ner: nanoscale sensing and control of biological processes objective: to provide a microelectronic...
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NER: Nanoscale Sensing and Control of Biological ProcessesNER: Nanoscale Sensing and Control of Biological Processes
Objective:
To provide a microelectronic and microfluidic environment as a test bed for nanoelectronic / biological interfaces; to sense and control low-level charge signals arising from redox events at nanoelectrode complexes in solution
Approaches and Contributions:
Design and calibration of a micro-cyclic voltammetry flow-chip prototype
Target DNA hybridization detection at the micro-cyclic voltammetry flow-chip
Molecular assembly of a redox enzyme system by a metallized peptide at the three-microelectrode cell
Development and characterization of nanoelectrode array grown on a Si substrate
Flow-through nanopore membrance design for efficient in situ electrochemical synthesis and detection
Gold Nanotubes as Flow-Through Bioreactors for Microfluidic Networks
Napat Triroj and Rod Beresford Napat Triroj and Rod Beresford Brown University, Providence, RIBrown University, Providence, RI
Micro cyclic voltammetry measurement
Molecular assembly of Npx system
Analyte solution: 10 mM K3Fe(CN)6 in 1 M KNO3
0.6 0.3 0.0 -0.3 -0.6
-2
-1
0
1
2
100 mV/s 200 mV/s 500 mV/s 1 V/s
Curr
ent (n
A)
Potential vs. Ag/AgCl (V)
0.2 0.4 0.6 0.8 1.0
-2.0
-1.5
-1.0
-0.5
0.0
0.5
1.0
1.5
2.0
Pea
k c
urr
ent
(nA
)
(Scan rate)1/2 (V/s)1/2
cathodic
anodic
DNA hybridization detection
0.0 -0.1 -0.2 -0.3 -0.4 -0.5
-0.1
0.0
0.1
0.2
0.3
0.4
0.5
thiolated ssDNA hybridization with target DNA
Cu
rren
t (n
A)
Potential vs. Ag/AgCl (V)
0.8 0.6 0.4 0.2 0.0 -0.2-2.5
-2.0
-1.5
-1.0
-0.5
0.0
0.5
Npx-PepCo-AuNP in KAc
Npx-PepCo-AuNP in KAc + H2O2
NPx-PepCo-AuNP in KAc + NADH
Npx-AuNP in KAcC
urr
en
t (n
A)
Potential vs. Ag/AgCl (V)
Nanoelectrode array fabrication onto working electrode
Analyte I/O
Digital I/O
The functionality of the microfluidic three- electrode cell is confirmed:
- formal potential is close to the literature values
- peak current is proportional to (scan rate)1/2
An increase in the electrocatalytic charge upon hybridization of the target DNA present at low-concentration
Analyte: 27 µM Ru(NH3)63+ and 2 mM Fe(CN)6
3-
2 µM thiolated ssDNA, 500 nM target DNA
Current density: 3.9 mA/cm2 compared to 0.21 mA/cm2 at a bulk gold electrode
In collaboration with Prof. Joanne Yeh at University of Pittsburgh Medical Center
Collaboration with Prof. Shana O. Kelley, University of Toronto
A self-assembled system consists of NADH peroxidase (Npx) enzyme, a metallized peptide, and a gold nanoparticle onto a microfluidic three-electrode cell
Detection of the changes in redox signals in the presence of H2O2 and NADH
Electrode array process
Assemble PDMS gasket to electrode substrate
Cl2 plasma treatment to convert part of Ag to AgCl
Etch Si3N4 using CF4 plasma
PECVD of Si3N4
E-beam evaporation of Ti/Au and lift-off PR
After Cl2 plasma of Ag and lift-off
Working electrode surface area: 9 µm2
30 µm
Fabrication results
Micro cyclic voltammetry flow-chip prototype fabrication
Mask design
Completed flow-cell chip
Integration: Chip package Si signal processors nanoelectrode array self-assembled linker system biomolecular target
Collaboration with Prof. Jimmy Xu at Brown Univ.
An on-chip “biology-to-digital" sensing and control system
Nanowire array grown in FIB-patterned Al2O3; wire diameter less than 50 nm
Nanocrystal array grown from Co catalyst in FIB-patterned Al2O3
Silicon microelectronic signal processing and control
Flow network chip
Flip and bond
Biosensor electronic chip
Flow-channel network
Electrochemical sensing module
In situ monitoring, sensing, control, and actuation of biomolecular reactions
Collaboration with Hitomi Mukaibo and Charles R. Martin, University of Florida
Andres Jaramillo (undergraduate), Florida State University
Collaborators:
Jimmy Xu, Brown University ~ Charles R. Martin, University of Florida ~ Shana O. Kelley, University of Toronto ~ Joanne I. Yeh, University of Pittsburgh
1 μm
Au dot
Collaboration with P. Jaroenapibal,University of Pennsylvania
Ultra-sensitive integrated enzymatic detector arrays
• In a conically shaped nanotube, flow from base to tip is continually focused to the tube wall, resulting in high conversion efficiency
• Resistance to flow can be adjusted at will by controlling the base opening, tip diameter, and cone angle
Base opening
Tip opening
• Conical nanopore PET membrane fabricated by Martin group
• Membrane sections captured between orthogonal channels in the chip assembly process
• Electrical connection to continuous deposited Au film on the PET membrane
• Planar working electrode also in each channel as a control
• Coupled channels: analyze → synthesize → analyze
membranecontact pad
Electrode cell in glass:channel depth = 12 μmarea of WE = 2.5 x 10-5 cm2
Continuity of Au trace into channel
Modeling and Simulation of Nanoelectrochemistry
r00 0.2 0.4 0.6 0.8 1 1.2 1.4
-1
-0.8
-0.6
-0.4
-0.2
0
0.2
0.4
0.6
0.8
1
Time
Vol
tage
TVo
ltag
e
Electrocatalytic model design
YOZRf
b
k
k
ReO
Time
Voltage, RT/F
Cu
rre
nt
de
nsi
ty,
FD
C/r
T = 107
20-20 -15 -10 -5 0 5 10 15
0
2
4
6
8
10
12
ZO = +3+2+1
0−1
− 2− 3
Voltage, RT/F
-20 -15 -10 -5 0 5 10
Cu
rre
nt
de
nsi
ty,
FD
C/r
ZZ = −3
2015
0
2
4
6
8
10
12
14
ZZ = 0
Large and positive charge number of O enhances migration current at nanoelectrode
Large and negative charge number of Z suppresses the current plateau and enhances cathodic peak
Outlet
PET membrane
Glass channel
PDMS channel
Inlet