Edwin Versteeg1, Tijl Van der Velden1, Jeroen Hendrikse1, Dennis Klomp1, and Jeroen Siero1,2
1Radiology, University Medical Center Utrecht, Utrecht, Netherlands, 2Spinoza Centre for Neuroimaging Amsterdam, Amsterdam, Netherlands
Synopsis
A silent gradient axis driven at 20 kHz can be used to
decrease acoustic noise and increase patient comfort in MR-exams. However, the
speed of this silent acquisition is determined by the amount of data needed for
artifact free reconstructions. In this work, we present a framework for
increasing the time efficiency while maintaining image quality of silent
imaging with a silent gradient axis. We show that, by using a generalized
conjugate gradient SENSE reconstruction, a 2-3-fold decrease in scan time is feasible
both on a phantom and in-vivo.
Introduction
Acoustic noise during an MR-exam can lead to substantial
discomfort in subjects and pose a potential health risk due the high sound
pressure levels reached (>100dB) during gradient intensive sequences. Previously,
we presented a method for imaging with a silent gradient axis driven at 20
kHz, which featured no peripheral nerve stimulation and was inaudible to the
human hearing.1 A segmented
readout scheme was used to fill k-space in a number of readout lanes. However,
as a gridding based reconstruction was performed, extra readout lanes were needed
to limit aliasing artefacts by oversampling where two readout lanes meet.
In this work, we present an alternate sampling scheme and reconstruction
framework to be much more time efficient by undersampling the data and using a
generalized conjugate gradient (CG) SENSE algorithm for reconstruction.Methods
The silent mode was achieved by driving a lightweight
single-axis (z-direction) gradient insert (Futura
Composites) with an 18-kW audio amplifier that produces 31.5 mT/m at 20.2
kHz. Imaging experiments were performed both in a phantom and in-vivo on a 7T
MR-scanner (Philips Healthcare) by using the gradient insert with an integrated
birdcage coil for transmit and a 32-channel receive coil (Nova Medical).
The setup is shown in Figure 1.
We used a 2D gradient echo sequence (Fig 2) with an
in-plane resolution of 1 x 1 mm2, a FOV of 224 x 224 mm2,
a flip angle of 26 degrees, and a TE of 11.7 ms. The TR was limited to a
minimum of 62 ms due to the maximum duty cycle of the audio amplifier. We acquired a reference “fully sampled”
acquisition consisting of 95 readout lanes. Here, each lane overlapped for 50%
with the next lane. The minimum number of lanes needed for a relatively
artefact free image reconstruction was investigated by retrospectively
undersampling this acquisition to yield 46, 31 and 23 readout lanes (Fig 3-4
a-d).
Two
reconstructions were performed: a gridding based non-uniform fast Fourier
transform (NUFFT) with density compensation and a CG-SENSE reconstruction (2). Both
methods required trajectory and density estimation, which were obtained from
field camera measurements (Skope Inc.) and an iterative density estimation
algorithm.3,4 Additionally,
the CG-SENSE reconstruction required coil sensitivity estimates which were
acquired and computed from coil reference scans. We used the absolute
difference between the degrees of undersampling to qualitatively assess the
residual aliasing artefacts present in the CG-SENSE reconstruction. A
quantitative assessment of the reconstruction results was performed by
computing the root-mean-square error (RMSE) of each reconstruction with respect
to the “fully sampled” acquisition. For
the RMSE calculation, we used the magnitude images which were scaled to their
mean value.Results and Discussion
The NUFFT reconstruction only returned an artifact
free reconstruction for the reference full k-space acquisition. Here, a
reduction in the number of readout lanes resulted in a direct increase in aliasing
artefacts (Fig 3-4 e-h). These originate
from the relatively large variations in k-space sampling density in the
direction of the silent gradient axis.
The CG-SENSE reconstruction showed no visible aliasing
artifacts when reconstructing using 46 out of the 95 readout lanes (Fig 3-4
i-j). A further reduction to 31 readout lanes resulted in noticeable but subtle
aliasing artifacts (Fig 3-4 k). Additionally, the decrease in readout lanes
yielded an increase in noise in the images due to the decrease in data points
used for reconstruction (Fig 3-4 m-p). Reducing the number of readout lanes to 23
resulted in visible aliasing artefacts in both the phantom and in-vivo
reconstructions (Fig 3-4 l).
Figure 5 shows the RMSE of each reconstruction. Here,
the CG-SENSE reconstruction showed a lower RSME than the NUFFT reconstruction
for all cases, as the addition of coil sensitivity data allowed for unfolding of the aliasing artifacts. When reducing the number of readout lanes, the RMSE of the
CG-SENSE reconstruction increased due to the presence of more aliasing
artifacts. The largest increase in RMSE (2.7-fold in the phantom and 1.9-fold
in-vivo) was observed when going from 31 to 23 readout lanes.
A fully sampled acquisition for the same image
parameters would acquire 224 k-space lines. In comparison, the 46 readout lanes
for no aliasing artefact would result in an acceleration factor of 224/46 =
4.8. A 224/31 = 7.2-fold acceleration
could be reached when limited aliasing artefacts in the image are permitted. When
expanding the presented framework to 3D-acquisitions a further acceleration is
foreseen by sampling the readout lanes in a CAIPI-like pattern. Conclusion
We have shown that by undersampling and CG-SENSE
reconstruction the efficiency of imaging with a silent gradient axis can be
increased 2-3-fold without noticeable artifacts. Acknowledgements
No acknowledgement found.References
1. Versteeg E, Klomp D, Hendrikse J, Siero J.
Supersonic imaging with a silent gradient axis driven at 20 kHz. In:
Proceedings of the 27th Annual Meeting of ISMRM. ; 2019. p. #4586.
2. Pruessmann KP, Weiger M, Börnert P, Boesiger P.
Advances in sensitivity encoding with arbitrary k -space trajectories. Magn.
Reson. Med. 2001;46:638–651 doi: 10.1002/mrm.1241.
3. Dietrich BE, Brunner DO, Wilm BJ, et al. A field
camera for MR sequence monitoring and system analysis. Magn. Reson. Med.
2016;75:1831–1840 doi: 10.1002/mrm.25770.
4. Zwart NR, Johnson KO, Pipe JG. Efficient sample
density estimation by combining gridding and an optimized kernel. Magn. Reson.
Med. 2012;67:701–710 doi: 10.1002/mrm.23041.