Christoph Birkl1,2, Jonathan Doucette1,3, Enedino Hernández-Torres1, and Alexander Rauscher1,3,4
1UBC MRI Research Centre, University of British Columbia, Vancouver, BC, Canada, 2Department of Neurology, Medical University of Graz, Graz, Austria, 3Department of Physics & Astronomy, University of British Columbia, Vancouver, BC, Canada, 4Department of Pediatrics (Division of Neurology), University of British Columbia, Vancouver, BC, Canada
Synopsis
We demonstrated that the measurement of MWF is
considerably influenced by the angle between the white matter fiber tracts and
the main magnetic field. Furthermore, we showed that the traditionally used
cut-off between myelin water and intra- and extracellular water of 40 ms
overestimates MWF.
Introduction
The human brain’s white
matter is an highly anisotropic structure, where the orientation of white
matter fibers in respect to the main magnetic field B0 affects the magnitude
and phase of the complex MRI signal. In general, all MRI techniques which
attempt to quantify physiological and pathological white matter have to deal
with the white matter's anisotropy. Orientation
effects have been reported for a wide range of quantitative MRI parameters such
as, R2* relaxation1–5, gradient echo phase2, T1
relaxation6,7, and dynamic
susceptibility contrast perfusion measurements conducted with both gradient
echo8 and spin echo scans9. The orientation
dependency of the gradient echo signal of white matter is extensively studied
and ascribed to the anisotropy of the magnetic susceptibility caused by the
myelinated nerve fibers. However, the observation that the spin echo signal
also depends on the fiber orientation suggests that MWI is potentially affected
as well. Therefore, we investigate whether and to what degree the MWF depends
on the angle between the white matter tracts and the main magnetic field B0.Methods
We acquired 3D T1, DTI
and MWI using a gradient and spin echo (GRASE) sequence and the standard
Carr-Purcell-Meiboom-Gill (CPMG) sequence. Eight healthy volunteers (3 female,
5 male) with a mean age of 26 years (age
range = 21 – 33 years) and without history of any neurological disorder
participated in this study. MR imaging was performed on a 3T Philips Ingenia
Elition MR system using a 32-channel head coil. The CPMG sequence was
accelerated with compressed SENSE (CS),
using a CS factor of 7 and all MWI sequences had 48 echoes with the first echo
at TE = 8 ms and ∆TE = 8 ms. DTI analysis was
performed using FSL. For MWI analysis, the T2 distributions were
calculated using a regularized non-negative least squares (NNLS) algorithm with
correction for stimulated echoes and a T2 range of 8 ms to 2.0 s10–13. The multi exponential
signal decay is expressed as a T2 distribution where the myelin water component
is defined as the T2 components
within 8 ms and a cut-off, and the intra- and extracellular water component
as the T2 components above
this cut-off. The T2 cut-off was set to (I) 40 ms, representing the
present standard cut-off and (II) 25 ms, based on inspection of the T2
distribution. The MWF was defined as the ratio of the myelin water T2 components to all T2 components. DTI and MWI data was linearly
registered to the 1 mm MNI152 space14 using FLIRT. The fiber
orientation was calculated from the angle between the 1st
eigenvector to the direction of the main magnetic field2. The MWF, was compared
with the corresponding fiber orientation in each WM voxel.Results
In Figure 1, representative maps of the fiber angle in
respect to B0 and the corresponding MWF maps averaged across seven
volunteers are shown. Overall, the GRASE and CPMG sequence provide comparable
results, but a decrease of the T2 cut-off from 40 ms to
25 ms resulted in an overall decrease of the MWF. The relationship between
the MWF and the WM fibre orientation is shown in Figure 2. In general for both
T2 cut-offs, the MWF decreased with increasing fibre angles up to 50° to 60° where
a minimum is reached. For angles between 0° and 50° both GRASE and CPMG show
the same trend, where as between 50° and 90° fibre orientation, the GRASE
revealed slightly lower MWF values than the CPMG. Changing the T2
cut-off from 40 ms to 25 ms significantly decreased the global WM MWF
by 50 % from 0.096 to 0.064 (p < 0.001) for the GRASE and by
43.3 % from 0.096 to 0.067 (p < 0.001) for the CPMG, respectively.
Furthermore, the orientation dependency seems to be slightly decreased when
using a T2 cut-off of 25 ms as indicated in Figure 2B. T2
showed an increase with increasing fibre angles up to a maximum between 50° and
60° followed by a slight decrease as shown in Figure 3.Discussion and Conclusion
In the present work, we
saw that overall T2 varies by less than 3%, whereas MWF was
approximately 30% lower at angles between 50° and 60° compared to tissue
parallel to B0. All MWF and R2 measurements followed this pattern, with a
minimum near the magic angle of 54.7°. Therefore orientation effects of the
transverse relaxation and MWF might arise from dipole-dipole interaction. The
attenuated recovery of the GRASE based MWF at angles above 54.7° may due
to some R2* weighting of the GRASE sequence, which may lead to an attenuation
of the signal due to field inhomogeneities created by the myelinated axons. The
orientation behaviour of the GRASE was similar to the CPMG with the 40 ms cut-off
but not with the 25 ms cut-off, where large differences in MWF between the two
scans were present at larger angles. Our results indicate that the present standard
cut-off of 40 ms overestimates MWF, as it is located within the left slope of
the intra- and extracellular water peak and therefore interprets some of that
water as myelin water.Acknowledgements
No acknowledgement found.References
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