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Basic Theory of MICRO- & NANOELECTROKINETICS Dielectrophoresis and Electrorotation
Methods for Determining the Forces and Torques CIRCUIT © 1998 CORBIS CORP, DROPPER: © DIGITAL STOCK, 1997 Exerted by Nonuniform Electric Fields on Biological Particles Suspended in Aqueous Media THOMAS B. JONES
he forces exerted by nonuniform ac electric fields can be free, electrostatic field Eo(r) imposed by electrodes not shown harnessed to move and manipulate polarizable micropar- in the figure. To define the effective moment, it is convenient ticles—such as cells, marker particles, etc.—suspended to start with the electrostatic potential due to this electric Tin liquid media. Using rotating electric fields, controlled dipole [1]: rotation can be induced in these same particles. The ability to p(1) · r manipulate suspended particles remotely without direct con- (1) = (1) 3 tact has significant potential for applications in µTAS (micro 4 πε1r total-analysis systems) technology. The nonuniform fields for ¯ these particle manipulation and control operations are created where r is the radial vector distance measured from the center =| | by microelectrodes patterned on substrates using fabrication of the dipole and r r . Note the radial dependence of this (1) ∝ −2 techniques borrowed from MEMS (microelectromechanical potential, viz., r . If the dipole is small compared to systems) technology. A wide variety of structures, ranging the length scale of the nonuniformity of the imposed field Eo, from simple planar geometries to complex three-dimensional then the force and torque may be approximated as follows [2]: (3-D) designs, are now under investigation. The implications of these various schemes in certain fields of biotechnology are (1) ≈ (1) ·∇ ( ) far-reaching. For example, cells, cellular components, and F p Eo 2a (1) (1) synthetic marker particles treated with biochemical tags can be T ≈ p × Eo.(2b) collected, separated, concentrated, and transported using microelectrode structures having dimensions of the order of 1 to 100 µm (10−6 to 10−4 m). Furthermore, these forces can The dipole contribution to the total electric field cannot exert a manipulate DNA particles, which are several orders of magni- force on itself and therefore is not included in E o. tude smaller than cells. Now imagine replacing the dipole by a small dielectric This article presents a concise, unifying treatment of the sphere of radius R and permittivity ε2 at the same position in electromechanics of small particles under the influence of the structure, as shown in Figure 1(b). The particle has the electroquasistatic fields and offers a set of models useful in effect of perturbing the electric field. Expressed as an electro- calculating electrical forces and torques on biological particles static potential, this perturbation has the form: ∼ ∼ µ in the size range from 1 to 100 m. The theory is used to 3 ( ) (ε − ε ) R E · r consider DEP trapping, electrorotation, traveling-wave 1 ≈ 2 1 o (3) induced (ε + ε ) 3 induced motion, and orientational effects. The intent is to pro- 2 2 1 r vide a basic framework for understanding the forces and where it has been assumed that the particle radius is small torques exploited in the research represented by the other arti- compared to the length scale of the imposed field nonunifor- cles presented in this special issue of IEEE Engineering in mity. Equation (3) has the same form as (1) and the effective Medicine and Biology Magazine. moment is defined by comparing these two expressions. Effective Moment Method (1) ≡ πε (1) 3 ( ) The effective multipoles, including the dipole, the quadrupole, peff 4 1K R Eo 4 and other higher-order terms, facilitate a unified approach to (1) electric-field-mediated force and torque calculations on parti- where K ≡ (ε2 − ε1)/(ε 2 + 2ε1) is the Clausius- cles. We first introduce the effective dipole, leaving considera- Mossotti factor. Equation (4) defines the moment of the equiv- tion of the higher-order multipoles for later. Figure 1(a) alent, free-charge, electric dipole that would create a ( ) depicts a small electric dipole of vector moment p 1 = qd perturbation field identical to and indistinguishable from that located in a homogeneous, isotropic dielectric fluid of permit- of the dielectric sphere for all |r| > R. The only distinction tivity ε1. The dipole experiences a nonuniform, divergence- between this induced dipole and a general electric dipole is
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that, because the particle is a sphere and because it is lossless, best example of these is a coplanar, quadrupolar electrode the moment will always be parallel to Eo. We later take advan- structure. A particle with ε2 <ε1 can be levitated passively tage of the fact that no such restriction need be imposed for along the centerline, where the field intensity is zero. For a force or torque calculations, thus facilitating consideration of particle located on the centerline, the net dipole moment is particle inhomogeneity, anisotropy, and electrical loss. exactly zero irrespective of particle size. Thus, the particle is To evaluate the force on the dielectric particle, the effective actually levitated by the quadrupolar force. If the particle size moment of (4) is substituted directly into (2a). The validity of is increased, octupolar and other, higher-order moments can this procedure may be argued from the standpoint of energy. come into play [5]. Except for the planar quadrupolar elec- An even simpler approach is to note that, if the Maxwell stress trode geometry, such a situation is unusual. In far more cases tensor is used to calculate the force, then the cases of the phys- with micron-sized particles, quadrupolar corrections are negli- ical dipole and the dielectric sphere must yield the same result gible. Nevertheless, it is likely that, as µTAS structure sizes because, by definition, the fields are indistinguishable on any approach the 1-µm limit, higher-order multipolar contribu- surface enclosing the particle. Combining (2a) and (4) gives tions to the DEP force will become more influential for bio- the well-known expression for the DEP force on a dielectric logical particles. sphere in a dielectric medium [3], [4]: Appendix A summarizes a dyadic tensor formulation for the general multipoles. In just the same way that the effective ( ) dipole moment is identified by comparing the induced electro- 1 ≡ π 3ε (1)∇ 2.() F 2 R 1K E o 5 static potential due to a particle in an approximately uniform electric field to the electrostatic potential of a physical dipole, According to (5), a particle will be either attracted to or one may establish the induced multipoles [6]. For the dielec- repelled from a region of strong electric field intensity, tric sphere shown in Figure 1(b), the general, induced tensor (1) (1) depending on whether K > 0 (ε2 >ε1) or K < 0 moment of order n is (ε2 <ε1), respectively. Note that combining (2b) and (4) ˙ 2n+1 gives zero for the torque, because the dipole moment and elec- ˙( ) 4πε1R n ( ) − p n = K n (∇)n 1E .(6) tric field are always parallel. To escape this restriction, the (2n − 1)!! o particle must be electrically lossy, nonspherical, or possess a permanent dipole moment. The lossy and nonspherical cases In (6), (2n − 1)!! ≡ (2n − 1) · (2n − 3) · ...· 5 · 3 · 1, are considered below in the “Particle Models” and “Illustrative (∇)n−1E represents n − 1 del operations performed on the (n) Cases in Biological DEP” sections, respectively. vector field, and K ≡ (ε2 − ε1)/[nε2 + (n + 1)ε1] is the generalized Clausius–Mossotti factor. The quadrupole and all Multipolar Force Contributions higher-order moments (n ≥ 2) are tensors induced by spatial The accuracy of (5) for the DEP force depends on how parti- derivatives of Eo. Note that, in a uniform field, only the dipole cle size compares to the length scale of the nonuniformity of moment (n = 1) survives. Combining (6) with (A1) gives a the imposed electric field Eo. The dipole-only approximation vector expression for the nth multipolar contribution to the is quite robust, and in only a few electrode geometries are force on a dielectric sphere. multipolar correction terms needed for accurate modeling. The 2n+1 (n) 4πε R F = 1 K(n)(∇)n−1E [·]n (∇)n E.(7) (n − 1)!(2n − 1)!!
In (7), the dyadic operation [•]n means n dot multiplications [7]. An indicial notation provides a form often more useful for analysis. The first three terms of the xi-directed compo- nent of the total force vector on a dielectric sphere are writ- ten below [6]. ∂E K(2)R2 ∂E ∂2E _ ε (F ) = 4πε R3 K(1)E i + n i d 2 total i 1 m ∂x 3 ∂x ∂x ∂x m m n m (3) 4 ∂2 ∂3 + K R En Ei +··· . ε 1 30 ∂xl∂xm ∂xn∂xm∂xl (8)
Equation (8) uses the Einstein summation convention, (a) (b) according to which all repeated indices are summed. The first term in this expression is the same as (5), the dipolar Fig. 1. Definition of the effective dipole moment: (a) small DEP force. The second term, the quadrupole (n = 2), can be physical dipole in nonuniform electric field; (b) dielectric par- interpreted as the attraction of the particle to the region ticle in the same nonuniform electric field. Assuming that the where the gradient of the electric field is highest. To make physical scale of the nonuniformity of the imposed field is use of these expressions, it is best to consider specific classes much larger than the particle radius R, (4) may be used to of electrode geometries, which is a task taken up in the evaluate the effective moment for the dielectric sphere. “Illustrative Cases in Biological DEP” section.
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Particle Models In biological DEP, electrical losses manifest themselves in Advantages of the effective moment method to determine terms of dramatic frequency dependence of force and torque; force and torque start to accrue when we seek realistic models thus, we assume sinusoidal time variation for the nonuniform for cells and other biological particles, such as concentric electric field imposed by the electrodes: shells and conductive or dielectric loss mechanisms. ( , ) = ( ) ( ω ) ( ) Eo r t Re Eo r exp j t 10 Spherical Shells Biological particles are complex, heterogeneous structures ( ) where Eo r √is a spatially dependent, rms electric field vector with multiple layers, each possessing distinct electrical prop- phasor, j = −1,ω is radian frequency, and t is time. erties. Reliable dielectric models for such particles are crucial Equation (10) accommodates any type of spatially varying, ac in biological dielectrophoresis. Consider the concentric, electric field, including linearly polarized, rotating (circularly dielectric shell subjected to an electric field Eo in Figure 2(a). or elliptically polarized), and traveling-wave fields. Assume As before, assume that the nonuniformity of this field is mod- that both the suspension medium and the particle are homoge- est on the scale of the particle’s dimensions. It may be shown neous dielectrics with ohmic electrical conductivities σ1 and that the induced electrostatic potential outside the particle, that σ , respectively. The method previously used to identify the | | > , 2 is, r R1 is indistinguishable from that of the equivalent, effective dipole can be employed again, this time using phasor ε homogeneous sphere of radius R1 with permittivity 2 shown quantities and the following substitutions: in Figure 2(b) [4], if ε1 → ε = ε1 + σ1/jω and 1 3 ε − ε ε → ε = ε + σ /jω. (11) ε = ε R1 + 3 2 2 2 2 2 2 2 2 R2 ε3 + 2ε2 The effective dipole moment, a vector phasor, becomes 3 R ε − ε ( ) ( ) 1 − 3 2 .() p 1 ≡ 4πε K 1 R3E .(12) 9 eff 1 o R2 ε3 + 2ε2 ε ε The multiplicative factor in (12) is 1, not 1. In the limit of a thin shell, i.e., (R1 − R2)/R1 1, (9) reduces The complex, frequency-dependent Clausius–Mossotti fac- to Maxwell’s mixture formula [8]. The identification proce- tor fits the Debye relaxation form: dure for the effective permittivity ε is the same one used to (1) (1) 2 (ε − ε ) K − K∞ identify the effective dipole moment, viz., an examination of K(1) ≡ 2 1 = K(1) + o (13) (ε + 2ε ) ∞ ωτ (1) + the external induced electrostatic potential function. The 2 1 j MW 1 effective, induced moment of the dielectric shell where ε → ε in Figure 2(a) is obtained by substituting 2 2 into the (1) Clausius–Mossotti factor, in other words, K → (ε − ε1)/ (1) 2 K∞ ≡ (ε2 − ε1)/(ε2 + 2ε1) and (ε + 2ε ). 2 1 (1) ≡ (σ − σ )/(σ + σ )() For a general multilayered shell, the procedure is to start Ko 2 1 2 2 1 14a τ (1) ≡ (ε + ε )/(σ + σ )() with the innermost sphere and the layer enclosing it, and to MW 2 2 1 2 2 1 14b define an effective permittivity using (9). The procedure is then repeated on the new, now homogeneous particle and the layer enclosing it. The same step is repeated until the outer- τ (1) most shell has been incorporated into the effective permittivi- MW is the dipolar Maxwell-Wagner relaxation time for ty. The particle is thus replaced by an equivalent, an ohmic, dielectric sphere suspended in a similar medium. (1) homogeneous sphere with a radius equal to that of the outer- Figures 3(a) and (b) contain typical plots of Re[K ] and most shell. Strictly speaking, it is not correct to use the above effective permittivity for the higher-order moments. In the case of an electric field with significant nonuniformity, (9) can not be substituted into K(2), K(3), etc., because the effective R permittivity differs for each multipolar moment. 2 R1 R1 Conductive Particles ε ε Accurate models for viable, biological cells suspended in 3 ´3 ε media must account for ionic charge conduction mechanisms 2 ε ε within and without the cell and, for frequencies above ∼1 1 1 MHz, dielectric losses. The simplest way to represent ionic charge transport is to employ an ohmic model. Largely (a) (b) because of their structure and because of the high internal, electrical conductivity, this approximation usually suffices Fig. 2. Multilayered shells: (a) spherical particle with one con- within the cell. On the other hand, an ohmic model is less suc- centric shell; (b) equivalent homogeneous particle. As long cessful in representing the aqueous, electrolytic media in as the physical scale of the nonuniformity of the imposed
which cells are commonly suspended. The problem is that field is much larger than the particle radius R1, the external double-layer phenomena introduce the complication of mobile field of the equivalent particle is indistinguishable from that of space charge outside but directly adjacent to the cell wall [9]. the heterogeneous particle.
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The effective multipoles, including the dipole, the quadrupole, and other higher-order terms, facilitate a unified approach to electric-field-mediated force and torque calculations on particles.
Im[K(1)] versus frequency. The rapid shift in the real part of Combining (12) with (2b), the time average torque is K(1) and the associated peak of the imaginary part at the relax- ( ) ation frequency, ω = 1/τ 1 , are of great importance in fre- (1) = (1) × ∗ c MW T Re p Eo quency-based dielectrometry of biological cells. eff = πε 3 (1) × ∗ .() The time-averaged, dipolar DEP force may now be written 4 1R Re K Eo Eo 18 using (12) in (2a): ∗ Equation (18) reveals that an electrical torque can be exerted F(1) = Re p(1) ·∇E .(15) eff o on a sphere only if i) loss is present (i.e., the Clausius- Mossotti factor is complex) and ii) the electric field has a Alternately, using indicial notation, the xi-directed vector com- spatially rotating component (i.e., the field is circularly or ponent of the time-average force is elliptically polarized). To incorporate dielectric loss—which is to be regarded as ∂ E∗ F = 4πε R3 Re K(1)E i .(16) distinct from ohmic loss—we replace the real permittivities total i 1 m ∂ xm ε = ε (ω) − ε (ω) + σ / ω with complex equivalents: 1 1 j 1 1 j and ε = ε (ω) − ε (ω) + σ / ω ε /ε 2 2 j 2 2 j . Note that tan( ) is the In (15) and (16), the effective dipole moment and all electric well-known dielectric loss tangent. When dielectric loss is field quantities take their rms magnitudes. incorporated in the force and torque expressions, ε replaces We can now reveal something of the nature of this time- 1 the multiplicative factor ε1 appearing in (16), (17), and (18) average, DEP force for a completely general alternating elec- [10], [11]. tric field by assuming E = ER + jEI.This form highlights the possibility that the electric field is circularly or elliptically More About Multilayered Particles polarized. Substituting into (15), one gets The introduction of loss mechanisms greatly enhances cell and bioparticle modeling capabilities. For example, (9) for the (1) = πε 3 (1) ∇ 2 effective permittivity of a layered particle can be modified to F 2 1R Re K Eo account for conductive loss using the substitution of (11). + (1) ∇× × ( ) 2Im K EI ER 17 3 R1 ε − ε ∗ ε = ε + 2 3 2 2 ≡ · 2 2 ε + ε where Eo Eo Eo . The first term in (17) looks just like (5) R2 3 2 2 and signifies that a particle will be attracted to or repelled from R 3 ε − ε regions of stronger electric field, depending on whether 1 − 3 2 .(19) (1) > (1) < ε + ε Re [K ] 0 or Re [ K ] 0, respectively. The second term R2 3 2 2 in (17) is a nonconservative force that exists only if the nonuniform field is rotating [6]. It is not useful to attempt to extract effective con- ductivity and permittivity expressions from (19). Rather, the best way to understand this expression 1.0 is to recognize that it adds a new Maxwell- DEP DEP Wagner interfacial charge relaxation mechanism ROT to K(ω) of the same form as (13) [12]. In general, 0.0 there will be one new relaxation frequency added ROT for each layer. Refer to Appendix E of Jones [4]. Particles with Thin Shells –1.0 0.01 0.11.0 10 100 0.01 0.11.0 10 100 Particles with thin, conductive, or insulative ω ω ω ω / MW / MW shells serve as useful models for some of the (a) (b) most important dielectric behavior of biological cells. Let R1 = R2 + δ, where δ R ≡ R1 . If Fig. 3. Examples of the DEP and ROT spectra, Re[K(ω)] and Im[K(ω)], respec- charge transport across the thin layer dominates, = ε /δ tively, for two limiting cases: (a) Ko = 1.0 and K∞ =−0.5. (b) Ko =−0.5 and one may define surface capacitance, cm 2 , K∞ = 1.0. A positive or negative peak of the ROT spectrum always accom- and transconductance, gm = σ2/δ. Taking proper panies a change in Re[K(ω)]. limits of (19) for δ/R 1, one obtains
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c Rε Illustrative Cases in Biological DEP ε = m 3 , where c ≡ c + g /jω. (20) 2 + ε m m m cmR 3 DEP trapping and levitation, electrorotation, and traveling- wave particle transport exemplify important applications of On the other hand, if the principal mechanism of ion trans- dielectrophoresis in biotechnology. In this section, we apply port involves motion tangential to the particle surface, the theory of multipolar dielectrophoresis, introducing reason- then we have able models for the electric field to reduce (15) and (18), and their multipolar generalizations, (24a) and (24b), to useable ε = ε + ε , 2 3 2 R where forms in each of these cases. The approach facilitates compar- ison of the ordinarily dominant dipole terms to the higher- ε ≡ ε + σ /jω, ε = δε2, and order multipolar corrections. σ = δσ2.(21) DEP Trapping and Levitation Figure 4 provides an interpretation for (20) and (21) in terms The most prevalent applications envisioned for biological of a circuit model for a biological cell, such as a plant proto- dielectrophoresis involve selective trapping or levitation of plast. A plant protoplast consists of a cell membrane enclosing individual cells or particles. Related schemes take the form of cytoplasmic fluid. The cytoplasm contains intracellular parti- continuous flow or batch separation systems. Trapping and cles, which are ignored here, but can be incorporated readily separation often rely on the frequency-dependent, dielectric into a somewhat more complex model. responses of particles. Highly effective schemes may be real- Equation (20) has the form of series-connected conduc- ized if one subpopulation of cells to be separated expresses a tances, and in Figure 4, this complex conductance is depicted positive DEP effect, that is, Re[ K(1)] > 0, while the other as a combination of transmembrane polarization and conduc- exhibits a negative effect, i.e., Re[K(1)] < 0. In practice, the tion. cm is the familiar membrane capacitance, which ordinari- use of frequency as a control parameter offers an excellent ly dominates over the transconductance gm. Equation (21) has means to achieve selective, single-pass separations. the form of parallel conductance, consisting of surface (tan- It may be shown that the net DEP force on a particle can be ε gential) permittivity , which accounts for electric-field- expressed as the sum of the gradients of a set of electro- induced, out-of-phase motion of bound ions tangential to the mechanical potentials Un, where n = 1, 2, 3, . . . correspond to cell wall or membrane, and the more familiar surface conduc- the dipole, quadrupole, octupole, etc.; that is, tivity, σ , which accounts for in-phase, ionic motions. If sur- face polarization can be ignored, i.e., ε σ /ω, then F =−∇[U + U + U +···] (25) further simplification results. DEP 1 2 3
ε ≡ ε + σ / ω() and the potentials are related to the electrostatic potential as 2 3 eff j 22 follows [13]:
where σeff ≡ σ3 + 2σ /R is the effective ohmic conductivity of an equivalent, homogeneous particle.
The Multipolar Terms It is a straightforward matter to incorporate ohmic and dielec- g tric loss into the general, multipolar model using complex per- m c mittivities and phasors. The tensor expression for the nth m Electrolytic Medium effective moment is: δ
˙ 4πε R2n+1n p(n) = 1 K(n)(∇)n−1E (23) (2n − 1)!! o σΣ εΣ (n) = (ε − ε )/ ε + ( + )ε where K 2 1 [n 2 n 1 1]. Then, time-aver- age expressions for force and torque are: Zint Cytoplasm ˙ ∗ p(n) [·]n (∇)n E (n) o F = Re (24a) Cell n! Membrane