Shu Zhang1, Abeer H. Abdelhafez2, Jong Bum Son3, Benjamin C. Musall3, Mitsuharu Miyoshi4, Xinzeng Wang5, Ken-Pin Hwang3, Gaiane M. Rauch2, Jingfei Ma3, and Mark D. Pagel1
1Cancer Systems Imaging, The University of Texas MD Anderson Cancer Center, Houston, TX, United States, 2Abdominal Imaging, The University of Texas MD Anderson Cancer Center, Houston, TX, United States, 3Imaging Physics, The University of Texas MD Anderson Cancer Center, Houston, TX, United States, 4Global MR Applications & Workflow, GE Healthcare Japan, Tokyo, Japan, 5Global MR Applications & Workflow, GE Healthcare, Houston, TX, United States
Synopsis
In our ongoing study of 13 completed patients, we compared two
saturation power levels (2.0 μT vs. 0.9 μT) and two analysis methods (MTRasym
vs. Lorentzian line fitting) of CEST for assessing treatment response to neoadjuvant
chemotherapy of triple-negative breast cancer (TNBC). A consistently decreasing
trend of the CEST signals was observed with the longitudinal treatment when a higher
saturation power of 2.0 μT was used
with the amide MTRasym analysis method. In contrast, the same trend was
observed when a lower saturation power of 0.9 μT was used
for the Lorentzian line fitting analysis method.
Introduction
Chemical exchange saturation transfer (CEST) MRI
is potentially useful for early assessment of treatment response of cancer.1
However, there are several different acquisition and analysis methods that
could impact the quantitative CEST signals. In this study, we investigated e CEST
MRI as an imaging biomarker for early treatment response for triple-negative
breast cancer (TNBC) patients receiving neoadjuvant chemotherapy (NAC) and
compared two saturation power levels and two analysis methods to determine if
they affect the CEST signal changes during the patient treatment.Methods
Our study was approved by the institutional IRB and
all patients provided their written informed consent. In total, 13 patients with
biopsy-proved TNBC were scanned on a 3T GE human
scanner (Discovery MR750) using an 8-channel bilateral breast coil
in a
prone position. The patients were scanned before the NAC (baseline
or BL, N = 13), after 2 cycles of treatment (C2, N = 9), after 4 cycles of
treatment (C4, N = 9), and before surgery (presurgery or PS, N = 6). CEST images
were acquired using a single-shot fast spin echo (SSFSE) sequence with Field of
view Optimized and Constrained Undistorted Single shot (FOCUS). 2 The same
sequence was scanned first with a CEST saturation power of 0.9 μT and a
saturation time of 3500 ms, and then repeated with a CEST saturation power of
2.0 μT and a saturation time of 2000 ms. For both acquisitions, 29
saturation frequencies from -7 to 7 ppm were used in addition to a reference
image without CEST saturation. WASSR was acquired in the same scan series for field
inhomogeneity correction.3 Fat saturation pulses were employed for
fat suppression. Other parameters included FOV = 180 mm × 144 mm, slice
thickness = 8 mm and acquisition matrix size = 128 × 128. For
both low and high saturation power sequences, TR/TE = 6000/33.6 ms and the
total scan time was 4 min 18 sec.
For data acquired at both saturation settings, we
measured the CEST signal using MTRasym averaged between 3.0 – 4.0
ppm (MTRasym3-4) and
Lorentzian line fitting with 2 line shapes that represent water and amide
signals at 3.5 ppm. Only the data from 7 to -1 ppm in the Z-spectrum
were used in order to minimize the influence of residual fat and NOE signals on
the fitting. The magnitude of the fitted amide line was used to represent the
CEST signal (Mag3.5). Tumor
ROIs were drawn manually on the CEST images by an experienced breast
radiologist with reference to the DWI and DCE images. The biopsy marker clip
and necrosis were excluded from the measurement ROIs. The changes of the CEST
signals for each patient during their treatment were monitored and analyzed.Results
The MTRasym maps and their corresponding
Z-spectra and MTRasym are shown for a representative patient from BL
to C4 scans in Figs. 1 and 2, respectively. The Mag3.5 maps and fitted lines for the same patient
are also shown in Figs. 3 and 4. The average results for all patients are shown
in Fig. 5. The Z-spectra were relatively smooth and no obvious fat residual
signals or NOE effects were observed. The low power Z-spectra were nosier than
the high power spectra (Fig. 2). The high power MTRasym3-4 was
higher than that of the low power at baseline and showed a decreasing trend as
the treatment progressed. In comparison, the low power MTRasym3-4 were
similar from BL to C4 (Fig. 2 and 5a). The low power Mag3.5 was higher than
that of the high power at baseline and also showed a decreasing trend from BL
to C4. However, the high power Mag3.5 had similar values from BL to C4 (Fig. 4
and 5b).Discussion
Despite being
potentially useful for monitoring cancer treatment, there is currently
no consensus on the optimal acquisition and analysis methods for CEST imaging. In our study of TNBC during NAC treatment, the
MTRasym in combination with the high saturation power or the
Lorentzian line fitting method in combination with the low saturation power
demonstrated more consistent CEST signal changes. A potential explanation of
our findings may relate to the amide signal strength and lineshape: the amide has
a slow exchange rate and hence is expected to produce higher CEST signal with higher
saturation power. 4 In comparison, lower saturation power produces
narrower CEST peaks which are more amenable to line fitting. Conclusion
Decreasing CEST signals were observed during the NAC treatment of
TNBC. However, signal changes were best observed when MTRasym was
used for data acquired at a high saturation power and when Lorentzian line
fitting was used for data acquired at a low saturation power. Acknowledgements
This
work was supported in part by the Odyssey Program and Cockrell Foundation Award
for Scientific Achievement at The University of Texas MD Anderson Cancer Center
(S.Z.).References
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