1.

Introduction

In this volume of Neurophotonics, much will be said about the inspiration and success of the early quest by Cohen and coworkers more than 50 years ago,¹ for optical signals to report electrical activity from excitable membranes. It was through this seminal work that the idea of optical recording of membrane electrical activity of cells and across cellular networks was born, initiating the development of optical functional imaging methods in neurophysiology.^2–4 Given the universal role of the optical microscope to visualize cellular structure and diversity in every domain of biology, it is easy to imagine the appeal this work had on generations of students and researchers, attracting many to devote their research careers to the optical imaging of neural function. While the development of an all-optical approach to electrophysiology continues, it is evident that the genealogy of this field roots in the early work of Cohen and coworkers starting in the 1960s during the golden era of membrane biophysics.

Since the discovery by Cohen and coworkers of Merocyanine-540, the first synthetic dye membrane voltage indicator,⁵ enormous efforts have been undertaken to identify new chemical compounds suitable as fluorescence probes of membrane voltage with improved sensitivity, reduced toxicity, and diverse spectral properties,^6–12 enabling myriads of applications in general physiology and neurophysiology.^13,14 Following the invention of voltage-sensitive dye imaging, indicators for intracellular calcium concentration later emerged as a practical alternative to probe spiking events in neurons by exploiting the large rise of intracellular calcium concentration associated with action potential discharge.^15–18 Although optical calcium measurements generally achieve significantly better signal-to-noise ratio (SNR) for action potential detection at the cellular resolution in two-photon imaging in vivo, limitations exist: first, given the intrinsic slowness of the intracellular calcium dynamics as opposed to the much faster membrane voltage change, spike times cannot be inferred with a temporal precision compatible with classical electrophysiological recordings. For the same reason, a reliable distinction of single spikes can be impaired if spikes are followed with a short delay, as in high-frequency spike trains or spike bursts. Second, events that do not reach the firing threshold evoke no (e.g., hyperpolarizing synaptic potentials) or vanishingly small (subthreshold excitatory synaptic potentials) calcium transients.

In principle, voltage imaging is better suited to probe the entirety of cellular electrical signals that define the language of the nervous system, including excitatory and inhibitory synaptic potentials, action potentials in single cells, as well as the associated population signals [local field potentials and the electroencephalogram (EEG)].^19,20 Today, voltage imaging using small molecular weight voltage-sensitive dyes is an established method in neurophysiology for probing population membrane potential dynamics on the mesoscopic scale (millimeters of field of views^13,21–23). At the subcellular level, voltage-sensitive dye imaging was applied to voltage signals in fine dendritic branches, spines, and axons.^24,25 Cellular level voltage imaging in intact mammalian brain has been technically very challenging.²⁶ The principal limitations of low-weight voltage-sensitive dyes remain their immanent, pharmacological side effects,²⁷ toxicity and phototoxicity, indiscriminate staining of neuronal and glial membranes, small signal amplitude, impossibility to target specific cells, and fugacity of dye staining impeding long-term imaging in vivo.¹⁹

The development of genetically encoded voltage indicators (GEVIs) over the last decade was animated by the idea to overcome these limitations.²⁸ While the GEVI class of voltage indicators is still rapidly growing, several GEVIs were already benchmarked for practical use in vivo. In the following sections, we will summarize the history and the present state of the development of these indicators together with the emerging applications of GEVIs in neurophysiology research.

2.

History of Genetically Encoded Voltage Indicator Development (1997 to 2012)

At the time of the cloning of green fluorescent protein (GFP) by Douglas Prasher in the early 1990s, traditional low-weight voltage-sensitive dyes and calcium indicators were already well established for imaging neuronal electrical activity.^29,30 However, the discovery of GFP’s heterologous expression³¹ and the subsequent development of its color variants opened the possibility of a fundamentally different class of fluorescence indicators that are entirely built from proteins and fully encoded in DNA.

The translation of traditional synthetic fluorescence indicators into protein space was, however, everything but straightforward. Organic fluorescence indicators are engineered to employ optical transitions, whose transition energy or strength is influenced by extramolecular parameters such as the local electrical field or ligand binding. In dyes, these interactions are usually reliant on delocalized valence states, as these states are highly sensitive to changes of the inner-molecular electrostatic field. In proteins, on the other hand, valence states are spatially much more constrained as a consequence of the much larger molecular size. The first genetically encoded calcium indicators were therefore designed, with a steric rather than an exclusively electronic mechanism in mind, as a construct where a cyan and a yellow fluorescent protein (FP) are, respectively, placed at the N- and C-terminal positions of a calmodulin-M13 calcium-binding domain.^32,33 It was speculated that upon calcium chelation, the conformational contraction of calmodulin-M13 would alter the steric distance between the two FPs. This would in turn manifest optically as a change of the electromagnetic exited state energy transfer from cyan to yellow FP via the steep distance-dependence of Förster resonance energy transfer (FRET) between the chromophores within the range of the nonradiative optical near field.³⁴ While the combination of a calcium-binding domain and a fluorescence reporter in Cameleon and other GECIs still reminds of the same structural dichotomy in low-molecular weight calcium indicators (e.g., Fura2 or Oregon Green BAPTA), the creation of the first protein voltage indicators was inspired by the conformational changes that control the opening and closing of voltage-gated ion channels. In 1997, Siegel and Isacoff³⁵ reported a fusion protein denoted as FlaSh, which consisted of a shaker voltage-gated potassium channel with a GFP fused to its C-terminus (Fig. 1). FlaSh is considered as the first GEVI and was based on the assumption that the voltage-dependent gating of an ion channel, involving conformational transition between the conducting and the nonconducting states of the channel, could be exploited to actuate a fluorescence reporter in a manner resembling the fluorescence modulation observed from channel-conjugated organic dyes known to be able to report conformational changes in ion channels.^36,37 Detailed analysis later, however, suggests that FlaSh is a reporter of C-type inactivation, rather than gating, of the shaker voltage-gated potassium channel.³⁵

Fig. 1

Overview of genetically encoded voltage indicator (GEVI) molecular designs: Upper row shows the GEVIs based on the insertion of fluorescent proteins (FPs) (depicted as barrels) into complete ion channel proteins with segments (e.g., S1–S6) that cross the plasma membrane (PM). In the FlaSh-type voltage indicator, a FP is fused into the C-terminal portion of a Shaker potassium channel subunit. Tetramers of subunits form a channel structure which is made nonconducting by a point mutation. Modulation of FlaSh fluorescence is triggered by voltage-dependent rearrangements, probably corresponding to channel C-type inactivation. Middle panels show the GEVIs based on isolated voltage-sensing domains. In Förster resonance energy transfer (FRET)-based voltage-sensitive probes of the voltage-sensitive fluorescent protein (VSFP1/2) type, the voltage-sensor domain, consisting of four segments (S1–S4), is fused to a pair of FPs (FP, D: FRET donor; FP, A: FRET acceptor). A change in membrane potential induces a rearrangement of the two FPs that is optically reported as a change in the ratio between donor and acceptor fluorescence. Single FP and circularly permuted (cp) FP probes of the VSFP3 family are monochromatic. In FRET-based voltage-sensitive probes of the VSFP Butterfly family, the voltage-sensor domain is sandwiched between two FPs. Lower panels show the GEVIs based on opsins. A change in membrane potential induces increased fluorescence of the retinal molecule. The microbial rhodopsin-based voltage indicator Arch shows an increased fluorescence of the retinal molecule when the membrane potential is increased. In opsin/FRET probes, a FP in quenched by retinal in a voltage-dependent manner.

Following this idea, but introducing GFP into a skeletal muscle sodium channel instead, led to another prototypic GEVI construct, named SPARC³⁸ (Fig. 1). A very different concept of a GEVI, named VSFP1 (voltage-sensitive fluorescent protein; Fig. 1), was introduced by our lab (Knopfel lab at RIKEN, Japan);³⁹ slightly earlier than SPARC. VSFP1 differed from FlaSh and SPARC in three major aspects: While voltage-gated potassium channels (Kvs) consist of four subunits each containing six transmembrane segments (S1–S6), VSFP1 included only transmembrane segments S1–S4 (that form the putative voltage sensor domain) of a single Kv2.1 potassium channel subunit. Second, directly linked to the end of the S4 transmembrane segment of the Kv2.1 voltage sensor domain VSFP1, carried a pair of cyan and yellow FPs conceived as a FRET reporter for voltage-activated conformational transitions of the S1–S4 voltage sensor. Third, VSFP1 was designed as a dual emission (ratiometric) indicator to help abridge movement artifacts and hemodynamic modulation of optical signals in in vivo imaging. While FlaSh, VSFP1, and SPARC were successful as proof-of-principle when tested in Xenopus oocytes, they performed poorly in mammalian neurons, presumably due to faint membrane expression and strong accumulation in internal membranes and organelles including the endoplasmic reticulum (ER) and the Golgi apparatus.⁴⁰ Many years of efforts to improve GEVI export from ER and trafficking to plasma membranes remained fruitless and helped to cast doubts on the concept. In particular, the “voltage-sensor-domain-only” concept of VSFP1 faced criticism citing the lack of proof that an isolated ion channel voltage sensor can function as a functionally independent domain.

While the search for improvements of GEVI membrane targeting mostly focused on channel trafficking signals, a solution eventually emerged from the discovery of voltage sensor-containing phosphatase in Ciona intestinalis (Ci-VSP) by Okamura and coworkers. Ci-VSP features a voltage sensor that resembles the S1–S4 voltage sensing domain of Kv channels. However, instead of operating an ion channel, the Ci-VSP voltage sensor controls the activity of an intracellular phosphatase.⁴¹ Ci-VSP was discovered by genomic data mining as it preserves the crucial sequence motives that define ion channel voltage sensors across species. Yet, it was the first time that a native voltage sensor was found in a protein other than an ion channel. The Ci-VSP discovery was of importance for the development of GEVIs for at least three reasons. First, it provided strong support for the view of the voltage sensor as an independent functional domain that has motivated the design of VSFP1, a conclusion that later was corroborated by other observations, notably the discovery of the voltage-sensor-only proton channel Hv1.^42,43 Second, even more importantly, in contrast to ion channels that require assembly into tetrameric superstructures to acquire plasma membrane localization and function, there was no evidence for oligomerization as a necessary condition for Ci-VSP function.⁴⁴ To ensure correct channel assembly in the ER, ion channels are thought to carry ER retention signals that become masked by successful tetramerization before trafficking to the membrane.⁴⁵ The possible existence of such unmasked retention signals was suspected as an impediment for efficient membrane trafficking of the first generation GEVIs. And third, because of the phylogenic distance between C. intestinalis and mammals, it seemed possible that even if ER retention signals were present in Ci-VSP they might not be recognized efficiently by mammalian cells. Based on these considerations, we began to generate a set of constructs based on the VSFP1 template, but with the Kv2.1 voltage sensor being replaced by that of Ci-VSP. Notably, the very first construct (VSFP2a-d) displayed dramatically improved membrane localization compared with VSFP1,^46,47 while at the same time showing a significant voltage report in mammalian cells. However, the voltage sensitivity was seen only at membrane potentials far above normal membrane potential fluctuations in mammalian cells. This was not a surprise since the Ci-VSP voltage sensor was known to activate at very positive voltages.⁴¹ This problem was solved by mutagenesis of the voltage sensor in a region of the S4 voltage sensor segment resulting in a charge-neutalizing mutation R217Q of a polar S4 arginine that shifted the Ci-VSP voltage sensor activation to negative potentials within the dynamic range of the neuronal electrical signaling.⁴⁷ Interestingly, this charge neutralization did not alter the total effective sensing charge available to the voltage gate of 1.2 elementary charges.⁴⁸ For the historic perspective taken here, we like to note that the prepublication sharing of these results with Cohen and colleagues provided preliminary data for the successful acquisition of the first multimillion NIH grant on the development of GEVIs in 2006. Further optimization by tailoring the peptide linker between the voltage sensor and the FP reporter of VSFP2.1 eventually produced VSFP2.3.⁴⁸ The VSFP2s were the first GEVIs to overcome the membrane trafficking impediment characteristic of the first GEVI generation and were the first GEVIs to exhibit convincing optical voltage report in the neuron-like PC12 cells,^47,48 mouse primary neuronal culture, acute cortical brain slices, and mouse cortex in vivo.⁴⁹ The VSFP2s were later extended into a larger family by several GEVI constructs engineered as fusions of the Ci-VSP voltage sensor with red-shifted FRET reporters, notably Mermaid,⁵⁰ VSFP2.4,⁵¹ and VSFP-CR.⁵²

In addition to overcoming the many years of deadlock in GEVI development, the VSFP2s also served as the first model for studies of the biophysical mechanism of GEVI function. Since the transition between the ion channel resting and activated conformations is driven by movable charges within the voltage sensor that will translocate between equilibrium positions as a function of membrane voltage,⁵³ sensor activation gives rise to a measurable extracapacitive current, named the sensing or gating current. This current is generated by the displacement of an ionic screening charge at the external membrane interface following translocation of the sensing charge within the membrane.⁵⁴ Simultaneous fluorometric and sensing current measurements from VSFP2.3 expressed in Xenopus laevis oocytes⁵⁵ and in PC12 cells⁴⁸ under voltage clamp revealed a two-step activation process of the VSFP2.3 fluorescence response, with a fast time component reflecting the transfer of sensing charge and a subsequent component with slower time course and little associated charge transfer.⁵⁶ At this stage, it came as a fortunate surprise that the measured kinetics of VSFP2.3 activation turned out to be faster in PC12 cells than in X. oocytes, as manifested by a fast activation ON time constant of 3 ms in PC12 cells at 25°C⁵⁶ versus 20 ms in oocytes.⁵⁵ At 35°C (that is closer to the physiological body temperatures of rodents and humans), the fast activation ON time constant of VSFP2.3 is 2 ms.⁵¹

While a slow component of fluorescence activation contributes significantly to the overall VSFP2.3 fluorescence response in the steady state, it is the fast-activating initial component that dominates the dynamic VSFP response on the time scale of fast neuronal voltage transients.^56,57 The contribution of the fast component relative to the slower component was significantly improved with the development of VSFP2.4s and VSFP3s^48,49,51,58 and other similar voltage sensing domain-based probes described below.

While VSFP2.3 and VSFP2.4 were the first GEVIs to be successfully tested in the mouse brain in vivo, it was obvious that further SNR improvement and kinetics acceleration were required to enable applications such as reliable detection of somatic action potentials in single neurons.⁴⁹ The search for improved GEVIs explored a variety of ideas leading to GEVI constructs that employed voltage sensors from non-Ciona VSPs,⁵⁹ GEVIs that used the Ci-VSP voltage-sensor together with a single FP reporter (dubbed VSFP3s)^48,58,60 or a circular-permuted FP,^61,62 split FPs into two half FPs inserted randomly into the Shaker potassium channel,⁶³ and a GEVI-turned archaerodopsin named Arch^64,65 (Fig. 1). In this series of constructs, Arch was perhaps the most surprising one due to its unique mechanism in the absence of an ion-channel-type of voltage sensor, but involving a modulation of fluorescence caused by a voltage-sensitive proton transfer in the transient excited state of the retinal chromophore.⁶⁶ Voltage-sensor-based GEVIs exhibit a sigmoidal fluorescence-voltage relationship consistent with a voltage-activated transition between the activated and the resting states of the voltage sensor, but Arch featured a more linear relationship and large voltage sensitivity. Unfortunately, the fluorescence quantum yield of the retinal chromophore in Arch is extremely low ($\sim 1/1000$ compared with GFP), resulting in an output signal that is easily disturbed by background fluorescence⁶⁷ and the requirement of high-illumination intensities may cause considerable heating of the preparation.

Reengineering of VSFP2.4 eventually led to a new GEVI, named VSFP Butterfly, with largely enhanced performance.⁶⁸ In VSFP Butterfly-1.2, the mKate2 acceptor FP is moved from the C-terminal (as in VSFP2.4) to a position at the N-terminus, thus yielding a configuration where the two FPs are flanking the voltage sensor (Fig. 1). While VSFP Butterfly-1.2 inherited its fast activation kinetics from VSFP2.4, its steady-state activation is shifted closer to the neuronal resting potential, characterized by a half activation voltage of $-70\mathrm{mV}$, versus $-50\mathrm{mV}$ in VSFP2.4, together with a larger weight of the fast component of fluorescence response.⁶⁸ This feature, together with the insertion of an ER export motif to enhance trafficking to the membrane,^69,70 greatly improved the sensitivity to subthreshold voltage transients, but also permitted the detection of fast action potentials in pyramidal cells in single trials.⁶⁸ The Butterfly design was later reproduced in Mermaid-2, using a cyan FP at the N-terminal and a yellow FP at the C-terminal position of the Ci-VSP voltage sensor,⁷¹ a construction that finally overcame the poor neuron membrane localization of Mermaid.⁷² At the same time, another GEVI called ArcLight was introduced using the pH-sensitive super ecliptic pHluorin with a A227D mutation as a single FP reporter attached to the Ci-VSP voltage sensor,⁶⁰ a principle that was first realized in the VSFP3 series of indicators.^48,58 ArcLight has a large steady-state dynamic range of 35% together with modest kinetics but can report broad action potentials in cultured neurons with high SNR⁶⁰ and action potentials and synaptic potentials in local neuronal circuits of Drosophila melanogaster in vivo.⁷³

3.

Current Trends in Genetically Encoded Voltage Indicator Development (2012 to 2014)

The remarkable boost in GEVI performance over the last years was accompanied by a steady increase in the number of available GEVI constructs (see Fig. 1) calling for a systematic approach to quantify the performance of each GEVI under experimental conditions that represent their main application. While indicator performance is partly predictable from biophysical parameters, including extinction coefficient, emission quantum yield, rate constant of photobleaching, total effective sensing charge, half activation voltage, and ON and OFF time constants,^19,56 it also depends on characteristics of the expression system comprising the biochemical identity of target cells, method of gene delivery, transcription regulation and trafficking mechanisms in target cells, altogether affecting expression level, surface density, and level of background fluorescence. The perhaps biggest hurdle on the route toward a broadly applicable “optogenetic” approach to electrophysiology⁷⁴ results from the difficulty to track high-frequency content in the power spectrum of neuron electrical signals. While traditional electrophysiological recordings permit cut-off frequencies to the MHz range at 100 kHz sampling rates or faster, the early generation of GEVIs had a cut-off well below 100 Hz,⁶⁸ although optical sampling at much higher rates is technically feasible. Therefore, increasing GEVI bandwidth and SNR remains a central objective for the development of next generation GEVIs. To this end, several new designs aiming to accelerate GEVI kinetics were recently developed. Our lab pursued the idea to substitute parts of the voltage gate of the Ci-VSP voltage sensor with homologous components of the fast-gating Kv3.1 potassium ion channel.⁷⁵ By establishing a library of VSFP constructs with chimeric Ci-VSP/Kv3.1 voltage sensors introduced into the VSFP2.3 template, we observed modest kinetic enhancements when replacing parts of the S4 region. Larger replacements in regions including S4, S3, S2, and part of the S1–S2 extracellular loop resulted in significantly accelerated ON and OFF kinetics, equivalent to time constants faster than 2 ms, and a complete annihilation of the slow secondary activation step characteristic of the Ci-VSP sensor. We also created a C5 chimeric mutant with part of the S4 transplanted from Kv3.1, and a Butterfly version where the acceptor FP in C5 is moved from the C to the N terminus⁷⁶ mimicking the FP configuration of the nonchimeric VSFP Butterfly. The chimeric C5 VSFP Butterfly mutant exhibited similar fast kinetics as C5 together with a negatively shifted activation⁷⁶ in agreement with a similar shift in nonchimeric VSFP Butterfly.⁶⁸ Compared with VSFP Butterfly-1.2, C5 chimeric VSFP Butterfly features a much faster OFF transition resulting in improved total bandwidth and the ability to report voltage commands up to 200 Hz as demonstrated in cell culture.⁷⁶

Meanwhile Adam Cohen and coworkers developed a second generation version of Arch making use of the intrinsically fast photoactivation kinetics of archaerodopsins and searching for brighter mutants by random mutagenesis combined with fluorometric screening.⁷⁷ This work resulted in two new rhodopsin-based GEVIs named QuasAr1 and QuasAr2, improving the low quantum yield of Arch by an order of magnitude. Most of all these variants can achieve fast GEVI kinetics in the absence of accompanying large photocurrent unlike Arch. With ON and OFF time constants faster than $100\mu \mathrm{s}$ at room temperature,⁷⁷ QuasAr1 is the fastest GEVI reported so far and thus the first GEVI to be able to map the waveform of a fast somatic action potential in a manner fully compatible with classical intracellular electrophysiological recording.⁷⁷ However, in spite of some improvement in brightness and membrane localization from Arch, QuasAr1 and QuasAr2 remain dim compared with GEVIs using high-yield FP reporters, and their untested in vivo reporting ability may still suffer from insufficient SNR.

A possibility to overcome the low brightness of Arch-type GEVIs was recently explored in the lab of Mark Schnitzer, as well as independently in the labs of Robert Campbell and Adam Cohen.^78–80 The basic idea was to fuse a high-quantum yield FP to Arch-type GEVIs, so that the FP can act as a FRET donor to the retinal rhodopsin chromophore (Fig. 1). This approach yielded MacQ-mCitrine, employing a Mac rhodopsin in lieu of Arch and showing a fast activation time constant of 2.8 ms, large dynamic range, and significant expression at the cell surface.⁸¹ As the MacQ-FRET GEVI owes its brightness to the mCitrine donor and its photon yield is compatible with other FP-based GEVIs, in vivo testing in the mouse cerebellum demonstrated the probe’s ability to report broad ($\sim 10\mathrm{ms}$) calcium spike-induced regenerative potentials in Purkinje cell dendrites.⁸¹ Similar GEVIs were created using QuasAr2 instead of MacQ as the FRET acceptor,⁷⁹ where efficient linkage of QuasAr2 to a C-terminal FP reporter within the distance of the Förster radius of the retinal/FP reporter gives rise to functional and bright indicators. However, when compared with QuasAr-2 itself, these GEVIs tend to show lower dynamics and slower kinetics, including increased contribution of slow activation.⁷⁹

Motivated by the quest for speedy GEVI kinetics, ASAP1 is a GEVI design developed by Michael Lin and coworkers.⁸² ASAP1 was constructed from the voltage sensor of Gallus gallus voltage-sensing phosphatase (Gg-VSP) by inserting permuted enhanced GFP into the S3–S4 extracellular loop, after attempts to insert the reporter at a similar position to the Ci-VSP voltage sensor failed to yield sufficient surface localization.⁸² ASAP1 differs from previous single FP-GEVIs that had been placing the FP reporter at the C-terminus of the Ci-VSP voltage sensor^58,60 and is the first GEVI featuring an extracellular reporter with good surface localization, large dynamic range, and fast kinetics, yielding a fast time constant of 2.1 ms at room temperature.⁸²

The ongoing development of enhanced GEVI variants apparently has established several successful design principles with leading constructs reaching voltage sensitivity and kinetics in par with the best performing VSDs, as judged from the available cell culture assays. Even though caution should be in place as careful comparative studies of GEVI variants are still missing, this is a remarkable progress. The GEVI function will necessarily be sensitive to the biochemical conditions in their host cells and to the method of gene transfer applied, creating complexity unknown to VSD staining procedures. For these reasons, validation of GEVI function and SNR (e.g., signal detectability) in in vivo imaging recordings remains a necessary step on the route to successful application of GEVIs in optical neurophysiology.

3.1.

Application of VSFPs to Cortical Functional Imaging In Vivo

We tested VSFP2.3, VSFP2.4, VSFP Butterfly-1.2, and chimeric VSFP Butterfly for transcranial cortical imaging in the mouse cortex.^49,76,83 Using in utero electroporation of pCAG-VSFP plasmids into neuroepithelial cells of the subventricular zone at embryonic age E15.5, we obtained indicator expression limited to a sparse population of pyramidal cells in layer 2/3. Simultaneous measurement of donor and acceptor emissions allowed efficient elimination of hemodynamic noise caused by the pulsatile blood flow and presented as a correlated signal at heart beat frequency in both imaging channels supplied by the mCitrine/mKate2 FRET reporter of Butterfly.⁸³ Elimination of hemodynamic noise is a significant advantage afforded by dual-emission reporters, such as FRET reporter, as real-time or off-line hemodynamic noise cancellation⁸³ significantly improves SNR in in vivo recordings.^84,85 By recording sensory responses in the whisker barrel cortex in anesthetized animals under similar conditions, we found that the recordings from VSFP Butterfly-expressing animals offered consistently better SNR than those expressing VSFP2.3 or VSFP2.4. This is consistent with in vitro characterization of the indicators. Voltage-clamped Butterfly-expressing pyramidal neurons in vitro exhibited faster voltage responses due to a larger weight of the fast response step and an activation onset at more negative potentials.⁸³

Given these properties, we reasoned that the Butterfly GEVIs should excel in high-resolution optical readout of electroencephalographic signals (EEG) across cerebral cortex. To show this, we optically recorded slow-wave activity in anesthetized animals and compared the VSFP signal acquired from a transcranial optical window over somatosensory cortex [Fig. 2(b)] with simultaneously recorded ipsilateral and contralateral single-channel-EEG [see Fig. 2(a)]. These signals reported the same slow-wave periodicity of 2 to 5 Hz as revealed by similar VSFP and EEG autocorrelations, as well as periodic cross-correlation [Fig. 2(c)], which is markedly stronger for the local EEG [Fig. 2(c)]. After optimizing the transfection protocol using multiple rounds of plasmid electroporation, it was possible to achieve nearly homogeneous VSFP expression across the cortical hemisphere enabling hemisphere-wide VSFP imaging [Fig. 3(a), bottom]. Presentation of a tactile stimulus to the contralateral C1 whisker in an anesthetized animal [Fig. 3(a), top] elicited the propagation of the Butterfly-reported sensory-evoked signal at a velocity of 0.1 to $0.05\mathrm{m}/\mathrm{s}$.⁸³ Cortical activity spreads from the principal barrel to the surrounding barrel field in primary somatosensory cortex (S1) and to primary motor cortex (M1) [Fig. 3(b)]. We extracted the somatosensory and motor signals in S1 and M1 cortices by integrating circular regions of interest (ROIs) of 1-mm diameter in S1 [Fig. 3(a), black circle] and M1 [Fig. 3(a), red circle] for 25 repetitions [30 s intertrial interval; Fig. 3(c), top]. This procedure yielded stimulus-induced responses with an SNR better than 5 (marked by gray dotted rectangle) as well as spontaneous depolarizing events, with similar SNR but not locked to the stimulus [outside of dotted rectangle, Fig. 3(c), top]. The onset latency of the M1 versus the S1 response is $\sim 40\mathrm{ms}$ [Fig. 3(c), bottom], corresponding to a velocity of propagation of 0.1 to $0.05\mathrm{m}/\mathrm{s}$. These observations are in agreement with earlier experiments using classical VSD imaging²² and also consistent with the view that the vibrassae sensory input to cortex in anesthetized mice is represented first in S1 and then horizontally propagates to motor areas by, at least in part, strong monosynaptic intracortical connections.^86,87

Fig. 2

Comparison of VSFP recording and cortical electroencephalogram (EEG): (a) VSFP Butterfly-1.2 signal (black) recorded from a large region of interest (ROI) over somatosensory cortex [see (b)] along with EEG signals from ipsilateral (red) and contralateral cortex (blue) showing spontaneous rhythmic cortical activity of a mouse under deep pentobarbital anesthesia. Signals are low-pass filtered with 10-Hz cutoff. (b) Optical window for transcranial voltage imaging of somatosensory cortex. The yellow rectangle marks the ROI used to extract the VSFP signal shown in (a). (c) Autocorrelations of VSFP (left) and EEG signals (middle) and cross-correlations (right) of the VSFP signal [black trace in (a)] with ipsilateral (red) and contralateral (blue) EEG signals. Data adapted from Ref. ⁶⁸

Fig. 3

Whole hemisphere VSFP imaging of sensory-evoked and spontaneous cortical electrical activity: (a) Top: schematic dorsal view of the mouse head with imaging region of the left cortical hemisphere indicated as dotted rectangular (cyan). Donor (mCitrine) and acceptor (mKate2) were recorded with two synchronized CCD cameras at $50\text{frames}/\mathrm{s}$ in 4 s trials with 30 s intertrial interval with a tactile stimulus (single deflection) delivered to the contralateral C1 whisker via a piezo drive triggered by the imaging clock after 2 s baseline recording. Bottom: transcranial mCitrine fluorescence image of the left cortical hemisphere. (b) Poststimulus, single-trial time lapse sequence (20 ms interval) of $\mathrm{\Delta }R/R_0$ images after spatial filtering with a $2\times 2$ Gauss filter. The first image (gray scale) shows the mCitrine baseline image with pixels outside of the optical window masked. (c) Top: time courses of 25 consecutive trials of primary sensory (S1) and primary motor (M1) signals over ROIs outlined in (a). The time window of stimulus response is indicated as dotted rectangle. Depolarizing events outside of this time window are spontaneous. Bottom: Average of the evoked S1 and M1 responses (25 trials) at enlarged time scale.

Like traditional EEG recordings, the optical imaging method is strictly noninvasive and in addition provides superior spatial resolution and permits dissociation of EEG activity into genetically defined cell types. The current work conducted on mice under anesthesia is certainly an insufficient model for modulations of brain states and cannot address normal behavioral brain states including natural sleep. Therefore, the ability to record from fully awake animals and/or animals during natural sleep is indispensable. Imaging of awake visual cortex of pCAG-VSFP Butterfly-electroporated, head-fixed mice on a treadmill was recently benchmarked for wide-field acquisition of cortical retinotopography and cortical sensory dynamics. Using this approach, VSFP Butterfly was shown to report electrical signals of time courses commensurate with local field potential recordings and of similar spatial structure as derived from intrinsic hemodynamic optical signals.⁸⁴ The wish to further ease the use of this methodology and make it widely applicable in different laboratories has motivated the development of a knock-in transgenic mouse line, Ai78, for Cre-recombinase and tetracycline transactivator-dependent conditional expression of VSFP Butterfly-1.2 (Madisen et al., submitted). Transgenic mice expressing VSFP Butterfly-1.2 in excitatory neurons of layer 2/3 demonstrated sensory-induced VSFP signals in somatosensory, visual, and auditory cortices in response to the presentation of tactile stimuli directed to the mouse vibrassae, visual gratings or tones, respectively, with single-trial sensitivity (Madisen et al., submitted). These studies demonstrated the feasibility and relative technical ease of cell- and layer-specific transcranial cortical voltage imaging.

4.

Conclusion

The GEVI imaging opens a new observational window to nervous system function fully complementary to optogenetic interference methods^88,89 by relying on genetic tools to define the population of target cells and to drive long-term indicator expression in vivo. The complementarity with optogenetic interference methods is the key toward an all-optical implementation of in vivo electrophysiology, combining optical electrical stimulation and optical read-out of electrical responses.^74,80,90 Technically, the integration of optical writing and reading of neuronal information requires a method to multiplex action control and fluorescence acquisition, either by spectral or by temporal isolation of action and excitation/emission channels.

The application of GEVI imaging is not limited to the brain and is beginning to be used in cardiac sciences.^91–94 For instance, heart-specific expression of VSFP2.3 exclusively targeting either myocyte or fibroblast cells in transgenic mice was used to assess the role of these cells in cardiac infarction physiology, revealing abnormal electronic coupling between these cell types in infarction border tissue and giving rise to action potential-like potentials in fibroblast cells.⁹² Future engineering applications may involve the control of neuromuscular signals, interfacing nervous systems with external electronic circuits and optical screening for drugs targeting the nervous system, for instance.

While the traditional domain of voltage imaging has been the visualization of supracellular spatial-temporal structure of cortical electrical signaling, there is strong interest to achieve cellular resolution imaging to support local circuit analysis in vivo, particularly of electrical activity inaccessible to calcium imaging, as argued above. For this, we tested the VSFP Butterfly-1.2 response under two-photon excitation detecting VSFP signals from resolved pyramidal cells in brain slices and population signals in vivo.⁹⁵

It took more than several decades for voltage-sensitive dye imaging starting with Merocyanine-540 to eventually arrive at the present generation of low molecular weight voltage-sensitive dyes and almost two decades to develop the current state of the art GEVIs. The fascinating aspect of the history of voltage imaging is that this development was initiated at a time where optical imaging hardware beyond the classical anatomical microscope did not yet exist. The strong hope today is that the GEVIs will add to building a powerful optical toolbox for neuronal system physiology to eventually justify the enthusiasm that has inspired this decade-long development of optical measurement of membrane voltage that began with the pioneering work of Cohen and colleagues.