Abstract

Local fiber orientation distributions (FODs) can be computed from diffusion magnetic resonance imaging (dMRI). The accuracy and ability of FODs to resolve complex fiber configurations benefits from acquisition protocols that sample a high number of gradient directions, a high maximum b-value, and multiple b-values. However, acquisition time and scanners that follow these standards are limited in clinical settings, often resulting in dMRI acquired at a single shell (single b-value). In this work, we learn improved FODs from clinically acquired dMRI. We evaluate patch-based 3D convolutional neural networks (CNNs) on their ability to regress multi-shell FODs from single-shell FODs, using constrained spherical deconvolution (CSD). We evaluate U-Net and High-Resolution Network (HighResNet) 3D CNN architectures on data from the Human Connectome Project and an in-house dataset. We evaluate how well each CNN can resolve FODs 1) when training and testing on datasets with the same dMRI acquisition protocol; 2) when testing on a dataset with a different dMRI acquisition protocol than used to train the CNN; and 3) when testing on a dataset with a fewer number of gradient directions than used to train the CNN. This work is a step towards more accurate FOD estimation in time- and resource-limited clinical environments.

Highlights

  • Diffusion magnetic resonance imaging can be used to investigate the organization of white matter (WM)

  • For all Tables and Figures, the acronym Queen Square (QS) 700-Human Connectome Project (HCP) 2000 CNN UNet indicates that Constrained spherical deconvolution (CSD) coefficients are from a CNN trained on the QS dataset using the 2-tissue CSD (2TS-CSD) coefficients from b = 700 s/mm2 shell and tested using as input 2TS-CSD coefficients from the HCP dataset from the b = 2000 s/mm2 shell

  • Experiment 1 – Intra-Scanner Acquisition Performance We assess how well CNNs were able to regress multi-tissue CSD (M-CSD) coefficients when using Diffusion magnetic resonance imaging (dMRI) acquired on the same scanner and with the same protocol for training and testing

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Summary

Introduction

Diffusion magnetic resonance imaging (dMRI) can be used to investigate the organization of white matter (WM). WM tissue microstructural organization, such as axon diameter [5] and local fiber orientation distribution (FOD or fODF) [6], can be esti­ mated from dMRI acquisitions. FODs can be used to perform fiber tractography [7,8], which has an important role in presurgical planning [9,10,11,12] and connectome analyses [13]. A common method to estimate local fiber orientation is diffusion tensor imaging (DTI) [3]. More robust methods for representing FODs have been proposed based on spherical deconvolu­ tion [14,15,16] or other approaches that estimate diffusion orientation distribution functions from q-space [16,17]

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