Ezequiel Farrher1, Richard Buschbeck1, Chang-Hoon Choi1, Li-Wei Kuo2,3, Seong-Dae Yun1, Farida Grinberg1,4, and N. Jon Shah1,4,5,6,7
1Institute of Neuroscience and Medicine 4, Forschungszentrum Jülich, Jülich, Germany, 2Institute of Biomedical Engineering and Nanomedicine, National Health Research Institutes, Miaoli, Taiwan, 3Institute of Medical Device and Imaging, National Taiwan University College of Medicine, Taipei, Taiwan, 4Department of Neurology, Faculty of Medicine, RWTH Aachen University, Aachen, Germany, 5JARA – BRAIN – Translational Medicine, RWTH Aachen University, Aachen, Germany, 6Institute of Neuroscience and Medicine 11, Forschungszentrum Jülich, Jülich, Germany, 7Biomedical Imaging, School of Psychological Sciences, Monash University, Melbourne, Australia
Synopsis
Free-water elimination allows one to reduce the bias in DTI metrics
induced by partial-volume effects. Unfortunately the fitting problem for this
model is ill-conditioned. However, it has been recently demonstrated that the
introduction of a second dimension determined by the echo-time, leads to a
well-conditioned fitting problem. In this work we investigate the experimental
design and data analysis pipeline of such experiments in vivo.
Introduction
Free-water elimination (FWE) has been proposed to reduce the
bias in DTI metrics induced by partial-volume effect (PVE).1,2 It has
been shown to be sensitive to the free-water content in the substantia nigra in
Parkinson’s patients3
and useful in detecting
microstructural white matter alterations in Alzheimer’s disease.4
Unfortunately, the fitting problem is
inherently ill-conditioned and consequently usually problematic.1,5
However, it has been recently demonstrated that the addition of a second
dimension, in this case spanned by the echo-time, TE, i.e., weighted by the transverse relaxation time, T2, transforms the problem into
a well-conditioned one.7 Thus the aim of this work is to investigate
the experimental design and data analysis workflow for FWE with T2 weighting (FWET2)
in vivo.Methods
The model we adopt here assumes that the diffusion MRI signal originates
from two compartments with different transverse relaxation rates and
diffusivities, in the slow-exchange limit1,7 $$S\left( T_\mathrm{E},b ,\mathbf{g}\right)=S_0\left[ f_\mathrm{w}e^{-\frac{T_\mathrm{E}}{T_{2,0}}}e^{-bD_0}+\left(1-f_\mathrm{w}\right)e^{-\frac{T_\mathrm{E}}{T_{2,\mathrm{t}}}}e^{-b\mathbf{g}^\mathrm{T}\mathbf{D}\mathbf{g}}\right]\mathrm{, (1)}$$ where S0 is the proton density, fw, T2,0 and D0
are the fraction, transverse relaxation time and diffusion coefficient of the
free-water compartment and T2,t
and D are the transverse relaxation
time diffusion tensor for the tissue compartment. The experimentally controlled
parameters are the strength and direction of the diffusion weighting gradient, b and g, and TE
(Fig.1).
Experiments were performed on a healthy volunteer, in a 3T Siemens Trio scanner (Siemens, Erlangen, Germany).
Prior written, informed consent was obtained from the volunteer. A
Stejskal-Tanner pulse sequence with monopolar pulse field gradients and EPI
readout was implemented for this purpose. The sequence was designed to
independently control the gradient pulse duration, δ, and separation, Δ, as
well as TE. Thus,
the diffusion-dimension and the relaxation-dimension are fully decoupled.
Experimental parameters included (Fig. 1): 4 experiments with TE = 70, 100, 130, 170 ms; b-values = 0 (6 repetitions), 500 (20
directions), 1000 (40 directions) s/mm2; Δ = 34 ms and δ = 19 ms.
Additionally, we acquired 8 more echo-times, in the range TE $$$\in$$$ [70, 210] ms. The experiment with TE = 70 ms was acquired twice with
opposite phase-encoding (anterior-posterior, posterior-anterior) in order to
correct for EPI distortions. Other parameters were voxel-size = 23 mm3;
matrix-size = 100×100×60; repetition-time, TR = 15 s and GRAPPA acceleration
factor = 2.
Eddy current and EPI distortions were corrected using
the EDDY toolkit available in FSL.8 FWET2 DTI parameter
estimation was performed in three steps:
- Experimental
data with b = 0 s/mm2 was
used to generate an initial guess for T2,t
using the linear least-squares (LLS) method: $$$\hat{\gamma}_\mathrm{SE}=\left(W^{\mathrm{T}}_{\mathrm{SE}}W_\mathrm{SE}\right)^{-1}W^{\mathrm{T}}_{\mathrm{SE}}y$$$, where $$$W_{\mathrm{SE}}=\left[1,-T_\mathrm{E}\right]^\mathrm{T}$$$, $$$\gamma_{\mathrm{SE}}=\left[\ln{S^\mathrm{SE}_0},1/T_{2,\mathrm{t}}\right]^\mathrm{T}$$$ and y is the measured data. Similarly the initial guess for D was generated using the DWI
experiment with TE = 70 ms
using LLS: $$$ \hat{\gamma}_\mathrm{DTI}=\left(W^\mathrm{T}_\mathrm{DTI}W_\mathrm{DTI}\right)^{-1}W^{\mathrm{T}}_{\mathrm{DTI}}y$$$, where $$$W_{\mathrm{DTI}}=\left[1,-bg^2_x,-2bg_xg_y,-2bg_xg_z,-bg^2_y,-2bg_yg_z,-bg^2_z,\right]^\mathrm{T}$$$ and $$$\gamma_{\mathrm{DTI}}=\left[\ln{S^\mathrm{DTI}_0},D_{11},D_{12}...,D_{33}\right]^\mathrm{T}$$$.
- Having had the
initial guess for D and T2,t, an initial guess for fw was generated using the
method proposed by Hoy et al.5 and Neto Henriques et al.6 using a non-linear least-squares (NLLS)
method.
- Finally FWET2
was fitted via NLLS minimisation using the initial guess generated in the
former steps, with the help of the Levenberg-Marquardt algorithm with in-house
Matlab scripts. The power images method9 was used to reduce the bias
due to background noise prior fitting. Values for D0 = 3×10-3 mm2/s and T2,0 = 500 ms
were fixed according to literature values.10 Thus, the model
parameters are $$$\gamma_\mathrm{FWET2}=\left[S_0,f_\mathrm{w},D_{11},D_{12},...,D_{33},T_{2,\mathrm{t}}\right]$$$. The NLLS estimator is given by $$\gamma_\mathrm{FWET2}=\arg \min \sum_{i} \left[y_i-S\left(T_{\mathrm{E},i},b_i,\mathbf{g}_i\right)\right]^2\mathrm{. (2)}$$
Results and Discussions
Figs. 2a and 2b show the maps of mean diffusivity (MD) and fractional
anisotropy (FA) obtained with conventional DTI analysis. Figures 2c-2g exhibit the
maps of S0, fw, MD, FA, and T2,t obtained via FWET2 analysis. One can observe that MD
and FA from DTI show strong bias due to PVE, which is improved by using FWET2.
In addition, T2,t values are
in the range published in the literature.11
Figure 3 shows the only T2-weighted signal averaged over 20 voxels in the inter-hemisphere
space, where fw was
between 0.25 and 0.35. The solid line shows the fitting of Eq. (1). A
monoexponential attenuation function is shown for reference. The signal attenuation is
found to be indeed deviated from the monoexponential behaviour.Conclusions
We have successfully implemented the experimental and data analysis
workflow for the FWET2 method. This allows one to reduce the bias conventional
DTI metrics due to the presence of a water pool with free, isotropic
diffusivity. FWET2 is particularly useful in the regions strongly
affected by PVE.Acknowledgements
No acknowledgement found.References
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