Abstract

Ca2+ influx triggers the release of synaptic vesicles at the presynaptic active zone (AZ). A quantitative characterization of presynaptic Ca2+ signaling is critical for understanding synaptic transmission. However, this has remained challenging to establish at the required resolution. Here, we employ confocal and stimulated emission depletion (STED) microscopy to quantify the number (20–330) and arrangement (mostly linear 70 nm × 100–600 nm clusters) of Ca2+ channels at AZs of mouse cochlear inner hair cells (IHCs). Establishing STED Ca2+ imaging, we analyze presynaptic Ca2+ signals at the nanometer scale and find confined elongated Ca2+ domains at normal IHC AZs, whereas Ca2+ domains are spatially spread out at the AZs of bassoon-deficient IHCs. Performing 2D-STED fluorescence lifetime analysis, we arrive at estimates of the Ca2+ concentrations at stimulated IHC AZs of on average 25 µM. We propose that IHCs form bassoon-dependent presynaptic Ca2+-channel clusters of similar density but scalable length, thereby varying the number of Ca2+ channels amongst individual AZs.

Introduction

Voltage-gated Ca2+ influx mediates stimulus–secretion coupling at the presynaptic active zone (AZ) and the ensuing transmission of information forms the basis for sensory, neural, and motor function1. For a few decades, synaptic neuroscience has aimed to establish a quantitative understanding of AZ Ca2+ signaling2,3,4,5,6,7,8,9,10. Progress has been limited, however, by technical challenges such as the resolution limit of conventional light microscopy, which has precluded direct visualization of nanoscale Ca2+ domains. Therefore, indirect approaches analyzing Ca2+-dependent processes such as transmitter release and the gating of presynaptic Ca2+-activated potassium channels3,5,6 as well as mathematical modeling3,4,8,9,10,11 have been employed to elucidate spatiotemporal Ca2+-concentration profiles at the AZ. But understanding synaptic transmission requires information on the number, biophysical properties, and topography relative to vesicular release sites of the presynaptic Ca2+ channels that determine the AZ Ca2+ signaling. Indeed, localization and quantification of presynaptic Ca2+ channels by electron microscopy9,12,13 or cell-attached recordings14,15 has recently fueled the progress.

Here, we studied the quantitative nanophysiology of presynaptic Ca2+ influx using AZs of sensory inner hair cells (IHCs) as a model system. IHCs are well-suited for studies of Ca2+ signaling at individual AZs because their AZs are relatively large and functionally separated due to µm-scale nearest-neighbor distance and strong Ca2+ buffering16,17,18. Moreover, voltage-gated Ca2+ influx in IHCs is almost exclusively mediated by a single type of Ca2+ channel (CaV1.3)19, which has also been characterized at the single-channel level15,20. Freeze-fracture electron microscopy21 and two-dimensional stimulated emission depletion (2D-STED) microscopy of immunolabeled Ca2+ channels8,22 suggest a stripe-like clustering of Ca2+ channels at the AZ, at least in fixed hair cells, similar to observations of the presynaptic protein bassoon at conventional synapses23. Based on analysis of the whole-cell Ca2+ current and the average number of AZs, the mean number of Ca2+ channels per AZ has been approximated to 80–10015,21,24. Ca2+ nanodomains with [Ca2+] up to hundreds of µM were postulated from modeling, readout of [Ca2+] by large conductance Ca2+-activated K+ channels3, or synaptic exocytosis6,8,18,24. Direct nanoscopic imaging of presynaptic [Ca2+], however, has yet to be established for AZs of IHCs or other presynaptic cells. Along with information on the number and topography of the Ca2+ channels and vesicular release sites8,9,11,12,14, such measurements will advance our understanding of stimulus–secretion coupling at the AZ. Moreover, a major heterogeneity of presynaptic Ca2+ signaling was observed among the AZs of a given cell12,14,17, which in IHCs likely contributes to the response diversity observed for postsynaptic neurons25,26. This calls for analysis beyond the average properties of AZs.

Here, we make use of the good experimental accessibility of individual AZs in IHCs to analyze the number, distribution, and activity of Ca2+ channels at individual synapses using innovative methods. We combine confocal Ca2+ imaging with selective inhibition of Ca2+ influx at individual AZs and optical fluctuation analysis for estimating the number of Ca2+ channels per AZ. Employing 3D-STED, we quantify the structure of AZ Ca2+-channel clusters in IHCs. We establish 2D-STED Ca2+ imaging and STED fluorescence lifetime measurements of AZ [Ca2+] and validate the method by mathematical modeling based on quantitative structural and functional characterization of presynaptic Ca2+ channels.

Results

Nanoscale anatomy of synaptic Ca2+-channel clusters in IHCs

We analyzed the nanoscale layout of presynaptic Ca2+ channels located at IHC AZs using super-resolution STED microscopy. AZs were immunolabeled against both the CaV1.3α1 subunit of the CaV1.3 Ca2+ channel as well as against the presynaptic protein bassoon, which marks the presynaptic density at IHC AZs22,27. Using 2D-STED, we imaged AZs that were located at the basal membrane of an IHC, selecting those that seemed to lie parallel to the imaging plane (Fig. 1a–j). Most of the AZs (~80%) showed linear arrangements of both Ca2+ channels and bassoon “clusters”, whereby the Ca2+-channel cluster co-aligned with the bassoon-labeled presynaptic density (Fig. 1a–e). We introduced a subjective classification of the apparent shapes of Ca2+-channel and bassoon clusters that yielded comparable results when performed by different observers. About 60% of the channel clusters formed narrow lines of an average full-width at half-maximum (FWHM) of ~70 nm (Fig. 1a–c), whereas another ~20% were somewhat wider (FWHM ~100 nm, Fig. 1d, e), with some of them forming what appeared to be double stripes of CaV1.3- or bassoon-immunofluorescence sandwiching the respective other type of cluster (Fig. 1d, e). At about 15% of the synapses, larger and more complex arrangements of Ca2+-channel and bassoon immunofluorescence were observed (Fig. 1f, g) and less than 5% of the synapses exhibited small, spot-like CaV1.3- and bassoon-immunofluorescence (Fig. 1h). The latter might represent spot-like clusters or stripe-like clusters that were aligned perpendicular to the imaging plane of the microscope.

Fig. 1
Fig. 1

2D nanoscale anatomy of IHC Ca2+-channel clusters. ah Representative examples of AZs assumed to run roughly perpendicular to the imaging axis at the base of IHCs, with immunofluorescence for the CaV1.3 Ca2+ channel (green) and bassoon (magenta), a protein of the presynaptic AZ, imaged with 2D-STED microscopy. Most (~60%) of the clusters seemed to form thin stripes, with CaV1.3 and bassoon lying side by side (ac), while some formed somewhat wider stripes, sometimes double stripes (~20%, d,e). About 15% of the AZs displayed a wider and more complex distribution of CaV1.3 and bassoon (f,g) and some clusters displayed small punctate staining for both proteins (~5%, h). Inset markers indicate our subjective classification of the displayed AZs according to i. Scale bar: 200 nm. i Summary of the distribution of different types of AZs as defined by the apparent shape of the individual AZs (ah) measured with 2D-STED microscopy in our sample of n = 138 AZs from N = 4 mice. j Average dimensions of thin stripe-like clusters of CaV1.3 (green) or bassoon (magenta), as presented in ac, obtained by fitting a 2D Gaussian function to the image and displayed as full-width at half-maximum (FWHM), from n = 81 AZs

For the most faithful 2D-STED measurements of the clusters, we used a secondary antibody tagged with the dye providing the highest resolution (Abberior STAR635P) for either CaV1.3 Ca2+ channels or bassoon. We then approximated the apparent size of the clusters by fitting a 2D Gaussian function to the raw STED images (Supplementary Fig. 1). This revealed that the FWHMs of the long and short axes for linear clusters of CaV1.3 channels and bassoon were very similar (Fig. 1j), with the short axis averaging to 73 ± 7 nm for CaV1.3 channel clusters and 65 ± 3 nm for bassoon (mean ± SEM; medians: 67 and 61 nm, respectively). The apparent length (i.e., long axis) of the CaV1.3 channel clusters averaged 239 ± 20 nm (mean ± SEM; median: 206 nm) and varied between approximately 100 and 600 nm, likely reflecting differences in AZ size16,26,28. Similarly, bassoon clusters showed an average apparent length of 235 ± 31 nm (mean ± SEM; median: 227 nm). When relating the length of Ca2+-channel and bassoon clusters with the lower resolution estimate of the length of their corresponding bassoon and Ca2+-channel clusters (labeled with Abberior STAR580-conjugated secondary antibody), respectively, we found a high degree of correlation (Fig. 2g; Pearson’s correlation coefficient of 0.71 for the entire data set including 3D-STED, see below; 0.58 for the 2D-data). Together with the identical length estimate, this indicates that Ca2+-channel clusters and corresponding presynaptic densities (marked by bassoon) scale with each other.

Fig. 2
Fig. 2

3D nanoscale anatomy of IHC Ca2+-channel clusters. ad Volumetric displays of representative examples of CaV1.3 (green) and bassoon (magenta) immunofluorescence at IHC AZs, acquired with 3D-STED microscopy. In the right panels of bd, CaV1.3 immunofluorescence is shown in isolation, blue lines indicate the 3D line profile plots used to estimate the length of the clusters by measuring the full-width at half-maximum of the line profile (e), here 455 nm (b), 389 nm (c), and 535 nm (d). Grid distance: 500 nm. e Average display of line profiles plotted through the 3D data from CaV1.3 (green) or bassoon (BSN, magenta) clusters along the long axis of Ca2+-channel clusters (n = 33 AZs from N = 2 mice), with representative examples of line profiles from individual clusters of CaV1.3 shown as dotted green lines. f Average length of the clusters of CaV1.3 channels (green) or bassoon (magenta), as measured from the full width at half maximum of the line profiles summarized in e. Crosses indicate individual data points. g Comparison of the lengths of associated CaV1.3- and bassoon-clusters as measured by fitting a 2D Gaussian function (2D-STED) or by measuring the FWHM of a 3D line profile (3D-STED) indicates a strong correlation between both measures (Pearson’s correlation coefficient of 0.71 for the combined data set)

One major drawback of a 2D-STED analysis is that the orientation of a given AZ relative to the imaging plane can have a marked effect on its apparent shape and size. If we assume that the imaged AZs were not oriented perfectly parallel to the imaging plane, but at an angle, then measuring the cluster sizes using 2D-STED (providing only lateral (xy) and no axial (z) super-resolution) would lead to an underestimation of the true cluster dimensions. We therefore turned to 3D-STED imaging29 to complement our 2D-STED data. While sacrificing some lateral resolution for increased axial resolution, we could obtain a near-isotropic effective point spread function (PSF), i.e., probing region. We acquired stacks of images (Fig. 2a–d) and, to reduce bleaching, lowered the power of the STED laser, achieving a 3D-resolution of ~160 nm (<20% of the focal volume of a confocal PSF). This way, although we could no longer reliably differentiate the apparent shapes we had previously defined in 2D-STED images, we were able to estimate the true length of the long axis of linear clusters by measuring the FWHM of the cluster signal along a line profile in 3D (Fig. 2b–e). The FWHM averaged to 461 ± 18 nm (median: 432 nm) and 450 ± 13 nm (median: 462 nm) for CaV1.3 and bassoon clusters, respectively (Fig. 2f; measurements of clusters tagged with both Abberior STAR635p and STAR580 were pooled, since due to the lower STED efficiency the resolution was not notably different). This indicates that the apparent length measured by 2D-STED microscopy underestimated the true length by approximately 45% for both Ca2+-channel and bassoon clusters. This was most likely caused by clusters that were tilted relative to the imaging plane and thus appeared shorter in the 2D-STED data. Indeed, performing the 2D-analysis on z-projections of the 3D-data resulted in average apparent lengths of 308 ± 11 nm for CaV1.3 and 286 ± 10 nm for bassoon clusters.

Counting Ca2+ channels per AZ by confocal Ca2+ imaging

We devised two different approaches to estimate the number of presynaptic Ca2+ channels at individual AZs: selective depletion of synaptic Ca2+ current and optical fluctuation analysis, both of which made use of confocal Ca2+ imaging.

For the first approach, we used focal microiontophoresis of the Ca2+-chelator ethylene glycol-bis(β-aminoethyl ether)-N,N,N',N'-tetraacetic acid (EGTA) to selectively reduce Ca2+ influx at a single AZ (ICa,AZ) by locally depleting free extracellular Ca2+ while maintaining the Ca2+ influx at the other AZs of the IHC. We employed fast confocal spinning-disk microscopy of patch-clamped mouse IHCs, loaded with the low affinity Ca2+-indicator Fluo-8FF (KD = 10 µM) and a fluorescently tagged peptide marking ribbon-type AZs30. This allowed us to simultaneously image Ca2+ signals at several AZs in the confocal section (Fig. 3a, b) and also to switch to adjacent sections by means of piezo-driven rapid refocusing (step size 500 nm). Based on previous results17, as well as given the low affinity of Fluo-8FF and the strong intracellular Ca2+ buffering (10 mM EGTA), we consider the observed Ca2+ signals to linearly relate to the voltage-gated Ca2+ influx.

Fig. 3
Fig. 3

Estimating the number of Ca2+ channels per AZ by confocal Ca2+ imaging with selective suppression of Ca2+ influx at individual AZs. a Representative image of hotspots of depolarization-evoked Ca2+ influx, visualized by increased fluorescence of the Ca2+-indicator Fluo-8FF (green, left), localized at AZs that are identified by a TAMRA-conjugated peptide (red, right) binding to the synaptic ribbon. Scale bar: 1 µm. b Hotspots of Ca2+ influx were additionally monitored in nearby AZs, also in different focal planes (500 and 1000 nm above and below the targeted AZ). Only those recordings were used where the targeted AZ (green arrowhead) showed a clear increase in fluorescence (green trace, bottom left) from baseline (i) upon depolarization (ii), which decreased upon microiontophoresis of EGTA (iii) but returned to full intensity after the end of iontophoresis (iv) and where nearby AZs (blue and purple asterisks) showed no obvious change in fluorescence (blue and purple traces, bottom right) due to iontophoresis. Scale bar: 1 µm. c Representative recording showing modulation of the depolarization-evoked increase in fluorescence at a single AZ (green, left axis) and of the evoked whole-cell Ca2+ current (gray, right axis) by microiontophoresis of EGTA from a micropipette close to the AZ. Changes in fluorescence increase (Δ(ΔF/F0)) and in whole-cell current (ΔICa) due to local depletion of extracellular Ca2+ by EGTA are estimated as the difference between measured data and a double-exponential function fitted to the data before and after iontophoresis (red dashed line). d Plotting ΔICa against Δ(ΔF/F0) allowed conversion of the synaptic fluorescence increase of a single AZ into the corresponding synaptic Ca2+ current. Data are from the recording shown in c. e Histogram of estimated numbers of Ca2+ channels per synapse from recordings of depolarization-evoked Fluo-8FF-fluorescence intensity increase due to Ca2+ influx. With the average slope of 14.3 pA, the hotspot intensities from a larger data set of n = 234 AZs (N = 25 IHCs) could be converted into currents. From these, an expected number of Ca2+ channels could be calculated using the assumptions of a single-channel current of iCa = 0.29 pA and an open probability of po = 0.4. On an average, a synapse contained 125 Ca2+ channels, with a median of 118 channels per AZ

We aimed for selective manipulation of a single AZ by (i) targeting a sufficiently isolated AZ, (ii) close apposition of the iontophoresis pipette to the membrane, and (iii) vivid bath perfusion (at least 1 ml min−1). Selective manipulation of an AZ was verified by monitoring signals from nearby AZs (Fig. 3b) in five confocal sections—the plane with the strongest Fluo-8FF fluorescence reduction of the targeted AZ as well as 500 and 1000 nm above and below it. We applied EGTA in a ramp-like manner after ΔF/F0 at the AZ had reached a steady state during a 200- or 270-ms long depolarization of the IHC to −14 mV (Fig. 3b, c). The reduction of synaptic Ca2+ influx resulting from local Ca2+ depletion was monitored by the decrease of the Fluo-8FF fluorescence at the targeted synapse (Δ(ΔF/F0), Fig. 3c, green arrow, on average down to 52%) and of the total IHC Ca2+ influx (ΔICa, Fig. 3c, black arrow). Next, we calculated the influence of the observed changes in neighboring AZs on the whole-cell calcium currents (Supplementary Fig. 2a) and corrected for this when estimating Ca2+ influx at the synapse under study. On average, the total signal change in neighboring AZs was 12 ± 4% that of the targeted AZ. We established a linear relationship between the IHC Ca2+ influx and the ΔF/F0 at the studied synapse (Fig. 3d, Supplementary Fig. 2b, c) and, by multiplying the slope of this linear fit with the maximal ΔF/F0 prior to EGTA application, obained ICa,AZ, which ranged from 9.9 to 31.1 pA (Supplementary Fig. 2d, mean: 25.0 ± 1.9 pA, median: 24.7 pA, n = 19 manipulated AZs from N = 19 IHCs). We then converted this into a distribution of total Ca2+-channel number per AZ assuming a single-channel current of 0.29 pA15,24,31 (−7 mV, 5 mM [Ca2+]e) and an open probability of 0.424.

In these experiments, we picked AZs with strong Ca2+ signaling to ensure good signal-to-noise ratio, resulting in a high number of synaptic Ca2+ channels (mean: 215 ± 16, median: 213). We then used the mean slope of those 19 manipulated AZs (14.3 ± 1.4 pA) to estimate ICa,AZ for a set of 234 AZs representing most of the synapses of a large sample of 25 IHCs (mean synaptic Ca2+ influx: 14.6 ± 0.4 pA, median: 13.7 pA; coefficient of variation (CV): 0.5). The resulting estimates of total Ca2+-channel number revealed major heterogeneity among the AZs: their Ca2+-channel complement ranged from 28 to 329 with a mean of 125 and a median of 118 (Fig. 3e). We observed two outliers (>average + 4× standard deviation) featuring 431 and 555 Ca2+ channels that we assumed to be multi-ribbon AZs or unresolved neighboring synapse pairs and hence excluded from further analysis.

In order to validate our approach, we repeated the experiment in the presence of the CaV1.3 channel agonist BayK8644, which maximizes open probability32—reaching 0.82 in IHCs24 (for lower estimates see ref. 15)—but does not change the single-channel current32. We argued that maxing out open probability would reduce potential errors in deriving the number of Ca2+ channels from the synaptic Ca2+ influx. We observed the expected doubling of ICa,AZ, but the slope of the relationship between ICa,AZ and ΔF/F0 was comparable (Supplementary Fig. 2b, c, +BayK8644: 16.67 pA, n = 12 AZs, N = 12 IHCs, vs. −BayK8644: 16.04 pA, n = 19 AZs, N = 19 IHCs, not corrected for the EGTA effects on neighboring synapses in either case). Importantly, the estimates of the number of Ca2+ channels per AZ in the presence and absence of BayK8644 did not differ for the strong synapses analyzed (+BayK8644: mean = 258 ± 39 vs. −BayK8644: 239 ± 18, median: 220 vs. 235, p = 0.779, Mann–Whitney U test, statistical power: 0.07).

Secondly, we counted Ca2+ channels at single AZs by analyzing non-stationary fluctuations of Ca2+-indicator fluorescence (Fluo-4FF, KD = 10 µM) during the injection of deactivating Ca2+ currents (tail currents, Fig. 4a). We depolarized the IHCs to +53 mV, past the (apparent) reversal potential of Ca2+ in IHCs (~45 mV), opening Ca2+ channels but not permitting Ca2+ influx, then elicited Ca2+-tail currents by hyperpolarization to −67 mV and recorded the accompanying transient increases in Fluo-4FF fluorescence at the center of the fluorescence hotspot (Fig. 4a, fluorescence plotted on inverted axis) by confocal spot detection17. The rationale is that fluctuations within ensembles of trials contain information on single-channel properties, a feature frequently exploited in non-stationary fluctuation analysis of membrane currents21,22,24,33. We buffered intracellular Ca2+ with 10 mM EGTA and 1 mM Fluo-4FF, such that the Fluo-4FF fluorescence change reported Ca2+ influx linearly17. We reasoned, therefore, that fluctuations of synaptic Ca2+-indicator fluorescence among repetitive trials could likewise provide access to microscopic Ca2+-channel properties at single AZs. However, while optical fluctuation analysis has proven helpful for estimating Ca2+-channel numbers in small compartments in conjunction with a failure analysis (dendritic spines34), it remained to be elucidated whether an analysis of non-stationary fluctuations could work at AZs facing a large cytosolic volume, as is the case in IHCs. The analysis of channel-gating-related fluctuations of Ca2+-indicator fluorescence is limited by the relatively low recording bandwidth resulting from the kinetics of Ca2+ binding (0.412 µM−1 ms−1) and unbinding (4 ms−1)35 of Fluo-4FF. Moreover, the contribution of the Ca2+ channels to the fluorescence signal varies dependent on their position within the cluster relative to the PSF of the microscope, due to uneven excitation and detection. In order to better match the signal to the limited recording bandwidth, we slowed Ca2+-channel deactivation by the agonist BayK864421,24 (5 µM), which increases the channel’s open time32. We addressed the impact of the inhomogeneous contribution of Ca2+ channels by mathematical modeling, which indicated that the mean and variance of the fluorescence signal are both affected in a way causing the error in the estimation of the number of Ca2+ channels to be rather limited (Supplementary Fig. 3).

Fig. 4
Fig. 4

Estimating the number of Ca2+ channels per AZ by fluorescence fluctuation analysis. a Voltage protocol (upper panel) used to evoke Ca2+ influx, visualized by the fluorescence signal (FCa, red trace, lower panel, note that increase points down for comparison with current) of local Ca2+ influx at a single synapse and simultaneously by recordings of whole-cell Ca2+ current (ICa, black trace, lower panel). b Trial-to-trial variance (red trace) and mean (black circles) of fluorescence. c Plot of baseline-subtracted variance of synaptic fluorescence (open circles) or of whole-cell Ca2+ current (filled diamonds) against mean fluorescence or current, respectively, from the exemplary cell shown in b. Lines indicate the fits of quadratic functions to the fluorescence data (blue) or the Ca2+-current data (red). Extrapolation of these fits back to baseline allows calculation of the total number of channels in the cell (from the Ca2+-current data) or at one AZ (from the fluorescence data). d Histogram of the number of Ca2+ channels, obtained from quadratic fitting of variance against mean as shown in d, to data from n = 57 AZs from N = 16 IHCs

We then isolated the ensemble variance (200 trials) resulting from Ca2+-channel gating (‘excess variance’) by subtracting the detector noise and photon shot noise (Fig. 4b). As expected for gating-related variance, it peaked at intermediate fluorescence intensities (Fig. 4b, c). Finally, we related the variance to the mean for the ensembles of fluorescence transients and also for the corresponding whole-cell Ca2+-tail currents (Fig. 4c). We estimated the total number of Ca2+ channels (NCa) per AZ (fluorescence) and per IHC (current) by binomial fitting to both data sets (Fig. 4c). NCa values per AZ ranged between 20 and 294 per AZ (Fig. 4d; mean: 78; median: 63; CV: 0.64). The total number of Ca2+ channels per IHC, estimated from the fluctuations of the whole-cell Ca2+ current, (mean: 1933; median: 1846; n = 16 IHCs) was consistent with previous estimates22,24.

In summary, both experimental approaches reported somewhat different estimates for the mean number of Ca2+ channels per AZ (125 and 78), suggesting either an overestimation of the number of channels during iontophoresis (e.g., due to additional effects on extrasynaptic Ca2+ channels, which are difficult—if not impossible—to quantify from our experiments), or an underestimation in the optical fluctuation analysis experiments (e.g., due to activity of synaptic channels outside the microscope’s PSF), or a combination of both. Also, we cannot exclude a small contribution of an age dependence of the AZ Ca2+-channel complement, because the two approaches made use of mice of different age (P15–17 for EGTA application and P21–28 for fluctuation analysis), for which we find subtle differences in the ΔF/F0,max of the Ca2+ indicator (Supplementary Fig. 4). Nevertheless, the observation of a large range of Ca2+ channels per AZ by both approaches confirms that the previously reported heterogeneity of Ca2+ signaling among the AZs of a given IHC17 results from different numbers of Ca2+ channels per AZ. Indeed, the CVs found for Ca2+-channel number per AZ by both approaches (0.5 and 0.64) were comparable to the one previously reported for the maximal synaptic Ca2+ influx (0.6517) and furthermore in good agreement with our data of the integrals of the 2D Gaussian fits to CaV1.3 immunofluorescence of Ca2+-channel clusters (0.67, data from Fig. 1). This AZ heterogeneity might be related to functional diversity of the spiking behavior of postsynaptic spiral ganglion neurons17,26. Finally, if we determine the total number of synaptic Ca2+ channels by multiplying the average number of Ca2+ channels per AZ (as assessed by both methods) with the count of synapses per IHC—typically 12 in the area of the organ of Corti used in our measurements—one arrives at a value between 950 and 1500. Relating this to the total number of Ca2+ channels per IHC (~1900, see above) indicates that approximately 20–50% of all channels localize extrasynaptically.

Modeling Ca2+ signals and Ca2+ imaging at IHC AZs

A previous study had estimated presynaptic [Ca2+] to reach ~3 µM at IHC AZs during depolarization17. This appears surprisingly low considering the large number of Ca2+ channels established here. Most likely, spatial averaging due to the microscope’s large PSF caused this low estimate, implying that the true [Ca2+] at the AZ might be far higher. We postulated that STED super-resolution imaging with its greatly reduced PSF size would provide much more accurate measurements of [Ca2+] at the AZ, allowing us to establish the concentrations occurring in vivo. First, we screened several Ca2+-indicator dyes for compatibility with STED nanoscopy and found Oregon Green BAPTA-5N (OGB-5N) to be the best-suited Ca2+ indicator with low affinity (Supplementary Figs 5, 6; reported KD = 32.5 µM36). In order to predict what [Ca2+] could be expected at the IHC AZ and whether super-resolution imaging could more accurately measure the local concentration, we performed reaction/diffusion simulations of the IHC AZ using the CalC modeling software37. Our model was based on the number and distribution of channels experimentally determined above (Table 1, Supplementary Fig. 7) and used OGB-5N as a Ca2+ indicator. Seeking imaging conditions for optimal super-resolution Ca2+ imaging, we generated several model implementations, changing the concentrations of Ca2+ indicator (from 25 to 1000 µM) and non-fluorescent intracellular Ca2+ chelators (from 0.8 mM EGTA and 0.4 mM BAPTA, emulating “physiological” Ca2+ buffering in IHCs with both fast and slow binding kinetics18, to 10 mM EGTA).

Table 1 Modeling parameters.

The model predicted that free [Ca2+] (Ca2+ not bound to Ca2+-indicator or non-fluorescent buffers) can reach up to 100–150 µM in close proximity (10–20 nm distance) to the channel mouth (Fig. 5a), but quickly drops as the distance to the channel increases, in agreement with previous studies3,8,18. Ca2+-bound indicator, however, can be found at greater distances from the channel cluster due to lateral diffusion of indicator and free Ca2+, such that the Ca2+ domains visible in Ca2+ imaging are larger than the Ca2+-channel cluster itself and do not permit resolution of nanodomains near individual Ca2+ channels. Still, when we calculated local [Ca2+] from the ratio of bound to unbound Ca2+ indicator (simulating the process in Ca2+ imaging), we found concentrations of up to ~45 µM (Fig. 5b), which matched the modeled free [Ca2+] at the AZ fairly closely.

Fig. 5
Fig. 5

Theoretical reaction/diffusion model of Ca2+ at the IHC AZ. a Theoretical model of Ca2+ influx at a 430 nm × 67 nm cluster of 120 Ca2+ channels (blue symbols, width of 10 nm) shows that the local increase in free [Ca2+] near the channel mouth, before the Ca2+ ions bind to the Ca2+-indicator or the non-fluorescent buffers, can reach values as high as 150 µM. Blue symbols indicate the positions of simulated Ca2+ channels. Inset shows a magnification of the area marked by the green square. Scale bar: 100 nm. b [Ca2+], as calculated from the simulated distribution of OGB-5N at the synapse (“reported [Ca2+]”), reaches peak values of 45 µM. The lateral diffusion of Ca2+ ions and buffers makes it impossible to acquire the [Ca2+] at the channel mouth and results in an elongated Ca2+ domain. Numbers indicate the [Ca2+] at the contour lines. c Increasing the simulated [OGB-5N] (here to 400 µM) results in a lower reported peak [Ca2+] of ~40 µM. d Increasing the simulated [EGTA] (here to 2 mM) results in a reported peak [Ca2+] of ~44 µM. e Same data as in b, but additionally convolved with a Gaussian PSF with a FWHM of 64 × 64 × 542 nm, mimicking 2D-STED imaging. The reported [Ca2+] after convolution reaches peak values of up to 10 µM, still considerably lower than the actual concentration near the channels

Evaluation of the model showed that low Ca2+-indicator concentrations could provide the most accurate approximations of local [Ca2+] (Fig. 5b, c). We therefore settled on the lowest feasible concentration of 25 µM. Similarly, since increasing the non-fluorescent Ca2+ buffers did not appreciably decrease the size of the Ca2+ domain (Fig. 5d), we decided on the aforementioned “physiological” imaging conditions, which would also more closely describe [Ca2+] at IHC AZs in vivo. To predict whether STED imaging could more accurately measure local [Ca2+], we convolved the simulated dye distributions with a 3D Gaussian function mimicking the PSF of a 2D-STED microscope (64 × 64 × 542 nm FWHM), and again calculated [Ca2+]. As expected, the spatial averaging (especially along the z-axis) caused by the PSF leads to a marked underestimation of [Ca2+], with maximum values of ~10 µM (Fig. 5e). Compared to a confocal PSF, however, the measured Ca2+ domain was much smaller, displaying a FWHM of 223 × 393 nm (STED) vs. 332 × 454 (confocal), indicating the potential benefits of STED Ca2+ imaging.

Super-resolution imaging of presynaptic Ca2+ signals

Building on the above results, we tested the feasibility of combining patch-clamp with live STED imaging in HEK-293 cells and IHCs, with regard to both the stability for patch-clamping and nanoscale imaging, as well as to the physiological condition of the cell. During STED imaging, we observed neither strong mechanical drifts nor detrimental effects to the stability of the patch-clamp recording. Both HEK-293 and hair cells tolerated exposure to even the highest possible STED beam intensities for several seconds typically without showing signs of light-induced leak currents.

We then performed live STED Ca2+ imaging, using physiological [Ca2+]e (1.3 mM) and 0.8 mM EGTA, 0.4 mM BAPTA, and 25 µM OGB-5N in the pipette solution. Aiming for AZs near the base of the cell (perpendicular to the optical axis), we depolarized the cell for 78 ms and imaged OGB-5N fluorescence hotspots in small (3 µm × 1.5 µm) xy-scans (see Fig. 6a–f for representative images). Hotspots appeared roughly spherical at confocal resolution, but STED revealed them to be elongated ellipsoids between 90–300 nm in width (Fig. 6g) and 200–450 nm in length (Fig. 6h), as measured by fitting a 2D Gaussian function (Fig. 6c). We found that both the short and the long axis were significantly smaller with STED Ca2+ imaging when compared to confocal Ca2+ imaging (Fig. 6a–h, 203 ± 7 nm vs. 303 ± 5 nm for the FWHM along the short axis and 305 ± 11 nm vs. 386 ± 8 nm for the FWHM along the long axis from n = 55 and n = 74 synapses for STED vs. confocal imaging, respectively, p = 1.9e−21, Student’s T-test, statistical power: 1, and p = 3.4e−11, Mann–Whitney U test, statistical power: 1, for short and long axis, respectively), in good agreement with the results of our modeling (Fig. 5). Typically, about 12–18 mW of STED power (in the back aperture of the objective lens) was sufficient to fully resolve the fluorescence hotspots. Only in a few cases did higher STED beam powers reveal even smaller hotspots. This implies that the measured size of the typical hotspot was, in most cases, limited not by the microscope’s lateral resolution, but by the size of the hotspots themselves, which is governed by the diffusion of Ca2+ and Ca2+ indicator and quickly reaches a steady state (see Supplementary Fig. 8). These functional observations therefore corroborate the stripe-like arrangement of presynaptic CaV1.3 immunofluorescence at wildtype AZs (Fig. 1a–e).

Fig. 6
Fig. 6

Super-resolution imaging of presynaptic Ca2+ signals in IHCs. ac Hotspot of OGB-5N fluorescence in a wildtype mouse IHC in “physiological conditions” (same in df, 25 µM OGB-5N, 0.8 mM EGTA, and 0.4 mM BAPTA inside the pipette, 1.3 mM [Ca2+]e), evoked by a 78-ms depolarization of the cell to −14 mV (a), as well as the corresponding fluorescence signal at the holding potential of −84 mV (b), both imaged using STED. c A 2D Gaussian fit to the background-subtracted hotspot image. Scale bars: 200 nm. df Background-subtracted images of depolarization-evoked hotspots of OGB-5N fluorescence, indicating synaptic Ca2+ influx, each imaged in confocal mode (d), with 12.3 mW STED laser intensity (e), and with 24.3 mW STED laser intensity (f). Increasing STED power leads to smaller and more elongated hotspots. Scale bar: 200 nm. g, h Significantly increased resolution of Ca2+ imaging by STED microscopy: the dimensions of the Ca2+ domains were measured by fitting a 2D Gaussian function to the background-subtracted images. Both short (g) and long axis (h) of the Gaussian were significantly smaller when measured with STED microscopy (red, n = 55 synapses, N = 43 IHCs, STED power 12.3–35 mW) compared to confocal microscopy (black, n = 74 synapses, N = 55 IHCs) with p = 1.7e−21 for g, Student’s T-test, statistical power: 1, and p = 3.3e−11 for h, Mann–Whitney U test, statistical power: 1. i, j Background-subtracted images of two representative depolarization-evoked hotspots of fluorescence from BsnΔEx4/5 mouse IHCs, imaged in “physiological conditions” (see ac) in confocal mode (i) and with 12.3 mW STED power (j). The hotspots are much larger than those from wildtype animals (ah) and do not decrease in size when using STED microscopy. Scale bar: 200 nm. k, l Same as in i, j, but imaged in “intensified conditions” (300 µM OGB-5N and 10 mM EGTA inside the pipette, 10 mM [Ca2+]e). m The size of hotspots of BsnΔEx4/5 mice (as measured by fitting of a 2D Gaussian function) is unchanged when using STED (red, n = 15 synapses, N = 13 IHCs, STED power 12.3–24.3 mW) compared to confocal recordings (black, n = 23 synapses, N = 21 IHCs), with p = 0.605, Mann–Whitney U test, statistical power: 0.176

We applied the same imaging protocol to observe IHC AZs in mice lacking functional bassoon (BsnΔEx4/5)38; these AZs typically lack the synaptic ribbon and hold fewer Ca2+ channels. Previous STED imaging of CaV1.3 immunofluorescence had suggested that these channels form small, spot-like clusters22, whereas live confocal Ca2+ imaging (with 2 mM intracellular EGTA and 5 mM [Ca2+]e) had reported that the width of the presynaptic Ca2+ domains at bassoon-mutant AZs was indistinguishable from wildtype AZs (FWHM of ~1 µm in both cases)22. Interestingly, we could clearly distinguish the bassoon-mutant AZs, which displayed significantly larger Ca2+ domains (Fig. 6i–m, short axis length of 607 ± 50 nm using STED, p = 8.6e−12, Mann–Whitney U test, statistical power: 1) than wildtype AZs. STED imaging did not reveal any further details within these large Ca2+ domains, suggesting that Ca2+ channels are more widely dispersed in the presynaptic membrane when tethering to the AZ by bassoon is not available. This leads us to suspect that the small spot-like appearance of CaV1.3 immunofluorescence22 was not physiological but artificial, e.g., resulting from the aggregation of untethered Ca2+ channels during precipitation by the fixative. Based on our above modeling, we assume that the inability of the previous study to visualize the size differences of the presynaptic Ca2+ hotspots in both genotypes is explained by the imaging conditions of that study, including a larger confocal PSF, high [Ca2+ indicator], and higher [Ca2+]e than [EGTA]. We further examined bassoon-deficient AZs in additional experiments using conditions designed to obtain a stronger signal (by enhancing Ca2+ influx (10 mM [Ca2+]e), utilizing higher [OGB-5N] (300 µM) and [EGTA] (10 mM); “intensified conditions”; Fig. 6k–l), but this did not affect the appearance of the large Ca2+ domains in confocal or STED Ca2+ imaging. Interestingly, in wildtype AZs these “intensified conditions” (with the expected presynaptic [Ca2+] [OGB-5N]) evoked somewhat larger Ca2+ hotspots than observed under “physiological” conditions.

In summary, live STED Ca2+ imaging is feasible and can be combined with patch-clamp for proper stimulus control and replenishment of Ca2+ indicator. STED Ca2+ imaging functionally demonstrated that Ca2+ channels at AZs of wildtype IHCs are, indeed, organized in stripe-like clusters. The size of the hotspots of Ca2+-indicator fluorescence matched well with the dimensions of Ca2+ domains in theoretical models based on the morphology of Ca2+-channel clusters as revealed by STED imaging of CaV1.3 immunofluorescence in fixed wildtype IHCs. The simulations show that the larger dimensions of the hotspots, when compared to those of the Ca2+-channel clusters in morphological STED imaging, reflect the diffusion of both free and indicator-bound Ca2+. Furthermore, Ca2+ imaging of bassoon-mutant IHCs revealed large presynaptic Ca2+ domains, showing that conclusions based solely on immunolabeled Ca2+ channels in fixed tissue do not always represent the physiological organization and should be complemented by functional imaging with high resolution. We conclude that bassoon and/or the synaptic ribbon are required for appropriate clustering of Ca2+ channels.

Estimating presynaptic [Ca2+] from fluorescence lifetimes

Next, we further adapted our method to not only observe the spatial distribution of presynaptic Ca2+, but to quantitatively measure [Ca2+] at the AZ. For this, we established time-correlated single photon counting (TCSPC) of OGB-5N fluorescence with STED resolution (Fig. 7), a method based upon measuring the stark changes in fluorescence decay of the dye upon Ca2+ binding39,40. OGB-5N is a low-affinity Ca2+ indicator with a fluorescence lifetime when bound to Ca2+ of τ = 3.24 ns, which is markedly quenched to τ = 0.23 ns in the absence of Ca2+ (Fig. 7a, b, Supplementary Fig. 9a–d). The fluorescence decay of both the Ca2+-bound and -free state is very well described by a mono-exponential function, allowing us to assume a true two-state system (Supplementary Fig. 9a–e). By double-exponential fitting of the OGB-5N fluorescence decay and analysis of the amplitudes of both components (Supplementary Fig. 9b–e), it is possible to calculate the number of photons per channel (fast or slow decay; Fig. 7c, d) and therefore to determine the ratio of Ca2+-free and Ca2+-bound dye for estimation of the actual [Ca2+]. However, given the nanoscale size of the Ca2+ domains at IHC AZs, we expected high spatial resolution to be essential in obtaining accurate estimates of localized presynaptic [Ca2+].

Fig. 7
Fig. 7

Calculation of [Ca2+] from measured photons by application of correction factors. a Time-correlated single photon counting (TCSPC) reveals how the fluorescence lifetime traces of OGB-5N are highly sensitive to different [Ca2+], with sensitivity over several orders of magnitude (measured in solution, 10 nM < [Ca2+] < 90 mM, traces averaged from 10 s recordings). Both amplitude and average lifetime of the fluorescence signal increase with rising [Ca2+]. b Even though STED imaging (here, with 12.3 mW of STED power) introduces an additional (fast) component to the fluorescence decay, the recorded fluorescence lifetime signal is still very sensitive to different Ca2+ concentrations. ci Detailed knowledge of the dye characteristics is needed to calculate accurate [Ca2+] estimates from the recorded TCSPC signal. After measuring the fluorescence decay of OGB-5N with TCSPC, the incoming photons (c, each box representing one photon) can be sorted into two channels, one corresponding to the fast (yellow) and one to the slow lifetime (blue), by fitting the fluorescence decay with a bi-exponential function (d, Supplementary Fig. 9). Downscaling the number of slow photons by the brightness correction factor b takes the diminished brightness (smaller quantum efficiency and extinction coefficient) of free vs. Ca2+-bound OGB-5N into account (e, Supplementary Fig 10), converting the number of fluorescence photons (per channel) into an approximation of the number of emitting fluorophores (molecules of OGB-5N). The STED efficiency correction factor s compensates the larger effective focal volume of the Ca2+-free dye (due to decreased STED efficiency), which (uncorrected) results in a larger number of sampled molecules than for Ca2+-bound dye (f, Supplementary Fig. 11). Finally, in IHCs (as opposed to in vitro), some of the dye appears not to be sensitive to Ca2+ anymore (g, Supplementary Fig. 13). When taking this into account (g, either by rescaling the ratios of bound over free dye or by introducing a Ca2+-insensitive dye fraction to the model), a corrected ratio of bound over free dye can be calculated (h) which allows calculating the [Ca2+] from the previously measured effective dissociation constant Keff (i, Supplementary Fig. 14)

Accurate, quantitative measurements of [Ca2+] require a precise understanding of the Ca2+-indicator dye, its behavior within the actual experimental environment, and its interaction with the microscope in order to perform the necessary calibrations and corrections. Most prominently, the quantum efficiency and extinction coefficient of OGB-5N change upon binding to Ca2+, resulting in a different brightness of the Ca2+-bound and -free dye (Fig. 7d, e, Supplementary Fig. 10). Furthermore, the shortened lifetime of Ca2+-free OGB-5N causes the STED de-excitation to be less efficient, resulting in different effective focal volumes for Ca2+-bound and -free dye (Fig. 7e, f, Supplementary Fig. 11). Also, the STED beam itself impacts the measured fluorescence lifetime (Fig. 7b, Supplementary Figs. 11, 12): by its very nature, STED causes an additional fast decay of fluorescence (τ = 0.19 ns), which needs to be considered to avoid overestimating the free (fast) dye contribution during STED measurements (Supplementary Fig. 12). When imaging with STED, we therefore excluded (“blanked”) the data recorded in the first 300 ps (i.e., during the STED laser pulse) from the fitting routine, resulting in only minimal errors (see Methods).

Furthermore, in contrast to the in vitro calibration, where the Ca2+-bound state of OGB-5N could be either saturated (>99%, 10 mM [Ca2+]) or completely de-populated (<0.5%, 10 mM EGTA), this was not the case when measuring inside living IHCs. Even when patching a cell with 60 mM [Ca2+], the contribution from the slow lifetime component never surpassed 60% (Supplementary Fig. 13). This might be due to the dye interacting with molecules inside the cell, which change its properties, as has previously been described elsewhere41. To incorporate this into our calculations, we devised two independent approaches (Fig. 7f–h): (i) rescaling the dynamic range of the dye to match the reduced range observed in IHCs (“scaled lifetime ratios”) and (ii) expanding our model system by considering a Ca2+-insensitive dye fraction (see Methods and Supplementary Methods for a detailed derivation of the calculations).

Finally, the Ca2+-binding behavior of OGB-5N varied strongly depending on its immediate experimental environment. Initially, we performed in vitro calibrations of Ca2+ binding by OGB-5N in “minimalistic” solutions with well-known [Ca2+] (containing only Ca2+, Ca2+ buffer, and OGB-5N) and found a KD of ~40 µM (Supplementary Fig. 14a), close to the published values of 30–40 µM36. When repeating the same calibrations in solutions designed to closely match the intracellular solutions used in patch-clamp (with additional Ca2+ and only citrate as Ca2+ buffer to set the free [Ca2+]), we found a much higher effective KD (Keff) of ~195 µM (Supplementary Fig. 14b). Such behavior has been observed before42, and might be explained by differences in ionic strength of the solution and by the binding and buffering capabilities of additional components of the intracellular solution41,43. As these second conditions most closely matched the actual experimental conditions, we used this value (Keff) for all further calculations (Fig. 7h,i).

We applied the TCSPC method to measure [Ca2+] at IHC AZs at confocal and STED resolution by measuring the fluorescence decay before and during depolarization of the patch-clamped IHCs in an 8 × 8 xy-matrix of points (spot detection17,44, each separated by 50 nm) covering an AZ (Fig. 8a–f). Taking into account the response function of the instrument, we sorted the total photon counts according to whether they originated from either Ca2+-free OGB-5N (fast lifetime) or Ca2+-bound OGB-5N (slow lifetime). After applying the aforementioned corrections, the ratio of fast and slow lifetime components allowed us to approximate the [Ca2+] at the AZ during depolarization (Fig. 8e, f, red traces) and at rest (black traces) both with confocal and STED resolution. The calculated [Ca2+] distributions typically matched the observed shape of the AZ Ca2+ domains, with peak [Ca2+] values agreeing with or slightly above our mathematical simulations. Both calculation methods were in agreement with each other, finding peak [Ca2+] in the center of the depolarization-evoked presynaptic Ca2+ domain to be slightly higher when imaging using STED (“scaled lifetime ratios”: Fig. 8g; STED: 14.8 ± 1.9 µM [CV: 0.5] vs. confocal: 11.4 ± 1.6 µM [CV: 0.6], “expanded model”: Fig. 8h; STED: 19.7 ± 2.6 µM [CV: 0.56] vs. confocal: 15.1 ± 2.6 µM [CV: 0.75]). Both calculation methods demonstrated a clear, yet modest advantage of 2D-STED Ca2+ imaging (over confocal) for reporting [Ca2+] close to the Ca2+-channel cluster. Clearly, however, the low resolution along the optical (z) axis of our 2D-STED microscope still caused significant spatial averaging, conflating the high [Ca2+] within the nanoscale space around the Ca2+ channels with the lower [Ca2+] further away from the AZ.

Fig. 8
Fig. 8

Measuring synaptic Ca2+ concentration by fluorescence lifetime imaging. ad Representative data from two 8 × 8 (50 nm steps in x and y) pixel raster scans of a hotspot of Ca2+-influx-evoked fluorescence at the AZ, depicting the rise in fluorescence during depolarization (left, shown for confocal imaging (a) and 12.3 mW STED imaging (b)) and the corresponding Ca2+ concentrations calculated from the lifetime data (right, c and d for confocal and STED, respectively). Scale bar: 100 nm. e, f Fluorescence lifetime traces from single pixels in the same recordings shown in ad, acquired with confocal (e) and STED imaging (f). Red traces show the fluorescence data during depolarization of the IHC, black traces at rest. For analysis of the STED imaging traces, we employed a blanking range (gray box). Data points inside this range were excluded from the fitting procedure (used to establish the ratio of Ca2+-bound and -free dye) to avoid influence of the artificial STED-evoked short lifetime component. g Average maximum Ca2+ concentrations (black symbols) calculated as “scaled lifetime ratios” from the fluorescence lifetime data of recordings acquired using both confocal imaging (left, n = 19 AZs, N = 19 IHCs) and STED imaging (right, n = 18 AZs, N = 18 IHCs) show an increase in measured Ca2+ concentration using STED imaging. h Same as in g, calculated considering a Ca2+-independent background signal according to Equation 11

To approach this issue, we modified our 2D-STED experiments to further reduce the volume from which [Ca2+] was sampled. For this, we shifted the focus of the objective below the AZ while measuring [Ca2+], so that the majority of the volume illuminated by the microscope’s PSF was outside the cell and thus devoid of dye (Fig. 9a). As the focus was moved outside the cell, the recorded fluorescence dropped (e.g., Figure 9b), yet the measured Ca2+ concentration indeed increased with increasing distance beneath the membrane (Fig. 9c, d), reaching average values as high as 25 ± 7 µM and peak values between 45 and 50 µM (for STED recordings) at a distance of 800 nm from the brightest point of the hotspot (and thus most likely the membrane). This agrees with our modeling that predicted similar concentrations (Fig. 9d, dashed lines). These recordings displayed high variance (especially when recording with STED), most likely because (due to drift) it was difficult to place and keep the recording in the exact center of the fluorescent hotspot, where [Ca2+] is at its highest.

Fig. 9
Fig. 9

Decreasing the focal volume of Ca2+ imaging by moving the PSF in z. a Schematic drawing illustrating the decreased volume of intracellular dye that is sampled when moving the focus of the microscope down below the membrane in an xz-scan. Green lines indicate the FWHM of the PSF. b Representative data from an 8 × 8 pixel raster scan in x (50 nm steps) and z (200 nm steps) of a hotspot of Ca2+-influx-evoked OGB-5N fluorescence at the AZ, depicting the rise in fluorescence during depolarization. c The corresponding Ca2+ concentrations calculated from the lifetime data of the recording shown in b. Notice the increase in [Ca2+] toward the bottom of the plot. d Average maximum Ca2+ concentrations (“scaled lifetime ratios”) calculated from the fluorescence lifetime data of recordings acquired using both confocal imaging (black circles, n = 10 AZs, N = 10 IHCs) and STED imaging (red circles, n = 13 AZs, N = 13 IHCs), overlaid on top of the modeling data (from the model shown in Fig. 5) convolved with a 243 nm × 243 nm × 542 nm Gaussian “PSF” (“confocal”, black dotted line) or a 64 nm × 64 nm × 542 nm Gaussian “PSF” (“STED”, red dotted line). Experimental data have been aligned in z relative to the maximal fluorescence intensity as estimated from a 1D Gaussian fit to the average fluorescence per z-line during stimulation and binned in 200-nm z-steps

Discussion

In the present study, we used high- and super-resolution light microscopy to quantify the number and spatial organization of synaptic Ca2+ channels and the resulting Ca2+ domains at a presynaptic AZ that is experimentally well accessible. We found that most of the IHC AZs form linear clusters that run in parallel to the presynaptic density, marked by the presynaptic scaffold bassoon (Fig. 1). In wildtype IHCs, the dimensions of the Ca2+ domains observed during voltage-gated Ca2+ influx (Fig. 6g, h) were compatible with those of the immunolabeled Ca2+-channel clusters, when considering diffusional spread of Ca2+ and Ca2+ indicator predicted by a theoretical model (Fig. 5e). Observations of intramembrane particles in the presynaptic membrane in freeze-fracture electron micrographs of frog hair cells21 had previously suggested similar arrangements of presynaptic Ca2+ channels. However, the molecular identity of these particles remained unclear.

Our study corroborates the notion that bassoon and/or the synaptic ribbon organize the spatial arrangement of Ca2+ channels. While previously published immunohistochemical data suggested a punctate clustering of Ca2+ channels in the absence of bassoon22, our Ca2+-imaging data indicate a widespread distribution of Ca2+ channels in the presynaptic membrane (Fig. 6i–m). This discrepancy might be explained by an artificial clustering of Ca2+ channels during immunohistochemistry, which in the absence of bassoon appear to be less efficiently localized to the AZ. In the presence of bassoon, on the other hand, the physiological organization of Ca2+-channel clusters appears to be well represented by immunohistochemistry: the elongated depolarization-evoked presynaptic Ca2+ domains seen in STED Ca2+ imaging are compatible with the stripe-like CaV1.3 immunofluorescence. In some instances, we observed more spatially extended synaptic Ca2+ signals in IHCs. These might represent the more complex clusters of Ca2+ channels (Fig. 1f, g). Whether these, in turn, represent especially large AZs or cases where multiple ribbons are situated at one AZ (as is sometimes observed in electron micrographs45) will need to be clarified in further experiments.

It will now be interesting for future studies to investigate the topography of the individual channels within the clusters, e.g., by SDS-replica labeling9, and ideally their spatial relationship to synaptic vesicles tethered at the AZ. This will provide important input into biophysical modeling of how Ca2+ influx couples to exocytosis of synaptic vesicles. Biophysical experiments and modeling have so far indicated that, at the IHC AZ, exocytosis of a given readily releasable vesicle is under “Ca2+-nanodomain-like” control of few Ca2+ channels with a mean effective coupling distance between mouth of channel and Ca2+ sensor of 17 nm8,18,24,46, which we postulate to be common to IHC AZs regardless of their size. Using two independent methods to assess the number of Ca2+ channels at a single synapse, we found on average approximately 80–120 Ca2+ channels per AZ, whereby the counts varied dramatically between AZs (20–330). The wide distribution of lengths we measured for the long axis of CaV1.3 clusters by STED microscopy (Fig. 2f, g) suggests that much of the variance in presynaptic Ca2+ influx is realized through varying the length of CaV1.3 clusters. In contrast, the widths of the clusters appear to be more similar among AZs. This is compatible with the hypothesis that the topography of Ca2+ channels and membrane-proximal vesicles is conserved at AZs with different numbers of Ca2+ channels. Such presynaptic heterogeneity is a candidate mechanism for the diversity in firing properties of postsynaptic spiral ganglion neurons17,47,48,26.

IHC ribbon-type AZs achieve the high average density of 4000 Ca2+ channels per µm2 (~120 channels on ~0.03 µm2)—considerably higher than typically found in central nervous system (CNS) neurons where it ranges from 500 to 15009,12,13—likely through a protein network organized by bassoon22,49 and including the synaptic ribbon22,50, RIM51,52, and RIM-binding protein53,54. Given this very high density it seems likely that the Ca2+ influx at IHC AZs serves additional roles besides triggering synaptic release, e.g., increasing [Ca2+] to facilitate vesicle resupply55. The distance between Ca2+ channels and synaptic vesicles appears to be comparable between IHC AZs and some CNS AZs56,57,58, which in some cases employ a placement of synaptic vesicles around the perimeter of Ca2+-channel clusters9. Thus, it seems possible that similar mechanisms are used in these presynaptic preparations, even though IHCs make use of a different set of proteins for the release of synaptic vesicles59. Our Ca2+-imaging data illustrates how disruption of bassoon disintegrates this sophisticated supramolecular machinery at the AZ in a manner reminiscent of what was seen at drosophila neuromuscular junctions upon mutation of the scaffold bruchpilot60. In addition, our study validated the previously assumed presence of extrasynaptic channels in IHCs8,20,24, which form a considerable fraction of 20–50%. In CNS AZs, a subdivision into smaller clusters has been described, with a 1:1 relationship between the number of Ca2+-channel clusters and the number of vesicular release sites13. Future analysis, e.g., employing MINFLUX microscopy61 or electron microscopy of immunolabeled SDS-replica9, will be required to test such a scenario for IHCs. Interestingly, despite the different complement of Ca2+ channels per AZ, the number of individual channels per release site appears comparable: nine channels/site reported in parallel fiber synapses13 vs. 80–120 channels for 10–15 release sites62 at IHC AZs.

Our study also shows, through theoretical modeling and direct [Ca2+] measurements, that insufficient spatial resolution causes artificially low estimates of AZ [Ca2+], because “spatial averaging” conflates the true [Ca2+] levels directly at the AZ with lower-[Ca2+] regions further from the Ca2+-influx sites. By establishing fluorescence lifetime Ca2+ imaging at confocal and 2D-STED resolution, we indeed saw higher (average) peak AZ [Ca2+] using 2D-STED (15–20 µM) compared to confocal microscopy (10–15 µM). We saw a further increase when additionally restricting the focal volume within the cell (by focusing slightly below the AZ membrane) up to 25 µM (average) with peak values up to 50 µM. Further refinement of the technique by application of 3D-STED microscopy can be expected to lead to more precise measurements of [Ca2+] in the immediate proximity of the Ca2+-channel cluster. We note, however, that functional 3D-STED imaging in living tissue faces challenges, such as the tissue-induced aberrations distorting both STED donuts in a different fashion, higher required laser powers, as well as the seemingly trivial problem of locating Ca2+-indicator hotspots with the reduced PSF size. Furthermore, we believe the comparatively modest increase in [Ca2+] measured with STED shows that our STED-efficiency correction is causing us to further underestimate [Ca2+]: the lower STED efficiency for the Ca2+-unbound dye means we are sampling the Ca2+-free dye from a much larger volume than the Ca2+-bound dye. So even if the focal volume of the bound dye is contained within the immediate AZ, the focal volume of the free dye might stretch considerably farther, encompassing more areas with lower [Ca2+] (and thus more free dye). Our STED-efficiency correction, however, is based on measurements within a homogeneous distribution of bound/unbound dye. This effect could be accounted for by either significantly increasing the spatial resolution or by considering the physical dimensions of the AZ when correcting.

In summary, using novel approaches we present an in-depth quantification of presynaptic Ca2+ signaling using the hair cell AZ as a model system. We propose that IHCs vary the strength of their AZs primarily by scaling the length of the ribbons, presynaptic densities, and Ca2+-channel clusters.

Methods

Animals

C57B6/N mice and mice carrying a deletion of exons 4 and 5 of the bassoon gene (BsnΔEx4/5)38 were used at the age of postnatal day 26 (P26) to P33 (for optical fluctuation analysis) or P15 to P18 (for all other experiments). Both male and female mice were used. All experiments complied with German national animal care guidelines and the guidelines issued by the University Medical Center Göttingen.


Immunohistochemistry

Freshly dissected apical cochlear turns were fixed in methanol for 20 min at −20 °C. Thereafter, the tissue was washed three times for 10 min in PBS and incubated for 1 h in goat serum dilution buffer (GSDB) (16% normal goat serum, 450 mM NaCl, 0.3% Triton X-100, and 20 mM phosphate buffer, pH 7.4) in a wet chamber at room temperature. Primary antibodies were diluted in GSDB and applied overnight at 4 °C in a wet chamber. After washing three times for 10 min (wash buffer: 450 mM NaCl, 20 mM phosphate buffer, and 0.3% Triton X-100), the tissue was incubated with secondary antibodies in GSDB in a wet light-protected chamber for 1 h at room temperature. Then, the preparations were washed three times for 10 min in wash buffer and one time for 10 min in 5 mM phosphate buffer, placed onto the glass microscope slides with a drop of fluorescence mounting medium (Mowiol), and covered with thin glass coverslips. The following antibodies were used: mouse anti-Sap7f407 to bassoon (1:600, Abcam ab82958), rabbit anti-CaV1.3 (1:75, Alomone Labs ACC-005), STAR 580-tagged goat-anti-rabbit or goat-anti-mouse (1:200, Abberior 2-0002-005-1 or 2-0012-005-8), and STAR 635P-tagged goat-anti-mouse or goat-anti-rabbit (1:200, Abberior 2-0002-007-5 or 2-0012-007-2). 2D- and 3D-STED immunofluorescence images were acquired on an Abberior Instruments Expert Line 775 nm 2-color STED microscope, with excitation lasers at 561 nm and 633 nm and a STED laser at 775 nm, 1.2 W, using a 1.4 NA 100× oil immersion objective. Images were acquired with pixel sizes of 20 × 20 nm (2D-STED) or 40 × 40 × 40 nm (3D-STED). Volumetric display of 3D stacks was performed using the software Imaris (Bitplane, Zurich, Switzerland). Images were analyzed using Igor Pro 6 software (Wavemetrics, Lake Oswego, OR, USA).


Patch-clamp recordings

IHCs from apical coils of freshly dissected organs of Corti were patch-clamped as described previously19. The pipette solution contained (in mM): for recordings with EGTA-mediated suppression of Ca2+ influx at individual synapses (“EGTA”): (123 Cs-glutamate, 1 MgCl2, 1 CaCl2, 10 EGTA, 13 tetraethylammonium (TEA)-Cl, 20 HEPES, 2 Mg-ATP, 0.3 Na-GTP, 0.8 Fluo-8FF (AAT Bioquest), and the TAMRA-conjugated CtBP2/RIBEYE-binding dimer peptide (20 µM, Biosynthan, Berlin, Germany) (pH 7.3); for fluorescence fluctuation analysis (“FA”): 92 Cs-glutamate, 13 TEA-Cl, 20 CsOH-Hepes, 1 MgCl2, 2 Mg-ATP, 0.3 Na-GTP, 10 EGTA, 10 Phosphocreatine-Na, 8 CsCl, and 1 Fluo-4FF (penta-K+ salt; Invitrogen) (pH 7.2); for STED Ca2+ imaging (“STED”): 130 Cs-gluconate, 10 TEA-Cl, 10 4-Aminopyridine (4-AP), 10 CsOH-HEPES, 1 MgCl2, 2 Mg-ATP, 0.3 Na-GTP, as well as either 0.025 OGB-5N, 0.8 EGTA, and 0.4 BAPTA (for “physiological” buffering conditions) or 0.3 OGB-5N and 10 EGTA (for “intensified” conditions) (pH 7.2). The extracellular solution contained: for “EGTA”: 102.2 NaCl, 2.8 KCl, 1 MgCl2, 5 CaCl2, 35 TEA-Cl, 10 HEPES; 2 g l−1 glucose (pH 7.2); for “FA”: 95 NaCl, 35 TEA-Cl, 2.8 KCl, 10 CaCl2, 0.005 BayK8644, 1 MgCl2, 1 CsCl, 10 NaOH-HEPES, and 10 D-glucose (pH 7.3); for “STED”: 35 TEA-Cl, 2.8 KCl, 1 MgCl2, 5 4-AP, 1 CsCl, 10 NaOH-HEPES, 10 D-glucose, as well as either 107.7 NaCl and 1.3 CaCl2 (“physiological”) or 99 NaCl and 10 CaCl2 (“intensified”) (pH 7.2). EPC-9 or -10 amplifiers controlled by Patchmaster or Pulse software (HEKA Elektronik, Lambrecht, Germany) were used for measurements. All voltages were corrected for liquid junction potentials (calculated). Currents were low-pass filtered at 5 kHz and sampled at 20 or 40 kHz, except for fluctuation analysis measurements, where currents were low-pass filtered at 8.5 kHz and sampled at 100 kHz. Ca2+ currents were leak-corrected using a p/n protocol (except for fluorescence lifetime recordings). Cells were patched at a holding potential of −84 to −87 mV.


Confocal Ca2+ imaging for isolation of synaptic Ca2+ current

Experiments were performed with a custom-built spinning disk confocal microscope. A Zeiss Axio Examiner microscope (Carl Zeiss Microscopy GmbH, Göttingen, Germany) was equipped with a spinning disk scanner (CSU22, Yokogawa Electric Corporation, Tokyo, Japan), a scientific CMOS camera (Neo, Andor Technology, Belfast, UK), and a Zeiss 63× water immersion objective (1.0 NA) mounted on a fast piezoelectric focus drive (MIPOS 100 PL, Piezosystem Jena, Germany). The fluorescent Ca2+ indicator and ribbon-labeling peptide were excited with a 491-nm diode-pump solid-state laser (Calypso, Cobolt AB, Solna, Sweden), and a 561 nm diode-pumped solid-state laser (Jive, Cobolt AB), respectively. Images were acquired at 5 ms/frame and processed with the software Andor Solis (Andor Technology). After the formation of the ruptured-patch configuration, the Ca2+ indicator was loaded into the cell for at least 4 min to reach a steady-state concentration. Data were analyzed using Igor Pro 6. Nine pre-depolarization frames were averaged to obtain the background fluorescence (F0); for the calculation of ΔF/F0, the central pixel of a background-subtracted depolarization-evoked Ca2+ hotspot and its eight neighbors were averaged and divided by the corresponding values from the F0 frame.

Neighboring AZs found within ±1 µm focal distance to the targeted AZ were monitored for changes in fluorescence during application of EGTA (Supplementary Fig. 2a). We found that some neighboring AZs were slightly affected by the application of EGTA and quantified this by fitting a line to the ΔF/F0 data for the time of the recording during which the iontophoresis occurred and noting the final ΔF/F0 value at the end of the fit. The final value of the targeted AZ was then divided by the sum of all values (targeted as well as neighboring AZs) to obtain the fractional contribution of the targeted AZ (rtarget) to the total change in Ca2+ current (ΔICa), and the Ca2+ current at the target synapse was obtained according to

$$\Delta I_{{\mathrm{Ca}}}^\prime = \Delta I_{{\mathrm{Ca}}} \cdot r_{{\mathrm{target}}}.$$
(1)

Optical fluctuation analysis of synaptic Ca2+ influx

Ca2+ imaging used a Fluoview 300 confocal scanner mounted on an upright microscope (BX50WI, Olympus, Tokyo, Japan) equipped with a 60× water immersion objective (0.9 NA) and a fiber-based (Picoquant) detection by a single-photon counting avalanche photo-diode (Perkin Elmer) read-out by custom hardware and software. The fluorescent Ca2+ indicator and ribbon-labeling peptide were excited with a 50 mW, 488 nm solid-state laser (Cyan, Newport-Spectraphysics, Santa Clara, CA, USA) and a 1.5 mW, 543 nm He–Ne laser, respectively. Fluorescent hotspots were identified during 200 ms depolarizations to −7 mV in xy-scans at ≈10 Hz (using 0.5% of maximum laser intensity [488 nm]) and further characterized using spot detection (“point scan” mode of the confocal scanner, centered on the center of the fluorescent hotspot, using 0.05% of maximum laser intensity [488 nm]) with detection by the single-photon counting avalanche photo-diode at 2 kHz. To elicit Ca2+-tail currents, cells were depolarized to +53 mV for 5 ms (opening Ca2+ channels, but preventing Ca2+ influx due to lack of driving force) and then repolarized to −67 mV. After recording fluorescence and whole-cell currents during ensembles of K = 200 tail currents, trial-to-trial variance was calculated as

$$\sigma ^2\left( t \right) = \frac{1}{{2\left( {K - 1} \right)}}\mathop {\sum}\nolimits_{i = 1}^{K - 1} {\left[ {x_i\left( t \right) - x_{i + 1}\left( t \right)} \right]^2}.$$
(2)

Fluorescence data was subsampled to 667 Hz to avoid the impact of correlation among neighboring data points63. After subtraction of baseline variance (shot noise and detector noise), variance of Ca2+-indicator fluorescence was plotted against mean fluorescence and fitted with a parabolic function

$${\rm var} = f_{\mathrm{s}} \cdot S_{{\mathrm{mean}}} - \frac{{S_{{\mathrm{mean}}}^2}}{N},$$
(3)

with fs being the contribution by a single open Ca2+ channel (fluorescence increase or single-channel current), Smean being the average signal (mean fluorescence or current) of all trials at a single time point, and N being the number of Ca2+ channels at the synapse (fluorescence data) or in the entire cell (whole cell currents). Curve fitting used weighting according to the error-covariance of the variance (estimated generalized least squares)63. An equivalent analysis was performed on the whole-cell current to estimate the total number of Ca2+ channels per IHC, as described in ref. 22.


Modeling

Diffusion and binding of Ca2+ and buffers at a simulated AZ were modeled with CalC software37 version 6.86 using the parameters given in Table 1. Data were analyzed using Igor Pro 6. Simulation of the effect of the microscope’s PSF was done by convolving both the distribution of Ca2+-bound and -free OGB-5N with Gaussian functions with FWHMs of 64 × 64 × 542 nm (STED) or 243 × 243 × 542 nm (confocal), corresponding to the PSFs of the microscope used in the experiments (Supplementary Fig. 16). The Ca2+ concentration derived from the ratio of Ca2+-bound and -free OGB-5N was calculated as

$$\left[ {{\rm Ca}^{2 + }} \right] = K_{\mathrm{D}} \cdot \frac{{[{\rm OGB-5N}]_{{\mathrm{bound}}}}}{{[{\rm OGB-5N}]_{{\mathrm{free}}}}}.$$
(4)

STED Ca2+ imaging

Super-resolution Ca2+ imaging was performed using a custom-built STED microscope64; the fluorophores were excited with a pulsed 488 nm diode laser (PicoTA, Toptica Photonics, Graefelfing, Germany) and de-excited using a pulsed 595 nm STED beam with a donut-shaped beam profile (Ti:Sapphire laser, Spectra-Physics, Darmstadt, Germany, which was frequency shifted using an optical parametric oscillator, APE, Berlin, Germany). Laser power in the back aperture of the objective lens ranged typically from 1.5 to 15 µW for the excitation and between 10 and 35 mW for the de-excitation, with STED pulse durations between 200 and 300 ps, depending on the power used. When acquiring super-resolution images, the excitation laser intensity was typically increased to maintain comparable signal levels between confocal and STED.

In order to find and image depolarization-evoked synaptic Ca2+ domains, we first needed to locate hotspots of Ca2+ influx, then bring them into the correct focal plane, and finally image them before, during, and after depolarization. We found hotspots of Ca2+ influx by focusing at the basal pole of the patched cell and depolarizing the cell briefly to −14 mV for 78 ms while acquiring xy-frames of 150 × 150 pixels (four frames, depolarization during the 2nd frame, 3 µm × 3 µm, 78 ms per frame) without activation of the STED laser. After identification of a depolarization-evoked Ca2+ hotspot, an xz-scan (±1.5 µm in z, 100 nm step size) was performed through the center of the hotspot to determine the correct focal plane. IHCs were then depolarized 4× for 78 ms each (78 ms inter-depolarization interval) while acquiring frames of 150 × 75 pixels (16 frames, with the depolarization occurring during the 5th, 8th, 11th, and 14th frame, 3 µm × 1.5 µm, 78 ms per frame). Fluorescence was acquired with a Single Photon Avalanche Diode (SPAD detector, PDM series, Micro Photon Devices, Bolzano, Italy) using the TTL counting output of the detector. For the analysis of the spatial extent of the Ca2+ domains in xy-scans, the detector signal was electronically time-gated by diverting the first 450 ps (equaling twice the fluorescence lifetime of unbound OGB-5N) of the signal into a separate detection channel, thereby reducing the contribution of the unbound OGB-5N signal by 80–90%, while only sacrificing 15–20% of the Ca2+-bound OGB-5N signal. Images were acquired with Imspector software (Max-Planck-Innovation, Munich, Germany) and data were analyzed with Igor Pro 6 as follows: the frames acquired during depolarization were averaged and the average background signal was subtracted (calculated from 11 non-depolarization frames, omitting the first one to exclude possible timing, shutter, or vibrational disturbances). The size of the Ca2+ domain was measured by fitting a 2D Gaussian function using a genetic fit algorithm65 to the subset of the frame containing the Ca2+ hotspot.


Measurement of [Ca2+] using fluorescence lifetime recordings

For the analysis of Ca2+ concentration at the synapse by fluorescence lifetime, we established TCSPC. Fluorescence was acquired using the NIM timing output of the SPAD detector with 35 ps timing resolution. The timing of the fluorescence photons was correlated with the excitation pulse at a TCSPC Module (SPC150N, Becker Hickl, Berlin, Germany) and sorted into a histogram of 25 ps time bins. The overall timing resolution of the setup was 110 ps FWHM, determined by measuring the instrument response function (IRF, see section “Fitting procedure and IRF” below and Supplementary Fig. 9a). In xy-scans (Fig. 8), Ca2+ hotspots were scanned with an 8 × 8 pixel matrix in xy in 50 nm steps, recording the fluorescence twice for each pixel: first for one 15 ms frame during a 19-ms depolarization, and then for two frames at rest (15 ms each), 330 ms after the initial depolarization. In xz-scans (Fig. 9b–d), hotspots were scanned with an 8 × 8 pixel matrix in xz with 50 nm x- and 200 nm z-steps, again recording the fluorescence twice for each pixel: first for one 8 ms frame during a 12-ms depolarization, and then for two frames at rest (8 ms each), 176 ms after the initial depolarization.

To analyze the fluorescence decay, the IRF was iteratively reconvolved with a bi-exponential function and optimized with a fitting routine implemented in Matlab (Mathworks) (Supplementary Fig. 9). The fluorescence lifetimes of free and Ca2+-bound OGB-5N (τfree = 0.23 ns and τbound = 3.24 ns) were determined in saturated ([Ca2+]=90 mM) and desaturated ([Ca2+]=10 nM, using EGTA) Ca2+ conditions (see section “Determination of the lifetime of Ca2+-free and -bound OGB-5N” below) and kept fixed in the analysis of the Ca2+ hotspots. When analyzing lifetime measurements taken with STED, the fitting routine ignored the first 300 ps of the fluorescence decay (during which the STED pulse was active) to avoid artifacts caused by the STED-evoked quenching of the signal. To ensure that this “blanking” of the first 300 ps did not significantly alter the results of the routine, we fitted fluorescence decay traces recorded in confocal mode using both the full data range and the blanked data (Supplementary Fig. 12). Both methods produced highly similar results: the differences in the number of photons assigned to the fast and slow lifetime channel were as small as 0.4%–2.8% for [Ca2+] between 10 nM and 40 µM.

The analysis procedure of STED fluorescence lifetime data is summarized graphically in Fig. 7c–i. First, the ratio of free to Ca2+-bound dye was obtained by first calculating the number of photons F i that were assigned to the fast and slow channels, respectively (F i  = α i  × τ i , with α i the amplitudes from the fitting routine; for STED data, the amplitude extrapolated to the (blanked) onset of the fit was used). Then the photon count of the Ca2+-bound dye was downscaled by a brightness factor of b = 28.02 (see section “Estimation of Fmax, Fmin, and the brightness increase factor” below and Supplementary Fig. 10) in order to account for the increased fluorescence when the dye is bound to Ca2+, thereby shifting the perspective from emitted photons per lifetime-channel to the actual ratio of fluorophores per channel. For STED imaging, an additional correction factor is needed to adjust for the lower STED efficiency (i.e., it requires a higher saturation intensity Isat) of the quenched, Ca2+-free dye with the short fluorescence lifetime. Less STED efficiency corresponds to a larger recorded focal volume, which would otherwise overestimate the Ca2+-free component. Therefore, the STED efficiency correction factor depends on the STED beam power and was determined by measuring the fluorescence depletion of the STED beam at different powers for OGB-5N dye solutions that were saturated with Ca2+ and Ca2+-free (see section “STED efficiency correction” below and Supplementary Fig. 11). The photon count of the Ca2+-free dye was typically downscaled by s = 0.491 or s = 0.424 (depending on STED beam power). Further corrections were necessary for recordings taken in live IHCs. As opposed to in vitro calibrations, where the percentage of Ca2+-bound/-free dye was measured to be <1% in a Ca2+-depleted/-saturated environment, in live IHCs the long-lifetime component of the signal (i.e., the Ca2+-bound dye) neither dropped below 2% for confocal and 4% for STED measurements (even in Ca2+-depleted cells that were patched with 10 mM EGTA in the pipette) nor did it rise above 60% (even in Ca2+-saturated cells patched with 60 mM Ca2+ in the pipette; Supplementary Fig. 13). We devised two separate approaches to correct for this: one by rescaling the results to accommodate the diminished dynamic range of the Ca2+ dye in cells, and one by adding a Ca2+-unresponsive dye fraction to our model system and deriving modified equations for calculating the Ca2+-bound/-free ratio of Ca2+-dependent dye (see Supplementary Methods).

According to the first method, we rescaled the fraction of the photon counts assigned to the Ca2+-bound and -free states of OGB-5N, respectively, by first calculating the corrected fraction rB of Ca2+-bound and rU of Ca2+-free OGB-5N as

$$r_{\mathrm{B}} = \frac{{F_{\mathrm{B}}/b}}{{F_{\mathrm{B}}/b + F_{\mathrm{U}} \cdot s}}$$
(5)

and

$$r_U = \frac{{F_{\mathrm{U}} \cdot s}}{{F_{\mathrm{B}}/b + F_{\mathrm{U}} \cdot s}},$$
(6)

with FB and FU the unmodified photon count assigned to the Ca2+-bound and -free (unbound) dye, respectively, b the brightness factor of 28.02 (describing the higher extinction coefficient and quantum yield of the Ca2+-bound OGB-5N), and s the STED correction factor of 1 (for confocal) or 0.424–0.491 (for STED, depending on STED beam intensity, describing the difference in effective focal volume for Ca2+-bound and -free dye). We then further scaled these ratios according to the minimal and maximal fraction of Ca2+-bound OGB-5N (Supplementary Fig. 13) as

$$r{\prime}_{\mathrm{B}} = \frac{{r_{\mathrm{B}} - r_{{\mathrm{min}}}}}{R}$$
(7)

and

$$r{\prime}_{\rm U} = \frac{{r_{\mathrm{U}} - (1 - r_{{\mathrm{max}}})}}{R},$$
(8)

with rmin(=rmin,bound) and rmax(=rmax,bound) the minimum and maximum fractions of photons assigned to the Ca2+-bound dye in Ca2+-free and Ca2+-saturated conditions, respectively, (rmin = 0.02 or rmin = 0.04 for confocal and STED, respectively, rmax = 0.6), and R = rmax − rmin the dynamic range of the dye.

The ratio of Ca2+-bound to free OGB-5N was then calculated as

$$\frac{{[{\rm OGB\text{-}5N}_{{\mathrm{bound}}}]}}{{[{\rm OGB\text{-}5N}_{{\mathrm{free}}}]}} = \frac{{r{\prime}_{\mathrm{B}}}}{{r{\prime}_{\mathrm{U}}}}.$$
(9)

Ca2+ concentrations for each pixel were calculated using

$$\left[ {{\rm Ca}^{2 + }} \right] = K_{{\mathrm{eff}}} \cdot \frac{{[{\rm OGB\text{-}5N}_{{\mathrm{bound}}}]}}{{[{\rm OGB\text{-}5N}_{{\mathrm{free}}}]}},$$
(10)

with Keff = 195 µM being the effective dissociation constant (KD) we had measured for OGB-5N in intracellular solution (Supplementary Fig. 14b).

Alternatively, if a Ca2+-insensitive dye fraction is assumed to be present in IHCs, [Ca2+] can be calculated according to a modified equation, which is less reliant on the more difficult to determine fast dye component (see below for a detailed description):

$$\left[ {{\rm Ca}^{2 + }} \right] = K_{{\mathrm{eff}}} \cdot \frac{{F_{{\mathrm{B}},{\mathrm{stim}}} - F_{{\mathrm{B}},{\mathrm{rest}}}}}{{F_{{\mathrm{U}},{\mathrm{rest}}} \cdot b \cdot s \cdot R - (F_{{\mathrm{B}},{\mathrm{stim}}} - F_{{\mathrm{B}},{\mathrm{rest}}})}}.$$
(11)

Here, FB,(stim/rest) and FU,(stim/rest) are the observed photon counts (during depolarization [stim] or at rest), which were assigned by the fitting routine to the slow (Ca2+-bound) and fast (Ca2+-free) states, respectively. Again, Keff is the effective KD of OGB-5N in intracellular solution, b is the brightness factor, s the STED correction factor, and R = rmax − rmin the dynamic range of the dye. Assuming a uniform [OGB-5N] and [Ca2+] inside the cell in resting condition, FU,rest was taken as the average of the 8 × 8 pixel frame for xy-raster scans to minimize noise. For xz-scans, where FU,rest decreases with z, no averaging was performed and individual pixel values were used. Comparison of this method with the first method of scaled lifetime ratios showed good agreement between the results (Supplementary Fig. 15).


Determination of the lifetime of Ca2+-free and -bound OGB-5N

In order to determine the lifetime of OGB-5N in the Ca2+-free and Ca2+-bound states, we prepared diluted solutions containing OGB-5N, Ca2+ ions, and Ca2+ buffer (non-fluorescent Ca2+ chelators) with various free [Ca2+]. We also verified the lifetime values in solutions that matched the used intracellular solutions for patch-clamping as close as possible.

We recorded each solution at various excitation powers for durations in excess of 9000 ms, with pixel dwell times of 25 ps, for 1024 pixels in total, therefore spanning a time of 25.6 ns, although due to triggering requirements of the single-photon detection module the actual time during which signal was recorded amounted to 11.5 ns. The data was read into the Matlab fit routine, which fitted a single-exponential curve convolved with the IRF to the recorded data (Supplementary Fig. 9).

The fluorescence signal was fitted between bins 450 and 850, corresponding to 11.2–21.2 ns, hence spanning a 10 ns interval. The onset of fluorescence (corresponding also to the IRF) was at around 12.2 ns and the recorded signal was fitted from 1 ns before onset of fluorescence until 9 ns after. The threshold for considering a pixel was set to 18 counts, the “shift” parameter, denoting the shift between the IRF and the recorded fluorescence signal, was typically left floating, but was consistently determined to be ~20 ps ± 15 ps (so the duration of one bin).

The lifetime values for Ca2+-free and Ca2+-bound OGB-5N (Supplementary Fig. 9) were identical for both the diluted and the intracellular-like solutions, and resulted in values of

$$\tau _{{\mathrm{bound}}} = 3.24\,{\mathrm{ns}} \pm 0.03\,{\mathrm{ns}},$$$$\tau _{{\mathrm{free}}} = 0.23\,{\mathrm{ns}} \pm 0.03\,{\mathrm{ns}}.$$

These lifetime values were used for the entirety of the bi-exponential fit procedures, where they were held constant, leaving only the two amplitude parameters floating freely.


Fitting procedure and IRF

When fitting a fluorescence decay curve recorded with STED, the fitting process needed to be modified to minimize the impact of STED de-excitation. The STED pulses were between 200 and 400 ps long (depending on the power, in typical recording conditions 200–300 ps) and started about 100 ps before the excitation pulse arrived. During the 300 ps in which the STED beam de-excites the fluorophores, a temporary, albeit steep, drop in apparent fluorescence lifetime is visible, which ceases after the end of the STED pulse. In order to avoid misinterpreting this additional short lifetime component as unbound OGB-5N, we omitted (“blanked”) the first 300 ps from the fitting procedure and only included the subsequent bins in the fit (Supplementary Fig. 12), i.e., we fitted from 12.75 to 21.25 ns. Despite omitting a significant portion (~50%) of fluorescence from the unbound dye, the “blanked” fitting method proved to be very robust: when imaging calibration solutions in vitro, the blanked fit results from the STED recordings matched the values obtained from the confocal recordings to a very high degree, at least for unbound dye ratios of <40% (Supplementary Fig. 15b) and the omission resulted in only minor errors of 0.4–2.8% (Supplementary Fig. 12e). Additionally, we tested the blanking robustness by fitting experimental data from IHCs recorded without STED using both the full and the blanked data range, resulting in an average [Ca2+] error of 2–3% (Supplementary Fig. 12c, d).

One other parameter that needed to be handled differently when recording with STED was the shift between IRF and fluorescence data, which was (for confocal data sets) determined by the fit automatically. However, as the initial onset of fluorescence was omitted from our fitting range, the algorithm had difficulty determining the shift accurately. Therefore, the shift parameter was first automatically determined in the standard range (from bins 450–850), then locked down as a fixed parameter for the actual fit of the STED data with the aforementioned truncated boundaries.


STED efficiency correction

The Ca2+-indicator OGB-5N exists in two distinct states: Ca2+-bound or Ca2+-free, which display different STED efficiencies (or: saturation intensities). This is mainly due to the fact that the lifetime of the unbound state is extremely short, of the same order of magnitude as the STED pulse itself. Therefore, the STED beam has little time to effectively de-excite the dye before it spontaneously fluoresces. Different STED efficiencies correspond to different effective focal areas achieved using the same STED beam power. More STED-efficient dyes are switched off better and show a much smaller focal area and thus higher spatial resolution. Since the resolution along the optical axis is unchanged by the 2D-STED donut, this corresponds to a smaller “effective focal volume”, meaning that in the same recording, we will be sampling a higher volume of Ca2+-free dye than of Ca2+-bound dye. For quantitative measurements, we need to compare the amount of Ca2+-bound to Ca2+-free dye, so we need to correct for any differences in sampling volume.

Assuming a homogenous dye distribution (on the scale of the focal area), we can say that the number of fluorophores in solution is proportional to the (sampled) volume. Assuming linear responses from each dye component, the number of recorded photons will depend on the number of fluorophores in the sampled volume and in consequence on the volume and focal area.

To correct for different STED efficiencies, we measured OGB-5N dye solutions, either Ca2+-bound or Ca2+-free, for different STED powers, including zero STED power, i.e., a pure confocal recording. For each STED power, we counted the number of photons emitted from the dye (keeping the excitation power and dye concentration constant) and plotted the ratio of deactivated dye against the STED power. Note the much steeper descent of the Ca2+-bound dye as opposed to relatively gentle decline of the Ca2+-free dye (Supplementary Fig. 11e). In order to correct for different sample volumes for different STED powers, we calculated the ratio of the remaining activated fluorophores. With this factor, dubbed the “STED efficiency correction” s, we reduced the number of recorded photons in the fast (unbound) channel by the factor of effective focal volumes.

To validate this correction factor, we measured [Ca2+] using the lifetime method at different STED powers. Without applying the STED efficiency correction factor, we got discordant results. When correcting with the factor, however, the resulting ratio of bound dye matches for all the used STED powers, as well as for the confocal powers (i.e., zero STED power). This held true for the range of bound dye (<40%), as encountered in the IHC experiments. When confronted with higher fractions of bound dye, additional considerations during evaluation need to be taken to correctly discern the diminishing amount of photons in the fast (unbound) channel amidst the increasing number of photons emitted from the bound dye.


Estimation of Fmax, Fmin, and the brightness increase factor

The brightness factor describes how many more photons are emitted from the bound dye, as opposed to the free dye, for the same amount of incoming light. The different brightness depends both on the extinction coefficient, i.e., the number of photons that are absorbed from a certain amount of incoming light, as well as on the quantum yield, referring to the fraction of excited dye molecules that go on to emit a fluorescence photon instead of decaying non-radiatively. The extinction coefficient can be observed in fluorescence decay curves as different peak heights, whereas the quantum yield is proportional to the inverse lifetime of the dye and can be seen as longer lifetimes of the decay. The brightness factor can be calculated either by measuring the amount of photons directly, or by measuring the relative quantum yield and the relative extinction factors separately. For all the following measurements, we recorded the fluorescence decay of OGB-5N in solutions containing identical amounts of dye, which were either saturated with Ca2+ (>8 mM) or devoid of Ca2+ (~10 nM).

The difference in quantum yield between both states is comparatively easy to measure and can be calculated directly from the ratio of fluorescence lifetimes in the bound and free states (see Supplementary Fig. 9):

$$\frac{{\tau _{{\mathrm{bound}}}}}{{\tau _{{\mathrm{free}}}}} = \frac{{3.24\,{\rm ns}}}{{0.23\,{\rm ns}}} = 14.1.$$
(12)

The ratio of extinction factors proved to be more challenging to measure (as has been observed previously36,40), probably in part due to the difficulty of obtaining identical concentrations of Ca2+-bound and Ca2+-free OGB-5N, as well as slight fluctuations in excitation laser power. Using our fitting algorithm, we extracted a peak height ratio (i.e., amplitude ratio) of bound to unbound dye of

$$\frac{{\alpha _{{\mathrm{bound}}}}}{{\alpha _{{\mathrm{free}}}}} = 1.99 \pm 0.12.$$
(13)

Combined with the above lifetime ratio, this results in a brightness ratio of

$$b = \frac{{\sigma _{\mathrm{B}}}}{{\sigma _{\mathrm{U}}}} = \frac{{{\mathrm{\alpha }}_{\mathrm{B}}\tau _{\mathrm{B}}}}{{\alpha _{\mathrm{U}}\tau _{\mathrm{U}}}} = 28.03.$$
(14)

We additionally measured the brightness ratio directly, by recording fluorescence decay curves for Ca2+-saturated and -“free” solutions at different excitation powers and directly comparing the recorded photons. This was repeated over and over, so as to be able to exclude strongly deviating measurements and resulted in a brightness factor of (Supplementary Fig. 10)

$$b = \frac{{\sigma _{\mathrm{B}}}}{{\sigma _{\mathrm{U}}}} = 28 \pm 3.$$
(15)

Both methods produced comparable results, albeit with a notable error. It is possible that the brightness factor in an ex vivo environment would deviate from these values, due to different dye behavior. Due to the difficulty of the involved experiments, this could not be measured directly, however.


In vitro determination of Keff, the effective KD of OGB-5N

The measured dissociation constant KD of a dye may be influenced by other Ca2+-binding factors, such as those present in the intracellular solution used in our patch-clamp experiments. Therefore, for our purposes, we refer to our measured KD as Keff to indicate that this does not represent the behavior of the pure dye. In order to calculate the effective dissociation constant Keff of the dye OGB-5N in an environment as close to the cellular surrounding as possible, we prepared solutions with different values of [Ca2+], ranging from nearly Ca2+-free (10 nM) to Ca2+-saturated (80 mM), with the highest number of different solutions near to the expected KD values between 20 and 200 µM. The solutions matched the intracellular solutions used for patch-clamping exactly, except for the amount of added Ca2+ and buffer. For each solution, we recorded various fluorescence decay curves, both for various excitation powers as well as for different STED powers. Free [Ca2+] was calculated using the software Patcher’s Power Tools in Igor pro.

We determined the Keff by plotting the photon counts Fslow in the slow channel (as determined by the fitting routine) against the calculated free [Ca2+] in the solution (Supplementary Fig. 14b). This curve was then fitted with

$$F_{{\mathrm{slow}}} = F_{{\mathrm{slow,max}}} \cdot \frac{{\left[ {{\rm Ca}^{2 + }} \right]}}{{\left[ {{\rm Ca}^{2+}} \right] + K_{{\mathrm{eff}}}}},$$
(16)

With Fslow,max the maximum number of counts recorded in the slow channel. The resulting values of Keff = 194.3 ± 23.7 μM or Keff = 195.7 ± 24.8 μM for confocal and STED data, respectively, were about six-fold higher than the KD we measured in diluted solution (Supplementary Fig. 13a) and as published in literature36.


Statistical analysis and presentation

Significance testing was performed using two-tailed tests, either Student’s T-test or the Mann–Whitney U test, as indicated. Statistical power was calculated post hoc using the software G*power66 with an α error probability of 0.05. When calculating the power for Mann–Whitney U tests, normal distributions were assumed and the asymptotic relative efficiency method was used. No statistical method was used to estimate sample size and no randomization or blinding was performed. Where box plots are presented, boxes indicate 25–75 percentile, whiskers 10–90, and the medians are indicated by the horizontal lines. Individual data points are marked by crosses. Averages are presented as ± standard error of the mean (SEM).


Data availability

The data supporting the findings of this study are available from the corresponding authors upon request. The CALC scripts of the Ca2+ reaction/diffusion modeling at IHC AZs can be obtained from www.innerearlab.uni-goettingen.de/materials.html. The Igor Pro and Matlab code is available from the corresponding authors upon request.

Additional information

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Acknowledgements

This work was supported by grants of the German Research Foundation: Collaborative Research Center 889 (to project B7 to K.I.W. and project A2 to T.M.), DFG Research Center and Cluster of Excellence, Center for Nanoscale Microscopy and Molecular Physiology of the Brain (FZT-103) to K.I.W., S.W.H., and T.M., and the Leibniz program (to T.M.) as well as by the German Federal Ministry of Education and Research (Bernstein Focus for Neurotechnology 01GQ0810 to T.M. and Alexander Egner and Bernstein Center for Computational Neuroscience 01GQ1005A to T.M.). T.L.O. was supported by a fellowship of the DAAD. We thank Drs. William Roberts and Murat Alp for sharing information on Ca2+-indicator properties. We thank Drs. David DiGregorio, Valentin Nägerl, Alexander Egner, Benjamin Harke, Mark Rutherford, and Tina Pangršič for participation in the early phase of experiments, Dr. Guiseppe Vicidomini for providing the code for the lifetime fitting routine, Drs. Gerald Donnert and Christian Wurm of Abberior Instruments for providing access to a STED microscope for morphological analysis, and C. Senger-Freitag and S. Gerke for expert technical assistance. We thank Eckart D. Gundelfinger for providing bassoon mutant mice. We are very grateful to Erwin Neher, Silvio Rizzoli, and Christian Vogl for critical discussion of the data and the manuscript.

Author information

Author notes

    • Thomas Frank

    Present address: Friedrich Miescher Institute for Biomedical Research, 4058, Basel, Switzerland

  1. Jakob Neef, Nicolai T. Urban and Tzu-Lun Ohn contributed equally to this work.

Affiliations

  1. Institute for Auditory Neuroscience and InnerEarLab, University Medical Center Göttingen, 37099, Göttingen, Germany

    • Jakob Neef
    • , Tzu-Lun Ohn
    • , Thomas Frank
    • , Philippe Jean
    •  & Tobias Moser
  2. Collaborative Research Center 889, University of Göttingen, 37075 Göttingen, Germany

    • Jakob Neef
    • , Tzu-Lun Ohn
    • , Katrin I. Willig
    •  & Tobias Moser
  3. Bernstein Focus for Neurotechnology, University of Göttingen, 37075 Göttingen, Germany

    • Jakob Neef
    • , Tzu-Lun Ohn
    •  & Tobias Moser
  4. Synaptic Nanophysiology Group, Max Planck Institute for Biophysical Chemistry, 37077, Göttingen, Germany

    • Jakob Neef
    •  & Tobias Moser
  5. Department of Nanobiophotonics, Max Planck Institute for Biophysical Chemistry, 37077, Göttingen, Germany

    • Nicolai T. Urban
    • , Stefan W. Hell
    •  & Katrin I. Willig
  6. Center for Nanoscale Microscopy and Molecular Physiology of the Brain, University Medical Center Göttingen, 37099 Göttingen, Germany

    • Nicolai T. Urban
    • , Stefan W. Hell
    • , Katrin I. Willig
    •  & Tobias Moser
  7. Optical Nanoscopy in Neuroscience, University Medical Center Göttingen, 37099, Göttingen, Germany

    • Katrin I. Willig
  8. Bernstein Center for Computational Neuroscience, University of Göttingen, 37075 Göttingen, Germany

    • Tobias Moser

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Contributions

J.N., N.T.U., T.-L.O., T.F., P.J., S.W.H., K.I.W. and T.M. designed the experiments. J.N. performed immunohistochemistry, and J.N., N.T.U., T.-L.O., T.F. and P.J. performed electrophysiology and Ca2+ imaging. STED and lifetime Ca2+ imaging was performed in the Department of NanoBiophotonics at the Max Planck Institute for Biophysical Chemistry by N.T.U. and J.N. J.N. set up the AZ model. J.N., N.T.U., T.-L.O., T.F., P.J., K.I.W. and T.M. analyzed the data. J.N., N.T.U., T.L.O. and T.M. wrote the manuscript.

Competing interests

S.W.H. owns shares of the company Abberior Instruments GmbH that built one of the STED microscopes used in this study. The remaining authors declare no competing financial interests.

Corresponding authors

Correspondence to Nicolai T. Urban or Katrin I. Willig or Tobias Moser.

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https://doi.org/10.1038/s41467-017-02612-y

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