Abstract
Network representation has been an incredibly useful concept for understanding the behavior of complex systems in social sciences, biology, neuroscience, and beyond. Network science is mathematically founded on graph theory, where nodal importance is gauged using measures of centrality. Notably, recent work suggests that the topological centrality of a node should not be over-interpreted as its dynamical or causal importance in the network. Hence, identifying the influential nodes in dynamic causal models (DCM) remains an open question. This paper introduces causal centrality for DCM, a dynamics-sensitive and causally-founded centrality measure based on the notion of intervention in graphical models. Operationally, this measure simplifies to an identifiable expression using Bayesian model reduction. As a proof of concept, the average DCM of the extended default mode network (eDMN) was computed in 74 healthy subjects. Next, causal centralities of different regions were computed for this causal graph, and compared against several graph-theoretical centralities. The results showed that the subcortical structures of the eDMN were more causally central than the cortical regions, even though the graph-theoretical centralities unanimously favored the latter. Importantly, model comparison revealed that only the pattern of causal centrality was causally relevant. These results are consistent with the crucial role of the subcortical structures in the neuromodulatory systems of the brain, and highlight their contribution to the organization of large-scale networks. Potential applications of causal centrality—to study causal models of other neurotypical and pathological functional networks—are discussed, and some future lines of research are outlined.
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Data availability
The data analyzed in this study were obtained from the COllaborative Informatics and Neuroimaging Suite Data Exchange tool (COINS; https://coins.trendscenter.org). Data collection was performed at the Mind Research Network, and funded by a Center of Biomedical Research Excellence (COBRE) grant 5P20RR021938/P20GM103472 from the NIH to Dr. Vince Calhoun. The improved parcellation map of the DMN (Alves et al. 2019) has been publicly shared by the authors on the NeuroVault repository: https://identifiers.org/neurovault.image:568084.
Code availability
A demo code for the computation of causal centrality is available at: https://github.com/tszarghami/CausalCentrality. SC-ICA is part of the Group ICA of fMRI Toolbox (GIFT): http://trendscenter.org/software/gift/. Spectral DCM, PEB and BMR have been implemented in SPM12: https://www.fil.ion.ucl.ac.uk/spm/. Graph-theoretical measures can be computed using the centrality function in MATLAB.
Notes
A graph consists of nodes and edges, which represent the network elements and their interrelations, respectively (Barabási 2014).
In principle, a DCG can be converted to a succession of time-dependent DAGs (as noted by the Reviewer). This leads to an SEM with time-lagged data, like the autoregression models typically used in Granger causality analysis. As shown in Friston (2011), these models can be regarded as discrete-time formulations of DCM in continuous-time.
More precisely, after the distributions over the causal strengths have been estimated.
Generally, \(\theta\) encompasses all the unobservable variables of the model, including the hidden states, parameters and hyperparameters. In this work, we only intervene on the causal influences (i.e., the effective connectivity parameters) of DCM, which shape the causal architecture of the graph.
Free energy is a lower bound on log model evidence, hence known as evidence lower bound (ELBO) in machine learning. In variational Bayesian inference, the optimized free energy serves as a proxy for log model evidence. Note that this variational free energy is the negative of free energy in statistical physics.
Here we make sure that the full model has been structurally optimized (using exploratory BMR); hence, intervention decreases the model evidence. Note that, for an over-parametrized model, edge (parameter) removal can increase the model evidence, which is the foundation of structure learning and optimization using Bayesian model reduction (Beckers et al. 2022; Friston and Penny 2011; Jafarian et al. 2019; Neacsu et al. 2022).
In this context, a functional network refers to an intrinsic/large-scale brain network, which is a collection of brain regions showing functional connectivity (Friston 2011). This is not to be confused with the specialized functional network term in network neuroscience: i.e., a network in which the links depict statistical dependence between the nodes' time series (typically correlation). The two definitions can be reconciled by noting that the former (i.e., an intrinsic brain network) can be detected as a community/cluster in the latter (i.e., the whole-brain functional network)—as noted by the Reviewer.
http://fcon_1000.projects.nitrc.org/indi/retro/cobre.html.
Previous studies have reported that spatial smoothing can affect (functional) network construction and subsequent network analysis in nontrivial ways (Alakörkkö et al. 2017; Fornito et al. 2013; Stanley et al. 2013; Triana et al. 2020; Wu et al. 2011). Note that these concerns are more pronounced for higher-resolution (e.g. voxel-wise) networks (Stanley et al. 2013; van den Heuvel et al. 2008; Zalesky et al. 2012). Also note that, the generative model of DCM is designed to separate the observation noise from the underlying causal effects; as such, effective connectivity might be less prone to spurious (observation-level) correlations, than functional connectivity.
The choice of a small kernel size was based on recent research (Chen and Calhoun 2018), which recommends minimal spatial smoothing of fMRI data (with kernels spanning 2–3 voxels) before ICA analysis at the subject level.
Recent work has revealed the implication of DMN subsystems in the execution of certain external activities as well (see Mancuso et al. 2022 and the references therein).
Ventro-median prefrontal cortex (VMPFC).
Antero-median prefrontal cortex (AMPFC).
Dorsal prefrontal cortex (DPFC).
Temporal pole (TP).
Middle temporal gyrus (MTG).
Cerebellar hemisphere (CbH).
Cerebellar tonsil (CbT).
Since cross-spectra are the Fourier counterparts of cross-correlations, spectral DCM is essentially a causal model of how fMRI functional connectivity is generated.
Hence, the effective connections encoded in matrix \(A\) have units of Hertz. For more intuition, note that a differential equation of the form \(\dot{x}\left( t \right) = A*x(t)\), has a solution of the form \(x\left( t \right) \propto \exp \left( {A*t} \right)\). As such, \(A\) admits units of 1/s = Hz.
Blood oxygenation level dependent (BOLD).
Self-connections control the region's excitatory-inhibitory balance, or equivalently its gain or sensitivity to inputs.
In general, graph theoretical measures of centrality may be applied to structural, functional, or effective connectivity networks (Bullmore and Sporns 2009; Iturria-Medina et al. 2008; Prando et al. 2020; Stam and Reijneveld 2007). However, causal centrality has been specifically designed for the latter.
In Bayesian statistics, model evidence is the gold standard for model comparison/selection. In this sense, causal relevance of a centrality measure is just shorthand for the ability of that centrality information to improve the causal model evidence. Other (indirect) methods to assess the dynamical and causal relevance of the centrality information (such as comparison with other measures of nodal importance in control theory and accordance with etiological information) have been elaborated in the Discussion.
\(R^2 = \frac{{\text{Predicted sum of squares}}}{{\text{Total sum of squares}}} = \frac{{{\text{PSS}}}}{{{\text{TSS}}}},\) where PSS denotes the sum of squares of cross-spectra predicted/modeled by spectral DCM, and TSS denotes the total sum of squares of cross-spectra estimated from empirical data. The summations (of cross-spectra squared) are performed over frequency bins and pairs of regions for which the cross-spectra are computed. In SPM12, \(R^2\) for any fitted DCM can be calculated using spm_dcm_fmri_check.m.
Note that, the optimized model structure does not necessarily match the ground truth/true model. Because, by design, DCM offers the most accurate and least complex explanation for the given data, which may not match the more complex ground truth that has generated the data (Litvak et al. 2019). As such, the modeling results and their interpretations are bound to the model assumptions and the model space.
Bayes factor (BF) is the ratio of model evidences (aka marginal likelihoods, ML) of two competing models explaining the same data \(y\). That is, BF ≜ P(y|M1)/P(y|M2) = ML1/ML2. In the log space, log BF = log (ML1) − log (ML2) ≈ F1 − F2 = ΔF. So, when ΔF = 3 nats, model 1 is deemed \(e^3 \approx 20\) times more plausible than model 2, reminiscent of the conventional 0.05 threshold in classical statistics.
Of course, what constitutes the right dynamics is application- and model-dependent.
Recent approaches in network neuroscience have proposed models of communication dynamics as potential generative models of effective connectivity in the brain (Avena-Koenigsberger et al. 2018), to explain how patterns of functional connectivity can be generated from the interplay between (anatomical) network topology and specific communication dynamics that unfold on the network. Note that, these dynamics are mostly route-based or diffusion-based (Avena-Koenigsberger et al. 2018)—although several biophysically grounded extensions exist (Cabral et al. 2014; Deco et al. 2017). More importantly, models of communication dynamics are forward generative models, often not accompanied by model inversion. As such, adapting causal centrality to these models is not straightforward and requires further study.
Note that, an inhibitory (excitatory) causal effect is not necessarily analogous to an inhibitory (excitatory) projection in the brain. Because, long range excitatory and inhibitory projections originating from one brain region (Urrutia-Piñones et al. 2022) can land on excitatory or inhibitory neural subpopulations in the target region; these subpopulations have their own interconnected dynamics. To separately model the activity and connectivity of excitatory and inhibitory neural ensembles, two-state DCMs and their extensions can be used (Marreiros et al. 2008; Sadeghi et al. 2020).
Future research can investigate whether the causal and GT centrality results would diverge further as the size of the causal network increases and the dynamics get more complex.
Controllability quantifies the capability of a node/module to drive the dynamical system towards a desired state, using external input. Higher controllability reflects lower average control energy needed to drive the network from that node or set of nodes (Cai et al. 2021; Gu et al. 2022; Liu and Barabási 2016; Pasqualetti et al. 2014).
Dynamical flexibility refers to the brain’s propensity to transition between multiple functional states (Gu et al. 2022).
Causal outflow has been defined as the absolute weighted out-degree of a node on a causal graph (Cai et al. 2021).
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Appendices
Appendix 1: Causal centrality derivation
In this appendix, the identifiable expression in Eq. 6 is derived from the definition of causal centrality in Eq. 4, and the normalization constant (Z in Eq. 4) is clarified in this process. To start, we expand the KL-divergence between the pre- and post-intervention distributions:
The first equality is just the definition of KL-divergence: \(D_{{\text{KL}}} \left( {P_1 ||P_2 } \right) \triangleq \smallint \limits_z P_1 \left( z \right)\log \frac{P_1 \left( z \right)}{{P_2 \left( z \right)}}{\text{d}}z\). The second equality uses the product rule of probability: \(P\left( {Y,\theta |m} \right) = P\left( {\theta |Y,m} \right) P\left( {Y|m} \right)\). Herein, R as a superscript refers to the reduced/post-intervention model, whereas the full/pre-intervention model bears no superscript. With some re-arrangement, Eq. 11 simplifies to:
In variational Bayesian inference, the optimized variational density and free energy replace the posterior density and log model evidence: \(Q\left( {\theta |Y,m} \right) \approx P\left( {\theta |Y,m} \right)\) and \(F \approx \log P\left( {Y|m} \right)\). Hence, Eq. 12 simplifies to:
Causal centrality is estimable as the normalized version of Eq. 13, where the normalization constant \(Z = P\left( {Y|m} \right) \approx \exp \left( F \right)\). As such, we arrive at Eq. 6:
where the posterior and free energy of the reduced model can be computed analytically using Bayesian model reduction, as elaborated in “Appendix 2”. Moreover, under Gaussian assumptions on the posterior distributions in variational Laplace (Friston et al. 2007; Zeidman et al. 2023), the KL-divergence between the two (full and reduced) Gaussian posteriors can be readily computed as:
where \(\mu\) and \({\Sigma }\) denote the mean vector and the covariance matrix, respectively; \(d\) is the dimensionality of the multivariate Gaussians; \(F\) and \(R\) subscripts refer to the full and reduced models, respectively; tr stands for the trace of a matrix, and \(\ln = \log_{\text{e}}\).
Appendix 2: Bayesian model reduction derivations
Bayesian model reduction refers to the analytic inversion of reduced models using the priors and posteriors of a full model. Reduced models are nested within a full model; that is, they include only a subset of the parameters of the full model after “switching off” the other parameters (by imposing very precise null priors, which shrinks them to zero). Consider Bayes rule replicated for the full and reduced models (denoted by \(m\) and \(m^R\), respectively) (Friston et al. 2016, 2018; Friston and Penny 2011):
Since the models differ only in terms of their priors, the likelihood terms are identical:
Hence, equating the expressions in Eqs. 16 and 17 over the likelihood gives:
By re-arranging Eq. 19, we get the posterior distribution over the parameters of the reduced model:
On the R.H.S. of Eq. 20 only \(P^R \left( {y|m^R } \right)\) is unknown, which is the model evidence for the reduced model. This term can be obtained by integrating both sides of Eq. 20 over \(\theta\):
In the last line, the optimized variational density and free energy have replaced the posterior density and log model evidence: \(Q\left( {\theta |Y,m} \right) \approx P\left( {\theta |Y,m} \right)\) and \(F \approx \log P\left( {Y|m} \right)\). Under Gaussian assumptions for the distributions (in variational Laplace), the reduced posterior and free energy take simple forms, as elaborated in Friston et al. (2016, 2018) and Friston and Penny (2011).
Appendix 3: Graph theoretical centralities
This appendix includes the mathematical expressions for several graph-theoretical centrality measures. These measures are defined for weighted networks, based on Opsahl et al. (2010), which generalizes the definitions originally proposed for binary networks (Freeman 1979).
Node strength is the generalization of node degree (i.e., the number of connections of a node) for weighted networks, which is defined for node \(x_i\) as:
where \(n\) is the number of nodes, |.| denotes the absolute value function, and \(a_{ij}\) is the \(\left( {i,j} \right){\text{th}}\) entry of the weighted adjacency matrix \(A\).
Closeness centrality is defined as:
where \(d(i,j)\) denotes the shortest path between nodes \(x_i\) and \(x_j\), which is the path that minimizes the cost of travelling from \(x_i\) to \(x_j\); the cost of travelling is the inverse of the weight of the (directed) edges connecting the two nodes—as encoded in the adjacency matrix.
Betweenness centrality is defined as:
where \(g_{jk} (x_i )\) is the number of shortest paths between nodes \(x_j\) and \(x_k\) that go through node \(x_i\); and \(g_{jk}\) is the total number of shortest paths between nodes \(x_j\) and \(x_k\).
Note that in the formulation of DCM (Eq. 7), \(A\) encodes the directed causal influences; hence, it corresponds to the adjacency matrix of a (directed weighted) signed graph, in which excitatory (positive) and inhibitory (negative) effects are equally important. In this case, the absolute values of the causal connections are typically computed (Cai et al. 2021; Dablander and Hinne 2019). So, to compute the closeness and betweenness centralities (based on the notion of shortest paths), \(A\) was converted to an unsigned matrix first, using the absolute function: \(A \to |A|\).
Finally, for a node to have high eigenvector centrality, it should be connected to many other nodes that also have high eigenvector centrality. In other words, connection to an important node counts more than connection to a less important node. This notion is formalized using the first eigenvector of the adjacency matrix (Bonacich 2007; Bonacich and Lloyd 2001):
where \(\lambda\) is the largest eigenvalue of an undirected adjacency matrix, and \(\nu_j\) is the jth element of the corresponding eigenvector; \(N(x_i )\) denotes the set of nodes that are adjacent/neighbor to \(x_i\). Since eigenvector centrality is defined for undirected graphs, the (unsigned weighted) directed adjacency matrix \(\left| A \right|\) was first symmetrized as follows: \(\left| A \right| \to \frac{{\left| A \right| + \left| {A^{\text{T}} } \right| }}{2} = \left| A \right|_{{\text{sym}}}\); where \(T\) denotes the transpose operator.
The graph-theoretical centrality measures were computed using the centrality function in MATLAB R2021b.
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Zarghami, T.S. A new causal centrality measure reveals the prominent role of subcortical structures in the causal architecture of the extended default mode network. Brain Struct Funct 228, 1917–1941 (2023). https://doi.org/10.1007/s00429-023-02697-w
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DOI: https://doi.org/10.1007/s00429-023-02697-w