Hwapyeong Cho1 and Hyung Joon Cho1
1Ulsan National Institute of Science and Technology, Ulsan, Korea, Republic of
Synopsis
Keywords: Data Analysis, Relaxometry, Myelin, Magnetic field perturbation
In
this study, the effects of myelin structures such as myelin volume fraction
(MVF) and myelin sheath thickness (MST) were investigated by measuring the intra/extracellular
water signals in post-mortem aging rat brains.
R2 values
calculated by intra/extracellular water signals obtained using Carr-Purcell-Meiboom-Gill
(CPMG) sequence are theoretically verified by comparison with transmission
electron microscopy (TEM) and simulation results. It was confirmed that MVF
affects the increase of
R2 and MST affects the decrease of
R2,
and the analysis of
R2
through this relationship was statistically significant. These results suggest
that effects of myelin structures may affect CPMG-based intra/extracellular
water signals.
Introduction
Myelin water imaging (MWI), known as a
representative technique in the myelin MRI field, evaluates myelin content by
capturing the signal of water within the myelin based on a multi-echo technique
: Carr-Purcell-Meiboom-Gill (CPMG) sequence.1–4 However, it is
difficult to detect myelin water signal because it is treated as a short-T2
component (10–40 ms in human).5 In addition, studies analyzing the influence
of myelin structures such as myelin volume fraction (MVF) and myelin sheath
thickness (MST) via intra/extracellular water signals has rarely been investigated.
Therefore, the main objective is to analyze the effects of structural
information of myelin on the intra/extracellular water signals of the CPMG
sequence.Methods
Three
age groups of female Sprague Dawley rats were used : young (6-week-old, n =
3), adult (4-month-old, n = 3), and old (20-month-old, n = 3).
The brains were extracted and fixed in formalin. MRI data were acquired on a 7T
MRI scanner using multi-slice multi-echo sequence with matrix size = 256×256,
field of view = 25×25
mm2, repetition time (TR) = 4000 ms, and echo time (TE) = 8–384 ms (echo
spacing = 8 ms). Voxel-wise R2 values were estimated in two
ways, mono- and bi-exponential functions, to ensure whether myelin water signals
were detected (mono-exponential fitting result : R2,
bi-exponential fitting results : R2,1 and R2,2).
The corpus callosum (CC) was selected as the region of interest in this study.
After
MRI experiments, CC regions from each brain were extracted and imaged on a transmission electron microscopy (TEM).
3–7 TEM images were collected per sample, and a total of 42 TEM images were
used for analysis. TEM images were manually segmented and the MVF value of each segmented
image was calculated as the ratio of myelin area to total area. Mean MST value
of each segmented image was calculated by the sphere fitting method using
ImageJ.6,7
The internal gradient produced by field
perturbation is known to affect the calculated R2 using CPMG
sequence.8,9 Thus, TEM-based field perturbation simulations were
performed to examine the effects of intra/extracellular water signal on myelin
structures. Field perturbation maps were simulated for each TEM image, considering
the isotropic and anisotropic magnetic susceptibilities of myelin (isotropic
component χi = - 0.13 ppm, anisotropic component χa = - 0.15
ppm).10–12 Then, the internal gradient strength g of each field
perturbation map was calculated as "g = sqrt(Gx2
+ Gy2)" by Gx and Gy,
the differences between adjacent pixels in each x and y direction.
When calculating the mean internal gradient strength values in each TEM image,
only pixels in the intra/extracellular space were counted.Results
A
summary of MRI and fitting results for each age group is shown in Figure 1. In
the mono-exponential fitted R2 maps, it was confirmed that
the age-related change was clear in CC region (Figures 1A and 1B). In addition,
it was confirmed that short-T2 components caused by myelin
water signal were not detected because R2,1 and R2,2
were equal to R2 (Figure 1C). Therefore, in this experiment, R2
values were affected by intra/extracellular water signals.
A
schematic diagram of the analyzes using TEM is shown in Figure 2. First, the
TEM images for each sample are segmented and used for MVF and MST calculations
(Figure 2A). In the early developmental stage (6-week to 4-month), MVF
increased with age, while MST showed little change (Figure 2B). For
verification, field perturbation simulation was performed on each segmented
image, and the effects of myelin are confirmed by measuring the internal
gradient strength of the field perturbation map (Figure 2C).
Summarized
MRI, TEM and simulation results are shown in Figure 3. In the early
developmental stage, R2 and internal gradient strength values
increased with increasing MVF (Figures 3A and 3C), whereas MST remained almost
unchanged (Figures 3B and 3D). In the aging stage (4-month to 20-month), the
rates of change in R2 and internal gradient strength values
appear to become slower, most likely due to increasing MST during the
corresponding period (Figures 3A–3D). Based on the assumptions that increasing
MVF affects R2 increase and increasing MST affects R2
decrease, the R2 values for the MVF and MST were empirically
modeled as “R2 = α×MVF - β×MST + R2,0”,
where α, β, and R2,0
are constants. Consequently, a strong correlation (Pearson’s correlation
coefficient r = - 0.8882) between “R2 - α×MVF” (α = 57.9771)
and “- β×MST + R2,0”
(β = 73.4970, R2,0
= 32.9837 [s-1]) was observed as shown in Figure 3E.Discussion and conclusion
We
confirmed that the changes in MVF and MST according to age were different
through TEM analysis, and we wanted to investigate how these changes affect
CPMG-based R2
(Figure 2). Both MRI and simulation results
showed that the effects of MVF and MST on R2 were opposite to
each other (Figure 3). Through these trends, we hypothesized
that R2 can be expressed as a relational expression for MVF
and MST, and confirmed that there is a significant correlation between these
relations (Figure 3E). Although it is a simple relational expression that does
not consider parts that may affect R2 such as chemical fixation
and iron concentration,13,14 it empirically suggests that the effect
of myelin structures can be seen through CPMG-based intra/extracellular water
signals.Acknowledgements
This work was partially supported by
grants from the National Research Foundation of Korea of the Korean government
(Nos. 2018M3C7A1056887 and 2022R1A2C2011191). This research was supported by
the 2021 Joint Research Project of the Institute of Science and Technology and
was also supported by a grant from the Korea Healthcare Technology R&D Project
through the Korea Health Industry Development Institute (KHIDI) funded by the Ministry
of Health & Welfare, Republic of Korea (grant No: HI14C1135).References
1. Carr
HY, Purcell EM. Effects of diffusion on free precession in nuclear magnetic resonance
experiments. Physical review. 1954;94(3):630.
2. Meiboom
S, Gill D. Modified spin‐echo method for measuring nuclear relaxation times.
Review of scientific instruments. 1958;29(8):688-691.
3. Mackay
A, Whittall K, Adler J, Li D, Paty D, Graeb D. In vivo visualization of myelin water
in brain by magnetic resonance. Magnetic resonance in medicine.
1994;31(6):673-677.
4. Heath
F, Hurley SA, Johansen‐Berg H, Sampaio‐Baptista C. Advances in noninvasive myelin
imaging. Developmental neurobiology. 2018;78(2):136-151.
5. MacKay
AL, Laule C. Magnetic resonance of myelin water: an in vivo marker for myelin.
Brain Plasticity. 2016;2(1):71-91.
6. Abràmoff
MD, Magalhães PJ, Ram SJ. Image processing with ImageJ. Biophotonics
international. 2004;11(7):36-42.
7. Dougherty
R, Kunzelmann K-H. Computing local thickness of 3D structures with ImageJ.
Microscopy and Microanalysis. 2007;13(S02):1678-1679.
8. Kleinberg
RL, Horsfield MA. Transverse relaxation processes in porous sedimentary rock.
Journal of Magnetic Resonance (1969). 1990;88(1):9-19.
9. Ronczka
M, Müller-Petke M. Optimization of CPMG sequences to measure NMR transverse
relaxation time T2 in borehole applications. Geoscientific Instrumentation,
Methods and Data Systems. 2012;1(2):197-208.
10. Wharton
S, Bowtell R. Fiber orientation-dependent white matter contrast in gradient echo
MRI. Proceedings of the National Academy of Sciences. 2012;109(45):18559-18564.
11. Sati P,
van Gelderen P, Silva AC, et al. Micro-compartment specific T2⁎ relaxation in the
brain. Neuroimage. 2013;77:268-278.
12. Li W,
Liu C, Duong TQ, van Zijl PC, Li X. Susceptibility tensor imaging (STI) of the brain.
NMR in Biomedicine. 2017;30(4):e3540.
13. Birkl
C, Langkammer C, Golob‐Schwarzl N, et al. Effects of formalin fixation and
temperature on MR relaxation times in the human brain. NMR in Biomedicine. 2016;29(4):458-465.
14. Langkammer
C, Krebs N, Goessler W, et al. Quantitative MR imaging of brain iron: a postmortem
validation study. Radiology. 2010;257(2):455-462.