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The intrinsic properties of distinct types of neuron play important roles in cortical network dynamics. One crucial determinant of neuronal behaviour is the cell's response to rhythmic subthreshold input, characterised by the input impedance, which can be determined by measuring the amplitude and phase of the membrane potential response to sinusoidal currents as a function of input frequency. In this study, we determined the impedance profiles of anatomically identified neurons in the CA1 region of the rat hippocampus (pyramidal cells as well as interneurons located in the stratum oriens, including OLM cells, fast-spiking perisomatic region-targeting interneurons and cells with axonal arbour in strata oriens and radiatum). The basic features of the impedance profiles, as well as the passive membrane characteristics and the properties of the sag in the voltage response to negative current steps, were cell-type specific. With the exception of fast-spiking interneurons, all cell types showed subthreshold resonance, albeit with distinct features. The HCN channel blocker ZD7288 (10 μm) eliminated the resonance and changed the shape of the impedance curves, indicating the involvement of the hyperpolarisation-activated cation current Ih. Whole-cell voltage-clamp recordings uncovered differences in the voltage-dependent activation and kinetics of Ih between different cell types. Biophysical modelling demonstrated that the cell-type specificity of the impedance profiles can be largely explained by the properties of Ih in combination with the passive membrane characteristics. We conclude that differences in Ih and passive membrane properties result in a cell-type-specific response to inputs at given frequencies, and may explain, at least in part, the differential involvement of distinct types of neuron in various network oscillations.
Information processing in neural networks depends on the behaviour of individual neurons, which is governed by both intrinsic membrane properties and synaptic inputs. Intrinsic membrane properties arise from the interaction of passive membrane properties and active conductances, i.e. the operation of voltage-gated ion channels. These built-in membrane characteristics of a cell shape the amplitude and the temporal dynamics of the neuronal response, influence the integration of synaptic inputs, and contribute to controlling the precise timing of the action potential output (Magee, 1998; Magee, 1999; Richardson et al. 2003; McLelland & Paulsen, 2009). Moreover, the presence of active conductances can endow neurons with the capability of producing intrinsic membrane potential oscillations and resonance at different frequencies (Hutcheon & Yarom, 2000). These frequency tuning properties enable the cells to respond preferentially to inputs at certain frequencies (Pike et al. 2000), and they can influence the precise spike timing of the cell relative to the ongoing network activity (Lengyel et al. 2005; Kwag & Paulsen, 2009; McLelland & Paulsen, 2009). As a net effect these features of the cells may play a significant role in setting network dynamics (Hutcheon & Yarom, 2000).
In the hippocampus pyramidal cells are known to express subthreshold resonance at frequencies within the theta range (4–7 Hz) (Leung & Yu, 1998; Pike et al. 2000; Hu et al. 2002; Narayanan & Johnston, 2007), which might contribute to their membrane potential oscillations in vivo (Ylinen et al. 1995; Kamondi et al. 1998) as well as to their discharge properties (Pike et al. 2000). Recent studies have revealed that subthreshold resonance in pyramidal cells is predominantly mediated by the hyperpolarisation-activated cyclic nucleotide-gated channels (HCN channels), which generate a non-selective cation current – termed Ih (Hu et al. 2002). In addition to having a key role in producing resonance in distinct types of neurons and its vital function in pacemaker activities as well as in network oscillations (Kocsis & Li, 2004), this conductance has been suggested to contribute to synaptic waveform normalization (Magee, 1999) and even to learning processes (Nolan et al. 2003).
In addition to pyramidal cells, cortical neuronal networks contain morphologically and functionally diverse populations of inhibitory interneurons (Freund & Buzsáki, 1996; Klausberger & Somogyi, 2008). It has been shown that some hippocampal interneurons also tend to show frequency tuning properties (Gloveli et al. 2005; Lawrence et al. 2006) and can also resonate at certain frequencies (Pike et al. 2000). However, it is still unclear which GABAergic cell types show resonance at which frequencies, and what cellular mechanisms are involved.
To understand how neuronal networks operate, detailed knowledge of the intrinsic properties of the cells that are embedded in them would appear necessary, serving as a basis for realistic modelling. Therefore, we investigated the impedance profiles of distinct types of anatomically identified neurons in the CA1 region of rat hippocampal slices. We focused on the dissimilarities in the voltage response of the cells to sinusoidal current inputs and wanted to determine the role of Ih in producing these differences. Experimental data and computational modelling indicated that impedance characteristics are cell-type dependent, and that the impedance profiles of the cells were predominantly determined by the kinetic properties of Ih in combination with the passive membrane properties of the neurons.
Animals were kept and used according to the regulations of the European Community's Council Directive of 24 November 1986 (86/609/EEC), and experimental procedures were reviewed and approved by the Animal Welfare Committee of the Institute of Experimental Medicine. Altogether 52 animals were used in this study and all the experiments comply with the policies and regulations of The Journal of Physiology given by Drummond (2009). Male Wistar rats (postnatal day 14–26) were decapitated under deep isoflurane anaesthesia, and their brains were removed into ice cold cutting solution (containing in mm: 252 sucrose, 2.5 KCl, 26 NaHCO3, 0.5 CaCl2, 5 MgCl2, 1.25 NaH2PO4, 10 glucose, saturated with 95% O2–5% CO2). Horizontal hippocampal slices (400 μm) were cut using a vibrating blade microtome (Leica VT1000S). The slices were kept in an interface chamber containing artificial cerebrospinal fluid (ACSF) at room temperature for at least 1 h before use. The ACSF had the following composition (in mm): 126 NaCl, 2.5 KCl, 26 NaHCO3, 2 CaCl2, 2 MgCl2, 1.25 NaH2PO4, 10 glucose, saturated with 95% O2–5% CO2. During the recordings the slices were kept submerged in a chamber perfused with ACSF at a flow rate of 3–4 ml min−1. All recordings were made at 34–37°C.
Whole-cell patch-clamp experiments were performed under visual guidance using a Versascope (E. Marton Electronics, Canoga Park, CA, USA) or an infrared differential interference contrast microscope (Olympus BX61WI). Electrodes were pulled from borosilicate glass capillaries (Hilgenberg, Malsfeld, Germany). Pipette resistances were 3–5 MΩ when filled with the intrapipette solution. The intrapipette solution contained (in mm): 125 potassium gluconate, 6 KCl, 4 NaCl, 10 Hepes, 10 disodium creatine phosphate, 4 Mg-ATP, 0.3 Tris-GTP (pH 7.38; 284–290 mosmol l−1). Biocytin at 5 mg ml−1 was added to the pipette solution for later morphological identification of the recorded cells. Recordings were made using an Axopatch 200B or a Multiclamp 700B amplifier (Molecular Devices, Sunnyvale, CA, USA). Data were digitised using a PCI-MIO-16-4E board (National Instruments, Austin, TX, USA). Traces were filtered at 2 kHz and digitised at 8 kHz in the current-clamp experiments and 6 kHz in the voltage-clamp experiments. Data for current-clamp experiments were acquired and analysed with Igor Pro 4.0 software (WaveMetrics, Inc., Lake Oswego, OR, USA). For voltage-clamp experiments data acquisition was carried out using the EVAN program (courtesy of Prof. I. Mody; UCLA, CA, USA) or Stimulog software (courtesy of Prof. Z. Nusser; Institute of Experimental Medicine, Hungarian Academy of Sciences, Budapest, Hungary), and analysed with Origin 7.0 software (OriginLab Corp. Northamton, MA, USA).
The extracellular solution for current-clamp experiments was ACSF as described above. In all voltage-clamp experiments 50–100 μm picrotoxin and 2–3 mm kynurenic acid (Sigma-Aldrich, St Louis, MO, USA) were added to abolish synaptic events, and 0.5 μm TTX (Alomone Labs, Jerusalem, Israel) was added to block voltage-dependent Na+ channels. Blocking the h-current was accomplished by adding 10 μm ZD7288 (4-ethylphenylamino-1,2-dimethyl-6-methylaminopyrimidinium chloride, Tocris Bioscience Ltd, Bristol, UK) to the bath solution. In voltage-clamp experiments, series resistance was compensated and was between 5 and 15 MΩ. Only cells with stable resting membrane potential and overshooting action potentials with stable amplitude were included in the study. Resting membrane potential was measured in bridge mode (I= 0) immediately after obtaining whole-cell access. Reported values for membrane potential were not corrected for the liquid junction potential.
From perisomatic region-targeting interneurons only those cells were included in this study which could be identified unequivocally as fast-spiking interneurons based on their action potential phenotype. These cells were characterised by a fast-decaying afterhyperpolarisation (AHP) measured at 25% of the AHP amplitude (less than 3.2 ms) and by the small width of action potentials determined at half peak amplitude of the first and the last action potentials of the train (less than 0.5 ms; for 800 ms, 0.2 nA pulses) (Han, 1994; Pawelzik et al. 2002; Lien & Jonas, 2003). To validate that the classification is not sensitive to this particular choice of parameters, we also did principal component analysis on 20 different parameters related to the action potential phenotype and firing pattern of these cells, and, by choosing an appropriate threshold value for the first principal component, obtained identical results.
The basic physiological characteristics of the cells were determined from the voltage responses to a series of hyperpolarising and depolarising square current pulses of 800 ms duration and amplitudes between −200 and 200 pA, at 20 pA intervals from a holding potential of −60 mV. To estimate the membrane time constant and the total membrane capacitance at −60 mV, single exponential functions with a common decay time constant were fitted simultaneously to the voltage responses to the five smallest amplitude hyperpolarising current steps (−20 to −100 pA) between 5 and 37.5 ms after the onset of the pulse. The median value of the membrane capacitance estimated from these fits was used. In order to estimate the input resistance of the cell, double exponential functions were fitted to the voltage traces during the current step, and the minimum and steady-state voltage values were determined (this procedure also allowed us to characterise the voltage sag; see below). Estimated steady-state voltage responses were then plotted against current amplitude for the five smallest amplitude hyperpolarising current steps (−20 to −100 pA), and the input resistance at −60 mV was estimated from the slope of the linear regression through these points (Fig. 2A).
In many cells, a voltage sag was observed in response to a hyperpolarising current pulse. We characterised this voltage sag by fitting the difference of two exponential functions to the membrane potential during the pulse (see above). The sag responses were described quite accurately by this class of function; our choice of functional description was further motivated by the fact that the response of a simple model of Ih-containing neurons (the linearised Ih model, described below) can be calculated analytically, and also predicts a sag shaped as a difference of exponential functions. Fitting a continuous function to the data allowed us to robustly estimate the relative sag amplitude, defined as the ratio of two differences in membrane potential: the difference between the minimum voltage during the sag and the steady-state voltage later in the pulse, and the difference between the steady-state voltage and the membrane potential measured immediately after the beginning of the step (see Fig. 2B). We also determined the peak delay, defined as the time of the negative peak of the membrane potential relative to the beginning of the current pulse. Both the relative sag amplitude and the peak delay were calculated for the five largest amplitudes of the negative current steps (−120 to −200 pA), and their median values were used to characterise the sag in each cell.
To determine the impedance profile and subthreshold resonance properties of each cell, 3 s-long sinusoidal currents were injected into the cells with a peak-to-peak amplitude of 120 pA at fixed frequencies (0.5, 1, 2, 3, 4, 5, 6, 7, 8, 9, 10, 15, 20, 40 Hz). This amplitude represented the optimal trade-off between linearity (which requires a small input) and signal-to-noise ratio (which is better for large signals). Since the neuronal impedance is in general voltage dependent, measurements were repeated at different subthreshold membrane potentials (−60, −70, −80, and in some cases at −90 mV). These baseline potentials were manually adjusted by direct current (DC) injection through the recording electrode. The complex impedance value (Z) at a given frequency (f) was determined by calculating the fast Fourier transform (FFT) of the voltage response and dividing the FFT component corresponding to the input frequency by the equivalent FFT component of the input current. We found that 3 s-long sinusoidal currents allowed us to estimate both the amplitude and the phase of the voltage response at a high level of precision, even for the lowest reported frequencies (see Supplemental Material).
The magnitude of the impedance was plotted against input frequency to give the impedance magnitude profile. In order to facilitate the comparison of multiple impedance magnitude profiles, we characterised the impedance magnitude curves by four summary statistics. First, we measured the impedance value at the lowest input frequency (0.5 Hz), Z(0.5 Hz). Cutoff frequency (fcutoff) was defined as the input frequency at which the magnitude of the impedance first dipped below (this definition returns the classic cutoff frequency for a passive linear cell, where R≈Z(0.5 Hz)). Since many of our cells displayed a clear peak in the impedance magnitude profile at some nonzero frequency, we also defined the resonance magnitude (Q) as the impedance magnitude at the resonance peak (maximal impedance value) divided by the impedance magnitude at the lowest input frequency (0.5 Hz), i.e. Q=Zmax/Z(0.5 Hz) (Hutcheon et al. 1996b). Finally, the frequency of maximal impedance (fmax) was determined as the frequency at which the maximum impedance magnitude value was detected. In those cells that showed no peak in their impedance profile (Q= 1), fmax is equal to 0.5 Hz.
The phase of the impedance (which equals the difference between the phases of the voltage and current oscillations) was also determined and plotted as a function of frequency to define the phase profile of the neuron. Since positive values of this quantity (i.e. the response leading the input) indicate a membrane with non-linear properties with potential computational significance (see Results and Discussion), following Narayanan & Johnston (2008) we defined ΦL as the area under the positive part of the phase profile. This is a robust measure of the resonance properties of the membrane. Finally, we combined the magnitude and phase of the impedance to obtain the complex-valued impedance of the neuron. A plot of the complex impedance for all frequencies (i.e. a plot of the imaginary part of the impedance against the real part as frequency varies, known as a Nyquist plot) is a useful indicator of the basic properties of a system, and is widely used in engineering applications.
In order to determine the properties of Ih, 800 ms-long voltage-clamp steps were given in −10 mV increments up to −120 mV from a holding potential of −40 mV. Since Ih has quite slow activation kinetics, rather long voltage steps are needed to activate the current fully at a given membrane potential. However, most of the interneurons proved to be sensitive to prolonged hyperpolarising pulses, and therefore we adjusted our protocol to have the shortest possible voltage step that still enabled us to measure the current. Nevertheless, we note that the shortness of the steps, in combination with the voltage-dependent kinetics of Ih, may cause some negative shift (up to a few mV) of the estimated activation curves.
Ih was obtained by subtracting the current traces before and after the application of 10 μm ZD7288, a specific blocker of HCN channels (Harris & Constanti, 1995). This current difference trace during the voltage step was used to determine the time constant(s) of Ih activation as well as the steady-state current, while the tail current recorded immediately after the end of the step was used to estimate the steady-state activation function. To determine the time constant(s) of Ih activation, either a single- or a double-exponential model was fitted to the difference current recorded from 20 ms after the beginning of the voltage step to the end of the step. The steady-state current was determined concurrently for all step potentials by fitting exponential functions with a common time constant to the current traces during the late phase (last 500 ms) of the voltage step. The Ih activation curve was calculated by fitting single exponential functions to the tail current between 2 and 20 ms after the end of the voltage step (the first 2 ms were excluded to ignore fast transients), and extrapolating back to the end of the step to determine the instantaneous tail current. We then plotted the tail current as a function of the step potential, and fitted a sigmoidal function:
where Imax is the asymptotic maximum of the sigmoid, V1/2 is the potential of half-maximal Ih activation, and is the slope of the activation function at V1/2. The measured tail current values at each voltage were then divided by Imax to arrive at the activation function for each cell.
The Ih reversal potential for each cell type was calculated for a subset of our cells from the open-channel I–V relationship, which was obtained by the following protocol: Ih was activated with an 800 ms-long pulse to −120 mV and this was followed by steps to different test potentials (from −110 to −40 mV in +10 mV increments). The instantaneous I–V plot was constructed from the tail current amplitudes measured at each test potential in the same way as described above, and a straight line was fitted through the data points. The reversal potential of Ih was defined as the voltage at which the fitted line crossed the V axis.
Once the Ih reversal potential was known, the maximal conductance of Ih in each cell could be determined from the steady-state I–V relationship. Assuming a sigmoidal form for the activation function, the steady-state current can be written as:
where is the maximal Ih conductance, and Eh is the Ih reversal potential. Three parameters of this function (, V1/2 and m) were optimised to fit the measured I–V relationship, resulting in an estimate of the maximal conductance value for each cell.
Since, in many cases, data were not normally distributed (according to a Lilliefors test), non-parametric statistical tests were used whenever possible. We employed Wilcoxon's signed rank test to compare medians from two groups. When comparing more than two groups, a Kruskal–Wallis test was used, often followed by post hoc comparisons based on average ranks using Tukey–Kramer critical values to account for multiple comparisons. However, in a few cases for which no appropriate non-parametric test has been established (such as in a three-way design, or a two-way design combining between- and within-subject factors), conventional parametric tests (such as ANOVA) were used. Summary statistics are also displayed in a form appropriate for non-Gaussian distributions, including box plots, which indicate the median of the data as well as its interquartile range, with whiskers showing the full range of the data, and extreme outliers (data points outside 2.5 times the interquartile range) marked by crosses outside the whiskers. The notch around the median value indicates a robust estimate of the confidence of the median, such that non-overlapping notches for two groups mean that the two medians are significantly different at the 5% level.
Comparisons of the goodness of fit between models with a different number of free parameters were performed using the Bayesian information criterion (BIC) (Bishop, 2006). The BIC attempts to compensate for the fact that better fits are more easily achieved with more complex models by penalising models according to the number of free parameters. For each model we calculate the quantity:
where RSS is the residual sum of squares for the model, n is the number of data points, and k is the number of free parameters. Then, out of two or more models of the same data set, the best model is the one for which the quantity defined by eqn (3) is the smallest.
The methods for anatomical identification have been described in detail in Gulyás et al. (1993). Briefly, the recorded cells were filled with biocytin during the recording. After the recording the slices were fixed in 4% paraformaldehyde in 0.1 m phosphate buffer (PB; pH 7.4) for at least 1 h, followed by washout with PB several times and incubation in 30% sucrose in 0.01 m PB for at least 2 h. Then slices were freeze-thawed three times above liquid nitrogen and treated with 1% H2O2 in PB for 15 min to reduce the endogenous peroxidase activity. Recorded cells were visualised using avidin-biotinylated horseradish peroxidase complex reaction (Vector Laboratories Inc., Burlingame, CA, USA) with nickel-intensified 3,3′-diaminobenzidine as chromogen giving a dark reaction product. After dehydration and embedding in Durcupan, representative neurons were reconstructed using a drawing tube.
In an attempt to capture quantitatively the experimentally measured impedance profiles of single hippocampal neurons, single-compartment models of varying complexity were constructed and their parameters were optimised. The simplest model, which will be referred to as the passive model, contained only the membrane capacitance and a (voltage-independent) leak conductance. The temporal evolution of the membrane potential (Vm) in this model cell can be described by the following equation:
where C is the total capacitance of the neuron, gl is the leak conductance, El is the reversal potential of the leak current, and Ii is the external current injection.
The second model (called the Ih model) also contained, in addition to the membrane capacitance and the leak conductance, a voltage-gated hyperpolarisation-activated conductance, which was described by a Hodgkin–Huxley-type formalism with a single gating variable, and whose parameters matched the properties of Ih in different cell types as determined in our experiments. This model is defined by the following set of equations:
where is the maximal conductance of Ih, mh is the gating variable for the activation of Ih, Eh is the Ih reversal potential, while is the steady-state value and τh (Vm) is the time constant for changes in mh as a function of Vm.
For both of the above models, the impedance profile (the amplitude and phase of the voltage response to small-amplitude sinusoidal current injection as a function of input frequency) could be determined analytically by linearising all the defining equations in the vicinity of a given baseline potential. The explicit formulae derived in this manner allowed us to explore how the various parameters affect impedance, and vastly simplified the task of finding the optimal set of parameters to fit experimental data. Linearisation involved neglecting terms of second and higher order in the difference between the current membrane potential and the baseline potential in both the membrane voltage equation and the expressions for steady state activation of conductances, and neglecting the voltage dependence of the time constant of all voltage-gated conductances. The rationale for and further details of this procedure may be found in Hutcheon et al. (1994). For the passive model, this approach is exact (since the model is linear to begin with), and results in the following expression for the impedance of the membrane:
where ω= 2πf, and f is the frequency of the oscillating input. Taking the absolute value of the complex impedance reproduces the well-known expression for the impedance magnitude.
In the Ih model, linearisation involved approximating the steady-state activation of Ih as (where V0 is the membrane potential in the absence of the oscillating input, b is the slope of the function at V0), and taking a voltage-independent value for τh. This allowed us to assume that, in response to a sinusoidal current injection, both Vm and mh have a sinusoidal time dependence at the input frequency, and the amplitude and phase of these oscillations (relative to the input current) can be determined from eqns (5) and (6), producing the following formula for the (complex) impedance of the Ih model:
Using the whole-cell patch-clamp method, we recorded from hippocampal neurons located in the stratum oriens or pyramidale of the CA1 region. During the recording the cells were filled with biocytin and morphologically identified post hoc on the basis of their dendritic and axonal arborisation. In addition to pyramidal cells (PCs, n= 27, Fig. 1A), three interneuron types were recognized. Those interneurons that could not be unambiguously classified as belonging to any one of these categories were excluded from the present study.
One group of interneurons had cell bodies and smooth or sparsely spiny horizontal dendrites restricted to the stratum oriens. Their axon, which predominantly originated from the soma, ramified sparsely in strata radiatum and oriens and carried en passant and often drumstick-like boutons, which were distributed irregularly along them (Fig. 1A). Some of the axon collaterals could be followed to the subiculum or to the CA3 region. The overall appearance of their axon cloud was spread out longitudinally compared to the other two interneuron types (see below). These neurons resembled a class of cells that were earlier characterised by Gulyás et al. (2003), Hájos et al. (2004) and Goldin et al. (2007) in slice preparations, and by Jinno et al. (2007) in intact brain. Although these neurons may represent a heterogeneous population of inhibitory cells including local interneurons as well as GABAergic cells with long-range projections (such as backprojecting cells, oriens retrohippocampal projection cells, or double projection cells based on the review of Maccaferri, 2005 and Klausberger & Somogyi, 2008), their physiological features were rather comparable; therefore the data obtained in neurons with this type of morphology were pooled under the name of oriens–radiatum (O-R) cells (n= 24). This name only refers to the fact that the axon collaterals of these neurons were restricted to the strata oriens and radiatum in hippocampal slices, and may not correspond to a functional category.
Another group of interneurons also had both the cell body and dendritic tree in the stratum oriens, but their horizontally running dendrites were often densely decorated with long spines. Their axon frequently originated from a proximal dendrite, and after ramification the main axon without boutons could be followed into the stratum lacunosum-moleculare. In this layer the axon ramified extensively bearing heavily packed varicosities. Some axon collaterals with boutons were also observed in the stratum oriens. These neurons were identified as oriens–lacunosum-moleculare (OLM) cells (n= 26) (Fig. 1A; McBain et al. 1994).
The somata of the third group of interneurons were also found in the stratum oriens, sometimes in the close vicinity of the stratum pyramidale. Their aspiny or sparsely spiny dendritic tree had either horizontal or vertical orientation, and the axonal arbour was predominantly located in the stratum pyramidale (Fig. 1A). Thus, these interneurons belonged to the perisomatic region-targeting inhibitory cells, which comprise both basket cells and axo-axonic cells (Freund & Buzsáki, 1996). Since the light microscopic examination of these interneurons did not allow us to unequivocally distinguish them from each other, data from all perisomatic region-targeting interneurons were pooled. Moreover, only those neurons were included in the following physiological comparison that could be classified as fast spiking cells based on the properties of their action potentials evoked by 800 ms long, 0.2 nA current pulses (n= 7). Therefore, we refer to them as fast-spiking perisomatic region-targeting interneurons (FS PTIs).
We first determined the apparent passive membrane properties (i.e. input resistance and time constant) of the neuronal classes included in our study by injecting small-amplitude hyperpolarising current steps (see Methods). Both input resistance and membrane time constant varied significantly among the different cell types (Kruskal–Wallis (KW) test, P < 0.001). Multiple post hoc comparisons (see Methods) indicated that OLM cells (n= 12) had a significantly higher input resistance than PCs (P < 0.01, n= 19) and FS PTIs (P < 0.05, n= 7) (Table 1). OLM cells also had a significantly slower membrane time constant at rest than any other cell type studied (OLM vs. PC: P < 0.001; OLM vs. O-R: P < 0.05; OLM vs. FS PTI: P < 0.001) (Table 1). In order to facilitate later comparisons with models that directly include capacitance as a parameter, we also estimated the membrane capacitance from the small-amplitude transient responses. Capacitance varied significantly between cell types (KW test, P < 0.01); in particular, OLM cells had a significantly larger capacitance than O-R cells (n= 11) and FS PTIs (both P < 0.05) (Table 1). The resting membrane potentials were estimated to be −62.4 ± 2.4 mV for PCs (n= 21), −55.4 ± 9.5 mV for O-R cells (n= 17), −55.7 ± 6.5 mV for OLM cells (n= 19) and −50.4 ± 8.1 mV for FS PTIs (n= 7) (data presented here as means ±s.d.).
We observed a sag in the voltage response of PCs, O-R cells and OLM cells to negative current steps of suitable magnitudes (Figs 1B and and2A).2A). In these cells a rebound depolarising hump could also be detected after the offset of the current step and in a few interneurons some rebound spikes could be observed as well (in 5 out of 17 O-R cells and in 4 out of 19 OLM cells). Both the sag and rebound depolarisation were eliminated by bath application of the specific Ih blocker, ZD7288 (10 μm; data not shown). The properties of the sag varied substantially between the cell types (Fig. 2C,D). In particular, the cell types differed significantly in the relative sag amplitude (P < 0.001, KW test), and post hoc multiple comparisons indicated that O-R cells and OLM cells had a significantly larger relative sag amplitude than PCs (O-R vs. PC: P < 0.001; OLM vs. PC: P < 0.01) and FS PTIs (both P < 0.001) (Fig. 2C). The time taken to reach the negative peak amplitude of membrane potential during the current step (i.e. peak delay) also varied significantly between cell types (P < 0.001, KW test). OLM cells, in particular, had a significantly slower sag than PCs and O-R cells (both P < 0.001, post hoc multiple comparisons as detailed above) (Fig. 2D).
Qualitatively, PCs (n= 18 out of 19) displayed a small but rather fast sag, O-R cells (n= 11) had the largest and fastest sag, while OLM cells (n= 12) usually showed a large but relatively slow sag. In 2 out of 7 fast-spiking cells some Ih-mediated sag could be observed, but even in these particular neurons the sag was rather small and tended to appear only at very negative potentials (more negative than −90 mV).
These data suggest that, in addition to passive membrane characteristics, the properties of some active conductances such as the non-selective cation conductance mediating Ih, might be different between these cell types.
The differences in sag characteristics among cell types suggest that the Ih-dependent resonance could also be dissimilar. In order to characterise the subthreshold impedance profiles and possible resonance properties of the cells, a 3 s-long sinusoidal current was injected into the cells at different membrane potentials negative to the firing threshold (Fig. 3). Impedance magnitude and phase curves were characterised by five summary statistics (Table 2): impedance at 0.5 Hz (Z(0.5 Hz); this quantity can also be used as an estimate of the input resistance of the cell, which, by definition, is the same as the impedance magnitude at 0 Hz), cutoff frequency (fcutoff), resonance magnitude (Q), the frequency of maximal impedance (fmax) and total inductive phase (ΦL), as described in Methods. These quantities were then compared statistically between the different cell types and experimental conditions.
We found that cell type had a significant effect on all five of the derived statistics: Z(0.5 Hz), fcutoff, Q, fmax and ΦL (P < 0.001 in each case, KW test; Fig. 3B–D). Multiple comparisons indicated that PCs had a significantly smaller Z(0.5 Hz) than OLM cells and O-R cells (both P < 0.001) and FS PTIs also had a smaller Z(0.5 Hz) than OLM cells (P < 0.01); fcutoff was significantly lower in OLM cells than in any other cell type studied (all P < 0.001); Q was significantly larger in PCs, O-R cells and OLM cells than in FS PTIs (P < 0.001 for PCs and O-R cells, and P < 0.05 for OLM cells) and it was significantly larger in PCs than in OLM cells (P < 0.01); PCs had a significantly higher fmax than any other cell type (all P < 0.001), and fmax was also significantly higher in O-R cells than in OLM cells (P < 0.01) and FS PTIs (P < 0.01). ΦL was significantly smaller in FS PTIs than in O-R cells (P < 0.001) and in PCs (P < 0.05) (Fig. 3D). In addition, the shape of the impedance profiles changed with variations in baseline membrane potential (Fig. 3). In particular, a two-way analysis of variance (ANOVA) using cell type as between-subject factor and membrane potential as within-subject factor showed that three of the summary statistics varied significantly with membrane potential (Z(0.5 Hz): P < 0.001; fcutoff: P < 0.001; ΦL: P < 0.05).
To separate cells with a monotonically decreasing impedance profile from those with resonance, resonating cells were defined as cells with a Q value greater than 1.05 at any of the investigated membrane potentials. We found that all PCs showed resonance (n= 9), indicated as a clear peak in the impedance curve. Resonance was most prominent at hyperpolarised potentials (at −70 and −80 mV), but was also apparent (though weaker) at depolarised potentials (Fig. 3B and D). The fmax values fell into the theta range (4–6 Hz) (Fig. 3D). Almost all O-R cells also exhibited resonance (n= 15 out of 16), although a rather large variance could be seen in Q values; fmax was between 2 and 6 Hz. Ten out of 15 OLM cells also showed resonance, but the resonance frequency fell in the range of 1–3 Hz. An obvious resonance peak could be observed in only 1 out of 7 FS PTIs at the investigated membrane potentials (Fig. 3B and D).
In line with the prediction based on the sag characteristics, both the impedance profiles and the resonance properties were found to vary substantially between the cell types. Therefore, we next investigated the contribution of Ih to their impedance profiles.
Ih is an active conductance, which was shown to be essential for the emergence of resonance behaviour in some neurons (Hutcheon et al. 1996b; Lüthi & McCormick, 1998; Hu et al. 2002; Narayanan & Johnston, 2007). In our experiments only those cells that showed an Ih-dependent sag showed subthreshold resonance. Furthermore, the application of 10 μm ZD7288, a blocker of HCN channels, strongly reduced or eliminated the sag in all cell types (P < 0.001 overall, and P < 0.05 in each individual cell type except FS PTIs). ZD7288 also had a moderate effect on passive membrane properties at −60 mV, increasing both the input resistance (P < 0.05 overall) and the apparent membrane capacitance (P < 0.001 overall) (Table 3). Therefore, the effect of ZD7288 on the impedance profile was tested in each of the investigated cell types. A three-way ANOVA, with cell type as a between-subject factor, and membrane potential and ZD7288 treatment as within-subject factors, indicated that ZD7288 had a significant effect on all five of our summary measures (Z(0.5 Hz), fcutoff, Q, fmax, and ΦL; Fig. 4). In particular, the blockade of HCN channels significantly increased Z(0.5 Hz) in PCs (n= 9, P < 0.001), O-R cells (n= 6, P < 0.01) and OLM cells (n= 7, P < 0.01) and significantly decreased fcutoff in the same three cell types (PCs: P < 0.001; O-R cells: P < 0.01; OLM cells: P < 0.001). Most importantly, ZD7288 completely abolished the resonance, resulting in a significant reduction in the Q value in PCs (P < 0.001), O-R cells (P < 0.01) and in OLM cells (P < 0.05) (Fig. 4). The elimination of resonance by ZD7288 was also evident in the change in fmax, which was significant in PCs (P < 0.001), O-R cells (P < 0.01) and in OLM cells (P < 0.01), and in ΦL, which was significantly reduced in the same three cell types (PCs: P < 0.001; O-R cells: P < 0.01; OLM cells: P < 0.05). However, ZD7288 had no effect on the shape of the impedance profile (as characterised by these five quantities) at any of the investigated membrane potentials in FS PTIs (n= 4) (Fig. 4).
These results suggest that Ih is essential for subthreshold resonance in pyramidal cells, O-R cells and OLM cells, and that it contributes substantially to the shape of the impedance profile even in some cells without a clear resonance, e.g. in some of the OLM cells. We also found that the shape of the impedance profile varied substantially between different cell types. Therefore, we set out to investigate whether the observed differences in the impedance curves among cell types might be due to distinct properties of Ih.
To examine the differences in the properties of Ih between the cell types (excluding FS PTIs since their impedance curve was not substantially affected by ZD7288 application), whole-cell voltage-clamp experiments were performed (Fig. 5A). First, the voltage-dependent activation of Ih was measured based on the instantaneous tail current at the end of 800 ms steps to different potentials (see Methods). We found that Ih was significantly more activated in PCs than in interneurons at all potentials between −60 and −100 mV; there was no significant difference between O-R cells and OLM cells at any membrane potential (Fig. 5B). Based on sigmoidal fits to activation values, the potential of half-maximal Ih activation (V1/2) was −82.9 ± 4.9 mV in pyramidal cells (n= 6), −97.3 ± 4.7 mV in O-R cells (n= 7) and −97.7 ± 5.0 mV in OLM cells (n= 7, Fig. 5B). The slope of the activation function was similar in all cell types: the parameter m was −12.4 ± 1.9 mV in PCs, −10.2 ± 2.7 mV in O-R cells and −8.9 ± 4.0 mV in OLM cells. No significant difference was found in the Ih reversal potential – measured using the instantaneous I–V plot, see Methods– between the different cell types (−33.0 ± 13.4 mV in PCs (n= 3), −38.8 ± 2.9 mV in O-R cells (n= 4), and −37.0 ± 5.9 mV in OLM cells (n= 4)). Therefore, reversal potential values from all cells were pooled and averaged to arrive at a single figure (−36.6 mV) that was used in all subsequent calculations and models (Fig. 5H and I). Next, we determined the maximal Ih conductance in each cell based on the steady-state current (Fig. 5C). We found no significant difference between the cell types, and a substantial variation within any given class (4.1 ± 1.9 nS in PCs, 5.9 ± 2.8 nS in O-R cells, and 4.6 ± 1.8 nS in OLM cells (data presented here as means ±s.d.) (Fig. 5J).
Finally, we analysed the kinetics of Ih by fitting either single or double exponential functions to the time course of Ih activation at different membrane potentials. Although the time course could be described fairly accurately using a single exponential function (Fig. 5D), a better fit was seen when a double exponential function was used, and the two components could be clearly identified in essentially all cells, with little variation within a given cell type (Fig. 5E,F). The single exponential fit indicated that activation of Ih was significantly faster at all membrane potentials between −80 and −120 mV in PCs than in O-R cells (P < 0.001 between −80 mV and −100 mV, and P < 0.01 at −110 and −120 mV) and OLM cells (P < 0.001 at all voltages in this range). The double exponential fit clearly identified a fast (time constant, 20–50 ms) and a slower (100–500 ms) component of Ih activation in all cell types. Both components tended to be slower in interneurons than in PCs, a difference that reached significance at some (more hyperpolarised) membrane potentials. However, the most substantial difference was in the relative weight of the two components: the activation of Ih was dominated by the fast component at all membrane potentials in PCs, while the two components contributed almost equally in interneurons (Fig. 5G). No significant difference was seen in the kinetics of Ih activation between O-R cells and OLM cells. The activation kinetics were found to be voltage dependent in all cell types investigated, approximated either with single or double exponential functions (Fig. 5D–F).
In summary, differences in the properties of Ih– specifically, the voltage dependence of steady-state activation and the kinetics of activation – between PCs and the two classes of interneuron with subthreshold resonance suggest that PCs and investigated interneuron types may express distinct subunit compositions of HCN channels, and that this may account for some of the differences in the impedance profiles between different cell types. On the other hand, the lack of any such difference in Ih characteristics between O-R cells and OLM cells, two cell types with distinct impedance profiles, indicates that factors other than the magnitude and kinetic properties of Ih are responsible for the observed variation in their impedance properties.
To provide a quantitative account of the observed differences in the impedance profiles and resonance properties between the different cell types, we fitted the impedance profiles of single-compartment, conductance-based model neurons to those measured experimentally. The simpler model contained a membrane capacitance and a leak conductance, while the more complex model also included a voltage-gated conductance (see Methods for details). The main advantage of using models of such moderate complexity is that the impedance profile could be computed analytically by linearising the defining equations around an arbitrary baseline potential (see Methods). The relatively small number of parameters in these models also allowed us to determine, using standard non-linear optimisation algorithms, the optimal set of parameters to fit a particular set of impedance profiles (see below).
We determined and compared the best fits to individual impedance profiles using the passive model and the linearised Ih model; examples of the fits for each cell type are shown in Fig. 6A–C (where amplitude, phase, and complex impedance are displayed separately). The passive model has only three free parameters (the input resistance, the total capacitance of the cell, and an additive serial resistance), while the linearised Ih model has five effective free parameters. (It has a total of seven parameters: the capacitance, the leak conductance, the maximal Ih conductance, the value of the activation variable at the baseline potential, the derivative of the activation variable with respect to voltage at the baseline potential, the time constant of the activation of Ih, and the series resistance, but these quantities appear only in certain combinations in the expression for the impedance, eqn (8), which reduces the number of actual free parameters to five.) We used the Bayesian information criterion (BIC, which takes into account the number of free parameters, see Methods) to compare the quality of the best fit in the two models (Fig. 6D). We found that the Ih model described the control impedance curves of PCs, O-R cells and OLM cells better than the passive model (median r2= 0.991 vs. 0.904 in PCs; r2= 0.992 vs. 0.949 in O-R cells; r2= 0.993 vs. 0.978 in OLM cells), and the value of the BIC was lower for the Ih model in these cell types, indicating that the Ih model is better even when we take into account the difference in the number of free parameters. On the other hand, the two models were about equally good at describing single control curves in FS PTIs (median r2= 0.976 for both models), and the BIC in this case favoured the passive model. In contrast, for the impedance curves measured in the presence of ZD7288, the Ih model did not perform significantly better than the passive model for any cell type (median r2= 0.992 for both models in PCs; r2= 0.983 for both models in O-R cells; r2= 0.977 vs. 0.976 in OLM cells; r2= 0.955 vs. 0.954 in FS PTIs); in fact, the simpler passive model was found to be better in all cell types according to the BIC. These results suggest that Ih makes an essential contribution to the shape of the impedance profile in PCs, O-R cells and OLM cells, converting a basically passive impedance curve into one that is more adequately described by assuming voltage-dependent mechanisms.
Next, we wanted to determine whether the presence of Ih in itself (in combination with appropriate passive characteristics) is sufficient to explain the observed impedance profiles of hippocampal neurons. We also wished to understand to what extent the observed differences in impedance curves between the different cell types could be due to differences in the properties of Ih itself, as described in the previous section. Thus, for each individual neuron, we simultaneously fitted all the available impedance curves (measured under control conditions at different baseline membrane potentials) using the linearised Ih model, with the properties of Ih (the value and the slope of the steady-state activation and the time constant, all at the appropriate membrane potentials) set according to our voltage-clamp data for the given cell type, and only four free parameters (capacitance, leak conductance and maximal Ih conductance of the neuron, and an additional series resistance) to fit for each cell. This is a much more heavily constrained fit than the ones considered above (which had 3–5 free parameters for every impedance curve, and thus up to 20 for each cell); here, the four fitted parameters are assumed to be the same at all membrane potentials in a given cell, and we constrain the voltage-gated conductance to have the cell-type-specific characteristics that we measured for Ih. Typical examples of the fit attained in different cell types are shown in Fig. 7A–C in the form of frequency–amplitude, frequency–phase, and complex (Nyquist) plots. The quality of the fit was fairly good in all cell types (median r2= 0.941 in PCs; r2= 0.931 in O-R cells; r2= 0.959 OLM cells), especially considering the small number of free parameters, indicating that Ih (in combination with passive membrane properties) is the main determinant of the subthreshold impedance profile in these cells. Importantly, the range of parameters determined through the fitting procedure (in particular, the total capacitance and the maximal Ih conductance) was in good agreement with the values measured in the experimental current-clamp and voltage-clamp protocols (Fig. 7D; cf. Fig. 2 and Fig. 5). Notably, our resonance fits predicted a significantly larger membrane capacitance in the OLM cell population than in the population of O-R cells (P < 0.01; Wilcoxon rank sum test), while there was no significant difference in the maximal conductance of Ih between the two cell types. Both of these conclusions are in agreement with our experimental measurements, and suggest that the observed differences between the impedance profiles of OLM cells and O-R cells are primarily due to a difference in passive properties rather than a difference in the kinetics or magnitude of a voltage-gated conductance (i.e. Ih).
Finally, some systematic deviations of the data from the fitted curves were also evident. These were quantified by computing for the fitted curves the five summary statistics we had defined for the characterisation of impedance profiles, and comparing them with the same statistics computed from the actual data (Fig. 7E). We found that the Ih model was able to capture the overall shape of the impedance profiles as measured by the input resistance and the cutoff frequency quite accurately. On the other hand, the degree of resonance (as measured by Q and Φtotal) and the resonant frequency were less well predicted. In particular, the fits consistently predicted a larger degree of resonance (a higher Q value) in interneurons (but not in PCs) than the value determined directly from the data. Thus, the single-compartment Ih model provides a fairly good but still incomplete account of the impedance profiles of the neurons in our study, and factors not included in this model (such as dendritic morphology, the subcellular localization of Ih, or additional voltage-gated conductances) might also contribute to the measured impedance characteristics.
Our results show that the impedance profiles of neurons calculated from their voltage responses to sinusoidal current inputs differ in pyramidal cells and different classes of interneurons investigated in the CA1 region of the hippocampus. Using electrophysiological measurements combined with computational modelling we could demonstrate that these differences arise primarily from differences in the activation properties of Ih, but the passive membrane properties of the cells also made significant contributions.
We found, in agreement with previous results, that the subthreshold resonance at theta frequencies in PCs is dependent on Ih (Hutcheon et al. 1996b; Pape & Driesang, 1998; Dickson et al. 2000; Hu et al. 2002; Fransén et al. 2004; Narayanan & Johnston, 2007). In addition to the Ih-mediated resonance, a so called M-resonance, produced by a depolarisation-activated potassium current below the firing threshold has also been described in PCs (Hu et al. 2002, 2009; Peters et al. 2005). According to their findings this type of resonance occurs at about −60 mV, whereas the Ih-mediated resonance they observed was only seen below −70 mV. The apparent lack of M-resonance in our experiments can be explained by the fact that we observed Ih-mediated resonance at −60 mV, suggesting that M-resonance might only be seen at more depolarised potentials, and possibly only above spike threshold under our conditions.
We found that horizontal interneurons of the stratum oriens were not uniform in their impedance properties. Although both O-R and OLM cells showed some frequency preference due to active membrane conductances, because of their high capacitance and low cutoff frequency the low-pass filter properties still dominated in OLM cells. Our results verify the earlier observations by Pike et al. (2000), in which some interneurons in the stratum oriens were shown to display resonance, and extend it by showing that not all oriens interneurons have the same high-pass characteristics. The finding that O-R cells and OLM cells have distinct impedance properties raises the possibility that similar synaptic input received by these two cell types (Blasco-Ibanez & Freund, 1995) may result in different discharge patterns during specific network events, such as theta and gamma rhythms or sharp-wave-associated ripple oscillations (Klausberger et al. 2003; Gloveli et al. 2005; Lawrence et al. 2006; Goldin et al. 2007; Jinno et al. 2007).
Previous studies (Aponte et al. 2006) and our observation that some FS PTIs (2 out of 7) expressed a minor sag indicate that Ih could also be present in this cell type. However, Ih does not seem to have any effect on the impedance profile of these cells at the investigated potentials. Whereas Ih-mediated subthreshold resonance was negligible in FS PTIs (present study, Hutcheon et al. 1996b), these cells exhibited obvious resonance at gamma frequencies in a study by Pike et al. (2000). This type of resonance is mediated by activation of persistent voltage-dependent sodium channels, opening at membrane potentials positive to −60 mV. Thus, under our conditions this form of resonance would not be expected, since we obtained recordings only at or negative to −60 mV. However, it is apparent already at these subthreshold membrane potentials that their fast membrane time constant and correspondingly high cutoff frequency would allow these cells to be capable of transmitting high frequency inputs.
Although ZD7288 is a widely used inhibitor of Ih (Harris & Constanti, 1995; Gasparini & DiFrancesco, 1997), it should be noted that ZD7288 may have unspecific effects on synaptic transmission (Chevaleyre & Castillo, 2002). However, these non-specific effects of ZD7288 were observed only after long application of the drug in rather high concentrations (~50 μm). Thus, it seems unlikely that our results were influenced in any major way by unspecific effects of ZD7288.
Since subthreshold resonance seemed to be related to the occurrence of the membrane potential sag, which also showed significant differences among the investigated cell types, our initial supposition was that distinct resonance properties could arise from the differences in Ih properties among the different cell types. Our data revealed no significant differences between the absolute amounts of Ih-mediated conductance in the investigated cell types. However, as the observed differences in apparent membrane capacitance probably reflect differences in membrane surface area, the conductance density could still differ substantially. Although it was not possible to directly determine the conductance density from our measurements, we can estimate the cell-type dependence of this quantity by looking at the ratio of the measured absolute conductance and the average membrane capacitance (as estimated from current clamp experiments) in the different cell types. This comparison suggests that differences in Ih conductance density may indeed be substantial, with O-R cells having an approximately two-fold higher density than PCs and OLM cells, which may explain the stronger resonance observed in O-R cells.
Our experiments also revealed that a significantly larger amount of Ih was activated in PCs than in interneurons at physiologically relevant potentials (above −90 mV), where the resonance properties were investigated. PCs are known to express HCN channels mainly on their distal dendrites (Magee, 1998; Lörincz et al. 2002); therefore the differences in Ih activation might be explained by space clamp limitations. However, analysis of the activation kinetics of Ih in the distinct cell types precluded this interpretation, as more distal localization would imply slower apparent kinetics, which is opposite to our findings.
We found a clear difference in the kinetics of Ih between PCs and interneurons. Not only the time course of activation but also the relative proportion of components with a slow and a fast time constant and its change with the membrane potential were different in PCs and interneurons (Fig. 5G). It has been shown that the activation kinetics of HCN channels are predominantly determined by the relative contribution of HCN channel isoforms to the composition of homomeric or heteromeric channels (Santoro et al. 2000); therefore, one possible explanation for these differences in the activation characteristics of Ih in hippocampal neurons is different subunit compositions of HCN channels. Indeed, both immunohistochemical (Brewster et al. 2002; Notomi & Shigemoto, 2004) and in situ mRNA hybridisation studies (Santoro et al. 2000; Bender et al. 2001; Brewster et al. 2007) suggest that while PCs express mainly HCN1 and HCN2 in their distal dendrites, the proportion of HCN2 and HCN4 (subunits which contribute to slower activation kinetics of Ih; Franz et al. 2000; Santoro et al. 2000; Ishii et al. 2001) is much larger in the stratum oriens, suggesting that they are likely to be expressed in interneurons. Of course we cannot exclude the possibility that various elements of the neuronal membrane, such as putative auxiliary subunits, scaffolding proteins or cytoskeletal proteins (Wahl-Schott & Biel, 2009) interact with the HCN channels and may also influence the properties of Ih in the distinct hippocampal neurons.
In summary, the different cell types in our study were distinct both in terms of the observed properties of Ih and in terms of their passive membrane properties. The effects of various neuronal properties on the impedance profile could be predicted by the Ih model, by first using average (median) parameter values (as determined in our various experiments) for measured cell types, and then varying parameters either individually or in combination to observe the changes in the shape of the impedance curve (Fig. 8). The consequences of several manipulations are highlighted by these examples. First, changes in the half-activation voltage, which may occur in response to neuromodulatory influences (e.g. Maccaferri & McBain, 1996), essentially convert each impedance curve into one that could be measured in the original cell at a membrane potential shifted by the equivalent amount to the change in V1/2 (but in the opposite direction). Second, alterations in the time constant of Ih profoundly affect the shape of the impedance curve, and especially the degree and frequency of resonance. Third, changes in the passive membrane resistance (the reciprocal of the leak conductance) can also have a pronounced effect on all aspects of the impedance profile, partly by changing the weight of voltage-gated conductances relative to the voltage-independent leak conductance. Fourth, the membrane capacitance affected mainly the cutoff frequency (as expected), but also played a role in shaping the resonance peak. A final important point is that no single parameter was found to be dominant in determining the differences in the characteristics of the impedance profiles of distinct cell types; concurrent changes in several parameters were required to convert one type of impedance curve into another type, as demonstrated by the last two examples in Fig. 8.
Our computational model strengthened the idea that Ih is the major determinant of the impedance characteristics at subthreshold membrane potentials in hippocampal neurons. However, our result that in stratum oriens interneurons a smaller degree of resonance was observed than that predicted from the model suggests that some other conductances might also be active at these membrane potentials in these particular cell types and dampen the effect of Ih on the impedance profile. The inward rectifier K+ current might be a good candidate for this effect, as suggested by both theoretical and experimental studies by Hutcheon et al. (1996a,b;) in neocortical neurons.
Several studies have shown that Ih substantially promotes firing when the fluctuation in the membrane potential can activate a sufficient number of HCN channels (Manseau et al. 2008). Importantly, if such fluctuation occurs simultaneously in several PCs even after the activation of a single perisomatic inhibitory cell (Cobb et al. 1995), then a large number of principal neurons could discharge action potentials synchronously, contributing to rhythm generation at theta frequencies. Thus, activation of Ih near or below the spike threshold might indeed be important for oscillatory activities (Kocsis & Li, 2004). This has been directly demonstrated in hippocampal slices, where blocking of Ih diminished the synchronous firing of pyramidal cells at theta frequencies (Cobb et al. 2003). Our voltage-clamp data support these results, since a substantial proportion of HCN channels in pyramidal cells was activated at the resting membrane potential. In contrast, a much lower proportion of HCN channels would be open at resting membrane potential in OLM cells and O-R cells, which is in line with the findings that interneurons in the stratum oriens exhibited less obvious membrane potential oscillations at theta frequencies (Chapman & Lacaille, 1999).
The activation curve of Ih can be profoundly shifted by cyclic nucleotides, which are regulated by G-protein coupled receptor activation (Chen et al. 2001); therefore, subcortical neurotransmitter systems acting on these receptors could significantly affect the opening of HCN channels. Thus, theta frequency membrane potential oscillations as well as the impedance of the interneurons that express HCN channels can be modulated in a state-dependent manner (Fig. 8; Maccaferri & McBain, 1996; Gasparini & DiFrancesco, 1999; Placantonakis et al. 2000; Bickmeyer et al. 2002; Rosenkranz & Johnston, 2006), controlling their recruitment into network activity.
Ih has been shown to influence the occurrence of dendritic spikes (Tsay et al. 2007) and the amplitude of EPSPs (George et al. 2009) by interacting with other voltage-gated ion channels, such as N- or T-type Ca2+ channels or the so-called M-current mediated by voltage-gated K+ channels. Therefore the observation that Ih is activated at more hyperpolarised potentials in oriens interneurons than in pyramidal cells might also be important in understanding the differences in dendritic signal-processing mechanisms of these cells.
While several studies have measured the impedance amplitude in various cell types, much less has been known about the phase of the impedance. We determined and compared the impedance phase profiles of four types of hippocampal neuron. In the three ‘resonant’ cell types in our study, positive as well as negative phase shifts could be seen depending on the frequency. Since Ih works effectively as an inductive element in the membrane, it can produce a significant positive phase shift in the voltage response of the cell to an oscillatory input. Both theoretical and experimental studies suggest that this feature of Ih might be important in many processes including control of spike timing (Lengyel et al. 2005; Kwag & Paulsen, 2009) and synaptic plasticity (Narayanan & Johnston, 2007, 2008). Specifically, during oscillations, the phase of the impedance quantifies the phase shift of the cell's membrane potential oscillation relative to the phase of its rhythmic current input. A positive phase shift is especially interesting, since it leads to an apparent paradox whereby the cell's response seems to lead the corresponding change in its input – although this holds in a rigorous sense only for regular sinusoidal oscillations. The fact that distinct classes of hippocampal cells show well-defined, cell-type-specific impedance amplitude and phase-response characteristics may indicate a crucial role of these cellular properties in the complex dynamics involved in information processing in the central nervous system.
We thank Ms Katalin Lengyel and Erzsébet Gregori for their excellent technical assistance. This work was supported by the Hungarian Scientific Research Fund (OTKA T049517, OTKA K60927, NKTH-OTKA CNK 77793), the Wellcome Trust, the BBSRC, and the British Council.
R.Z., S.K., O.P. and N.H. contributed to the conception and design of the experiments. R.Z. conducted the electrophysiological experiments. S.K. performed the modelling part of the study. R.Z. and S.K. analysed the data. R.Z., S.K., O.P., T.F.F. and N.H. participated in the interpretation of the data. All authors drafted the manuscript and approved the final version for publication. Experiments were conducted in the Department of Cellular and Network Neurobiology, Institute of Experimental Medicine, Hungarian Academy of Sciences, Budapest, Hungary.
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