Changes in membrane structure induced by electroporation as revealed by rapid-freezing electron microscopy.

Cells can be transiently permeabilized by exposing them briefly to an intense electric field (a process called "electroporation"), but it is not clear what structural changes the electric field induces in the cell membrane. To determine whether membrane pores are actually created in the electropermeabilized cells, rapid-freezing electron microscopy was used to examine human red blood cells which were exposed to a radio-frequency electric field. Volcano-shaped membrane openings appeared in the freeze-fracture faces of electropermeabilized cell membranes at intervals as short as 3 ms after the electrical pulse. We suggest that these openings represent the membrane pathways which allow entry of macromolecules (such as DNA) during electroporation. The pore structures rapidly expand to 20-120 nm in diameter during the first 20 ms of electroporation, and after several seconds begin to shrink and reseal. The distribution of pore sizes and pore dynamics suggests that interactions between the membrane and the submembrane cytoskeleton may have an important role in the formation and resealing of pores.     

Mechanism of electroporative dye uptake by mouse B cells.

The color change of electroporated intact immunoglobulin G receptor (Fc gammaR-) mouse B cells (line IIA1.6) after direct electroporative transfer of the dye SERVA blue G (Mr 854) into the cell interior is shown to be dominantly due to diffusion of the dye after the electric field pulse. Hence the dye transport is described by Fick's first law, where, as a novelty, time-integrated flow coefficients are introduced. The chemical-kinetic analysis uses three different pore states (P) in the reaction cascade (C <==> P1 <==> P2 <==> P3), to model the sigmoid kinetics of pore formation as well as the biphasic pore resealing. The rate coefficient for pore formation k(p) is dependent on the external electric field strength E and pulse duration tE. At E = 2.1 kV cm(-1) and tE = 200 micros, k(p) = (2.4 +/- 0.2) x 10(3) s(-1) at T = 293 K; the respective (field-dependent) flow coefficient and permeability coefficient are k(f)0 = (1.0 +/- 0.1) x 10(-2) s(-1) and P0 = 2 cm s(-1), respectively. The maximum value of the fractional surface area of the dye-conductive pores is 0.035 +/- 0.003%, and the maximum pore number is Np = (1.5 +/- 0.1) x 10(5) per average cell. The diffusion coefficient for SERVA blue G, D = 10(-6) cm2 s(-1), is slightly smaller than that of free dye diffusion, indicating transient interaction of the dye with the pore lipids during translocation. The mean radii of the three pore states are r(P1) = 0.7 +/- 0.1 nm, r(P2) = 1.0 +/- 0.1 nm, and r(P3) = 1.2 +/- 0.1 nm, respectively. The resealing rate coefficients are k(-2) = (4.0 +/- 0.5) x 10(-2) s(-1) and k(-3) = (4.5 +/- 0.5) x 10)(-3) s(-1), independent of E. At zero field, the equilibrium constant of the pore states (P) relative to closed membrane states (C) is K(p)0 = [(P)]/[C] = 0.02 +/- 0.002, indicating 2.0 +/- 0.2% water associated with the lipid membrane. Finally, the results of SERVA blue G cell coloring and the new analytical framework may also serve as a guideline for the optimization of the electroporative delivery of drugs that are similar in structure to SERVA blue G, for instance, bleomycin, which has been used successfully in the new discipline of electrochemotherapy.     

Size of the pores created by an electric pulse: Microsecond vs millisecond pulses

Here, the sizes of the pores created by square-wave electric pulses with the duration of 100μs and 2ms are compared for pulses with the amplitudes close to the threshold of electroporation. Experiments were carried out with three types of cells: mouse hepatoma MH-22A cells, Chinese hamster ovary (CHO) cells, and human erythrocytes. In the case of a short pulse (square-wave with the duration of 100μs or exponential with the time constant of 22μs), in the large portion (30-60%) of electroporated (permeable to potassium ions) cells, an electric pulse created only the pores, which were smaller than the molecule of bleomycin (molecular mass of 1450Da, r≈0.8nm) or sucrose (molecular mass of 342.3Da, radius-0.44-0.52nm). In the case of a long 2-ms duration pulse, in almost all cells, which were electroporated, there were the pores larger than the molecules of bleomycin and/or sucrose. Kinetics of pore resealing depended on the pulse duration and was faster after the shorter pulse. After a short 100-μs duration pulse, the disappearance of the pores permeable to bleomycin was completed after 6-7min at 24-26°C, while after a long 2-ms duration pulse, this process was slower and lasted 15-20min. Thus, it can be concluded that a short 100-μs duration pulse created smaller pores than the longer 2-ms duration pulse. This could be attributed to the time inadequacy for pores to grow and expand during the pulse, in the case of short pulses.     

Modeling electroporation in a single cell

Electroporation uses electric pulses to promote delivery of DNA and drugs into cells. This study presents a model of electroporation in a spherical cell exposed to an electric field. The model determines transmembrane potential, number of pores, and distribution of pore radii as functions of time and position on the cell surface. For a 1-ms, 40 kV/m pulse, electroporation consists of three stages: charging of the cell membrane (0-0.51 micros), creation of pores (0.51-1.43 micros), and evolution of pore radii (1.43 micros to 1 ms). This pulse creates approximately 341,000 pores, of which 97.8% are small ( approximately 1 nm radius) and 2.2% are large. The average radius of large pores is 22.8 +/- 18.7 nm, although some pores grow to 419 nm. The highest pore density occurs on the depolarized and hyperpolarized poles but the largest pores are on the border of the electroporated regions of the cell. Despite their much smaller number, large pores comprise 95.3% of the total pore area and contribute 66% to the increased cell conductance. For stronger pulses, pore area and cell conductance increase, but these increases are due to the creation of small pores; the number and size of large pores do not increase.     

Reversible and irreversible modification of erythrocyte membrane permeability by electric field

Electric fields of a few kV/cm and of duration in microseconds are known to implant pores of limited size in cell membranes. We report here a study of kinetics of pore formation and reversibility of pores. Loading of biologically active molecules was also attempted. For human erythrocytes in an isotonic saline, pores allowed passive Rb+ entry formed within 0.5 microsecond when a 4 kV/cm electric pulse was used. Pores that admitted oligosaccharides were introduced with an electric pulse of a longer duration in an isosmotic mixture of NaCl and sucrose. These pores were irreversible under most circumstances, but they could be resealed in an osmotically balanced medium. A complete resealing of pores that admitted Rb+ took approximately 40 min at 37 degrees C. Resealing of pores that admitted sucrose took much longer, 20 h, under similar conditions. In other cell types, resealing step may be omitted due to stronger membrane structures. Experimental protocols for loading small molecules into cells without losing cytoplasmic macromolecules are discussed.     

Monitoring electropermeabilization in the plasma membrane of adherent mammalian cells.

When an electrical potential of order one volt is induced across a cell membrane for a fraction of a second, temporary breakdown of ordinary membrane functions may occur. One result of such a breakdown is that molecules normally excluded by the membrane can now enter the cells. This phenomenon, generally referred to as electropermeabilization, is known as electroporation when actual pores form in the membrane. This paper presents a unique approach to the measurement of pore formation and closure in anchored mammalian cells. The cells are cultured on small gold electrodes, and by constantly monitoring the impedance of the electrode with a low-amplitude AC signal, small changes in cell morphology, cell motion, and membrane resistance can be detected. Because the active electrode is small, the application of a few volts across the cell-covered electrode causes pore formation in the cell membrane. In addition, the heat transfer is very efficient, and the cells can be porated in their regular growth medium. By this method, the formation and resealing of pores due to applied electric fields can be followed in real time for anchorage-dependent cells.     

Cell membrane fluidity related to electroporation and resealing

In this paper, we report the results of a systematic attempt to relate the intrinsic plasma membrane fluidity of three different cell lines to their electroporation behaviour, which consists of reversible and irreversible electroporation. Apart from electroporation behaviour of given cell lines the time course required for membrane resealing was determined in order to distinguish the effect of resealing time from the cell’s ability to survive given electric pulse parameters. Reversible, irreversible electroporation and membrane resealing were then related to cell membrane fluidity as determined by electron paramagnetic resonance spectroscopy and computer characterization of membrane domains. We found that cell membrane fluidity does not have significant effect on reversible electroporation although there is a tendency for the voltage required for reversible electroporation to increase with increased membrane fluidity. Cell membrane fluidity, however, may affect irreversible electroporation. Nevertheless, this effect, if present, is masked with different time courses of membrane resealing found for the different cell lines studied. The time course of cell membrane resealing itself could be related to the cell’s ability to survive.     

Modeling electroporation in a single cell. I. Effects Of field strength and rest potential.

This study develops a model for a single cell electroporated by an external electric field and uses it to investigate the effects of shock strength and rest potential on the transmembrane potential V(m) and pore density N around the cell. As compared to the induced potential predicted by resistive-capacitive theory, the model of electroporation predicts a smaller magnitude of V(m) throughout the cell. Both V(m) and N are symmetric about the equator with the same value at both poles of the cell. Larger shocks do not increase the maximum magnitude of V(m) because more pores form to shunt the excess stimulus current across the membrane. In addition, the value of the rest potential does not affect V(m) around the cell because the electroporation current is several orders of magnitude larger than the ionic current that supports the rest potential. Once the field is removed, the shock-induced V(m) discharges within 2 micros, but the pores persist in the membrane for several seconds. Complete resealing to preshock conditions requires approximately 20 s. These results agree qualitatively and quantitatively with the experimental data reported by Kinosita and coworkers for unfertilized sea urchin eggs exposed to large electric fields.     

Dependence of Electroporation Detection Threshold on Cell Radius: An Explanation to Observations Non Compatible with Schwan’s Equation Model

It is widely accepted that electroporation occurs when the cell transmembrane voltage induced by an external applied electric field reaches a threshold. Under this assumption, in order to trigger electroporation in a spherical cell, Schwan’s equation leads to an inversely proportional relationship between the cell radius and the minimum magnitude of the applied electric field. And, indeed, several publications report experimental evidences of an inverse relationship between the cell size and the field required to achieve electroporation. However, this dependence is not always observed or is not as steep as predicted by Schwan’s equation. The present numerical study attempts to explain these observations that do not fit Schwan’s equation on the basis of the interplay between cell membrane conductivity, permeability, and transmembrane voltage. For that, a single cell in suspension was modeled and the electric field necessary to achieve electroporation with a single pulse was determined according to two effectiveness criteria: a specific permeabilization level, understood as the relative area occupied by the pores during the pulse, and a final intracellular concentration of a molecule due to uptake by diffusion after the pulse, during membrane resealing. The results indicate that plausible model parameters can lead to divergent dependencies of the electric field threshold on the cell radius. These divergent dependencies were obtained through both criteria and using two different permeabilization models. This suggests that the interplay between cell membrane conductivity, permeability, and transmembrane voltage might be the cause of results which are noncompatible with the Schwan’s equation model.     

Electroporation in dense cell suspension--theoretical and experimental analysis of ion diffusion and cell permeabilization

Electroporation is a process where increased permeability of cells exposed to an electric field is observed. It is used in many biomedical applications including electrogene transfection and electrochemotherapy. Although the increased permeability of the membrane is believed to be the result of pores due to an induced transmembrane voltage U(m), the exact molecular mechanisms are not fully explained. In this study we analyze transient conductivity changes during the electric pulses and increased membrane permeability for ions and molecules after the pulses in order to determine which parameters affect stabilization of pores, and to analyze the relation between transient pores and long-lived transport pores. By quantifying ion diffusion, fraction of transport pores f(per) was obtained. A simple model, which assumes a quadratic dependence of f(per) on E in the area where U(m)>U(c) very accurately describes experimental values, suggesting that f(per) increases with higher electric field due to larger permeabilized area and due to higher energy available for pore formation. The fraction of transport pores increases also with the number of pulses N, which suggest that each pulse contributes to formation of more and/or larger stable transport pores, whereas the number of transient pores does not depend on N.     

Kinetics and mechanism of cell membrane electrofusion.

A new quantitative approach to study cell membrane electrofusion has been developed. Erythrocyte ghosts were brought into close contact using dielectrophoresis and then treated with one square or even exponentially decaying fusogenic pulse. Individual fusion events were followed by lateral diffusion of the fluorescent lipid analogue 1,1'-dihexadecyl-3,3,3',3'-tetramethylindocarbocyanine perchlorate (Dil) from originally labeled to unlabeled adjacent ghosts. It was found that ghost fusion can be described as a first-order rate process with corresponding rate constants; a true fusion rate constant, k(f), for the square waveform pulse and an effective fusion rate constant, k(ef), for the exponential pulse. Compared with the fusion yield, the fusion rate constants are more fundamental characteristics of the fusion process and have implications for its mechanisms. Values of k(f) for rabbit and human erythrocyte ghosts were obtained at different electric field strength and temperatures. Arrhenius k(f) plots revealed that the activation energy of ghost electrofusion is in the range of 6-10 kT. Measurements were also made with the rabbit erythrocyte ghosts exposed to 42 degrees C for 10 min (to disrupt the spectrin network) or 0.1-1.0 mM uranyl acetate (to stabilize the bilayer lipid matrix of membranes). A correlation between the dependence of the fusion and previously published pore-formation rate constants for all experimental conditions suggests that the cell membrane electrofusion process involve pores formed during reversible electrical breakdown. A statistical analysis of fusion products (a) further supports the idea that electrofusion is a stochastic process and (b) shows that the probability of ghost electrofusion is independent of the presence of Dil as a label as well as the number of fused ghosts.     

Evaluations of a mechanistic hypothesis for the influence of extracellular ions on electroporation due to high-intensity,nanosecond pulsing

The effect of ions present in the extracellular medium on electroporation by high-intensity, short-duration pulsing is studied through molecular dynamic simulations. Our simulation results indicate that mobile ions in the medium might play a role in creating stronger local electric fields across membranes that then reinforce and strengthen electroporation. Much faster pore formation is predicted in higher conductivity media. However, the impact of extracellular conductivity on cellular inflows, which depend on transport processes such as electrophoresis, could be different as discussed here. Our simulation results also show that interactions between cations (Na⁺ in this case) and the carbonyl oxygen of the lipid headgroups could impede pore resealing.     

Electrical behavior and pore accumulation in a multicellular model for conventional and supra-electroporation

Extremely large but very short (20 kV/cm, 300 ns) electric field pulses were reported recently to non-thermally destroy melanoma tumors. The stated mechanism for field penetration into cells is pulse characteristic times faster than charge redistribution (displacement currents). Here we use a multicellular model with irregularly shaped, closely spaced cells to show that instead overwhelming pore creation (supra-electroporation) is dominant, with field penetration due to pores (ionic conduction currents) during most of the pulse. Moreover, the model's maximum membrane potential (about 1.2 V) is consistent with recent experimental observations on isolated cells. We also use the model to show that conventional electroporation resulting from 100 microsecond, 1 kV/cm pulses yields a spatially heterogeneous electroporation distribution. In contrast, the melanoma-destroying pulses cause nearly homogeneous electroporation of cells and their nuclear membranes. Electropores can persist for times much longer than the pulses, and are likely to be an important mechanism contributing to cell death.     

细胞电穿孔动态过程的荧光测量

利用改进后的Ｔｈ／ＤＰＡ荧光方法及探针ＥＢ对人血影及大鼠骨髓细胞电穿孔的动态过程及其与电脉冲参数的关系进行了系统的研究．测量结果表明,在临界点以上电场作用下,血影电穿孔在电击后０．２—０．３ｓ时达最大,在约０．８ｓ时愈合;而大鼠骨髓细胞电穿孔在电击后０．４—０．９ｓ达到最大,３－５ｓ左右愈合;电穿孔大小及扩大、愈合速率与电脉冲参数有关。１０－４０ｍｍｏｌ／Ｌ乙醇和５－２０ｍｍｏｌ／Ｌ成二醛抑制血影对Ｔｂ３＋离子的电通透,相同浓度的成二醛作用强于乙醇。这些结果将为电穿孔技术的合理应用提供参考。     

The Role of Ph Fronts in Tissue Electroporation Based Treatments

Treatments based on electroporation (EP) induce the formation of pores in cell membranes due to the application of pulsed electric fields. We present experimental evidence of the existence of pH fronts emerging from both electrodes during treatments based on tissue EP, for conditions found in many studies, and that these fronts are immediate and substantial. pH fronts are indirectly measured through the evanescence time (ET), defined as the time required for the tissue buffer to neutralize them. The ET was measured through a pH indicator imaged at a series of time intervals using a four-cluster hard fuzzy-c-means algorithm to segment pixels corresponding to the pH indicator at every frame. The ET was calculated as the time during which the number of pixels was 10% of those in the initial frame. While in EP-based treatments such as reversible (ECT) and irreversible electroporation (IRE) the ET is very short (though enough to cause minor injuries) due to electric pulse characteristics and biological buffers present in the tissue, in gene electrotransfer (GET), ET is much longer, enough to denaturate plasmids and produce cell damage. When any of the electric pulse parameters is doubled or tripled the ET grows and, remarkably, when any of the pulse parameters in GET is halved, the ET drops significantly. Reducing pH fronts has relevant implications for GET treatment efficiency, due to a substantial reduction of plasmid damage and cell loss.     

Model of creation and evolution of stable electropores for DNA delivery

Electroporation, in which electric pulses create transient pores in the cell membrane, is becoming an important technique for gene therapy. To enable entry of supercoiled DNA into cells, the pores should have sufficiently large radii (>10 nm), remain open long enough for the DNA chain to enter the cell (milliseconds), and should not cause membrane rupture. This study presents a model that can predict such macropores. The distinctive features of this model are the coupling of individual pores through membrane tension and the electrical force on the pores, which is applicable to pores of any size. The model is used to explore the process of pore creation and evolution and to determine the number and size of pores as a function of the pulse magnitude and duration. Next, our electroporation model is combined with a heuristic model of DNA uptake and used to predict the dependence of DNA uptake on pulsing parameters. Finally, the model is used to examine the mechanism of a two-pulse protocol, which was proposed specifically for gene delivery. The comparison between experimental results and the model suggests that this model is well-suited for the investigation of electroporation-mediated DNA delivery.     

Self-electroporation as a model for fusion pore formation

The creation of a small opening called the fusion pore is a necessary prerequisite for neurotransmitter release from synaptic vesicles. It is known that high intensity electric fields can create pores in vesicles by a process called electroporation. Due to the presence of charged phosphatidylserine (PS) molecules on the inner leaflet of the cell membrane, an electric field that is strong enough to cause electroporation of a synaptic vesicle might be present. It was shown by K. Rosenheck [K. Rosenheck. Biophys J 75, 1237-1243 (1998)] that in a planar geometry, fields sufficient to cause electroporation can occur at intermembrane separations of less than approximately 3 nm. It is frequently found, however, that the cell membrane is not planar but caves inward at the locations where a vesicle is close to it. Indentation of the cell membrane in the fusion region was modelled as a hemisphere and a theoretical study of the electric field in the vicinity of the cell membrane taking into account the screening effect of dissolved ions in the cytoplasm was performed. It was discovered that fields crossing the electroporation threshold occurred at a distance of 2 nm or less, supporting the claim that electroporation could be a possible mechanism for fusion pore formation.     

Life Cycle of an Electropore: Field-Dependent and Field-Independent Steps in Pore Creation and Annihilation

Electropermeabilization, an electric field-induced modification of the barrier functions of the cell membrane, is widely used in laboratories and increasingly in the clinic; but the mechanisms and physical structures associated with the electromanipulation of membrane permeability have not been definitively characterized. Indirect experimental observations of electrical conductance and small molecule transport as well as molecular dynamics simulations have led to models in which hydrophilic pores form in phospholipid bilayers with increased probability in the presence of an electric field. Presently available methods do not permit the direct, nanoscale examination of electroporated membranes that would confirm the existence of these structures. To facilitate the reconciliation of poration models with the observed properties of electropermeabilized lipid bilayers and cell membranes, we propose a scheme for characterizing the stages of electropore formation and resealing. This electropore life cycle, based on molecular dynamics simulations of phospholipid bilayers, defines a sequence of discrete steps in the electric field-driven restructuring of the membrane that leads to the formation of a head group-lined, aqueous pore and then, after the field is removed, to the dismantling of the pore and reassembly of the intact bilayer. Utilizing this scheme we can systematically analyze the interactions between the electric field and the bilayer components involved in pore initiation, construction and resealing. We find that the pore creation time depends strongly on the electric field gradient across the membrane interface and that the pore annihilation time is at least weakly dependent on the magnitude of the pore-initiating electric field and, in general, much longer than the pore creation time.     

The loading of human erythrocytes with small molecules by electroporation

The technology for loading the cell with membrane-impermeable substances by means of electroporation consists of the following three stages: (i) the creation of pores permeable for the desired substance; (ii) the introduction of a substance into the cell cytosol; and (iii) the restoration of the membrane barrier function. In this paper, the experimental data on the loading of human erythrocytes with small molecules (molecular weight below 500 Da) is presented. The results obtained show that increasing the intensity of the electric field pulse increases the fraction of electroporated cells. The pores through which the molecules of ascorbic acid and mannitol (radius below 0.5 nm) can enter the erythrocytes appear when the field strength exceeds 2.5 kV/cm. The concentration of ascorbic acid inside the cells increases linearly. At 4 degrees C, the rate of ascorbic acid influx was constant for at least 4 hours. The original permeability of most of the cells towards ascorbic acid and mannitol was restored after about 6-7 min at 37 degrees C, and the characteristic time for complete resealing was about 20-40 min. The procedure described here can be used for loading cells with membrane-impermeable substances.