ORIGINAL RESEARCH article
Front. Neuroeng., 20 April 2009 | https://doi.org/10.3389/neuro.16.004.2009
School of Electrical Engineering, Tel-Aviv University, Tel-Aviv, Israel
Institute of Neuroscience, Medical School, Newcastle University, Newcastle, UK
We have investigated the use of carbon nanotube coated microelectrodes as an interface material for retinal recording and stimulation applications. Test devices were micro-fabricated and consisted of 60, 30 μm diameter electrodes at spacing of 200 μm. These electrodes were coated via chemical vapor deposition of carbon nanotubes, resulting in conducting, three dimensional surfaces with a high interfacial area. These attributes are important both for the quality of the cell-surface coupling as well as for electro-chemical interfacing efficiency. The entire chip was packaged to fit a commercial multielectrode recording and stimulation system. Electrical recordings of spontaneous spikes from whole-mount neonatal mouse retinas were consistently obtained minutes after retinas were placed over the electrodes, exhibiting typical bursting and propagating waves. Most importantly, the signals obtained with carbon nanotube electrodes have exceptionally high signal to noise ratio, reaching values as high as 75. Moreover, spikes are marked by a conspicuous gradual increase in amplitude recorded over a period of minutes to hours, suggesting improvement in cell-electrode coupling. This phenomenon is not observed in conventional commercial electrodes. Electrical stimulation using carbon nanotube electrodes was also achieved. We attribute the superior performances of the carbon nanotube electrodes to their three dimensional nature and the strong neuro-carbon nanotube affinity. The results presented here show the great potential of carbon nanotube electrodes for retinal interfacing applications. Specifically, our results demonstrate a route to achieve a reduction of the electrode down to few micrometers in order to achieve high efficacy local stimulation needed in retinal prosthetic devices.
In recent years, multielectrode arrays (MEAs) have become a widespread tool for interfacing with neural assemblies, both for stimulation and recording purposes. Moreover, they are now recognized as one of the main approaches for the design of neural prosthetic devices to artificially restore impaired neural function (e.g. for vision, hearing and limb movement). With the exception of cochlear implants, this emerging technology does, however, still face tremendous challenges before these interfaces will become realistically useful as neural implants. One key issue is the biocompatibility of the electrode-tissue interface which must not only allow good electrical recording and stimulation performance, but also encourage strong cell adhesion and proliferation so that the electrodes remain effectively long-term coupled with the neurons. For optimal electrical coupling, the electrode surface must be as rough as possible so that it effectively enlarges the surface area. Independently, to achieve good biological coupling, the surface must be cell-adhesive. Interestingly, these two requirements can be attained concurrently if extremely rough and conducting surfaces are used (Gabay et al., 2007 ; Sorkin et al., 2006 ). Such surfaces can function both as excellent electro-chemical electrodes and substrates for neuronal growth. Using this novel approach it is possible to directly interface with neurons in an unmediated fashion (Shein et al., 2009 ).
Carbon nanotubes (CNTs) appear to be a most suitable interface material for these applications because they are chemically inert, robust against mechanical damage and easy to produce. In addition, high density CNT-coated surfaces are characterized by having an extremely high surface area. Most interestingly, CNTs appear to encourage neuronal growth. Finally, since CNTs are good electrical conductors, they may also function as very effective electrochemical electrodes. Resulting from this unique combination of properties, CNT electrodes offer exciting new opportunities as an interface material for neuronal applications. This has now been validated by several recent studies (Gabay et al., 2007 ; Hu et al., 2004 , 2005 ; Malarkey and Parpura, 2007 ; Mattson et al., 2000 ; Sorkin et al., 2006 ).
One medical application that may particularly benefit from this technology is retinal implants. Vision loss due to retinal degeneration (e.g. Leber Congenital Amaurosis; den Hollander et al., 2008 or age-related macular degeneration; Ehrlich et al., 2008 ) is a world-wide impairment in ageing populations, often leading to complete blindness. The common phenotype of these retinal dystrophies is photoreceptor degeneration, whilst retinal ganglion cells (RGCs), the output cells of the retina, remain intact and can still transmit information to the visual centers of the brain. Consequently, a plethora of projects aiming at developing retinal implantable prosthetic devices to stimulate RGCs directly, circumventing the degenerated photoreceptor pathway, have emerged in recent years (Rizzo et al., 2007 ). The results are indicative of the viability of MEA stimulation, but this technology is still very much in its infancy (Dowling, 2008 ; Mahadevappa et al., 2005 ; Rizzo et al., 2003 ). The present limited success arises from many technical challenges, ranging from biocompatibility and intraocular implant stability, to problems of stimulation efficacy and restriction of current spread across the retina following focal stimulation. Whilst an optimal device would have a 1:1 ratio of electrode to RGCs, most of the devices currently under development comprise arrays of as few as 12–16 electrodes, each with diameters of several hundred micrometers, thereby covering large retinal areas. Recent studies indicate significant improvement in spatial resolution (MEAs comprising 61 ITO electrodes; spacing 60 μm, diameters 6–25 μm) (Gunning et al., 2005 ; Sekirnjak et al., 2006 ). It is estimated that an array of 625 electrodes with center–center spacing of 20 μm would restore enough visual acuity to enable the patient to navigate their surroundings without additional external aids.
It is evident from many recent studies in the field that a key challenge in developing better MEAs for retinal implant devices is to achieve better coupling between the electrodes and the tissue. This, in turn, will allow the reduction of the electrode size and increase the electrode density on the device.
In this paper, we examined the suitability and the possible advantages of CNT MEAs for retinal implant applications. Using electrophysiological recordings from retinal whole mounts, we bring evidence, for the first time, that CNT electrodes lead to better electrode–tissue coupling, resulting in remarkable signal-to-noise ratio.
CNT MEAs were produced and packaged as reported previously (Gabay et al., 2007 ). Briefly, TiN electrodes were micro-fabricated on oxidized silicon or quartz substrates and were then passivated with SiN and coated with CNTs using chemical vapour deposition. CNTs grown are multi wall carbon nanotubes (MWCNTs). CNT diameters, estimated from scanning electron microscope imaging (Sorkin et al., 2009 ), average around 82 nm with very narrow distribution. CNT length is several microns. Moreover, energy-dispersive X-ray (EDX) analysis was carried out and reported in Gabay et al. (2007) and revealed no measurable quantities of the catalyst. Amorphous carbon may be present in our electrodes, and can be reduced, for long term, applications by varying growth parameters and post-growth thermal treatment (Wang et al., 2006 ). Samples were diced prior to growth to fit into a custom designed circuit board (PCB). After CNT growth, samples were mounted and glued to the PCB. A shallow quartz ring was glued to the PCB-silicon assembly to form a well to accommodate the artificial cerebrospinal fluid. The quartz ring was glued using a thin disk of polydimethylsiloxane (PDMS), which was shaped to accommodate the silicon-PCB and to provide leak-tight seal against liquid.
Tissue Preparation and Recordings
This study was done using C57bl/6 neonatal mice. All animal procedures were conducted under the UK Home Office, Animals (Scientific procedures) Act 1986. As described elsewhere (Hennig et al., 2009 ), mouse pups were killed by cervical dislocation and enucleated prior to retinal isolation. The isolated retina was then transferred to the experimental chamber and placed, RGC layer facing down, onto MEAs consisting either of 60 titanium nitride (TiN) electrodes (30 μm diameter, 200 μm spacing) arranged in an 8 × 8 grid on indium tin oxide substrate (MultiChannel Systems, Reutlingen, Germany) or of 60 CNT electrodes (30 μm diameter, 200 μm spacing) in an 8 × 8 grid on silicon substrate. Better coupling between the tissue and the electrodes was achieved by placing a small piece of polyester membrane filter (5 μm pores) (Sterlitech, Kent, WA, USA) on the retina followed by a slice anchor holder. Retinas were kept at 32°C and continuously perfused (2–5 ml/min) with artificial cerebrospinal fluid containing the following (in mM): 118 NaCl, 25 NaHCO3, 1 NaH2PO4, 3 KCl, 1 MgCl2, 2 CaCl2, and 10 glucose, equilibrated with 95% O2 and 5% CO2. It is standard in vitro procedure to keep brain slices or isolated retinas around 32°C rather than 37°C. Keeping them at higher temperature shortens the time recordings can be performed.
Signals were amplified (gain ×1,200) and acquired using a 128-channel analogue to digital converter (MultiChannel Systems MC_Card, Reutlingen, Germany). Signals were digitized at 25 kHz and acquired with 80 Hz high pass filtering using the software MC_Rack (MultiChannel Systems, Reutlingen, Germany). Once the retina was laid on the MEA, neural activity was sampled during 2–5 min at intervals ranging between 2–20 min. Typically the intervals were shorter at the beginning of the recording session, when changes in coupling occur fast, reflected by an increase in signal amplitude.
Spikes were threshold-detected with MC_Rack (the typical threshold was at signal amplitude that is three times above the RMS baseline noise) so that the firing on each electrode reflects the overall activity level generated by all RGCs on that same electrode (typically up to five cells). Once threshold-detected, spikes were additionally screened according to the method described in Hulata et al. (2002) . This method uses wavelet based spike detection and is used to remove non-biological spike-like data. Only electrodes yielding spontaneous activity equal or above 0.2 Hz were taken into consideration for further analysis.
Figure 1 A shows a CNT MEA on silicon substrate. Note that there are more CNT islands than electrodes. These extra CNT islands are used to assist in stabilizing the dissociated neuronal culture (Shein et al., 2009 ) or in this case, the whole tissue. Figure 1 B shows a high magnification (×9,500) micrograph of one CNT island, revealing its highly porous nature. Retinas were mounted on MEAs immediately after isolation. Figure 1 C illustrates a retina flattened on a CNT (30 μm CNT islands on 50 μm TiN support) array on quartz. The picture was taken from underneath the array using an inverted microscope (20× magnification). The cellular layer in focus with the CNT islands is the RGC layer and the arrow shows the edge of the retina. Figure 1 D was taken at higher magnification (32×) and clearly reveals well delineated RGC bodies (the arrow points to one RGC) as well as retinal blood vessels (asterisks). Previous studies on dissociated neurons have demonstrated high cell affinity to these porous CNT coatings (Gabay et al., 2007 ; Hu et al., 2004 , 2005 ; Malarkey and Parpura, 2007 ; Mattson et al., 2000 ; Sorkin et al., 2006 ), suggesting that CNTs have the potential for high biocompatibility for intact neural tissue such as the retina.
Figure 1. Carbon nanotube MEAs for retinal interfacing and recording. (A) General view of a CNT MEA. Each black dot is a CNT island. All 60 islands in the center of the field are electrodes whilst those at the periphery are not. (B) Micrograph of one CNT island (9,500× magnification) revealing the porous nature of the CNTs. Note that the island in Figure 1 B is a smaller island than those used in the CNT MEA configuration. (C) Micrograph (20× magnification) of a retina laid on a CNT MEA. The retina is flattened on the CNTs, with the RGC layer facing down, hence in contact with the CNTs. The arrow indicates the edge of the tissue. (D) Micrograph (32× magnification) of the same retina as in (C). The arrow points to a RGC body and the asterisks to blood vessels.
To compare how the retina interacts with CNT electrodes versus commercially available electrodes made of more conventional material, we have recorded RGC signals both from TiN-electrodes MEAs and from CNT-electrodes MEAs. Commercial TiN electrodes are porous by design to achieve high surface area and low impedance (Janders et al., 1996 ) with similar electrochemical properties to our CNT MEAs (Gabay et al., 2007 ) and they can therefore serve as a good platform for comparison. A systematic comparison between the electrochemical properties of CNT and commercial TiN electrodes is presented and discussed in Gabay et al. (2007) . Activity was recorded from retinas isolated from 2- to 3-week-old pups, when the retina has high levels of spontaneous activity, with RGCs firing in bursts of action potentials (Hennig et al., 2009 ; Sernagor et al., 2001 ). Figure 2 illustrates RGC spontaneous activity recorded from a TiN electrode (Figure 2 A) and from a CNT electrode (Figure 2 B). Both types of electrodes reveal action potential waveforms. Both recordings also suggest that the 30 μm-diameter electrodes recorded from more than one cell simultaneously, as indicated by at least two clear sets of signal amplitudes, suggesting that two RGCs contributed to the recordings. The quality of the recordings was typically superior with CNT electrodes both in terms of signal-to-noise ratio and in signal amplitude. Indeed, the baseline noise generally ranged from −10 to +10 μV in TiN electrodes whilst it was only −5 to +5 μV in CNT electrodes. Moreover, spike amplitudes reached substantially higher values in CNT electrodes.
Figure 2. Recordings of neural activity with CNT electrodes yield higher signal-to-noise ratio and amplitudes than commercial electrodes do. (A) Recordings obtained with a TiN electrode. The upper trace shows the typical unfiltered baseline noise level. The lower trace illustrates spontaneous spiking activity. The baseline noise is about ±10 μV. The largest spikes are about 100 μV in amplitude. (B) Recordings obtained with a CNT electrode. The larger spikes (lower trace) have amplitudes reaching up to nearly 300 μV.
The apparent superiority of the CNT electrodes is better demonstrated by examining the amplitude of the recorded signals. Figure 3 illustrates spike amplitude histograms from two TiN electrodes (Figure 3 A) and two CNT electrodes (Figure 3 B) recorded about 1 h after mounting the tissue on the MEAs (both electrodes in each case are from the same MEA, hence recording from the same retina). The overall activity shown in each panel of Figure 3 is similar, with a total of 500–700 spikes. Indeed there is no conspicuous difference between the activity rates of retinas on TiN and CNT electrodes. However, there is variability in the activity rate between different recording sites and between retinas (data not shown). Indeed, spontaneous activity patterns change dramatically over very short periods of time in the developing retina, switching from propagating waves (present from postnatal day 0–12) to scattered bursting activity that can occasionally be extremely strong (postnatal day 12–30). Moreover, there is also variability in activity with retinal eccentricity. Signals recorded from CNT electrodes can reach amplitude values that are more than twice as high as those recorded with TiN electrodes. It is interesting to notice that the higher values are not related to the total number of recorded spikes. Indeed, there was more neural activity in the retina used with both TiN electrodes than in the retina used with the CNT electrodes. Nevertheless, the TiN electrodes did not record particularly large signals. It is also important to note that the high amplitude signals are single unit recordings (as can be clearly seen in Figure 2 B) so, for the most part, the amplitude increase is not due to superposition of simultaneous recordings from several cells but rather to a real increase in the amplitude recorded from a particular neuron.
Figure 3. Comparison of spike amplitude distributions recorded with commercial versus CNT electrodes. (A) Histograms of spike amplitudes recorded from two TiN electrodes on the same MEA. Both distributions look relatively similar, with maximal amplitudes of about 100 μV. (B) Histograms of spike amplitudes recorded from two CNT electrodes on the same MEA. The amplitude distributions are broader than with TiN electrodes, starting from similar values (25–35 μV), but reaching much higher values (175 μV for electrode 35 and 290 μV for Electrode 83).
The porous nature of CNTs together with the fact that both the signal-to-noise ratio and the signal amplitudes are larger in CNT electrodes than in TiN electrodes led us to assume that the coupling between the tissue and the electrodes may improve with time on CNTs as the retina settles on the MEA and retinal cells become more intimately intermingled with the CNTs. This would be indicated by a gradual increase in spike amplitudes. To test this possibility, we have recorded signals at discrete intervals after tissue mounting on the electrodes, with the first sample always recorded within minutes after the beginning of the experiment, as soon as spontaneous activity becomes visible on the MEA. For both types of electrodes, the number of electrodes exhibiting neural activity generally increased with time. This is probably due both to tissue recovery from isolation from the eye and to improvement in coupling. However, signals recorded from TiN electrodes stabilized relatively quickly after tissue mounting whereas those recorded with CNT electrodes continued improving with time. Figure 4 illustrates the gradual increase in signal amplitude for two CNT electrodes (from the same MEA). The vertical axis represents spike amplitudes and the five panels respectively illustrate the recordings obtained from the electrodes at five consecutive time intervals. The strength of the bar shading on the graphs is proportional to the probability of recording and detecting spikes of given amplitude. In both cases there is a conspicuous increase in signal amplitude with time. The increase was already visible within 22 min from mounting for both electrodes. For electrode 75 (Figure 4 A), there was a gradual increase in amplitudes for spikes below 100 μV in subsequent samplings, as indicated by a downwards shift of high probabilities (dark shading). In addition to these changes, a new population of amplitudes ranging between 150 and 200 μV emerged at 47-min post mounting. The probability of occurrence of these larger spikes was low, as indicated by the light shading on the graph (marked by asterisks for easier detection). For electrode 83 (Figure 4 B), the amplitude group around 100 μV at the time of mounting clearly separated from the lower amplitudes in subsequent sampling periods, shifting to 150–200 μV at 22-min post-mounting. In later sampling periods, this same group of amplitudes increased to values above 200 μV.
Figure 4. Increase in spike amplitudes over time after retinal mounting on CNT electrodes. (A,B) Show two examples of amplitude changes recorded at increasing times after mounting (as indicated below the boxes) on two different electrodes from the same MEA. The vertical positions of the shaded bars in each box indicate the spike amplitudes whereas the shading itself indicates the probability of recording a spike at a given amplitude, with darker shading for higher probabilities. Asterisks indicate the positions of bars that are particularly difficult to detect because of the low probability of spike occurrence.
To systematically compare this effect for CNT and commercial MEAs, we have quantified the increase in signal amplitude for many electrodes in the following way. For each electrode on the MEA, the mean of the 25% highest spike amplitudes within the whole amplitude distribution was calculated for each one of the sampling periods. A linear approximation was then found between those means and the corresponding starting times of the sampling periods. The slope of this approximation was normalized to the mean of the first sampling period in order to obtain a growth rate parameter (%/min) to quantify the changes in amplitude with time.
We have calculated the spike amplitude growth rate for several MEAs, both with TiN and with CNT electrodes. Figure 5 illustrates the comparison in growth rate between a TiN MEA (Figure 5 A) and a CNT MEA (Figure 5 B). In nearly all cases, spikes recorded with CNT MEAs exhibited a clear positive amplitude growth rate over the sampling period. Spikes recorded with TiN MEAs, on the other hand, did not behave in a similar way. There was no conspicuous spike amplitude growth as a function of time with these electrodes. For the TiN MEA, values remain around 0, whereas for the CNT MEA, there is a clear growth in amplitudes, with growth rates of up to 2% per minute.
Figure 5. Comparison of spike amplitude growth rate between TiN and CNT electrodes. (A) A histogram of amplitude growth rate for all electrodes on a TiN MEA. The dotted grey line indicates 0 growth rate. (B) A histogram of amplitude growth rate for all electrodes on a CNT MEA. There is a clear positive growth rate for the CNT electrodes, but not for the TiN electrodes.
The superiority of CNT electrodes for stimulation applications have already demonstrated in an earlier study (Wang et al., 2006 ). We performed a preliminary investigation to validate the suitability of our CNT electrodes as an interface for retinal stimulation. Using an 8-channel STG stimulating system from MultiChannel Systems, we have stimulated individual electrodes (80 μm in diameter) on the MEA and recorded evoked spikes on neighboring electrodes (200 μm spacing). The stimulus applied were cathodic charge-balanced bi-phasic square current waveforms of various amplitudes and durations ranging from 50–700 μA and 60–100 μs per phase respectively. At 480 μA, a 60-μs pulse (corresponding to 28 nC) yielded responses in 16% of trials. Responses were generally observed on a single neighboring electrode. For 80 μs pulses (38 nC), responses were elicited in 75% of trials, and finally, responses were obtained in 100% trials for 100 μs pulses (48 nC). As these tests were performed with recording electrodes located away from the stimulated electrodes, these results only provide a proof of concept to the ability to effectively use CNT electrodes for stimulations. The values reported here are comparable to previously reported data (Ahuja et al., 2008 ).
Here we have demonstrated the use of CNT micro electrodes as an improved scheme to record from the retina. Overall, our findings provide very compelling evidence that CNT-based electrodes are the way forward to improve the biocompatibility and durability of retinal prosthetic devices. Indeed, our observations demonstrate that CNT-based electrodes offer excellent electrochemical and adhesive properties, which could potentially make this material the ideal choice for long-term in vivo implantation.
The most conspicuous attribute of the CNT electrode compared with their more conventional counterparts is the improved signal to noise ratio achieved during recordings and an apparent increase in the signal amplitude over several hours after recording had begun. Since there is no change in waveform shape over time, we attribute the increase in recorded signal to improved coupling between the tissue and the electrode. It is conceivable to associate the increase in the recorded signal with tissue growth (Leng et al., 2004 ; Winter et al., 2008 ). Otherwise improvement in the mechanical coupling between the tissue and the electrodes through mere sinking of the tissue onto the CNTs may explain the improved interfacing. In the latter case the three-dimensional nature of the CNT matrix may contribute to better recorded signal due to a better (larger) contact between the cells and their processes and the electrodes. Penetration of CNTs into neurons may also give rise to improved signal to noise. However, it is unlikely that tubes have actually penetrated through the membrane as we rarely saw changes in signal shape. CNT penetration may result in intracellular-like action potentials, a phenomenon we have never observed. Long-term studies and careful examination of the electrode-tissue interface will help to elucidate this issue.
The affinity of neuronal cells to adhere and entangle into the three-dimensional matrix of the CNTs has been studied by us extensively (Sorkin et al., 2009 ) with dissociated cells. This is a relatively rapid process in which dissociated cells can regenerate processes which readily intertwine with the CNTs. It remains to be investigated whether a related process takes place in the retina. We intend to study these effects with organotypic cultures of retinal explants. The three dimensional structure of the CNT electrodes and the manner by which neurites intertwine with the electrode surface is one of the most important features of these electrodes. Due to this intertwining, glial cells are less prone to block the interface between the electrode and the cells. We have directly demonstrated this effect with cultured cells (see Shein et al., 2009 ; Sorkin et al., 2009 ). As glia “scaring” is amongst the most challenging aspects in the design of high efficacy neural implant electrodes it is important to validate this effect with long-term, organotypic retinal cultures.
As CNT electrodes are gaining increased attention as novel neuronal interfaces, understanding the manner by which they interact or affect the activity of the overlying neurons is becoming important. One issue of increased attention is the nature of the electrical interface between the CNTs and the neurons. The data presented here is overall consistent with an improved capacitive coupling between the electrodes and the neurons. The vast majority of recorded signals have a similar shape, typically observed in extracellular recordings. On very rare occasions, atypical spikes were recorded (Fromherz et al., 1991 ). This effect will be further investigated and analyzed in the future.
An additional issue is whether CNTs affect the levels of neuronal firing. A recent investigation has demonstrated qualitative differences between the activity of neurons cultured on CNTs and on smooth surfaces (Lovat et al., 2005 ). Overall these conspicuous differences may be related to various parameters affecting cellular activity such as cell density, cell morphology, and mechanical tension to name just a few. Our data show no conspicuous increase in the firing rate of neurons on CNTs. As a matter of fact, in the examples shown in Figure 3 , neural activity was stronger on the TiN electrodes. Overall, we did not observe significant differences in neural activity levels in TiN versus CNT MEAs. As our investigation involved only short term recordings (several hours) it is possible that additional processes take place at later stages. These effects will be explored using organotypic retinal cultures. It is important to note that culturing whole retinal explants will provide a reliable mean to study the effect of CNTs on neurons within their natural microenvironment (rather than in dissociated cultures). Indeed, the retina is a highly organized system, with a well defined cellular arrangement in discrete layers, and therefore it will provide a powerful mean to explore brain-CNT interactions for future long-term neural implant applications.
Finally, as we have discussed in the introduction, the use of optimized MEAs for retinal stimulation is of great importance. An earlier study by Wang et al. (2006) has already validated the effectiveness of CNT electrodes for stimulation applications. The advantages offered by CNT electrodes are stemming from their improved electrochemical capacitance, and accordingly, their improved charge injection limit. We plan to further validate this issue using organotypic retinal cultures, towards the formation of a superior MEA-retina interface.
The TAU CNT-MEA project was partially supported by an ISF grant and a grant from the TAU Adams Super Center for Brain Studies. The NCL retinal project is funded by the Centre of Excellence for Life Sciences the EPSRC, BBSRC and Newcastle University Hospitals Special Trustees.
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