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Sequential estimation of intrinsic activity and synaptic input in single neurons by particle filtering with optimal importance density
EURASIP Journal on Advances in Signal Processing volume 2017, Article number: 65 (2017)
Abstract
This paper deals with the problem of inferring the signals and parameters that cause neural activity to occur. The ultimate challenge being to unveil brain’s connectivity, here we focus on a microscopic vision of the problem, where single neurons (potentially connected to a network of peers) are at the core of our study. The sole observation available are noisy, sampled voltage traces obtained from intracellular recordings. We design algorithms and inference methods using the tools provided by stochastic filtering that allow a probabilistic interpretation and treatment of the problem. Using particle filtering, we are able to reconstruct traces of voltages and estimate the time course of auxiliary variables. By extending the algorithm, through PMCMC methodology, we are able to estimate hidden physiological parameters as well, like intrinsic conductances or reversal potentials. Last, but not least, the method is applied to estimate synaptic conductances arriving at a target cell, thus reconstructing the synaptic excitatory/inhibitory input traces. Notably, the performance of these estimations achieve the theoretical lower bounds even in spiking regimes.
Introduction
Measurements of membrane potential traces constitute the main observable quantities to derive a biophysical neuron model. In particular, the dynamics of auxiliary variables and the model parameters are inferred from voltage traces, in a costly process that typically entails a variety of channel blocks and clamping techniques (see, for instance, [1]), as well as some uncertainty in the parameter values due to noise in the signal. Recent works in the literature deal with the problem of inferring hidden parameters of the model; see, for instance, [2–4] and, for an exhaustive review, [5]. In the same line, attempts to extract connectivity in networks of neurons from calcium imaging, see [6], are worth mentioning.
Apart from inferring intrinsic parameters of the model, voltage traces are also useful to obtain valuable information about synaptic input, an inverse problem with some satisfactory (see, for instance, [7–13]) but no complete solutions yet. The main shortcomings are the requirement of multiple (supposedly identical) trials for some methods to be applied and the need of avoiding signals obtained when ionic currents are active. The latter constraint arises from the fact that many methods rely on the linearity of the signal and this is not possible to achieve under quite general situations, like spiking regimes (see [14]) or subthreshold regimes when specific currents (e.g., AHP, LTS) are active (see [15]).
The problem investigated in this paper considers recordings of noisy voltage traces to infer the hidden gating variables of the neuron model, as well as filtered voltage estimates, model parameters, and input synaptic conductances.
Figure 1 shows the basic setup we are dealing with in this article. The neuron under observation has its own dynamics, producing electrical voltage patterns. The generation of action potentials is regulated by internal drivers (e.g., the active gating variables of the neuron) as well as exogenous factors like excitatory and inhibitory synaptic conductances produced by pools of connected neurons. This system is unobservable, in the sense that we cannot measure it directly. The sole observation from this system are the noisy membrane potentials y _{ k }. In this experimental scenario, the ultimate goal is to extract the following quantities:

1.
The timeevolving states characterizing the neuron dynamics, including a filtered membrane potential and the dynamics of the gating variables

2.
The parameters defining the neuron model

3.
The dynamics of synaptic conductances and its parameters, the final goal being to discern the temporal contributions of global excitation from those of global inhibition, g _{E}(t) and g _{I}(t), respectively.
An ideal method should be able to sequentially infer the time course of the membrane potential and its intrinsic/extrinsic activity from noisy observations of a voltage trace. The main features of the envisaged algorithm are fivefold: (i) Singletrial: the method should be able to estimate the desired signals and parameters from a single voltage trace, thus avoiding the experimental variability among trials; (ii) Sequential: the algorithm should provide estimates each time a new observation is recorded, thus avoiding reprocessing of all data streams each time; (iii) Spike regime: contrary to most solutions operating only under the subthreshold assumption, the method should be able to operate in the presence of spikes as well; (iv) Robust: if the method is modeldependent, thus implying knowledge of the model parameters, then the algorithm should be provided with enhancements to adaptively learn these parameters; and (v) Statistically efficient: the performance of the method should be close to the theoretical lower bounds, meaning that the estimation error cannot be substantially reduced. Notice that the focus here is not on reducing the computational cost of the inference method, and thus, we allow ourselves to use resourceconsuming algorithms. Indeed, the target application does not demand (at least as a main requirement) realtime operation, and thus, we prioritized performance (i.e., estimation accuracy and the rest of features described earlier) in our developments.
According to the above desired features, in this work, that substantially extends our previous contributions [16, 17], we are interested in methods that can provide estimations from a single trial and avoid the need of repetitions that could be contaminated by neuronal variability. Particularly, we concentrate on methods to extract intrinsic activity of ionic channels, namely the probabilities of opening and closing ionic channels, and the contribution of synaptic conductances. We built a method based on Bayesian theory to sequentially infer these quantities from singletrace, noisy membrane potentials. The material therein includes a discussion of the discrete statespace representation of the problem and the model inaccuracies due to mismodeling effects. We present two sequential inference algorithms: (i) a method based on particle filtering (PF) to estimate the timeevolving states of a neuron under the assumption of perfect model knowledge and (ii) an enhanced version where model parameters are jointly estimated, and thus, the rather strong assumption of perfect model knowledge is relaxed. We provide exhaustive computer simulation results to validate the algorithms and observe that they are attaining the theoretical lower bounds of accuracy, which are derived in the paper as well.
In this paper, we use the powerful tools of PF to make inferences in general statespace models. PF are a set of methods able to sample from the marginal filtering distribution in situations where analytical solutions are hard to work out or simply impossible. In the recent years, PFs played an important role in many research areas such as signal detection and demodulation, target tracking, positioning, Bayesian inference, audio processing, financial modeling, computer vision, robotics, control, or biology [18–24]. At a glance, PF approximates the filtering distribution of states given measurements by a set of random points, properly weighted according to Bayes’ rule. The generation of the random particles can be done through a variety of distributions, known as importance density. Particularly, we formulate the problem at hand and observe that it is possible to use the optimal importance density [25]. This distribution generates particles close to the target distribution, and thus, it can be shown to reduce the variance of the particles. As a consequence, for a fix number of particles, usage of this approach (not always possible) leads to better accuracy results than other choices. To the authors’ knowledge, the utilization of such sampling distribution is novel in the context of neural model filtering. Similar works have used PF to track neural dynamics, but with no optimal importance density (see [2, 3, 26]), or to estimate synaptic input from subthreshold recordings [11], as opposite to our proposed approach where we aim at providing estimates during the, highly nonlinear, spike regime. These references use the expectationmaximization algorithm to estimate the model parameters. In this paper, we use the Particle Marginal MarkovChain MonteCarlo (PMCMC) method to estimate the parameters. Lighter filtering methods based on the Gaussian assumption were considered in the literature (see [12, 13, 27] for instance), but the assumption might not hold in general, for instance, due to outliers in the membrane measurements or if more sophisticated models for the synaptic conductances are considered. In these situations, a PF approach seems more appropriate. As mentioned earlier, the focus here is on highly efficient and reliable filtering methods, rather than on computationally light inference methods. Summing up, our method jointly treats the features of handling singlevoltage traces governed by nonlinear models, estimating both neuron parameters and synaptic conductances, even in the spiking regimes, and using optimal importance density for the PF together with a MCMC algorithm. The above references cope with some of these features, but to our knowledge, none of the recent methods in the literature accounts for all of them. It is worth noting that other simulationbased solutions can be adopted besides the PMCMC. For instance, the works [28–32] tackle state estimation and model fitting problems jointly.
The remainder of the article is organized as follows. In Section 2, we expose the problem and present the statistical model, essentially a discretization of the wellknown MorrisLecar model, and we analyze the model inaccuracies as well. Next, in Section 3, we present the different inference algorithms we apply depending on the knowledge of the system. Results are given in Section 4, where we tackle three inference problems: (i) when the parameters defining the model are known; (ii) when the parameters of the model are unknown, and thus, they need to be estimated; and (iii) estimation of synaptic conductances from voltage traces assuming unknown model parameters. Finally, Section 5 concludes the paper with final remarks.
Problem statement and model
Measurement modeling
The recording of the membrane potential is a physical process, including some approximations/inaccuracies involving:

1.
Voltage observations are noisy. This is due, in part, to the thermal noise at the sensing device, nonideal conditions in experimental setups, etc.

2.
Recorded observations are discrete. All sensing devices record data by sampling at discrete timeinstants k, at a sampling frequency f _{ s }=1/T_{ s }, the continuoustime natural phenomena. This is the task of an AnalogtoDigital Converter (ADC). Moreover, these samples are typically digitized, i.e., expressed by a finite number of bits. This latter issue is not tackled in the work as we assume that modern computer capabilities allow us to sample with relatively large number of bits per sample.
The problem can thus be posed in the form of a discretetime, statespace model, where the observations are
with v _{ k } representing the nominal membrane potential and \(\sigma _{y,k}^{2}\) modeling the noise variance due to the sensor or the instrumentation inaccuracies when performing the experiment. To provide comparable results, we define the signaltonoise ratio (SNR) as SNR=P _{ s }/P _{ n }, with P _{ s } being the average signal power and \(P_{n}=\sigma _{y,k}^{2}\) the noise power.
Neural dynamical system
The methods presented in this paper rely on continuous models for the evolution of the voltagetraces and the hidden variables of a neuron. Our reference framework are conductancebased models endowed with a synaptic input term I _{syn} and an (steady) applied current I _{app}, that is, equations of type
where \(\bar {g}_{L} \left (v  E_{L}\right)\) is the leakage current and each \(I_{j}=\bar {g}_{j} ~ p_{j} \left (v  E_{j}\right)\) is the timevarying ionic current for the jth ionic species, \(\mathcal {J} = \{\text {Na}, \mathrm {K}, \text {Cl}, \text {Ca}, \dots \}\), where \(\bar {g}_{j}\) is the maximal conductance, p _{ j } involves the socalled gating variables, and E _{ j } is the reversal potential of the ionic channel. The synaptic input is expressed as I _{syn}=g _{E}(t)(v(t)−E _{E})+g _{I}(t)(v(t)−E _{I}). We use the socalled effective pointconductance model, see [7, 33], where the excitatory/inhibitory global conductances are treated as OrnsteinUhlenbeck (OU) processes
where u={E,I} and χ(t) is a zeromean, white noise, Gaussian process with unit variance. Then, the OU process has mean g _{ u,0}, standard deviation σ _{ u }, and time constant τ _{ u }. This simple model was shown in [33] to yield a valid description of the synaptic noise, capturing the properties of more complex models. Other dynamics could be considered instead.
Concerning the neuron model, that is, the equation \(C_{m} \dot {v} =  \bar {g}_{L} \left (v  E_{L}\right)  \sum _{j\in \mathcal {J}} I_{j}\), in this work, we focus on the MorrisLecar model [34] for the sake of clarity, which is able to model a wide variety of neural dynamics; see [35]. Details of the MorrisLecar model can be found in Appendix 1. The unknown state vector in this case is composed of the membrane potential, v, and a unique ionic (K ^{+})current involving the gating variable n. We write
Notice that the MorrisLecar neuron model is defined by a system of continuoustime, ordinary differential equations (ODEs) of the form \(\dot {\boldsymbol {x}}= f({\boldsymbol {x}})\). In general, mathematical models for neurons are of this type. However, due to the sampled recording of measurements, we are interested in expressing the model in the form of a discrete statespace,
where \(\boldsymbol {\nu }_{k} \sim \mathcal {N}(\mathbf {0},\boldsymbol {\Sigma }_{x,k})\) is the process noise which includes the model inaccuracies. The covariance matrix Σ _{ x,k } is used to quantify our confidence in the model that maps f _{ k }:{v _{ k−1},n _{ k−1}}↦{v _{ k },n _{ k }}. In general, obtaining a closedform analytical expression for f _{ k } without approximations is not possible. In such a case, we could use the Euler method:
where Δ t=T_{ s } is the sampling period. Thus, we can write (5) as
which is of the Markovian type.
If we focus on the MorrisLecar model, the resulting discrete version of the ODE system in (40)–(41) is:
with m _{ ∞ }(v _{ k }), n _{ ∞ }(v _{ k }) and τ _{ n }(v _{ k }) defined in Appendix 1. Then, (8) and (9) can be interpreted as x _{ k }=f _{ k }(x _{ k−1}).
Statespace formulation
The goal is to express the inference problem in statespace formulation and apply stochastic filtering tools learned from signal processing. The final ingredient to do so is to introduce the socalled process noise in the state equation. Leveraging on the observation equation in (1), the statespace can be formulated as
where the noise terms ν _{ v,k } and ν _{ n,k } are assumed jointly Gaussian with covariance matrix Σ _{ x,k }. Further details of this matrix are discussed in Section 2.4. The measurement noise ν _{ y,k } is assumed zeromean, Gaussian, and with variance \(\sigma ^{2}_{y,k}\). Notice that the system is characterized by Gaussian distributions and is linear in the observations; this allows for an optimal design of the proposal density in the PF as exploited in Section 3.1.
This general form of Markovian type is preserved when the model is extended with a couple of OU processes associated to the excitatory and inhibitory synaptic conductances. In this case, the resulting statespace model is composed by the MorrisLecar model used so far (with the peculiarity that the term −I _{syn} is added to (40)), plus the OU stochastic process in (3) describing I _{syn}. Therefore, the continuoustime state is x=(v,n,g _{E},g _{I})^{⊤}. The discrete version of the statespace is used again.
Model inaccuracies
The proposed estimation method relies on the fact that the neuron model is known. This is true to some extent, but most of the parameters in the MorrisLecar model discussed are to be estimated. Typically, this model calibration is done beforehand, but as we will see later in Section 3.2, this could be done in parallel to the filtering process. Therefore, the robustness of the method to possible inaccuracies should be assessed. In this section, we point out possible causes of mismodeling. Computer simulations are later used to characterize the performance of the proposed methods under these impairments.
In the singleneuron model considered, three major sources of inaccuracies can be identified. First, the applied current I _{app} can be itself noisy, with a variance depending on the quality of the instrumentation used and the experiment itself. We model the actual applied current as a random variable
where I _{ o } is the nominal current applied and \(\sigma ^{2}_{I}\) the variance around this value. Plugging (12) into (8), we obtain that the contribution of I _{app} to the noise term is \(\frac {\mathrm {T}_{s}}{C_{m}}\nu _{I,k} \sim \mathcal {N} \left (0, (\mathrm {T}_{s}/C_{m})^{2}\sigma ^{2}_{I}\right)\).
Secondly, when the conductance of the leakage term is estimated beforehand, some inaccuracies might be taken into account. In general, this term is considered constant in the models although it gathers relatively distinct phenomena that can potentially be timevarying. The maximal conductance of the leakage term is therefore inaccurate and modeled as
where \(\bar {g}_{L}^{o}\) is the nominal, estimated conductance and \(\sigma ^{2}_{g}\) the variance of this estimate. Similarly, inserting (13) into (8), we see that the contribution of \(\bar {g}_{L}\) to the noise term is \(\frac {\mathrm {T}_{s}}{C_{m}}\nu _{g,k} \sim \mathcal {N} \left (0, (\mathrm {T}_{s}/C_{m})^{2}\left (v_{k1}E_{\mathrm {L}}\right)\sigma ^{2}_{g}\right)\).
Finally, the parameters in m _{ ∞ }(v _{ k }), n _{ ∞ }(v _{ k }), and τ _{ n }(v _{ k }) are to be estimated. In general, these parameters can be properly obtained offline by standard methods; see [36]. However, as they are estimates, a residual error typically remains. To account for these inaccuracies, we consider that the equation governing the evolution of gating variables is corrupted by a zeromean additive white Gaussian process with variance \(\sigma _{n}^{2}\).
This analysis allows us to construct a realistic Σ _{ x,k }, as the contribution of the aforementioned inaccuracies. In a practical setup, in order to compute the noise variance due to leakage, we need to use the approximation \(\hat {v}_{k1} \approx v_{k1}\), where \(\hat {v}_{k1}\) is estimated by the filtering method. We construct the covariance matrix of the model as
where we used that the overall noise in the voltage model is \(\frac {\mathrm {T}_{s}}{C_{m}}\left (\nu _{I,k}  \nu _{g,k}\right) \sim \mathcal {N} \left (0, \sigma ^{2}_{v}\right)\) and
as an estimate of \(\sigma _{v}^{2}\), provided accurate knowledge of \(\sigma ^{2}_{I}\) and \(\sigma ^{2}_{g}\). Otherwise, the covariance matrix of the process could be estimated by other means, as the ones presented in Section 3.2 for mixed stateparameter estimation in nonlinear filtering problems.
Notice that we are implicitly assuming white processes due to the diagonal structure of Σ _{ x,k }. It is worth mentioning that, should correlated noise be a more realistic model, the method proposed in this article would be still valid. The proposed method can cope with colored noise statistics since Σ _{ x,k } can be used seamlessly if it is not diagonal.
Methods
Two filtering methods are proposed here, depending on the knowledge regarding the underlying dynamical model. Section 3.1 presents an algorithm able to estimate the states in x _{ k } by a PF methodology, the particularity being that an optimal distribution is used to draw the random samples characterizing the joint filtering distribution of interest. This method assumes knowledge of the parameter values of the system model, although we account for some inaccuracies as detailed in Section 2.4. An enhanced version of this method is presented in Section 3.2, where we relax the assumption of knowing the parameter values. Leveraging on a PMCMC algorithm and the use of the optimal importance density as in the first method, we present a method that is able to filter x _{ k } while estimating the values describing the neuron model.
Sequential estimation of voltage traces and gating variables
The type of problems we are interested in involve the estimation of timeevolving signals that can be expressed through a statespace formulation. Particularly, estimation of the states in a singleneuron model from noisy voltage traces can be readily seen as a filtering problem. Bayesian theory provides the mathematical tools to deal with such problems in a systematic manner. The focus is on sequential methods that can incorporate new available measurements as they are recorded without the need for reprocessing all past data.
Bayesian filtering involves the recursive estimation of states \({\boldsymbol {x}}_{k} \in {\mathbb {R}}^{n_{x}}\) given measurements \(y_{k} \in {\mathbb {R}}\) at time t based on all available measurements, y _{1:k }={y _{1},…,y _{ k }}. To that aim, we are interested in the filtering distribution p(x _{ k }y _{1:k }). Assuming the Markovian property in (10) and (11), the distribution can be recursively expressed as
with p(y _{ k }x _{ k }) and p(x _{ k }x _{ k−1}) referred to as the likelihood and the prior distributions, respectively. Unfortunately, (16) can only be obtained in closedform in some special cases, and in more general setups, we should resort to more sophisticated methods. In this paper, we consider PF to cope with the nonlinearity of the model. Although other lighter approaches might be possible as well [22], we seek the maximum accuracy regardless the involved computational cost. Theoretically, for sufficiently large number of particles, particle filters offer such performances.
Particle filters, see [18, 20, 21, 23], approximate the filtering distribution by a set of N weighted random samples, forming the random measure \(\left \{{ {\boldsymbol {x}}}^{(i)}_{k},w^{(i)}_{k} \right \}_{i=1}^{N}\). These random samples are drawn from the importance density distribution, π(·),
and weighted according to the general formulation
The importance density from which particles are drawn is a key issue in designing efficient PFs. It is well known that the optimal importance density is
in the sense that it minimizes the variance of importance weights. Weights are then computed using (18) as \(w^{(i)}_{k} \propto w^{(i)}_{k1} p\left ({ y}_{k}{ {\boldsymbol {x}}}^{(i)}_{k1}\right)\). This choice requires the ability to draw from \(p({ {\boldsymbol {x}}}_{k}{ {\boldsymbol {x}}}^{(i)}_{k1}, { y}_{k})\) and to evaluate \(p\left ({ y}_{k}{ {\boldsymbol {x}}}^{(i)}_{k1}\right)\). In general, the two requirements cannot be met, and one needs to resort to suboptimal choices. However, given the particular structure of the statespace model, we are able to use the optimal importance density. The fact that the model is Gaussian and the observations are related linearly to states allow to solve for the conditional distribution of states from the joint Gaussian distribution of states and observations. The equations are:
with
and the importance weights can be updated using
with h=(1,0)^{⊤}. The PF provides a discrete approximation of the filtering distribution of the form
which gathers all information from x _{ k } that the measurements up to time k provide. The minimum mean square error estimator can be obtained as
where \(\hat {{\boldsymbol {x}}}_{k} = \left (\hat {v}_{k}, \hat {n}_{k} \right)^{\top }\). Recall that the method discussed in this section could be easily adapted to other neuron models by simply substituting the corresponding transition function f _{ k } and constructing the state vector x _{ k } accordingly.
As a final step, PFs incorporate a resampling strategy to avoid the collapse of particles into a single state point. Resampling consists in eliminating particles with low importance weights and replicating those in highprobability regions [37]. The overall algorithm can be looked up in Algorithm 1 at instance k. Notice that this version of the algorithm requires knowledge of noise statistics and all the model parameters, which for the MorrisLecar model are
When we add the dynamics of the synaptic conductances, the vector Θ of model parameters also includes τ _{ E }, τ _{ I }, g _{ E,0}, g _{ I,0}, σ _{ E }, and σ _{ I }.
Joint estimation of states and model parameters
In practice, the parameters in (24) might not be known. It is reasonable to assume that Θ, or a subset of these parameters θ⊆Θ, are unknown and need to be estimated at the same time the filtering method in Algorithm 1 is executed. Therefore, the ultimate goal in this case is to estimate jointly the time evolving states and the unknown parameters of the model, x _{1:k } and θ, respectively.
Joint estimation of states and parameters is a longstanding problem in Bayesian filtering and specially hard to handle in the context of PFs. Refer to [38–40] and their references for a complete survey. Here, we follow the approach in [41] and make use of the socalled PMCMC to enhance the presented PF algorithm with parameter estimation capabilities. In the remainder of this section, we provide the basic ideas to use the algorithm, following a similar approach as in [24]. Connections to other methods are discussed in [42].
Following the Bayesian philosophy we adopt here, the problem fundamentally reduces to assigning an a priori distribution for the unknown parameter \(\boldsymbol {\theta } \in \mathbb {R}^{n_{\theta }}\) and extending the statespace model (here, we adopt its probabilistic representation)
and initial state distribution x _{0}∼p(x _{0}θ). Applying Bayes’ rule, the full posterior distribution can be expressed as
with
Notice here that we are dealing with a finite horizon of observations T. Then, from a Bayesian perspective, the estimation of θ is equivalent to obtaining its marginal posterior distribution \(p(\boldsymbol {\theta }  y_{1:T}) = \int p({\boldsymbol {x}}_{0:T}, \boldsymbol {\theta }  y_{1:T}) d{\boldsymbol {x}}_{0:T}\). However, this is in general extremely hard to compute analytically, and one needs to find workarounds. Evaluation of the full posterior turns out to be not only computationally prohibitive but useless if states cannot be marginalized out analytically. Alternative methods resort on the factorization of the parameter marginal distribution as p(θy _{1:T })∝p(y _{1:T }θ)p(θ) and how Bayesian filters can be transformed to provide characterizations of the marginal likelihood distribution p(y _{1:T }θ) and related quantities. The marginal likelihood distribution can be recursively factorized in terms of the predictive distributions of the observations:
with \(p(y_{k}  y_{1:k1}, \boldsymbol {\theta }) = \int p(y_{k}  {\boldsymbol {x}}_{k}, \boldsymbol {\theta }) p({\boldsymbol {x}}_{k}  y_{1:k1}, \boldsymbol {\theta }) d{\boldsymbol {x}}_{k}\) obtained straightforwardly as a byproduct of any of the Bayesian filtering methods; see [22].
A useful transformation of the marginal likelihood is the socalled energy function, which is sometimes more convenient to deal with. The energy function is defined as φ _{ T }(θ)=− lnp(y _{1:T }θ)− lnp(θ) or, equivalently, p(θy _{1:T })∝ exp(−φ _{ T }(θ)). The energy function can then be recursively computed as a function of the predictive distribution
for k≥1.
Then, the basic problem is to obtain an estimate of the predictive distribution p(y _{ k }y _{1:k−1},θ) from the PF we have designed in Section 3.1 and use it in conjunction with p(θ) to infer the marginal distribution p(θy _{1:T }) of interest. This latter step can be performed in several ways, from which we choose to use the MarkovChain MonteCarlo (MCMC) methodology to continue with a fully Bayesian solution. Besides, it is known to be the solution that provides the best results when used in a PF. Next, we detail how φ _{ k }(θ) can be obtained from a PF algorithm, we present the MCMC method for parameter estimation, and finally we sketch the overall algorithm.
Computing the energy function from particle filters
The modification needed is rather small. Actually, it is noninvasive in the sense that the algorithm remains the same and the energy function can be computed adding some extra formulae. Recall that the predictive distribution p(y _{ k }y _{1:k−1},θ) is composed of two distributions and that the PF provides characterizations of these two distributions. Then, one could use a particle approximation \(p(y_{k}  y_{1:k1}, \boldsymbol {\theta }) \approx \hat {p}(y_{k}  y_{1:k1}, \boldsymbol {\theta }) = \sum _{i=1}^{N} w^{(i)}_{k1} \zeta ^{(i)}_{k}\) with \(w^{(i)}_{k1}\) as in the original algorithm and
Then, it is straightforward to identify the energy function approximation as
which can be computed recursively in the PF algorithm and becomes an approximation \( \hat {\varphi }_{T}(\boldsymbol {\theta })\) of the energy function.
The Particle MarkovChain MonteCarlo algorithm
Once an approximation of the energy function is available, we can apply MCMC to infer the marginal distribution of the parameters. MCMC methods constitute a general methodology to generate samples recursively from a given distribution by randomly simulating from a Markov chain [43–47]. There are many algorithms implementing the MCMC concept, the MetropolisHastings (MH) algorithm being one of the most popular. At the jth iteration, the MH algorithm samples a candidate point θ ^{∗} from a proposal distribution q(θ ^{∗}θ ^{(j−1)}) based on the previous sample θ ^{(j−1)}. Starting from an arbitrary value θ ^{(0)}, the MH algorithm accepts the new candidate point (meaning that it was generated from the target distribution, p(θy _{1:T })) using the rule
where u is drawn randomly from a uniform distribution, \(u \sim \mathcal {U}(0,1)\), and
is referred to as the acceptance probability.
It is critical for the performance of the algorithm the choice of the proposal density. A common choice is \(q(\boldsymbol {\theta }  \boldsymbol {\theta }^{(j1)}) = \mathcal {N} (\boldsymbol {\theta } ; \boldsymbol {\theta }^{(j1)}, \boldsymbol {\Sigma }^{(j1)})\) with the selection of the transitional covariance remaining as the tuning Σ ^{(j−1)} parameter. This covariance can be adapted as iterations of the MCMC method progress. In this work, we have adopted the Robust Adaptive Metropolis (RAM) algorithm [48], although other methods could be considered for the same purpose [49, 50]. The RAM algorithm is provided in Algorithm 2. We use the notation that S=Chol(A) denotes the Cholesky factorization of an Hermitian positivedefinite matrix A such that A=S S ^{⊤}, and S is a lower triangular matrix [51]. The RAM algorithm outputs a set of samples \(\left \{\boldsymbol {\theta }^{(j)}\right \}_{j=1}^{M}\), where M is the number of iterations of th e MCMC procedure. These samples are originated from the target distribution \(\left \{ \boldsymbol {\theta }^{(j)} \sim p(\boldsymbol {\theta }  y_{1:T}) \right \}_{j=1}^{M} ~,\) which can be used to approximate (after neglecting the first samples corresponding to the transient phase of the algorithm) it as
and one can obtain the desired statistics from the characterization of the marginal distribution. For instance, point estimates of the parameter like
The main assumption in Algorithm 2 is the ability of evaluating the energy function, φ _{ T }(·). We have seen earlier how this can be done in a PF. Roughly speaking, the PMCMC algorithm consists of putting together these two algorithms [41]. We refer to Algorithm 3 for the resulting PMCMC method.
Computer simulation results
We simulated the data of a neuron following the MorrisLecar model. Particularly, we generated data sampled at f _{ s }=4 kHz. Notice that typical sampling rates are on the order of kilohertz, therefore ensuring that we are operating in the regime where the Nyquist rate is well satisfied (that is, f _{ s }>2·BW, with BW the bandwidth of the recorded signal) [1, Chapter 3]. The model parameters were set to C _{ m }=20 μF/cm^{2}, ϕ=0.04, V _{1}=−1.2 mV, V _{2}=18 mV, V _{3}=2 mV, and V _{4}=30 mV; the reverse potentials were E _{L}=−60 mV, E _{Ca}=120 mV, and E _{K}=−84 mV; and the maximal conductances were \(\bar {g}_{\text {Ca}}=4.4~\mathrm {mS/cm}^{2}\) and \(\bar {g}_{\mathrm {K}}=8.0~\mathrm {mS/cm}^{2}\). We considered a measurement noise with a standard deviation of 1 mV, which corresponds to an SNR of 32 dB. This value is considered a reasonable value in nowadays intracellular sensing devices. Model inaccuracies were generated as in Section 2.4.
Three sets of simulations are discussed. First, we validated the filtering method considering perfect knowledge of the model. In this case, the method in Algorithm 1 was used. Secondly, the model assumptions were relaxed in the sense that the parameters of the model were not known by the method. We analyzed the capabilities of the proposed method to infer both the timeevolving states of the system and some of the parameters defining the model. In this case, the method in Algorithm 3 was used. Finally, we validated the performance of the proposed methods in inferring the synaptic conductances. We tested both PF and PMCMC methods, that is, with and without full knowledge of the model, respectively.
Model parameters are known
In the simulations, we considered the model inaccuracies described in Section 2.4. To excite the neuron into spiking activity, a nominal applied current was injected with I _{ o }=110 μA/cm ^{2} and two values for σ _{ I } were considered, namely 1 and 10% of I _{ o }. The nominal conductance used in the model was \(\bar {g}_{\mathrm {L}}=2~\mathrm {mS/cm}^{2}\), whereas the underlying neuron had a zeromean Gaussian error with standard deviation \(\sigma _{\bar {g}_{\mathrm {L}}}\). Two variance values were considered as well, 1 and 10% of \(\bar {g}_{\mathrm {L}}\). Finally, we considered σ _{ n }=10^{−3} in the dynamics of the gating variable.
To give some intuition on the operation and performance of the PF method in Algorithm 1, we show the results for a single realization in Fig. 2. The results are for 500 particles and two different values of \(\sigma _{y,k}^{2}\), corresponding to 0 and 32 dB, respectively. Even in very low SNR regimes, the method is able to operate and provide reliable filtering results.
In order to evaluate the efficiency of the proposed estimation method, we computed the Posterior CramérRao Bound (PCRB) [52] in Appendix 2. We plot the PCRB as a benchmark for the root mean square error (RMSE) curves obtained by computer simulations, obtained after averaging 200 independent MonteCarlo trials. For a generic time series w _{ k }, the RMSE of an estimator \(\hat {w}_{k}\) is defined as
where \(\hat {w}_{j,k}\) denotes the estimate of w _{ k } at the jth realization and M the number of independent MonteCarlo trials used to approximate the mathematical expectation.
Figures 3 and 4 show the time course of the RMSE using N={500, 1000} particles. We see that in both scenarios, our method efficiently attains the PCRB. We measure the efficiency (η≥1) of the method as the quotient between the RMSE and the PCRB, averaged over the entire simulation time. The worst efficiency on estimating v _{ k } was 1.43 corresponding to 500 particles and 10% of inaccuracies (see Fig. 4), and the best was 1.11 for 1000 particles and 1% of errors (see Fig. 3). In estimating n _{ k }, the discrepancy was even lower, 1.06 and 1.03 for maximum and minimum η, respectively. Notice that, for larger inaccuracies, the method seems more reactive. This is because the covariance associated with the statespace has larger values, resulting in a more nervous filter and, consequently, with smaller convergence rates. As a conclusion, the PF tends to the PCRB with the number of particles. Also, the performance (both theoretical and empirical) could be improved if model inaccuracies are reduced, i.e., if the model parameters are better estimated at a previous stage. For the sake of completeness, we summarize the results in Table 1, where the average RMSE and PCRB along the 500 ms simulation are provided. It is apparent that increasing the number of particles from N=500 to N=1000 does not improve significantly the performance of the method.
Model parameters are unknown
In this section, we validate the algorithm presented in Section 3.2. According to the previous analysis, we deem that 500 particles are enough for the filter to provide reliable results. The parameters of the PMCMC algorithm were set to γ=0.9 and \(\bar {\alpha }_{\ast } = 0.234\).
Figure 5 shows the results for a single realization when a number of parameters in the nominal model are unknown. We considered one, two, and four unknown parameters. Each of the plots include M=100 iterations of the MCMC showing the evolution of the parameter estimation (top) and the superimposed recorded voltage in black and the filtered voltage trace in red (bottom). Model inaccuracies are of 1%, similarly as in Fig. 3. In these plots, we omitted the results for the gating variable for the sake of clarity. The true and initial values used in the experiments, as well as the initial covariances assumed, are detailed in Table 2. From the plots, we can observe that the method performs reasonably well even in the case of estimating the model parameters at the same time it is filtering out the noise in the membrane voltage traces.
A biologically meaningful signal is the leakage current. In general, the leakage gathers those ionic channels that are not explicitly modeled and other nonmodeled sources of activity. The parameters driving the leak current are \(\bar {g}_{L}\) and E _{L}. We tested and validated the proposed PMCMC in an experiment where the leak parameters were estimated at the same time the filtering solution was computed. Moreover, the statistics of the process noise were estimated as well, Σ _{ x,k }. In this case, we iterated the PMCMC method 1000 times and average the results over 100 MonteCarlo independent trials. The results are shown in Fig. 6, where the RMSE performance of the PMCMC method is compared to the performance of the original PF with perfect knowledge of the model.
It can be observed that the filtering performances with perfect knowledge of the model and with estimation of parameters by PMCMC are similar. Moreover, both approaches attain the theoretical lower bound of accuracy given by the PCRB, which is derived from the true model; see Appendix 2.
In Fig. 7, validation results for the parameter estimation capabilities of the PMCMC are shown. Particularly, we plotted a number of independent realizations of the sample trajectories \(\left \{\boldsymbol {\theta }^{(j)}\right \}_{j=1}^{M} \). We observe that all of them converge to the true values of the parameter. Recall that these true values were \(\boldsymbol {\theta } = (\bar {g}_{L}, E_{\mathrm {L}})^{\top } = (2,60)^{\top }\). The average of these realizations is given in Fig. 7, where the aforementioned convergence to the true parameter is highlighted.
Estimation of synaptic conductances
Finally, once the methods to estimate state variables and unknown parameters were consolidated, we proceeded to test the methods to our ultimate goal: estimating jointly the intrinsic states of the neuron and the extrinsic inputs (i.e., the synaptic conductances).
First, the method with perfect knowledge of the model was validated in Fig. 8. It can be observed that the intrinsic signals can be effectively recovered as before where synaptic inputs were not accounted for. The estimation of g _{E}(t) and g _{I}(t) is quite accurate, and the presence of spikes does not degrade the estimation capabilities of the method.
The PMCMC algorithm was tested similarly. In this case, we assumed that the model parameters related to v _{ k } and n _{ k } were accurately estimated, for instance, using an offline procedure or that analyzed in Section 4.2. Therefore, we focused on the estimation of those parameters that describe the OU process of each of the synaptic terms. Particularly, we considered the values in Table 3. The results can be consulted in Fig. 9 and compared to those in Fig. 8.
In Fig. 10, we compare the estimated excitatory and inhibitory synaptic conductances with the actual ones. We show both the performance of the PF method (round circles) and the PMCMC method (red dots). We appreciate a slightly better performance of the PF method, which is normal since in this case a perfect knowledge of the model is assumed while the PMCMC needs to estimate both model parameters and synaptic conductances. More precisely, we have computed the normalized error
in both cases and obtained values of 0.2957 and 0.1939 for the excitatory and inhibitory conductances, respectively, with the PF method, and 0.3313 and 0.2095 (excitatory and inhibitory, respectively) with the PMCMC method. Compared to previous results in the literature, see, for instance, Figs. 2, 3, 4, 5, 6, and 8 in [4], where the authors performed an exhaustive comparison with different methods, our estimations provide excellent agreement with the prescribed conductances. Moreover, our statistics include data obtained in the spiking regime while the methods compared in [4] are applied only to subthreshold voltage traces. We also observe that the errors for the PMCMC method are, in average, only 12% (excitatory) and 8% (inhibitory) worse than the errors for the PF method. Given the complexity of the PMCMC method, these findings encourage future applications of the method to experimental data even when the model is not well defined.
We refer to the Additional file 1 to visualize a dynamic simulation showing how the estimations evolve as the PMCMC algorithm was applied in a case where the values of \(\bar {g}_{\mathrm {L}}\) and E _{L} were unknown.
Additional file 1: Evolution of the iterative learning when estimating leakage parameters. (MP4 2129 KB)
Conclusions
In this paper, we propose a filtering method that is able to sequentially infer the time course of the membrane potential, the intrinsic activity of ionic channels, and the input synaptic conductances from noisy observations of voltage traces. The method works both for subthreshold and spiking regimes. It is based on the PF methodology and features an optimal importance density, providing enhanced use of the particles that characterize the filtering distribution. In addition, we tackle the problem of joint parameter estimation and state filtering by extending the designed PF with an MCMC procedure in an iterative method known as PMCMC. Another distinctive contribution with respect to the other works in the literature is that here, we provide accuracy bounds for the problem at hand, given by the PCRB. The RMSEs of our methods are then compared to the bound, and therefore, we can assess the efficiency of the proposed inference methods.
Filtering methods of different types (e.g., PF or sigmapoint Kalman filtering) have been used in other recent contributions to similar problems; see [7–13]. From a methodological perspective, the novelty of this paper is in the use of an optimal importance density to generate particles, a fact that increases the estimation accuracy for a given budget of particles. This technical detail only applies to PF methods. Although Gaussian methods (e.g., the family of sigmapoint Kalman filters) have a lower computational cost in general, they require Gaussianity of the measures, whereas PFs do not. This is an advantage that we think can be crucial in estimating synaptic conductances, since the assumption of Gaussianity is generally assumed in the literature [4, 33], but there are no conclusive evidences to assert this assumption. In this paper, we have still applied the PF to an OrnsteinUhlenbeck process in order to check that basic results can be attained, but further research will go in the direction of assuming other types of distributions for the synaptic conductances. The use of more complex distributions nicely fits within the framework of our PFbased method. Another advantage of PFs versus Gaussian filters is their enhanced robustness to outliers [53]; for instance, due to recording artifacts, future applications shall also incorporate this feature.
We have found excellent estimations of the synaptic conductances, even in spiking regimes. Estimating synaptic conductances in spiking regimes is a challenge which is far to be solved. It is well known that linear estimations of synaptic conductances are not trustable in this situation when data is extracted intracellularly from the spiking activity of neurons; see [14]. In experiments, thus, caution has to be taken in eliminating part of the voltage traces, thus losing also part of the temporal information of both excitatory and inhibitory conductances. Our method is able to perform well in this regime. This information is highly valuable in problems (epilepsy, schizophrenia, Alzheimer’s disease, etc.) where a debate on the balance of excitation and inhibition is open; see the introduction of [12] for a rather complete overview on this feature.
The results show the validity of the approach when applied to a MorrisLecar type of neuron. However, the procedure is general and could be applied to any neuron model exhibiting more complex dynamics like bursting and mixedmode oscillations. Nevertheless, a clear drawback is the need for specifying a model although its parameters are estimated by the method. This is an ubiquitous problem in other modelbased methods. Future research includes the enhancement of the proposed method to account for model variability, for instance, the use of Interacting Multiple Model (IMM) approaches. Other forthcoming applications could be validating the method using real data recordings, both for inferring parameters of the model and synaptic conductances. The latter problem is a challenging hot topic in the neuroscience literature, which is recently focusing on methods to extract the conductances from singletrace measurements. We think that our PF method would give useful and interesting results to physiologists that aim at inferring the brain’s activation rules from neurons’ activities. Actually, knowing the excitatoryinhibitory timecourse separation can help in getting important conclusions about the brain’s functional connectivity (see [54–56]).
We have not tried to obtain estimations when subthreshold ionic currents are active, where the presence of nonlinearities could also contaminate the estimations; see [15]. According to the excellent performance in spiking regimes, where nonlinearities are stronger, we expect also a good agreement between the estimated data and the prescribed synaptic conductances. Other extensions of the model can be devoted to incorporate the dendrosomatic interaction (see, for instance, [57]), by considering multicompartmental neuron models, thus taking into account the morphology and the functional properties of the cell. This is another big challenge for which we think that our method can account for.
Appendix 1: MorrisLecar neuron model
From the myriad of existing singleneuron models, we consider without loss of generality the MorrisLecar model proposed in [34]. The model can be related (see [36]) to the I _{Na,p}+I _{K} model (persistent sodium plus potassium model). The dynamics of the neuron is modeled by a continuoustime dynamical system composed of the currentbalance equation for the membrane potential, v=v(t), and the K ^{+} gating variable 0≤n=n(t)≤1, which represents the probability of the K ^{+} ionic channel to be active. Then, the system of differential equations is
where C _{ m } is the membrane capacitance and ϕ a nondimensional constant. I _{app} represents the (externally) applied current. For the time being, we have neglected I _{syn} in (40). The leakage, calcium, and potassium currents are of the form
respectively. \(\bar {g}_{\mathrm {L}}\), \(\bar {g}_{\text {Ca}}\), and \(\bar {g}_{\mathrm {K}}\) are the maximal conductances of each current. E _{L}, E _{Ca}, and E _{K} denote the Nernst equilibrium potentials, for which the corresponding current is zero, a.k.a. reverse potentials.
The dynamics of the activation variable m is considered at the steady state, and thus, we write m=m _{ ∞ }(v). On the other hand, the time constant τ _{ n }(v) for the gating variable n cannot be considered that fast and the corresponding differential equation needs to be considered. The formulae for these functions are
which parameters V _{1}, V _{2}, V _{3}, and V _{4} can be measured experimentally [36].
The knowledgeable reader would have noticed that the MorrisLecar model is a HodginHuxleytype model with the usual considerations, where the following two extra assumptions were made: the depolarizing current is generated by Ca ^{2+} ionic channels (or Na ^{+} depending on the type of neuron modeled), whereas hyperpolarization is carried by K ^{+} ions, and that m=m _{ ∞ }(v). The MorrisLecar model is very popular in computational neuroscience as it models a large variety of neural dynamics while its phaseplane analysis is more manageable as it involves only two states [35].
The MorrisLecar, although simple to formulate, results in a very interesting model as it can produce a number of different dynamics. For instance, for given values of its parameters, we encounter a subcritical Hopf bifurcation for I _{app}=93.86 μA/cm ^{2}. On the other hand, for another set of parameter values, the system of equations has a SaddleNode on an Invariant Circle (SNIC) bifurcation at I _{app}=39.96 μA/cm ^{2}.
Appendix 2: PCRB in MorrisLecar models
This appendix is devoted to the derivation of the PCRB estimation bound for the MorrisLecar model used to benchmark the proposed methods in the simulations. We follow the sequential procedure given in [58], accounting that we have nonlinear functions in the state evolution and linear measurements, both with additive Gaussian noise. We are interested in an estimation error bound of the type of
where \(\hat {{\boldsymbol {x}}}_{k}(y_{1:k})\) represents an estimator of x _{ k } given y _{1:k }.
Recall that the statespace we are dealing with is of the form
where h=(1,0), x _{ k }=(v _{ k },n _{ k })^{⊤}, and f _{ k−1}(x _{ k−1}) defined by (8) and (9). The noise terms are of the form
In this case, the PCRB can be computed recursively by virtue of the result in [58] by computing the following terms
and plugging them into
for some initial J _{0}. Notice that, in our case, \(\mathbf {D}_{k}^{22}\) becomes deterministic, but the rest of the terms involving expectations should be computed by MonteCarlo integration over independent state trajectories.
Since the state function is nonlinear, we use the Jacobian evaluated at the true value of x _{ k } instead, that is,
where functions f _{1} and f _{2} are as in (8) and (9), respectively. Therefore, to evaluate the bound, we need to compute the derivatives in the Jacobian. These are
with
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Funding
The work of the second author was supported by the project MTM201571509C22R (MINECO/FEDER) and by the grant 2014SGR504 (Government of Catalonia).
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Closas, P., Guillamon, A. Sequential estimation of intrinsic activity and synaptic input in single neurons by particle filtering with optimal importance density. EURASIP J. Adv. Signal Process. 2017, 65 (2017). https://doi.org/10.1186/s1363401704993
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Keywords
 Statespace models
 Inference and learning
 Particle filtering
 Synaptic conductance estimation
 Spiking neuron
 Conductancebased model
 Intracellular recording