathode are immersed into an electro l yte so lution and a vo lt age is appli e d using a power suppl y. The t e mp e rature (usuall y between o 0 and 1 s C) i s controlled usin g a cooling bath. The expansion of a luminum during the oxidation process depends

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10 strongly on e perimental conditions, such as temperature, oltage applied, type of electrolyte and concentration of the electrolyte (57-59). Smaller pore sizes require lower applied oltages and therefore more conducti e e l ectrolytes (such as sulfuric acid) 48) Larger pores n ed larger oltages which causes a high rate of dissolution in highly conducti e electrolytes (62). Anode Alumin\ Stirring bar Power supply / Porous Alumina Cathode Electrolyte Figure 1-2 Electrochemical cell setup for alumina growth. Thus, the formation of large pores will require lower conductivity electrolytes such as oxalic acid. The pore diameter in the grown alumina films varies in direct proportion to the voltage applied and the concentration of the electrolyte. Figure 1-3 shows the dependence of the pore diameter on the voltage applied, when using 5 % oxalic acid as electrolyte Figure 1-4 shows the variation of the pore diameter with the concentration of

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11 electrolyte solution when 50 V was applied. The thickness of the formed alumina film depends on the anodization time ; longer anodization times yield thicker membranes After the first anodization alumina film is removed in a solution which is 0.4 Min phosphoric acid and 0 2 Min chromic oxide at 60 C The removal of alumina film leaves behind aluminum with a hexagonal scalloped pattern due to the self-organi z ing into a hexagonal arrays of the pores during the anodization (50) That is the removal of the alumina leaves indentations or pits in the aluminum that correspond to each pore. 80 75 s 70 C ,_~ 65 Q,> 60 Q,> s 55 -~ 50 "O Q,> 45 I. 0 40 35 30 0 1 2 3 4 5 6 Oxalic Acid Concentration, % Figure 1-3. Variation of pore diameter with applied voltage 160 140 120 ,.; 100 8 80 Q 60 Q,> 40 I. 0 20 0 0 20 40 60 80 Voltage, V Figure 1-4 Variation of pore dian1eter with electrolyte concentration.

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12 To obtain this pattern on aluminwn the duration of th e anodization process must at least 12 hours. The pre-pattern e d alwninwn is then re-anodi ze d in exactly the same conditions which were used in the first anodization step The pores nucleat e in the pits w hi ch are a lread y highly ordered and monodisperse ( 52) The second anodization step is carried out for a l e ngth of time depending on the thickness of alwnina membran es desired. In our laborator y we obtained alumina membranes of thickness es between 0 3 and 150 m. Detaching. After the second anodi za tion step alwnina can b e detached from the uno x idi ze d alwninwn b y two m et hods One method utili zes dissol vi n g the aluminum in a saturated solution ofHgCb. One side of the formed alumina membrane, which faced during the growth the electrolyte solution has open pores while pores on the other side are clos e d ( 60). The two sid e s are call e d "s olution and barrier side r espect i ve l y Figure 1-5 shows th e scanning e lectron micro graphs of the solution side and barri er side o f an alwnina membrane obtained in our laboratory F i gure 1 -5 Scanning e l ectron micro gra phs of (A) so lution side and (B) barrier side of an a lumin a membrane fo rm e d at 50 V in 5 % oxalic ac id

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13 This barri e r l aye r can be remo ve d b y e tchin g o f alumina films for very sho rt t i me i n dilut e aci d o r basic soluti o ns Th e s e cond m e t ho d for deta c hin g t h e a lumin a fil ms is kn o wn as t h e vo l tage r e duction pro ce ss (6 1 ) T h i s pro c ess us e s a p rogre ssi ve red u ction o f th e a ppli e d v olt age unt i l it r e ach e s 4-5 % fr om the initial va lu e B eca u se t h e p o r e di a m e t e r i s dir e ctl y proporti o n a l to th e v olt age a ppli e d t h e r esu l ting po r es br anch d ow n to s m a ll e r s izes T h e a nodi z ation is t h e n stopp e d and th e a lumin um/a l umina system is pl ace d int o a n e t c hin g solution w hi c h c a n b e a dilu t e ac id i c o r ba s ic so lu tio n T h e t h i n b arrie r l aye r and th e sm a ll por e s di s sol ve fa s te r r e sul t in g i n d e t a chm en t o f th e a lu m i na fr om t h e a luminum In o ur l a b ora tor y, usin g t w o-st e p an odi za tio n me thod we o b ta i ne d highly ordered porous alumin a m e mbran e s T h e por e s ar e v er y uni fo rm throu g hout th e w hol e thi ckne s s of th e mem b ra n e, as ca n b e seen i n Figure 1 -6. l ; E r,;. ._ ,. ..... :; .,Y ...... ........... I t ..... .............. .. . .......... ....................... i . : ..... ............... .. ....... ...... t ......... ................. ....................... ..... .. ................... .. ... ........... ............ .... .. , ... ... ..... ... & ---F i gur e 1 -6. Scann in g e l e ctro n m i cro gra ph s of (A) surface and (B) cross-section of a n a lumin a m e mb rane o bt ai n e d at 50 V in 5 % oxa li c ac id A l um i na m e mbr anes w i t h pore di amete r s of 200 nm are commerciall y avail a b l e from Whatman Int e rnat i ona l. P ores of 1 00 nm and 20 nm in d i am e t e r ar e a l so av a i l a b l e, a nd a ll t h e m e mbr an e s h ave a thi ckness of 60 m Fo r d iam e t e rs of 2 0 and 1 00 nm on l y

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14 on one side the pores have these diameters on a l engt h of 200 nm; on the other side the membranes have pore with 200 nm in diameter. Figure 17 shows scanning electron micro graphs of the (A) surface and (B) cross-section of a conunercially available alumina membrane with a pore diameter of 200 nm. Compared to the home-grown membranes (Figure 1-6) these membranes have pores which are not uniformly distributed throughout the membrane and are characterized by much more h e terogeneous diameter. Figure 1-7. Scanning electron micro graphs of (A) surface and (B) cross-section of a commercial alumina membrane (Whatman) with pore diameter of 200 nm. Mechanism The formation of a hi g hly ordered pore array in the alumina membranes is the resu l t of two competing processes: 1) the pore initiation process due to a geometric effect, which is called "field assisted dissolution process (52) and 2) the self organization of the pores which is thought to be driven by mechanical stress at the alumina/aluminum interface (62). In the pore initiation process the alumina film developed a t the m etal-fi lm e lectrolyt e interfac e, at preferred sites (small pits or d efec ts) und ergoes dissolution assis t e d by the e lectric field. At these sites, a lo ca l increase in field strength takes place Int erac tion with the e l ec trolyt e r es ults in th e developm e nt of penetration paths from th e

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15 outer film surface which are the precursors of the pores. Field-assisted dissolution effectively polarizes the Al-O bonds, allowing more Al 3 + dissolution than in the absence of the fie l d. As a consequence of the pore development, the electric field and the ionic current become concentrated in the barrier layer beneath the major pores. This implies continued migration of the 0 2 0H ions from the electrolyte to form a solid film at the metal-fi l m interface and corresponding Al 3 + ejection at the pore base-electrolyte interface as well as field-assisted dissol u tion of Al 3 + ions (59). This mechanism of pore nucleation is illustrated schematically in Figure 1-8. Al Al Figure 1-8. Schematic representation of the pore formation in the porous alumina film The pore initiation process is followed by a steady-state film formation In this state there is a dynamic equilibrium between film growth at the metal-film interface and field-assisted dissolution at the pore base-electro l yte. The mechanical stress, a possible origin of repulsive forces between neighboring pores is associated with the expansion of the aluminum during oxide formation (62). This leads to the self-organization of the pores.

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16 Applications of alumina membranes Due to the packed array of columnar hexagonal cells with cylindrical uniformly sized pores porous alumina membranes have been used to fabricate many types of nanocomposites using the template synthesis method. For instance template pores were filled with metals or semiconductors used for the preparation of magnetic recording meilia (63 64), optical devices (65), functional electrodes (66 67), electrochromic (68), and electroluminescence display devices (69,70). The outside diameter of the nanocomposit es is determined by the pore diameter of the membranes and the length of the nanocomposites is controlled b y the thickness of the membranes. Natan and co workers synthesized submicrometer metallic barcodes by alternating Au and Ag segments along the length of a nanowire (7 1 ) For sensing and nanoelectrode applications the nanowires can remain in the template and function as an array. For single-nanowire applications removing the template produces individual nanowires that can be isolated. Porous alumina has also been used as a template to make Au Ni and Si nanoring arrays by a sputtering redeposition method (72) The channels of alumina membranes were us ed to produce a new kind of artificial lipid membrane system. In this system lipid bilayers were immobili z ed on the surface (73) and inside of the pores of the membranes (74) creating a platform with potential applications for biosensing Porous alumina membranes were a lso used as a support to incorporate metal clusters or colloid particles (75). This opens the way to new applications such as chemical complexation inside the membranes of radioactive organo-metallic compounds for possibl e c lini ca l use or for catalytic studies

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17 Lahav et. al. reported a procedure to make metal nanoparticles nanotubes" that combines nanotube geometry with nanoparticle morphology and properties (76). When the alumina membranes are used as templates to make nanotubes an important issue is controlling the inside diameter of the formed nano tubes. This problem has been approached by the layer-by-layer film deposition process. In this method, films of materials are deposited layer-by-layer on the pore walls of the membranes to make nano tubes The resulting inner diameter of the nanotubes is dictated by the thickness and the number of film layers deposited. Using this method, Ai, et al. deposited layers of polyelectrolytes (77). Kovtyukhova et al. have also used a method based on alternate SiC14/H20 deposition cycles to make silica nanotubes (78), and Hou et al. us e d Mallouk's alternating a w-diorganophosphonate / Zr chemistry (79) to prepare nanotubes within the pores of alumina template membranes (80). Highly selective silica nanotube membranes can be used as both sensors and as molecular filters (81 82 83). A sol-gel template method was us e d to prepare the silica nanotub e membran es (84) In th e ne xt section, a detail ed review of the chemistr y involved is pr ese nted. Two applications of the silica nanotube membranes are their use for biological extraction and for biocatalysi s. In this procedure, silica nanotubes were remove d from th e membrane by dissolving th e template and collected by filtration. They were functionali ze d with octadecyl silane on the insid e, resulting into a hydrophobic nanotub e int erior while the outside was l eft unfunctionali z ed g iving an hydrophilic nanotube exte rio r. These hydrophilic / hydrophobic nanotubes were us ed successfully to extract lipophilic compounds from a qu eous solution. The tubes were a dd ed to an aq u eo us

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18 solution of 7,8-benzoquinoline, a lipophilic compound that preferentially entered the hydrophobic interior of the tubes In thjs way, more than 90% of the compound was removed from the solution (81 ). In the same work Mitchell et al. showed that enantiomers of a drug can be separated using a suspension of nano tubes (81 ). In trus case the nano tubes were functionali z ed with an antibody that binds the RS isomer of the drug over the SR isomer. These nano tubes successfully extracted 75 % of the RS isomer from a 20 M racemic mixture and all of the RS isomer from a l0M racemic mixture Another application of the silica nanotube membranes is their use in bioseparation. Lee and co-workers also looked at the separation of RS and SR enantiomers of a drug (82). In trus case, the membrane was not removed, and the silica nanotube membranes were modified again with an antibody that selectively binds the RS isomer. They found that these membranes facilitate the transport of the RS enantiomer as the RS flux was twice the SR flux, for nanotubes with an inner diameter of 35 nm. It was also shown that the binding affiruty of RS over SR could be tuned by addition ofDMSO to the protein buffer solution, leading to an optimal DMSO concentration that maximized the selectivity The selectivity could be further enhanced by decreasing the silica nanotube diameter yielding a selectivity of 4.5 when the nanotube diameter was 20 nm Yamaguchi and co-workers have reported a method to form a hybrid membrane composed of silica surfactant nanocomposites inside a porous alumina membrane, wruch functions as a nanometer-order si z e-exclusive separation (83) In this work they added a precursor solution of TEOS (tetraethoxyortosilicate) and CT AB (cetyltrimethylammoruum bromide) to the alumina membranes r e sulting in the deposition of silica-surfactant nanocomposites into the porous alumina membranes T h ey

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19 were able to separate two small protein molecules myoglobin and bovine serum albumin, (diameter 2: 4 nm) from two other smaller molecules rhodamine Band v itamin Bl 2, ( diameter :S 2 .4 nm) Nanorods made in alumina membranes were used as gene delivery systems (85). Leong and co-workers fabricated nickel-gold nanorods by template electrodeposition in alumina membranes. Transferrin an iron transport protein was bound to the Au segments by a tluol linkage. They served to promote cellular uptake of the rods by a receptor mediated pathway The Ni portions were functionalized with DNA plasmid that contained a fluorescent reporter gene. They showed that the nanorods were i nternali ze d by the cell but they did not enter to the nucleus. These nanorods have two functions one to target the cells and to deliver the DNA In the nucleus green fluorescence was observed, indicating the delivery of the reporter gene into the nucleus Porous alumina membranes in a tubular shape were made when the aluminum to be oxidized was purchased in the form of wires or cylinders These porous a lumin a tubes were used in studies of catalysis (86), and as drug deliver y s ystems (87). Sol-Gel Chemistry Sol-gel chemistry is a powerful m et hod to generate inorganic materials It originated in the 19 70' s as scientists attempted to find low temp erature routes to glass synthesis (88 89). The high temperatures (1300 to 2000C) n ee d e d to form g lass are a result of the need to destroy the crystallinity of the precursors; that is eve n the g l ass is an amorphous material it is ge nerally m a d e from crystalline oxide precursors As a result a method to us e noncrystalline precursors was searched for. It was found that liquid alkoxysilanes hydroly ze r eadi ly in the presence of water to form s ilanols by the followin g process :

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20 R 0 Si-O-R+H O + R-OH 3 2 3 (1 -3 ) The silanols than can undergo further polymeri za tion reactions with another silanols or other alkoxysilanes: R ~ Si-O-H + H-O-SiR ~ + H 2 O (1-4) R 0 Si-O-H + R-O-SiR + R-OH 3 3 3 3 ( 1-5 ) In both cases the result is formation of a three-dimensional siloxane network. At the start of the polymeri za tion many small siloxanes particles are formed. They are very well dispersed in the liquid phase and form colloids. When the particles are we ll isola t ed from each other the density of the suspension res e mbles that of the solvent. At this stage the colloidal form is called a sol ". As polymeri za tion continues, the particles increase in size and the viscosity of the solution increases. The particles d eve lop a three dimensional network throughout the solution which is named a "ge l (90) Temperature solution pH water concentration and the type of the alkyl group are parameters that influence th e rate of hydrol ys is and polym e ri za tion (9 1 ). T he rate of ge lation incr eases wi th the temperature T h e hydrol ys is reaction is very s l ow and entails the replacement of alkoxy gro up s w ith h y dro xy l groups. It is much faster when the r eactions are eit h e r acid or b ase ca t a l yze d (92) A l arger, mor e sterica ll y bulk y alky l gr oup s l ows down the reac tion rate (92). T h e r e are two ways of converting gels to silica. In the first method, the gel i s h eate d or plac e d und e r vac uum to remove the so l vent phas e. T h e open three-dimensional structure co ll apses con d ensing it into a d e n se phase ca ll ed a xeroge l (91) In the second method the liquid is e liminat ed by a critica l -point drying procedure, forming a porous

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21 material called an aero gel (93). The maximum temperature for both processes can be kept below 1 oo 0 c. Silane Chemistry Siliceous surfaces (e.g. silicates and alurninates) can be derivatized with a large variety of different functional groups using silane chemistry. Organosilanes form cova l ent bonding with these surfaces (94). The general formula of an organosilane is RnSiX. < 4 -n ) where X is a hydrolyzable group capable of forming strong covalent bonds with the hydroxyl groups on silica surfaces such as halogen, alkoxy or aciloxy The R group is a nonhydrolyzable group that may posses a desired functionality (95). The two most used types of organosilanes for surface modification are chlorosilanes and alkoxysilanes. The attachment chemistry of both types is equiva l ent because when the chlorosilanes are dissolved in alcohol, they react with the alcohol to form alkoxysilanes: R ~ Si-Cl+ R-O-H R ~ Si-O-R + HCl (1-6) The extent of this reaction can be monitored by measuring the pH Alkoxysilane chemistry is analogous to the sol ge l formation chemistry Silanes with one hydrolyzable group can be utilized to produce monolayers on the surfaces. Because there is only one reactive group, the silanes can either bind to the surface or dimerize. Dimers cannot bind further and can be washed away The si lan es with one hydrolyzable group yield to hydrophobic surfaces (95). When surfaces with a higher degree of coverage are desired silanes with two or three hydroly z able groups are used. These are first allowed to oligomeri z e in a slightly aqueous a l cohol solution (water content is typically 5 % vo l/v ol) in order to initiate the formation of silanols (hydrolysis step) (94) The pH is adjusted between 5 and 5 .5 with acetic acid to further faci li tate the substitution reaction of the

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22 alkoxysilanes (94). The surface to be modified is than added to this solution and the oligomers bind to the surface through the surface hydroxyl groups (coupling step ) Figure 1-9 shows the reactions involved in the hydrolysis and coupling steps Surfac e modification by this route requires only a few minutes of immersion If a 2 % of trialcoxyor trichlorosilane solution is used the resulting modified surface is normall y 3 8 monolayers thick (95). The silani z ed surfaces must be cured usually at 120 c for 30 minutes or for 24 hours at room temperature. Chlorosilanes can also be deposited from aprotic solvents, such as toluene and tetrahydrofuran (94) If these solvents are anhydrous ( and the surface is fre e of wat e r ), then no alkoxysilane can be formed and no polymerization of the silanes can take place The reaction must proceed by the nucleophilic attack from surface h y dro xy l sites and as a result only one monolayer can be formed (94). Surface modification in these cases takes longer time usually 12-24 hours.

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Step 1. Hydrolysis Step 2. Coupling Si 0 Si 0 Si 0 H H . . 0 HO,.J})H (/) < >OH OH 23 OH --v/\/\siLoH + 3ROH 'oH Glass surface Si 0 Si 0 Si 0 0 0 HO' \
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24 Carrier proteins bind specific some molecules that are transported. They then undergo confonnational change that allows molecules to pass to the other side of the membrane. Channel proteins fom1 open pores through the membrane, allowing free diffusion of any molecule of the appropriate size and charge. In biological systems this phenomenon is called facilitated diffusion. By the 1950 's, scientists started to develop synthetic analogs of natural systems that function on the base of facilitated transport concept. Facilitated transport that uses a chemical complexing agent immobili ze d into a synthetic membrane has been the subject of numerous articles (96-104). Facilitated transport was accomplished in liquid membranes in which two aqueous phases were separated by an organic solvent containing carrier molecules, such as crown ethers. Diffusion of metal ions in liquid membranes is governed by the complex formation with the carrier at the aqueous / organic interface and the selectivities are generally very high. The fluxes in the membranes are very low because they are limited by the convection of the carrier in the organic phase (104). The bi gges t disadvantages of using liquid membranes are the low fluxes the l eac hin g of the carrier and the poor physical stability. These problems have prevented wide-scale application of liquid membranes in industrial separations. Polymeric facilitated transport has been applied more recently to eliminate liquid loss Tsuchida and co-workers have published results based on various metalloporphyrins cast into polymer films for selective 0 2 transport (105 106) and N 2 transport (107) Yoshikawa et al. d escribed CO 2 transport in thes e fixed site carrier membran es (108). Polymeric facilitated membranes hav e been applied also to ion separations. For in stance polymer inclu s ion m embra n es containing crown et her carriers wer e used to separate

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25 potassium from sodium and ru b idium (97), an d potassi u m from lithium (101). Facilitated transport of metal ions resu l ted in good selectivity with marked improvement in membrane stability as compared to liqu i d membranes. Some other applications include transport and separation of ethane and ethane through Nafion membranes (109), olefin (110) and small carbohydrate separation (111). The first faci li tate d transport-based system described was that of Scholander (112) who showed that oxygen diffusion through a filter paper membrane containing a hemoglobin so l ution was enhanced. O xygen diffusion through a membrane that has been soaked in methemog l ob i n, which has no carrier oxygen binding capacity, showed the same low diffusion rate that wou l d be expected for simple diffusion of oxygen through water. However, in the presence of hemoglobin an additional amount of oxygen is carried through the membrane due to the hemoglobin-oxygen complex formed in the membrane (113). The increase in oxygen transport due to the action of hemoglobin as a carrier is termed the "facil i tation effect" (1 1 4). Figure 1-10 shows a typical nonlinear flux pattern for carrier mediated facilitated diffusion. Flux Enhanced diffusion Facilitation Effect Passive diffusion Concentration Figure 1-10. Typical non l inear flux pattern for carrier-mediated diffusion.

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26 As can be seen in Figure 1-10 facilitated diffusion occurs at low concentration of feed solution Facilitation effect reaches a maximum value due to the saturation of carrier molecules which binds the analyte (115). The basic mechanism for this enhanced transport is a reversible reaction (see equation 1-7) between an analyte molecule A which can enter the membrane phase, with a carrier B, which is immobilized on the membrane (114). A+B<:=>AB (1-7) In this process both the chemical reaction and diffusion occur simultaneously in the system, resulting in an accelerating transport of the permeate species A through the membrane. C: 0 .:; co I,. C: Q) (.) C: 0 (.) Membrane C r oss Sect i on Leng t h Concentration gradient in the case of facilitated diffusion Concentrat i on g r a di e n t in the case o f pass i v e d iff u si on Figure 1-11. Schematic representation of how facilitated transport works. A schematic explanation of how facilitated transport works is shown in Figure 111 where CAf represents the concentration of the permeant A in the feed side C 8 is the

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27 concentration of the immobilized carrier and CAp is the concentration of the permeant A in the permeate side. According to Fick's fust law of diffusion, the flux of a permeate molecule across a membrane is directly proportional to the concentration gradient across the membrane. One-dimensional representation of the Fick' s law ( see equation 1-8) has the following form: J=-Dac ax (1-8) In equation 1-8, J represents the flux, D is diffusion coefficient and ac represents ax concentration gradient of a permeate molecule across the membrane. Inside the membrane the concentration of the immobilized carrier is higher than the concentration of the permeate molecule in the feed side. Due to that the concentration gradient for the permeate molecule that react with the carrier is higher than the concentration gradient of a pem1eate molecule that does not interact with the carrier and is transported by passive diffusion. This results in an enhanced flux of molecules that interact with the carrier, compared with those that do not interact. Single Pore Polymeric Membranes Ion channels and pores are crucial for functioning of a living organism (116 11 7 ). Channels and pores are the principal nanodevices mediating the communication of a cell with other cells where ion channels serve as extremely sensitive electromechanical devices that regulate electric potential, ionic flow, and molecular transport across cellular membranes (116). Emulating the function and structure of these natural nanodevices would be very helpful in designing new types of biosensors and understanding the ion transport through nanopores.

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28 It has been shown that a protein nanopore ( e.g.,the a-hemolysin channel) which is embedded into a lipid bilayer membrane, can function as a biosensor for biomolecules for example, DNA (118). The sensing procedure is based on directing the biomolecule to the pore by means of an electric field. When passing through the pore a biomolecule brings about its temporary blockage which is observed as a change in the ion current signal. The ion current blockade depends on the structure and chemistry of the biomolecule (e.g. the DNA sequence) (118) which is the basis of its detection. This biological pore is however quite fragile. A more realistic approach to applying this idea on an industrial scale would involve replacing the protein channel with a durable synthetic nanopore. Recent research has shown that a single conical-shaped pore generated in a polymeric foil presents similar transport properties to those of natural biological channels (119-123). In these studies they have prepared model nanoporous systems of known geometry and chemistry to study the relationship between the structure and transport properties of nanopores, as well as creating abiotic analogues of biological channels. Such an approach enab l es one to focus on the basic physical and chemical phenomena underlying biochannels function. A special emphasize was given to the family of voltage-gated channels. Ion current rectification and the dependence of ion current fluctuations on voltage across the membran e are fingerprints of this type of chann e l (117). The synthetic pores studied were prepared by the track-etch technique This technique is based on irradiation a polymer foi l wit h swift heavy ions and subsequent c h emical development of th e lat e nt tracks (37) What differ e ntiates the track e tchin g technique from conventional lithographic methods is the sing l e-particle exposure. It is one swift heavy ion which

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29 penetrates the foil and produces one latent track (37). Subsequently, one latent track after chemical development results in the formation of one pore. Counting the number of ions, which penetrate the foil gives a possibility to prepare membranes with a designed number of pores. Controlling the irradiation down to one ion enables preparin g a macroscopic sample containing just one pore. The Department of Materials Research GSI Darmstadt possesses a unique world wide facility suitable for single-ion irradiation (37) A membrane with a single pore creates an optimal system for fundamental studies of ion transport through nanopores, because averaging effects resulting from ion transport through many pores can be avoided. To prepare voltage-gated nanopores, an asymmetric pore geometry has been used because it was found that biological voltage-gated channels are asymmetric (124-126). The conically shaped nanopores in polymer membranes were shown to rectify ion current and ex hibit ion current fluctuations of similar statistical properties as the ion current through biological voltage-gated channels (119, 121 ) The application of a single conical gold tube membrane to protein biosensing will b e presented in chapter 5. The steps invol ved in preparing these membranes are present ed h ere, and are as follows: Irradiation with heavy ions Polyethylene terephthalate (PET) (Hostap han RN12 Hoechst) and polyirnide (Kapton HN50, Du Pont) foils, ha ving a thickness of 12 mare irradiated with single swift heavy ions at normal incidence Figure 1-1 2 shows the chemical formula of P E T and Kapton.

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30 A H H -0I I tr TT -OT ? 0 0 0 H H n n Figure 1-12 Chemical formula of the PET (A) and Kapton (B). Gold xenon and uranium ions of energy 11.4 MeV per nucleon are used at the linear accelerator UNILAC (GSI Darmstadt). At this energy the penetration range of ions in PET foil is lar ger than the thickness of foils and the energy loss of ions along the track is well above the energy threshold which assures a homogeneous etching (127). Single ion irradiation is performed by defocusing the ion beam and placing a metal mask with an aperture of 0.3 mm in front of the polymer foils The ions pass through the aperture in a discrete way and as soon as one ion reaches the detector placed behind the sample the beam is switched off by a beam chopper within several microseconds Ion track etch in g Chemical etching of single-ion irradiated foils is performed in a conductivity cell connected to a voltage source and picoamperometer (see Figure 1-13) u etchant I stopping solution Figure 1-13 Schematic representation of a conductivity cell used for chemical etching

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31 To obtain conical pores, etching is performed only from one side. The other side of the membrane is protected against etching by a stopping medium which neutralizes the etchant (121,122,128,129). For etching of PET, 9 M NaOH has been used therefore an acidic solution plays the role of a stopping medium. Ion tracks in Kapton were developed in sodium hypochlorite with 13 % active chlorine content. A stopping medium of 1 M potassium iodide was used which serves to reduce the OCr ions acti v e in etching, to er (122,129). The chemical stopping is supported by an electrical one. The platinum two electrode system is configured in a way that the anode is placed on the etching side and the cathode is placed within the neutralizing side (128) At the very beginning of the etching process the two halves of the conductivity cell are not connected with each other and the ion current measured is zero. When the pore is etched through the ion current increases gradually indicating increase of the pore diameter The etching process is stopped by washing the pore with a stopping medium and water. The big opening of the pore, D, has been determined by scanning electron microscopy For conical pores in PET, D ~ 600 nm and for pores in Kapton D ~ 2 m. The difference in D values results from difference in non-specific etching of the two polymers the so-called bulk etch rate, which detem1ines the big openin g of the pores (129) The small opening of the conical pores is below scanning electron microscop y resolution and its diameter d was estimated by measuring a current-volta g e characteristic of a single nanopore in a standard solution of 1 M KCl. Assuming an id e al conical shap e of the pore its small opening can be calculated using the following equation (128 122): d = 4LI KnDU (1-9)

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32 where L is the length of the pore, K stands for the specific conductivity of the electrolyte, U denotes the voltage applied across the membrane and I is the ion current measured. This etching process gives the possibility of producing pores with an effective diameter d as small as 2 nm. Gol d electro l ess plating The single conical tube membranes are obtained using a template synthesis method Single pore membranes are electroless plated w i th gold ( 40) as described before in this chapter. Dissertat i on Overview The aims of the research presented in this dissertation are to investigate potential applications of the nano tube membranes in chemical and biochemical sensing and transport. Chapter 1 provides background information on the template synthesis method and two types of templates (porous alumina and polymeric membranes) that are used in this research. Chapter 2 presents the preparation of a biomimetic ligand-gated ion channel membrane, based on a microbattery / nanoporous system. This membrane turns on the battery and attendant ion current in the presence of a targeted chemica l stimulus (a surfactant in this case). This microbattery was prepared by depositing anode and cathode materials on either side of a nanoporous alumina membrane The pores in the membrane were made hydrophobic by reaction with an 18 -ca rbon (C 18 ) alkyl silane. When placed b etwee n two salt solutions, the pores in the C 1 8 -modified membrane are not wetted by water (the biomimetic ga te is closed) and thus the microbattery is "off'. When exposed to a surfactant solution, the surfactant mo l ecules partition into the hydrophobic

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33 membrane causing the biomimetic gate to open, which results in a high flux of ions through the nanoporous membrane, and consequently, the microbattery turns "on". Once on" the microbattery discharges and the discharging current is collected in an external circuit. Chapter 3 presents silica nanotube membranes are used to prepare highly selective membranes for protein separation. Two antibodies with different affinities for hevein have been immobilized on highly ordered porous alumina membranes. Hevein was labeled with green fluorescence protein (GFP). The transport of both GFP-Hevein and red fluorescence protein (RFP) which was used as a control analytehas been monitored. The transport of both proteins has been recorded simultaneously at two different emission/excitation wavelengths. As a control experiment we used membranes with an immobilized antibody that does not have any affinity towards GFP-Hevein or RFP. The alumina membranes were prepared by two step anodization method having pore diameters between 50 and 100 nm and thickness from 40 to 200 mm Both the influence of pore diameter and the membrane thickness on the transport of GFP-He v ein and RFP were studied. These membranes selectively transport the protein (GFP-Hevein) that binds to the antibody, relative to the other protein (RFP) that has no affinity for the antibody Chapter 4 explores another application of the porous alumina membranes, in this case, serving as protein microarrays Two methods of preparing alumina-based microarrays are presented. The first method implies growing alumina membranes on a pre-patterned aluminum surface. In the other approach commercial alumina m e mbranes are patterned by electrodeposition of silver in certain areas. The influence of the

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34 thickness of the membranes on the fluorescence intensity and also the capability of thes e microarrays to selectively recognize different analytes were studied Chapter 5 deals with a new class of artificial ion channels based on a synthetic membrane that contains a single conically shaped nanotube. These nanotube-based abiotic ion channels exhibit transport properties analogues to voltage-gated biological channels. The ion current through a single nanotube fluctuates in time in a voltage dependent manner as well as it is rectified. The membrane with a single conically shaped gold nanotube was prepared by the template method The nanotube has a large-diameter opening of ~ 600 nm and a small-diameter opening of 2 5 nm. In the biosensing application the nanotube-containing membrane is placed between the two chambers of a conductivity cell filled with an electrolyte. Electrodes present in each half-cell solution are used to apply a transmembrane potential and measure the resulting ion current through the nanotube. The internal surfaces of the nanotube are modified with a specific biochemical molecular-recognition agent (the 'capture" agent, e.g ., an antibody) which interacts specifically with a given biomolecule (the analyte) present in one of the contacting solution phases. The binding interaction between the nanotube-bound capture agent and the solution-phase analyte is transduced as a change in the ion current that flows through the nanotube. This new biosensing technology was demonstrated usin g both biotin as the capture agent and streptavidin as the analyte and protein G as the capture agent and IgG as the analyte. The detection of a biological warfare ag e nt ( ricin) is also presented. The results and conclusions of this dissertation are summari z ed in C hapt e r 6

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CHAPTER2 ION CHANNEL MIMETIC SENSOR WITH AN ON-BOARD MICROBATTERY Introduction Ion channels are the heart of many biological processes including nerve activity and muscle contraction Channels operate by being either open or closed There are several aspects of the channel environment which affect the channel opening (gating) such as voltage, a molecular ligand phosphorylation or mechanical stimulus (1 1 6) Mimicking the principles of such natural sensor system is of great importance in sensor development (130,131). One example of a natural ligand-gated ion channel is the acetylcholine -g ated ion channel (132) which is closed ("off' state) in the absence of acetylcholine but opens (and supports an ion current, "on" state) when acetylcholine binds to the channel. This concept of ion-channel mimetic sensing originally proposed by Umezawa's group (133), has been of considerable interest in analytical chemistry (134-136) In the biological channel there are no electrodes, and the ion current is driven by an electrochemical potential difference across the cell membrane (137). That is the cell membrane has its own built-in transmembrane power supply that drives the ion current when the channel opens. Whether this power supply can be utili ze d in this way depends on whether the channel is open or closed We describe h ere the preparation of a biomimetic ligand -ga ted ion channel membrane, bas ed on a microbattery / nanoporous system. To explore this concept we prepared h ydrop hobic microporous a lumin a membranes as before, but we deposited a 35

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36 thin-film battery anode onto one face, and a thin-film battery cathode onto the opposite face, of the membrane. Hence in analogy to the naturally occurring channel case, we have an ion-channel mimetic membrane with a built in electrochemical potential difference across the membrane We show here that in the absence of the ligand (again a hydrophobic ionic surfactant), the membrane is in its "off' state, and the electrochemical potential difference cannot be utili ze d to drive a transmembrane ion current. In contrast, when the ligand is detected the membrane switches to its "on" state and the transmembrane battery discharges producing a corresponding transmembrane ion current. Experimental Materials Octadecyltrimethoxysilane was obtained from Aldrich. Dodecyltrimethylammoniurn chloride, hexadecyltrimethylammoniurn chloride, dodecylbenzenesulfonic acid, and the nonionic surfactant Triton X-100 were obtain e d from Acros Chemicals. Octyltrimethylammonium bromide was obtained from from Fluka and N-Dodecyl-N N-dimethyl-3-ammoniol-propanesulfonate from Sigma. Silver powder 99.9% was obtained from Strem Chemicals and z inc powder (99.33%) from Fisher Chemicals. All chemicals were used as received. MiliQ 18-MQ water was u sed for preparing all aqueous solutions. Commercial porous alumina membran es ( ~ 200 nm diam eter pores, 60 m thick) were obtained from Whatman Inc. Silanization of the Alumina Membranes A so lution that was 5% (v / v) in octadecyltrimethoxysilane (C 1 8 -s ilan e) was prepared in et hanol ; to this solution was added acetate buff er (50mM pH = 5. l ) to make the so lution 5 % (v / v) in this buff e r. The r es ultin g solution was st irr ed for 30 minutes and th e alumina m e mbran e was th e n immersed After 2 hours th e m embrane was removed

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37 from the solution and rinsed with ethanol. The membrane was sonicated for 10 rrunutes in ethanol to remove the physisorbed silanes from the surface. The modified membrane was cured at 150 C in air for 20 min The perfom1ance of the coating was assessed b y measuring a contact angle of 130 ) Microbattery Fabrication As shown schematically in Figure 2-1 the anode and cathode of the battery were deposited as thin films coating the faces of the C 1 8 -modified membrane. These films were deposited by thermal evaporation of either Zn (anode material) or Ag (precursor to cathode material) from a tungsten boat. A Denton Vacuum DV-502 vapor-phase depositor was used. The pressure inside the deposition chamber was ~ 10-5 Torr Deposition time was 10 minutes for both the silver and zi nc films. The Ag film was deposited first and then a portion at the surface of this film was converted to AgCl which acted as the cathode for the microbattery. This was accomplished by immersin g the silver-coated membrane in an aqueous solution that was 0 lM in FeCh and 0.3M in HCl. The Zn film was then deposited on the opposite face of the membrane. It is important to point out that these films are porous and are thus permeable to ions and molecule present in solution phases that contact the membrane (vid e infra)

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38 l] [] lD l] Ag [] 0 1 MFe0 3 [l Zn lD 0.3MHO lrerrml 1rerrml evaix>ration evaix>ration l] [] [l lD Ci g -rrodified alumina Ag,'Ci g -rrodified Ag0Ag,'Ci 8 -mxlified Ag:JAg/Ci g -rrodified alumina alurrina Alumina/Zn Figure 2-1 Schematic representation of the micro battery fabrication Scanning Electron Microscopy (SEM) SEM was used to study the surface morphology of the anode and cathode films. Data were obtained using a JEOL 6400 microscope. Elemental compositions for the films were obtained using an Oxford energy dispersive spectrometer (EDS) attached to the JEOL microscope. Cell Assembly and Battery Discharge Measurements After deposition of the electrode films the membrane was sandwiched between two pieces of Scotch tape that had 0.47 cm diameter holes punched through them These holes defined the area of the membrane exposed to the contacting solution phases. In addition the tape was used to attach a Pt foil lead to the surface of each battery electrode film in order to make electrical contact with the electrodes The membrane was then mounted between the two halves of a U-tube permeation cell (31 40 43) Figure 2-2 shows a schematic representation of a U-tube permeation cell. The electrolyte solution used in both half-cells was 0.1 M NaCl. As noted above surfactants were used as the ligand or chemical stimulus to tum the transmembrane micro battery from off to on ."

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39 This was accomplished by injecting the desired volume of a stock surfactant solution into the 0 1 M NaCl in both half-cells The surfactant solutions were also 0.1 Min NaCl. The battery discharge current was monitored using a potentiostat (EG&G model 273) interfaced to a PC running CorrView and CorrWare software packages (Scribner Associates Inc. Southern Pines North Carolina). / Glass -cell Feed so lution Membrane ~ Permeate solution Figure 2-2. Schematic representation of a U-tube permeation cell. Results and Discussions Characterization of the Electrode Films Stirring bars Surface and cross-sectional SEM images (Figure 2-3) show that both the Ag/AgCl and the Zn thin films are porous This porosity results because the films are deposited as particles The cross-sectional images indicate that these particulate films are ~ 500 run thick and that deposition does not propagate down into the pores (The particles seen in the pores in the cross-sectional images were dislodged from the surface films during fracture of the membrane )

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40 EDS spectra for the Ag A 0 AgC I and Zn films are shown in Figure 2-4. The Ag film (F i gure 2-4 A) shows prominent peaks for Ag and Au; the Au peak results because the surface of the film was sputtered with Au prior to taking the SEM image. Much v eaker signals are observed for Cu (from the Cu foi l tape used to attach the sample to the SEM stub) and Al and O (from the underlying a lumin a membrane). The upper surface of the Ag film was chemically oxidized to AgCl which served as the cathode for the transmembrane microbattery. Ag/ AgCI film Zn film C111.:1111~t,y Sll 1~JlkV ><22~ WO 13 0111111 Cross-section Cross-section Top view Top view Figure 2-3. Cross sectiona l (upper) and surface ( lo wer) SEM images of the batter y e l ectrode films that coat the faces of the alumina membrane After o x idation a prominent Cl peak is observed in the EDS spectrum (Fi g ure 2 -4 B). The Zn film shows prominent peaks for Zn and Au and much weaker Al Cu and 0 (Figure 2-4 C)

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41 0 2 4 6 8 10 12 14 16 18 20 keV 0 2 4 6 8 10 12 1'4 16 18 20 0 2 4 6 8 10 12 14 16 18 20 kt!N Figure 2-4. EDS spectra of the membrane surface after deposition of Ag (A) and after conversion of the Ag surface to AgCl (B) EDS spectrum of the opposite membrane surface that had been coated with Zn (C) Battery Discharge Experiments Control e x periments were first conducted with membranes that were not modified with the hydrophobic C 1 s -silane As described above a Zn anode film was applied to one face of the membrane and a Ag/AgCl cathode film was applied to the opposite face. The membrane was mounted in the U-tube cell and the electrode films were connected to the leads of the potentiostat. However the half-cells were initially devoid of electrolyte solution and as a result there was no ionically conductive pathway through the membrane to link the anode and cathode films This prevented battery discharge and no current was detected (t < 7 min Figure 2-5 A). At t = 7 minutes electrolyte (0.1 M

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42 NaCl) was added to both half-cells Because the untreated alumina membrane is so hydrophilic electrolyte immediately flooded the pores, allowing for ionic conduction between the anode and cathode films This allowed the transmembrane microbatter y to discharges via the following discharging half-reactions : Zn 2 + + 2e 2AgCI + 2e 2Ag + 2Cr E 0 = 0.763 V E 0 = 0.222 V (2-1) (2-2) As indicated by E 0 values this battery delivers almost 1 V As shown in Figure 2-5 A the current raises immediately to a peak value of ~2 50 A and then decays away w ith time Before this experiment, the face of the membrane coated with the AgCI cathode film was dark purple in color due to the AgCl. After this experiment this face of th e membrane was white indicating that all of the AgCl had been reduced during the battery discharge This explains why the current ultimately decays to ze ro (Figure 2-5 A). An analogous experiment was conducted with a C 1 s-modified membrane that had the Zn anode and AgCl cathode films on its surfaces (Figure 2-5 B) In this case electrolyte was added to the half-cells at t = 0 However, the current obtained is at t he noise level of the potentiostat indicating that battery discharge is prevented. As shown in our prior work, this is because the hydrophobic pores are not water wetted (138) and as a result there is again, no ionic-conduction pathway through the membran e. These results show that when the hydrophobic microbattery membrane is exposed to Na C l solution, t he membrane is in its off state, and transmembrane battery dischar ge is pr eve nt e d

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43 0 0 003 ------------~ A 00002 i t 00001 -00001 '---~------'---~---'---~---' 0 1000 2000 3000 T1me(Sec ) le 10 i,e-10 E Je 10 -4e 10 -5e-1 0 0 B II I I I 1 11 11111111 r 111 11 1 1 1 1 II J t I 1 I 1 1 )1 1000 2000 3000 T1me ( Sec ) Figure 2-5 Current-vs.-time response for the transmembrane microbattery applied to an alumina membrane that was not rendered hydrophobic by silane functionalization (A) Analogous current-vs.-time response for the hydrophobic C 18-modified membrane (B). Figure 2-6 shows current-vs.-time data for the C 1 8 -modified membrane before and after injection of dodecylbenzene sulfonate (DBS) into the half-cell solutions Prior to injection of DBS t < 200 s the membrane was again in its off' state, and battery discharge was prevented At t = 200 s DBS was injected to make the DBS concentration in both half-cells 1 mM After injection there was an induction period followed by a time region in which a low-level discharge current ( ~ 1.5 A) was observed (inset Figure 2-6). This low-level discharge current flowed for ~ 1300 s after which a burst of current at a much higher level was observed. Analogues results were obtained for C 1 8 membranes upon exposure to the cationic surfactant dodecyltrimethylarnmonium (DT A) These results are in many ways similar to results obtained in our prior investigations of the effect of DBS on the ionic resistance of the C 18 -modified alumina membrane (138). First when 0.1 M KCl was present in both half-cells without added DBS the membrane resistance was very large ( > 50 MQ), again signaling the off' state of the m e mbrane Addition of low levels of DBS to both half-cells( < 1 M) caused the

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44 membrane resistance to decrease, but still the resistance remained high ( > 20 MO). When the DBS concentration reached 10 Ma precipitous 4-order of magnitude drop in resistance was observed. The key point is that two "o n" states were observed a high resistance on state at low concentrations of DBS followed by a sharp transition to a low-resistance "on" state at higher concentrations of DBS. We showed that the sharp transition from the high-resistance "o n" state to the low resistance "on" state is associated with flooding of the pores with the electrolyte solution (138). That is, at some critical solution-phase concentration of DBS the quantity of DBS partitioned into the membrane is sufficiently high that the pores are no longer hydrophobic and water cannot be prevented from entering the pores In this flooded state charge is carried through the membrane by migration of ions in the solution-filled pores. At lower DBS concentrations the ionic current is presumably carried b y surface migration of the DBS and attendant counterion along the pore walls in pores that are devoid of water (138). This accounts for the high resistance of this "on" state. In the transmembrane microbattery experiments described here after injection of DBS into the electrolyte solutions, DBS must diffuse through the porous electrode films (vide infra) and then into the hydrophobic por es. The two "o n" states observed previously (138) are analogous to the two current-levels observed here. The low current "o n state ( e.g. inset Figure 2-6) is associated with surface migration in pores d evo id of water and the sharp transition to the higher current "o n state is associated with floodin g of th e pores with water and electro! yte As b efo re flooding occurs when diffusion brings some critical lev e l of DBS into the membrane. Finally, the induction period prior to the low current "o n state is simply associated with achieving a hi g h e nou gh quantity of DBS

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"' a. E <( 45 in the membrane such that a discharge current above the detection limit for the potentiostat can be supported. 0 0 0 0 5 0 000 4 0 0 0 0 3 0 0002 0 0001 0 -0 000 1 0 l I 1 000 I 2000 T i me(Sec) I 3000 Figure 2-6 Current-vs.-time response for a hydrophobic membrane before and after injection ofDBS surfactant solution. After injection the DBS concentration in both half-cells was 1 mM. The timescale of this induction process however seemed long; e.g. in Figure 2-6 it takes in excess of 1300 s before the critical membrane level of DBS is achieved. Th.is suggests that there is some barrier to transport of DBS into the membrane. The most likely source ohhis barrier is diffusion of DBS through the battery electrode films on the surfaces of the membrane. To explore this issue we attempted to make thinner electrode films however because of the particulate nature of these films the lateral electronic resistance of these thinner films was too high and battery discharge was not observed. To circum ent this problem we first sputtered both faces of the membrane v ith a thin (25 nm) layer of Au. Thinner Ag and Zn films (400 nm as opposed to the 500 nm

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46 used abo e) were then thermally e aporated onto these Au films. In essence, the Au films act as current-collectors for the overlying battery electrode films. We found that the induction times for these thinner battery electrode films were shorter than for thicker films For example, with the 1 mM DTA solution a membrane with the thinner battery electrode films showed a response time of 400 s as opposed to 1000 s for the membrane with the thicker films. These results show that transport of surfactant through the battery electrode films is a kinetic barrier in this system. Effect of Surfactant Concentration on the Response Time The response time of this device is defined as the induction time period between injection of surfactant into the half-cell solutions and observation of the low current on" state Over the concentration range 0 01 mM to 1 mM the response time is inversely proportional to the solution-phase DBS concentration (Table 2-1 ). This result is consistent with our model that the response time is associated with transport of DBS through the electrode films and into the pores of the membrane. Higher DBS concentrations yield higher concentrations at the membrane solution interface and thus higher net fluxes into the membrane. As a result the time required to achieve a concentTation of DBS in the membrane sufficient to support the low current "on" state decreases with increasing solution-phase DBS concentration. Table 2-1. Effect of DBS concentration on the response time. DBS Concentration (mM) Response time ( s) 2 350 1 1.5 0.1 52 0.01 70

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47 Table 2-2 shows that analogous results are obtained for the cationic surfactant DTA ; however at both the 0.01 and 0.001 mM levels the response times for DTA are about a factor of three times higher than for DBS. These results also fit our diffusional transport model because the diameter of the DT A head group is larger than the diameter of the DBS head group ~ 3.7 nm vs ~ 2.0 nm (139) The larger diameter for the DTA head group makes the surface diffusion coefficient smaller and as a result the diffusional transport time longer. Table 2-2 Effect of DTA concentration on the response time DTA Concentration (mM) Response time ( s) 1 1000 0 1 140 0.01 216 0 001 600 When the solution-phase DBS concentration is increased to 2 mM the response time goes up again indeed to a value higher than is observed for the lowest DBS concentration (Table 2-1) While analogous results are obtained for DTA the concentration producing the longest response time (1 mM Table 2-2) is lower than for DBS. Our initial hypothesis was that these longer response times at the highest surfactant concentrations were in some way associated with micelle formation ; howe v er the critical micelle concentrations (CMCs) for DBS and DTA are 1.1 mM (140) and 4.4 mM (141) respectively. Hence while the concentration that yields the longest response time for DBS (2 mM) is above the CMC the concentration that yields the longest response time for DT A (1 mM) is below the CMC It is not yet fully understood why the response time goes up again for the high concentrations of surfactant.

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48 In estigations of Alkyl Chain Length on the Response Time During the in estigations of hydrophobic alkyl thiol-modified go ld nano tube m mbranes it as shown that the transmembrane flux increases with the hydrophobicity of the permeate mo! cule ( 44). This is because the flu is directly proportional to the partition coefficient for the permeate molecule at the membrane / feed-solution interface (Equation 2 in reference 44). The same principle should apply for flux of hydrophobic surfactant molecules into the C 1 -modified alumina membranes studied here. As a result response time should decrease with increasing hydrophobicity of the surfactant. To e plore this issue we investigated response times for three alkyl trimethylammoniurn surfactants (Table 2-3). In agreement with the above analysis, response decreases with increasing hydrophobicit y (alkyl chain length) of the surfactant. Table 2-3. Effect of alkyl chain length in alkyl trimethylammonium surfactants on the response time. Concentration in all cases = 1 mM. These results were obtained using the Cl8-modified membrane with thinner battery electro de films. Number of carbons in alkyl chain Response time (s) 8 > 3600 12 400 16 5 Conclusions It has been shown in this work that a microbattery / nanoporous membrane acts as a biomimetic' smart membrane' in the sense of emulating the function of ligand-gated ion channels i e. they can be switched from an "off' state to an "on" state in response to the presence of a targeted chemical stimulus. Modifying the aluminum oxide with long chain alkylsilanes makes the membrane pores hydrophobic and the microbattery is "off'. In the presence of surfactant the pores became hydrophilic which turns the microbattery "on". The results can be briefly summarized by pointing out three factors which influence the

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49 response time of the system: the hydrophobicity of the analyte (shorter response time for more hydrophobic analytes), the nature of the polar head group of the analyte (anionic surfactants are sensed faster than the cationic ones) and the concentration of the anal yte (shorter response time for lo wer concentration). This concept could ultimately lead to a remote sensing technology where the battery discharge current is use to dri ve a device ( e.g., a bu zze r) that signals to the outside world that the ligand has been detected

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CHAPTER3 HIGHLY SELECTIVE ANTIBODY-BASED NANOTUBE MEMBRANES FOR PROTEIN SEPARATION Introduction Many technically challenging and commercially attractive separation problems can not be solved with existing membranes because the typically achieved separations of complex mixtures are only fractionation into substance groups (142). Membranes with high selectivities for example for chiral drugs, toxins or complex biomolecules are required. The aim of current membrane development is preparing "tailored" membranes with high selectivity and/or high flux of the analytes of interest across the membranes; this can be achieved by developing membranes modified with molecular recognition elements, with high pore density and a narrow pore size distribution. Active research is devoted to highly specific membrane separations based on molecular recognition inside the nanoporous membranes (47,82,152) We report here a protein separation method based on facilitated transport selectivity that utilizes immobilized molecular recognition elements in a porous alumina membrane. We found that by modifying the walls of the alumina membrane pores with antibodies, proteins that have an affinity towards these antibodies are transported at a higher rate than proteins that do not interact with the antibodies. We used two Fab fragments (1C2 and 1A4) of antibodies that were grown against the protein hevein; 1A4 has higher affinity (Ki ~ 10 8 M) towards hevein than 1C2 (143) Hevein is a latex protein which has been identified as an allergen; it is a defense protein of the rubber tree 50

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51 Hevea Brasiliensis involved in the inhibition of several chitin-containing fungi (144,145). Hevein was produced as a green fluorescence protein (GFP) fusion protein (GFP-Hevein) in insect cells (143). In this way GFP-Hevein can be detected by fluorescence spectroscopy. Red fluorescence protein (RFP) was used as a control protein because it does not have any affinity towards any of the antibodies Because their excitation and emission spectra do not overlap (Aex G FP=395 nm AemGFP=510 nm, A exRF P=563 nm, AemRFP=582 nm) GFP and RFP are very well suited for dual-label experiments (146). Experimental Materials The antibodies ENA 11 His 1A4 and 1 C2 Fab fragments were pro vide d by VTT Biotechnology Finland. Red fluorescence protein (rDsRed2 protein) was purchased from BD Biosciences Cl on tech High purity aluminum foils 100 mm x 500 mm x 0.2 mm purity 99.9998%) were obtained from Alfa Aesar tetraethyl orthosilicate (TEOS) from Sigma Aldrich and triethoxysilylaldehyd e from Gelest. Fabrication of the Nanoporous Alumina Membranes We used a two-step anodization method (52,53) to fabricate the porous alumina membranes. Briefly the aluminum foils were first electropolished at 15 V in a solution with th e following composition : 95 wt. % H 3 PO 4 5 wt. % H 2 SO 4 and 20 g/ L CrO 3 T h e solution was heated at 70 The polished aluminum foil was anodi z ed at 40 50 and 70 V to obtain membranes havin g 50, 70 and 100 nm pore diamet er, respectively. We us ed 5% oxalic acid as th e e l ec trolyt e solution and th e anodi za tion ex p e rim en ts h ave b een done at O 0 c T h e first film of the membrane was dissolved away in an aq u eo us so lution that was 0 2 Min C rO 3 and 0.4 Min H 3 PO 4 at 60-70 The second anodi za tion step was carried out in exac tly th e same conditions as the first step This yie lds the d es ir e d

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52 highly ordered nanoporous alumina membranes. The aluminwn that was not oxidi z ed was dissolved into a saturated HgCl 2 solution. Then the barrier layer of the alumina membranes was removed in 5% H 3 PO 4 solution. Scanning electron microscopy was used to measure the pore diameters and the thicknesses of the a lumina membranes prepared A JEOL FE-SEM 6438 was used. Alumina nanoporous membranes (Figure 3-1) were used as templates for immobili z ation of the antibodies. Figure 3-1. Scanning electron micrograph of a porous alumina membrane with pores of 50 nm in diameter and pore density of ~ 1 0 1 0 pores / cm 2 Antibody Immobilization Figure 3-2 shows a schematic representation of the modification steps involved in antibody immobili z ation Silica nano tubes were deposited inside the pores of the alumina membranes using a sol-gel method (81 84). Briefly a sol-gel silica precursor was prepared by mixing absolute ethano l TEOS and 1 M HCl (50:50: 1 ) This solution

PAGE 68

53 was allowed to hydrolyze for 30 minutes. Alumina membranes were than immersed into the sol-gel for l minute under sonication, after which they were air dried for l 0 minutes at room temperature and cured in the oven for 12 hours at 150 C. Triethoxysilylaldehyde has been used to attach aldehyde terminal groups onto the pores of the membranes The free amino sites of the antibody Fab fragments react with the aldehyde groups via a Schiff base chemistry (147,176 177). The aldehyde-modified silica nanotube membranes were incubated for 12 hours at 4 c in a solution containing 0 2 mg/ml antibody Fab fragments solutions All solutions of the antibody Fab fragments, GFP-Hevein and RFP were made in phosphate buffer saline (PBS) solution having pH = 7.4. After washing them with PBS, the antibody-modified membranes were incubated for 3 hours in a blocking solution containing 1 % bovine serum albumin (BSA) and 1 % Tween-20 in PBS Blocking solution was used to block both the unreacted aldehyde groups and nonspecific adsorbtion The membranes were washed copiously with PBS afterwards and stored in PBS at 4 C until used in transport experiments. OH OH OH OH Surface of the silica nanotube membrane 0 t OVe Si OVe I ave 0 Q .,,..._ /"--..lj s( cH cf \ O O I > I /'.. /"--.. II .________, Si ,,. rn a Figure 3-2. Modification steps involved in antibody immobilization.

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54 Transport Experiments The antibody-modified si li ca nanotube membranes were sandwiched between two pieces of Scotch tape that had 0.314 cm 2 area holes punched through th e m These holes defined the area of the membrane in contact with the so lu tion phases. The membranes were then mounted between two halves of a U -tube permeation cell (40,43,4 4 ,148). The feed so lu tio ns had eq ual concentrations in GFP-Hevein and RFP. A vo lu me of 3 ml PBS was used on both halves of the permeation cell. The rate of transport (flux) was determined by periodically measuring the fluorescence intensity of the permeate solution using a Varian Cary Eclipse spectrofluorometer. GFP-Hevein and RFP were detected simu lt aneously Results and Discussions Effect of Antibody Affinity on Selectivity Coefficient Transport plots in Figure 3-3 show the number ofpicomoles of GFP-Hevein and RFP transported through th e nanotube membranes versus the permeation time A single membrane was c ut into three pieces and they were mod i fied with E A 1 lH i s Fab fragments (Figure 3-3A), 1 C2 Fab fragments (Figure 3-3B) and 1A4 Fab fragments (Figure 3-3C) respectively The membrane used fo r these experiments had pores 70 nm in diameter and a thi ckness of 90 A concentration of 10 nM in both GFP-Hevein and RFP in PBS was used in feed side with PBS on l y in the permeate side. Due to the fact that E A 1 lHis does not ha ve affinity for either GFP-Hevein or RFP, membran e s modified with this antibody were used for contro l experimen t s. As can b e seen from Figure 3-3A RFP is transported b y passive diffusion at a higher rate than GFP-Hevein, when the membrane is modified with E A 1 lHi s. This is due to higher molecular weight of GFP Hevein ; GFP and RFP ha e approximate l y the same molecular weight of

PAGE 70

55 28 000 Da (149 150) and Hevein has a molecular weight of 4 000 Da (151) When the antibody having an affinity towards Hevein (1A4 or 1C2 Fab fragments) was immobilized, the membranes transported GFP-Hevein at a much higher rate (Figure 3-3A and 3-3B) than they transported RFP. A : 1 QI -..-GFP-Hevein t:: 3 5 0 -RED C. 3 V) C: 2 5 nl ... ... 2 V) .S! 1 5 0 1 E c. 0 5 0 0 500 1000 1500 Time, min 3 5 "O 3 $ ... 2 5 0 C. C: nl 2 --+-GFP-Hevein -= V) 1 5 -RED QI 0 E 0 c.J ii 0 5 0 0 500 1000 1500 Time, min 7 "O 6 QI C t: g_ 5 V) C: 4 --+-GFP-Hevein nl ... ... V) 3 QI -RED 0 2 E .[ 1 i 0 0 500 1000 1500 Time.min. Figure 3-3 Transport plots of GFP-Hevein and RFP through ENA l lHis (A) 1 C2 (B) and l A4 (C) modified nano tube membranes.

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56 Because 1A4 and 1 2 Fab fragments bind hevein these data suggest that immobilization of these antibodies facilitates the transport of GFP-Hevein versus RFP The transport of GFP-Hevein through the membranes is not linear in time because the concentration gradient decays with time so the driving force for diffusion decays as well. Due to that the fluxes of GFP-Hevein and RFP through the membranes were calculated with respect to the linear part of the transport plots (the first two points of the plots). We defined a selectivity coefficient for a membrane s as the ratio between the flux of GFP Hevein and the flux ofRFP. Figure 3-4 shows the influence of the type of the antibody immobilized on the selectivity coefficient. I I I 25 I 21.5 20 15 3.6 s 10 i 0.6 5 0 I ENA 1C2 1A4 Figure 3-4. Effect of the antibody immobilized on the selectivity coefficient. As can been observed from Figure 3-4, immobilization of an antibody with higher affinity towards the analyte yields a higher selectivity coefficient. Immobilization of an antibody of high binding affinity towards an analyte, results in increase of the analyte concentration inside the pore. Consequently it leads to creation of higher concentration gradients across the membranes and hence higher fluxes

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57 Effect of the Feed Solution Concentration on the Flux and Selectivity Coefficient An important parameter in characteri z ing facilitat e d transport of the molecules through membranes is the feed solution concentration A plot of flux versus feed concentration should have a Langmuirian shape ( 4 7 82 152). We investigated the effect of the feed solution concentration on flu x es of GFP-Hevein and RFP (Figure 3-5) In these e x periments the membranes were modified with 1A4 Fab fragments and they had pores of 70 nm in diameter and 90 m thickness. 8 7 N 6 E (.) >< 5 .r. 1/) 4 0 E a. 3 >< :::::s U:::: 2 ---------------------+-GFP-Hevein -RED o.__.~~~!::: ::::: ~ :_____,--.-------,------r-----,--,------r-------,------r----.---r--~--l 0 5 10 15 2 0 25 3 0 3 5 40 45 50 55 60 65 7 0 75 80 8 5 90 95 1 00 Feed Concentration, nM Figure 3-5 Plot of fluxes of GFP-Hevein and RFP versus feed solution concentration. The plot showed in Figure 3-5 has a Langmuirian shape for GFP-Hevein. It can be observed that at high feed concentration the membrane transports RFP at higher rates than GFP-Hevein. At high feed concentration (100 nM) passive diffusion is predominant. Facilitated transport theory also predicts that the highest selectivity co ef ficient should be obtained at low feed concentrations. Figure 3-6 shows the transport

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58 plots of GFP Hevein and RFP through a 1A4 antibody-modified membrane when using 5 nM (A) 20 nM (B) 50 nM (C) and 1 00 nM (D) feed so l ution concentration 6 A 9 C 8 5 7 4 6 r -+I ~ t RD ) 1 1 ~ 0 0 5D 11D 15D 3ID 0 5D 11D Tne,rm Tine, rm 8 B D 7 6 5 I : RD RD 1 2 c 1 0 5D 11D 0 5D 11D Tne,rm line,rm Figure 3-6 Transport plots of GFP-Hevein and RFP through a 1A4 antibody-modified membrane when using 5 nlv1 (A) 20 nM (B) 50 nM (C) and 100 nM (D) feed solution concentration These transport plots were used to calculate the selectivity coefficient (Figure 37). Indeed the selectivity coefficient decreases as the feed so lu tion increases For 5 nM feed solution concentration a se l ectivity coefficient of 30.6 is obtained and for 100 nM feed solution concentration we obtained a value of 0. 7 of the se l ectivity coefficient which corresponds to passive diffusion of the proteins

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59 35 30 25 20 15 10 5 0 Feed Concentration, nM s Figure 37. Variation of the selectivity coefficient with feed solution concentration Effect of the Pore Diameter on the Flux and Selectivity Coefficient The diameter of the pores of the alumina membranes is another important parameter that influences the flux of the proteins and selectivity coefficient of a membrane. Figure 3-8 shows the transport plots obtained when membranes with pores of 50 nm (Figure 3-8A) 70 nm (Figure 3-8B) and 100 nm (Figure 3-8C) in diameter were used. The membranes with pores of 50 nm and 70 nm in diameter had thickness of 80 m and 90 m respectively and were modified with 1C2 Fab fragments. The membrane with pores of 100 nm in diameter had a thickness of 50 m and was modified with 1A4 Fab fragments In all cases a feed solution concentration of 10 nM in GFP-Hevein and RFP has been used The selectivity coefficient decreases as the pore diameter increases (Figure 3-9) The increase in selectivity coefficient is obtained at the cost of lowering the fluxes. For 100 nm pore diameter the selectivity coefficient has a value of0.7 which

PAGE 75

60 means that when using membranes with this pore diameter faci li tated transport is not predominant only passive diffusion is observed at hi gh pore diameters I 3 5 1 3 A 2 5 2 4 i RED Kl 1. 5 L : J ,.500 1000 1500 Ti me, rrin I 2 5 B "O 2 0 Q. II) C ~ -He\in l Cll !:; D _j 1 0 E 0 0 5 u c. 0 0 500 1000 1500 Time min 16 C 14 "O 12 0 10 C Cll ~G FP H e\i n !:; 8 II) -RED QI 0 6 E 0 u 4 a. 2 0 ---, 0 500 1000 1500 Time min Figure 3 8 Transport plots obtained when us ed membranes with pores of 50 nm (A) 70 run (B) and 100 run (C) in diameter.

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61 / ,. 19 ,. / / / 20 / 18 16 14 12 10 8 6 0.7 4 2 .,,, 0 50 nm 70 nm 100 nm Figure 3-9 Selectivity coefficient variation with the pore diameter. C onclu s ion s Highly selective nanotube membranes for protein separations have been prepared The separation is based on molecular recognition inside the nanopores of alumina membranes We have used antibody Fab fragments which as molecular recognition elements selectively bind and transport proteins. There are important parameters that should be taken into account in obtaining a desired protein separation with certain fluxes and selectivity coefficients. These parameters are: binding affinity between the antibody and the antigen feed so l ution concentration pore diameter of the membrane and membrane thickness. A higher binding affinity is desired because it leads to a higher selectivity ; although a very high binding affinity is not appropriate because the analyte should be released from the antibody and transported through the membrane Higher selecti v ity coefficients are obtained at lower feed solution concentration and when using membranes with small pore diameters Using membranes with small pore diameters

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62 however lo wer fluxes are obtained. High fluxes are important in separation processes higher fluxes can possibly be obtained by decreasing the membrane thickness by applying pressure ( 15 3) or by applying an electric field across the membrane (154).

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CHAPTER4 3-D POROUS ALUMINA-BASED MICROARRA YS Introduction Microarray technology is an emerging technology which is having a considerable impact in proteomic research Protein microarrays allow the identification and quantification of a large number of target proteins using a small amount of sample within one single experiment (155 ) This technology requires rapid, high throughput protein assays. Recent studies showed that protein microarrays can be used to screen for proteinprotein interaction (156 157), antibody specificity profiling (158,159), immune profiling (160), and protein-small molecule interactions (161) Significant challenges exist for protein microarrays which do not exist for gene arrays (155,162,163 164) The initial challenge is developing a system capable of detecting a broad range of concentrations; proteins can exist in a very broad dynamic range (up to 10 1 0 ) in any cell. The second challenge is detecting very low abundance proteins; for DNA PCR methods exists for amplification while for proteins no amplification method is available yet. DNA is a very uniform and stable molecule (it does not lose its activity when stored dry), with a well defined activity prediction based on primary nucleotide sequence These factors are different for proteins. Proteins exhibit very diverse individual tertiary molecular structures; further, their 3D structure is important for their activity, they should always be kept wet to avoid denaturation Protein binding interaction takes place by different means such as electrostatic forces 63

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64 hydrogen bonds hydrophobic or Van der Waals interactions. In a ddi t ion proteins may ha e multiple binding sites and can possibly interact with different molecules in t h e same tim e. Because of thes e challenges substrate requirements are mor e d emandi n g for protein microanay te c hnology Various types of substrate ha ve be e n exp l ored (165, 1 66) and the search for n ew supports with superior performances is still a chall enge. The r e ha ve been reports on th e spotting of protein micro arrays usin g a va ri e t y of surfaces and immobili za tion chemistries including but not limited to agarose ( 167) polyvinylidene difluoride (168) and polyacrylamide gel pads (169). Proteins anays on g lass surfaces coated with aldehyde (161), poly-L-lysine and gold surfaces deri va ti ze d w ith SAMs ( 170) have been reported also. Application of nanoporous silicon as support for prot ei n microana ys has b ee n recentl y r e ported (171). Three dim e nsional porous surfaces offe r several advantages over the flat surfaces including higher sensitivity due to th e hi ghe r san1ple loadin g capacity broader dynamic ran ge of concentrations and a 3-D e nvironm e nt that pr ese rv es prot e in activity and accessibility. Here we report two m e thods of fabrication of 3D porous alumina-based microarrays and show their applications in antibody specificity screening Besides t h e advantages offered by a 3-D support for microarrays alumina membranes present a very we ll d efi n e d morpholo gy, which is important for uniform immobili za tion of the proteins and pro v idin g r e producibl e d etec tion of th e li g and binding eve nts Experimental Materials High purity a luminum foils 1 00 mm x 500 mm x 0 .2 mm (purity 99.9998 % ) were o bt ained fro m Alfa Aesar, 3 aminopropyltrimethoxysilane (APTES) from U nit e d

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65 Chemical Technologies, and triethoxysilylbutyl aldehyde from Gelest. Triton X-100, tetraethylorthosilicate (TEOS), rhodamine B isothiocyanate human and mouse IgG anti human IgG labeled with Alexa 488 and anti-mouse IgG labeled with Alexa 594 were purchased from Sigma Aldrich. Surface coating polymer FSC-M was obtained from Shipley and polymer remover (remover 1165 Shipley) was purchased from MicroChem. All the materials were used as received. The TEM copper grids ( 400 mesh PELCO) that were used as masks were purchased from Ted Pella The porous alumina membranes that were used for the second method were bought from Whatrnan, and they had a nominal pore diameter of 200 nm. Silver plating solution (Ag 1025) was purchased from Technic (Cranston, RI). Silver wire (2 mm thick) were purchased from Alfa Aesar (Ward Hill MA). Fabrication of porous alumina microarrays Method 1 High purity aluminum foil was first glued to a glass by using an epoxy glue. Then the Al foil/glass plate was electropolished into a solution composed of 95 wt % H 3 PO 4 5 wt. % H 2 SO 4 and 20 g/L CrO 3 heated at 70 c. Al foil/glass was washed with distilled water and dried under vac uum at room temperature. Figure 4-1 shows a schematic representation of the first method of fabrication of the porous alumina microarra ys. There are four steps involv ed in this procedure and they are as follow : Step 1. The e l ectro polish ed Al foil/glass was first spin-coated with a surface coating polymer (FSC M) From the SEM measurements we found that t h e thickness of the polymer film was 3

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66 Step 2. The polymer / Al foil was then inserted into a reactive ion etching apparatu s (Samco Plasma Ion Etching System model RIE-1 C). The polymer surface was etched for 5 seconds in order to make the surface hydrophilic. This was accomplished using o ygen plasma ith radio frequency 13.56 MHz) of 140 W. The plasma pressure was 20 Pa oxygen and oxygen flow rate was 30 seem Copper grids ( 400 mesh) were placed on top of the polymer with a dilute Triton X so lutio n which is a wetting agent and ensures the copper grid was stick flat to the surface after drying. Step 3. The plate with copper grids was etched for 4.5 minutes and then the copper grids were blown away. In this way we obtained Al surfaces patterned with the coated polymer. 0 2 plasma etching l u grid removing Electrochemical anodization of Al Cu g rid P o l y m e r Al foil gla s s Figure 4-1. Schematic representation of the microarray fabrication by method 1.

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67 Step 4. The patterned Al/glass system was electrochemically oxidized to form porous alumina films, only in the areas where the Al was exposed. The anodization was carried out in 5% oxalic acid as electrolyte, at 0 C, under a constant voltage of 50 V. In a similar way patterning of anodic alumina into aluminum was reported ( 172 ) In this case, the aluminum was patterned with silica either by a sol-gel process or by dielectric evaporation. In the first case they reported the presence of cracks at the interface between aluminum and alumina, and in the second case they observed the growth of tilted pores underneath the silica layer. Method 2 Figure 4-2 shows a schematic representation of the steps involved in fabrication of the alumina microarrays by method 2. A thin Au-Pd layer (approximately 90 nm in thickness) was sputtered on one side of the alumina membrane. Au-Pd sputtering was performed using a Denton Vacuum Desk II Cold Sputter. The Au-Pd layer was used as a seed layer for electroplating. Commercial alumina membranes having 60 m in thickness and 200 nm pore diameter were used. A copper TEM grid was placed on top of Au-Pd sputtered alumina membrane. Another mask (aluminum foil) was placed on top of the copper grid just to have enough Au-Pd material for making the electrical contact. This assembly was then inserted into the center of the vacuum chamber of a reactiv e ion etching apparatus (Samco Plasma Ion Etching System, model RIE-1 C) and Ar plasma was used to etch the Au-Pd seed layer. The Ar plasma parameters were as follows : 10 mins 13 56 MH z 140 W, 10 Pa Ar Ar flow rate = 12 seem. Aft e r etchin g, an Au-Pd replica of copper grid was transferred to the membrane

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l lTTTl l I I I I I I I I I I I I I I I I I I ilver Cu g rid Au-Pd layer Alumina m e mbrane e l ec trod e position 68 I Polym er s pin coa tin g I Sil ve r J e l ec trod e po s ition Po l ymer removing Figure 4-2 Schematic representation of the microarray fabrication by met h od 2. Electroplating was accomplished using a EG&G PAR Mode l 273 galvanostat / potentiostat which was contro ll ed using a CorrWare software package (Scribner Associates Inc ., Southern Pines North Carolina). Electrochemica l ce ll s were prepared from a Teflon cell (17 mm inner diameter) and stainless sti ll plate, which were h e ld together using screws and o rings (see Figure 4-3). To e l ectrodeposit Ag into the membran e, the membrane was p l aced on Teflon tape Au-Pd sputtered layer side up Electrical contact was made to the membrane using copper adhesive tape. A silver wire was used as the counter electrode. Ag was then deposited at 2 mA cm 2 for 8 minutes resulting in a 1 m thick of Ag on the Au Pd l ayer. The cell was then disassembled The spin coated polymer layer (ca. 3.5 m thick) was added on the top of the electroplating

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69 la yer to prevent the leakage of plating solution through the membrane and suppress the lateral growth of the electrodeposits The spin-coated membrane was place into the electrochemical cell again. In this case the Ag electroplated layer was side down so that the open pores faced up Additional Ag was then plated into the membrane at -0.50 mA cm 2 for 90 minutes. After electroplating the membrane was immersed into spin coating polymer remover for 10 minutes rinsed with ethanol and dried at room temperature. G B C E Figure 4-3 Electrochemical cell setup for silver electrodeposition: A Ag wire counter and reference electrode ; B Ag plating solution; C, Cu foil D Au-Pd modified alumina membrane as working electrode ; E stainless steel plate; F teflon tape; G, O-ring seal. Membrane modification for sensitivity studies For sensitivity experiments five membranes with 0.5, 1.2 50 60 and 90 m thickness have been prepared They were prepared by electrochemically oxidation of aluminum using the two step anodization method (52). Briefly high purity (99.9998 %) aluminun1 foils were electropolished at 15 V in a solution with the following composition : 95 wt % H 3 PO 4 5 wt % H 2 SO 4 and 20 g/L CrO 3 at 70 c and for 10 minutes The electropolished aluminum foils were then anodized at 50 V using 5 %

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70 oxalic acid as the electrolyte. The anodization was conducted at o 0 c, for 15 hours. The first film of the membrane was dissolved away in an aqueous solution that was 0.2 Min CrO 3 and 0.4 M in H 3 PO 4 at 6070 c The second anodization step was carried out in exactly the same conditions (referring to the voltage applied and the electrolyte solution used) as the first step. The time of the anodization in the second step varied for the five membranes from 20 minutes to 16 hours, resulting in formation of highly ordered nanoporous alumina membranes having pore diameter of 75 run and thicknesses between 0.5 and 90 The aluminum that was not oxidized was dissolved into a saturated HgCh solution, except for the case of 0 5 and 1.2 m thick membranes due to their more susceptibility to fragment into the small pieces. A sol-gel template synthesis method was used to deposit silica nanotubes (with a wall thickness ~ 3 run) within the pores of the alumina films (173 174 ) First a sol-gel silica precursor was prepared by mixing absolute ethanol TEOS and 1 M HCI (50:50: 1). This solution was allowed to hydrolyze for 30 minutes. Alumina template membranes were than immersed into the sol-gel for 1 minute under sonication, after which they were air dried for 10 minutes at room temperature and cured in the oven for 12 hours at 150 C. The inside walls of the silica nano tubes were reacted then with APTES a silane with an amino terminal group. The silica nanotube membranes were immersed into an ethanol based solution which contained 6% APTES and 6 % pH 5.1 acetate buffer solution. The membranes were kept in solution for 10 minutes under vacuum followed by 20 minutes in ambient air at room temperature. They were dried under nitrogen and cured at 120 130 0 C und e r vacuum Amino groups react with the isothiocyanate (175) This approa c h was used to covalently bind rhodamine B to the silica nanotube membranes (see Figure 4

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71 4). The amino modified silica nanotube membranes were immersed in a solution of 1 % (wt) rhodamine B isothiocyanate in DMF for 16 hours in the vacuum, under nitrogen The rhodamine B modified membranes were washed in DMF, chloroform and ethanol. The washing was performed for 10 minutes under sonication in each solvent. APTES 3-aminopropyltrimethoxysilane OH OH ====~:::.> OH OH Silica Nanotube Membrane RHODAMINE B ISOTHIOCYANATE "-ex = 570 nm "-em = 595 nm Figure 4-4. Modification steps for sensitivity studies As a control experiment we modified a piece of glass with rhodamine B in the same conditions as the alumina membranes The glass was initially cleaned in a piranha solution (3:1 H 2 SO 4 :30% H 2 O 2 ) at 90C and washed copiously with deionized water. Fluorescence spectra of the alun1ina membranes and glass modified with rhodamine B were taken using a Zeiss fluorescence microscope. The Rhodamine B dye was excited using 570 nm light and the emission was monitored using a 590 nm band pass filter. The dye was excited while simultaneously monitoring the emission with a fluorescence detector for 30 ms

PAGE 87

72 Microarray modification for selectivity studies The alumina microarrays made by method 2 were used to investigate their selectivity in terms of screening for antibody specificity. Again a silica thin film was deposited on the pore walls of alumina membrane-based microarrays. These were immersed into a ethanolic solution that was 5 % in an aqueous acetate buffer with a pH of 5 1 and 5 % in triethoxysilylbutyl aldehyde. The aldehyde groups react readily with the primary amines on the proteins to form a Schiff s base linkage (176 177 ). This approach was used to covalently attach the capture proteins, which in this case were human and mouse IgG s. The proteins were spotted on the alumina microarrays using a 10 X microscope connected to a monitor and a manual microinjection system (Brinkman, Westbury NY) A volume of 10 L of protein solution (0 2 m g/ ml in PBS pH = 7.4) was back loaded into a fem to tip (Fisher Scientific Pittsburgh, PA) and a compensation pressure of 50 psi applied. The tip was positioned using a micromanipulator until the tip touches the alumina surface. Due to the porous nature of the alumina the dye is pulled into the islands through capillary action without the need for addition pressures Once the surfac e was saturated with protein solution the tip was reposition to another spot and filled in a similar manner. After 12 hours incubation at 4 C the arrays were immersed into a blocking PBS buffer solution that contained 1 % BSA and 0.1 % Twe e n-20 for 3 hours This step is n e cessar y not only for blocking the unreacted aldehyde groups but also for reducing th e non-specific adsorption of the proteins (161). After washin g thorou g hl y with PBS th e arrays w e re incubat e d in a solution containin g th e tar ge t proteins (a mixtur e of anti human I g G labeled with Alexa 488 dye and anti mous e I g G lab e l e d with

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73 Alexa 594 dye, both having a concentration of lmg/ml in PBS). After 12 hours of incubation, the arrays were washed three times with PBS and then twice with deionized water. Fluorescence microscope imaging was performed in order to evaluate the selectivity of the alumina-based microarrays. The Alexa 488 dye was excited with 495 nm light and the emission monitored using 515 nm band pass filter. The Alexa 594 dye was excited using 590 nm light and the emission monitored using a 590 nm band pass filter. After individual image acquisition, the fluorescence images for each dye were overlaid. Also an optical image of the surface was acquired using reflected light from the surface. Results and Discussions Microarrays fabricated by method 1 Figure 4-5 shows scanning electron micro graphs (SEM) of the porous alumina microarrays fabricated by method 1 at a lo w (A) and higher (B) magnification. As can be seen in the SEM image, the porous alumina films are very distinct areas on the polymer / Al surface. The pores of the alumina film are not highly ordered in this case due to the fact that the anodization process took place only in one step and for a v er y short period of time (20 minutes). Uniform ly cylindrically pores can be obtained by using a two step anodization method (52)

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74 Figure 4-5. Scanning electron micrographs of the porous alumina microarrays fabricated by method 1 at a low (A) and higher (B) magrufication. M i c ro a rr ays ma d e by m et hod 2 Figure 4-6 A shows the SEM image of the silver patterned porous membrane The silver metal was not electrodeposited throughout the whole length of the membrane ; it was deposited only a l ong on a distance that represents 5 % of the membrane thickness (see Figure 4-6 B) The possibility of using commercially available alumina membranes presents an advantage of this method. For quantitative studies however because of poor homogeneity of the pores diameter in these alumina membranes one will have to use membranes prepared in house with highly ordered pores. These membranes will have to be patterned by method 2.

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75 Figure 4-6. Scanning electron micro graphs of the porous alumina microarrays fabricated by method 2: A, Ag patterned on porous alumina and B Ag rods after dissolving the membrane Effect of the silica on the sensitivity measurements Although silanes can be attached directly on the alumina surfaces we found that the fluorescence signal is enhanced if a thin film of silica is deposited primarily on the pore walls of the membrane (Figure 4-7). The silica film introduces a higher densit y of hydro xy l groups on the surfaces, which provides a higher reactive surface area for further modification. The fluorescence spectra in Figure 47 show that for samples modified with silica, the fluorescence signal is approximately 7 times higher than for samples modified initially only with the silanes.

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60000 ;40000 ro ---
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77 450 400 350 300 250 a 200 150 100 50 .., .,, 0 glass 0 5 1 2 50 60 90 Membrane thickness, m Figure 4-8. Relative fluorescence coefficient for rhodamine B-modified membranes of different thicknes Selectivity As an application for the porous alumina-based microarrays we have screened the arrays for antibody specificity After capture proteins were immobilized (human and mouse IgG s) the arrays were probed with a mixture of the target proteins (anti human IgG-Alexa 488 and anti-mouse IgG-Alexa 594). The left side image of Figure 4-9 represents an optical image of a 350 m x 350 m section of the microarrays showing the spots where we immobilized the capture proteins and the right side image shows the fluorescence image acquired after the imobilization of the target proteins It can be seen from these images only the spots containing the capture proteins were highly fluorescent indicating that the proteins were immobilized and able to retain their functional properties on the porous surfaces. The spots where no capture proteins were immobilized are lightly visible indicating some nonspecific binding on the alumina surface

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I lgG Mouse lgG 78 ' d' Human l gG Mouse lgG Figure 4-9: Optica l (left) and fluorescence (right) image of a 350 m x 350 m area of the microarrays after immobilization of the target proteins Investigations of the fluorescence intensity profile (Figures 4-10 and 4-11) denoted cross-reactivity between the human and anti-mouse IgG, and mouse and anti-human IgG respectively. The uneven peaks in the intensity profile graphs are the resu l ts of both an inhomogeneous delivery of capture proteins using the manual injection system and the disordered structure of porous alumina. These drawbacks can easily be overcome by using a automatic i njection system and a very high l y ordered pore alumina support. That is high uniformity of the porous support is one general demand for quantitative protein immobilization; both geometry (pore size) and morpho l ogy (pore shape level of branching) affect the physical properties of the protein microarrays and thus their performances and characteristics (171) One important feature of our microarrays is that the arrays are very well defined on the platform. They are separated from each other by either Al (method 1) or Ag (method 2) This eliminates the tendency of the samples to spread out, which is a main issue in the microarray technology.

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f so C :, ; 4 0 ;;; C: ., 5 c 20 .. 0 2 0 u. -200 -150 100 -50 79 0 50 100 150 200 X AxlS (m) Figure 4-10. Excitation with 495 nm light: A 2D fluorescence image; B. 3D fluorescence image; C fluorescence intensity profile.

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80 ;,, 40 i: 8 20 !l 5 0 -200 -150 100 -50 0 50 100 150 200 X Al
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81 samples can be spotted on the same surface Furthermore the sample loading capacit y can be controlled by varying the thickness and the pore diameter of the alumina membranes. The uniformity of the spot intensity profile can be improved by us i ng alumina membranes with very highly ordered pore diameter distribution The ability to make protein arrays on a surface with very well defined features and morphology should increase the capabilities of researchers to stud y protein interactions on a whole proteome scale using the array technology

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CHAPTER 5 PROTEIN SENSING WITH SINGLE NANOPORE MEMBRANES Introduction There has been a big interest in constructing single molecule sensors bas e d on nanopor es The principle of the sensor operation is based on the nanomet e r op ening of th e pore which is comparable to the size of molecules to be det ecte d (178). When a molecule enters the pore th e pore is temporarily blocked which can be observ e d as a significant temporary reduction in the ion current passing through th e pore The d ev i ce operates ther e fore as a Coulter counter on a single molecul e level (178). This type of sensor has b ee n constructed on the basis of a protein cx.-hemolysin and its functioning was d e monstrated for DNA analysis (118,179 180). The nanopore sensor enabled d ete rmination of the len g th distribution as well as chemical composition of DNA strands in a solution, which built hopes for single-nanopore super fast DNA sequencing ( 181 182). A further major advance was made in the group of Hagan Ba y le y in e n g in ee rin g a bios e nsor that is capable of identifying individual DNA strands with single b ase resolution Eac h bios e n so r e lem e nt consists of an individual D NA oligonucleotide cova l e ntl y attached within th e lum e n of th e cx. -hemol ys in pore to form a DNA nanopore". The other single strand th e analyte is in the e l ectro l yte solution. This system co uld distin gu i s h between complementary a nd non complementary DNA strands making it specific for a given D NA sequence. This biolo gical pore-bilayer system is ho wever very fragile (178). A mor e r ea listi c approach to a pplyin g this id ea on an 82

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83 industrial scale would involve replacing the protein channel with a durable, robust, synthetic nanopore. Detecting single DNA molecules and characterizing their distribution was demonstrated with several types of solid state nanopores but none of them was equipped with recognition sites specific for a given biomolecule (183 187) Here we present a 3-dimensional nano-immunoassay based on a single pore system, capable of probing protein-protein interactions and detecting warfare agents. The principle of operation of this device is very simple and based on an intuitive and checked experimentally fact that transport properties of a nanopore depend very strongly on the pore walls surface characteristic (119, 188,189). If an analyte to be detected binds to the recognition sites placed on the pore walls and the pore has an opening of several nanometers the transport characteristic of a nanopore, expressed for examp l e in a form of current-voltage (I-V) characteristic will be significantly changed. Basing the detection signal on I-V curves rather than time series wi 11 significantly simplify the recording as well as data analysis process. I-V curve repres ents average transport properties and as such is much less demanding concerning the noise-free environment for recording than time series, which is the main detecting signal for Cou lt er counter based devices (178) As a base for the 3-dimensiona l nano-immunoassay we chose polymeric membranes covered e lectrol ess ly with go ld. Gold surface enables easy modification of chemistry of the pore walls by application of a thiol chemistry ( 44 1 90). The pores in polymer membranes were prepared by the track etching technique, which is based on irradiation of polymer films with heavy ions and subsequent development of the latent tracks by chemical etching (37). The technique gives ama z ing freedom in preparation of pores of various shapes and as sma ll diameters as several nanom eters. For preparation of

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84 our ]-dimensional nano-immunoassay we chose asymmetric conical shape of the por e (120-128). A conical pore has a much lower resistance than an equivalent cylindrical pore of the same limiting diameter. Additional advantage of using asymmetric pores is that we limit the interactions z one in the pore which makes the sensor s respons e fast e r and is expected to lower the detection limit. The pores were subsequently cov e red electrolessly with gold (40) which resulted in formation of gold tubes (123) The principles of the nanodevice operation were shown first with the system biotin streptavidin which is known to have a very high binding constant and the binding is regarded as practically irreversible (191). We also checked applicability of the de v ice for s e nsing protein-protein interactions on the example of protein G modified Au tubes Protein G is a cell surface-associated protein isolated from Goward Group G Streptococci and binds with high affinity immunoglobulins (IgG s) (192 193). In our experiments we have used cat IgG which has no affinity for protein G and horse IgG which has a stron g affinity to the protein G (194 195). It is also shown the potential of this nanopore s y s t em in building sensors for warfare agents on the example of ricin. Experimental Materials We used 1 2 m thick polyethylene terephthalate (Hostaphan RN 12 Ho ec hst) foils irradiated with single swift heavy ions (e. g. Au Xe U) (196) of 2. 2 G e V kin e tic en e r gy (UNILAC GSI Darmstadt). To obtain conical pores the sin g le ion irradiat e d pol y m e r foils were mounted between two chambers of a conducti v ity cell and etched from on e sid e in 9 M NaOH as d e scrib e d e ls e wh e r e (120 122 128). The ch e mical e tchin g was monitor e d by applyin g a volta ge of 1 V across the membran e It allow e d d e t ect in g o f th e br e akthrou g h moment when the pore was e tched throu g h. E tchin g for a lon ge r t im e

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85 resulted in increase of the pore diameter. The diameter of the large pore opening was estimated on the basis of the so called bulk etch rate, which for PET at 9 M aOH and room temperature is 2.13 nm/min (120). For example 2 hours etching results in 520 nm pore diameter. The diameter of the small opening was obtained on the basis of conductivity measurements assuming a conical shape of the pore (37). The pores we prepared had a diameter of ~ 40 nm Plating the nanopores with go ld resulted in final diameters varying between 5 and 20 nm function of the gold deposition time. The big diameter of the pores did not change significantly. Electroless plating of PET membranes The electroless plating was performed according to the procedure described elsewhere (40). The plating process was performed at 3.6 c and pH 9.9. Tipically after 2.5 hours of plating, the gold layer has an approximative thickness of 4 nm Proteins Lyso z yme streptavidin bovine serum albumin (BSA) protein G biotin labeled cat IgG and horse IgG were purchased from Sigma Aldrich EZ-Link Biotin-HPDP or (N-(6-(Biotinamido )hexy l )-3 -(2 'pyridyldithio )-propionamide was bought from Pierce. Ricin Toxoid and Biotinylated Anti-Ricin IgG were bought from Toxin Technology Inc ., Sarasota FL. Ricin Toxoid has been toxoided using glutaraldehyde crosslink:ing and has less than 1 % of the original toxicity. Experimental Setup The single conical-Au-nanotube membrane was mounted between two hal ves of a conductivity cell (128) and a Ag/AgCl electrode was insert ed into each half-cell solution Current vo lt age (l V) curves associated with ion transport through single nanotubes and transient time series were obtained usin g an Axopatch 200B (Axon Instruments) The

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86 working Ag/ AgCl e l ectrode was in the half-cell solution facing the large-diameter opening and the potential of this electrode was controlled re l ative to the counter Ag/ AgC I electrode in the opposite so l ution The potentia l was stepped in l 00 m V steps through the desired potential range and the resu l ting transmembrane ion current was measured Ion current time series were recorded at 10 kH z sampling frequency and filtered with a Bessel filter at 2 kH z R es ult s a nd Di sc u ss i ons In investigation the biotin/streptavidin system the Au tubes were modified with biotin by incubating them in ~ 0.2 mM EZ-Link Biotin-HPDP in ethanol (1 % DMSO) at room temperature for 24 hours. The tubes which we used for that series of experiments had the small opening typically of ~ 5 nm, while the big opening of conical pores was kept ~ 0 6 With that size of the pores, binding of streptavidin was expected to block the current totally. Streptavidin would "cap" the pore and prevent the ion flow. Figure 51 shows the resu l ts obtained for sensing l ysozyme with a sing l e conical go l d nanotube The 1-Y characteristic of a single Au tube before and after modification with biotin are showed in Figure 5-1 A As expected, the biotin modification did not change the 1-V curve very strongly the low mo l ecular weight biotin did not diminish the si z e of the pore in a significant way. Before subjecting the pore to a streptavidin so l ution we checked how the pore "reacts" and "sees other proteins which do not bind to biotin. Figure 5-1 B and 5-C shows ion current in time through a biotin modified Au tube in th e absence (B) and in the presence of 100 nM of lyso z yme (C) The protein was add e d to the chamber facing the small opening of the pore. The experiments were performed at pH 7 where lyso z yme is positively charged (pl ~ 11) ( 46). The net electric char ge allo w s the prot e in to follow the direction of external electric field resultin g in trans lo c ation

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87 through the pore. As the pore diameter is comparable with the protein size we observe transient blockages of the pore, which we attribute to single lysozyme molecules passing through the pore. pA B 0 400 pA C -50 -100 150 A nAs 3 -1CXX) ". -E.00 -1 ' ' ' -3 -5 I I I I I Buffer 1 M KCI, pH 7 2000 ms I I 1cm 1 M KCI + 107 M lysozyme pH 7 200 ms mV -200 mV -50 mV Figure 5-1. Sensing lysozyme with a single conical gold nanotube. (A) Current-voltage characteristic of the Au nano tube before (red points) and after modification with thiolated biotin (blue points). The diameters of the pore opening are 5 nm and 0 6 m respectively (B) Ion current versus time through the Au nanotube modified with biotin recorded at 1 M KCl, pH 7. (C) Ion current versus time as in (B) at presence of 100 nM lysozyme in contact with the small opening of the pore

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88 It is important to notice that our sensor also functions as the oulter ounter for molecules and can be used for stochastic sensing in case when the analyte does not interact with the pore walls Identical results were obtained for the another un-binding protein bovine serum albumin as the analyte After washing the chamber with a buffer solution we exposed the membrane to a strep ta vi din solution. The protein was again added only on one side of the membrane with the small openjng. Figure 5-2 shows ion current recorded before and directly after exposure of the membrane to 180 pM streptavidin. nA A mV 1 o a o 5 00 5 00 1000 2 B p A o 2 s 500 ---............. ... _,... ____ ,, .,.. __ ,.., __ ..._ .. ~ ...... ......_ C .~ 1 ~--------2-s ______ Figure 5-2. Sensing streptav idin with a single conical gold nanotube. (A) Current-vo lta ge characteristics of a single conical Au tube modified with SH-biotin at presence of 180 pM strep ta vi din added on the small side of the conical nanotube (B) Ion current in time through a sing l e Au nanotube modified with biotin recorded at l M KCl, pH 4.5 recorded at -1000 mV. (C) Ion current in time as in (B) at presence of 180 pM streptavidin.

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89 As can be seen in Figure 5 2 A and C the current shut off totally, and was not recovered after washing with buffer solution or lowering pH to strongly acidic conditions (it is known from affinity chromatography that acidic conditions weaken the protein protein bonding (197)) The membrane recovered only after exposure to UV light for 24 hours which resulted in breaking the thiol bonds and washing out biotin and strepta v idin. We prepared a series of pores with the small diameter ~ 5 nm and exposed them to solutions of different concentration of streptavidin The questions we asked are ( i) what is the detection limit and (ii) whether the response time of our sensor is streptavidin concentration dependent. In order to be detected the analyte streptavidin must randoml y walk through the solution until it encounters and binds to, a biotin at the mouth of the nanotube. As such the time required for blockage, 1 b, should be inversely related to the concentration of streptavidin (198) and Figure 5-3 shows that this is the case. While the 'tb values for the lowest concentrations are long 'tb can be shortened by convectively transporting the analyte to the nanotube mouth. For charged analytes electrophoresis provides a particular powerfu l way to apply convective transport (46,198) Indeed Lee et al. have shown that the time required to drive charged particles to the mouth o f a nanopore can be contro ll ed at will in this way (198). The error bars in Figure 5-3 are associated with three measurements made with three different nanotube sensors The error in 't b increases with decreasing analyte concentration which is not surprising given the random-walk nature of the respons e However since -c b can be decreased by eletrophoretically driving the analyte to the nanotub e (198) and since the error in 1 b is less for smaller 't b values it should be possibl e to obtain better reproducibilty at low conc e ntrations if convectiv e transport is used.

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'rb (min) 600 400 2 00 0 9 90 t t + ..--, 1 0 1 1 1 2 1 3 Log [SA (M )] Figure 5-3 Blockage time vs log of the mo l ar streptavidin concentration. The well-studied system of biotin-streptavidin enabled us to show the potential of our nanoporous system which subsequently was applied for bui l ding real nano imrnunoassays on the pore wa ll. Nano-immunoassay requires normally performing a series of modifications to expose the recognition site of interest. For example if we want to immobilize protein G and subsequently study its affin i ty to various IgGs we needed to dev e lop as assay for a non-destructive attaching the protein to the pore wal l. Figure 5-4 shows the modification steps we performed together with I-V curves recorded aft e r every modification. Transport properties of the nanopores served as a probe for successful modifications. In the first modification step we again covered the Au tubes with biotin via EZ-Link Biotin-HPDP Subsequently the membranes were immersed in 2mg/ml streptavidin in PBS pH = 7.4 solution for 24 hours at 4 C The l ast modification step was the attachment of protein G onto the membrane using biotin-streptavidin chemistry. We immersed the membranes into lmg/ml protein G-biotin label e d in PBS pH = 7.4 solution at 4 C for 24 hours Au tubes modified in this way enabled us to probe interactions of the protein G with cat IgG which is known to have no affinity towards

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91 protein G and of horse IgG with very strong binding affinities to protein G The first case resembled our biotin modified tubes through whic h lysozyme was translocating (Figure 5-1 ). The experiments were again performed at the pH which assured a non-zero surface charge of IgG (pl oflgG is ~ 7.0). A t-&vv'[J l Bdin-tlid ?,,o p ? -0 0. -{] 0M 10 7 5 -1CID -till 1 0 l D D A D A o -5 D D 1 5 -' B D 0 D D D 1 A D t t. X Q X t. tm 1cm Figure 5-4. Chemical modifications of a single Au tube leading to preparations of 3 dimensional nano immunoassay for detection of IgGs and probing their interactions with protein G. (A) Schematic representation of the subsequent modifications of a single Au tube. (B) Current-voltage characteristics recorded at l M KCI pH 7 performed after each modification step The gold tube after modifications has diameters of ~ 15 nm and 0.6 m respecti ely

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92 Figure 5-5 A shows an I-V characteristic of a single Au tube with protein G exposed to 1 00 nM cat lgG at pH 8 7. The cat IgG does not bi n d to protein G and the I-V curves remains the same If one looks howe er at the time series of ion current at constant transmembrane potential temporary blockages of ion current are observed They correspond to cat IgG molecules passing through the tube (Figure. 5-5 B and ) nA 5 A 3 X !l !ll 500 3 0 0 1 1 1 00 300 500 mV .3 5 ,oo L : ... 2 5 00 I $ Ji l ;t .. __........, ........... M~CW'Wts ... ftl l LliP t 2s 3000 ~ c -~ ~ ~--.~~2800 1 = .,...,, ~ T'' l 2s Figure 5-5 Sensing of cat IgG with a single conical Au nanotube modified with protein G as shown in Fig. 4. (A) Current-voltage characteristic of a sing l e Au tube recorded at 1 M KC pH 8.7 Ion current i n time recor d e d at 500 mV transmembrane potential before (B) and after (C) adding 100 nM cat lgG The gold tube after modifications has diameters of ~ 15 nm and 0.6 m respectively.

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93 On the other hand after exposure the nano tubes to horse IgG, even at 10 times lower concentration that cat lgG the pore was totally blocked (Figure 5-6). For 10 nM horse lgG concentration we waited 40 minutes to observe the blockage. A longer response time of this sensor compared to the streptavidin shown before results most probably from a higher molecular weight of the lgG and lower diffusion constant. nA 3 2 A X .< X X X X X X 1 0'.XJ {DJ X !ID 1 0'.XJ X X 1 rrW X X pA B -800 4s -1200 pA C 0 100 4s Figure 5-6. Sensing of horse lgG with a single conical Au nano tube modified with protein G as shown in Fig. 4. (A) Current-voltage characteristics of a single gold tube recorded at pH 4.4 1 M KCl before (x) and after ( ) adding 10 nM horse IgG The gold tube after modifications has diameters of ~ 5 nm and 0.6 respectively. Finally ricin 199) (molecular weight = 60 kDa) is a highly toxic protein and has been used as bioterror agent. However the protein that we used had < l % of the toxicity

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94 of the wi Id-type protein. Exposure of the anti-ricin-based sensor to ricin shuts down the ion current wher as exposure to non-binding bovine serum albwnin has no effect on the Icurv Figure 5-7 shows a set ofl-V curves of an Au tube with anti ricin on th walls b fore and after exposure to BSA and ricin. BSA and ricin have the same molecular w ight of ~ 60 kDa therefore BSA served as a control for the ricin detection. nA .500 -300 100 100 300 500 1 mV 2 Figure 5-7 1-V curves for the ricin sensor in the presence ofno protein (x) 100 nM and ~ 100 nM ricin ( ) Concl u sions We have demonstrated a new class of protein biosensors based on biofunctionalized conical Au nanotubes. The results reported here indicate that these biosensors can be both highly sensitive and highly selective. This sensor can be used for detection of any protein for which a nano-immunoassay can be developed. An important feature of the system is that it is no need for chemical pretreatment or labeling of the analyte to be detected. A nanotube with controlled surface chemistry can also be treated as a special probe for surface properties of nanopores, not accessible by any other techniques.

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CHAPTER6 CONCLUSIONS The main aim of the research presented in this dissertation has been the development of new nanostructures based on nanoporous membranes, and investigation of their applications as sensors and separation devices. A template synthesis method was used to produce nanotubes inside the pores of both aluminum oxide and polymeric membranes. After an introduction in the template synthesis method and the processes of fabrication of the porous membranes, the dissertation was centered on investigating new applications of these nanotube membranes. There were three applications of the nano tube a l umina membranes explored, and one application of the single nanotube polymeric membranes was also examined. Chapter l presents the development of alumina nanopore membranes that mimic the function of ligand-gated ion channels. In biological channels there are no electrodes and the ion current is driven by an electrochemical potential difference across the cell membrane. This function of the ligand-gated ion channel is mimicked by applying a porous battery cathode film to one face of the hydrophobic alumina membrane and a porous battery anode film to the other face. Hence, in analogy to the naturally occurring channel case this is a membrane with a built in electrochemical potential difference across the membrane In the absence of the ligand (again, a hydrophobic ionic surfactant) the membrane is in its "off' state and the electrochemical potential difference cannot be utili z ed to drive a transmembrane ion current. In contrast, when the ligand is detected the membrane switch e s to its on" state and the transmembrane battery discharges 95

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96 producing a corresponding transmembrane ion current. This concept could ultimat ely lead to a remote sensing technology where the batt ery discharge current is used to drive a device that signa l s that the ligand has been d e tected The application of silica nanotube membranes in selective separation of prot eins is pres e nted in chapter 2. A new separation m et hod for prot e in separation v ia membrane facilitated transport selectivity is develop e d based on introduction of the molecular recognition e l ements into the nanotube membran e s. Two antibodies with different affinities for a protein (hevein in this case) are immobili ze d on silica nanotube m e mbran es The aldehyde silane is used as a linker for antibodies attachment. Hevein is labeled with green fluorescence protein (GFP). The rates of transport of t he GFP-Hevein and red fluorescence protein (RFP) that was used as a control analyte are monitored The transport of both proteins is recorded simultaneously at two diff e rent emiss io n/excita ti on wavelengths. As a control experiment membranes with immobili ze d antibody that does not ha ve any affinity towards GFP-H eve in or RFP are used Both th e influ ence of pore diameter and the membrane thickness on the transport of GFP -Heve in and RFP are studied. These m e mbranes selectively transport th e protein (GF P-H evein) that specifically bind s to th e antibody r e l at iv e to th e other prot e in (RF P ) that ha s no affinity for the antibody. In Chapter 3 th e silica nanotub e m e mbran es are inv estigated as a support u sed in the prot ei n microarra y techno l ogy. Two m e thods of fabrication of 3-D al umin a-based microarrays are presented. These m e mbran es r ep r ese nt distinct microfeatures on a robust platform and they ha ve cylindrical pores with monodisperse nanoscopic diameters A

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97 potential application in antibody specificity screening is explored, along with the studies of the sensitivity of the system. Chapter 5 deals with a new class of artificial ion channels based on a synthetic membrane that contains a single conically shaped nanotube These nanotube-based ion channels show a voltage-gating, or ion-current rectification, function completely analogous to biological voltage-gated ion channels. The membrane with a single conically shaped gold nanotube was prepared by the template method. The nanotube has a large-diameter opening of ~ 600 nm and a small-diameter opening of 2-3 nm. In the biosensing application the nanotube-containing membrane is placed between the two chambers of a conductivity cell filled with an electrolyte. Electrodes present in each half cell solution are used to apply a transmembrane potential and measure the resulting ion current through the nano tube. The internal surfaces of the nano tube are modified with a specific biochemical molecular-recognition agent (the "capture" agent, e.g. an antibody) which interacts specifically with a given biomolecule (the analyte) present in one of the contacting solution phases. The binding interaction between the nanotube bound capture agent and the solution-phase analyte is transduced as a change in the ion current that flows through the nanotube. This new biosensing technology was demonstrated using biotin as the capture agent and streptavidin as the analyte and protein G as the capture agent and IgG as the analyte. The detection of a biological warfare agent (ricin) is also presented

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109 BIOGRAPHICAL SKETCH Lacramioara Trofin was born in Bucharest Romania. She attended a very prestigious mathematics-physics high school, B.P. Hasdeu, in Buzau Romania. Lacramioara developed an interest in chemistry since high school, when she was placed on the third place at the national Olympiads for Chemistry She graduated with a B.S degree in chemical engineering and a M.S. degree in organic chemistry from the Politechnica University Bucharest in 1993. After that she worked as a research engineer at the Research Institute for Elastomer Processing Bucharest Romania In January 2000, Lacramioara entered graduate schoo l in the Chemistry Department at the University of Florida under the guidance of Prof. Charles R. Martin. She completed her research in December when she received a Doctor of Philosophy degre e.

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I certify that I have read this study and that in my opinion it conforms to acceptable standards of scholarly presentation and is fully adequate, in scope and quality, as a dissertation for the degree of Doctor of Philosop~ i ( i2 /\ Char l es R. Martin hairman Professor of Chemistry I certify that I have read this study and that in my opinion it conforms to acceptable standards of scholarly presentation and is fully adequate, in scope and quality as a dissertation for the degree of Doctor of Philo p . Reynolds essor of Chemistry I certify that I have read this study and that in my opinion it conforms to acceptabl standards of scholarly presentation and is fully adequate, in scope and quality as a dissertation for the degree of Doctor of Philosophy. Vaneica Young Associate Professor of I certify that I have read thls study and that in my opinion it conforms to acceptable standards of scholarly presentation and is fully adequate, in scope and quality, as a dissertation for the degree of Doctor of Philosophy. 4t~~---Anna B~aJter-ioii; ._, Associate Professor of Chemistry I certify that I hav e read this study and that in my opinion it conforms to a ceptable standards of scholarly presentation and is fully adequate, in scope and quality, as a dissertation for the degree of Doctor of Philos~. L Associate Professor of Electrical and Computer Engineering

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This dissertation was submitted to the Graduate Faculty of the Department of Chemistry in the College of Liberal Arts and Sciences and to the Graduate School and was accepted as partial fulfillment of the requirements for the degree of Doctor of Philosophy. May 2005 Dean Graduate School

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