Online proceedings - EDA Publishing Association
Online proceedings - EDA Publishing Association
Online proceedings - EDA Publishing Association
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11-13 <br />
May 2011, Aix-en-Provence, France<br />
<br />
**<br />
⎡ − εε ⎤<br />
mp<br />
f = ⎢ ⎥<br />
(2)<br />
CM<br />
**<br />
⎢⎣<br />
+ 2εε<br />
mp<br />
⎥⎦<br />
*<br />
*<br />
where ε and<br />
p<br />
ε are the complex permittivity of the<br />
m<br />
particle and the medium, respectively. The complex<br />
permittivity is related to the conductivity σ and angular<br />
frequency ω, which relates to ω = 2πf<br />
, through the<br />
formula:<br />
σ<br />
* εε j−≡<br />
ω<br />
(3)<br />
where j equals − 1 . Therefore, the DEP force is<br />
dependent mainly on difference between the dielectric<br />
properties of particles and the suspending medium solution.<br />
It can be either a positive DEP, which pulls the particle<br />
toward the location of the high-electric field gradient, or a<br />
negative DEP, that repels the particle away from the region<br />
of high-electric-field gradient.<br />
The schematic diagram of the cDEP microfluidic chip is<br />
depicted in Fig. 1. Four insulating structures which formed<br />
an X-pattern in the microchannel, as shown, were employed<br />
to squeeze the electric field in a conducting solution, thereby<br />
generating the regions high-electric-field gradient. The inlet<br />
flow field and the electric field were applied vertically. The<br />
negative-dielectrophoretic particles were repelled from the<br />
high- electric-field region, moving to the center of the<br />
microchannel where the flow velocity was higher. The<br />
insulator was designed 60 μm in width and 200 μm in length.<br />
The distance of the insulators along the direction of flow, as<br />
well as along the direction of the electric field, was 120 μm.<br />
The inclined angle of the insulator was 45 degrees. The<br />
particles were introduced into the microchannel and<br />
pre-confined hydrodynamically by the funnel-shaped<br />
insulating structures close to the inlet. The particles with a<br />
negative dielectrophoretic response were repelled toward the<br />
center of the constricting region. The electric field in the<br />
main microchannel was generated by using electrodes<br />
inserted into two conductive micro-reservoirs, which were<br />
separated from the main microchannel by thin insulating<br />
barriers made of 20 μm-width of PDMS [7].<br />
III.<br />
EXPERIMENTAL SECTION<br />
A. Chip Fabrication<br />
A biocompatible material of polydimethylsiloxane<br />
(PDMS) was adopted for cDEP microfluidic chip. The mold<br />
master was fabricated by using the inductively coupled<br />
plasma (ICP) dry etching technique on the silicon wafer<br />
(around 100 μm in height) to define the micropatterns, as<br />
showed in Fig. 2a. The PDMS prepolymer mixture was<br />
poured and cured on the mold master to replicate the<br />
structures (Fig. 2b). After the PDMS replica had been peeled<br />
off, the replica was bonded with the glass substrate after<br />
treatment of the oxygen plasma in the O 2 plasma cleaner<br />
(Model PDC-32G, Harrick Plasma Corp. Ithaca, NY, USA).<br />
The image of the fabricated microchip for particle focusing<br />
taken by the optical microscope was revealed in Fig. 2c.<br />
B. Apparatus and Materials<br />
A function/arbitrary waveform generator (Agilent<br />
33220A, Agilent Technology, Palo Alto, CA, USA) was<br />
employed as the AC signal source and connected to an RF<br />
amplifier (HSA-4011, NF corporation, Japan) to apply<br />
electric fields required for dielectrophoretic manipulation in<br />
the microchannel. Polystyrene particles, 10 mm in diameter,<br />
(G1000, Thermo Scientific Inc., USA) were used to<br />
investigate the efficiency of focusing. A sample of<br />
polystyrene particles with a concentration of 10 6<br />
particles/mL was injected using a syringe pump (Model KDS<br />
101, KD Scientific Inc., Holliston, MA, USA). The<br />
dielectric permittivity and conductivity of polystyrene<br />
particles at the frequency of 1 MHz are about ε r =2.6; σ=10 -16<br />
S/m, respectively [9]. The particles are suspended in a<br />
sucrose solution with an 8.62 wt% and 2.74×10 -2 wt% of<br />
K 2 HPO 4 (ε r =78; σ=4.50×10 -2 S/m). The dielectrophoretic<br />
focusing of particles was observed and recorded by an<br />
inverted fluorescence microscope (model CKX41, Olympus,<br />
Tokyo, Japan) mounting a CCD camera (DP71, Olympus,<br />
Tokyo, Japan) and a computer with Olympus DP controller<br />
image software.<br />
IV. RESULTS AND DISCUSSION<br />
To investigate the capacitive behavior of the PDMS barrier,<br />
the Wayne Kerr precision impedance analyzer 6420 was<br />
used to measure the impedance of the PDMS in DMEM<br />
medium (Gibco, Grand Island, NY, USA), which was<br />
commonly used in cell culture. The micro-reservoirs were<br />
filled with DMEM medium with an electric conductivity of<br />
0.8 S/m; besides, this medium in light red color could be used<br />
for confirm that there was no leakage from insulating barriers.<br />
The experimental set up was depicted in Fig. 3. The<br />
measured impedance of the PDMS barrier under different<br />
frequencies and the fitting curve to experimental data using<br />
the least-squares method were depicted in Fig. 4. The results<br />
revealed the capacitive behavior of the PDMS barrier. The<br />
impedance decreased with the frequency. The relative<br />
dielectric permittivity and conductivity of PDMS at a<br />
frequency of 1 MHz were 10.46 and 7.6×10 -4 S/m,<br />
respectively. The numerical simulations of the electric and<br />
flow fields, as well as the particle trajectory, were performed<br />
using the commercial software CFDRC-ACE + (ESI Group,<br />
France). Fig. 5 showed the transient simulation of the tracks<br />
of latex particles (ε r =2.6; σ=10 -16 S/m) [9] under varying<br />
electric field strengths and inlet velocity. The increase in the<br />
applied electric field significantly enhances the performance<br />
of focusing. Furthermore, decreasing inlet velocity increases<br />
the efficiency of focusing because the higher velocity results<br />
in more lateral expansion. Experimental results of focusing<br />
of fluorescent latex particles at different inlet flow rates and<br />
under varying electric field strengths of a frequency of 1<br />
MHz were demonstrated the performance of focusing, as<br />
showed in Fig. 6. The latex particles of 10 μm in diameter<br />
suspended in the sucrose medium with 8.62 wt% and<br />
2.74×10 -2 wt% of K 2 HPO 4 (ε r =78; σ=4.50×10 -2 S/m) were<br />
used to investigate the efficiency of focusing. The sample of<br />
latex particles was injected using a syringe pump. The<br />
experimental results showed that the performance of<br />
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