Abstract

The Soma and Neurite Density Imaging (SANDI) three-compartment model was recently proposed to disentangle cylindrical and spherical geometries, attributed to neurite and soma compartments, respectively, in brain tissue. There are some recent advances in diffusion-weighted MRI signal encoding and analysis (including the use of multiple so-called ’b-tensor’ encodings and analysing the signal in the frequency-domain) that have not yet been applied in the context of SANDI. In this work, using: (i) ultra-strong gradients; (ii) a combination of linear, planar, and spherical b-tensor encodings; and (iii) analysing the signal in the frequency domain, three main challenges to robust estimation of sphere size were identified: First, the Rician noise floor in magnitude-reconstructed data biases estimates of sphere properties in a non-uniform fashion. It may cause overestimation or underestimation of the spherical compartment size and density. This can be partly ameliorated by accounting for the noise floor in the estimation routine. Second, even when using the strongest diffusion-encoding gradient strengths available for human MRI, there is an empirical lower bound on the spherical signal fraction and radius that can be detected and estimated robustly. For the experimental setup used here, the lower bound on the sphere signal fraction was approximately 10%. We employed two different ways of establishing the lower bound for spherical radius estimates in white matter. The first, examining power-law relationships between the DW-signal and diffusion weighting in empirical data, yielded a lower bound of 7μm, while the second, pure Monte Carlo simulations, yielded a lower limit of 3μm and in this low radii domain, there is little differentiation in signal attenuation. Third, if there is sensitivity to the transverse intra-cellular diffusivity in cylindrical structures, e.g., axons and cellular projections, then trying to disentangle two diffusion-time-dependencies using one experimental parameter (i.e., change in frequency-content of the encoding waveform) makes spherical radii estimates particularly challenging. We conclude that due to the aforementioned challenges spherical radii estimates may be biased when the corresponding sphere signal fraction is low, which must be considered.

Highlights

  • Diffusion magnetic resonance imaging is a non-invasive technique widely used to study brain microstructure in vivo

  • There is a large difference in the sensitivity to sphere radius, with linear tensor encoding (LTE) being the least sensitive and planar tensor encoding (PTE) and spherical tensor encoding (STE) tracking each other closely in the plot of diffusivity of the spherical compartment (Dsphere) vs Rsphere

  • Continuous advances in image hardware, sequences and reconstruction mean that acquisitions times are getting shorter and shorter, which will allow this extended Soma and Neurite Density Imaging (SANDI) protocol to be incorporated into clinical studies

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Summary

Introduction

Diffusion magnetic resonance imaging (dMRI) is a non-invasive technique widely used to study brain microstructure in vivo. Using linear encoding, disentangling different microstructural properties such as their size, shape, and orientation is far from trivial (Lampinen et al, 2017a; Novikov et al, 2019). Such features may be entangled in the encoding process resulting in low specificity in their estimation. Most contemporary dMRI models for neural tissue share some common assumptions and features. They separate the tissue into intra- and extra- neurite compartments. Has a fixed and time-invariant signal fraction fi, most models treat the intra-neurite compartment as a ’stick’ - that is a compartment in which the diffusivity perpendic-

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