Local White Matter Architecture Defines Functional Brain Dynamics
Total Page:16
File Type:pdf, Size:1020Kb
2018 IEEE International Conference on Systems, Man, and Cybernetics Local White Matter Architecture Defines Functional Brain Dynamics Yo Joong Choe* Sivaraman Balakrishnan Aarti Singh Kakao Dept. of Statistics and Data Science Machine Learning Dept. Seongnam-si, South Korea Carnegie Mellon University Carnegie Mellon University [email protected] Pittsburgh, PA, USA Pittsburgh, PA, USA [email protected] [email protected] Jean M. Vettel Timothy Verstynen U.S. Army Research Laboratory Dept. of Psychology and CNBC Aberdeen Proving Ground, MD, USA Carnegie Mellon University [email protected] Pittsburgh, PA, USA [email protected] Abstract—Large bundles of myelinated axons, called white the integrity of the myelin sheath is critical for synchroniz- matter, anatomically connect disparate brain regions together ing information transmission between distal brain areas [2], and compose the structural core of the human connectome. We fostering the ability of these networks to adapt over time recently proposed a method of measuring the local integrity along the length of each white matter fascicle, termed the local [4]. Thus, variability in the myelin sheath, as well as other connectome [1]. If communication efficiency is fundamentally cellular support mechanisms, would contribute to variability constrained by the integrity along the entire length of a white in functional coherence across the circuit. matter bundle [2], then variability in the functional dynamics To study the integrity of structural connectivity, we recently of brain networks should be associated with variability in the introduced the concept of the local connectome. This is local connectome. We test this prediction using two statistical ap- proaches that are capable of handling the high dimensionality of defined as the pattern of fiber systems (i.e., number of fibers, data. First, by performing statistical inference on distance-based orientation, and size) within a voxel, as well as immediate correlations, we show that similarity in the local connectome connectivity between adjacent voxels, that can be quantified between individuals is significantly correlated with similarity in using diffusion MRI (dMRI) by measuring the fiber-wise their patterns of functional connectivity. Second, by employing density of microscopic water diffusion within a voxel [1]. The variable selection using sparse canonical correlation analysis and cross-validation, we show that segments of the local connectome collection of these multi-fiber diffusion density measurements are predictive of certain patterns of functional brain dynamics. within all white matter voxels is termed the local connectome These results are consistent with the hypothesis that structural fingerprint (LCF). The LCF is a high-dimensional feature variability along axon bundles constrains communication be- vector that describes the unique configuration of the structural tween disparate brain regions. connectome along the segments of white matter pathways [5]. Index Terms—local connectome, structure-function relation- ship, high-dimensional statistics, canonical correlation analysis Thus, the LCF provides a diffusion-informed measure along the fascicles that supports inter-regional communication, rather than determining the start and end positions of a particular fiber bundle. I. INTRODUCTION Since the LCF measures the local integrity along white The function of macroscopic neural networks is constrained matter bundles that connect regions across the entire brain, by the integrity of structural connections between disparate it reflects the overall communication capacity of the brain [2]. regions. This form of long-distance (i.e., centimeters) commu- Hence, we expect to see that variations in the LCF should also nication relies on dense bundles of axons that are known as correlate with those in the dynamics of brain networks, mea- white matter [3]. To prevent degradation of action potentials sured by connectivity patterns in the resting-state functional across long distances, these fiber bundles are supported by MRI (fMRI). To formally validate this intuition, we employ the myelin sheath, non-neuronal glial cells that insulate axons statistical approaches to examine the following hypotheses: and facilitate communication along the fascicle. As a result, Hypothesis 1 Similarity in the LCF, between individuals, is associated with similarity in their functional connectivity The research was sponsored by the U.S. Army Research Laboratory, patterns measured with resting-state fMRI. including work under Cooperative Agreement Number W911NF-10-2-0022, Hypothesis 2 Variability in specific segments of the LCF is and the views espoused are not official policies of the U.S. Government. *Y. C. is currently on leave from Carnegie Mellon University, where most associated with patterns of functional connectivity in specific of this work was done. circuits. 2577-1655/18/$31.00 ©2018 IEEE 595 DOI 10.1109/SMC.2018.00110 TABLE I: Summary of Abbreviations and Notation Notation Definition LCF Local connectome fingerprint FCG Functional correlation graph HCP The Human Connectome Project (dataset) n Number of subjects (793) p Dimension of LCF vectors (433,386) q Dimension of FCG vectors (195,625) xi p-dimensional LCF vector of subject i yi q-dimensional FCG vector of subject i dX The scaled Euclidean distance between LCFs (1) Fig. 1: Pipeline for generating LCFs. See [5] for details. dY The Pearson correlation distance between FCGs (2) DX Scaled Euclidean distance matrix between n LCFs DY Pearson correlation distance matrix between n FCGs X n × p matrix containing the n LCFs as rows code for this analysis are publicly available on the same Y n × q matrix containing the n FCGs as rows website. ·1, ·2 The 1- and 2-norm of a real-valued vector Sn The permutation group on {1,...,n} A spin distribution function (SDF) sampling framework was used to provide a consistent set of directions to sample the magnitude of SDFs along axonal directions in the cerebral II. MATERIALS AND METHODS white matter. Since each voxel may have more than one axonal direction, multiple measurements were extracted from the We summarize our abbreviations and notation in Table I. SDF for voxels that contained crossing fibers, while a single A. Data Acquisition measurement was extracted for voxels with fibers in a single 1) Participants: We used publicly available dMRI and direction. The appropriate number of density measurements fMRI data from the S900 (2015) release of the Human from each voxel was sampled by the left-posterior-superior Connectome Project (HCP) [6], acquired by Washington Uni- voxel order and compiled into a sequence of scalar values. versity in St. Louis and the University of Minnesota. Out Gray matter was excluded using the ICBM-152 white matter of the 900 participants released, 841 genetically unrelated mask (MacConnell Brain Imaging Centre, McGill University, participants (370 male, ages 22-37, mean age 28.76) had Canada). The cerebellum was also excluded due to different viable dMRI datasets. Among them, n = 793 participants slice coverage in cerebellum across participants. Since had at least one viable resting-state fMRI measurement. Our the density measurement has arbitrary units, the LCF was analysis was restricted to this subsample. All data collection scaled to make the variance equal to 1 [5]. For each subject i =1,...,n i procedures were approved by the institutional review boards , we denote this high-dimensional LCF of the th p = 433, 386 x ∈ Rp at Washington University in St. Louis and the University subject, across sampled directions, as i . n of Minnesota. The post hoc data analysis was approved as The collection of all LCFs are compactly represented as a X =[x ,...,x ]T ∈ Rn×p exempt by the institutional review board at Carnegie Mellon data matrix 1 n with each LCF as a University, in accordance with 45 CFR 46.101(b)(4) (IRB row vector. Protocol Number: HS14-139). 2) Diffusion MRI Acquisition: The dMRI data were ac- 4) Functional MRI Acquisition & Processing: We analyzed quired on a Siemens 3T Skyra scanner using a 2D spin-echo the minimally processed resting-state fMRI data acquired as single-shot multiband EPI sequence with a multi-band factor part of the Human Connectome Project (HCP) [8], [6] which of 3 and monopolar gradient pulse. The spatial resolution was used a multi-band gradient echo-planar imaging protocol (see 1.25 mm isotropic (TR = 5500 ms, TE = 89.50 ms). The b- [9] for details on aquisition parameters). The dataset con- values were 1000, 2000, and 3000 s/mm2 . The total number tains volumetric NIFTI data for resting-state fMRI scans (14 of diffusion sampling directions was 90 for each of the three minutes each), motion parameters, and physiological data. shells in addition to 6 b0 images. The total scanning time was Only data for the first resting-state scan collected at the A- approximately 55 minutes. P phase encoding direction were used for analyses. Using 3) LCF Reconstruction: An outline of the pipeline for these measurements, we computed the average BOLD (blood- generating LCFs is shown in Fig. 1. The dMRI data for oxygen-level dependent) signals at each of the 626 regions each subject was reconstructed in a common stereotaxic space of interest (ROIs) [10] and regressed out the linear effects using q-space diffeomorphic reconstruction (QSDR) [7], a of the noise terms via ordinary least-squares (OLS). The 16 nonlinear registration approach that directly reconstructs water noise terms include the global signal, 12 motion parameters (6 diffusion density patterns into a common stereotaxic space estimates from a rigid-body transformation to the SBRef image at 1 mm resolution. The LCF reconstruction was conducted acquired at the start of each scan; 6 temporal derivatives of using DSI Studio (http://dsi-studio.labsolver.org), an open- these estimates), and the top-3 principal component projections source diffusion MRI analysis tool for connectome analysis. of the voxel-level white matter signals (measured at each of To compute the LCF, the axonal direction in each voxel was 2,258 voxels and 840 seconds).