Yuki Kanazawa1, Masafumi Harada1, Mitsuharu Miyoshi2, Takashi Abe1, Yuki Matsumoto1, and Yasushi Takagi3
1Tokushima University, Tokushima, Japan, 2Global MR Applications and Workflow, GE Healthcare Japan, Hino, Japan, 3Department of Neurosurgery, Tokushima University, Tokushima, Japan
Synopsis
To achieve
detailed characterization of brain tumors, we demonstrated CEST imaging with multi-pool model [bulk water, magnetization
transfer (MT), amide proton transfer (APT), and nuclear Overhauser effect (NOE)]
derive from the Bloch equation. This study was performed using five patients
with brain tumors. As a result, there was high linearity between MTRasym
and T2/T1 in each tumor (R2
= 0.91, P<0.05). Moreover, there were significantly different NOE
signals for tumors and normal white matter (P<0.05). Detection using APT
and NOE make it possible to provide more detailed information of brain tumors
than MTRasym analysis.
Introduction
Chemical exchange transfer (CEST) imaging has been
reported as clinically useful for brain tumor analysis. Amide proton transfer (APT)
imaging has been applied to histological grading, assessment of treatment
effectiveness and/or monitoring of brain tumors at 3 Tesla. On the other hand, the
nuclear Overhauser effect (NOE) signal is generally observed as an oppositional
offset frequency to the CEST signal, of which has been clearly observed with
low B1 power at ultra-high-field MRI.1 Moreover, various CEST
pool models have been developed and demonstrated including APT and NOE. On a 3 Tesla
scanner, because a high B1 setting is used for acquiring adequate
APT contrast, the NOE signal which is on the opposite side of APT would be
challenging of distinguish with MTR asymmetry (MTRasym) analysis. Detecting
a NOE signal in a brain tumor may be useful for histological classification when
compared to APT signals. The purpose in this study was to demonstrate CEST
imaging with multi-pool Bloch equation modeling for different types of brain
tumors.Materials and Methods
This
study was approved by the institutional
review board
and performed using five patients with brain tumors (two glioblastomas, one
lymphoma, and two radiation necrosis). On a
3.0 Tesla MR system (GE Healthcare), CEST imaging was performed with a
single-shot fast spin-echo (SSFSE) sequence and phase cycle radio frequency
(RF) preparation; the frequency offset range was from -7 to +7 ppm at intervals
of 0.5 ppm. The mean B1
values of the MT pulses with 1.5 sec RF duration were set at 0.5, 1.0 µT; then,
0.5 µT B1 was used for B0
correction. The other imaging parameters were echo time, 27.1 ms; repetition
time, 9588 ms; bandwidth, 488 Hz/pixel; field of view, 22 cm; matrix size, 128
× 128; slice thickness, 8 mm. Slice positions were set at center of tumor for a
maximum of three slices. Acquired imaging data had motion correction applied to
each pixel. Post processing of CEST imaging was performed using the multi-pool model Bloch equation; T2/T1
as bulk water, magnetization transfer (MT), amide proton transfer (APT), and
nuclear Overhauser effect (NOE). Each parameter estimation of the multi-pool
model Bloch equation was as follows;
$$\frac{dm}{dt}=A\cdot{m}+R_{1}{m_{0}}=0\left(Eq.1\right) $$
$$m=-A^{-1}R_{1}m_{0}\left(Eq.2\right)$$
where, A is the matrix representation
including parameters of MT, APT, and NOE, m0 is thermal equilibrium including bulk water. m is a steady state signal, which includes
measured Z-spectrum. R1 is relaxation rate, which was fixed in this fitting. Each parameter was calculated
from Z and CEST peak extraction (CPE) spectrum fitting,2 this minimized the
error between measured and calculated Z-spectrum. Then APT and NOE
concentration map were generated. Regions of interest (ROIs) within the tumors
and contralateral white matter (WM) were manually delineated in CEST images to
be used as a comparison of each of the tumors.Results and Discussions
Table 1 shows the histological diagnoses of brain
tumors and estimated parameters derived from CEST for each patient. Figure 1
shows the relationship of each estimated parameter of each tumor and bilateral
normal WM. Mean values for MTRasym at 3-4 ppm, APT3.5 ppm,
NOE3.5 ppm, T2/T1, and MT of
brain tumors were 0.008 ± 0.017, 7.91 ± 5.42 (×10-4),
5.24 ± 3.32 (×10-4), 0.08 ± 0.43, and 0.19 ± 0.85, respectively.
Mean values for each parameters of normal WM tissue were -0.009 ± 0.018, 7.00 ±
4.44 (×10-4), 0.12 ± 3.27 (×10-4), 0.06 ± 0.11, and 0.53 ± 0.12, respectively.
Figure 2 shows the relationship between mean MTRasym at 3-4 ppm and
estimated CEST parameters derived from the multi-pool Bloch equation model of
each brain tumor. Figures 3 and 4 show each image and Z-spectrum of each
patient with brain tumors. In the glioblastomas case (patient No. 2), we observed high MTRasym_3-4
ppm and APT3.5 ppm, and low NOE3.5 ppm signal areas
(Fig. 3). In the other glioblastomas case (patient No. 4), we observed negative value
of MTRasym_3-4 ppm and a higher NOE3.5 ppm signal than that
found in the other tumors (Fig. 2b&4). Because NOE
signal was significantly different between tumors and normal white matter, MTRasym
was affected by NOE. In the future, we must research what the biomechanism
is that causes the NOE signal in a brain tumor or normal brain tissue.Conclusion
Distinguishing APT to NOE signal may lead to more
detailed characteristics of metabolism in brain tumors than that of MTRasym
analysis. Acknowledgements
No acknowledgement found.References
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APT-weighted and NOE-weighted image contrasts in glioma with different RF
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