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Poisson equation based modeling of DC and AC electroosmosis

Poisson equation based modeling of DC and AC electroosmosis. Michal Přibyl & Dalimil Šnita. Institute of Chemical Technology, Prague, Czech Republic Department of Chemical Engineering Michal.Pribyl @vscht.cz. Content. Introduction electroosmosis principle

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Poisson equation based modeling of DC and AC electroosmosis

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  1. Poisson equation based modeling of DC and AC electroosmosis Michal Přibyl & Dalimil Šnita Institute of Chemical Technology, Prague, Czech Republic Department of Chemical Engineering Michal.Pribyl@vscht.cz

  2. Content • Introduction • electroosmosis principle • Governing equations of electrokinetic flow • full model • slip approximation • Mathematical models • model of a biosenzor driven by an external DC electric field • limitations of the slip modeling • model of electrokinetic flow driven by an AC electric field in a microchannel • properties of the AC electrokinetic flow • Conclusion

  3. Electric double layer (EDL) F = 0 V F = Fz EDL1 nm – 1 mm Microchannel wall Cation distribution ck, zk = 1 cK = cA = c0 Anion distribution ca, za = -1 Non-zero electric charge Local electroneutrality

  4. nonslip slip Electroosmosis induced by DC field Positive ions accumulates at the charged surfaces Axially imposed electric field acts on cloud of electric charge and starts fluid movement Santiago J.G., Stanford microfluidic lab

  5. Governing equations • Mass balances of ionic components(at least 2 equations) • Navier-Stokes and continuity equations(3 or 4 equations, vx, vy, (vz), p) • Poisson equation

  6. Slip model of flow • Simplified Navier-Stokes equation • Non-zero velocity on microcapillary walls (Helmholtz-Smoluchowski approximation) • Electroneutrality

  7. Non-slip model of flow • Navier-Stokes equation with electric volume force • Zero velocity • Local deviation from electroneutrality

  8. s1 = 0 s2 < 0 s3 s2 < 0 s1 = 0 r = R r = 0 R r z = 0 z = L z = 2L z = 3L z = 4L z = 5L z DF Model of a biosenzor driven by an external DC electric field Device consists of 5 compartments DC electric field is applied Electric charge attached to walls Ligand + Receptor = Complex solutionsolid ph. solid ph.

  9. Meshing • 2860 rectangular elements • non-equidistant • anisotropic • the ratio of the larger and the smaller edge of rectangles in interval 100 - 104

  10. Short-time elecrokinetic dosing ofa ligand in aqueous solution Formation of the ligand-receptor complex on microchannel wall Level of saturation of the receptor binding sites Ligand concentration field

  11. nonslip slip Example of limitation of the slip model – electrolyte concentration Water Bioapplication

  12. Example of the slip model limitations –ligand-wall (receptor) electrostatic interaction Effects of the surface electric charge s3 and ligand charge number zAb on formation of ligand-receptor complex on the microchannel wall NC is the total number of molecules of the ligand-receptor complex

  13. _ _ _ + _ _ + Principle of AC electroosmosis M. Mpholo, C.G. Smith, A.B.D. Brown, Sensors andActuators BChemical,92, pp. 262-268, 2003. Distribution of electric potential along the electrodes (red line) induces tangential movement of the electric charge and thus eddies formation.

  14. y = h y l3 l4 l2 l1 l5 x y = 0 x = 0 ~ Model of electrokinetic flow driven by an AC electric field in a microchannel Periodic array of electrodesdeposited a microchannel wall Geometry and dimensions of the microchannel(l1= l5 =h = 10 mm, l2 = 5 mm, l3 = 2 mm, l4 = 3 mm).

  15. Meshing • 2800 rectangular elements • non-equidistant • anisotropic • the ratio of the larger and the smaller edge of rectangles in interval 100 - 2×104

  16. Steady periodic regime A = 1 V, f = 1 kHz Electric potential distribution (blue DF = -1V, red DF = +1V) Velocity distribution

  17. Time course of global velocity Global velocity = the tangential velocity vx averaged over depth of the microchannely 0 , h Most of the stable periodic regimes (exceptf = 1×104 s-1) exhibits changes in flow direction during one period (1/f)  fluid motion in the microchannel has a zigzag character. However, a continuous flux of electrolyte can be experimentally observed because of high frequency of the zigzag motion (2f or 4f). fA = 1×101 s-1, fB = 1×102 s-1, fC = 1×103 s-1,fD = 1×104 s-1, fE = 1×105 s-1, fF = 1×106 s-1.

  18. Dependence of global velocity onAC frequency, A = 1 V The dependence of the global velocity averaged over one period (1/f ) on the applied frequency of AC electric field. This dependence is in a good qualitative agreement with the experimentally reported one. For the given set of parameters, there are several flow reversals observed in the studied frequency interval. The maximum global velocity is few tents of microns per secondd in the frequency interval 102,104 Hz.

  19. Conclusions • COMSOL Multiphysics software enables numerical analysis of electro-transport processes based on EDL in macroscopic objects • Slip approximation is not necessary • Limitations of the slip approximation ina DC system were identified • Electroosmosis induced by AC electric field was analyzed in a microfluidic channel • Dependence of global velocity on AC frequency was computed • Experimentally observed phenomenon (flow turnover at some frequencies) was proved by numerical analysis • This phenomenon probably does not rely on chemical and/or electrode reaction

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