Holger Eggers1, Bernhard Schnackenburg2, Marc Kouwenhoven3, Alan Huang3, Tim Leiner4, Rolf Gebker5, and Sebastian Kelle5
1Philips Research, Hamburg, Germany, 2Philips Healthcare, Hamburg, Germany, 3Philips Healthcare, Best, Netherlands, 4Department of Radiology, University Medical Center Utrecht, Utrecht, Netherlands, 5German Heart Institute Berlin, Berlin, Germany
Synopsis
Chemical shift encoding-based
water-fat imaging, or Dixon imaging, has recently been demonstrated to permit first-pass
peripheral MRA without subtraction. While previous work focused on an
evaluation at 1.5 T, this work explores the feasibility of this subtractionless method at 3 T. Results on the first six patients are presented and are compared with the
established subtraction method. Substantial improvements in image quality are seen,
and the use of three stations is, despite particular challenges at 3 T, preliminarily
found to be practicable.Introduction
Currently,
the most widely used approach in first-pass peripheral MRA is the so-called
stepping table subtraction method
1,2. It involves corresponding 3D
acquisitions before and during the initial arterial passage of a contrast agent
to suppress background signal by subtraction, typically at three or four table
positions to cover the vascular tree from the infrarenal aorta down to the
feet. Recently, a subtractionless method was proposed, which relies on fat
suppression to reduce background signal instead
3. It was shown to
offer advantages over the subtraction method in terms of SNR and CNR, robustness
to motion, and scan time, in both theory and practice
3,4. The first
clinical study with this method was performed at 1.5 T
3. The purpose
of this work was to investigate the basic feasibility of subtractionless first-pass
peripheral MRA at 3 T, in particular with three stations only, and to qualitatively
compare image quality with the established subtraction method.
Methods
Six patients were examined on
a 3 T Ingenia scanner (Philips Healthcare, Best, Netherlands). During and
after injection of 10 ml Gadovist (Bayer Healthcare, Berlin, Germany) at 0.5
ml/s, contrast-enhanced images were acquired successively at three table
positions, each with a FOV of 430 x 400-450 x 180-200 mm
3, using a 3D
T
1-weighted spoiled dual-gradient-echo sequence with a TE
1/TE
2/TR
of 1.5-1.6/2.8-2.9/4.4-4.7 ms. The measured spatial resolution increased from
1.3 x 1.3 x 2.8 mm
3 at the first, abdominal station to 1.0 x 1.0 x
1.5 mm
3 at the third, lower leg station. Scan times ranged from 13 s
for the first station to 26 s for the third station, with an 8-fold acceleration
by SENSE and a partial Fourier factor of 0.7. A direct comparison between the
subtraction and the subtractionless method was enabled by additionally
collecting corresponding non-contrast-enhanced images before injection. Moreover,
RF shimming was performed at each station.
Water images were
reconstructed from the contrast-enhanced images using mDIXON with a multi-peak
spectral model of fat
5, and subtraction images were generated from
the first gradient echo images. The comparison between water and subtraction
images was thus made on the basis of equal effective acquisition times. For
visualization, coronal MIPs were calculated for each station and were stitched together
to reach a virtual FOV of 1210 mm in FH direction.
Results
Stitched coronal MIPs obtained
in two selected patients are shown in Figs. 1 and 2. While all stations suffer
from bulk patient motion in the first case, primarily the abdominal station is
affected by inconsistent breathholds in the second case. Resulting misregistration
artifacts reduce the vessel-to-background contrast and even conceal vasculature
in the subtraction images, whereas the subtractionless method effectively
eliminates them. Compared to 1.5 T, the expected higher SNR in the water images
was visually less striking, probably due to the overall better SNR with a
single dose of contrast agent at 3 T. Limitations to the useable FOV due to B
0
inhomogeneity, manifesting as signal drop toward the corners of the rectangular
FOV at each station, were more noticeable at 3 T, but basically concerned subtraction
images and water images alike, as seen in the upper right leg in Fig. 3. Signal
loss in the right femoral artery, previously reported without RF shimming by
others
6, was not observed. Remaining spatial variations of B
1+
only led to minor inhomogeneity in the residual background signal in the water
images, especially in the right musculus tibialis anterior, as also seen in Fig. 3.
Discussion
This work
demonstrates the basic feasibility of subtractionless three-station first-pass peripheral MRA
at 3 T in patients. Compared to the subtraction method, the suppression of
misregistration artifacts induced by bulk patient motion was the most striking improvement.
In view of the considerable number of elderly among the patients examined with
peripheral MRA, this is considered as a significant advance toward reliable, high
image quality. Using four stations allows avoiding most of the mentioned
additional challenges encountered at 3 T, but prolongs the scan time by about
20 s. A virtual FOV of 1210 mm, as reached in this work with three stations, suffices
for most patients and seems attainable with the subtractionless method at 3 T based
on the results obtained so far.
Acknowledgements
No acknowledgement found.References
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