Vision restoration is an ideal medical application for optogenetics, because the eye provides direct optical access to the retina for stimulation. Optogenetic therapy could be used for diseases involving photoreceptor degeneration, such as retinitis pigmentosa or age-related macular degeneration. We describe here the selection, in non-human primates, of a specific optogenetic construct currently tested in a clinical trial. We used the microbial opsin ChrimsonR, and showed that the AAV2.7m8 vector had a higher transfection efficiency than AAV2 in retinal ganglion cells (RGCs) and that ChrimsonR fused to tdTomato (ChR-tdT) was expressed more efficiently than ChrimsonR. Light at 600 nm activated RGCs transfected with AAV2.7m8 ChR-tdT, from an irradiance of 1015 photons.cm−2.s−1. Vector doses of 5 × 1010 and 5 × 1011 vg/eye transfected up to 7000 RGCs/mm2 in the perifovea, with no significant immune reaction. We recorded RGC responses from a stimulus duration of 1 ms upwards. When using the recorded activity to decode stimulus information, we obtained an estimated visual acuity of 20/249, above the level of legal blindness (20/400). These results lay the groundwork for the ongoing clinical trial with the AAV2.7m8 - ChR-tdT vector for vision restoration in patients with retinitis pigmentosa.
Optogenetics has transformed neurobiology, by enabling scientists to control the activity of excitable cells with light1. Optogenetic therapy has also raised considerable hopes for new forms of brain–machine interfaces, with cell selectivity and distant optical control. Rebuilding vision through optogenetic approaches is conceptually straightforward, as the aim is to restore light sensitivity in the residual retinal tissue after photoreceptor degeneration, in diseases such as retinal dystrophies2 and age-related macular degeneration3. These diseases mostly affect photoreceptors, so the remaining retinal layers, including the retinal ganglion cells (RGC) can still communicate with the brain via the optic nerve. The feasibility of reactivating these retinal layers has already been demonstrated with retinal prostheses4,5 despite their major limitations in terms of surgery, spatial resolution, and cell specificity6.
The use of optogenetics to restore vision was first proposed by Zhao Pan and his colleagues7,8. They expressed the microbial opsin channelrhodopsin-2 (Chr2) in the RGCs of blind mice7, and subsequently in the retina of normal marmosets8. These studies led to a clinical trial using this microbial opsin, which began in February 2016, but for which no results have yet been published9. Other retinal cells (bipolar cells10,11,12 and dormant cone photoreceptors13,14) were subsequently targeted to restore vision in blind rodents, postmortem retinal tissue, and non-human primates. Clinically, the choice of cell type targeted depends on the stage of tissue remodeling after photoreceptor degeneration15,16,17. We performed translational studies targeting retinal ganglion cells (RGCs), the neurons projecting their axons out of the retina because this strategy could potentially work in all patients who have lost their photoreceptors, regardless of disease stage18.
RGCs in the non-human primate retina can be activated with a more sensitive form of Chr2, “CatCH”19. We tested this approach with an RGC-specific promoter20. However, the intensity of blue light required was close to radiation safety limits21. It was therefore of clinical importance to evaluate other opsins potentially conferring a better balance between light sensitivity and channel kinetics22.
In this study, we used the optimum AAV capsid with the most red-shifted opsin, operating at a wavelength 45 nm longer than ReaChR23. We demonstrate here that the high spatiotemporal resolution of this system is suitable for use in vision restoration. A single intravitreal injection, at a dose of 5 × 1010 or 5 × 1011 vg/eye transfects up to 7000 RGCs/mm2 in the perifovea. Responses were elicited at a stimulus duration of 1 ms and saturated at a stimulus duration of 30–50 ms. Furthermore, using the responses to moving bars and letters generated on a multielectrode array, we obtained an estimated theoretical visual acuity of 20/249, which is above the threshold for legal blindness. These characterizations of the visual response in the non-human primate retina paved the way for the ongoing clinical trial with the AAV2.7m8-ChrimsonR-tdT vector for vision restoration in patients with retinitis pigmentosa.
AAV2.7m8–ChR-tdT provides the highest transduction efficiency
Our primary objective was to determine the best genetic construct for expressing ChrimsonR in primate RGCs. The intravitreal delivery of AAV vector in non-human primates (NHPs) has been shown to lead to transduction of the ganglion cell layer in the perifoveal ring20,24. The mutated capsid AAV2.7m8 has been demonstrated to yield stronger transduction of the perifovea25. We, therefore, decided to compare the efficiency of ChrimsonR (ChR) expression from the AAV2.7m8 vector with that of the wild-type AAV2. ChR is often fused to the fluorescent protein tdTomato for visualization of its expression within cells. We therefore also investigated whether the native ChR protein and the ChrimsonR-tdTomato (ChR-tdT) fusion protein were produced in similar amounts in primate RGCs. The four selected constructs (AAV2 and AAV2.7m8 vectors encoding either ChR or ChR-tdT) were each injected into four eyes, at the same concentration (5 × 1011 vg/eye); eight animals in total were used for this experiment (Supplementary Table S1). While no in-depth behavior analysis was performed, none of the treated animals displayed signs of photophobia or vision-related changes in behavior under normal lighting in the animal house. The level of microbial opsin expression was assessed in functional analyses two months after the intravitreal injection in vivo. The transduced retinas were isolated ex vivo and divided into hemifovea for extracellular large-scale 256-multielectrode array (256-MEA) recordings for one hemifovea and two-photon targeted patch-clamp recordings for the other hemifovea (Fig. 1). No natural light responses were recorded in our experimental conditions, but we nevertheless added synaptic blockers to the bath to suppress any residual natural light responses (see Supplementary Materials and Methods). For the quantitative measurement of functional efficacy, the results shown are the multiunit activity on all electrodes following full-field stimuli; the use of this approach may have amplified the differences between results (see below). 256-MEA recordings revealed large differences in the ability to generate functional ChR expression between vectors (Fig. 1a–d). Recording quality was defined as the number of electrodes for which spontaneous spiking activity could be measured (active electrodes: 152 ± 46 electrodes per retina explant, on average), whereas ChR efficacy was defined as the number of electrodes displaying an increase in activity during the presentation of light flashes (responsive electrodes, SN ratio >4). This quantification revealed the existence of a significant difference between the constructs, with the highest efficacy for AAV2.7m8–ChR-tdT (Fig. 1c, 64.4% of active sites responsive vs. 13.4%, 10.6 and 0% for AAV2.7m8–ChR-tdT, AAV2.7m8–ChR, AAV2–ChR-tdT, and AAV2–ChR, respectively, P < 0.001). For all constructs, the foveal area was identified and selected for recording. The corresponding retinal explant was positioned on the MEA before confirmation of the eventual presence of fluorescence. If no light response was measured, we repositioned the tissue on the array to increase the sampling area. Light sensitivity was measured with a range of light intensities, from 1.37 × 1014 to 6.78 × 1016 photons cm−2 s−1 on all responsive retinas (Fig. 1b, d). Responses were obtained with AAV2.7m8–ChR-tdT, in all four retinas tested with this construct (verses 2, 1, and 0 for AAV2.7m8–ChR, AAV2–ChR-tdT, and AAV2–ChR, respectively). This vector also yielded the highest light sensitivity, with responses recorded for 2.34 × 1015 photons cm−2 s−1, at a frequency higher than for the other constructs.
Consistent with its optogenetic origin, the spiking activity had a short latency, was activated for the whole duration of stimulation and its frequency was modulated by light irradiance. Furthermore, an increase in the number of responsive electrodes with increasing irradiance was clearly observed (Fig. 1b). We recorded the action spectrum of the responses (Fig. 1e), and the measured peak was consistent with the known spectral sensitivity of ChR, at about 575 nm23.
The results of 256-MEA experiments were confirmed in two-photon targeted patch-clamp recordings (Fig. 1f–h) on the other hemifovea from the same eye. At the highest irradiance, AAV2.7m8–ChR-tdT elicited robust responses, with a typical photocurrent shape, consisting of a fast transient followed by a steady-state current (Fig. 1g, 12 to 375 pA, mean: 88.7 ± 25.5 pA, n = 17). These currents increased steadily with increasing light intensity, from 5.8 × 1014 to 3.15 × 1017 photons cm−2 s−1 (Fig. 1h). With the AAV2.7m8–ChR-tdT combination, we recorded 18 responsive cells (5, 0, 7, 6 cells/retina), whereas only four responsive cells (0, 3, 1, 0 cells/retina) were obtained with the AAV2–ChR-tdT construct. In the absence of tdT fluorescence, for AAV2.7m8–ChR and AAV2–ChR, extracellular recordings were performed on random healthy RGCs in the perifoveal area (>40 cells per condition). In these conditions, none of the RGCs for which recordings were made displayed light-evoked responses, even under conditions known to activate ChR. We cannot exclude a potential bias in favor of the construct including tdTomato, particularly in the patch-clamp experiments, but the positioning of the MEA based on foveal identification probably rule out such a bias in MEA recordings. These MEA recordings were consistent with greater efficacy of the AAV2.7m8–ChR-tdT constructs; this construct was therefore used in all subsequent experiments.
AAV2.7m8–ChR-tdT provides greater light sensitivity at a dose of 5 × 1011 vg/eye
Once the capsid and genetic payload had been selected, we assessed transgene stability over time (6 months). In the same set of experiments, we optimized virus load, using three different amounts of vector for intravitreal delivery: 5 × 109, 5 × 1010, and 5 × 1011 vector genomes per eye (vg/eye), for a total of six animals (four eyes per dose). Additional results were obtained with four more retinas treated with the high dose. After the injections, we examined the eyes of the animals monthly for posterior uveitis and vitreal haze. Clinical evaluation showed no significant immune response following ChR-tdT expression (Supplementary Fig. S1). The success of our vision restoration strategy depends on: (1) a large, dense area of transfected cells and 2) high light sensitivity per cell. For correct estimation of the number of cells transfected and of the retinal coverage of expression, we performed manual cell counts on RGC layers in the confocal stack of images for hemifoveas. We used these counts to establish density maps (Fig. 2a) and density profiles (Fig. 2b). The number of ChR-tdT-expressing cells increased with increasing vector dose (mean total number of transfected cells: 491 ± 64, 4395 ± 631, and 5935 ± 715, for ChR-tdT at 5 × 109, 5 × 1010, and 5 × 1011 vg/eye, respectively, see “Methods”). The local densities achieved with the two highest concentrations were not significantly different (Fig. 2a), but eyes receiving 5 × 1011 vg expressed ChR-tdT with a moderately higher eccentricity (Fig. 2b), resulting in expression over a potentially larger area for this dose. Based on the automatic counting of DAPI-stained nuclei in the same samples, we estimated the peak density at ~40,000 RGCs/mm2, with an eccentricity of 0.4 mm (Supplementary Fig. S2), consistent with previous RGC density maps26. Based on this number, we estimated that ~20% of RGCs expressed ChR-tdT. Before fixation these hemifoveas were used for MEA recordings, to assess light sensitivity following long-term expression (Fig. 2c). In terms of the fraction of responsive electrodes, there was no clear difference between 5 × 1010 and 5 × 1011 vg/eye, but the number of retinas with responsive electrodes was smaller for the lower dose (only one of four retinas with responsive electrodes, Fig. 2d). More importantly, the different viral doses led to different levels of light sensitivity, with 5 × 1011 vg/eye yielding the strongest overall responses and the lowest response threshold (Fig. 2e, see Supplementary Table S2 for Tukey’s multiple-comparison test). We cannot exclude the possibility of a decrease in the number of ChR-tdT-expressing cells between 2 and 6 months, as we were unable to obtain cell counts for both time points. However, we observed no major differences in the expression profile on the fovea and no changes in the subcellular pattern of expression (Supplementary Fig. S3). Furthermore, we observed no difference in the fraction of responsive electrodes (Fig. 2d, 102 ± 58 vs. 73 ± 65 for 2 months and 6 months, respectively, for 5 × 1011 vg/eye), or light sensitivity (Figs. 1d and 2e). Based on these findings and the absence of a significant immune response to viral load or ectopic gene expression (Supplementary Fig. S1), we selected 5 × 1011 vg/eye as the most appropriate dose for our therapy. Thus, all the data presented hereafter are for a dose of 5 × 1011 vg/eye after 6 months of expression.
Activity modulation at the millisecond scale
Natural vision is dependent on a highly dynamic temporal range of information for the perception of moving objects. In virtual reality goggles, the minimum information transfer mode seems to be dependent on the video rate (30 Hz27). Vision restoration for locomotion or for the perception of dynamic scenes should therefore restore light sensitivity to at least this temporal scale. We, therefore, measured the temporal dynamics of our optogenetic responses with full-field monochromatic stimuli (2 × 1017 photons cm−2 s−1 at 600 nm ± 10 nm) of increasing duration (1–2000 ms). This light intensity was selected because it generated the highest firing rates while remaining below radiation safety limits for continuous eye exposure (~6 × 1017 photons cm−2 s−128,29). Significant light responses were detected for stimulus durations as short as a few milliseconds (Fig. 3a). Interestingly the firing rate of RGCs reached a plateau for durations of 30–100 ms, depending on the retina tested (Fig. 3b). We defined the minimal stimulus duration generating a reliable response, by calculating the time to the first spike after the onset of stimulation, for all responsive electrodes (Fig. 3c). For stimuli lasting 5 ms or more, we observed a median time to a first spike of about 9 ms. Stimulation for 5 ms is, therefore, sufficient for the reliable activation of RGCs reliably, and the intracellular integration of the ChR-tdT photocurrent initiated spiking in less than 10 ms for most of the responsive electrodes. Furthermore, for a stimulation duration of 20 ms, the time to first spike was between 3 and 11 ms for 50% of the responsive electrodes. We then looked at the distribution of firing rates following stimulations of increasing duration (Fig. 3d). Even for 1 ms stimuli (Fig. 3c, d, dark-blue curves), 12% of electrodes measured a peak firing rate exceeding 100 Hz. We considered multiunit recording, but this observation indicates that, for some RGCs, a 1 ms stimulus was sufficient to elicit a strong response, as clearly seen in Fig. 3a. For stimuli lasting 5 and 20 ms, 48% and 69%, respectively, of the responsive electrodes had firing rates above 100 Hz. Finally, for the longest stimulus duration tested (2 s), peak responses and the sustained firing rate decreased during consecutive stimulations (Fig. 3a, b, d), but both these parameters subsequently recovered. We investigated this effect further for long stimulation durations, by calculating the Fano factor, a measurement of the variability of spike number relative to the mean number of spikes, for all electrodes, as a function of stimulation duration. The Fano factor was below 1 for the short duration (1–200 ms), indicating a lower variability than for the Poisson distribution, but we observed a large increase in spike train variability for stimulations lasting 2 s (Fig. 3e). Most of this effect can be attributed to stimulus hysteresis, as retinal sensitivity subsequently recovered. Consistent with this observation, recordings of activity in response to achromatic binary white noise with a 50% pseudorandom selection rate revealed a gradual decline of evoked activity. The underlying mechanism of this modulation may involve an inactivated state of the microbial opsin30 or the inactivation of the voltage-gated channels in the ganglion cells. A simple monochrome transformation of natural images would result in a large number of pixels with high values (i.e., light gray) potentially leading to rapid deactivation of retinal ganglion cells. The goggles used for visual stimulation include an event-based asynchronous camera outlining object contours31. It should therefore be possible to overcome the problem of retinal ganglion cell deactivation by reducing the number of active pixels in a projected frame through the limitation of active pixels to object contours. Flickering stimuli should be used, to reduce the total amount of light and the risk of an increase in spike train variability. For a light pulse width between 5 and 20 ms, stimulation frequencies between 100 and 25 Hz could be used.
ChR-tdT can produce a high temporal photocurrent and spiking modulations
In parallel with our population study on MEA, we investigated temporal dynamics, at the single-cell level, by recording photocurrent modulation in single cells. In all recorded hemifovea, fluorescent transfected cells could be seen in the characteristic half-torus shape (Fig. 4a, b). Using two-photon guided patch-clamp techniques, we obtained recordings for ChR-tdT-expressing RGCs in the perifoveal area with a cell-attached or voltage-clamp intracellular configuration (Fig. 4c). We first replicated the analysis of photocurrent modulation by light intensity, comparing responses at 6 months (Fig. 4c–e) and 2 months of expression (see Fig. 1f–h). The mean normalized photocurrent followed a similar photosensitivity curve at two and six months (Fig. 4d), with an activation threshold in the 1015 photons cm−2 s−1 intensity range, and robust responses to light stimuli at a wavelength of 600 nm (±10 nm) well below the illumination radiation safety limits for the human eye (~6 × 1017 photons cm−2 s−1)21,29,32. In comparisons of peak photocurrent or peak firing rate at maximal light intensity (3.15 × 1017 photons cm−2 s−1), we found no significant difference between the two durations of expression (Fig. 4e, 2 and 6 months), suggesting that ChR-tdT expression remained stable for as long as 6 months.
We then investigated response kinetics, by recording responses to light stimuli of increasing durations (Fig. 4f) in the cell-attached mode (spikes) and in the whole-cell configuration (photocurrent). The photocurrent and the spike rate both precisely followed stimulus components, such duration (Fig. 4f) and frequency (Fig. 4g, h) precisely. Interestingly, the decrease in photocurrent amplitudes, from the initial peak to the lower sustained amplitude, was paralleled by a similar decrease in firing rates. We further investigated the effect of flicker stimuli in a 50% duty cycle (half the stimulus period with the light ON, at 2–28 Hz) or at a specific stimulus duration (5 ms, from 10 to 100 Hz) (Fig. 4g–i). For full duty-cycle stimulation (Fig. 4g), the photocurrent closely followed the stimulus frequency, for flicker stimulations of up to 30 Hz. These results are consistent with the rapid opening and closing kinetics of the ChR channel in RGCs (10 to 90% rise time, 5.2 ± 1.7 ms; decay time, 27 ± 2.9 ms for a stimulus duration of 250 ms at 3.15 × 1017 photons cm−2 s−1, n = 5, Fig. 4c). The fast photocurrents allow neurons to translate each light pulse robustly into a burst of spikes, but the decay time of the photocurrent does not allow a complete return to the resting level during trains of the stimulus (e.g., 30 Hz flicker, Fig. 4g). We then used a lower duty cycle, consisting of trains of 5 ms stimuli (20 pulses at frequencies between 10 and 100 Hz), which has been shown to activate ChR-tdT-expressing RGCs in MEA experiments (Fig. 3). With such short stimuli, our recordings showed that photocurrent could be modulated at high frequencies, with large amplitudes (50–100 pA), generating periodic spiking activities. The cells for which recordings were obtained followed the stimulus train precisely, even at 100 Hz, but current deactivation was incomplete between light pulses (Fig. 4h, i). Recordings in cell-attachment mode confirmed the ability of neurons to follow stimulus frequencies of up to 66 Hz, despite incomplete current deactivation (Fig. 4i). This 60 Hz range is compatible with the flicker perception limits observed for natural vision in human subjects33,34 and could potentially be used for fast video rate stimulation in human patients. Finally, we activated cells with a stimulus simulating natural properties: a one-dimensional random walk, and consisting of a rapidly changing contrast stimulus (full-field stimulus with intensities ranging from 3 × 1014 to 3 × 1017 photons cm−2 s−1). Response reliability was strikingly high across trials (n = 4) for both current and firing rate activities (Fig. 4j). Together, these results demonstrate that RGCs expressing ChR-tdT can follow a high dynamic range of light stimulation compatible with human perception.
ChR-tdT can generate a high spatial precision for visual perception
Having shown that the RGC responses precisely follow the temporal resolution of optogenetic stimuli we then tested the spatial sensitivity of optogenetic responses, by stimulating the retina on the MEA using circular spots of various sizes (25 µm, 50 µm, and 100 µm) centered on the MEA electrodes (100-µm electrode pitch, 10 µm diameter) at a light intensity of 2.10 × 1017 photons cm−2 s−1 (600 nm ± 10 nm) (Fig. 5). The multiunit electrode-based analysis showed that even the electrodes far away (up to 1 mm) from the stimulated spot elicited an increase in spiking frequency (Fig. 5a). For identification of the electrode closest to the recorded cell, we performed spike sorting on the electrode signals, to obtain single-cell activity with an unsupervised sorting algorithm (Supplementary Fig. S4). This spike sorting indicated that individual spikes were recorded on several electrodes, as a consequence of spike propagation in the RGC axons running along the surface of the retina toward the optic disk (Fig. 5A and Supplementary Fig. S5). The increase in latency with distance to the stimulated area was consistent with an anterograde propagation of spikes along axons. We made use of this spike propagation to measure the spike velocity in ChR-tdT-expressing cells (Supplementary Fig. S5). The unimodal distribution peaking at 0.5 m/s (Supplementary Fig. S5H) suggests that the ChR-tdT-expressing population of RGCs contains a majority of midget RGCs35. This conclusion concerning cell identity is consistent with the midget cell morphology of tdTomato-expressing cells observed on two-photon microscopy (Supplementary Fig. S5A–E). However, a very small number of cells (n = 9) had faster velocities of axonal spike propagation (>1 m/s), indicating the possible presence of parasol RGCs among the ChR-tdT-expressing RGCs.
As tdTomato fluorescence was detected in RGC axons, we investigated whether light stimulation could elicit spikes directly in ChR-tdT-expressing axons, with anterograde and/or retrograde propagation. When a spot of light was centered on an electrode in contact with ChR-tdT-positive axons but not ChR-tdT-expressing soma, we observed no increase in spike activity in any neighboring or distant electrodes (Fig. 5b). Thus, the optical stimulation of ChR-tdT expressed in axons was not sufficient to trigger spikes. Indeed, a high degree of correspondence was found between the area containing cell bodies expressing TdTomato and the location of electrodes with optogenetic responsive cells (Fig. 5c). When spot size and presentation duration were varied, we observed single-cell activation for spots as small as 50 µm (Fig. 5d–f and Supplementary Movie S1). The number of responsive cells and their spiking frequencies depended on spot size and stimulus duration (Fig. 5g, h and Supplementary Fig. S6). It should be noted that our stimulations were centered on the opaque MEA electrodes (10 µm diameter), potentially greatly decreasing light intensity for the smallest spot (25 µm in diameter). Nevertheless, these observations are consistent with the notion that optogenetic stimulation can provide a high spatial resolution in RGC activation.
The optogenetic stimulation of ChR-tdT-expressing RGCs can support pattern discrimination
We assessed the functional impact of our visual restoration strategy by evaluating the ability of treated retinas to encode information about the direction and speed of motion and to discriminate patterns. We first presented moving bars (75 µm wide), at various velocities (2.2 mm/s or 4.4 mm/s), and with different orientations and directions across the treated retina (Supplementary Movie S2). Based on the known retinal magnification factor, 1 arc-degree of visual size corresponds to 211 µm on the retina36. Our bar stimuli, therefore, corresponded to a visual field angle of 0.375° moving at 11 or 22 °/s. For calculation of the visual flow elicited, we used spike sorting on the recorded activity, followed by plane fitting to the peak of the cell responses, to estimate the direction of the bar (Fig. 6a and Supplementary Fig. S7) and its speed (Fig. 6d). The plane fitting method made it possible to identify, for each direction, the unique succession of cells activated along the path of the bar (Fig. 6a–c). This temporal response of the cells was found to be sufficient for correct estimation of the direction and velocity of the bar over the retina, despite the discrete spacing of electrodes.
The most widely used clinical test for measuring visual acuity, the Snellen chart, assesses patient performance in reading letters and can be used to evaluate vision restoration strategies37. We estimated the visual acuity our strategy could be expected to restore, by stimulating retinas with different optotypes (X shape, circle, and square) of various sizes, from 55 to 330 µm (symbol width). All the characters presented were moved over the retina explants through the fovea center (8 different directions, 50 trials each, randomized presentations; Supplementary Movie S3), and the recorded spikes were sorted to analyze single-cell responses. Figure 7a represents the different patterns of cell activation for the moving shapes (top row: X, middle row: circle and bottom row: square) at a different time in their trajectories (from 12 ms to 114 ms, from the left to the right column). While the same cells can be recruited by different optotypes, the temporal pattern of cell activation depends on the shape presented (Fig. 7b). To confirm this, we used an algorithm38 (see “Methods” for details) to discriminate directly between symbols of similar size from the spike responses generated by the ChR-tdT-expressing cells. We obtained for a symbol size of 220 µm a discrimination rate of 83% (Fig. 7c, the edge of the symbol: 44 µm), and a consistent maximal value for mutual information (Fig. 7d).
Due to the imperfections inherent to spike sorting and electrode array sampling, only a fraction of the transfected cells were detected (~80 cells after spike sorting vs. >1000 ChR-tdT-expressing cells per retina (Fig. 2)). Our estimates of the information transmission capabilities of this strategy are, thus, almost certainly considerably underestimated. Interestingly, for smaller stimuli, we measured a steady increase in discrimination accuracy and information (Fig. 7c, d). With access to the complete information transmitted by RGCs, we would probably have achieved a higher rate of discrimination for smaller symbols.
Despite this limitation, our findings demonstrate the ability of our strategy to encode information about the speed and direction of stimuli, even for small fast-moving stimuli, and its ability to support a discrimination task.
We show here that the AAV2.7m8–ChR-tdT construct is more efficient than the wild-type capsid AAV2 and the non-fused ChrimsonR protein in primate retinal ganglion cells. Furthermore, the therapeutic vector dose was defined as 5 × 1011 vg/eye, which allows greater light sensitivity, with expression in more cells and over a wider area. We explored key parameters of optogenetic activation (i.e., light intensity, temporal, and spatial modulation) and demonstrated an ability to decode the direction and speed of a moving bar and the identity of different stimulus shapes from the recorded cell activity. These data supported the application to launch the ongoing clinical trial in patients with retinitis pigmentosa39.
Vector optimization for a high level of functional efficacy
For the successful achievement of our therapeutic goals, the viral optogenetic construct must have a large functional impact on a large proportion of the cells in the RGC population. Our results confirm the higher transduction efficiency of the AAV2.7m8 variant in the retina25 relative to AAV28,20. Surprisingly, we also found that efficacy was greater for the ChR-tdT fusion protein than for ChR alone. We cannot entirely rule out an experimental bias, as ChR expression cannot be localized by fluorescence imaging as for ChR-tdT. However, the expected location of the transduced gene at the fovea20,25 greatly decreases the chances of missing expression clusters during tissue isolation and positioning on the MEA. Differential protein trafficking, with td Tomato working as a trafficking helper and possibly also preventing protein aggregation, appears more likely40. The result would be a higher level of opsin construct targeting to the membrane41. We demonstrated a greater efficacy for both the mutated AAV capsid, AAV2.7m8, and for the ChR-tdT fusion protein, in non-human primates. Given the high degree of structural similarity between the eyes of NHPs and humans, we would expect intravitreal AAV2.7m8–ChR-tdT injection to transduce the retina effectively in blind patients too.
Once the construct has been selected, the next critical issue is AAV safety. Previous studies of gene therapy within the eye used AAV doses of 1.5 × 1011 vg in the subretinal space42 and of up to 1 × 1011 vg/eye43 or 1.8 × 1011 vg/eye44 for intravitreal injections. No adverse effects were reported at these doses, but other delivery methods use much higher doses (up to 1014 vg) with potentially disruptive effects45. In this study, none of the eyes treated displayed an inflammatory response (Supplementary Fig. S1), with only a few cells in the vitreous and one eye displaying vitreal haze (associated with light hemorrhaging during the IVT procedure). Doses of 5 × 1010 and 5 × 1011 vg/eye induced ChR-tdT expression and strong functional responses highly efficiently in NHPs. The highest dose used here (5 × 1011 vg/eye) appears to provide more extensive retinal coverage and higher light sensitivity (Fig. 2). This greater coverage would enlarge the patient’s visual field, translating to ~6° in the visual field (211 µm on the primate retina per degree angle36). A visual field of this size may appear rather limited, but it should be borne in mind that the fovea is the center of high visual acuity. This high visual acuity results from the high density of cone photoreceptors, and the marked predominance of midget RGCs, which receive inputs from a single photoreceptor and have a very small receptive field46,47,48,49. We showed, by spike propagation speed analysis (Supplementary Fig. S5) and morphology examinations, that most of the ChR-tdT-expressing RGCs were, indeed, midget RGCs, likely to mediate visual perception with a high level of acuity. Specific activation of this midget RGC population in the foveal area could potentially provide patients with high-acuity vision.
Effective and safe stimulation intensity
We show here that the stimulation of ChR-tdT, as for most microbial opsins, is effective from 1015 photons cm−2 s−1. Given that only a quarter of visible light effectively stimulates any given light-sensitive channel, it would be hard to find situations in everyday life in which stimulation would occur. Outside on a bright day, the effective light intensity on the retina would be around 1014 photons cm−2 s−1, and this would fall to 2 × 1012 photons cm−2 s−1 in an office. We would not, therefore, expect transfection with opsin to yield useful levels of perception in isolation. Our strategy will need to include an external photostimulation device for converting images into tailored patterned photostimulation of the optogenetically engineered retina.
This study focused on the red-shifted opsin ChrimsonR, which has a reported peak sensitivity at 575 nm23, a result confirmed here by MEA recordings (Fig. 1e). This is a much safer wavelength than highly phototoxic blue-light wavelengths, making it possible to expose the retina to higher light intensities safely29. For the clinical trial, we opted for a middle ground between optimal opsin sensitivity and the lower phototoxicity of higher wavelengths. We decided to use a 595 nm LED (Cree XP-E2, Lumitronix) as the light source for external photostimulation. For this reason, we mostly used light at a wavelength of 600 nm (±10 nm) in this study, and this is the wavelength considered for the safety evaluation.
The International Commission on Non-Ionizing Radiation Protection published limits for ocular exposure to visible and infrared radiation in 201328. These limits were translated into retina irradiance by Sengupta et al., using published conversion rates50,51. The resulting threshold for continuous exposure was 5.6 × 1017 photons cm−2 s−1 at 590 nm and 5 × 1015 photons cm−2 s−1 at 500 nm. In 2016, Yan et al. published a review of the 2014 ANSI Z136.1 exposure limits for laser illumination of the retina with ophthalmic instruments (§8.3) and the potential use of these limits in optogenetic systems21,32. For a full-field continuous stimulus applied for 8 h during a 48-h period, the maximal permissive retinal peak irradiance is 1.1 × 1017 photons cm−2 s−1 at 600 nm and 8 × 1015 photons cm−2 s−1 at 505 nm.
Both sets of proposed exposure limits are higher for the 600-nm wavelength used here than for the blue light used for opsins such as Chr2. Importantly, we demonstrate here that light intensities below the 600 nm radiation safety limit can activate the transfected retina very efficiently.
Exposure limits are, by nature, conservative. They are set for continuous illumination, as the photochemical hazard, which depends on the total illumination received per 48 h, is the highest risk. However, our strategy will involve stimulation with light patterns extracted from an event camera, reducing moving faces and objects to their outlines31,52. The scarcity of stimulation will increase the maximal retinal peak irradiance permitted21.
The risk of photochemical injury in the retina of patients with advanced RP lacking functional photoreceptors remains unclear, but the build-up of potentially toxic retinoids in the RPE would, presumably, be minimal.
For further guarantees of patient safety during the clinical trial, it will be important to limit the initial duration of exposure and to monitor the state of the retina after each stimulation period very closely.
Comparison with other studies and constructs
A previous clinical trial of optogenetic therapy for visual restoration focused on the blue-sensitive microbial opsin, Chr29. This first clinical study built on preclinical studies in mice7 and marmosets8. In the marmoset study, a single MEA electrode recorded spike trains reaching >300 Hz at 6.6 × 1016 photons cm−2 s−1. More recently, using the human codon-optimized Ca2+-permeable Chr2, (CatCh), which is 70 times more efficient than Chr2, we recorded multiunit spiking frequencies in a similar range in macaque foveal RGCs (~300 Hz at 8 × 1015 photons cm−2 s−1 20). These studies focused on opsins sensitive to blue-light wavelengths and they reported results at intensities above safety limits. In this study, we observed multiunit spiking frequencies above 700 Hz (Fig. 3a) at 2 × 1017 photons cm−2 s−1 and a peak firing rate above 300 Hz for light intensities well below the safety limits (9 × 1015 photons cm−2 s−1, Fig. 2c).
ChrimsonR is currently the most red-shifted opsin available, with peak sensitivities shifted by ~100 nm for Chr2 and 45 nm for ReaChR23, but future work may even result in the development of infrared-sensitive opsins, as in snakes53,54. Alternatively, mutagenesis could be used to enhance the properties of existing opsins: ChrimsonR was generated by the site-directed mutagenesis of Chrimson23, and was further modified to drive neuron firing rates to higher spiking frequencies22. This kinetic enhancement was achieved at the expense of light sensitivity, and this new variant is not, therefore, relevant for vision restoration, as it would reduce the safe range for stimulation. Based on previous studies aiming to develop an optogenetic vision restoration strategy, we show here a highest level of evoked activity at a wavelength of 600 nm, with a temporal resolution of milliseconds, at intensities below the safety threshold.
Pattern discrimination for the restoration of vision
The restoration of vision with retinal prostheses is classically assessed by stimulating individual electrodes55,56, defining object positions and shape5,56,57,58, identifying bar orientation5,55,57, and reading letters or words. An issue encountered with epiretinal prostheses is that single-electrode stimulations activate RGCs axons on their way to the optic nerve, leading to patients perceiving an arc, rather than a point59. In our optogenetic approach, RGCs axons expressed ChR-tdT, as indicated by tdT fluorescence, but the light stimulation applied did not trigger spikes (Fig. 5b, c). This specificity of activation is a requirement for spatially restricted stimulation. We show here through spot stimulations that responses can be elicited with a spot diameter of 50 µm, even for a duration of 10 ms (Fig. 5 and Supplementary Fig. S6). These findings are encouraging, but probably represent an underestimate of actual spatial resolution, for two reasons. First, the circular spot used in these experiments was centered on the 10 µm opaque electrodes, reducing photon flux, especially for smaller stimuli (i.e., 25 μm, Fig. 5). Second, due to the limitations on sampling during MEA recordings, it is unlikely that we recorded the activity of all responsive cells. It is, therefore, difficult to compare our results with those for subretinal implants, because most of these prosthetic devices activate RGCs indirectly through bipolar cells. However, electrodes have a 70–100-µm pitch that can be activated only in a stepwise manner, as all or most of the implanted electrodes must be stimulated for an activation current to be generated5,60,61. Whereas optogenetic therapy can activate RGCs with smaller spot size, and increasing the size of the stimulation spot increases the number of cells recruited in an almost linear manner (Fig. 5h).
Visual acuity is considered normal for a value of 20/20, corresponding to the ability to identify an object of 5 arc-minutes, with a critical gap of 1 arc-minute that needs to be resolved. The best reported visual acuity achieved with current retinal prostheses was 20/546, when assessed with Landolt C- rings5. In our optogenetic strategy, using an approach similar to the Snellen chart, we obtained correct shape discrimination (Fig. 7: 83% discrimination for symbols of 220 µm with 44-µm edges). For adult Macaca fascicularis monkeys, 1 arc-degree in the visual field corresponds to a size of 211 µm on the retina36; to obtain 20/20 acuity, a gap of 3.6 µm must be resolved,. In our case, the size of the gap correctly discriminated (edge of the symbol: 44 µm) represents a visual acuity of 20/249, which is above the legal threshold for blindness (20/40062,63). This value is consistent with the predictions of simulations64 and better than any acuity reported to date with visual prosthetics (20/5465). The impossibility of recording all cells from the ChR-tdT-expressing population would clearly have underestimated visual acuity, which could probably be enhanced even further. One important perifoveal feature not taken into account here is the lateral displacement of the RGC cell body with respect to its receptive field. Indeed, to ensure minimal optical aberration for the light hitting the photoreceptor in the most central part of the fovea, other retinal layers are displaced centrifugally around the fovea pit. Due to this displacement, the direct stimulation of RGCs should occur through a corrected image of the visual field. Finally, degenerated retinas have a much lower signal-to-noise ratio than our pharmacologically isolated RCGs, due to abnormal circuit reorganization. Furthermore, RGCs in the degenerating retina have abnormally high spontaneous firing rates, which may have a large effect on their response to optogenetic stimulation, decreasing visual acuity in patients. However, a recent study has suggested treating this consequence of tissue reorganization with retinoic acid blockers65.
We showed, by making use of the reliability of spike train generation, that pulse width modulation might be preferable to continuous illumination (Fig. 4). Evaluations in patients will define the best duration of stimulation, but we can infer, from our data, that RCGs are reliably activated in the 5–20 ms range (Figs. 3 and 4). We hypothesize that this ability to evoke high-frequency modulation would help (1) to reduce the total amount of light entering the eye, and (2) to maintain precise control over cell activity, potentially improving the outcome of this strategy.
We describe here the initial selection process for genetic content, vector serotype, and vector dose in an ambitious “two-prong” vision restoration strategy involving a biological component and an external light stimulation device. While we could not assess thoroughly the behavioral impact of our strategy on sighted or blind macaques, the results for the biological component presented here provide all the essential information required for the design of the external light stimulation device necessary for the conversion of visual scenes into a stimulation pattern. Both the biological component and external light stimulation device are now in use, together, in the recently launched phase I/II clinical trial of AAV2.7m8–ChR-tdT39.
Experiments were performed on 18 male and female crab-eating macaques (Macaca fascicularis). The exact number of animals included in the different experiments is listed in Supplementary Table S1. All experiments were performed in accordance with the National Institutes of Health Guide for the Care and Use of Laboratory Animals. The protocol was approved by the local animal ethics committees (#044) and conducted in accordance with Directive 2010/63/EU of the European Parliament. Animals are housed in a room lit with fluorescent tubes which are filtered through diffuser panels above each housing unit to deliver a cool white light (4000 K), during a 12-h photoperiod. The maximum amount of light that could be measured, corresponding to an animal looking directly at the light in the upper part of its enclosure, is 585 µW/cm2. This maximal possible exposure does not reach the light intensity threshold for activating ChrimsonR, measured here at 2.34 × 1015 photons cm−2 s−1 (784 µW/cm2, Figs. 1d and 2e). Furthermore, the light to which the animals are exposed in these housing conditions is a broad white light with a large spectrum that would be unable to activate ChrimsonR in an optimal manner, unlike the pure 595 nm orange light used in the study. We, therefore, expected to see no behavioral changes due to ChrimsonR activation in these normal housing conditions. We nevertheless continually monitored the behavior of the animals, by checking that their feeding habits were normal and evaluating general stress and behavior during enrichment periods. None of the treated animals showed any sign of stress due to photosensitivity. No noticeable changes in behavior (during feeding and enrichment) were observed after the surgery.
Statistics and reproducibility
All data shown in the figures are expressed as the mean ± standard deviation. P values below 0.05 were considered significant. In tests of different genetic constructs, the fraction of active and responsive electrodes were compared between groups in Chi-squared contingency tests, followed by Fisher’s exact test (Fig. 1c). For calculations of RGC density as a function of eccentricity (Fig. 2b), we used Tukey’s multiple-comparison tests and compared 5 × 1009 (n = 3) to 5 × 1010 vg/eye (n = 4): P = 7.6e-3 at 175 µm, P = 1e-4 for 225 µm; P < 1e-4 from 275 to 375 µm, P = 2e-4 at 425 µm, and P = 0.02 at 475 µm. Comparing 5 × 1011 (n = 6) to 5 × 1010 vg/eye (n = 4), we obtained: P = 2.6e-2 at 475 µm and P = 4.5e-2 at 525 µm. For the percentage of electrodes responding at the different virus concentrations and the two expression times (Fig. 2d), we performed, for each pair of conditions, a nonparametric Mann–Whitney test and showed no significant differences (n = 4 for all condition except for 5 × 1011 vg/eye at 6 months, where n = 8). The additional amount of firing for stimulations at different light levels, for retinas treated with three doses of vectors (Fig. 2e), was compared in Tukey’s multiple-comparison test (see Supplementary Table S2), n = 1, 3, and 8 for 5 × 109, 5 × 1010 and 5 × 1011 vg/eye at 6 months, respectively. We compared photocurrent size in patch-clamp conditions and firing rate in cell-attached conditions for the two expression times (Fig. 4e), in nonparametric Mann–Whitney tests (n.s., P = 0.155 and P = 0.669, respectively). For spot stimulation (Fig. 5) we performed pairwise t tests on spike rate data for the recorded retinas in different stimulation conditions. For stimulus of increasing size compared with the same duration: 25–50 µm, P = 7.67e-7, P = 5.41e-8, and P = 5.41e-7 for 10, 20, and 40 ms stimulation, respectively. In all, 50–75 µm, P = 6.19e-8, P = 1.24e-6, and P = 6.40e-6 for 10, 20, and 40 ms stimulation, respectively. In all, 75–100 µm, P = 6.51e-8, P = 7.61e-6, and P = 1.6e-3 for 10, 20, and 40 ms stimulation, respectively. Furthermore, we measured, when comparing the same stimulus size at a different time: 10–20 ms, P = 7.942e-7, P = 0.0043, and P = 2.515e-6, for stimulus size of 50, 75, and 100 µm, respectively. In all, 20–40 ms, P = 0.0012, P = 0.0087 for stimulus size of 50 and 75 µm, respectively. For Figs. 6 and 7, see Supplementary Methods for details.
Further information on research design is available in the Nature Research Reporting Summary linked to this article.
The data that support the main findings of this study are openly available in figShare (https://figshare.com/projects/AAV2_7m8-ChrimsonR-tdTomato_for_vision_restoration/83675).
The codes supporting our findings are available on the repository Github (https://github.com/himstien/Optogenetic_Retinal_Data_Analysis).
Repina, N. A., Rosenbloom, A., Mukherjee, A., Schaffer, D. V. & Kane, R. S. At light speed: advances in optogenetic systems for regulating cell signaling and behavior. Annu Rev. Chem. Biomol. Eng. 8, 13–39 (2017).
Nash, B. M., Wright, D. C., Grigg, J. R., Bennetts, B. & Jamieson, R. V. Retinal dystrophies, genomic applications in diagnosis and prospects for therapy. Transl. Pediatr. 4, 139–163 (2015).
Hernandez, O. et al. Three-dimensional spatiotemporal focusing of holographic patterns. Nat. Commun. 7, 11928 (2016).
da Cruz, L. et al. Five-year safety and performance results from the Argus II Retinal Prosthesis System clinical trial. Ophthalmology 123, 2248–2254 (2016).
Stingl, K. et al. Interim results of a multicenter trial with the new electronic subretinal implant alpha AMS in 15 patients blind from inherited retinal degenerations. Front. Neurosci. 11, 445 (2017).
Paraskevoudi, N. & Pezaris, J. S. Eye movement compensation and spatial updating in visual prosthetics: mechanisms, limitations and future directions. Front. Syst. Neurosci. 12, 73 (2019).
Bi, A. et al. Ectopic expression of a microbial-type rhodopsin restores visual responses in mice with photoreceptor degeneration. Neuron 50, 23–33 (2006).
Ivanova, E., Hwang, G.-S., Pan, Z.-H. & Troilo, D. Evaluation of AAV-mediated expression of Chop2-GFP in the marmoset retina. Investig. Ophthalmol. Vis. Sci. 51, 5288–5296 (2010).
RST-001 Phase I/II Trial for Advanced Retinitis Pigmentosa - Full Text View - ClinicalTrials.gov. https://clinicaltrials.gov/ct2/show/NCT02556736 (2015).
Lagali, P. S. et al. Light-activated channels targeted to ON bipolar cells restore visual function in retinal degeneration. Nat. Neurosci. 11, 667–675 (2008).
Doroudchi, M. M. et al. Virally delivered channelrhodopsin-2 safely and effectively restores visual function in multiple mouse models of blindness. Mol. Ther. 19, 1220–1229 (2011).
Macé, E. et al. Targeting channelrhodopsin-2 to ON-bipolar cells with vitreally administered AAV restores ON and OFF visual responses in blind mice. Mol. Ther. 23, 7–16 (2015).
Khabou, H. et al. Noninvasive gene delivery to foveal cones for vision restoration. JCI Insight 3, 96029 (2018).
Busskamp, V. et al. Genetic reactivation of cone photoreceptors restores visual responses in retinitis pigmentosa. Science 329, 413–417 (2010).
Marc, R. E., Jones, B. W., Watt, C. B. & Strettoi, E. Neural remodeling in retinal degeneration. Prog. Retinal Eye Res. 22, 607–655 (2003).
Marc, R. E. et al. Neural reprogramming in retinal degenerations. Investig. Ophthalmol. Vis. Sci. 48, 3364–3371 (2007).
Jones, B. W. et al. Retinal remodeling and metabolic alterations in human AMD. Front. Cell Neurosci. 10, 103 (2016).
Jacobson, S. G. et al. Identifying photoreceptors in blind eyes caused by RPE65 mutations: prerequisite for human gene therapy success. Proc. Natl Acad. Sci. USA 102, 6177–6182 (2005).
Kleinlogel, S. et al. Ultra light-sensitive and fast neuronal activation with the Ca2+-permeable channelrhodopsin CatCh. Nat. Neurosci. 14, 513–518 (2011).
Chaffiol, A. et al. A new promoter allows optogenetic vision restoration with enhanced sensitivity in macaque retina. Mol. Ther. 25, 2546–2560 (2017).
Yan, B., Vakulenko, M., Min, S.-H., Hauswirth, W. W. & Nirenberg, S. Maintaining ocular safety with light exposure, focusing on devices for optogenetic stimulation. Vis. Res. 121, 57–71 (2016).
Mager, T. et al. High frequency neural spiking and auditory signaling by ultrafast red-shifted optogenetics. Nat. Commun. 9, 1–14 (2018).
Klapoetke, N. C. et al. Independent optical excitation of distinct neural populations. Nat. Methods 11, 338–346 (2014).
Yin, L. et al. Intravitreal injection of AAV2 transduces macaque inner retina. Invest. Ophthalmol. Vis. Sci. 52, 2775–2783 (2011).
Dalkara, D. et al. In vivo-directed evolution of a new adeno-associated virus for therapeutic outer retinal gene delivery from the vitreous. Sci. Transl. Med. 5, 189ra76 (2013).
Wässle, H., Grünert, U., Röhrenbeck, J. & Boycott, B. B. Retinal ganglion cell density and cortical magnification factor in the primate. Vis. Res. 30, 1897–1911 (1990).
Peli, E. Real vision & virtual reality. Opt. Photonics N., OPN 6, 28 (1995).
ICNIRP Guidelines on visible radiation (380–780 nm). http://www.icnirp.org/en/frequencies/visible/index.html (2013).
Sengupta, A. et al. Red‐shifted channelrhodopsin stimulation restores light responses in blind mice, macaque retina, and human retina. EMBO Mol. Med. 8, 1248–1264 (2016).
Sabatier, Q. et al. Modeling the electro-chemical properties of microbial opsin chrimsonr for application to optogenetics-based vision restoration. Preprint at https://www.biorxiv.org/content/10.1101/417899v1 (2018).
Galluppi, F. et al. A stimulation platform for optogenetic and bionic vision restoration. Proc. IEEE ISCS (2017).
Delori, F. C., Webb, R. H. & Sliney, D. H. Maximum permissible exposures for ocular safety (ANSI 2000), with emphasis on ophthalmic devices. J. Opt. Soc. Am. A 24, 1250–1265 (2007).
Hecht, S. & Verrijp, C. D. The influence of intensity, color and retinal location on the fusion frequency of intermittent illumination. Proc. Natl Acad. Sci. USA 19, 522–535 (1933).
Bernardi, L., Costa, V. P. & Shiroma, L. O. Flicker perimetry in healthy subjects: influence of age and gender, learning effect and short-term fluctuation. Arq. Bras. Oftalmol. 70, 91–99 (2007).
Li, P. H. et al. Anatomical identification of extracellularly recorded cells in large-scale multielectrode recordings. J. Neurosci. 35, 4663–4675 (2015).
Lapuerta, P. & Schein, S. J. A four-surface schematic eye of macaque monkey obtained by an optical method. Vis. Res. 35, 2245–2254 (1995).
Zrenner, E. et al. Subretinal electronic chips allow blind patients to read letters and combine them to words. Proc. Biol. Sci. 278, 1489–1497 (2011).
Lagorce, X., Ieng, S.-H., Clady, X., Pfeiffer, M. & Benosman, R. B. Spatiotemporal features for asynchronous event-based data. Front. Neurosci. 9, 46 (2015).
Dose-escalation Study to Evaluate the Safety and Tolerability of GS030 in Subjects With Retinitis Pigmentosa - Full Text View - ClinicalTrials.gov. https://clinicaltrials.gov/ct2/show/NCT03326336 (2017).
Shaner, N. Improved monomeric red, orange and yellow fluorescent proteins derived from Discosoma sp. red fluorescent protein. Nat. Biotechnol. http://www.ncbi.nlm.nih.gov/pubmed/15558047 (2004).
Garita-Hernandez, M. et al. Optogenetic light sensors in human retinal organoids. Front. Neurosci. 12, 789 (2018).
Bennett, J. et al. Safety and durability of effect of contralateral-eye administration of AAV2 gene therapy in patients with childhood-onset blindness caused by RPE65 mutatons: a follow-on phase 1 trial. Lancet 388, 661–672 (2016).
Cukras, C. et al. Retinal AAV8-RS1 gene therapy for X-linked retinoschisis: initial findings from a phase I/IIa trial by intravitreal delivery. Mol. Ther. 26, 2282–2294 (2018).
Vignal, C. et al. Safety of rAAV2/2-ND4 gene therapy for leber hereditary optic neuropathy. Ophthalmology 125, 945–947 (2018).
Hudry, E. & Vandenberghe, L. H. Therapeutic AAV gene transfer to the nervous system: a clinical reality. Neuron 101, 839–862 (2019).
Kolb, H. & Dekorver, L. Midget ganglion cells of the parafovea of the human retina: a study by electron microscopy and serial section reconstructions. J. Comp. Neurol. 303, 617–636 (1991).
Patterson, S. S., Neitz, M. & Neitz, J. Reconciling color vision models with midget ganglion cell receptive fields. Front. Neurosci. 13, 865 (2019).
Dacey, D. M. & Petersen, M. R. Dendritic field size and morphology of midget and parasol ganglion cells of the human retina. Proc. Natl Acad. Sci. USA 89, 9666–9670 (1992).
Dacey, D. et al. Center surround receptive field structure of cone bipolar cells in primate retina. Vis. Res. 40, 1801–1811 (2000).
Degenaar, P. et al. Optobionic vision–a new genetically enhanced light on retinal prosthesis. J. Neural Eng. 6, 035007 (2009).
Sliney, D. H., Fast, P. & Ricksand, A. Optical radiation hazards analysis of ultraviolet headlamps. Appl. Opt. 34, 4912–4922 (1995).
Posch, C., Matolin, D. & Wohlgenannt, R. A QVGA 143 dB dynamic range frame-free PWM image sensor with lossless pixel-level video compression and time-domain CDS. IEEE J. Solid-State Circuits 46, 259–275 (2011).
Gracheva, E. O. et al. Molecular basis of infrared detection by snakes. Nature 464, 1006–1011 (2010).
Nelidova, D. et al. Restoring light sensitivity using tunable near-infrared sensors. Science 368, 1108–1113 (2020).
Wilke, R. et al. Spatial resolution and perception of patterns mediated by a subretinal 16-electrode array in patients blinded by hereditary retinal dystrophies. Investig. Ophthalmol. Vis. Sci. 52, 5995–6003 (2011).
Humayun, M. S. et al. Visual perception in a blind subject with a chronic microelectronic retinal prosthesis. Vis. Res. 43, 2573–2581 (2003).
Humayun, M. S. et al. Interim results from the international trial of second sight’s visual prosthesis. Ophthalmology 119, 779–788 (2012).
Stingl, K. et al. Subretinal visual implant alpha IMS—clinical trial interim report. Vis. Res. 111, 149–160 (2015).
Nanduri, D. et al. Frequency and amplitude modulation have different effects on the percepts elicited by retinal stimulation. Investig. Ophthalmol. Vis. Sci. 53, 205–214 (2012).
Lorach, H. et al. Photovoltaic restoration of sight with high visual acuity. Nat. Med. 21, 476–482 (2015).
Prévot, P.-H. et al. Behavioural responses to a photovoltaic subretinal prosthesis implanted in non-human primates. Nat. Biomed. Eng. 4, 172–180 (2020).
Eye Health Data and Statistics | National Eye Institute. https://www.nei.nih.gov/learn-about-eye-health/resources-for-health-educators/eye-health-data-and-statistics (2019).
Ray, P. L. et al. Representing vision and blindness. J. Biomed. Semantics 7, 15 (2016).
Ferrari, U. et al. Towards optogenetic vision restoration with high resolution. PLoS Comput. Biol. 16, 7 (2020).
Telias, M. et al. Retinoic acid induces hyperactivity, and blocking its receptor unmasks light responses and augments vision in retinal degeneration. Neuron 102, 574–586.e5 (2019).
We thank Matthew Chalk for critical proofreading. We thank Guillaume Labernède and Antoine Rizkallah for the manual counts of RGCs. This work was supported by BPIfrance (grant reference 2014-PRSP-15), Gensight Biologics, Foundation Fighting Blindness, Fédération des Aveugles de France, and by French state funds managed by the Agence Nationale de la Recherche within the Investissements d’Avenir program, RHU LIGHT4DEAF (ANR-15-RHU-0001), LABEX LIFESENSES (ANR-10-LABX-65), IHU FOReSIGHT (ANR-18-IAHU-0001), and (ANR-11-IDEX-0004-02).
D.D., R.B., and S.P. are consultants for Gensight Biologics. J.A.S. and S.P. have financial interests in Gensight Biologics. D.P., A.D., D.D., D.J., R.C., G.G., M.D., J.A.S., and S.P. have filed a patent application relating to the results presented in this paper. The remaining authors declare no competing interests.
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Gauvain, G., Akolkar, H., Chaffiol, A. et al. Optogenetic therapy: high spatiotemporal resolution and pattern discrimination compatible with vision restoration in non-human primates. Commun Biol 4, 125 (2021). https://doi.org/10.1038/s42003-020-01594-w