Alexis Reymbaut1,2
1Physical Chemistry, Lund University, Lund, Sweden, 2Random Walk Imaging AB, Lund, Sweden
Synopsis
Either on the voxel scale or within sub-voxel diffusion compartments, tissue microstructure can be described using a diffusion tensor distribution P(D). One way to resolve microstructural heterogeneity relies on choosing a plausible parametric functional form to approximate P(D). However, such a high-dimensional mathematical object is usually intractable. Here, we define matrix moments enabling the computation of diffusion metrics for any arbitrary functional choice approximating P(D). Applying these general tools to the matrix-variate Gamma distribution on the voxel scale, we obtain a new signal representation, the matrix-variate Gamma approximation, that we validate in vivo and in silico.
Introduction
The millimeter-scale resolution of diffusion MRI encompasses multiple microstructural tissue types, which implies that the diffusion signal probes a collection of microscopic diffusion profiles. Mathematically, this collection is described by a diffusion tensor distribution (DTD)
P(D),
1 yielding the diffusion signal
S(b)S0=∫Sym+(3)P(D)exp(−b:D)dD=⟨exp(−b:D)⟩,where
b is the encoding tensor,
2-4 Sym+(3) denotes the space of 3x3 symmetric positive-definite matrices, ":" is the Frobenius inner product, and
⟨⋅⟩ is the voxel-scale average. While nonparametric estimation of the DTD's features may be achievable,
5-7 an alternative approach consists in approximating
P(D) with a plausible parametric functional form whose parameters can be fitted against the acquired signals. This second approach, first implemented with distributions of scalar diffusivities,
8-10 has recently been extended to DTDs in two ways:
- the covariance tensor approximation,11 a two-term cumulant approach equivalent to considering a voxel-scale matrix-variate Gaussian (mv-Gaussian) DTD.12
- the DIAMOND model,13-15 a compartmental model wherein each anisotropic sub-voxel compartment is described by a matrix-variate Gamma (mv-Gamma) DTD.12
The former approach considers a distribution that, unlike the mv-Gamma distribution, allows for unphysical negative-definite diffusion tensors. However, the latter approach relies on assumptions regarding the voxel content.
In this work, we first derive general tools facilitating the implementation of any functional choice for
P(D). We then apply these tools to the mv-Gamma distribution and develop a new signal representation that describes the voxel content with a single mv-Gamma DTD: the "matrix-variate Gamma approximation". Finally, we validate this approximation in vivo and in silico.
Theory - Matrix moments of diffusion tensor distributions
We denote by "⋅" and "⊗" the matrix product and outer tensor product, respectively, with D⊗2≡D⊗D. Considering an arbitrary P(D), its moment-generating function writes12M(Z)=∫P(D)exp[Tr(Z⋅D)]dD=⟨exp[Tr(Z⋅D)]⟩,for Z such that M(Z) is well-defined. M(Z) relates to the diffusion signal as15S(b)=S0M(−b).By analogy with the moment-generating function of any scalar distribution, we showed that the first and second matrix derivatives of M(Z) yield the mean diffusion tensor ⟨D⟩ and the fourth-order covariance tensor C=⟨D⊗2⟩−⟨D⟩⊗2 associated to P(D). Indeed, we computed these derivatives using previous works16-18 as ∂M/∂Z=⟨exp[Tr(Z⋅D)]D⟩ and ∂2M/∂Z2=⟨exp[Tr(Z⋅D)]D⊗D⟩, deducing⟨D⟩=∂M∂Z|Z=0andC=∂2M∂Z2|Z=0−∂M∂Z|⊗2Z=0.Additional efforts would yield the sixth-order skewness tensor11 S=⟨D⊗3⟩−3⟨D⟩⊗⟨D⊗2⟩+2⟨D⟩⊗3 via ∂3M/∂Z3. While measures of voxel-scale diffusivity and anisotropy are extracted from ⟨D⟩, measures of sub-voxel anisotropy and sub-voxel variance in isotropic diffusivities are obtained from C according to previous work.11
Validation: We used the above formulae to retrieve the known mean tensor M and covariance tensor Σ⊗Ψ of the mv-Gaussian distribution12PGauss(X)=1(2π)9/2Det(Σ)3/2Det(Ψ)3/2exp[Tr(−12Σ−1⋅(X−M)⋅Ψ−1⋅(X−M)T)],for X,M arbitrary 3x3 real matrices, and Σ,Ψ∈Sym+(3), given its moment-generating function12MGauss(Z)=exp[Tr(Z⋅M+12ZT⋅Σ⋅Z⋅Ψ)].Theory - Matrix-variate Gamma approximation
We considered the non-central mv-Gamma distribution12 used in DIAMOND:14,15PΓ(D)=Det(D)κ−2Det(Ψ)κΓ3(κ)exp[−Tr(Θ+Ψ−1⋅D)]F0,1(κ,Θ⋅Ψ−1⋅D),where D∈Sym+(3), κ∈]1,+∞[, Ψ∈Sym+(3), and Θ∈Sym(3), with Sym(3) denoting the space of 3x3 symmetric matrices. Γ3 is the multivariate Gamma function and F0,1 is the hypergeometric function of matrix argument of order (0,1). The moment-generating function MΓ(Z) of PΓ is defined as12,15MΓ(Z)=[Det(I3−Z⋅Ψ)]−κexp[Tr([(I3−Z⋅Ψ)−1−I3]⋅Θ)]for Z∈Sym(3) such that (I3−Z⋅Ψ)∈Sym+(3), with the 3x3 identity matrix I3. The diffusion signal associated to PΓ is given by15SΓ(b)=S0MΓ(−b)=S0[Det(I3+Ψ⋅b)]−κexp[−b:[(I3+Ψ⋅b)−1⋅Ψ⋅Θ]].Using our expressions for the matrix moments, we retrieved the mean diffusion tensor of PΓ (employed in DIAMOND),14,15 and computed for the first time its covariance tensor, yielding⟨D⟩=Ψ⋅[κI3+Θ]andC=⟨D⟩⊗Ψ+Ψ⊗⟨D⟩−κΨ⊗Ψ. The expression of ⟨D⟩ and the symmetry of the different tensors imply that Ψ and Θ share the same eigenvectors. Therefore, fitting SΓ requires 11 parameters: S0, κ, the eigenvalues for Ψ and Θ, and the Euler angles orienting Ψ's eigenvectors. If numerically non positive-semidefinite, C is substituted with the nearest symmetric positive-semidefinite tensor.19Validation of the matrix-variate Gamma approximation
Statistical descriptors of interest: The mean diffusivity E[Diso], variance of isotropic diffusivities V[Diso], and normalized mean anisotropy ˜E[D2aniso]=E[(DisoDΔ)2]/E[Diso]2 (similar to the microscopic FA),10 with the isotropic diffusivity Diso, normalized diffusion anisotropy DΔ∈[−0.5,1], and the voxel-scale expectation and variance E[⋅] and V[⋅], respectively.
In vivo human brain: After implementing an iterative fitting of SΓ in Matlab,20 we applied it to a dataset available online,21 which signal-to-noise ratio (SNR) was around 30 in the corona radiata.22 Fig.1 presents the acquisition scheme and shows that mv-Gamma reasonably fits the signals arising from diverse voxel contents. Fig.2 features consistent estimated parameter maps of S0, E[Diso], V[Diso] and FA. However, ˜E[D2aniso] vanishes in areas of crossing fibers.
In silico: Various voxel contents were simulated in terms of distributions of Diso, DΔ and orientations, with identical in vivo acquisition scheme and SNR. Medians and interquartile ranges on estimating E[Diso], ˜E[D2aniso] and V[Diso] were assessed across 100 Rician-noise realizations of the covariance tensor approximation (Cov)11 and the matrix-variate Gamma approximation (MV-Gamma), and compared to the simulated ground truth in isotropic (Fig.3) and anisotropic (Fig.4) systems. MV-Gamma adequately captures voxel-scale anisotropy and shows superior performance to Cov in accurately capturing V[Diso], but is inferior in estimating E[Diso]. Besides, it cannot capture sub-voxel anisotropy (˜E[D2aniso]) in anisotropic systems with low orientational order, thereby confirming the previous in vivo observations.Conclusion
We defined matrix moments enabling the computation of diffusion metrics for any functional choice approximating a diffusion tensor distribution P(D). Applying these tools to the mv-Gamma distribution up to its second matrix moment yields a new signal representation, the matrix-variate Gamma approximation, that performs adequately in orientationally ordered anisotropic systems (further justifying its use within DIAMOND),14,15 but misses sub-voxel anisotropy in systems with low orientational order. This missing information is likely contained in the sixth-order skewness tensor, which can be obtained via a third matrix moment.Acknowledgements
This work was financially supported by the Swedish Foundation for Strategic Research (AM13-0090, ITM17-0267) and the Swedish Research Council (2018-03697).References
1. Jian B et al., A novel tensor distribution model for the diffusion-weighted MR signal. Neuroimage 2007;37(1):164-176
2. Eriksson S et al., Isotropic diffusion weighting in PGSE NMR by magic-angle spinning of the q-vector. Journal of Magnetic Resonance 2013;226:13-18.
3. Eriksson S et al., NMR diffusion-encoding with axial symmetry and variable anisotropy: Distinguishing between prolate and oblate microscopic diffusion tensors with unknown orientation distribution. The Journal of Chemical Physics 2015;142(10):104201.
4. Topgaard D, Multidimensional diffusion MRI. Journal of Magnetic Resonance 2017; 275:98-113.
5. de Almeida Martins J P and Topgaard D, Two-dimensional correlation of isotropic and directional diffusion using NMR. Physics Review Letters 2016;116:087601.
6. de Almeida Martins J P and Topgaard, D Multidimensional correlation of nuclear relaxation rates and diffusion tensors for model-free investigations of heterogeneous anisotropic porous materials. Scientific Reports 2018;8,2488.
7. Topgaard D. Diffusion tensor distribution imaging. NMR in Biomedicine 2019;32(5):e4066
8. Yablonskiy D A et al., Statistical model for diffusion attenuated MR signal, Magnetic Resonance in Medicine 2003;50:664.
9. Jbabdi S et al., Model-based analysis of multishell diffusion MR data for tractography: How to get over fitting problems. Magnetic Resonance in Medicine 2012;68:1846.
10. Lasic S et al., Microanisotropy imaging: quantification of microscopic diffusion anisotropy and orientational order parameter by diffusion MRI with magic-angle spinning of the q-vector. Frontiers in Physics 2014;2:11.
11. Westin C-F et al. Q-space trajectory imaging for multidimensional diffusion MRI of the human brain. NeuroImage 2016;135:345-362.
12. Guptar A K and Nagar D K, Matrix Variate Distributions. Edited by Chapman and Hall/CRC, Boca Raton, Florida, 2000.
13. Scherrer B et al., Characterizing brain tissue by assessment of the distribution of anisotropic microstructural environments in diffusion-compartment imaging (DIAMOND). Magnetic Resonance in Medicine 2016;76:963.
14. Scherrer B et al., Decoupling axial and radial tissue heterogeneity in diffusion compartment imaging. In: Information Processing in Medical Imaging (IPMI) 2017;440-452.
15. Reymbaut A et al., The “Magic DIAMOND" method: probing brain microstructure by combining b-tensor encoding and advanced diffusion compartment imaging. In: International Society for Magnetic Resonance Imaging (ISMRM) 2018.
16. Brewer J, Kronecker products and matrix calculus in system theory. IEEE Transactions on Circuits and Systems 1978;25:772.
17. Laue S et al., Computing higher order derivatives of matrix and tensor expressions. In: Advances in Neural Information Processing Systems (NIPS) 2018.
18. Laue S et al., Matrix calculus, www.matrixcalculus.org. Accessed: 2019-07-30.
19. Higham N J, Computing a nearest symmetric positive semidefinite matrix. Linear algebra and its applications 1988;103:103-118.
20. Nilsson M et al., An open-source framework for analysis of multidimensional diffusion MRI data implemented in MATLAB. In: International Society for Magnetic Resonance Imaging (ISMRM) 2018.
21. Szczepankiewicz F et al., Linear, planar and spherical tensor-valued diffusion MRI data by free waveform encoding in healthy brain, water, oil and liquid crystals. Data in Brief 2019;25:104208.
22. Szczepankiewicz F et al., Tensor-valued diffusion encoding for diffusional variance decomposition (DIVIDE): Technical feasibility in clinical MRI systems. PLoS ONE 2019;14(3):e0214238.