Molecular medicine through gene therapy is challenged to achieve targeted action. This is now possible utilizing bionic electrode arrays for focal delivery of naked (plasmid) DNA via gene electrotransfer. Here, we establish the properties of array-based electroporation affecting targeted gene delivery. An array with eight 300 μm platinum ring electrodes configured as a cochlear implant bionic interface was used to transduce HEK293 cell monolayers with a plasmid-DNA green fluorescent protein (GFP) reporter gene construct. Electroporation parameters were pulse intensity, number, duration, separation and electrode configuration. The latter determined the shape of the electric fields, which were mapped using a voltage probe. Electrode array-based electroporation was found to require ~100 × lower applied voltages for cell transduction than conventional electroporation. This was found to be due to compression of the field lines orthogonal to the array. A circular area of GFP-positive cells was created when the electrodes were ganged together as four adjacent anodes and four cathodes, whereas alternating electrode polarity created a linear area of GFP-positive cells. The refinement of gene delivery parameters was validated in vivo in the guinea pig cochlea. These findings have significant clinical ramifications, where spatiotemporal control of gene expression can be predicted by manipulation of the electric field via current steering at a cellular level.
Electroporation is a technique widely used to deliver a variety of molecules, including drugs, proteins and nucleic acids, into cells.1, 2, 3, 4, 5 The underlying principle is that an electric field generated by a voltage pulse between two electrodes causes a transient dielectric breakdown of the plasma membrane of cells within the electric field, enabling molecules, such as negatively-charged DNA, to enter the cells. The process by which the cell membrane responds to the electric field, enabling DNA entry, is not well understood.4, 6, 7, 8, 9 DNA migration across the transiently permeabilized plasma membrane is not by simple diffusion, but may involve surface binding to a sustained ‘electropore’ compartment.10 Internalization is thought to occur via electrophoretically-driven movement of the DNA across the porated membrane,11, 12 or sphingosine (lipid raft)/DNA complex formation, which mitigates the hydrophobic plasma membrane domains of the electroporated zone.13 It is clear that once inside the cell, the DNA is able to migrate to the nucleus. Circularized plasmid DNA remains extra-chromosomal and can drive sustained episomal expression, while linearized DNA may be integrated into the chromosomal DNA, enabling targeted genetic modifications.
The most common use for electroporation-based gene delivery is for molecular biology research, where simple plate electrodes within cuvettes enable routine transformation of electro-competent cells. High intensity electric field electroporation (~8000 V cm−1) was first utilized for mammalian gene delivery in a suspended cell application.14 Electroporation-based gene delivery has subsequently been extended to in situ, ex vivo and in vivo applications with the development of specialized electroporation systems. These electroporation systems include a variety of electrode designs and voltage pulse shaping as part of optimized electroporation parameters, along with custom electroporation solutions and electrodes. Key parameters include pulse intensity, pulse duration and repetition frequency.4, 15, 16, 17, 18 These systems have proved effective in facilitating research in a range of cell and tissue types, including developmental neurobiology studies,19, 20, 21 clinical electro-gene therapy and electrochemotherapy applications.22, 23, 24
Despite the wide range of electroporation applications both in vitro and in vivo, current technology has largely involved the application of electric fields utilizing conventional ‘open-field’ electrode configurations where two electrodes (typically plates or needles) are located either side of the target cells or tissue. This necessarily determines the electric field at the tissue level (macro domain), rather than considering electric fields at the cellular level (micro domain). A limited number of studies have investigated micro domain electroporation using glass microelectrodes with an external current return.25, 26, 27 Closely apposed electrodes (for example, created by ion deposition and photolithography) with sub-millimetre spacing for electroporation of immediately adjacent cells or cell processes within culture chambers have also been investigated.28, 29 In such cases, the voltages required to achieve electroporation-based delivery of reporter gene constructs are considerably reduced over conventional electroporation modes (typically less than 10 V in comparison with several 100s V or even 1000 V in conventional electroporation).
In a recent study,30 we reported the development of bionic electrode array-based electroporation (defined in that study as ‘close-field electroporation’), whereby a cochlear implant array comprising a linear series of 300 μm diameter platinum ring electrodes was used to control electroporation within the cellular domain. Unlike macro domain electroporation, where cells are targeted between the electrodes through the shortest path for the current, array-based electroporation (micro domain) targets cells adjacent to the array of electrodes, where the electric field is shaped around the array by the combination of current sources and current returns with sub-millimetre separation between the anodes and the cathodes. In a pre-clinical proof of concept study,30 we utilized a linear 8-node cochlear implant electrode array that provided unanticipated efficiency and spatial control of delivery of a bicistronic neurotrophin and GFP expression cassette within the deafened guinea pig cochlea. The array-based electroporation gene therapy targeted mesenchymal cells adjacent to the array to express the neurotrophin alongside the GFP reporter, stimulating auditory nerve regeneration towards the electrodes. The result of this neural regeneration was a marked improvement in cochlear implant performance. To follow on from this discovery, here we describe, using a high-throughput HEK293 cell monolayer model, a systematic analysis of array-based electroporation parameters and measurement of electric field shaping, directed to optimizing control of gene delivery. These findings have significant ramifications for the translation of array-based directed gene electrotransfer into the broad realm of gene therapy applications within the nervous system and beyond.
Validation of HEK293 cell monolayers as a model for evaluating array-based electroporation
Initial studies utilized the two bionic array electrode configurations adopted for ex vivo and in vivo gene delivery by array-based electroporation in the auditory nerve regeneration study by Pinyon et al.30 to confirm gene delivery was reproducible in a HEK293 cell monolayer. The pulse parameters were comparable to that previous study (40 V, 5 pulses at 40 and 20 ms). Array electrode configurations were as previously defined: The ‘tandem’ configuration utilized four consecutive electrodes ganged together as anodes and the other four electrodes were cathodes; an ‘alternating’ configuration had the anodes and cathodes alternating along the length of the array (Figure 1). Nuclear-localized GFP expression by the HEK293 cells was imaged after 48 h (n=3 per array configuration; Figure 2). These preliminary experiments demonstrated consistent cell transformation and showed that the array configuration affected the shape of the region of GFP-expressing cells. The use of the tandem configuration of electrodes provided a quasi-circular area of GFP-positive cells centred around the confluence between the four anodes and the four cathodes (Figure 2a). In contrast, the ‘alternating’ array configuration typically produced smaller areas of GFP-positive cells, with a linear pattern aligned with the longitudinal axis of the array (Figure 2b).
Effect of varying electrode configuration on array-based electroporation
To determine the impact of the electrode configuration on array-based electroporation gene delivery, five different electrode configurations (‘alternating’; ‘tandem’; ‘1+2’; ‘1+5’; ‘1+8’; Figure 1) were compared using a common set of pulse parameters (40 V, 10 pulses of 50 ms duration). There was a significant effect on transformation efficiency due to array configuration, with variation in the space between anode and cathode, and in the number and pattern of anodes and cathodes (one-way ranked analysis of variance (ANOVA), P<0.001; n=4 per configuration; Figure 3). All electrode configurations produced significant cell transduction compared with the control group (Table 1). The control group (no-electroporation) exhibited 0.8±0.8 GFP-positive cells per coverslip. Within particular configurations, the number of transduced HEK293 cells was highly reproducible (varying from 7.0±3.1 (‘1+8’ configuration) to 219.0±37.7 (‘tandem’). The ‘1+2’ array configuration resulted in a circular area of cells ~1 mm diameter, with the active electrodes at the centre (Figure 3d). As for the initial experiments, the ‘alternating’ electrode configuration produced a linear bias to the area of transfected cells, extending the length of the array (~5 mm; 81.8±11.3 GFP-positive cells; Figure 3e). The ‘1+8’ and ‘1+5’ array configurations yielded smaller average numbers, which had a broad, low density distribution (Figures 3b and c). The transfection efficiency with the tandem configuration was significantly higher than any of the other configurations (Figures 3f and g; Table 1). As noted in the preliminary experiments (Figure 2a) using different pulse parameters, the pattern of transduction was circular in shape, centred around the mid-point of the array, which was the confluence point between the four anodes and the four cathodes. These data suggest that a key feature of array-based electroporation is sub-millimetre separation between the anode and cathode poles within the array; highlighting the difference between transduction using local electric field focusing and conventional ‘open-field’ electroporation, where the target region is located between separated electrodes.
Electric field mapping
Given the profound influence of electrode array configuration on the shape and density of the area of transformed cells, electric fields were mapped for all five electrode array configurations (Figures 4 and 5). The fields were sampled via the voltage probe with ~300 μm sampling separation parallel to the array and ~1 mm orthogonal separation of the tracks. The voltage applied to the array was 4 V, with quasi steady-state voltages at 100 ms measured at each position using all five configurations. This approached the maximum potential (~500 mV peak) that could be recorded via the isolated probe immediately adjacent to the array (Figures 4 and 5a). The ‘tandem’ array exhibited the greatest change in electric field around the null position, tracking from the junction between the anodes and the cathodes (Figures 5a and b). In contrast, despite utilizing an equivalent number of electrode elements, the ‘alternating’ array configuration had potentials that changed more gradually with distance from peak values close to electrode nodes, with the highest potentials around the tip of the array (Figure 5c). The electric field around the arrays was closely correlated with the spatial mapping of GFP-reporter gene expression. Thus, the cell transduction was dependent upon the change of voltage across the cells, rather than the maximum voltage that could be measured within the sampled region around the array. In the ‘tandem’ configuration, the magnitude of the measured potentials was greatest at either end of the array, but the field was relatively uniform in that region. With regard to the electric field map for the ‘tandem’ configuration, the null point in the field migrates orthogonally to the array between electrodes 4 and 5 (Figure 5b). The field contour lines are steepest about this null region and are maintained in a spherical shape, which corresponds to the transduced cell map (Figures 2a and 3f). In configurations ‘1+2’, ‘1+5’ and ‘1+8’, as the distance separating the bipolar electrodes increased, the rate of decline in the field relative to the electrode nodes lessened (Figures 5d–f).
Although the voltages applied to the array to measure these voltages in the bath solution were below those required for array-based gene electrotransfer (imposed by the upper voltage limit of the isolated voltage-following amplifier), nevertheless, estimates of field intensity required for gene delivery can be extrapolated from the linearity in growth of the sampled local voltage with increasing voltage applied to the electrode array (shown in Figure 4b). On this basis, from Figure 5b, the measured electric field ~500 μm lateral to the tandem array spanning electrode 2 to electrode 7 (defining the diameter of the area of GFP-positive cells in Figure 3f) was 114 μV μm−1 for 4 V applied. Thus, the electric field intensity that transduced the cells in Figure 2a (40 V applied) can be estimated at ~2.17 mV μm−1 (~22 V cm−1; allowing for ~2 V polarizing potential of the Pt. electrodes). The maximum electric field strength for the ‘alternating’ configuration was ~100 μV μm−1 (1 V cm−1) for the 4 V applied, around the apex of the array, but was more spatially limited (~1/3rd of the diameter of the tandem field), with multiple foci along the array. This is consistent with the linear rather than spherical area of GFP-positive cells achieved using this array configuration.
Electric pulse parameters
The effect of electric pulse parameters was systematically resolved utilizing the most efficient electrode configuration (‘tandem’).
The numbers of transformed cells increased significantly with increasing pulse amplitude (40 ms duration, 10 pulses, 1 per second; Figure 6). The 40 V amplitude produced more than 40 times greater transformation than the 10 V amplitude (196.7±18.5 vs 5.9±1.1 for 10 V and 32.3±6.3 for 20 V; n=9 per group). No transformed cells were detected in the six control experiments (GFP plasmid, no-electroporation). The perimeters of the areas of GFP-positive HEK293 cells were determined for the 40 V group to estimate density (29±2 cells per mm2, n=6). The overall density of HEK293 cells was established using 4′,6-diamidino-2-phenylindole (DAPI) fluorescence (5097±333 cells per mm2). Hence, transduction efficiency was ~0.6%, which reflects a fall-off towards the perimeter.
Pulse number was a significant factor in cell transduction; at both 40 and 20 V × 40 ms pulses (two-way ranked ANOVA, P<0.001; n=6 per group, except for 5 pulses (n=9)). At 40 V, all pulse numbers (1, 3, 5, 10, 20 and 40) resulted in significantly greater transduction than the control (no-electroporation); ranked ANOVA, multiple comparisons vs control group (Holm–Sidak method; P<0.001 above 1 pulse; P=0.031 1 pulse; n=6 per group, except for the 5 pulses group (n=9)) (Figure 7; Table 2), with 5, 10 and 20 pulses providing the maxima (range 147–170 cells) with no significant difference between these treatments (ANOVA, Holm–Sidak comparisons). At 20 V, sets of 3, 5, 10 and 20 pulses resulted in significantly greater transduction than the control (no-electroporation); ranked ANOVA, multiple comparisons vs control group (Holm–Sidak method; P<0.003; n=6 per group) (Figure 7; Table 2). The peak number of GFP-positive cells averaged 22 for 10 V. There was a decline in transfected cell numbers at 40 pulses for both 20 and 40 V. In addition, we observed propidium iodide fluorescence close to the electrode array position (Figure 8). This is a marker of cell permeability and cell toxicity, and the finding suggests that this roll-off in cell transformation is probably attributable to electrolytic and mechanical disruption of the cell monolayer associated with gassing, which was evident as fine bubbles on the surface of the electrodes after the electroporation sequence (evident in Figure 5a). On this basis, higher charge deliveries were not undertaken.
Pulse duration experiments were undertaken with a single pulse or 5 pulses. All pulse duration experiments other than 0.1 ms for 1 pulse produced significant cell transduction (P<0.004; ranked ANOVA; Holm–Sidak multiple comparisons for 1 pulse; Mann–Whitney rank sum test for 5 pulses, 0.1 ms; P=0.026; n=6 per group). Cell transduction was maximum at 100 ms pulse duration. Five pulses produced significantly greater transduction than 1 pulse (two-way ranked ANOVA, 10–400 ms indicating a significant interaction between pulse number and pulse duration; P<0.001; Figure 9; Table 3). With a single pulse, there was no difference between 40 ms (38.3±5.1 cells), 100 ms (51.7±7.8 cells; n=6) and 400 ms (49.2±6.9 cells; n=6) (P>0.05; Holm–Sidak multiple comparisons), whereas with the 5-pulse treatment, 40 ms (147.2±12.4 cells) and 100 ms (211.7±16.6 cells) pulse durations produced significantly greater cell transformation than the other durations (P=0.003 and P<0.001, respectively). The 400-ms pulse duration with 5 pulses resulted in a 5.5-fold decline from maximum (38.3±10.2 cells; n=6 per group) (P<0.001; two-way ranked ANOVA, Holm–Sidak multiple comparisons), because of electrolytic toxicity.
Separation of pulses between 50 ms and 1 s for 2 × 40 ms pulses, or 5 × 40 ms pulses, had no effect on the level of cell transduction (2 pulses, P=0.255; 5 pulses, P=0.437; two-way ranked ANOVA; Holm–Sidak multiple comparisons); n=3 per group (2P), n=5 per group (5P) (Figure 10).
In vivo gene delivery
The refinement of the array-based electroporation parameters was validated in vivo, in the guinea pig cochlea, with 2 × 100 ms pulses (10 V) resulting in GFP-positive mesenchymal cell nuclei consistently localized to the basal of the four turns of scala tympani (19.6±7.8; range 6–47 cells (5/6 animals); no-electroporation controls showed 0 and 8 cells in two animals). This aligned closely with the placement of the electrode array (Figure 11). In one of the five GFP-positive test cochleae mesenchymal cells on scala vestibuli surface of Reissner’s membrane were also labelled, as described previously.30 The region of GFP-positive cells spanned ~2 mm along scala tympani, consistent with the focused gene delivery evident in the HEK293 cell monolayer experiments.
In our proof-of-principle study that demonstrated gene electrotransfer in the guinea-pig cochlea using a linear bionic electrode array,30 we showed that the charge delivery required to achieve efficient cell transduction was least when the array was configured for anodes and cathodes ganged together as bipoles (‘tandem’ configuration). The HEK293 cell monolayer is shown here to provide a high-throughput model for analysis of electrode array-based gene delivery; validating and extending our earlier ex vivo and in vivo findings of the significance of array configuration. As shown by Pinyon et al.,30 the ‘tandem’ configuration permitted significantly greater transduction efficiency compared with the equivalent number of electrodes wired in ‘alternating’ configuration. The current study also demonstrated that smaller bipolar electrode configurations were less efficient (1+2, 1+5, 1+8). The reason that the ‘tandem’ array configuration shows unanticipated efficiency of cell transduction is attributed here to the geometry of electric field focusing (Figure 5). The ‘tandem’ array showed the highest electric field intensity adjacent to the electrodes compared with the other configurations. Given the spherical GFP-positive area of cells centred around the null point of the ‘tandem’ array (Figures 2a and 3f; orthogonal to the point between electrodes 4 and 5—Figure 5b), our data indicate that it is the change in electric potential across the cell (local electric field intensity), rather than the absolute step change in electric potential amplitude, that drives electroporation and DNA uptake. Thus, the tip region of the tandem array exhibited the largest local change in voltage, but this did not generate the most intense electric field (located lateral to the mid-region of the array). The cell distributions for the other array configurations showed similar association with the measured electric field intensity, and the drop off in number of GFP-positive cells in the 1+2>1+5>1+8 was correlated with the broadening in the electric field relative to the electrodes (Figures 5d–f). Electric field mapping using our low impedance probe had high spatial resolution, and depended upon isolation of the current stimulator and voltage probe and preclusion of ground loops. We also had the benefit of the quasi two-dimensional space provided by the HEK293 cell monolayer for stereotaxic manipulation of the probe census positions. An indirect approach for mapping electric field distribution in mouse tumour during electroporation has utilized magnetic resonance electric impedance tomography current density analysis with brief (100 μs) high field pulses between two needle electrodes.31 This study resolved local high voltages around each of the electrodes, with a minimum at the mid-point between the electrodes, resembling our voltage measurements for the 1+8 bipolar array configuration (Figure 5f).
The present study also demonstrates that pulse duration is a key determinant of the cell transduction process, with an optimum around 100 ms. Direct measurement of electric fields with increasing voltage steps shows some initial decay from peak due to the faradaic capacity of the platinum electrodes (Figure 4b). At voltages >2 V, sustained voltages are developed, approaching steady state by ~100 ms (Figure 5a). This is compatible with the concept that a sustained voltage gradient across the cells is required for efficient micro domain electroporation. The electric fields recorded here provide a relative representation of the fields that were generated, as the isolated voltage sensor was unsuitable for recording at the applied voltages associated with DNA uptake. However, above 2.5 V the voltages in the bath increased linearly with increasing voltage applied to the array, and at 4 V the maximum sustained potentials approached ~± 250 mV immediately adjacent to the distal ends of the anode and cathode in the ‘tandem’ configuration. Extrapolating to a 20-V pulse, which is efficient for gene delivery, the electric potential is likely to approach ±2250 mV. In the ‘tandem’ array, the effective diameter of the area of GFP-positive cells was ~50% of the array (2.5 mm), which indicates that the electric field would be ~1125 mV per 2.5 mm=4.5 V cm−1. Hence at the cellular level, the effective field is ~450 μV μm−1.
Electroporation is still considered problematic for therapeutic gene delivery due to the low efficiency, trauma from placement of electrodes into tissues, and the typically high voltages that are required to enable DNA uptake. This can be perceived as a noxious stimulus, affecting the target organs and tissues, and may also impact on DNA stability.23, 32 Study of the electroporation process at the single cell level has revealed that the transfection efficiency follows a different relationship to the electroporation efficiency with regard to the electric fields. Faurie et al.6 demonstrated using suspended Chinese hamster ovary cells that field strengths of 200 V cm−1 were sufficient for electroporation, but 400 V cm−1 was required for transfection based on expression of a reporter transgene. Similarly, Zhou et al.33 utilized 400 V cm−1 for macro domain electroporation of HEK293 cells (160 V between electrodes in a cuvette with a 4-mm gap). A study of DNA uptake into skeletal muscle showed benefit from a combination of short duration (100 μs) ‘high voltage’ (800 V cm−1) and longer duration (100 ms) ‘low voltage’ (8 V cm−1) pulses to respectively permeablize and facilitate electrophoresis of the DNA across the plasma membrane.1 Studies using fluorescently-labelled DNA indicate that while the cells are permeabilized on both sides across the electric field, the (TOTO-1 labelled) plasmid-DNA only entered the cells on the cathode side.4, 6 The permeabilization of the cell membrane occurs in the short time domain of the voltage pulses (typically in the μs–ms range), while recovery of cell integrity occurs over minutes.34 This is consistent with our propidium iodide fluorescence imaging, which was performed 30 min after electroporation and indicated that membrane integrity was restored in the transduced cells. Pulse amplitude affects the rate at which the cell membrane becomes permeable and the area of the membrane that is electroporated; pulse duration and pulse number affect the degree of permeabilization.4, 34 The permeabilization process depends upon the electric field causing charge redistribution on the cell membrane that occurs faster than the capacitance time constant of the cell. Thus, cell geometry is crucial, with mammalian cells requiring lower voltages than the smaller bacterial cells. In any case, it has been suggested that the applied voltages need to cause transmembrane potentials of ~200 mV or more for electroporation gene delivery.34 To achieve such a transient change in transmembrane potential, typically high field strengths are required in the macro domain for cell suspensions and tissue transfection (for example, ~1.2 kV cm−1, equivalent to 480 V with a 4mm electrode gap34). Our current data indicate that the electric potential required outside the cells for electroporation and gene delivery can be achieved using applied voltages ~100 times less with array-based micro domain electroporation than those required for macro domain electroporation. This is consistent with the reduction in applied voltages reported for electrotransfer of DNA in chick embyro neurodevelopment studies with very closely apposed electrode pairs (1 mm exposure, 4 mm separation, 3–5 × 50 ms pulses at 25 V);19 approximating our micro domain 1+5 array configuration. Our electric potential measurements show that the electric field compression, and hence electrotransfer, increases as the anode and cathode separation is minimized within the bionic array.
Clinical measures that utilize implantable bionic prostheses such as cochlear implants and deep brain stimulators are by their nature amenable to the incorporation of complementary gene therapy via array-based electrotransfer. This method of gene delivery, validated in our original proof of principle experiments showing cochlear implant array-mediated delivery of the BDNF-GFP gene cassette to the guinea-pig cochlea30 and refined here in vivo using just two 100 ms pulses at 10 V applied in the ‘tandem’ configuration, has the potential to provide a much safer and more targeted genetic enhancement than can currently be provided by other approaches, such as viral vectors or lipofection. The more immediate translation of electrode array-based gene delivery would be via adaptation of existing bionic neural prosthesis, while future development of custom electrode arrays may extend the control of the shape and extent of the transduced area of cells which the current study demonstrates as a proof of principle. Bionic array-based gene electrotransfer provides an imminently controllable targeting of gene delivery using naked DNA, which is not achievable with other processes. The utility of combining directed gene delivery that enhances the neural interface—such as demonstrated by Pinyon et al.,30 for neurotrophin-driven repair of the auditory nerve, may complement current (bionic) approaches and improve outcomes for patients. For example, the spatiotemporal control of gene delivery achievable with this micro domain array-based electroporation may offer a refinement of possible viral vector-based treatment of Parkinson’s disease by gene therapy targeting neurochemical modulation of the subthalamic nucleus with a glutamic acid decarboxylase (GAD65) DNA construct.35 Electroporation of naked DNA gene cassettes also has clear advantages over other gene delivery technologies due to the lack of inflammatory responses compared with lipofection33 or viral vectors (particularly adenovirus)36 and because the size of the plasmid DNA cassettes is relatively unconstrained.
Overall, the study demonstrated remarkable control of cell transformation with naked DNA was achievable—with ‘dial-up’ predictability in localized gene delivery and consequent expression of the gene construct being achieved. This evident control of the site and extent of gene expression is a key element in safe and effective gene therapy approaches for treatments of brain disorders in particular, where therapeutic action is required at specific sites. With regard to potential tissue damage, the highest charge deliveries resulted in electrolytic action and significant physical disruption to the HEK293 cell monolayer due to gassing. This is a result of the Faradaic current limits of the platinum electrodes, we previously estimated as a minimum effective charge delivery of ~25 mC cm−2,30 where the pseudocapacity of the platinum electrodes for reversible charge delivery is ~210 μC cm−2.37 Thus even with inert electrodes such as platinum, possible electrochemical damage to cells may be a factor when relatively long pulse durations, high voltages and long pulse trains are utilized, with potential changes in pH arising from production of H+ at the anode and O2 or Cl2 gas, and OH− production at the cathode from reduction of water.38 Tissue (Joule) heating may also be associated with electroporation and both raise cell temperature and potentially destabilize DNA.39 Translation of bionic array-based gene therapy applications would need to be achieved below charge delivery levels that could damage cells in the neighbourhood of the electrode array. Such an outcome has been demonstrated in vivo, in the case of BDNF gene cassette delivery in the guinea-pig cochlea.30 In the cochlea, the physical dimensions of the fluid space (scala tympani) where cochlear implants are inserted closely match the spatial dimensions for effective electrode array-based gene delivery. The mapping of the electric fields around the cochlear implant shows close overlap between the area of GFP transduction in HEK293 monolayers and the site of transfection within the perilymphatic compartments of the cochlea, in which the basal turn of the guinea pig is around 2 mm in diameter. That study also showed that transduction of a few hundred (mesenchymal) cells with a neurotrophin gene cassette was sufficient to stimulate neural regeneration. Thus, intrinsic therapeutic peptide synthesis and release by limited number of cells achieved by array-based plasmid DNA electrotransfer may have strategic therapeutic advantages over conventional drug delivery or broader gene delivery using alternative approaches.
The current study utilized a high-throughput model, the HEK293 cell monolayer, to characterize the parameters contributing to the newly identified process of electrode array-based gene delivery. The study showed that the shaping of the electric field around a linear array of closely spaced sub-millimetre sized electrodes contiguous with the target cell population was the key element in efficient cell transduction. The potential difference across the cell, an approximate estimate of local electric field to which the cell is exposed, was the principal factor in transduction, rather than the absolute change in voltage during the electric pulse. Pulse duration and number of pulses also contributed to the transduction efficiency. The configuration of the array of electrodes, and hence the shape of the resulting electric field, provided control over the shape of the area of transduced cells. In combination, these factors lend ‘dial-up’ control of electrode array-based gene electrotransfer.
Materials and methods
The experiments utilized a plasmid (7481 bp) encoding the humanized renilla green fluorescent protein (GFP) reporter fused to a nuclear localization signal. The reporter was driven by the cytomegalovirus early enhancer element, chicken β-actin (CAG) hybrid promoter. The woodchuck post-transcriptional regulatory element was added downstream from the open reading frame. For electrode array-based electrotransfer, the plasmid was purified from E. coli using a Plasmid Maxi Kit (Qiagen, Melbourne, VIC, Australia) and resuspended at 2 μg μl−1 in 50 mM Tris-buffered saline (pH 7.4).
The human embryonic kidney (HEK293) cell line (Thermo Fisher Scientific, Melbourne, VIC, Australia) was used as the substrate for evaluation of electrode array-based gene delivery. The cells were maintained in Dulbecco’s Modified Eagle’s Medium supplemented with 10% heat-inactivated fetal bovine serum (HI-FBS, Thermo Fisher Scientific), 1% Penicillin/Streptomycin mix (Thermo Fisher Scientific), 1% non-essential amino-acids (Thermo Fisher Scientific). Cells were split the day before electroporation and applied to glass coverslips that had the array placement marked on the underside (~80% confluence). Cells were maintained in an incubator (37 oC, 5% CO2).
Electroporation used a CUY21 Square Wave Electroporator (NepaGene), connected to a linear 8-node cochlear implant array (Cochlear Ltd, Sydney, NSW, Australia; part no. Z60276; after 30). The array consisted of eight platinum ring electrodes each 350 μm diameter, of 300 μm width, separated by a 300μm gap. To electroporate the HEK293 cells, the coverslip with the cells was removed from the cell culture well and placed on a raised flat surface. The electrode array was lowered onto the coverslip, and the DNA was evenly applied over the array (20 μl). Electroporation was then initiated using particular electrode configurations and electroporation parameters. Immediately after electroporation, coverslips were placed in a humidity chamber for 2 min before returning to fresh, pre-warmed media in the incubator.
At 48 h post electroporation, HEK293 cell monolayers were fixed with 4% paraformaldehyde for 30 min and then gently washed with phosphate-buffered saline for 15 min. The coverslips with the transformed cells were mounted on glass slides using Prolong Gold mounting medium containing 4′,6-diamidino-2-phenylindole (DAPI) (Thermo Fisher Scientific). The slides were left to cure at room temperature for 24 h in the dark before storage at 4 oC until imaging. The areas of transformed HEK293 cells were imaged using a × 2.5 objective on a confocal laser scanning microscope (Zeiss LSM 710; Carl Zeiss Pty Ltd, Sydney, NSW, Australia, argon ion laser; 488 nm excitation; 493–598 nm emission). Transfected cells expressing GFP were manually counted from the images.
Effect of electrode array configuration on gene electrotransfer
The electrodes within the array were configured as anodes and cathodes as follows (Figure 1): 1+2 (a single anode and a single cathode with 300 μm separation), 1+5 (a single anode and a single cathode with 2.45 mm separation), 1+8 (a single anode and a single cathode with 4.55 mm separation), ‘tandem’ (four juxtaposed ganged cathodes, then four ganged anodes, all elements with 300 μm separation; total length 5.4 mm) and ‘alternating’ (alternating cathodes and anodes with 300 μm separation; total length 5.4 mm) (‘tandem’ and ‘alternating’ configurations are after Pinyon et al.30). Comparison of the effect of array configuration on gene electrotransfer utilized a single electric pulse parameter set: 40 V, 10 pulses, 50 ms duration, 1 pulse per second.
Effect of pulse parameters on gene electrotransfer
Using the ‘tandem’ array configuration, the pulse parameters were 10 V, 20 V or 40 V, 10 pulses, 40 ms pulse duration, 1 pulse per second (n=9 per group).
Using the ‘tandem’ array configuration, the pulse was set at 10 V or 20 V, pulse number ranging from 1 to 40 (1, 3, 5, 10, 20 and 40), 40 ms pulse duration, 1 pulse per second (n=6 per group, except for 5 pulses where n=9).
Using the ‘tandem’ array configuration, the pulse was set at 40 V, 1 or 5 pulses, and a range of pulse durations (0.1–400 ms), with appropriate gap durations to achieve 1 pulse per second (999.9–600 ms) (n=6 per group).
Using the ‘Tandem’ array configuration, the pulse was set at 40 V, 2 or 5 pulses, 40 ms pulse duration, and a range of pulse separations (50, 100, 250, 500 and 1000 ms) (n=3 per 2 pulses group and n=5 per 5 pulses group).
Evaluation of cell toxicity
Using the tandem array configuration, a range of pulse profiles was used to assess cell toxicity (0–100 V; 1–40 pulses, 40 ms pulse duration, 1 pulse per second). The plasmid DNA in Tris-buffered saline was applied to the coverslip. Immediately after electroporation, coverslips were placed in a humidity chamber for 2 min. Coverslips were then placed in fresh, warmed media, and returned to the incubator for 30 min. Cell death was identified by propidium iodide fluorescence, where incubation with propidium iodide (2 μg ml−1) was undertaken for 5 min at 37 oC. Coverslips were washed in phosphate-buffered saline and fixed in PFA, before imaging using the confocal LSM (Helium-Neon laser, 633 nm excitation; emission 588–649 nm).
Electric field mapping
The electric field focusing produced by the five different cochlear implant electrode array configurations was mapped using a custom platinum electrode insulated to ~300 μm from the tip (SAFELEAD F-E2-24; Grass Technologies, Rockland, MA, USA), with an isolated voltage-following amplifier (Axopatch 200B; Axon Instruments, Molecular Devices, Sunnyvale, CA, USA) and a silver silver-chloride reference electrode (Figure 4a). Junction potentials were offset-adjusted to zero, and potentials were measured at the end of a 100ms 4 V pulse applied to the array (Figure 4b). Below ~2 V, the potential decayed to zero as the platinum electrodes polarized (Figure 4b). From ~3 V, the quasi steady-state potential at 100 ms increased linearly with increasing applied voltage. Data were low-pass filtered at 1 kHz and captured at 50 kHz sampling rate using a Digidata 1440 interface (Axon Instruments). Data were analyzed using the Clampex Software (version 10.2.0.12; Axon Instruments). The voltage-sensing electrode was positioned relative to the electrode array using a translational stage (SliceScope Pro 6000; Scientifica, East Sussex, UK), and a 3D micromanipulator (ROE-200; Sutter Instrument Company, Novato, CA, USA). Images were captured to map the location of the probe in relation to the electrode array using video imaging (Zeiss LSM710, 0.5 × converter; MF cool ProgRes CCD camera and software; JENOPTIK, Jena, Germany). Constant voltage pulses were delivered to the electrode array using an analogue controlled isolated stimulator (Model 2200; AM Systems, Sequim, WA, USA).
In vivo gene delivery
Bionic array-based gene delivery of the GFP reporter plasmid DNA was undertaken in the normal hearing guinea pig cochlea. This followed the procedure outlined by Pinyon et al.30 using coloured guinea pigs of both sexes 300–900 g in weight, following a UNSW Australia Animal Care and Ethics Committee approved protocol. No randomization or blinding was done for animal experiments. Six array-based gene delivery experiments were undertaken, along with two no-electroporation control experiments. These sample sizes were determined from the previous low background signals in controls;30 no statistical comparisons were undertaken for these experiments and no exclusion criteria were used. Under isoflurane anaesthesia, the plasmid DNA (2 μg μl−1 in Tris(hydroxymethyl)aminomethane (Tris) buffer) was delivered to the cochlea via the round window (20 μl in 40 s using a microdrive pump; Narashige IM-1, Narishige International USA, Inc., Amityville, NY, USA). The electrode array was then inserted into the basal turn scala tympani via the round window and 2 × 100 ms pulses (10–15 V) were applied using the ‘tandem’ configuration. The array was removed after 2 min, and the post-auricular surgical field was closed. The animals were killed after 1 week and following fixation with 4% paraformaldehyde, the nuclear-localized GFP reporter signal in the target mesenchymal cell area adjacent to the electrode array was visualized using confocal laser scanning microscopy (Zeiss NLO710 LSM, Jena, Germany; argon laser 488 nm nm excitation, 492–548 nm emission; background fluorescence was imaged using a 561-nm diode pumped solid state laser, 564–690 nm emission).
Treatment effects were analyzed using ranked one- or two-way ANOVA with validation of normal distribution (Sigmaplot v.12.5; Systat Software, Inc., San Jose, CA, USA). Individual comparisons used Holm–Sidak multiple comparisons with alpha=0.05 for baseline statistical threshold; or ranked ANOVA with Tukey’s test post hoc pairwise comparisons. Data are presented as mean±standard error of mean. Sample sizes are stated for each experiment within the Results section and Figure legends.
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Professor Gregg Suaning is thanked for discussion around electric field modelling. Funded by an Australian Research Council Discovery Grant (DP151014754).
Three patent filings are associated with this research: (i) Title: Method of providing agents to the cochlea. Inventor: GD Housley. Filing status: National Phase Examination—Europe (application no. 10799287.7; filing date 5 July 2010), National Phase—United States (application no. 13/384020; filing date 5 July 2010). Assignee: NewSouth Innovations Pty Limited. (ii) Title: Method and apparatus for close-field electroporation. Inventor: GD Housley, M Klugmann, J Pinyon. Filing status: Provisional, Australia (application no. 2013902263; filed 21 June 2013). Assignee: NewSouth Innovations Pty Limited. (iii) Title: Electroporation system for controlled localized therapeutics delivery. Inventor: GD Housley, NH Lovell. Filing status: Australian Provisional Patent filing (application no. 2015902456; filing date 25 June 2015). Assignee: NewSouth Innovations Pty Limited.
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Browne, C., Pinyon, J., Housley, D. et al. Mapping of bionic array electric field focusing in plasmid DNA-based gene electrotransfer. Gene Ther 23, 369–379 (2016). https://doi.org/10.1038/gt.2016.8
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