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Neuronal morphologies built for reliable physiology in a rhythmic motor circuit

  1. Adriane G Otopalik  Is a corresponding author
  2. Jason Pipkin
  3. Eve Marder  Is a corresponding author
  1. Brandeis University, United States
  2. Marine Biological Laboratories, United States
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Cite this article as: eLife 2019;8:e41728 doi: 10.7554/eLife.41728

Abstract

It is often assumed that highly-branched neuronal structures perform compartmentalized computations. However, previously we showed that the Gastric Mill (GM) neuron in the crustacean stomatogastric ganglion (STG) operates like a single electrotonic compartment, despite having thousands of branch points and total cable length >10 mm (Otopalik et al., 2017a; 2017b). Here we show that compact electrotonic architecture is generalizable to other STG neuron types, and that these neurons present direction-insensitive, linear voltage integration, suggesting they pool synaptic inputs across their neuronal structures. We also show, using simulations of 720 cable models spanning a broad range of geometries and passive properties, that compact electrotonus, linear integration, and directional insensitivity in STG neurons arise from their neurite geometries (diameters tapering from 10-20 µm to < 2 µm at their terminal tips). A broad parameter search reveals multiple morphological and biophysical solutions for achieving different degrees of passive electrotonic decrement and computational strategies in the absence of active properties.

https://doi.org/10.7554/eLife.41728.001

Introduction

Neurons often present complex and highly-branched morphologies. How synaptic voltage events propagate within and across neurite branches is determined by the structure’s geometrical and biophysical properties. Passive voltage propagation is influenced by the neurite’s diameter, membrane resistance, and axial resistance (Rall, 1959; Rall, 1960; Rall, 1969; Jack et al., 1975; Holmes, 1989). Rall and colleages were the first to apply passive cable theory and develop the equivalent cylinder model for the study of electrotonus in single dendrites and branched dendritic trees (Rall, 1959; Rall, 1960; Rall, 1969). Schierwagen then devised a broader mathematical description of membrane voltage distributions in complex, highly-branched neurite trees with non-uniform boundary conditions and geometries (Schierwagen, 1989). These seminal theoretical studies have provided an invaluable framework for understanding passive neuronal physiology. However, in a functioning neuron, synaptic inputs, receptors, and ion channels may shunt or amplify propagating voltage signals (London and Häusser, 2005). Thus, the transformation from neuronal morphology to electrophysiological activity patterns is often unpredictable in the absence of direct experimental assessment. To date, measuring voltage attenuation across the many neurite paths presented in complex neuronal structures using electrophysiological techniques has proven difficult. Thus, electrotonus has been experimentally assessed in only a handful of neuron types (for example: Spruston and Johnston, 1992; Spruston et al., 1994; Rapp et al., 1994; Carnevale et al., 1997; Stuart and Spruston, 1998; Chitwood et al., 1999; Jaffe and Carnevale, 1999; Otopalik et al., 2017b; Medan et al., 2018), and this greatly restricts our understanding of the breadth of biophysical organizations utilized in different neuron types and circuit contexts.

In two recent studies, we characterized the morphology (Otopalik et al., 2017a) and passive electrophysiology (Otopalik et al., 2017b) of the identified neurons of the crustacean stomatogastric ganglion (STG), a small central pattern-generating circuit mediating the rhythmic contractions of the animal’s foregut. The 14 identified neurons of the STG present distinct, cell-type-specific electrophysiological waveforms, firing patterns and circuit functions (Harris-Warrick et al., 1992). We quantified numerous morphological features pertaining to the macroscopic branching patterns and fine cable properties of four neuron types (Otopalik et al., 2017a). Interestingly, the four neuron types did not adhere to optimal wiring principles (Cuntz et al., 2010) or Rall’s 3/2 rule (Rall, 1959) and exhibited expansive neurite trees that sum to >10 mm of total cable length, tortuous and long individual branches (ranging between 100 µm and 1 mm in length) and thousands of branch points with complex geometries. There was quantifiable inter-animal variability in many features within neuron types, and no single metric or combination of metrics distinguished the four neuron types.

In a second study, we then asked: How do STG neurons produce reliable firing patterns across animals, given their apparently inefficient and highly variable structures? As a first examination of how neuronal morphology maps to physiology in the STG, we characterized electrotonus, or passive voltage signal propagation, in one STG neuron type, the Gastric Mill (GM) neuron. We were surprised to find that, despite their expansive and complex neuronal structures, GM neurons are relatively electrotonically compact and operate much like single electrical compartments (Otopalik et al., 2017b). We suggested that compact electrotonic structures may effectively counteract the potential physiological consequences of morphological variability observed in GM neurons across animals (Otopalik et al., 2017a; Otopalik et al., 2017b).

We first motivate the present study with an empirical numerical model that measures electrotonus in a library of cable models with varying geometrical and passive properties. In doing so, we recapitulate passive electrotonic decrement described in the aforementioned seminal theoretical studies (Rall, 1959; Rall, 1960; Rall, 1969). Yet, we also show that a subset of cable models with geometries consistent with those observed in multiple STG neuron types (Otopalik et al., 2017a), are relatively resilient to electrotonic decrement. Given this prediction, we asked whether compact electrotonus is a generalizable feature in the STG, and therefore common among multiple, distinct neuron types. Using glutamate photo-uncaging in tandem with intracellular electrophysiology (as in Otopalik et al., 2017b), we measure electrotonus in four STG neuron types. We then investigate how neurite geometry shapes voltage integration in these complex neuronal structures. By complementing these experiments with validating computational simulations, we demonstrate that STG neurite geometries and passive properties are sufficient to account for the compact electrotonus and voltage integration observed in this pattern-generating circuit. Furthermore, our numerical simulations suggest that different neurite geometries may be suitable for circuits that subserve different functions.

Results

Simulating electrotonus in diverse neurites

In previous work, we were surprised to find that STG neurons exhibit neurite lengths as long as 1 mm and neurite diameters between 10–20 µm at their primary neurite junctions, that decrement to <1 µm at their terminating tips (Otopalik et al., 2017a), suggesting geometries with a 1–2% taper. Passive cable theory suggests that voltage signals passively propagating such long distances are likely to undergo a great deal of attenuation (Rall, 1960; Rall, 1964; Rall, 1969; Jack et al., 1975; Schierwagen, 1989). Experimental studies to date have validated predictions presented in these theoretical studies in dendrites with uniform and/or smaller diameters (typically <3 µm; Holmes, 1989; Jaffe and Carnevale, 1999; Stuart and Spruston, 1998). These studies suggested that diameter is a critical parameter in determining electrotonic decrement in the absence of amplifying or shunting mechanisms. Yet, none of these studies examined electrotonus in neurites with the wide diameters exhibited by STG neurites. Thus, we first asked whether there may be a boundary at which a neurite’s diameter is wide enough to overcome distance-dependent attenuation.

We conducted a proof-of-concept computational characterization of electrotonus in a library of 720 passive cable models with a much broader range of geometries (Figure 1A) and passive properties (specific Ra values between 50–300 Ω x cm and specific Rm values between 1,000–20,000 Ω x cm2; see Materials and methods) than explored in earlier studies. These geometries range from narrow cables with uniform diameters (Figure 1A, gray) to broad cables with diameters reminiscent of STG neurites (Figure 1A, blue), thereby spanning the broad range of neurite geometries existing in diverse nervous systems. Electrotonus was characterized by measurement of an effective electrotonic length constant (λeffective in µm; see Materials and methods), which is equivalent to the distance at which a voltage signal decrements to 37% of the maximal voltage amplitude (at the activation site). Thus, greater λeffective values are suggestive of less electrotonic decrement. Figure 1B illustrates the measurement of λeffective in a classic cable model with a uniform diameter of 0.5 µm, Ra = 100 Ω x cm, Rm = 10,000 Ω x cm2. In this case, the voltage event attenuates greatly with distance (λeffective is approximately 300 µm). This voltage attenuation is robust and λeffective is less than 1 mm for a broad range of passive properties (Figure 1C). Altering the morphology of this cable model to reflect the geometry of an STG neurite (Figure 1D) results in a smaller response amplitude at the site of activation (compare maximum amplitudes in Figure 1B and D). However, this is accompanied by a robust increase in λeffective and similar signal amplitudes across the cable. Larger λeffective values are observed for a broad range of passive parameters (Figure 1E). Ra values between 50–150 Ω x cm and Rmvalues > 10,000 Ω x cm2 yield λeffective values greater than 1 mm. Examining the entire morphological and biophysical parameter space (Figure 1—figure supplement 1) demonstrates that a range of λeffective values can be achieved across neurites varying not only in their passive properties, but also in their geometries. Neurites with wide proximal diameters present relatively long λeffective values even in the presence of a large load at the proximal end of the cable (d0), made to mimic a putative shunt imposed by the rest of the neurite tree (Figure 1—figure supplement 2). Importantly, these simulations demonstrate that long λeffective values can be achieved as a consequence of neurite geometry alone, in the absence of voltage-gated ion channels or other amplifying mechanisms that have been implicated in boosting distally-evoked events in other neuron types (Magee and Cook, 2000; Andrasfalvy and Magee, 2001; Smith et al., 2003; Gulledge et al., 2005; Lavzin et al., 2012).

Figure 1 with 2 supplements see all
Electrotonus in cable models with diverse passive properties and geometries.

(A) Illustration of the complete matrix of cable model geometries assessed in the computational simulation. Proximal diameters (d0) ranged between 0.5–20 µm and distal diameters (d1) ranged between 0.5–10 µm, yielding 20 different geometries spanning from fine, uniform-diameter cylinders to immensely tapered cables. Shaded areas indicate geometries consistent with vertebrate neocortical and hippocampal pyramidal neuron dendrites (gray) and neurites of STG neurons (blue). (B) Top: illustration depicting simulated measurement of the effective electrotonic length constant (λeffective) in a classic cable model with a uniform 0.5 µm-diameter (Rm = 10000 Ω*cm2 and Ra = 100 Ω*cm). An inhibitory potential (Erev = −75 mV, 𝜏 = 70 ms, gmax = 10 nS) was evoked at a distal site (gray circle) and recorded (blue traces) at increasing distances from the site of activation (0, 100, 250, 400, 550, 700, 850 µm). Bottom: Plot depicts the amplitude of the evoked inhibitory potential measured at increasing distances from the activation site (at 0 µm; gray dashed line), illustrating electrotonic decrement of propagating voltage signal. λeffective (315 µm) was calculated as the distance (black dashed line) at which the recorded potential was 37% of the maximal amplitude at the activation site (purple dashed line). (C) λeffective for cables with fixed, narrow, uniform diameter (as in B; d0 = d1=0.5 µm) and varying passive properties. λeffective is plotted as a function of axial resistivity (Ra in Ω*cm) for cables with different specific membrane resistivities (Rm in Ω*cm2; plotted in different colors). (D) Top: illustration showing simulated measurement of λeffective (as in B, Top) in a cable model with geometry reminiscent of an STG neurite (d0 = 20 µm, d1 = 0.5 µm) and the same passive properties as the cable examined in B and C. Bottom: Plot depicts the amplitude of the evoked inhibitory potential measured at increasing distances from the activation site (as in B, Bottom; λeffective >1 mm in this case). (E) λeffective for cables with fixed tapering geometry (as in D) and varying passive properties (plotted as in C).

https://doi.org/10.7554/eLife.41728.002

Linking electrotonus and neurite geometry in STG neurons

Characterization of electrotonus in our cable model library suggests that the wide diameters of STG neurites may effectively equalize passive voltage signal propagation. Consistent with this prediction, we recently demonstrated that the Gastric Mill neuron exhibits a relatively uniform electrotonic structure (Otopalik et al., 2017b). To determine if this is a generalizable feature across different STG neuron types, we characterized electrotonus in multiple neurites of three additional STG neuron types: Lateral Pyloric (LP), Ventricular Dilator (VD), and Pyloric Dilator (PD) neurons, while also corroborating our previous findings in GM neurons (N = 5–6 neurons of each type). These four neuron types present equally complex and expansive morphologies, but distinct voltage waveforms and circuit functions (Figure 2). PD, LP, VD, and GM neurons were unambiguously identified by their innervation patterns (Figure 2A) and by matching their intracellular spiking patterns with concurrent extracellular recordings of nerves known to contain their axons (Figure 2B). PD and LP neurons innervate two muscles in the pylorus of the foregut (Figure 2A) and participate in the ongoing, triphasic pyloric rhythm (Figure 2B). PD and LP can both be identified by matching their intracellular firing patterns with spiking units on the lateral ventricular nerve (lvn; Figure 2B). The VD neuron innervates the cv1 muscle of the pylorus and can be identified on the medial ventricular nerve (mvn; Figure 2B). The GM neuron participates in the episodic gastric mill rhythm, innervates gm1, 2, and 3 muscles (Figure 2A), and can be identified on the dorsal gastric nerve (dgn; Figure 2B). When filled with fluorescent dye, each neuron presents highly branched and expansive neurite trees (Figure 2C). The morphological features of these neuron types have been described quantitatively and in detail in previous studies (Wilensky et al., 2003; Bucher et al., 2007; Thuma et al., 2009; Otopalik et al., 2017a). To examine neurite geometries in these four neuron types, we completed volumetric reconstructions and continuous measurement of neurite diameters (from soma to terminating tip) for 23 neurite paths, for which we had confocal image stacks with sufficient resolution. Recapitulating previous work, we observed neurite paths that taper from 10 to 20 µm at the soma-primary neurite junction to <2 µm at terminating tips (Figure 2D–E, Figure 2—figure supplement 12 to Figure 2; Otopalik et al., 2017a). Geometrical taper from proximal to distal end is thought to increase the electrotonic length constant for long neurite paths (Holmes and Rall, 1992). Yet, we found that, while some STG neurites tapered gradually, others presented diameters that decrease in an abrupt step. Previous study has demonstrated that geometrical taper influences action potential shape and velocity (Goldstein and Rall, 1974). But, it is unclear whether this geometrical feature influences the electrotonic decrement of slower inhibitory potentials. Thus, we simulated and measured λeffective (as in Figure 1 and Figure 1—figure supplement 12 to Figure 1) in cables with varying degrees of taper from proximal to distal end (Figure 2—figure supplement 3 to Figure 2, Part A). We ran this simulation in cables with varying proximal diameters (ranging between 1 and 10 µm) and maintained the same 80% reduction in diameter from proximal to distal end (Figure 2—figure supplement 3 to Figure 2, Part B). In brief, we found that cables with a gradual taper presented longer λeffective than those with abrupt step reductions (consistent with Holmes and Rall, 1992). Yet, cables with wide diameters consistent with those measured in STG neurons (Figure 2E), presented λeffective> 1 mm for even abrupt step-reductions in diameter for a range of passive properties (Ravalues < 100 Ω x cm and Rmvalues > 10,000 Ω x cm2). This contrasts with finer cables (tapering from 1 to 2 µm to sub-µm diameters), wherein any step reductions along the path of propagation resulted in λeffective < 0.5 mm.

Figure 2 with 3 supplements see all
Characteristics of four identified STG neuron types.

(A) Bilateral innervation patterns of each neuron type, depicted on one side of the dissected foregut. Axons from the four neuron types project from the STG (top) and project to specific muscle groups (indicated with the same colors). The axonal spiking activity for each of these neurons can be recorded with extracellularly nerve recordings at the circled locations on the mvn, dgn, and lvn nerves. (B) Each neuron type can be identified electrophysiologically by matching intracellular firing patterns with concurrent extracellular recordings of nerves known to contain their axons (as shown in A). (C) Representative z-projections show complex neurite trees for each neuron type acquired at 40x magnification. (D) Left: volumetric reconstruction of soma and a subset of branches in an example PD neuron (inset scale bar 200 µm and black scale ball in reconstruction is 40 µm). Both the full reconstruction (red – used to measure cross-sectional area and infer branch diameter) and skeleton reconstruction (black line – as used to calculate path distance of glutamate photo-uncaging sites to soma in Figure 3 and Supplements to Figure 3) are shown. Right: the diameter of the three branches shown in reconstruction as a function of distance from the soma. (E) Flattened representations of the reconstructed branches from a subset of preparations. The width of the shape at a given distance from the soma is directly proportional to the inferred diameter of the branch at that distance. Top: Scaled linearly-tapered branch (black) for reference with a starting width of 10 µm (at x = 0 µm) distal width of 1 µm (at x = 800 µm). For branches in D (right) and E, cross-sectional area and path distance were calculated for each node in the skeleton. Inferred diameters were calculated by treating the cross-section as if it were circular; in actuality very few, if any, cross-sections were exact circles. To reduce abrupt irregularities in the inferred diameter, the plots displayed here are a running average with a sliding window of three skeletal nodes. For A- E: PD = Pyloric Dilator; LP = Lateral Pyloric; VD = Ventricular Dilator; GM = Gastric Mill; lvn = lateral ventricular nerve; dgn = dorsal gastric nerve; mvn = medial ventricular nerve. For all subfigures: red = PD, orange = LP; light blue = VD; dark blue = GM.

https://doi.org/10.7554/eLife.41728.005

Measuring electrotonus in four STG neuron types

We experimentally assessed passive voltage signal propagation by evoking inhibitory potentials at numerous sites on the neurite tree with focal photo-uncaging of MNI-glutamate and two-electrode current clamp recordings at the soma (as in Otopalik et al., 2017b). Figure 3A shows example traces of evoked inhibitory potentials at six sites on an individual PD neurite. When the somatic membrane potential is at rest (approximately −50 mV) evoked events at the six sites are inhibitory but vary in magnitude. Two-electrode current clamp was used to manipulate the somatic membrane potential (between −40 and −100 mV) and the apparent reversal potentials (Erevs) for events evoked at each site were determined by plotting response amplitude (measured at the soma) as a function of somatic membrane potential (Figure 3B). The x-intercept of the linear fit of these data serves as our measure of the apparent Erev for each site. Across the six sites evaluated in Figure 3A and B, apparent Erevs ranged between −59 and −70 mV.

Figure 3 with 4 supplements see all
Variable response amplitudes and invariant apparent reversal potentials (Erevs) across STG neuronal structures.

(A and B) Glutamate photo-uncaging and measurement of apparent Erevs in a representative PD neurite. (A) Fluorescence images of an Alexa Fluor 488 dye-fill showing the neurite tree at 20x magnification and a single branch at 40x magnification (outlined in blue on the 20x image). Glutamate photo-uncaging sites are indicated with colored circles and corresponding responses (measured at the soma) for each site are shown. At each site, inhibitory events were evoked with a 1 ms, 405 nm laser pulse at a starting somatic membrane potential of −50 mV. (B) Plots showing evoked response amplitude (∆V) as a function of somatic membrane potential (Vm). At each site, glutamate responses were evoked at varying somatic membrane potentials (achieved with two-electrode current clamp). These data were fit with a linear regression (colored lines) and the Erev for each site was calculated as the x-intercept of this fit (values for each site shown on bottom right of each plot). C. Response amplitudes plotted as a function of distance from the somatic recording site for each neuron type. Maximum response amplitudes were measured at −50 mV for individual sites and normalized to the maximum response amplitude within each neuron (−1 is equivalent to the maximum response within individual neurons). There was no quantitative relationship between response amplitude and distance (supported by poorly fit linear regression analyses in Table 1). D. Apparent Erevs for each site were normalized to the mean apparent Erevs within each neuron (one is representative to the mean). Horizontal black lines denote boundaries of ±5% of the mean apparent Erevs and serve as a graphical depiction of the low variance in apparent Erevs within each neuron for sites as far as 800–1000 µm away from the soma. Raw response amplitudes and apparent Erevs for individual sites in individual neurons are shown in Figure 3—figure supplement 14 to Figure 3.

https://doi.org/10.7554/eLife.41728.009

Maximal response amplitudes (as measured at a somatic membrane potential of −50 mV) and apparent Erevs were measured for numerous sites across the neurite trees of each neuron type (for 10–30 distinct sites across the neurite trees of five LP, VD, GM neurons and six PD neurons; Tables 1 and 2). These data are summarized in Figure 3C and D, where maximal response amplitudes and apparent Erevs for individual sites are plotted as a function of distance from the somatic recording site for each neuron. For comparison across multiple neurons, maximal response magnitudes (which varied between 0–4 mV) were normalized to the minimum (always 0 mV) and maximum response amplitudes within each neuron (Figure 3—figure supplement 14 to Figure 3 show raw maximum response amplitudes and apparent Erevs for individual PD, LP, VD, and GM neurons, respectively). Figure 3C shows that, across all neuron types, maximal response amplitudes show no quantitative trend as a function of distance, nor is there any evidence of normalization of response amplitude with distance (such that response amplitudes are uniform across sites). This is reflected in poorly-fit and insignificant linear regressions of these data (Table 1).

Table 1
Linear regression analyses for response amplitudes and apparent reversal potentials (Erevs) as a function of distance from the somatic recording site for sites in individual neurons or pooled by cell type.

The data contributing to these analyses are shown graphically in Figure 3C and D and Figure 3—figure supplement 14 to Figure 3.

https://doi.org/10.7554/eLife.41728.014
Amplitude vs. DistanceApparent Erev vs. Distance
NeuronSitesMSERpSlope (mV/µmMSERpSlope (mV/µm)
PD300.080.057.98E-011.67E-0413.610.174.22E-01-7.23E-03
PD230.15-0.058.38E-01-1.03E-044.66-0.738.43E-05-1.35E-02
PD100.05-0.068.28E-01-1.77E-046.65-0.422.26E-01-1.60E-02
PD230.37-0.472.05E-02-1.56E-0315.13-0.193.88E-01-3.87E-03
PD200.40-0.184.26E-01-6.35E-0417.960.058.50E-011.05E-03
PD230.770.405.18E-022.62E-0332.090.378.55E-021.62E-02
PDMEAN 21.50.30-0.054.94E-015.18E-0511.60-0.293.77E-01-7.91E-03
PDSD6.50.270.293.86E-011.40E-039.790.383.04E-011.16E-02
LP110.140.431.23E-015.87E-0412.09-0.812.67E-03-1.54E-02
LP260.50-0.029.25E-01-1.15E-045.07-0.193.08E-01-4.00E-03
LP250.17-0.154.75E-01-5.56E-0414.18-0.174.16E-01-5.79E-03
LP250.34-0.404.70E-02-1.56E-035.75-0.096.75E-01-2.15E-03
LP240.510.029.30E-017.01E-050.700.555.00E-037.26E-03
LPMEAN 22.20.33-0.025.00E-01-3.15E-0410.16-0.142.81E-01-4.02E-03
LPSD6.30.180.304.22E-018.08E-045.450.482.86E-018.12E-03
VD270.310.057.95E-012.32E-04193.71-0.357.64E-02-4.17E-02
VD190.54-0.533.49E-03-6.51E-0328.63-0.455.57E-02-3.85E-02
VD240.28-0.145.06E-01-2.46E-0441.440.223.16E-015.07E-03
VD150.07-0.203.36E-01-3.28E-0415.74-0.292.97E-01-7.76E-03
VD150.870.354.73E-021.81E-0333.58-0.693.29E-03-5.59E-02
VDMEAN 20.00.42-0.093.38E-01-1.01E-0362.62-0.311.50E-01-2.78E-02
VDSD5.40.310.333.29E-013.19E-0373.870.331.46E-012.54E-02
GM100.04-0.846.83E-04-3.23E-030.56-0.146.93E-01-1.17E-03
GM280.09-0.532.02E-03-8.74E-042.090.311.13E-012.49E-03
GM250.64-0.241.78E-01-1.12E-035.56-0.135.28E-01-2.23E-03
GM200.09-0.413.50E-02-5.76E-0411.760.174.76E-019.37E-03
GM190.03-0.574.56E-03-1.14E-034.03-0.243.26E-01-6.53E-03
GMMEAN20.40.18-0.524.41E-02-1.39E-034.80-0.014.27E-013.85E-04
GMSD6.90.260.227.62E-021.06E-034.330.232.19E-015.97E-03

Figure 3D shows normalized apparent Erevs as a function of distance from the somatic recordings site. For comparison of apparent Erevs evoked at sites on multiple neurons, apparent Erevs were normalized to and plotted as a percent of the mean apparent Erev across sites within each neuron. Horizontal lines denote 0.05, or 5%, above and below the mean Erev. For PD, LP, and GM neurons, there appears to be no substantial hyperpolarization in apparent Erevs with distance from the somatic recording site (this is validated with linear regressions shown in Table 1). Figure 3B shows that GM neurons present exceptionally invariant apparent Erevs across sites on their neurite trees (mean coefficient of variance (CV) within individual GM neurons was 0.04; Table 2). This result is consistent with previous findings (Otopalik et al., 2017b). Likewise, LP, and PD neurons exhibit relatively invariant apparent Erevs (mean CVs were: 0.06, 0.05, and 0.08, respectively; Table 2). It should be noted that a subset of VD neurons shows higher standard deviations and CVs, suggesting heterogeneity of voltage signal propagation across the neuronal structure. Yet, statistical comparison of CVs (ANOVA, [F(3, 17)=1.2 p=0.341]) and mean apparent Erevs (ANOVA, [F(3, 17)=2.29, p=0.1154]) revealed no statistically significant differences across neuron types. This suggests that the four neuron types are similarly electrotonically compact neuronal structures, wherein apparent Erevs typically varied by <10% of the mean within individual neurons. This translates to a range of mean apparent Erev ± 6–8 mV within each individual neuron.

Table 2
Apparent Mean Erevs, standard deviations (SD) and coefficients of variance (CV) for individual neurons and within neuron type.
https://doi.org/10.7554/eLife.41728.015
NeuronSitesBranchesMean Erev (mV)SD (mV)CV
PD306-64.703.800.06
PD234-66.303.200.05
PD103-74.303.000.04
PD234-64.184.050.06
PD204-69.564.350.06
PD234-83.006.220.08
PDMEAN21.54.2-70.344.100.06
LP112-65.726.180.09
LP265-72.822.330.03
LP255-71.873.890.05
LP255-81.674.070.05
LP245-71.873.890.05
LPMEAN22.24.4-72.794.070.05
VD274-76.223.750.05
VD194-80.836.140.08
VD244-83.866.750.08
VD154-74.814.290.06
VD155-77.848.230.11
VDMEAN204.2-78.715.830.08
GM102-62.330.800.01
GM285-74.001.550.02
GM256-74.782.430.03
GM205-75.423.570.05
GM194-65.667.050.11
GMMEAN20.44.4-70.443.080.04

Directional sensitivity and voltage integration in diverse neurites

Next, we examined (i) the directional sensitivity of voltage signal propagation and (ii) how multiple voltage events are integrated in single neurites varying in their geometry and passive properties. We first characterized these two properties in our library of cable models with varying geometries and passive properties. Figure 4 illustrates the measurement of directional sensitivity and summation arithmetic in two cable models: a classic cable model with a narrow diameter (0.5 µm) and a cable model reminiscent of an STG neurite (with an axial diameter tapering from 20 µm to 0.5 µm; as in Figure 1).

Figure 4 with 2 supplements see all
Simulating voltage summation in neurites with diverse passive properties and geometries.

Voltage summation experiments were simulated in NEURON. Inhibitory potentials were evoked at five sites (500, 600, 700, 800, and 900 µm away from the recording electrode) individually or in sequence at 5 Hz in the inward or outward directions relative to the recording site. (A-C) summarizes results from a classic cable model without a tapering geometry, as in Figure 1B. (D-F) summarizes results from a cable model with neurite geometry reminiscent of that observed in STG neurons, as in Figure 1D. (A) Schematic showing a classic cable model simulation for a 0.5 µm, uniform-diameter cable. (B) Simulated traces show consequence of activating individual sites (top) and sequential activation in either direction (below), as depicted by colored arrows in (A). (C) Quantification of directional bias and linearity for 0.5 µm-diameter cables varying in their passive properties. Top: directional bias as a function of specific axial resistivity (Ra in Ω*cm). Directional bias was calculated as inward integral minus the outward integral; positive values suggest an inward bias, whereas negative values suggest an outward bias. Points close to the y = 0 suggest no directional preference. Bottom: Linearity as a function of Ra. Linearity was calculated as the inward integral minus the integral of the arithmetic sum of events evoked at individual sites (as in B, top); positive values suggest supralinear summation, whereas negative values suggest sublinear voltage summation. Points close to the y = 0 suggest linear summation. All plots show data for a range of specific membrane resistivity (Rm in Ω*cm2) values in different colors (indicated in the key below). Data for the full simulation exploring a broad parameter space are shown in Figure 4—figure supplement 1 and 2 to Figure 4. (D) Schematic showing a cable model simulation for a neurite that tapers from 20 µm at the recording end (d0) to 0.5 µm at the distal end (d1). (E) Simulated traces for activation of individual sites (top) and sequential activation in either direction (below), as depicted by colored arrows in D. (F) Directional bias and linearity plotted as a function of Ra and varying Rm values (indicated in key) for a cable with the geometry shown in D. B and E: Rm = 10000 Ω*cm2 and Ra = 100 Ω*cm.

https://doi.org/10.7554/eLife.41728.016

Inhibitory events of equivalent conductance magnitude and kinetics (see Materials and methods) were evoked at 500, 600, 700, 800, and 900 µm from the recording site individually and in sequence (5 Hz) in the inward and outward directions (Figure 4A–D).

Directional bias was calculated as the integral of the inward response minus the integral of the outward response (Figure 4E and F, top). Thus, positive directional biases are indicative of an inward bias in voltage signal propagation (toward the recording electrode) and negative directional biases are indicative of an outward bias in voltage signal propagation. Figure 4E and F illustrate a notable difference in the directional sensitivity of passive voltage propagation in these two cable models; the classic cable model shows a robust inward bias and the STG neurite shows no directional sensitivity. These biases persist across a broad range of passive properties. However, the inward bias in the classic cable model does attenuate with increasing axial resistivity (Ra) and decreasing membrane resistivity (Rm).

The arithmetic of voltage integration was characterized by comparing the combined response to the arithmetic sum of the individual events (example traces depicted in Figure 4C and D, bottom). Integration is described as sublinear, linear, or supralinear if the combined response is less than, equal to, or larger than the predicted arithmetic sum. We calculated the arithmetic, or linearity, of the evoked responses as the integral of the inward response minus the integral of the combined individual responses (Figure 4E and F, bottom). The classic cable presents sublinear integration of inhibitory voltage events. Yet, as the Rm decreases and Ra increases, voltage summation transitions from sublinear to linear. In contrast, the STG neurite presents relatively linear integration across a broad range of passive properties. Examination of directional sensitivity (Figure 4—figure supplement 1) and summation arithmetic in the entire cable library (Figure 4—figure supplement 2) demonstrates that a broad range of computations can arise as a consequence of neurite morphology. Taken together, these simulations predict that STG neurites will present directional insensitivity and near-linear voltage integration if they operate predominantly by passive propagation and in the absence of active properties serving to shunt or amplify voltage signals.

Direction insensitivity in STG neurites

To test for directional bias in voltage signal propagation, sequential voltage events were evoked at multiple sites within the same secondary branches (from tip to primary neurite junction; Figure 5Ai). The integrals of the summed responses for inward and outward activation were measured at the soma (Figure 5Aii). Directional preference for each branch was assessed by plotting the response integrals for the inward and outward directions against each other and comparison with the identity line, which is indicative of direction insensitivity wherein the inward and outward response integrals are equal (Figure 5Aiii). Any branches with points left of the identity line present an inward, or centripetal bias, whereas any points right of the identity line are suggestive of a centrifugal, or outward, bias. Interestingly, all four neuron types show little directional selectivity (this is supported by root-mean-square error values (RMSE) <0.5 mV*s, a measure of goodness-of-fit to the identity line). Example traces and direction selectivity plots for each cell type can be found in Figure 5—figure supplement 14 to Figure 5. Taken together, these results suggest that neurites in each of these four STG neuron types do not exhibit the directional selectivity that has been described in other neuron types (Barlow and Levick, 1965; Euler et al., 2002; London and Häusser, 2005; Branco et al., 2010).

Figure 5 with 4 supplements see all
Directional sensitivity of voltage propagation in four STG neuron types.

(A) (i) 4–6 sites on single secondary neurites were sequentially photo-activated at 5 Hz in the inward (IN) or outward (OUT) directions. The integrals (ii) of these inhibitory summation responses were calculated as the area above the trace (in mV*s) and plotted against each other as shown in (iii). As plotted, any points that lie to the right of the identity line (shaded in blue) show a centripetal, or inward bias, whereas any points that lie to the left of the identity line (shaded in red) show an outward, or centrifugal, bias. Any points near or on the identity line are unbiased (as is the case with the example traces shown in (ii), depicted with the white data point in (iii)). (B) Directional bias plots for numerous branches within neuron type: (i) 19 branches from 6 PD neurons, (ii) 27 branches from 9 LP neurons, (iii) 20 branches from 5 VD neurons, (iv) 22 branches from five neurons. These data were fit to the identity line, and the root-mean-square error (RMSE) boundaries for this fit is plotted in gray lines.

https://doi.org/10.7554/eLife.41728.019

Arithmetic of voltage signal integration

If voltage signal propagation in STG neurons is predominantly shaped by passive properties and tapered neurite geometries, and less so by active biophysical properties, which may shunt or amplify propagating voltage signals, we would expect to observe linear voltage summation as predicted by our simulation (Figure 4 and Figure 4—figure supplement 2). To assess the arithmetic of voltage summation, we calculated the arithmetic sum of responses evoked at individual sites across single neurites (Figure 6Ai–iii; offset by 200 ms to mimic a 5 Hz sequential activation rate). The integrals of the measured response and expected arithmetic sum for a given branch were plotted against each other and compared with the identity line, which is indicative of linear summation, wherein the measured and expected response integrals are equal (Figure 6Aiii). Any branches with points left of the identity line present sublinear summation, whereas any points right of the identity line are suggestive of supralinear summation. Figure 6B shows these plots for more than 20 branches for each neuron type. Across all neuron types, the majority of branches showed linear summation. RMSE values were less than 1.5 mV*s; thus, the measured response integrals were within 1.5 mV*s of the integral expected of linear summation. GM neurons (Figure 6Biv) exhibited particularly uniform linear summation across all branches evaluated and this is reflected in a small RMSE value of 0.32 mV*s. LP branches and PD branches show slightly higher RMSE values (greater than 1 mV*s), perhaps providing some evidence of variable shunting or amplifying mechanisms. Even so, RMSE values less than 2 mV*s across all cell types suggests relatively linear summation across most branches evaluated. Voltage summation arithmetic was similarly linear in the centrifugal direction (consult Figure 5—figure supplement 14 to Figure 5). It should be noted that these experiments were performed in the absence of TTX-sensitive sodium channels, which have been abolished with 10−7 M TTX in the bath.

Arithmetic of voltage propagation in four neuron types.

(A) (i) 4–6 sites spaced 50–100 µm apart on the same secondary neurite were sequentially photo-activated at 5 Hz in the inward (IN) direction. (ii) Raw responses at individual sites from most distal (top) to most proximal (bottom) for one representative PD branch. (iii) Comparison of the inward voltage sum to the arithmetic sum for photo-activation of the individual sites (the traces shown in (ii) were summed with a 200 ms offset). (iv) The integrals (mV*s) of the measured responses were plotted against that of the expected arithmetic sum. This provides a graphical depiction of the linearity of voltage summation for each branch. Points to the left of the identity line suggest sublinear summation, points to the right of the identity line suggest supralinear summation, and points near or on the identity line suggest linear summation. The singular point depicted in (iv) depicts voltage summation for the responses shown in (iii). In this case, the measured voltage had a lesser integral than the arithmetic sum and therefore showed sublinear summation. (B) (i–iv) Plots showing the measured integrals as a function of the expected integral for the arithmetic sum for the inward activation of many branches within the four neuron types: (i) 19 branches from 6 PD neurons, (ii) 27 branches from 9 LP neurons, (iii) 20 branches from 5 VD neurons, (iv) 22 branches from five neurons. These real data were fit to the identity line, and the root-mean-square error (RMSE) boundaries for this fit is plotted in gray lines.

https://doi.org/10.7554/eLife.41728.024

Discussion

Compact computing in STG neurons

In the present study, we find that multiple STG neuron types present electrotonically compact structures and within-neurite voltage summation that is relatively linear and directionally insensitive. Taken together, these findings suggest that STG neurons are built to linearly sum and unify synaptic inputs distributed across their expansive and complex structures, rather than perform distributed computations on a branch-by-branch, or subtree-by-subtree basis. Our computational simulations suggest that this biophysical architecture may be achieved passively and as a simple consequence of neurite geometry in these neurons, which present neurites with wide diameters that taper from 10 to 20 µm near the soma, to sub-micron diameters at their terminating tips.

This computing strategy stands in contrast to that which has been observed in other neuron types with similarly complex neuronal structures. When voltage signals propagate long distances in the absence of amplifying mechanisms, electrotonic decrement is thought to result in sublinear voltage integration and directional bias within single branches (Rall, 1964; Gulledge et al., 2005; London and Häusser, 2005). This has been demonstrated experimentally in a variety of vertebrate neuron types in different circuit contexts, from cortex to retina (Barlow and Levick, 1965; Cash and Yuste, 1998; Euler et al., 2002; Poirazi et al., 2003; Polsky et al., 2004; Branco et al., 2010). Linear and supralinear integration are thought to require amplifying mechanisms, such as voltage-gated ion channels or distance-dependent scaling of receptors (Magee and Cook, 2000; Andrasfalvy and Magee, 2001; Smith et al., 2003; Gulledge et al., 2005; Lavzin et al., 2012). Collectively, these studies support the notion that highly-branched and expansive neuronal structures, are likely to present some degree of passive voltage attenuation (in the absence of amplifying mechanisms) and perform compartmentalized computations as a consequence. Yet, this framework for dendritic computation does not rely on the study of, or account for, the diverse dendrite and neurite morphologies observed in nature.

To make sense of our findings in the STG, we revisited basic cable theory and simulated electrotonus and passive voltage integration in a library of neurites exhibiting diverse geometries and passive biophysical properties. We observed a surprising range of electrotonic decrement, directional bias, and voltage summation arithmetic across the surveyed morphological and biophysical parameter space. Thus, this simulation revealed multiple morphological and biophysical solutions for achieving varying degrees of passive electrotonic decrement and different computational strategies. We also show that linear summation and directional insensitivity, as observed in four STG neuron types, can be achieved in the absence of active properties altogether and in the face of potential heterogeneity of passive biophysical properties. Altogether, this proof-of-concept simulation both recapitulates the principles describe in early theoretical studies and also demonstrates that different biophysical and morphological strategies are likely to be utilized by different neuron types, to suit their unique physiological function. Thus, the widely-accept principles derived from the study of so-called canonical neuron types may be less general than previously thought.

A general solution for reliable pacemaking physiology

Our findings are interesting in light of the synaptic organization of the STG. Synaptic sites are sparsely distributed throughout the neuropil and pre- and post-synaptic sites are closely apposed on the same neurites (King, 1976a; King, 1976b; Kilman and Marder, 1996). Thus, sufficiently large synaptic potentials may originate anywhere on the neurite tree, propagate in any direction, and achieve consistent neuronal output.

The motor rhythm generated by the STG relies on slow oscillations and graded inhibitory transmission (Eisen and Marder, 1982; Marder and Eisen, 1984; Maynard and Walton, 1975; Graubard et al., 1980; Manor et al., 1997; Manor et al., 1999Bose et al., 2014; Golowasch et al., 2017). The biophysical features we have described in STG neurons may allow for the averaging of very large and slow synaptic conductances in space and time, thereby sustaining pattern generation in this motor circuit. Rhythmic networks that compute with slow oscillations and/or graded transmission (Walsh et al., 1972; Wilson and Wachtel, 1974; Pearson and Fourtner, 1975; Robertson and Pearson, 1985; Angstadt and Calabrese, 1991; Dicaprio, 1989; Dicaprio et al., 1997; Dale, 1995DiCaprio, 2003; Smarandache-Wellmann et al., 2013) may benefit from a similar biophysical and morphological architecture. Moreover, we suggest that wide neurites may aid STG neurons in generating consistent physiological output, in the face of variable conductance magnitudes and subcellular distributions of intrinsic and synaptic properties across animals (Prinz et al., 2004; Schulz et al., 2006; Marder and Goaillard, 2006; Goaillard et al., 2009; Marder, 2011).

In the present study, we assessed the integration of inhibitory glutamate events in the presence of TTX, which blocks voltage-gated sodium currents and silences circuit activity. Thus, we can only speculate how action potentials, arising from such TTX-sensitive currents, may influence the integration of graded inhibitory glutamatergic synaptic events in the intact circuit. We would not expect TTX-sensitive currents to substantially alter inhibitory voltage signal propagation or integration at the range of membrane potentials probed here (−100 to −40 mV for apparent reversal potentials measurements and −50 mV for the voltage summation and directional sensitivity measurements). Moreover, spike initiations zones, where such TTX-sensitive channels are most likely to reside, are located just outside the neuropil, where the axons exit the ganglion (Raper, 1979; Miller, 1980). PD neurons exhibit a second, dopamine-sensitive axonal spike initiation zone between the upper dvn and its split into the bilateral lvns (refer to Figure 2A; Bucher et al., 2003). Given the peripheral locations of the spike initiation zones in these neurons, it is unlikely that TTX-sensitive voltage-gated channels would shunt the current arising from these evoked events in the same way as has been seen in other systems (Laurent, 1990). Spatial separation of spike initiation zones from synaptic integration and slow wave generation in the neuropil may reduce shunting of synaptic currents. A thorough investigation of this possibility requires experiments in varying pharmacological and modulatory conditions, which may reveal how various currents and ongoing circuit activity may influence these voltage propagation and integration in these otherwise compact passive neuronal structures.

Taken together with previous work (Otopalik et al., 2017a; Otopalik et al., 2017b), the present study suggests that, given the relatively compact electrotonic architecture of STG neurons arising from their neurite geometries, other features of their morphologies and the exact spatial organization of synaptic contacts may not be critical determinants of the distinct physiological waveforms and firing patterns exhibited by different STG neuron types. Thus, one is left with the expectation that their different activity patterns are predominantly determined by their cell-type-specific ion channel and receptor expression profiles. And, indeed, there is much evidence that the 14 different neuron types express different palettes of receptors (Swensen et al., 2000; Swensen and Marder, 2000; Swensen and Marder, 2001) and cell-type-specific ratios of ion channels (Schulz et al., 2006; Schulz et al., 2007).

Of course, one is left wondering why these neurons present such expansive and complex morphologies, if they instead act as single electrotonic compartments. One possibility is that this allows STG neurons to make appropriate synaptic contacts wherever partner neurons ramifying throughout the neuropil find each other. Additionally, it is likely that STG neurons grow to fill distinct spatial fields in the neuropil (Otopalik et al., 2017a) for the purpose of maximizing surface area for the reception of the many diffuse neuromodulatory substances that are released in the hemolymph and by descending modulatory inputs of the stomatogastric nerve (Marder and Bucher, 2007; Blitz and Nusbaum, 2011).

Materials and methods

Animals and dissections

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Wild-caught adult male Jonah Crabs (Cancer borealis) were acquired and maintained by the Marine Resources Center at the Marine Biological Laboratories in Woods Hole, MA. Animals were maintained on a 12 hr dark/12 hr light cycle without food and in chilled natural seawater (10–13 deg C) in a 2000-liter tank at a density of no more than 30 crabs per tank. STG dissections were executed as in Otopalik et al. (2017b) and as previously described (Gutierrez and Grashow, 2009) in saline solution (440 mM NaCl, 11 mM KCl, 26 mM MgCl2, 13 mM CaCl2, 11 mM Trizma base, 5 mM maleic acid, pH 7.4–7.6). The intact stomatogastric nervous system, including: two bilateral commissural ganglia, esophageal ganglion, and stomatogastric ganglion (STG), as well as the lvn, mvn, dgn were dissected from the animal’s foregut and pinned down in a Sylgard-coated petri dish (10 mL). The preparation was continuously superfused with chilled saline (11–13 degrees C) for the duration of the experiment using a bipolar temperature control system (Harvard Apparatus, CL-100).

Electrophysiology and Dye-fills

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All electrophysiology and dye-fill methods are consistent with those utilized in Otopalik et al. (2017b). The STG was desheathed for access to somata for intracellular recordings. These recordings were executed with glass micropipettes (20–30 MΩ) filled with internal solution: 10 mM MgCl2, 400 mM potassium gluconate, 10 mM HEPES buffer, 15 mM NaSO4, 20 mM NaCl (Hooper et al., 2015). Intracellular recordings signals were amplified with an Axoclamp 900A amplifier (Molecular Devices, as described in Otopalik et al. (2017b). For extracellular nerve recordings, Vaseline wells were built around the lvn, mvn, and dgn nerves and stainless-steel pin electrodes were used to monitor extracellular nerve activity (as indicated in Figure 1A). Extracellular nerve recordings were amplified using a Model 3500 extracellular amplifier (A-M Systems). All recordings were acquired with a Digidata 1550 (Molecular Devices) digitizer and visualized with pClamp data acquisition software (Axon Instruments, version 10.7). Neuron types were identified by matching concurrent intracellular spiking patterns with units on nerves known to contain their axons (as in Figure 1B) and verified with positive and negative current injections. After identification, a single neuron was filled with dilute alexa488 dye (2 mM Alexa Fluor 488-hyrazide sodium salt (ThermoFisher Scientific, catalog no. A-10436, dissolved in internal solution)) with negative current pulses (−4 nA, 500 ms at 0.5 Hz) for 15–25 min. Following the dye-fill, input resistance was measured at the soma in two-electrode current clamp (neurons with input resistances < 5 MΩ were discarded). For two-electrode current clamp, the electrode containing dilute alexa488 was used for recording and amplified on a 0.1xHS headstage. The electrode used for cell identification was used for current injection and amplified with a 1xHS headstage. Input resistance was measured throughout the experiment and neurons with input resistances < 5 MΩ were discarded. Reversal potentials for glutamate-evoked responses were determined by evoking responses at >eight membrane potentials between −100 and −40 mV. In some experiments, neurons were filled with 2% Lucifer Yellow CH dipotassium salt (LY; Sigma, catalog no. L0144; diluted in filtered water) for post-hoc imaging. LY was injected with a low-resistance (10–15 MΩ) glass micropipette for 20–50 min with negative current pulses (−six to −8 nA, 500 ms at 0.5 Hz).

Focal glutamate Photo-uncaging

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Focal glutamate photo-uncaging methodology was consistent with the methods used in Otopalik et al. (2017b), although different instrumentation was used. For photo-uncaging experiments, preparations were superfused with a re-circulating peristaltic pump to maintain a stable bath volume. 250 µM MNI-caged-L-glutamate (dissolved in saline; Tocris Bioscience, catalog no. 1490) was bath applied. 10−7 M teterodotoxin (TTX) was also superfused to minimize spike-driven synaptic activity. Alexa Fluor 488-filled neurons were visualized and focal photo-uncaging was achieved with a Laser Applied Stimulation and Uncaging (LASU) system (Scientifica). In brief: this system was composed of an epifluorescence microscope (SliceScope, Scientifica) equipped with a 4x magnification air and 40x magnification water-immersion objective lenses (Olympus; PLN 4X and LUMPLFLN 40XW, respectively). A 780 IR-LED was used to visualize the stomatogastric ganglion and locate neurons of interest. A white fluorescence illumination system (CoolLED) and FITC/Alexa Fluor 488/Fluo3/Oregon Green filter set (Chroma) were used to excite and visualize fluorescent emission from neuronal dye-fills. Images were captured with a monochrome CCD camera (Scientifica, SciCam Pro; 1360 × 1025 array and 6.54 µm2 pixel size). Focal photo-activation of MNI-glutamate was achieved with a 405 nm laser (1 ms pulses, 35 mW, spot size <1.5 µm with the 40x objective). The preparation platform and micromanipulators were mounted on a motorized movable base plate, allowing for smooth re-positioning (in the X-Y plane) of the objective over different neurites. For photo-activation at multiple sites within the field of view, the laser spot was re-positioned in quick sequence (5 Hz) using a set of X-Y galvanometers (Cambridge Technology, 6251H). Photo-uncaging sites within the field of view, laser pulse duration, and pulse rate were selected with the assistance of the LASU system software (Scientifica).

Electrophysiology analysis

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Electrophysiological responses to focal glutamate photo-uncaging were visualized and analyzed offline, as previously described (Otopalik et al., 2017b), using a set of custom MATLAB (Mathworks, version 2017b) scripts that will be made available on the Marder Lab GitHub (https://github.com/marderlab) (Otopalik, 2019; copy archived at https://github.com/elifesciences-publications/Otopalik-Pipkin-Marder-2019). Maximal response amplitudes, directional bias, and voltage integration arithmetic were calculated as an average of 3 trials of photo-stimulation at individual sites or of individual branches, accordingly. Apparent reversal potentials (Erevs) were calculated for individual sites by plotting response amplitudes as a function of somatic membrane potential and fitting these scatter plots with a linear regression. The apparent Erev for each site was calculated as the x-intercept of this fit. These methods are described in detail in Otopalik et al. (2017b). The For the linear regressions for all sites depicted in Figure 3D and supplements (plots in Part C), R-values were >0.85.

Post-hoc imaging and morphological analysis

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For each neuron, all photo-uncaging sites were re-located in fluorescence images of the Alexa Fluor 488 and/or Lucifer Yellow dye-fills acquired with the LASU microscope (at 40x and 20x magnification; described above). The distance between each site and the somatic recording site was measured utilizing a combination of 2-D and 3-D image stacks with the assistance of Simple Neurite Tracer on ImageJ/FIJI (Longair et al., 2011). Although most experiments were exclusively conducted using the LASU microscope, a subset of neurons were imaged at 40x magnification (Zeiss C-apochromat40x/1.2 W) on a VIVO microscope system equipped with a Yokogawa (CSU-X1, Japan) spinning disk confocal scan head mounted on a Zeiss Examiner microscope. Fluorescent dye-fills were visualized with standard GFP filters and images were captured with a Prime CMOS camera (Photometrics, 95B). Multiple image stacks in the z-dimension, spanning the STG, were stitched together with the assistance of the Stitching tool in ImageJ/FIJI (Preibisch et al., 2009). Maximum projections of these stacks are shown in Figure 2C.

Volumetric neurite reconstructions

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For high-resolution imaging and volumetric neurite reconstructions, a subset of preparations were fixed in 4% paraformaldehyde following photo-uncaging experiments and kept at 4° C until immuno-staining. For immuno-staining, each preparation was incubated with a rabbit anti-Lucifer Yellow IgG antibody (Invitrogen A5750) overnight at room temperature in phosphate-buffered saline (PBS) containing 0.1% Tris, then washed and subsequently incubated with a goat anti-rabbit IgG secondary antibody conjugated to Alexa-488 (Invitrogen A11034) in PBS at room temperature. Preparations were mounted on slides using VectaShield (Vector Laboratories H-1000). Seven preparations survived this full sequence, from electrophysiology and glutamate photo-uncaging, through immuno-staining, mounting, and imaging: one PD, three LPs, two VDs, and one GM.

High-resolution confocal images of each preparation were taken on a Leica SP5 system. We used a 63x objective to collect a montage of Z-stacks spanning the entire neuropilar arbor of the labeled cell at a voxel resolution of 0.114 μm x 0.114 μm in the X-Y plane and 0.797 μm in Z dimension. We found this resolution was sufficient to relocate and trace the branches that were subjected to glutamate photo-uncaging. Image montages were aligned and reconstructions acquired within the TrakEM2 (fiji.sc/TrakEM2, RRID: SCR_008954; Cardona et al., 2012) environment of ImageJ/FIJI. We fully traced each neuron from the origin of the primary neurite near the soma to the tips of each branch. As our analyses concerned only the branches visited for photo-uncaging, our reconstructions therefore do not recapitulate the entirety of the neuronal arbor. We traced each preparation in two ways. First, we generated a skeleton wherein the neuron is represented by a tree of connected nodes. Second, we traced the full volume of each branch containing the skeleton by manually coloring in a region in each z-layer that contained that branch.

Using these two reconstructions for each neurite, we measured the path distance of each node in the skeleton to the soma along with the cross-sectional area of the branch at each node. From these cross-sectional areas, we calculate an approximated diameter of the branch assuming the branch were cylindrical; in most cases, of course, the branches are not perfectly cylindrical. To generate cross-sectional area, we used the built-in coding environment of FIJI to write a custom Python script. Briefly, the algorithm generates a list of all points on the edge of branches in the arbor, then finds those which lie within a small threshold (0.5 μm) of a plane orthogonal to the arbor of the branch at each node. The number of these points are further reduced by excluding those which lie outside a certain distance of the node (which corresponds to the maximum expected radius of the branch at that node). For most branches, we used a distance threshold of 3 μm, while for thicker branches we used 11 μm. Finally, the projection of these points onto the orthogonal plane through the branch at each node defines a polygon of which the area is calculated using the shoelace formula.

Passive cable models

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The library of cable models utilized in Otopalik et al. (2017b) was adapted to explore electrotonus, directional bias, and voltage integration in neurites with varying geometries (depicted in Figure 6) and passive properties: six specific axial resistances (Ra): 10, 50, 100, 150, 200, 300 Ω*cm; and six specific membrane resistances (Rm): 2 × 104, 1.6 × 104, 1 × 104, 5 × 103, 1 × 103, 1 × 102 Ω*cm2. All cables were 1000 µm in length and had a membrane capacitance of 1 µF*cm−2. Electrotonus was assessed as described in Figure 1 and voltage summation was assessed by simulating our experimental glutamate photo-uncaging procedure using the simulation platform NEURON (Hines and Carnevale, 2001). All possible combinations of neurite geometries, membrane resistances, and axial resistances were assessed in Figure 1—figure supplement 1 to Figure 1, Figure 4, and Figure 4—figure supplement 1and 2 to Figure 4, whereas a representative cross-section of cable models are presented in Figure 1—figure supplement 2 to Figure 1 and Figure 2—figure supplement 3 to Figure 2. To assess voltage integration directional bias and arithmetic, voltage was recorded 100 µm from the proximal end (d0) and inhibitory potentials (Erev = −75 mV, 𝜏 = 70 ms, gmax = 10 nS) were evoked at five sites with increasing distance from the recording site (as depicted in Figure 4A,B). Sites were activated individually, and then at 5 Hz in the inward (toward the recording site) or outward (away from the recording site) directions. Using MATLAB (Mathworks, version 2018b), integrals were calculated for the inward and outward summed responses and the expected linear sum of the individual events in either direction. Directional bias was calculated as the inward integral minus the outward integral. Linearity was calculated as the expected arithmetic sum minus the recorded voltages sum for the inward direction. Custom scripts written to generate cable models and simulate experimental procedures in NEURON were composed in Sublime Text (Sublime HQ Pty Ltd, Sydney) and can be found on the Marder Lab GitHub (https://github.com/marderlab), along with all simulation output.

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Decision letter

  1. Inna Slutsky
    Reviewing Editor; Tel Aviv University, Israel
  2. Ronald L Calabrese
    Senior Editor; Emory University, United States

In the interests of transparency, eLife includes the editorial decision letter and accompanying author responses. A lightly edited version of the letter sent to the authors after peer review is shown, indicating the most substantive concerns; minor comments are not usually included.

Thank you for submitting your article "Neuronal morphologies built for compact computing in a rhythmic motor circuit" for consideration by eLife. Your article has been reviewed by two peer reviewers, and the evaluation has been overseen by a Reviewing Editor and Ronald Calabrese as the Senior Editor. The following individuals involved in review of your submission have agreed to reveal their identity: Gilles Laurent (Reviewer #1).

Summary:

This nice paper is the continuation of a series of studies from the Marder lab investigating the functional consequences of STG neuron morphology in the passive regime. The authors combine an exploration of parameter space by compartmental modeling with experimental tests, contrasting dendritic integration in neurites with large taper (as in STG neurons) with integration in dendrites with low taper (as is typical of cortical neurons, often used as "typical" or representative examples). The basic claim is that the geometry of the dendrites in this system makes the neurons act virtually as a single compartment even though they have a very elaborate dendritic structure. The authors claim that this is a result of substantial tapering of the dendrites and conduct compartmental simulations to support their conclusion. The paper is well written and the experimental sample size impressive. It seems to do a good job in considering and testing different cases with simulation and matching experimental data to simulations which is the gold standard in this type of studies. Nevertheless, we ask the authors to address several concerns, as listed below, to strengthen the conclusions of this work.

Essential revisions:

1) Reading the manuscript gives the feeling a negative result (synaptic inputs seem to be location independent) is turned into a feature. However, there may be methodological reasons why location dependence of some features is found to be weak (see below) and even if it is true, it does not justify consideration as a special mechanism. There are many neurons even in mammalian CNS where apparently there is not much dendritic integration (e.g. cerebellar granular cells).

2) Figure 1 – the authors perform many simulations to test the effect of change in diameter on voltage attenuation along the dendrites. They make the point that geometry can affect attenuation along the dendrites even when all other parameters are kept the same.

a) While the results are presented as a surprise, the understanding that dendritic geometry affects voltage attenuation is at the heart of cable theory and is present already in Rall's 59 paper.

b) In addition, the specific case of tapering is analytically covered in the papers of Schierwagen (admittedly very difficult to read): Schierwagen, A.K., A non-uniform equivalent cable model of membrane voltage changes in a passive dendritic tree, J. Theor. Biol. (1989) 141, 159-179, which is not even cited.

c) The simulated case assumes sealed end boundary condition at both sides of the cable, while in fact the relevant case is that there is a large "load" (e.g. killed end boundary condition) on the side with large diameter, because the rest of the dendritic tree is connected to that part. This might have a significant effect on the conclusions.

d) The authors have both the experimental data of the geometry of the neurons (which they studied in detail in the first paper) and the physiological properties (allowing them to extract the biophysical properties of the membrane). They could simulate the specific neuron they record from, rather than choose to simulate simplified models, which might fail to capture the intricate properties of the real geometry.

3) The authors use sharp electrode recordings and in fact two of them at the soma, which indeed makes the current clamp better. However, it is accepted that sharp electrode recordings may fundamentally change the estimate of membrane parameters and may create a significant conductance leak in the recording location. On top of that, most of the relevant integration happens near the location of synaptic inputs and far away from the recording site. So, it is difficult to escape the alternative explanation in which all the input looks similar at the recording point because they all very far from it, especially when the inputs are very slow (0.5 s rise time, voltage attenuation is far smaller for steady state inputs as compared to transients, and here the inputs are so slow that they are virtually steady state).

4) The authors find a fit for the data with effective space constant of order of magnitude of 1mm with total dendritic length of > 10mm. This means that there are certainly points that are quite far from each other, and still they claim that the neuron acts as a single compartment.

5) The measurements of Erev in their hands shows almost no sensitivity to dendritic location of the activation. This together with simulation that shows that under certain condition (short space constant) Erev estimation should be sensitive to location is taken as an indication that the space constant is long. However, for this the authors are only using very simplified models, which we suspect are very different in terms of boundary conditions than their experimental setup (see above).

6) The individual responses presented in Figure 5—Figure supplements 1, 2 and especially 3, seem to have different shape indices (i.e. rise time and decay time, consistent with classical cable theory of inputs arriving from different locations along the dendrites) and inconsistent with a single compartment scenario.

https://doi.org/10.7554/eLife.41728.030

Author response

Essential revisions:

1) Reading the manuscript gives the feeling a negative result (synaptic inputs seem to be location independent) is turned into a feature. However, there may be methodological reasons why location dependence of some features is found to be weak (see below) and even if it is true, it does not justify consideration as a special mechanism. There are many neurons even in mammalian CNS where apparently there is not much dendritic integration (e.g. cerebellar granular cells).

We have adjusted the text of the Results and Discussion sections to clearly state the predictions generated by the proof-of-concept computational simulations and how these predictions relate to the experimental results. We hope that it is now clear that the experimental results align well with the predictions generated by the passive cable simulations. This is not a negative result, but an excellent outcome. The alignment of the experimental and simulation results tells us that the compact electrotonic structures and voltage integration properties observed in these four neuron types can potentially arise from passive voltage propagation in the absence of active properties, in part because they present such wide neurite diameters. This is stated clearly in the Discussion:

“…we find that multiple STG neuron types present electrotonically compact structures and within-neurite voltage summation that is relatively linear and directionally insensitive. […] Our computational simulations suggest that this biophysical architecture may be achieved passively and as a simple consequence of neurite geometry in these neurons, which present secondary branches with wide diameters that taper from 10-20 µm at their proximal, primary-neurite junctions, to sub-micron diameters at their terminating tips.”

Although the reviewer suggests that there are many neuron types thought not to perform compartmentalized, dendritic computations, the direct experimental assessment of electrotonus and such compartmentalization has actually only been executed in a handful of neuron types. We describe this in the Introduction:

To date, measuring voltage attenuation across the many neurite paths presented in complex neuronal structures using electrophysiological techniques has proven difficult. Thus, electrotonus has been experimentally assessed in only a handful of neuron types (for example: Spruston and Johnston, 1992; Spruston et al., 1994; Rapp et al., 1994; Carnevale et al., 1997; Stuart and Spruston, 1998; Chitwood et al., 1999; Jaffe and Carnevale, 1999; Otopalik et al., 2017b; Medan et al., 2018), and this greatly restricts our understanding of the breadth of biophysical organizations utilized in different neuron types and circuit contexts.

While we understand that STG neurons may not be the first neuron types to be described as electrotonically compact, we do think it important to present this study, along with the founding papers (Otopalik et al. 2017a, b), as a case wherein the complex morphologies are in fact compact, and this is perhaps what allows for robust circuit output in the face of a great deal of morphological variability in the same neuron types across animals.

2) Figure 1 – the authors perform many simulations to test the effect of change in diameter on voltage attenuation along the dendrites. They make the point that geometry can affect attenuation along the dendrites even when all other parameters are kept the same.

a) While the results are presented as a surprise, the understanding that dendritic geometry affects voltage attenuation is at the heart of cable theory and is present already in Rall's 59 paper.

Our description of the simulation results as ‘surprising’ was not meant to be interpreted as ‘novel.’ This said, we have altered the text throughout the manuscript to clarify this. Our computational simulations in NEURON rely heavily on the seminal theoretical findings of Rall, Schierwagen, and many others. Our intention in presenting these simulations was to apply these seminal theories, generate predictions, and provide a useful pedagogical narrative throughout the paper (Goldstein, 2018). Yet, it is also important to distinguish the analytical approaches of these seminal studies from our numerical simulations: whereas these earlier studies generated biophysical rules and cable equations, in our simulations we were able to scan a broad parameter space of passive and morphological properties and test the boundaries of these aforementioned rules regarding electrotonus, directional sensitivity, and passive voltage integration. By doing this, we found that the wide neurite diameters exhibited by STG neurons renders them relatively resilient to the conventional electrotonic decrement expected from such long neurite paths. The fact that this phenomenon is predicted by passive cable models in NEURON, suggests that our experimental observations can indeed be explained by passive propagation and neurite geometry. By revising the last paragraph of the Introduction, we believe we will have prepared the reader to enter the Results section with this outlook.

b) In addition, the specific case of tapering is analytically covered in the papers of Schierwagen (admittedly very difficult to read): Schierwagen, A.K., A non-uniform equivalent cable model of membrane voltage changes in a passive dendritic tree, J. Theor. Biol. (1989) 141, 159-179, which is not even cited.

We appreciate that this study was brought to our attention and regret that it was not on our radar at the time of writing this manuscript. One hurdle faced in pursuing this work is synthesizing and making sense of the wealth of previous studies examining geometry, electrotonus, and neuronal function. The diverse numerical, analytical, and experimental methods used in previous studies have led to a somewhat incongruous literature. This said, we have now read Schierwagen (1989) closely. In this study, Schierwagen derived the equations for equivalent cable models for multiple branched trees or subtrees. These were then used to determine the distribution of subthreshold membrane voltage in highly branched neuronal structures. This is now cited in the Introduction (first paragraph) and again in the Results section (subsection “Simulating Electrotonus in Diverse Neurites”, first paragraph). It is important to note that, in this study, Schierwagen considered taper as a descriptor of an equivalent cylinder for multiply branched trees or subtrees; the taper we refer to in our manuscript is simply referring to the geometry of individual neurite paths, not multiply branched trees. Additional studies we failed to reference in the original manuscript, that consider the role of taper and flare of individual branches (Goldstein and Rall, 1974; Holmes and Rall, 1992), have now been properly cited in the subsection 2 Linking Electrotonus and Neurite Geometry in STG Neurons”.

c) The simulated case assumes sealed end boundary condition at both sides of the cable, while in fact the relevant case is that there is a large "load" (e.g. killed end boundary condition) on the side with large diameter, because the rest of the dendritic tree is connected to that part. This might have a significant effect on the conclusions.

This issue that is also brought up in essential revision #5 (below). In this work, we have simulated neurite paths that we view as a representation of the entire path from terminal neurite tip to a recording electrode at the soma. These two ends are, in fact, sealed. However, it is true that there may be some shunting at branch points along this path, particularly at the junction between the secondary and primary neurites. To test how such putative shunting may influence our measurements of electrotonus, we ran a set of cable simulations with a large load on the proximal side of the cable (with the larger diameter, d0) in a representative cross-section of our cable model library (Rm = 10000 Ω × cm2,d1 = 0.5 µm (constant); d0 = 0.5, 1, 5, 10, 20 µm; Ra = 50, 100, 150, 200, 300 Ω × cm). We added the shunt by simply adding a compartment at 300 µm from this proximal end of the parent cable (passive properties consistent with the parent cable), effectively mimicking the rest of the neurite tree. We varied the size of the shunt by simply varying the length of this added compartment (as choosing an exact leak conductance magnitude or cable length was somewhat arbitrary; the different shunt sizes had lengths 100, 300, 500, 1000 µm; all had an axial diameter of 5 µm). We measured the effective λ in these cables, as in Figure 1 and Figure 1—figure supplement 1. We found that increasing the shunt did indeed alter the effective λ measured, but that the relative relationships across the varying cable geometries shown in Figure 1 and Figure 1—figure supplement 1 remained true (that is, increasing the proximal diameter to 10 microns resulted in effective λ greater than 1 mm for a range of axial resistance values). The results of this simulation are now presented in Figure 1—figure supplement 2, and discussed briefly in the Results text (subsection “Simulating Electrotonus in Diverse Neurites”, last paragraph).

d) The authors have both the experimental data of the geometry of the neurons (which they studied in detail in the first paper) and the physiological properties (allowing them to extract the biophysical properties of the membrane). They could simulate the specific neuron they record from, rather than choose to simulate simplified models, which might fail to capture the intricate properties of the real geometry.

In the first submission of this manuscript, path lengths were the only geometrical measurements that we had for the evaluated neuronal structures. In previous work, we had shown that the apparent reversal potentials measured across many sites in GM neurons were independent of distance from soma, neurite diameter, and branch order (Otopalik et al., 2017). Thus, for this paper we simply used ImageJ to measure distance from soma for each photo-activated site, and set aside these other geometric measurements. Thus, in the first submission we lacked other geometrical data for these neurons.

To address this and other concerns expressed by the reviewers in this revised manuscript, we have completed volumetric reconstructions and continuous measurement of neurite diameter from primary neurite to terminating tips of 23 neurites from neurons for which we had high-quality confocal stacks with sufficient resolution (now described in the Materials and methods section “Volumetric Neurite Reconstructions”). In these analyses, we found that, while some neurites tapered gradually from the proximal primary neurite junction to terminal tip, others decreased in diameter in surprisingly abrupt steps. We have summarized these data in Figure 2D-E and presented all diameter measurements in Figure 2—figure supplements 1 and 2. These results are discussed in the subsection “Linking Electrotonus and Neurite Geometry in STG Neurons”.

Having made these finer measurements, we then completed a new set of simulations in a revised set of cable models that test the influence of taper, versus step-reductions, in cable models with varying diameters. We found that, for cables with the wide diameters presented by STG neurites, there exists a regime of passive properties that are resilient to step-reductions in diameter. These results are now shown in Figure 2—figure supplement 3 and discussed in the aforementioned subsection.

3) The authors use sharp electrode recordings and in fact two of them at the soma, which indeed makes the current clamp better. However, it is accepted that sharp electrode recordings may fundamentally change the estimate of membrane parameters and may create a significant conductance leak in the recording location. On top of that, most of the relevant integration happens near the location of synaptic inputs and far away from the recording site. So, it is difficult to escape the alternative explanation in which all the input looks similar at the recording point because they all very far from it, especially when the inputs are very slow (0.5 s rise time, voltage attenuation is far smaller for steady state inputs as compared to transients, and here the inputs are so slow that they are virtually steady state).

We appreciate that sharp recordings are not the standard in many biological preparations, whereas they are the standard in the crustacean stomatogastric ganglion preparation. This is, in part, because STG neurons present relatively large somata (125.8 ± 47.5 µm in diameter; Otopalik et al., 2017a) that are well-suited for sharp recordings with one or two electrodes. In the present study, experiments were only conducted in cells with inputs resistances > 5 MOhms following the insertion of both electrodes, which is consistent with the input resistance cut-off specified in other STG studies, even those utilizing only a single electrode. The kinetics of the events described here are consistent with the glutamate-evoked potentials conducted in cultured, transplanted STG neurons (e.g. Cleland and Selverston, 1995). These transplanted neurons are thought to act essentially as a single compartment, as they grow few neurites in vitro. Furthermore, we and others who work in the STG have now provided increasing evidence that these neurons are relatively compact and that voltage decrement must be minimal for these inhibitory glutamate-mediated voltage events:

1) In this and previous work (Otopalik et al., 2017b), we have demonstrated that we can inject current at the soma and alter the membrane potential at distal activation sites sufficiently enough to flip the sign of the evoked glutamate response at somatic membrane potentials that are within close range of the predicted reversal potential based on the chloride-dependence of the evoked current (Otopalik et al., 2017b; Figure 3 and associated supplements in this manuscript).

2) Summation of events activated in sequence across branches appears relatively linear (Figure 5) and independent of direction of activation. This is consistent with our interpretation of compact electrotonus; dendrites that present a greater degree of electrotonic decrement are thought to give rise to a centripetal bias in voltage propagation and current flow toward the open end of the cable (Barlow and Levick, 1965; Euler et al., 2002; London and Häusser, 2005; Branco et al., 2010). In our study, it appears that the wide diameters of STG neurites render them impervious to such directional biases.

3) Although technically difficult, in previous studies experimentalists have completed dual recordings with one electrode at the soma and a second electrode several hundred microns away on the primary or secondary neurites (Golowasch and Marder, 1992; Miller, 1980). In both accounts, they found that while action potentials are subject to attenuation across this distance, graded inhibitory potentials with kinetics consistent with the events evoked in the present study do not undergo much attenuation. It was not clear from these studies, however, whether the many neurite paths in these complex neuronal structures were uniformly electrotonically compact, or if this was a specific feature of this experimentally accessible path from primary neurite to soma.

4) The authors find a fit for the data with effective space constant of order of magnitude of 1mm with total dendritic length of > 10mm. This means that there are certainly points that are quite far from each other, and still they claim that the neuron acts as a single compartment.

In the Abstract and Introduction (second paragraph) we write that STG neurons often present total cable lengths > 10 mm. The total cable length is the summed length of the entire neuronal structure, not the length of single neurite branches. Because individual secondary branches are typically no longer than 1mm, events arising at disparate locations are unlikely to be greater than 2 mm apart. A lambda of ~1 mm would certainly allow for integration of events evoked at sites separated by this distance. To ensure that this confusion does not arise among readers, we have clarified the meaning of total cable length in the Introduction. We now write: “expansive and complex neurite trees that sum to > 10 mm of total cable length…”.

5) The measurements of Erev in their hands shows almost no sensitivity to dendritic location of the activation. This together with simulation that shows that under certain condition (short space constant) Erev estimation should be sensitive to location is taken as an indication that the space constant is long. However, for this the authors are only using very simplified models, which we suspect are very different in terms of boundary conditions than their experimental setup (see above).

This is addressed in our response to comment 2, part c.

6) The individual responses presented in Figure 5—figure supplements 1, 2 and especially 3, seem to have different shape indices (i.e. rise time and decay time, consistent with classical cable theory of inputs arriving from different locations along the dendrites) and inconsistent with a single compartment scenario.

The kinetics of the events described here are consistent with the glutamate-evoked potentials conducted in cultured, transplanted STG neurons (Cleland and Selverston, 1995). Yet, it is true that there is heterogeneity in shape (as described by the reviewer) and amplitude across sites. Given the uniformity of apparent reversal potentials and the long lambdas predicted with the cable simulations in neurites with geometries similar to those observed in these neurons, we are inclined to speculate that these variable shape indices arise from local variations in receptor densities across photo-activated sites (this is discussed in Otopalik et al., 2017b).

https://doi.org/10.7554/eLife.41728.031

Article and author information

Author details

  1. Adriane G Otopalik

    1. Volen Center and Biology Department, Brandeis University, Waltham, United States
    2. Grass Laboratory, Marine Biological Laboratories, Woods Hole, United States
    Present address
    Department of Biological Sciences, Columbia University, New York, United States
    Contribution
    Conceptualization, Resources, Data curation, Software, Formal analysis, Funding acquisition, Investigation, Visualization, Methodology, Writing—original draft, Writing—review and editing
    For correspondence
    aotopali@brandeis.edu
    Competing interests
    No competing interests declared
    ORCID icon "This ORCID iD identifies the author of this article:" 0000-0002-3224-6502
  2. Jason Pipkin

    Volen Center and Biology Department, Brandeis University, Waltham, United States
    Contribution
    Software, Formal analysis, Investigation, Visualization, Methodology, Writing—original draft, Writing—review and editing
    Competing interests
    No competing interests declared
    ORCID icon "This ORCID iD identifies the author of this article:" 0000-0001-5525-3951
  3. Eve Marder

    Volen Center and Biology Department, Brandeis University, Waltham, United States
    Contribution
    Conceptualization, Resources, Supervision, Funding acquisition, Writing—original draft, Writing—review and editing
    For correspondence
    marder@brandeis.edu
    Competing interests
    Deputy Editor, eLife
    ORCID icon "This ORCID iD identifies the author of this article:" 0000-0001-9632-5448

Funding

National Institute of Neurological Disorders and Stroke (F31NS092126)

  • Adriane G Otopalik

National Institute of Neurological Disorders and Stroke (R35NS097343)

  • Eve Marder

Grass Foundation

  • Adriane G Otopalik

The funders had no role in study design, data collection and interpretation, or the decision to submit the work for publication.

Acknowledgements

We thank Jennifer Bestman for assistance in spinning disk and confocal microscopy; the Marine Resources Center at the Marine Biological Laboratories for acquiring and maintaining animals; Louie Kerr at the Central Microscopy Facility; Dana Mock-Munoz de Luna for administrative support; Kamran Kodhakhah, Heather Rhodes, and the 2017 Grass Fellows for their support and feedback; and lastly, Edward Dougherty at the Brandeis University Confocal Imaging Lab for support and microscope maintenance. This study was funded by the Grass Foundation and NINDS awards to F31NS092126 to AO and R35NS097343 to EM.

Senior Editor

  1. Ronald L Calabrese, Emory University, United States

Reviewing Editor

  1. Inna Slutsky, Tel Aviv University, Israel

Publication history

  1. Received: September 7, 2018
  2. Accepted: January 12, 2019
  3. Accepted Manuscript published: January 18, 2019 (version 1)
  4. Version of Record published: January 28, 2019 (version 2)

Copyright

© 2019, Otopalik et al.

This article is distributed under the terms of the Creative Commons Attribution License, which permits unrestricted use and redistribution provided that the original author and source are credited.

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