Systematic approximations of neural fields through networks of neural masses in the virtual brain
Introduction
With the availability of full brain structural connectivity information, the so-called connectome (Sporns, 2011), a new type of network models emerged that needed to address novel challenges characteristic for this macroscopic level of description. These challenges included the handling of a complex connectivity matrix in three-dimensional physical space, the inclusion of many time delays as a function of fiber lengths, as well as the correct choice of the mathematical model for a network node. Depending on the structural parcellation (Kötter and Wanke, 2005), a network node typically comprised a brain region of the size of multiple square centimeters (Hagmann et al., 2008). The full brain modeling approach proved successful in explaining the mechanisms underlying the emergence of network patterns and their coherent intermittent dynamics for resting state conditions (Deco and Jirsa, 2012, Deco et al., 2009, Deco et al., 2011, Ghosh et al., 2008). Crucial elements of the resting state dynamics include stochastics and multistability (Freyer et al., 2009, Freyer et al., 2011, Freyer et al., 2012). The resting state patterns and its dynamics are robust and reproducible within healthy populations (Damoiseaux et al., 2006, He et al., 2007, Mantini et al., 2007, Raichle et al., 2001), but differ quite significantly across diseases, such as schizophrenia, autism, epilepsy and others (Buckner et al., 2008, Cherkassky et al., 2006, Corbetta et al., 2005, Kennedy et al., 2006, Symond et al., 2005, Uhlhaas and Singer, 2006, Uhlhaas and Singer, 2010), as well as the aging brain (Beason-Held et al., 2009, Damoiseaux et al., 2008, Fransson et al., 2007, Koch et al., 2010, Supekar et al., 2010). For this reason the resting state dynamics finds enormous interest as a potential biomarker for disease or disorder. Of particular interest in these network manipulations is the ratio of local versus global connectivity. Local connectivity represents intracortical connections, whereas the global connectivity is the connectome comprising the white matter fibers between cortical and subcortical areas. Often local connectivity is absorbed in the parameters of the network node model. Manipulations of local connectivity (such as pruning of fibers during development or sprouting in epileptic tissue), however, are a key to modeling studies in a number of situations and require a representation of the full brain network, in which the brain region as a network node acquires more complexity and encompasses the notion of local connectivity. A natural extension of a network of coupled brain regions towards a spatially continuous sheet is provided by the neural field theory (Coombes, 2010, Deco et al., 2008, Jirsa, 2004). The aim of this work is to develop accurate numerical approximations of neural field models on folded cortical sheets with local and global connectivities, the latter typically obtained from tractographic data.
The numerical approximation of a neural field is realized via a network of neural masses. Neural field models cover the continuous description of interacting neural ensembles. A neural ensemble refers to a local set of commonly interacting neurons (Freeman, 1992). An ensemble of neurons of a certain class (e.g., due to receptor, location and/or morphological classifications) can be described in terms of mean firing rate and mean postsynaptic potential as a so-called neural mass. Hence, a neural mass model is a lumped representation, especially neglecting the spatial extend of a neural ensemble (Spiegler et al., 2010). Note that a single neural ensemble (or even a cortical area under certain functional circumstances Spiegler et al., 2011) can be described as a set of interacting neural masses, for instance, a neural mass of pyramidal cells, a neural mass of glutamatergic spiny stellate cells and a neural mass of GABAergic neurons (Spiegler et al., 2010). Usually nonlinear differential equations are used to mimic the complex behavior of neural ensembles. These equations are difficult to solve analytically and therefore such models are, nowadays, translated into a digital scheme for integration. This approach brings a discretization problem in its wake. That means that a neural field model is translated into a network of spatially separated sets of neural masses. For this purpose, a crucial step is the sampling of the spatial distribution function of the connections.
The sampling task can be addressed from three points of view with the aim: (i) to construct a model based on biophysical or theoretical considerations, (ii) to describe spatial patterns in specific empirical data, or (iii) to assess dynamics of an implemented neural field model. All three approaches are subject to restrictions of the considered underlying techniques. The resolution of human brain measurements, for instance, electrocorticography (ECoG) and functional magnetic resonance imaging (functional MRI) is in the order of mm (e.g., Blakely et al., 2008, Freeman, 2000, Yoo et al., 2004, Zhang et al., 2008). In the case of electro- and magneto-encephalography (EEG and MEG) the spatial resolution is in the order of cm (e.g., Freeman et al., 2003, Hämäläinen et al., 1993, Malmivuo and Suihko, 2004, Srinivasan et al., 1999). Moreover, implementations of a model in a digital regime underlie, for instance, a finite representation of numbers and its precision, and a finite number of network nodes.
This work deals with the spatial sampling of two specific but widely used choices of the homogeneous connectivity distribution function, namely, the sum of Gaussian (e.g., Amari, 1977, Atay and Hutt, 2005, Markounikau et al., 2010) and the sum of Laplace distributions (e.g., Jirsa and Haken, 1996). Because the main focus is on cortical dynamics, the spatial distribution function is to a first approximation assumed to be independent of the location on the cortical surface.
The main three emphases of this paper are: (i) what is the error that appears due to sampling a spatial distribution function; (ii) what are the usable parameters for a spatial distribution function considering the resolution of such measurements as EEG, MEG, ECoG and functional MRI; and (iii) how can the parameters of a spatial distribution function be specified giving a specific discrete approximation of a cortical geometry.
This work extends previous studies of neural fields, such as Bojak et al. (2010) and Freestone et al. (2011) in three points: (i) the sampling procedure can be assessed using two measures (ii) that are applicable in any dimensional physical space (iii) for two widely used spatial distribution functions.
Section snippets
Material and methods
Let φ be a variable of activity captured by the model (e.g., currents or potentials), the evolution in time t can then be described by the following ordinary differential equationwhere D(d/dt) is the temporal differential operator with the polynomial of constant coefficients D(λ) = ∑u = 0U buλu of order U and ϵ describes the (differentiable) input from interventions (e.g., transcranial magnetic stimulation) or other structures that are not explicitly described by the model (e.g.,
Results
The magnitude Gζ (qdB , k) and the frequency measure αζ (qα , k) allow for the assessment of the approximation of the homogeneous connectivity function Whom,ζ (z). The spatial cutoff frequency qc of the homogeneous connectivity is measured (see, for example, Fig. 3) as a function of the magnitude decay Gζ (qc , k) and the amount of uncovered spatial frequencies αζ (qc , k) for both building blocks, namely, Gaussian and Laplacian distributions (i.e., ζ = 1 and ζ = 2) with the standard deviation σζ :
Discussion
In this paper an approach is presented with the aim to assess the translation of neural field models into a network of neural masses. A translation is often inevitable, in particular with the aim to incorporate discrete information on heterogeneous connections established by white matter fibers (i.e., connectome). For this reason it is crucial to assess the translation of a spatiotemporal dynamic model in a digital scheme for integration. The work presented in this paper extends previous
Conclusion
Local connectivity contributes to the organization of the spatiotemporal large-scale brain dynamics. Before the full brain network modeling with local and global connectivity is carried into the applied domains, some ground truths need to be established. This has been the objective of the current article.
In general, a neural field needs to be approximated by a network of neural masses when
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inherent nonlinearities (e.g., transfer function S(φ) is sigmoidal) complicate solving the equation(s)
Acknowledgment
The authors would like to thank Anthony R. McIntosh and his group at the Rotman Research Institute of Baycrest Centre (University of Toronto, Ontario, Canada) for providing the structural data. We wish to thank Stuart Knock for many helpful discussions around the issue of extracting the cortex model. The research reported herein was supported by the Brain Network Recovery Group through the James S. McDonnell Foundation and the FP7-ICT BrainScaleS.
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