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Biomech Model Mechanobiol. Author manuscript; available in PMC 2013 January 1.

Published in final edited form as:

Published online 2011 March 2. doi: 10.1007/s10237-011-0296-0

PMCID: PMC3158267

NIHMSID: NIHMS291299

Natalie Nilsen, Department of Biomedical Engineering, Johns Hopkins University, 720 Rutland Ave, Traylor 411, Baltimore, MD 21205, USA;

Alexander A. Spector: ude.uhj@rotcepsa

The publisher's final edited version of this article is available at Biomech Model Mechanobiol

Prestin was found in the membrane of outer hair cells (OHCs) located in the cochlea of the mammalian inner ear. These cells convert changes in the membrane potential into dimensional changes and (if constrained) to an active electromechanical force. The OHCs provide the ear with the mechanism of amplification and frequency selectivity that is effective up to tens of kHz. Prestin is a crucial part of the motor complex driving OHCs. Other cells transfected with prestin acquire electromechanical properties similar to those in the native cell. While the mechanism of prestin has yet to be fully understood, the charge transfer is its critical component. Here we investigate the effect of the mechanics of the surrounding membrane on electric charge transfer by prestin. We simulate changes in the membrane mechanics via the corresponding changes in the free energy of the prestin system. The free energy gradient enters a Fokker-Planck equation that describes charge transfer in our model. We analyze the effects of changes in the membrane tension and membrane elastic moduli. In the case of OHC, we simulate changes in the longitudinal and/or circumferential stiffness of the cell’s orthotropic composite membrane. In the case of cells transfected with prestin, we vary the membrane areal modulus. As a result, we show the effects of the membrane mechanics on the probabilistic characteristics of prestin-associated charge transfer for both stationary and high-frequency conditions. We compare our computational results with the available experimental data and find good agreement with the experiment.

The protein prestin was originally found in the membrane of the outer hair cells located in the cochlea of the mammalian ear (Zheng et al. 2000). These cells provide the ear with the amplification and sharp frequency selectivity via generating an active force and energy. The outer hair cell has two active sites, the soma (Brownell et al. 1985; Spector et al. 2006 for review) and stereocilia bundle on the cell’s top (Kennedy et al. 2005). Through the somatic activity (termed electromotility), the cylindrical cell converts changes in its membrane potential into length as well as radius changes (Brownell et al. 1985; Dallos et al. 1993). If cell is constrained, its electromotility results in an active force production (Hallworth 1995; Adachi and Iwasa 1997; Liao et al. 2007). The outer hair cell is capable of the electromotile force production up to frequencies of several tens of kHz (Frank et al. 1999). Prestin is a critical part of the motor complex driving outer hair cell electromotility (Zheng et al. 2000; Liberman et al. 2002; Dallos et al. 2008), and it is probably the fastest known membrane protein. The secondary and tertiary structures of this protein are being debated, however, it is commonly assumed that prestin undergoes conformational changes as a result of transfer of an electric charge through the membrane. In the whole cell or membrane patch clamp experiments, this charge is manifested as nonlinear current and nonlinear (voltage-dependent) capacitance (Ashmore 1987; Santos-Sacchi 1989). What is the nature of this charge? Its understanding evolved from purely protein charges (Ashmore 1994) through purely extrinsic chloride ions (Oliver et al. 2001) to the later appreciation that the transferred charge probably includes the interrelated intrinsic prestin charges and intracellular chloride ions (Rybalchenko and Santos-Sacchi 2003; Muallem and Ashmore 2006; Bai et al. 2009; Sun et al. 2009). Coupling (interconnection) of the mechanical and electrical processes is the physical basis of outer hair cell electromotility, and the molecular manifestation of such coupling is the interrelated conformational changes and electric charge transfer. Several modifications (treatments) of membranes associated with changes in their mechanical properties or tension indeed resulted in changes in the charge transferred by prestin and nonlinear capacitance (Kakehata and Santos-Sacchi 1995; Adachi and Iwasa 1997; Dong and Iwasa 2004; Murdock et al. 2005). Thus, the interaction with the surrounding membrane plays an important role in prestin function.

Previously, the mechanical effects on charge transfer in outer hair cells and cells transfected with prestin were analyzed on the basis of 2(3)-state models (Iwasa 1994; Adachi and Iwasa 1997; Adachi et al. 2000) under the conditions of application of a DC electric field. Here, our analysis of the effects of the membrane mechanics considers novel features of prestin-associated charge transfer, including a probabilistic characterization of the charge being at a given position inside the membrane and high frequency effects. While the exact nature of the prestin-associated charge and prestin structure are not fully understood our approach is general: depending on the free energy as a function of the *z*-coordinate different scenarios can be simulated, including a finite set of the states of the charge. In our consideration, the high-frequency charge is composed of capacitive and resistive components, also a feature that was not considered before our model.

In our modeling of the effects of membrane mechanics, we consider changes in the membrane in-plane moduli and membrane tension. We consider two types of cells: outer hair cell that has a cylindrical shape and an orthotropic membrane and a representative cell transfected with prestin (e.g., HEK cell) whose membrane is assumed to be isotropic and spherical. The changes in the membrane mechanics are introduced via changes in the system’s free energy that enters a Fokker-Planck equation describing the process of charge transfer in our model. We show that the considered changes in the membrane properties can significantly affect the probability of the charge being at a particular position inside the membrane as well as the amplitude of such probability in the DC+AC case. These effects are greatest near the DC-potential value that corresponds to the point of highest sensitivity of the system. In addition to the probability densities, we also consider the total probabilities of charge being transferred. In the case DC fields, we compare the total computed probabilities with the experimental values of the transferred charge and show good qualitative and quantitative agreement with the experiment. The proposed approach can be extended to include other membrane effects such as bending, strain in the direction normal to the membrane, and membrane thickness change. The model can also be used in studies of other membrane proteins, including voltage-gated and mechano-sensitive channels.

Prestin was found in the membrane of outer hair cells, one of two sensory cells located in the organ of Corti of the mammalian cochlea (upper introductory panel in Fig. 1). While inner hair cells passively convert the information on the mechanics of the cochlear structures into a neural signal going to the brain, outer hair cells, affect the mechanics of these structures by generating an active force and energy. Prestin, a critical part of the outer hair cell motor complex that includes the protein, surrounding membrane, and external ions, undergoes conformational changes associated with electric charge transfer across the membrane. We assume that a system of charges that involves external charges (chloride ions shown as—circles in Fig. 1) and internal protein charges (amino acid residues shown as × circles in Fig. 1) is perturbed by the application of an electric field (changes in the transmembrane potential). Since experiments report charge translocation in terms of a single coordinate across the membrane, *z*, we will describe the evolution of the prestin-associated charges in terms of its average position as a function of *z*. The average position of the prestin-associated charges is characterized by a probability density, *ρ*(*z*, *t*), of taking *z*-coordinate at a moment of time, *t* (shown as black squares in Fig. 1). This function satisfies a stochastic Fokker-Planck equation (Sun et al. 2009):

$$\frac{\rho t=\frac{z(\frac{D}{{k}_{B}T}\frac{Vz\rho +D\frac{\rho z}{)}}{}}{}}{}$$

(1)

where *D* is the effective diffusion coefficient, *k _{B}* is the Boltzmann constant,

$$\frac{\text{d}P}{\text{d}t}={k}_{1}(1-P)-{k}_{-1}P$$

(2)

where *P* is the probability of chloride ion binding and *k*_{1} and *k*_{−1} are the attachment and detachment rate constants. The boundary conditions for Eq. 1 are formulated in terms of flux, *J*, where

$$J=-\frac{D}{{k}_{B}T}\frac{Vz\rho -D\frac{\rho z}{}}{}$$

(3)

We assume that

$$J(t,0)=\frac{\text{d}P}{\text{d}t}\phantom{\rule{0.38889em}{0ex}}\phantom{\rule{0.38889em}{0ex}}\phantom{\rule{0.38889em}{0ex}}\text{and}\phantom{\rule{0.38889em}{0ex}}\phantom{\rule{0.38889em}{0ex}}\phantom{\rule{0.38889em}{0ex}}J(t,L)=0$$

The first of the above boundary conditions ensures the continuity of flux at the point of chloride ion binding, and the second condition assumes that there is no charge transport outside the protein. Thus Eqs. 1 and 2 are related through the first boundary condition at *z* = 0. The second boundary condition at *z* = *L* can be easily modified if experimental evidence for prestin transferring charge through the membrane becomes available. We assume that prestin undergoes a conformational change when the charge (average position of the charge system) reaches an upper part of the protein of fractional length, *l*^{*} (Fig. 1). Thus, this event is characterized by a probability, *P*^{*},

$${P}^{}$$

In general case, *P*^{*} is a function of time. Below we consider DC and AC+DC electric fields applied across the protein, and we use constant limiting *P*^{*} (its amplitude) that corresponds to the steady state (steady oscillation) regime of charge transfer. As it was previously shown (Sun et al. 2009), the solution of the system (1), (2) in the AC + DC-case has an intrinsic feature of a phase shift (delay) with respect to the applied electric field. The phase shift is determined by the effective diffusion coefficient, and it increases with frequency. Such phase shift constitutes two, capacitive (in-phase with the applied field) and resistive (at 90° to the applied field) components of the transferred charge.

The main focus of the consideration below is the effect of changes in the membrane elastic (in-plane) properties or membrane tension on charge transfer by prestin. Mathematically, this effect is analyzed via the corresponding changes in the *z*-gradient of the free energy of the system, which is the charge driving force in Fokker-Planck equation (1). We assume that the free energy of the system, *V*, can be presented as the sum of electrical and mechanical components

$$V={V}_{\text{el}}+{V}_{\text{mech}}$$

The electrical component of the free energy is determined by the externally applied electric field as well as by the field generated by the system of involved charges, extrinsic ions, internal protein charges, membrane surface charges, etc., but we limit our consideration to the contribution of the applied electric field. We approximate the *z*-gradient of the electrical energy that enters Eq. 1 as

$$\frac{{V}_{\text{e}1}z\approx -\frac{q\mathrm{\Psi}}{L}}{}$$

where *q* is a typical charge and Ψ is the applied transmembrane potential. We associate the elastic component of the free energy with the energy accumulated in the elastic membrane surrounding prestin as a result of the conformational change in the protein. We approximate the *z*-gradient of this component of the free energy as

$$\frac{{V}_{\text{mech}}z\approx \frac{\mathrm{\Delta}{V}_{\text{mech}}}{L}}{}$$

(4)

where Δ*V*_{mech} is the increment in the membrane elastic energy related to a conformational change of prestin. Note, that such approximation of the *z*-gradient of the free energy allows us not to consider the intermediate strains in the surrounding membrane that correspond to the changing position of the charge moving along the *z*-axes. Instead, we can use the ultimate membrane strain associated with the protein conformational change, and this strain corresponds to the fully transferred charge. Note also that while we can neglect the intermediate positions of the charge in the consideration of the free energy gradient, all these positions are under consideration when we analyze the effect of membrane mechanical changes of the electric charge.

In the case of changes in the elastic moduli of the membrane, the mechanical energy in Eq. 4 is a quadratic function of the strains generated in the membrane by conformational changes of prestin. The coefficients in this function are determined by the elastic moduli of the membrane. In the case of variation of the membrane tension, the mechanical energy is a linear function of the change in the membrane area caused by the conformational change of prestin. The coefficients in this linear function are determined by the membrane tension. Below, we consider several examples of changes in the membrane properties coming from experiments or in vivo models of prestin performance, derive the corresponding changes in the free energy (its mechanical component), and estimate the resulting effect on the transferred electric charge.

Here we consider the outer hair cell case and find how the elastic energy accumulated in the membrane due to the conformational change of an individual prestin molecule depends on the membrane elastic moduli. The outer hair cell membrane is a tri-layer composite that can be effectively described by a linear orthotropic model (Tolomeo and Steele 1995; Spector et al. 1998, 2002). Note that prestin molecules distributed along the cylindrical surface of the outer hair cell also contribute to the effective mechanical properties of the composite outer hair cell membrane. The elastic energy that we seek depends on membrane/cell constraints, and a sketch of such constraints for the outer hair is shown in Fig. 1. The model used here can be applied to the in vivo case where the cell is constrained by the cochlear structures (Fig. 1) as well as the experiment to measure the cell active force where the cell is stimulated electrically and interacts with an elastic fiber. The total (observable) strain *ε*(*ε _{x}*,

$$\begin{array}{l}{C}_{xx}{\epsilon}_{x}^{m}+{C}_{x\theta}{\epsilon}_{\theta}^{m}=\mathrm{\Delta}pR-k{\epsilon}_{x}\\ {C}_{x\theta}{\epsilon}_{x}^{m}+{C}_{\theta \theta}{\epsilon}_{\theta}^{m}=\mathrm{\Delta}pR\end{array}$$

Here Δ*p* is reactive pressure occurring due to incompressibility of the cell’s liquid core when the cell deforms under the action of the applied electric field, *k* is the stiffness of the constraint (for the simplicity, we neglect here the viscous and inertial properties of the constraints), and *R* is the radius of the cylindrical cell. The volume preservation of the cylindrical cell yields to the condition of *ε _{θ}* = −0.5

$${C}_{xx}={C}_{\theta \theta}\phantom{\rule{0.16667em}{0ex}}(0.25+2.08\gamma )$$

(5)

$${C}_{x\theta}={C}_{\theta \theta}(0.5+1.08\gamma )$$

(6)

where the dimensionless parameter, *γ*, is defined as

$$\gamma =\frac{{C}_{xx}-{C}_{x\theta}+0.25{C}_{\theta \theta}}{{C}_{\theta \theta}}$$

(7)

The numerator in Eq. 7 for *γ* is proportional to the longitudinal cell stiffness, and this parameter is small within a realistic range of the cell stiffness. As a result, the membrane strains can be expressed in terms of the prestin-associated strain by the following equations

$${\epsilon}_{x}^{m}=\frac{0.54-\alpha}{1+\alpha}{\epsilon}_{x}^{pr}+\frac{1.08}{1+\alpha}{\epsilon}_{\theta}^{pr}$$

(8)

$${\epsilon}_{\theta}^{m}=-\frac{0.77}{1+\alpha}{\epsilon}_{x}^{pr}-\frac{1.54+\alpha}{1+\alpha}{\epsilon}_{\theta}^{pr}$$

(9)

where *α* = *k*/*γC _{θθ}*.

For the simplicity, we use a relationship between two components of the prestin-related strain that was observed in the microchamber experiment with outer hair cell electrical stimulation (Dallos et al. 1993; Hallworth et al. 1993). This experiment is suitable to extract the circumferential component of the prestin-associated strain or its ratio to the longitudinal one. First, this is the only available experiment that provides both the length and radius changes of the electromotile cell. Also, the liquid volumes of the cell’s parts inside and outside of the microchamber are not constrained, and the reactive pressure and tension are relatively small. Thus in this case, the observable strain can be interpreted as the active strain (e.g., Tolomeo and Steele 1995; Spector and Jean 2004). The prestin-associated strain used in our model can be extracted from the active strain that corresponds to the conditions of extreme negative and positive voltages. When the electric field changes between these extremes all prestin molecules located along the cell (membrane) surface fully transfer their electric charges and undergo conformational changes. We use the data of Dallos et al. (1993) that correspond to the equal lengths of included and excluded parts of the cell to extract the ratio of two components of the prestin-associated strain. We found this ratio being close to $-0.3\phantom{\rule{0.16667em}{0ex}}({\epsilon}_{\theta}^{pr}=-0.3{\epsilon}_{x}^{pr})$. It should be noted that not all the data of Dallos et al. (1993) are from the direct experimental measurements. However, we interpret them as an effective analytical extrapolation that is based on numerous direct measurements (Dallos et al. 1993; Hallworth et al. 1993) of the electromotile diameter changes for various voltages.

The surface density of the elastic energy accumulated as a result of changes in the membrane moduli, *C _{xx}*,

$$\mathrm{\Delta}{\widehat{V}}_{\text{mech}}=0.5\left[{C}_{xx}{({\epsilon}_{x}^{pr})}^{2}+2{C}_{x\theta}{\epsilon}_{x}^{pr}{\epsilon}_{\theta}^{pr}+{C}_{\theta \theta}{({\epsilon}_{\theta}^{pr})}^{2}\right]$$

(10)

Taking into account Eqs. 5–6 and 8–9, the energy density in Eq. 10 can be presented as

$$\mathrm{\Delta}{\widehat{V}}_{\text{mech}}=\frac{{({\epsilon}_{x}^{pr})}^{2}{C}_{\theta \theta}}{2{(1+\alpha )}^{2}}f(\alpha ,\gamma )$$

(11)

where

$$f(\alpha ,\gamma )=\left[(0.25+2.1\gamma )(0.22-\alpha )-2(0.5+1.1\gamma )\times (0.22-\alpha )\phantom{\rule{0.16667em}{0ex}}(0.31-0.3\alpha )+{(0.31-0.3\alpha )}^{2}\right]$$

The free energy change is the product of the energy density, Δ_{mech}, and a characteristic membrane surface area, *S _{m}*, involved in the deformation due to the conformational change of an individual prestin molecule. Assuming (for the simplicity) that the prestin molecules are circular with a radius of 10 nm and an edge-to-edge distance of 3 nm, such membrane area can be estimated as 100 nm

The cylindrical outer hair cell is under the action of turgor pressure, and we assume that changes in the cell membrane tension are caused by changes in the cell turgor pressure. Thus the mechanical component of the free energy associated with changes in the longitudinal,
${t}_{m}^{x}$ and circumferential,
${t}_{m}^{\theta}$, components of membrane tension (turgor pressure, *p*,) is expressed by the following equation

$$\mathrm{\Delta}{V}_{\text{mech}}={t}_{m}^{x}{S}_{m}^{x}+{t}_{m}^{\theta}{S}_{m}^{\theta}={\mathit{pRS}}_{m}^{x}+0.5{\mathit{pRS}}_{m}^{\theta}$$

Based on previous estimates (Dong and Iwasa 2004) of the components of the membrane area change in the outer hair cell due to prestin conformational change and direct comparison with experimental data (see below), we use ${S}_{m}^{x}\approx 3.75\phantom{\rule{0.16667em}{0ex}}{\text{nm}}^{2}$ and ${S}_{m}^{\theta}\approx -0.75\phantom{\rule{0.16667em}{0ex}}{\text{nm}}^{2}$.

We consider a membrane of an incompressible prestin-transfected cell of spherical shape and assume that its tension changes. We are interested in what would be the corresponding change in the elastic energy accumulated in the membrane surrounding an individual prestin molecule in response to its conformational change. The electrical stimulation does not change the volume of the spherical cell, which means that its surface area does not change either. This is true for any tension (pressure). It means that *S _{m}* = −

$$\mathrm{\Delta}{V}_{\text{mech}}=-{t}_{m}{S}_{pr}=-0.5pR{S}_{pr}$$

where *t _{m}* (

If a spherical membrane undergoes changes in its elastic properties (areal expansion modulus *K*) then the corresponding free energy density takes the form

$$\mathrm{\Delta}{\widehat{V}}_{\text{mech}}=0.5K{\left(\frac{{S}_{m}}{{S}_{0}}\right)}^{2}$$

(12)

where *S*_{0} is the membrane area associated with a single prestin molecule. Thus, the total energy can be determined by the following equation

$$\mathrm{\Delta}{V}_{\text{mech}}=\mathrm{\Delta}{\widehat{V}}_{\text{mech}}\phantom{\rule{0.38889em}{0ex}}\phantom{\rule{0.38889em}{0ex}}\phantom{\rule{0.38889em}{0ex}}{S}_{0}=0.5K\frac{{({S}_{m})}^{2}}{{S}_{0}}$$

(13)

First, we present the results for the outer hair cell cylindrical membrane. Figure 3 shows the effect of changes in the membrane elastic moduli on the probability density of the charge being at a position, *z*, and at a moment of time, *t*. The considered charge is moved by a DC electric field. The results in Fig. 3 are presented for three different values of the DC potential, Ψ = −10, 40, and 100 mV, respectively. Previously (Fig. 2), we showed the free energy change as a result of changes in the longitudinal and circumferential stiffness of the cell composite membrane. Here, we consider two changes in the free energy resulting in its increase by 4 × 10^{−21} J (dashed lines in Fig. 3) or its decrease by the same value (dotted lines). Such free energy increase can be achieved, for example, by a simultaneous increase in the longitudinal, from 0.001 to 0.012 N/m, and circumferential, from 0.02 to 0.5 N/m, stiffness of the membrane (Fig. 2). The solid lines in Fig. 3 correspond to the reference state without perturbation of the elastic properties of the membrane. In Fig. 4, we present the total probabilities, *P*^{*}, (normalized) of the charge being transferred as a function of DC voltage. We also consider the effect of the membrane mechanics on charge transfer under the action of an AC+DC field. In Fig. 5, we present the amplitudes of the probability density, Δ*ρ*(*z*, *t*), for two different frequencies, 6 and 57 kHz (upper and lower panels, respectively). The results in Fig. 5 are given for the same DC potential, Ψ = −10 mV. Here we consider the same perturbations in the mechanical properties of the composite membrane as those above in Figs. 3 and and4.4. Finally in Fig. 6, we present the amplitudes of the total probability, Δ*P*^{*}, as a function of the DC component of the electric field for the same two frequencies. The amplitudes are normalized by their low-frequency value. The presented curves for each frequency show the results for the same increase and decrease in the free energy that we considered for the purely DC field in Figs. 3 and and4.4. Figure 7 presents the results of our study of the effect of tension changes in the outer hair cell cylindrical membrane. We assume that tension changes via changes in the cell turgor pressure by its increase and decrease by 1 kPa (shown, respectively, in dashed and dotted lines in Fig. 7a). The results corresponding to the unperturbed pressure are given as a solid line. Here we consider the DC-field case and show the total probability, *P*^{*}, of charge being transferred. Figure 7b shows a comparison of our computational results for the total probability in the purely DC case with the available experimental data.

The probabilities, *ρ*, of the charge being at *z* (dimensionless)-position inside the protein for two changes in the electromechanical driving force (free energy of the system), 4×10^{−21} (*dashed lines*) and −4 × 10^{−21} **...**

The total (normalized) probability of the charge being transferred as a function of the DC potential. The free energy change due to changes in the membrane orthotropic properties are 4 × 10^{−21} (*dashed line*) and −4 × 10 **...**

The amplitudes of the probability of the charge being at the position *z* (dimensionless) for two frequencies, 6 and 57 kHz for the same DC potential of −10 mV. The results are presented for the changes in the free energy equal to 4 × 10 **...**

The amplitude of the total probability as a function of the DC potential for two frequencies, 6 (in *black*) and 57 kHz (in *red*). The *dashed and dotted lines* correspond, respectively, to changes in the free energy equal to 4 × 10^{−21} and **...**

Finally, we consider the effect of changes in tension (Fig. 8a) and elastic properties (Fig. 8b) in membranes of spherical prestin-transfected cells. Figure 8a shows the total (normalized) probability, *P*^{*}, as a function of the DC potential for an increase (dashed line) and decrease (dotted line) in turgor pressure by 1 kPa. The curve corresponding to the unperturbed cell is presented as a solid line. Based on Dong and Iwasa (2004), we use *S _{pr}* ≈ 2 nm

The dependence of prestin-associated charge transfer and nonlinear capacitance on the mechanics of the surrounding membrane is a manifestation of electromechanical coupling, a fundamental aspect of the outer hair cell motor complex and this cell’s active properties. The phenomenon of electromotility can be effectively described by continuous nonlinear or linearized piezoelectric relations (e,g., Tolomeo and Steele 1995). In continuum relations, the electrical displacement (charge per unit area) depends on the local strains. Here we develop a prestin-level model and analyze a similar effect of the mechanics of the surrounding membrane on the prestin-associated charge.

We found that the changes in the membrane mechanical properties or its tension have a significant effect on the process of electric charge transfer by prestin. In our model this process is described by the probability density (its amplitude) of the charge being at a given position at a particular moment of time. In the DC-case, it is convenient to use the probability densities corresponding to the steady state of the system (Fig. 3). The effect of the outer hair cell membrane mechanics (Fig. 3) is mainly determined by two factors: the closeness of the DC-potential to the point of highest sensitivity and the sign of the change in the mechanical component of the free energy. The electric charge measured in isolated outer hair cells as a function of voltage has the point of highest sensitivity close to −30 mV (e.g., Gale and Ashmore 1997a). In our model, the physical charge is represented by the probability density and the total probability of charge being transferred. Previously, Sun et al. (2009) adjusted the parameters of the solution of the Fokker-Planck equation to reflect that experimentally observed point of the highest sensitivity. The effect is most pronounced if the applied DC-potential is close to the point of highest sensitivity: compare changes due to the same amount of free energy change in the cases of Ψ* _{DC}* = −10 mV and Ψ

In addition to the local characteristics of charge transfer, we analyze the effect of the membrane mechanics on the total probability of the charge being transferred (Fig. 4). In the DC-case, the increase in the mechanical component of the free energy results in a uniform shift of the curve toward more negative potentials (hyperpolarization direction). A decrease in the free energy results in a shift in the depolarization direction. Such pattern means that a decrease (increase) in the mechanical component of the free energy causes a uniform decrease (increase) in the total probability of the charge being transferred. Similar shifts were found in the amplitude of the total probability for both frequencies in Fig. 6. Note that the total probability in Fig. 6 reflects both capacitive and resistive components of the transferred charge (Sun et al. 2009).

The experimental information on the effect of changes in the mechanical properties of the orthotropic outer hair cell membrane is limited. The diamide treatment (Adachi and Iwasa 1997) of the outer hair cell destroys the connections between the spectrin and actin fibers in the cytoskeleton, changing the composite membrane elastic properties. It has been shown that the longitudinal stiffness of the cell decreases with increasing concentration of diamide. Although the resulting changes in nonlinear capacitance or transferred charge have not been reported, there are results for electromotility of unconstrained cells. Electromotility (whose behavior is normally similar to that of nonlinear capacitance) exhibits a shift toward the hyperpolarization direction in response to cell treatment with diamide. Our model predicts that a decrease in the longitudinal stiffness of the cell shifts the *P*^{*}-probability, that represents the transferred charge, in the depolarization direction. This qualitative result is fully consistent with the experimental data of the diamide treatment. Quantitatively, Adachi and Iwasa (1997) reported a shift of about 37 mV in electromotility of unconstrained cells treated with 3 mM concentration of diamide. This treatment results in an about three-time decrease in the cell longitudinal stiffness. The computed here *P*^{*}-shift that corresponds to a three-time decrease in the parameter *C _{xx}* −

In addition to the effect of changes in the outer hair cell in-plane moduli, we also consider changes in the mechanical properties of the cells transfected with prestin. Since we assume that membranes of such cells are isotropic the only elastic modulus describing the membrane in-plane elastic properties is the areal modulus, *K*. The estimates of this parameter under normal conditions are 0.16 N/m for a pure lipid bilayer, 0.45 N/m, for the red blood cell membrane (Evans and Skalak 1980), and 0.07 N/m for the outer hair cell membrane (Iwasa and Chadwick 1992). Although in the two latter cases the membranes are composite, the outermost plasma membrane is probably responsible for the effective areal modulus. The estimate for the lipid bilayer is probably most relevant to this study. Thus, we consider an increase and decrease in this modulus by 0.1 N/m. We found a very small effect of such changes on the charge transfer. This small change is enlarged in the insert in Fig. 8 that corresponds to the voltage range of the highest sensitivity of the total probability, *P*^{*}.

We also analyze the effects of changes in the membrane tension in the cylindrical (outer hair cell) and spherical (cell transfected with prestin) membranes. We assume that tension is changed via changes in cell turgor pressure. The resulting voltage dependence of *P*^{*} shows shifts in the depolarization (hyperpolarization) direction if turgor pressure increases (decreases). This shift is about 25 mV per unit turgor pressure change in the cylindrical membrane (Fig. 7a), and it is about 61 mV/kPa in the spherical membrane (Fig. 8a). The tension effect due to changes in cell turgor pressure has been studied experimentally (Kakehata and Santos-Sacchi 1995; Adachi et al. 2000; Dong and Iwasa 2004) and theoretically (Adachi et al. 2000; Dong and Iwasa 2004). It is important here to compare our computational results on the tension effect in the purely-DC case with the available experimental data. Our computational probability, *P*^{*}, exhibits shifts similar to those observed in the experimental charge and nonlinear capacitance. The experimental data have also shown a slight decrease in the magnitude of the capacitance as a function of pressure. We do not discuss this effect here because we present the normalized values of the probability, *P*^{*}. To make a quantitative comparison with experimental data, we combine in Fig. 7b the data from two groups (Kakehata and Santos-Sacchi 1995 and Adachi et al. 2000; black and open circles, respectively). Figure 7b shows good qualitative and quantitative agreement of our results (solid line as a linear approximation) and the experimental data. In addition, Dong and Iwasa (2004) analyzed the turgor pressure (tension) effect in prestin-transfected HEK cells. In order to study the purely membrane effect, the cells were treated with trypsin that destroyed the cell cytoskeleton. Our computational result for spherical cells under variable turgor pressure is about 61 mV/kPa which is quite close to the experimental shift in experimental nonlinear capacitance of about 59 mV/kPa.

Some effects of the membrane mechanics on electric charge transfer by prestin are not associated with the in-plane mechanical properties or tension, and their explanation requires a modification of the current version of the model. One of such examples is the treatment of prestin-containing membranes with chlorpromazine. Lue et al. (2001) observed an about 20 mV shift of outer hair cell nonlinear capacitance in the depolarization direction in outer hair cells treated with chlorpromazine. On the other hand, Murdock et al. (2005) probed the outer hair cell membrane mechanical properties pulling membrane tethers and measuring the equilibrium tether holding force. This force decreases with the application of chlorpromazine. These results can not be explained from the standpoint of changes of membrane in-plane properties or tension. However, these results could be consistent with an effect on other membrane mechanical properties. Chlorpromazine is known to affect the membrane bending properties (Sheetz and Singer 1976) and the above observations are consistent with changes in the membrane bending modulus. Indeed, the tether holding force is proportional to the square root of the membrane bending modulus (Derényi et al. 2002). Thus, a chlorpromazine-related decrease in the membrane bending modulus can result in decreases in the tether force, and it could also cause the observed shift in nonlinear capacitance toward the depolarization direction. Another example of this type is the modulation of the membrane properties via changes the concentration of cholesterol. It has been shown that nonlinear capacitance in membranes with prestin shifts up to 100 mV in the depolarization direction in response to loading the membranes with cholesterol (Rajagopalan et al. 2007; Sfondouris et al. 2008). It was also shown (Nguyen and Brownell 1998) that such treatment is associated with an increase in the membrane stiffness. This is also inconsistent with changes in in-plane membrane moduli or tension and points out at other mechanisms involved. In addition, the damping in the membrane can affect prestin-associated charge transfer under high-frequency conditions. Such phenomenon can be analyzed by introducing a bi-directional coupling where the transferred charge is modulated by the time-dependence of free energy and the time-dependent mechanics of the surrounding membrane charge, in turn, is affected by the prestin charge. Our approach is general and it can be used for the analysis of various mechanical effects, such as membrane bending, thinning, and viscosity as well as effects of non-mechanical nature by incorporation of the corresponding components in the free energy of the system.

The proposed model describes the effects of the membrane mechanics on fine properties of electric charge transfer by the protein prestin, including the probability density of charge being at a given position inside the protein and its amplitude in the case of DC+AC-fields. This analysis covers high-frequency regimes that are characteristic to this protein that is functional throughout the whole frequency range. The elastic moduli of the outer hair cell orthotropic membrane can have a significant effect on electric charge transferred by prestin, especially at DC-voltages close to the point of the highest sensitivity of the system. In isotropic membranes of cells transfected with prestin, a variation of the area modulus has a little effect on the transferred charge. Changes in membrane tension can affect transfer of the electric charge significantly both in outer hair cells and cells transfected with prestin. A comparison of the tension-caused shifts in the total probability of charge being transferred show good qualitative and quantitative agreement with the available experimental data for the transferred charge and nonlinear capacitance. The current model can be extended to include other properties of the membrane such as bending modulus, membrane stiffness in the normal direction, and membrane thickness.

This research was supported by research grants DC 002775 and DC 000354 from National Institute on Deafness and Other Communication Disorders (NIH). We thank Dr. Aleksander Popel for the discussion of the obtained results.

Natalie Nilsen, Department of Biomedical Engineering, Johns Hopkins University, 720 Rutland Ave, Traylor 411, Baltimore, MD 21205, USA.

William E. Brownell, Bobby A. Alford Department of Otolaryngology, Head & Neck Surgery, Baylor College of Medicine, Houston, TX 77030, USA.

Sean X. Sun, Department of Biomedical Engineering, Johns Hopkins University, 720 Rutland Ave, Traylor 411, Baltimore, MD 21205, USA. Department of Mechanical Engineering, Johns Hopkins University, Baltimore, MD 21218, USA.

Alexander A. Spector, Department of Biomedical Engineering, Johns Hopkins University, 720 Rutland Ave, Traylor 411, Baltimore, MD 21205, USA. Department of Mechanical Engineering, Johns Hopkins University, Baltimore, MD 21218, USA.

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