Shu Zhang1, Xinzeng Wang2, F. William Schuler1, R. Marc Lebel3, Mitsuharu Miyoshi4, Ersin Bayram2, Elena Vinogradov5, Jason M. Johnson6, Jingfei Ma7, and Mark D. Pagel1
1Cancer Systems Imaging, The University of Texas MD Anderson Cancer Center, Houston, TX, United States, 2Global MR Applications & Workflow, GE Healthcare, Houston, TX, United States, 3Global MR Applications & Workflow, GE Healthcare, Calgary, AB, Canada, 4Global MR Applications & Workflow, GE Healthcare Japan, Tokyo, Japan, 5Radiology, UT Southwestern Medical Center, Dallas, TX, United States, 6Neuroradiology, The University of Texas MD Anderson Cancer Center, Houston, TX, United States, 7Imaging Physics, The University of Texas MD Anderson Cancer Center, Houston, TX, United States
Synopsis
Image
reconstruction using deep learning (DL Recon) is capable of enhancing image signal-to-noise
ratio (SNR) without losing image resolution or altering the image contrast. Our
study demonstrates that CEST imaging and quantification, which are often
limited by SNR and long scan time, can be improved with DL Recon. Our results clearly indicated that DL Recon can be used for CEST imaging with
higher spatial resolution without or with only a mild increase in scan time or
for CEST imaging in reduced scan time by using parallel imaging without the
typical SNR penalty.
Introduction
CEST
imaging is currently limited by low SNR and long scan time.1 Image
reconstruction using deep learning (DL Recon) is capable of enhancing image
signal-to-noise ratio (SNR) without losing image resolution or altering the
image contrast. However, the influences of the deep learning based denoising
methods were not well evaluated in quantitative imaging, especially CEST MRI. The
objective of this study was to investigate if the enhanced SNR from DL Recon
can help CEST imaging with higher spatial resolution without increasing scan
time and if DL Recon enables CEST imaging with parallel imaging without its
typical loss of SNR.Methods
A spherical
phantom (QalibreMD, Inc.) was used to hold five vials of gelatin (Verisol B,
Gelita, Inc.) with different pH values of 6.0, 6.5, 7.0, 7.5 and 8.0, along
with vials of distilled water and vegetable oil. The phantom was scanned on a
3T GE whole body scanner (Discovery MR750) using an 8-channel head coil at room
temperature. The
CEST images were acquired using a single-shot fast spin echo (SSFSE) sequence
with fat saturation.2 A saturation power of 2.0 μT and a saturation
time of 2000 ms were used. 29 saturation frequencies from -7 ppm to 7 ppm in
equal steps were acquired to obtain Z-spectra. A reference image was acquired
without CEST saturation. WASSR was used for field inhomogeneity correction.3
Six sets of CEST images were acquired using a
matrix size of 64, 128, 256, 384, 512 without parallel imaging (ASSET) and 512 with
ASSET = 2. The TR was set to minimum to shorter scan time. It had a range from
2338.8 to 8607.7 ms. TE was set to minimum too, with a range from 27.0 to 35.8
ms. The FOV = 220 mm × 220 mm and slice thickness = 2
mm for all phantom scans. Three glioma patients
were also enrolled and imaged using the same sequence as for the phantoms except
with a matrix size of 256 and a slice thickness of 5 mm. All patient
scans were approved by the institutional IRB and with written informed consents.
MTRasym at 3.5 ppm was measured for
CEST analysis.
In
addition to the standard recon, a vendor supplied DL Recon was used to
reconstruct images using the same CEST raw data. The network was based on a
deep convolutional residual encoder network pre-trained to reduce image noise
without a loss in spatial resolution. Results
Figure 1 compared low resolution CEST images with and
without DL Recon. DL Recon was noted to be crispier and reduced the Gibbs ringing
artifact (Fig. 1a vs. 1d). Because of the high SNR at the low resolution, CEST
signals and local variations appeared to be similar with and without DL Recon (Fig.
1). With lower SNR at high resolution, DL Recon denoised the images (Fig. 2a
vs. 2d) and generated a MTRasym map that had lower noise (Fig. 2b,c
vs. e,f). Due to its high SNR, the DL Recon Z-spectra and MTRasym at
a pixel-level were smoother and had a quality comparable to the ROI averaged
Z-spectra and MTRasym using standard recon (Fig. 2g, h). The MTRasym
maps relative to the matrix size were compared using standard recon and DL
recon (Fig. 3a vs. 3b). As expected, the MTRasym maps from standard recon
became nosier as matrix size increased and with ASSET (Fig. 3a). DL Recon
compensated the SNR loss, and the corresponding high resolution MTRasym
maps from DL Recon images were smoother (Fig. 3b). While the standard deviation
increased with spatial resolution for standard recon, it remained relatively
unchanged for all resolutions for DL recon (Fig. 4). The MTRasym was
noted to increase with matrix size (Fig. 4), possibly due to an increased TR
that allowed more magnetization recovery from saturation. Due to the same
effect, the MTRasym decreased when ASSET was used because TR was
halved with ASSET (Fig. 4 512 vs. 512 with ASSET). For the in vivo images, the
MTRasym map was noted to be substantially less noisy with DL Recon
(Fig. 5).Discussion and conclusion
Our
study demonstrated that DL Recon was applicable to CEST imaging which is
currently limited by SNR and long scan time. With the SNR gain, DL Recon
enabled higher resolution CEST imaging without the increase in scan time, which
can potentially improve voxel-wise analyses or assessments of small ROIs. DL
Recon also enabled CEST imaging with parallel imaging without its typical SNR
loss, which can largely shorten the scan time. In this study, the images were acquired using
FSE sequences, which had higher SNR compared with gradient echo sequences.
Thus, the noise could be more of a problem in gradient echo based sequences, in
which case DL Recon can be very beneficial. These benefits are expected to
improve the CEST quantitation and its performance in clinical applications.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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