Bayesian analysis of the neuromagnetic inverse problem with ℓp-norm priors
Introduction
Magnetoencephalography (MEG) allows non-invasive measurement of the magnetic fields generated by neural activity of the living brain (e.g., Baillet et al., 2001, Hämäläinen et al., 1993, Vrba and Robinson, 2001). Along with clinical applications, MEG is used in studies of basic sensory (auditory, visual, and somatosensory) processes as well as cognitive functions. Time resolution of this method is excellent (∼milliseconds), but in order to locate the underlying source currents accurately on the basis of MEG data, one needs to solve the so-called electromagnetic inverse problem, which does not have a unique solution (Sarvas, 1987). Therefore, additional constraints are needed to select the most feasible estimate from the multitude of possible solutions.
A traditional approach to the MEG inverse problem is to employ the equivalent current dipole (ECD) model, which relies on the assumption that the extents of the activated areas are small enough to be adequately modeled with dipolar point-like sources. Using fully automatic or manually guided, often partly heuristic, fitting methods, the model giving best fit to the measured data is obtained. A downside is that the number and locations of the source dipoles need to be known to a certain extent (although, see Mosher et al., 1992). This is a problem especially when complex cognitive brain functions are studied.
Other widely used methods employ distributed source current estimates (e.g., Hämäläinen et al., 1993, Pascual-Marqui, 2002, Uutela et al., 1999). In the well-known minimum-norm (Dale and Sereno, 1993, Dale et al., 2000, Hämäläinen and Ilmoniemi, 1984, Hauk, 2004) and minimum-current (Uutela et al., 1999) estimates (MNE and MCE), extra information is embedded to the model as mathematical ℓ2- and ℓ1-norm constraints on the source currents, respectively. Specifically, the least squares error function is combined with an additional penalty term consisting of a weighted norm of the current distribution. Unlike dipole fitting, the exact number and approximate locations of the sources do not need to be known in advance. However, the resulting estimate may be quite diffuse, especially in the case of the minimum-norm estimate and, therefore, it may be equally difficult to discern the number of distinct activated areas in practice.
In Bayesian interpretation, MNE and MCE correspond to ℓ2- and ℓ1-norm priors for the source currents with a Gaussian likelihood for the measurements (Uutela et al., 1999). The use of predefined values 1 or 2 for the ℓp-norm order p is somewhat arbitrary as it leads to prior-wise feasible inverse models even though any value between 1 and 2 could be used. The ℓ2-norm prior produces overly smooth and widely spread estimates whereas ℓ1-norm estimates might be too focal. The choice of p is subject to uncertainty, hence p should be treated as an unknown variable utilizing Bayesian inference, which has lately gained popularity in solving the electromagnetic inverse problem (e.g., Baillet and Garnero, 1997, Phillips et al., 1997, Schmidt et al., 1999). Markov chain Monte Carlo (MCMC) methods have become popular in this methodology due to rapid expansion of computing resources (e.g., Kincses et al., 2003, Schmidt et al., 1999).
In this paper, we perform a Bayesian analysis of the MEG inverse problem with ℓp-norm priors, using MCMC methods and simulated source currents with a realistic MRI-based forward head model. Furthermore, we apply the model on a set of real MEG measurement data. The purpose of this study is to focus on the Bayesian interpretation of the problem, determine an optimal source space discretization size when the discretized points are assumed independent of each other, and to determine whether there is enough information in the data to clarify which ℓp-norm prior should be used. We specifically hypothesize that there is no single value for p that would be optimal for all cases, but instead the value depends on the grid discretization size and also on the underlying source configuration and, therefore, it should be inferred from the data rather than determined ad hoc.
Section snippets
Materials and methods
Simulated data were generated in order to test the performance of our model with a priori known, functionally realistic, source locations (see Fig. 1). Source space was discretized according to real anatomical MRI-based brain surface reconstruction (Dale and Sereno, 1993, Dale et al., 1999, Fischl et al., 1999) and simulated sources were then used to calculate the measurements, to which Gaussian noise was added. The spatial inverse problem was addressed with a Bayesian model utilizing numerical
Results
An MCMC chain was produced for each of the simulated sources and for each of the grid sizes separately. For the smaller grid sizes (∼200, ∼400, and ∼800 points per hemisphere), the time required to draw one sample (i.e., one set of source current parameters and hyperparameters) from the joint posterior distribution was in the order of 1–4 s. At least 10,000 samples were drawn for each of these chains. For the chains of the larger grid sizes (∼1600 and ∼3200 per hemisphere), the time required
Discussion
We studied a Bayesian MEG inverse model with ℓp-norm priors for the source currents. This type of model has not been implemented before, even though similar ideas considering different values of p have been suggested (e.g., Beucker and Schlitt, 1996, Bücker et al., 2001, Matsuura and Okabe, 1995, Uutela et al., 1999). Using Bayesian methodology, the full joint posterior distribution of the parameters and hyperparameters of the model, such as the ℓp-norm order p and prior width σc, can be
Acknowledgments
This research was supported in part by Academy of Finland (projects: 200521, 202871, 206368), Instrumentarium Science Foundation, Finnish Cultural Foundation, National Institutes of Health (RO1-HD40712), The MIND Institute, and Jenny and Antti Wihuri Foundation. Authors would like to thank anonymous reviewers for helpful remarks and Mr. Antti Yli-Krekola for a helping hand with the preprocessing of MR-images.
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