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A mammalian “RGC model” (retinal ganglion cells) is distinguished from the Hodgkin-Huxley model by the virtual absence of K-current during, and the virtual absence of Na-current after, the regenerative (rising) phase of the action potential. Both Na- and K-currents remain negligible throughout the interspike interval, whose control is therefore relinquished to stimulus currents. These properties yield a highly flexible and energy-efficient nerve impulse encoder. For the Hodgkin-Huxley model, in contrast, only 15 % of the Na-ions enter the axon regeneratively during the action potential (squid giant axon); a wasteful 85 % enter during the falling phase. Further, early activation of K-current causes the Na- and K-currents of the action potential to dominate over stimulus currents in controlling the sub-threshold membrane potential (interspike interval). This property makes the Hodgkin-Huxley model an intractable high frequency oscillator, which cannot be converted to flexible impulse encoding. The temperature difference between the squid giant axon (6.3° C) and RGCs (37° C) is bridged by a Q10 analysis, which suggests that an additional molecular gating mechanism of high Q10 – which is not present in the squid – is active in RGCs.
The demands placed on a nerve axon are simple and all-or-none; i.e., to faithfully pass on (propagate) all approaching action potentials and, equally important, to otherwise remain silent. In contrast, the encoding of nerve impulses can be a delicate process of creating highly variable signals in response to a wide range of stimuli. The requirements of these two purposes are contradictory, in that faithful propagation is best assured with a high threshold for the action potentials (i.e., electrical stability) which, however, prevents the necessary sensitivity for flexible impulse-encoding. The Hodgkin-Huxley model satisfies the stability requirement, but violates that of flexibility, even when its impulse-threshold is lowered by increasing the sodium conductance, G Na.
The Hodgkin-Huxley model has been remarkably durable, in part because of its mathematical elegance (simplicity and transparency), and in part because its gating kinetic rate constants reproduce the action potential waveform (roughly triangular), and large ionic membrane currents of the squid giant axon remarkably well (Loligo pealei, L. vulgaris). However, many action potentials of mammalian central neurons are of a more rounded waveform, associated with significantly smaller membrane ion-currents (cf Attwell and Laughlin, 2001). In a comparative model developed for retinal ganglion cells (“RGC model”), these features arise exclusively from the temporal relationships and relative voltage-dependence among the gating rate constants of the regenerative Na- and delayed rectifier K-channels. Although the RGC model shares the underlying gating-kinetic structure of Hodgkin and Huxley (1952), including the property of a “quasi-threshold” for action potentials (coined by FitzHugh, 1955), functionally the two models differ fundamentally. It is shown here that flexibility in impulse encoding is directly related to the efficient use of the energy that drives the ionic currents, that optimizing the efficiency yields the greatest flexibility, and both efficiency and flexibility are inversely related to the magnitudes of the Na- and K-currents that are minimally necessary to generate action potentials in the face of membrane capacitance.
The steady state fraction of open activation gates in the RGC model is – for all membrane potentials – smaller for K-channels than for Na-channels (i.e., for all V, n ∞ 4 (V) < m ∞ 3 (V); see Figure 1B). Thus the K-current of the RGC model becomes substantially activated only after the threshold for an action potential is crossed. This contrasts with the Hodgkin-Huxley model (see below), and reflects a relative voltage-shift in the rate constants α n (V) and β n (V), so that similar levels of K-channel activation occur 13 mV more depolarized in the RGC model (rate constants are listed in Computational Procedure).
There is, in addition, a significantly greater difference between the overall rate of Na-gating and the overall rate of K-gating in the RGC model, than for the Hodgkin-Huxley model (underlined coefficients of the listed rate constants, and Fig. 1C). Therefore, Na-inactivation is nearly complete by the time of onset of significant K-activation gating in an RGC model action potential. The resulting virtual absence of K-current throughout the regenerative phase, and the virtual absence of Na-current throughout the falling phase of the action potential (Fig. 1A, Fig 2A), make the RGC model highly energy-efficient, in the sense of minimizing the ionic currents.
After the K-channels close in afterhyperpolarization, the virtual absence of both primary currents, I Na and I K, continues throughout the interspike interval of the RGC model. Thus the sub-threshold membrane potential “drifts easily” and – unlike the Hodgkin-Huxley model – responds exclusively to small or large stimulus currents (synaptic or injected). This is the essence of flexible impulse encoding, which yields a large dynamic range of impulse-frequencies, including very low frequency repetitive firing (see Discussion). The RGC model rests close to its leakage reversal potential, which is arbitrary within a wide range (~ − 75 to − 55 mV).
A prominent feature of the Hodgkin-Huxley model is that its peak of sodium current occurs after the peak of the action potential, a period during which the sodium current of the RGC model is virtually zero (Fig. 2A). Thus, for the Hodgkin-Huxley model, 85 % of the Na-ions that enter the axon during an action potential do so after the regenerative phase (Fig. 2B). Although this percentage is reduced to 68 % at 37° C, the late and large I Na flows in direct opposition to the (therefore necessarily) large I K throughout the repolarizing phase. This rate constant-imposed competition between the ionic currents I Na and I K makes the Hodgkin-Huxley model highly wasteful of the energy used by the ionic currents.
Note that in the Hodgkin-Huxley model, n ∞ 4 (V) > m ∞ 3 (V) throughout the range of V < − 28 mV (Fig. 1B). Thus, unlike the RGC model, the K-channels begin to substantially activate prior to reaching the subsequent impulse-threshold in repetitive firing. This causes the (sub-threshold) interspike trajectory of the Hodgkin-Huxley model to be controlled primarily by the rate constants of gating, I Na and I K, just as these control the waveform-trajectory of the action potential, and both trajectories are relatively weak functions of stimulus current.
This gating-kinetic control of the interspike trajectory is unrelated to the high threshold of the Hodgkin-Huxley model. That threshold can be reduced, or entirely eliminated, by unilaterally increasing the sodium current (i.e., increasing G Na, listed in Computational Procedure). The model becomes spontaneously firing (stimulus = 0) when G Na is increased by a factor of about 1.8. Despite these threshold-changes, the length of the interspike interval is – in all cases – constrained by the rate constants of I Na and I K; the maximum length (minimum impulse frequency) is absolutely restricted, and large stimulus currents are required to reduce the length of the interspike interval. It is this ubiquitous gating-kinetic control that makes the Hodgkin-Huxley model an intractable high frequency oscillator, and therefore incapable of flexible impulse-encoding (cf. also Fohlmeister et al., 1980).
When membrane capacitance is zero (C M = 0), the ionic conductances can be reduced almost to zero (maintaining the model-specific ratios of G Na: G K), and both models continue to generate “zero-C” (i.e., purely conductive) action potentials of full amplitude. Thus, in the absence of capacitive current (I C = CM dV/dt = 0), the gating kinetics alone, with arbitrarily small (or large) G Na and G K, yield the appropriate sequential timing of Na- and K-activation and Na-inactivation to generate the I Na (t) and I K (t) necessary for an action potential.
In the presence of membrane capacitance, conservation of current (Kirchoff’s law) requires that the sum I C + I Na + I K = 0 (apart from stimulus, leakage, and other negligible currents). In the RGC model, I Na + I K ~ I Na during the regenerative phase, and I Na + I K ~ I K during the falling phase of the action potential (where Ca-current also contributes; see Fig. 1A). Because I K is small during the rising phase and I Na is small during the falling phase, each of these two currents is comparable to I C during their respective phases, and this implies substantial capacitive effects.
These capacitive effects reduce dV/dt (capacitive “smoothing”). This alters the temporal voltage profile to which the gating rate constants respond, which can change the sequential timing among the several channel gating processes. Figure 3 shows that for the RGC model, the temporal duration (width) of the “capacitive” action potential is greater than the width of the zero-C action potential by factors of about 2 (at mid-amplitude) or 3 (impulse-threshold to afterhyperpolarization). The ability of the RGC model to generate both capacitive and zero-C action potentials with this degree of difference in voltage profile implies that the gating rate constants of I Na and I K coordinate the separate rising and falling phases. Further, because the ionic conductances, G Na and G K, change with temperature at the specific rate of Q10 = 1.47, these same factors (about 2 or 3) hold at every temperature from 6.3° to 37° C (Fig. 3). (Q10 < 1.47 would cause to increase these factors with increasing temperature; Q10 > 1.47 would cause to reduce them.) Thus the gating coordination of the RGC model over different temperatures is not much influenced by capacitance.
For the Hodgkin-Huxley model, in contrast, the gating of I Na and I K is not coordinated into separate rising and falling phases for the action potential. The primary reason is that both Na- and K-activation are closely linked to the rising phase, and capacitive loading will change their relative timing, which can cause impulse-failure. For this reason, I Na and I K are both large in comparison with I C. The broad current maxima during an action potential [threshold-shock induced] reach I Na = − 767.7 µA/cm2, I K = 801.8 µA/cm2, and I C = − 68.2 µA/cm2 with a brief early peak of I C = 214.8 µA/cm2 (cf Fig. 2A). This comparatively small I C yields little capacitive smoothing, and therefore the capacitive and zero-C action potentials of the Hodgkin-Huxley model are of nearly the same duration (width) at any given temperature (see Fig. 3).
The high threshold (H-type) Ca-current of the RGC model increases the peak amplitude of the action potential by several millivolts, and reshapes the falling phase. Because of the resulting increased depth of afterhyperpolarization, the presence of I Ca also somewhat reduces the impulse frequency in repetitive firing (Fohlmeister and Miller, 1997a). However, because the flow of H-type Ca-current is virtually zero throughout the interspike interval, removing the Ca-channel has no effect on the RGC model’s flexible encoder properties. For the same reason, adding a Ca-current to the Hodgkin-Huxley model (in the RGC ratio of G Ca: G Na = 0.0275, see [*] in Computational Procedure), has no effect on that model’s rigid oscillator characteristic (see Discussion).
In bridging the temperature span between the standard 6.3° C of the Hodgkin-Huxley model, and the mammalian 37° C of the RGC model, the following features were found (the ‘matches’ in [1, 2] are in the durations of the action potentials):
To relate  and , note that the action potential of the 6.3° C squid axon (and Hodgkin-Huxley model) is about 2.5 milliseconds in duration. For retinal ganglion cells, in contrast, the duration of action potentials at the lowest temperatures (7° to 8° C) is about 10 milliseconds (Fig. 4D). Thus, the empirical impulse ‘match’ with the 6.3° C squid axon occurs for RGC data at 13.9° C. Indeed, retinal ganglion cells do not generate action potentials at 6.3° C.
Regarding , the combination of a substantial temperature range of uniformly constant Q10, and a neighboring lower temperature range of increasing Q10, is consistent with two simultaneously active processes in RGC gating, whereby the process of constant Q10 is rate-limiting at high temperatures, and a second process (of high Q10) becomes rate-limiting at low temperatures (see Discussion). A distinct second process is specifically suggested for RGC gating, because of its apparent absence in the squid axon:
Thus, in order to match the relatively short action potential duration of the 6.3° C squid axon, the gating kinetic Q10 = 2 is flat across the full temperature range (6.3° to 37° C) [1, 2]. A flat Q10 suggests a simpler gating mechanism for the squid axon. The similarity between the flat Q10 (= 2), and the partial range constant Q10s (= 1.95, 1.9) of RGC gating, suggests that this simpler gating mechanism is the same process in both preparations. Being conserved across the species, this process may represent the irreducible minimum mechanism necessary for Na-and K-channel gating in general, to which other processes of high Q10 appear to be added in mammalian channel gating. Further details are given in Discussion.
Flexible impulse encoding requires that stimulus currents (synaptic or injected) have a “free hand” in moving the sub-threshold membrane potential, without interference from the effects of voltage-gating of the Na- and K-currents of the action potential (cf Fourcaud-Trocme et al., 2003; van Rossum et al, 2003). This condition is inherently satisfied by the RGC model rate constants, which simultaneously optimize the gating kinetics metabolically. Thus the functionally needless, and therefore wasteful fraction of 85 % of Na-ions (and balancing K-ions) that cross the membrane during the action potential of the Hodgkin-Huxley model, is reduced to virtually zero in the RGC model (Fig. 1A, Fig 2A). The metabolic energy demand for Na-K-ATPase ion pumping is thereby reduced by a factor of nearly eight (7.76 in Fig. 2B; cf Attwell and Laughlin, 2001). The associated reduced membrane conductances also lower the necessary number of channel molecules (channel density) by a factor of nearly six (cf Naundorf et al., 2006). Thus, the primary conclusion of the present comparative results is that the elegant framework and mathematical simplicity of the Hodgkin-Huxley model may well be employed in simulating encoder-excitation of mammalian neurons, provided appropriately modified rate constants are used.
The RGC model rate constants involve two types of modification relative to Hodgkin and Huxley (1952):  Voltage-shifts, and  changes in the overall gating rates. Voltage-shifts apply primarily to K-channel gating (also Na-inactivation; cf Fig. 1B); changes in the overall gating rates to Na-channels (see listed rate constants in Computational Procedure). Na-channel gating is significantly faster in the RGC model, which separates and coordinates the ionic currents I Na and I K in the rising and falling phases of the action potential (see Results). The voltage-shifts suppress the early K-channel activation of the Hodgkin-Huxley model, in that they cause to require a greater depolarization for equivalent K-channel gating.
In a remarkable empirical coincidence it was found that the voltage-shifts alone are not sufficient to yield either the efficiency or the flexibility properties of the RGC model. Thus, Figure 4B shows an experimental impulse train from a rat RGC, with “sleepy” Na-channels. The impulse train was generated in response to a just over threshold constant stimulus current, at 8° C (data courtesy of Eric A. Newman). Note the (sporadic) spiking, in conjunction with sub-threshold oscillations that are characteristic of the Hodgkin-Huxley model (see below); note also the Hodgkin-Huxley-like shape of the interspike trajectory (expanded in Fig. 4C). Precision fitting (phase plots) of the experimental action potentials – which took full account of the non-space clamped nature of the experimental recording – showed that the Na-channels of rat RGCs consistently become “sleepy” for T ≤ 8° C, while the K-channels remain non-sleepy (Fohlmeister et al., 2009). The modeling showed that “sleepy” Na-channels retain the voltage-shifts of the RGC model, but their gating is slowed by a factor of about 10.
The modeling showed further that “sleepy” Na-channels induce a competitive overlap of I Na and I K, and cause the peak of I Na to occur during the falling phase in “sleepy action potentials,” with 74.7 % of Na+ ions entering the cell after the peak of the action potential (see Figure 9 in Fohlmeister et al., 2009). Except for the sporadic nature of the spiking – which may be due to channel or synaptic noise in this just over threshold recording – these phenomena are characteristics of the Hodgkin-Huxley model (Fig. 2A). The peak currents during the action potential are I Na = − 31 µA/cm2, I K = 36 µA/cm2, and I C = 7.5 µA/cm2, whose relative proportions, and the ionic currents’ dominance over I C, are again like those of the Hodgkin-Huxley model (see Results). For this reason too, there is little capacitive smoothing of the “sleepy action potentials,” which are of about 10 ms duration (Fig. 4D).
When the currents of the action potential, I Na and I K, are coordinated as they are in the RGC model, the impulse frequency (in repetitive firing) is determined by external stimulus in conjunction with (typically small) intrinsic neural currents. Thus, it was previously found with morphologically reconstructed model neurons, that the electrotonic current (in the encoder region of the neuron) can significantly reduce the impulse frequencies generated by small stimulus currents (Fohlmeister and Miller, 1997b; Fohlmeister et al., 2009). It was also found that the Ca-activated K-current, I K (Ca), can similarly reduce the impulse frequencies in space clamped (single compartment) simulations (Fohlmeister and Miller, 1997a).
The top traces of Figure 5 show an impulse train of the space clamped RGC model (which implicitly includes I K (Ca)) at 37° C. The low frequency segments of that impulse train (< 2 impulses / sec) are interrupted by two periods of larger stimuli, and the three resulting impulse frequencies fall on a nearly linear F/I curve (frequency-versus-stimulus; see Fig. 5 caption), and also show that the RGC model is fully capable of generating and following very high impulse frequencies (> 1,000 impulses / sec, at 37° C).
The center traces of Figure 5 show two superposed impulse trains generated by the Hodgkin-Huxley model at 37° C, with I STIM = 21 µA/cm2 (dashed curve; which does not sustain repetitive firing), and I STIM = 21.5 µA/cm2, which does yield steady-state repetitive firing near the lowest model-attainable impulse frequency (~ 360 impulses/sec, at 37° C). The exclusion of lower frequencies lies in the model’s gating rate constants, not in the high threshold-stimulus, which can be reduced by increasing the sodium conductance, G Na (see Results). To introduce some encoding flexibility into the Hodgkin-Huxley model, therefore, requires an added mechanism to delay the onset of activation gating of I K and I Na in the interspike interval.
This was done in the bottom traces of Figure 5, for which I K (Ca) was added the Hodgkin-Huxley model (also I Ca to activate the I K (Ca)). The threshold of this compound model was also reduced to just above spontaneous firing (see Fig. 5 caption); this was necessary because the relatively small I K (Ca) becomes functionally ineffective with large I STIM. Thus, the low frequency segments of the impulse train were generated with the relatively small I STIM = 2 µA/cm2.
Note that when the stimulus is increased to I STIM = 6 µA/cm2, the individual action potentials of the impulse train become replaced by impulse-doublets (bottom left record of Fig. 5, segment 0.3 – 0.5 sec). As I STIM is further increased, the impulse-doublets are replaced by damped impulse-bursts (of the type seen in the dashed record immediately above). The impulse-bursts coalesce and convert to continuous high frequency firing when I STIM reaches 8 µA/cm2 (record segment of 0.775 – 0.85 sec). Thus the F/I curve of this compound Hodgkin-Huxley model includes a substantial range of low impulse frequencies (for I STIM < 6 µA/cm2), followed by a relatively rapid transition to the very high frequency firing characteristic of the Hodgkin-Huxley model.
This type of encoding “flexibility” may be appropriate to the head of the squid giant axon (a motor neuron), one of whose primary purposes is to induce strong and rapid mantle-contraction, resulting in escape motion, a “flight response.” The range of low impulse frequencies could serve to modulate the muscle tonus of the resting mantle, which then readily converts to high frequency impulse activity when necessary for “flight.”
Note that a kind of ‘ringing’ (high frequency oscillation) precedes the action potentials in low frequency firing by the compound Hodgkin-Huxley model (seen most clearly in the bottom-right records of Fig. 5). This ‘ringing’ (of increasing amplitude) occurs with any slowly and smoothly increasing stimulus current (‘ramp stimulus’) as the threshold of the Hodgkin-Huxley model is approached (FitzHugh, 1955). In the present case, the difference, I STIM - I K (Ca), acts as an ‘effective ramp stimulus’ on the primary spiking currents, I Na and I K. This is so because I K (Ca) declines throughout each interspike interval as the excess cytoplasmic Ca2+ is sequestered. Ca-influx during the subsequent action potential re-activates I K (Ca), and therewith resets the ‘effective ramp stimulus’ (the gating of I K (Ca) is given in Computational Procedure). It is perhaps worth noting that, although the ‘ringing’ is an active gating response of I Na and I K, the response is subthreshold and therefore remains local (i.e., near the site of impulse-initiation in multi-compartment simulations). Thus, the ‘ringing’ does not propagate with the subsequently traveling action potentials on the axon, which are more abruptly initiated by the tri-phasic electrotonic current-pulse that ‘sweeps’ along the axon with each action potential.
The ‘ringing’ is an expression of the high frequency oscillator characteristic of the Hodgkin-Huxley model, and is a direct consequence of the model’s early K-channel activation gating (see Results). Note in the right hand panels of Fig. 5, that G K > G Na throughout the interspike interval for both Hodgkin-Huxley models, in contrast to the RGC model for which G K < G Na, and which does not ‘ring.’ Note also that the magnitude-scale of the ionic conductances in the interspike interval, G K and G Na, is two orders of magnitude larger for the Hodgkin-Huxley models than for the RGC model. Finally, the compound Hodgkin-Huxley model remains highly energy-inefficient, with 86.4 % of Na+ ions entering the neuron after the peak of the action potential (at 37° C).
In assessing the Hodgkin-Huxley model for mammalian excitation, it was necessary to bridge the wide temperature span between the standard 6.3° C of the Hodgkin-Huxley model, and the mammalian 37° C (standard for the RGC model). It was noted in Results that the gating of retinal ganglion cells involves two distinct Q10 behaviors in neighboring temperature ranges (uniformly constant Q10 = 1.9 to 1.95 for T > 23° C; increasing Q10 for T < 23° C; see Fig. 4A).
This empirical Q10-behavior of RGC gating is consistent with an earlier study of K-channel activation-gating in rat skeletal muscle, which shows Q10 = 2 for the range 30° ≤ T ≤ 38° C, and Q10 = 6 in the range 1° < T < 10° C (Beam and Donaldson, 1983). Significantly, perhaps, this relatively high Q10 = 6 occurs in conjunction with a time delay in activation-gating. Such an emerging time delay can be an indication of additional kinetic steps that were previously hidden, as was proposed by Cole and Moore (1960) in an analogous situation. The hidden steps here become exposed by low temperature (in place of the pre-hyperpolarization for the “Cole-Moore shift”). As pointed out in Results, a substantial temperature range of constant Q10 (T > 23° C), with its neighboring lower temperature range of increasing Q10 also suggests that two distinct processes are simultaneously active in mammalian channel gating. Thus, the process of high Q10 (= 6 to 8; see Fig. 4A) is electro-physiologically detected because it becomes rate-limiting at low temperatures (specifically for T < 23° C), but speeds up sufficiently at high temperatures, so as to be masked (i.e., electro-physiologically hidden) by the then slower process of low Q10 (= 2).
It is remarkable that the Hodgkin-Huxley model and RGCs share a common Q10 (= 1.9 to 2) for the partial temperature range of T > 23° C (Fig. 4A), as determined from impulse-matches throughout the range of 23° to 37° C. This suggests the existence of a common gating process for the two preparations. This common process appears to be the only process in squid axon gating, because virtually the same Q10 (= 2) yields also a match with the experimental squid axon at 6.3° C, and thus extends the applicable range of Q10 = 2 for the squid axon down to 6.3° C. Because Q10 = 2 is also typical for enzyme-kinetics, this common process could be restricted to conformational changes in a single protein molecule (e.g., the Na-channel of electroplax sequenced by Noda et al., 1984). The second process – the one associated with the high Q10 in RGC gating – appears to be absent in squid axon gating.
Antibody or in-situ hybridization studies of sodium channels have shown sub-types Nav 1.1, 1.2, 1.3 and 1.6 in the retinal ganglion cell layer (Caldwell et al., 2000; Craner et al., 2003). The potassium channel subunits Kv 1.1 – 1.6 have also been reported to hybridize to ganglion cells (Hötje et al., 2007). It is possible that the kinetic differences exhibited by these channel sub-types are associated with the additional gating steps of high Q10, which could be in the nature of changing the phosphorylation state (Hidaka and Ishida, 1998), or reconfiguring polypeptide channel-subunits (Hanlon and Wallace, 2002; cf also Tiwari and Sikdar, 1999), i.e., processes whose rates may be strongly temperature-dependent. One may speculate that one (or more) of these additional processes are the molecular basis of the differences in the two models’ rate constants. Because of their slow rates at low temperatures, such processes are likely to be detrimental to excitation in the cold environment of the squid, and are therefore absent in the squid axon. Their absence could be the cause of the early onset of K-activation gating in the squid giant axon, leading to the functional differences between the RGC model (encoder), and the Hodgkin-Huxley model (oscillator). One may speculate finally, that the additional gating process(es) – whose speed (rate) is no longer a hindrance above room temperature – evolved because of the need for highly flexible impulse encoding in mammalian central neurons, as well as the desirability of energy-efficient channel gating (Attwell and Laughlin, 2001).
Numerical integration of the basic gating kinetic equations was carried out using the Runge-Kutta method with variable integration step. The error criterion: a maximum allowable difference of < 0.01 % in all variables of state (m, h, n, V, dV/dt) when the integration steps are increased by a factor of 10.
All rate constants and parameters listed under “Hodgkin-Huxley Model” are original, except modified to modern convention. The RGC model rate constants involve two principal types of modification of Hodgkin and Huxley (1952):
There is, in addition, a small reduction in the steepness of the voltage-rate-of-change in Na-activation gating (see Fig. 1B, and β m (V) below).
The (underlined) coefficients listed under “RGC Model” yield ‘matching’ action potentials (duration and amplitude) with the Hodgkin-Huxley model at 6.3° C (these correspond to RGC data at 13.9° C, see Results). The steady-state fractions of open channels, and the activation time constants of the two models are compared in Figs. 1B and 1C, respectively.
|Hodgkin-Huxley Model||RGC Model|
|α m (V):||−0.1(V + 35) / [exp(− 0.1(V + 35)) − 1]||− 0.3753(V + 35) / [exp(− 0.1(V + 35)) − 1]|
|β m (V):||4 exp[− (V + 60) / 18]||12.51 exp[− (V + 60) / 20]|
|α h (V):||0.07 exp[− (V + 60) / 20]||0.2502 exp[− (V + 52) / 20]|
|β h (V):||1 / [1 + exp(− 0.1 (V + 30))]||3.753 / [1 + exp(− 0.1 (V + 22))]|
|K-activation (delayed rectifier):|
|α n (V):||− 0.01(V + 50) / [exp(− 0.1(V + 50)) − 1]||− 0.01319(V + 37) / [exp(− 0.1(V + 37)) −1]|
|β n (V):||0.125 exp[− (V + 60) / 80]||0.2638 exp[− (V + 47) / 80]|
|α c (V):||− 0.05(V + 13) / [exp(− 0.1(V + 13)) − 1] *||− 0.1877(V + 13) / [exp(− 0.1(V + 13)) − 1]|
|β c (V):||1.667 exp[− (V + 38) / 18] *||6.256 exp[− (V + 38) / 18]|
|Open Channel Conductances [Reversal Potentials]|
|G Na [V Na]:||120 mS / cm2||[+ 55 mV]||19.425 mS / cm2||[+ 54.96 mV]|
|G K [V K]:||36 mS / cm2||[− 72 mV]||7.286 mS / cm2||[− 91.90 mV]|
|G Ca [V Ca]:||3.305 mS / cm2||[variable] *||0.535 mS / cm2||[variable]|
|G K (Ca) [V K (Ca)]:||0.247 mS / cm2||[− 72 mV] *||0.050 mS / cm2||[− 91.90 mV]|
The Ca-activated K-current, I K (Ca), is gated according to:
where the dimensionless X = [Ca 2+] i / Ca diss, with Ca diss = 10 −3 (Ca-dissociation constant in milliMolar), and variable [Ca 2+] i (cytoplasmic Ca-concentration in the same units), which is determined by the equation (Fohlmeister and Miller, 1997a):
where F = Faraday, r = 15 µm (cell radius), τCa = 50 ms (Ca-sequester time), and [Ca 2+] res = 10 −4 mM (residual cytoplasmic Ca-concentration). The Ca-reversal potential varies according to:
To obtain the gating rate constants for 37° C, apply Q10 = 2 to the above underlined coefficients for both models. This is equivalent to multiplying the underlined coefficients by the factor = 2 (T − 6.3) / 10 (= 8.398 for T = 37° C). The voltage-dependence of the rate constants remains temperature-independent.
For the RGC model, apply also the conductance Q10 = 1.47 to the above listed G Na, G K, G Ca and G K (Ca) (multiplicative factor = 3.263 for T = 37° C; cf Milburn et al., 1995; Rodriguez et al., 1998). For the Hodgkin-Huxley model, apply the conductance Q10 = 1.25 (multiplicative factor = 1.984 for T = 37° C). These Q10s are chosen to maintain model matches in impulse-amplitude at both 6.3° C and 37° C.
The reversal (Nernst) potentials were temperature-adjusted by applying the factor: (273 + T)/(273 + 6.3) to the values listed above; this factor = 1.11 for T = 37° C. Fig. 1A gives the action potential and associated membrane currents of the RGC model at 37° C.
Thanks to the Minnesota Supercomputer Institute for access to computing facilities for this study. This research was supported by NIH grant R01EY012833-06 to R. F. Miller.
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