Synopsis
Keywords: White Matter, Brain, crossing fibers, biomarker, NuFO, FA
Diffusion MRI-based
biomarkers are commonly used to assess brain microstructural properties.
Mathematical models have been developed to calculate various metrics; each are
sensitive to different tissue features. Here, we investigate whether there are
differences in the number of fiber orientations (NuFO) between male and female
brains and how these results compare to corresponding DTI-derived fractional
anisotropy (FA) findings. Results show NuFO-based differences with high effect
size (>1 Cohen’s D) in hippocampi, which are undetected in FA-tests.
Therefore, NuFO could provide complementary aspects to DTI metrics to capture
differences in microstructural organization.
Introduction
Diffusion
MRI is among the most popular techniques to investigate brain microstructure. Most clinical applications are based on the diffusion
tensor imaging (DTI) model. DTI metrics have been repeatedly shown as sensitive
biomarkers of brain tissue microstructure[1,2].However, in voxels containing
multiple fiber orientations, changes in DTI metrics, e.g. fractional anisotropy
(FA), are not specific, and can originate from changes in any of the underlying
tissue fibers. This conceptual limitation affects a large part of the brain, as
multi-fiber configurations are present in the vast majority of the brain white
matter[3,4]. More recently, methods investigating
fiber orientation distributions (FOD) obtained from spherical deconvolution are
becoming an increasingly popular solution to obtain microstructural metrics
that overcome the limitations of DTI. In this work, we evaluate whether the
number of fiber orientations (NuFO) can provide complementary insights into tissue
microstructure when compared to conventional FA-based results. As an example
study, we opted to evaluate potential differences between female and male brain
microstructure, as such group differences are already established in the
literature serving as a reference[5,6].Methods
Minimally processed dMRI data were collected from the Human Connectome Project (HCP)[7,8]. Briefly, a motion- and distortion corrected dataset consisted of 18
non-DWIs (b-value = 0 s/mm2) and 90 DWIs per shell with b-values
equal to 1000/2000/3000 s/mm2, with a voxel size of 1.25mm isotropic
and a sample size of 408(243 females) participants.
The diffusion tensor was estimated with 9 non-DWIs and 90 DWIs at b=1000
s/mm2 using the weighted linear least squares[9] method.
NuFO[10] was calculated after estimating the
FOD with the Generalized Richardson-Lucy (GRL)[11] spherical deconvolution framework. Corrections for gradient non-linearities were performed both in the DTI
fit and the FOD estimation[12–14].
The signal contributions of white matter (WM), grey matter (GM) and cerebrospinal fluid were
modelled separately. The WM signal was modelled using DTI. The tensor
eigenvalues were derived for each subject by looking at voxels with FA>0.7. The
main orientations of the FODs were derived with a gradient descent method and
then NuFO was determined while discarding FOD peaks below 20% of maximum peak
amplitude. The maximum NuFO was limited to 3.
For the group comparison, we used Permutation Analysis of Linear Models[15–19]. Significance was determined at pcorr<0.05
using family-wise error rate adjustment. Threshold-Free Cluster Enhancement[20] was used to amplify p-values. Total intracranial volumes (TIV) of the
subjects were added as a nuisance regressor. Results
Fig. 1 shows an example
subject from the HCP cohort and the population mean maps for NuFO and FA in MNI
space. In WM, there is a reverse relationship between the two metrics, for
example, in the corpus callosum, a high FA value has a NuFO value of 1. Therefore,
this region has single fiber orientation as shown by the population maps.
However, DTI estimation in areas with divergent fiber populations results in a lower
FA. Deep GM nuclei like the thalamus or caudate also have ~3 NuFO and low FA.
Fig. 2 shows a joint
distribution histogram of voxel-wise NuFO and FA. High FA values (>0.8) only
occur in WM and coincide with a NuFO value of 1. In other WM regions a higher
NuFO corresponds to a lower FA. FA values in GM are generally low (~0.2) and in
a narrow range, while NuFO assumes values between 1 and 3 at the same locations.
In Fig. 3, we examine voxel-wise differences in FA and NuFO between
females and males. Both NuFO- and FA-based comparisons show widespread differences
(left panel). Moreover, the NuFO-based analysis reveals differences in hippocampi
with large effect sizes (Cohen’s D>1), whereas the effect sizes observed for
FA are remarkably lower. Since there is a reverse relationship between NuFO and
FA in WM, as shown in Fig. 2, we compared the effect sizes of ‘Male > Female’
NuFO-tests with ‘Female > Male’ FA-tests. Also, males do not show higher FA
than females and females do not show higher NuFO than males, hence both are not
shown.
Fig. 4 shows the distribution
of effect sizes in voxels where FA or NuFO were significantly different between
males and females. The figure shows separate distributions for voxels in which both
metrics were significantly different (in section A) or only one of the two (in
section B). Fig 4/B shows that the largest amount of differences were observed
for NuFO only (340 cm3 or 18.4% of the MNI brain volume), followed by FA only
(188 cm3 or 10.2%), and both metrics (125 cm3 or 6.7%).Discussion and Conclusion
We investigated
sex-specific differences in the human brain with DTI-based FA and GRL-based
NuFO biomarkers, while adjusting for TIV.
NuFO-based comparisons showed considerably more differences between sexes than
FA. Of the total significant areas, only 19% of the regions show differences
with both metrics, while 52% was showed with NuFO only. NuFO-based tests show
large amount of differences with high effect sizes in the hippocampi. Most
previous research shows similar patterns of higher FA for females, but are
limited to core WM areas[21,22]. NuFO was able to reveal complementary differences
compared to FA-based tests when used to investigate sex-specific differences in
the brain and may offer new insights into the structure of the brain.Acknowledgements
No acknowledgement found.References
[1] Baek SH, Park
J, Kim YH, Seok HY, Oh KW, Kim HJ, et al. Usefulness of diffusion tensor
imaging findings as biomarkers for amyotrophic lateral sclerosis. Sci Rep
2020;10:1–9. doi:10.1038/s41598-020-62049-0.
[2] Andica C, Kamagata K, Hatano T, Saito Y,
Ogaki K, Hattori N, et al. MR Biomarkers of Degenerative Brain Disorders
Derived From Diffusion Imaging. J Magn Reson Imaging 2020;52:1620–36.
doi:10.1002/jmri.27019.
[3] David S, Mesri HY, Guo F, Leemans A, De
Luca A. Diffusion MRI analyses of complex fiber configurations in white matter
and the cortex. Int Soc Magn Reson Med 2020:7045.
[4] Jeurissen B, Leemans A, Tournier JD, Jones
DK, Sijbers J. Investigating the prevalence of complex fiber configurations in
white matter tissue with diffusion magnetic resonance imaging. Hum Brain Mapp
2013;34:2747–66. doi:10.1002/hbm.22099.
[5] Tyan YS, Liao JR, Shen CY, Lin YC, Weng
JC. Gender differences in the structural connectome of the teenage brain
revealed by generalized q-sampling MRI. NeuroImage Clin 2017;15:376–82. doi:10.1016/j.nicl.2017.05.014.
[6] Ingalhalikar M, Smith A, Parker D,
Satterthwaite TD, Elliott MA, Ruparel K, et al. Sex differences in the
structural connectome of the human brain. Proc Natl Acad Sci 2014;111:823–8.
doi:10.1073/pnas.1316909110.
[7] Glasser MF, Sotiropoulos SN, Wilson JA,
Coalson TS, Fischl B, Andersson JL, et al. The minimal preprocessing pipelines
for the Human Connectome Project. Neuroimage 2013;80:105–24.
doi:10.1016/j.neuroimage.2013.04.127.
[8] Van Essen DC, Smith SM, Barch DM, Behrens
TEJ, Yacoub E, Ugurbil K. The WU-Minn Human Connectome Project: An overview.
Neuroimage 2013;80:62–79. doi:10.1016/j.neuroimage.2013.05.041.
[9] Veraart J, Sijbers J, Sunaert S, Leemans
A, Jeurissen B. Weighted linear least squares estimation of diffusion MRI
parameters: Strengths, limitations, and pitfalls. Neuroimage 2013;81:335–46.
doi:10.1016/j.neuroimage.2013.05.028.
[10] Dell’Acqua F, Simmons A, Williams SCRR,
Catani M. Can spherical deconvolution provide more information than fiber
orientations? Hindrance modulated orientational anisotropy, a true-tract
specific index to characterize white matter diffusion. Hum Brain Mapp
2013;34:2464–83. doi:10.1002/hbm.22080.
[11] Guo F, Leemans A, Viergever MA, Dell’Acqua
F, De Luca A. Generalized Richardson-Lucy (GRL) for analyzing multi-shell
diffusion MRI data. Neuroimage 2020;218:116948.
doi:10.1016/j.neuroimage.2020.116948.
[12] Sotiropoulos SN, Jbabdi S, Xu J, Andersson
JL, Moeller S, Auerbach EJ, et al. Advances in diffusion MRI acquisition and
processing in the Human Connectome Project. Neuroimage 2013;80:125–43.
doi:10.1016/j.neuroimage.2013.05.057.
[13] Bammer R, Markl M, Barnett A, Acar B, Alley
MT, Pelc NJ, et al. Analysis and generalized correction of the effect of
spatial gradient field distortions in diffusion-weighted imaging. Magn Reson
Med 2003;50:560–9. doi:10.1002/mrm.10545.
[14] Mesri HY, David S, Viergever MA, Leemans A.
The adverse effect of gradient nonlinearities on diffusion MRI: From voxels to
group studies. Neuroimage 2019:116127. doi:10.1016/j.neuroimage.2019.116127.
[15] Winkler AM, Ridgway GR, Webster MA, Smith
SM, Nichols TE. Permutation inference for the general linear model. Neuroimage
2014;92:381–97. doi:10.1016/j.neuroimage.2014.01.060.
[16] Eklund A, Nichols TE, Knutsson H. Cluster
failure: Why fMRI inferences for spatial extent have inflated false-positive
rates. Proc Natl Acad Sci 2016;113:7900–5. doi:10.1073/pnas.1602413113.
[17] Nichols T, Holmes A. Nonparametric
Permutation Tests for Functional Neuroimaging. Hum Brain Funct Second Ed
2003;25:887–910. doi:10.1016/B978-012264841-0/50048-2.
[18] Holmes AP, Blair RC, Watson JDG, Ford I.
Nonparametric analysis of statistic images from functional mapping experiments.
J Cereb Blood Flow Metab 1996;16:7–22. doi:10.1097/00004647-199601000-00002.
[19] Winkler AM, Ridgway GR, Douaud G, Nichols
TE, Smith SM. Faster permutation inference in brain imaging. Neuroimage
2016;141:502–16. doi:10.1016/j.neuroimage.2016.05.068.
[20] Smith SM, Nichols TE. Threshold-free cluster
enhancement: Addressing problems of smoothing, threshold dependence and
localisation in cluster inference. Neuroimage 2009;44:83–98.
doi:10.1016/j.neuroimage.2008.03.061.
[21] Bava S, Boucquey V, Goldenberg D, Thayer RE,
Ward M, Jacobus J, et al. Sex differences in adolescent white matter
architecture. Brain Res 2011;1375:41–8. doi:10.1016/j.brainres.2010.12.051.
[22] Kanaan RA, Allin M, Picchioni M, Barker GJ,
Daly E, Shergill SS, et al. Gender differences in white matter microstructure.
PLoS One 2012;7. doi:10.1371/journal.pone.0038272.