Jonathan Cuthbertson1,2, Trong-Kha Truong1,2, Vani Yadav1,2, Fraser Robb3, Allen Song1,2, and Dean Darnell1,2
1Brain Imaging and Analysis Center, Duke University, Durham, NC, United States, 2Medical Physics Graduate Program, Duke University, Durham, NC, United States, 3GE Healthcare Inc., Aurora, OH, United States
Synopsis
The integrated
RF/wireless coil design enables MRI imaging and wireless data transfer with the
same coil thereby reducing the number of wired connections in the scanner. Here,
we implement this design onto a 48-channel head coil array to enable two
independent wireless data streams for two separate applications, specifically,
wireless 1) control of the DC currents used for B0 shimming and 2) respiratory tracking with a respiratory belt. In vivo experiments in
the brain showed that this coil array significantly reduced B0 inhomogeneities (-41%) and EPI distortions while simultaneously streaming
respiratory data from the subject without data loss.
Introduction
In
MRI, data transfer between the scanner subsystems (e.g., RF coils and shim
coils) or peripheral systems (e.g., respiratory and cardiac monitoring) and the
computers outside the scanner room currently requires a network of carefully
routed wired connections, which take up space within the scanner and require
costly RF filters, baluns, and cable traps to preserve data integrity and MR
image quality. To reduce the number of wired connections, a novel integrated
RF/wireless coil design has recently been developed, in which RF currents
at the Larmor frequency (e.g., 127 MHz for 3T scanners) and in a wireless
communication band (e.g., 2.4 GHz for WiFi) can flow on the same coil to enable
simultaneous MR image acquisition and wireless data transfer for different
applications, respectively, without requiring any scanner modifications or
additional antenna systems within the scanner bore1,2.
Previously, this coil design was combined with the integrated
parallel reception, excitation, and shimming (iPRES) coil design3,
in which a DC current can also flow on the same coil to enable wireless
localized B0 shimming1,4. In this iPRES-W coil design, the coil wirelessly receives commands from
outside the scanner room to control an MR-compatible power supply in the
scanner bore, which delivers the DC currents for shimming. In this work, the
integrated RF/wireless design is implemented onto a 48-channel head coil array
to enable two independent wireless data streams for two separate applications,
specifically, wireless 1) control of the DC currents used for B0 shimming and 2) respiratory tracking with a respiratory belt. Methods
First, the 16 anterior
coil elements of the 48-channel head coil array were modified into iPRES coil
elements by adding: inductors to bypass the capacitors; an MR-compatible
battery pack to provide the DC currents for B0 shimming (range: ±2 A, resolution: 4 mA); and
inductive chokes to provide RF-isolation between the coil elements and the
battery pack to maintain a high SNR3. Next, two of the iPRES coil
elements were modified into iPRES-W coil elements by adding 127-MHz and 2.4-GHz
band-stop filters between each of these coil elements and the WiFi
micro-controller or the preamplifier, respectively1, to enable two
wireless single-input single-output data streams (Fig. 1a, orange). The
two iPRES-W coil elements were chosen to be spatially orthogonal to provide a high
RF-isolation (S21 ~ -35 dB) between them, which reduces coupling and
increases the amount of power radiated from each coil element in the WiFi
frequency band (Fig. 1b).
One of the iPRES-W coil
elements (Fig. 1a, coil 1) was used to wirelessly control the DC
currents for B0 shimming. In this work, 8 of the iPRES coil elements
were connected to the battery pack and used for shimming (Fig. 1a,
blue). The optimal DC currents to shim a slice were determined by minimizing the
root-mean-square error (RMSE) between a combination of basis B0 maps
acquired on a phantom3 with 1 A separately applied in each iPRES
coil element and a B0 map acquired in the brain of a healthy
volunteer. The commands to control the DC currents were then wirelessly transmitted from
outside the scanner room to the WiFi micro-controller of the iPRES-W coil
element via an access point (AP) placed on the scanner room wall. B0 maps and spin-echo EPI images (2 x 2 mm resolution) were acquired on a 3T scanner with and
without DC currents to assess the B0 shimming performance.
The other iPRES-W coil
element (Fig. 1a, coil 13) was used to perform real-time wireless
respiratory tracking during MR image acquisition and shimming. The signal from
a force-sensitive respiratory belt placed around the subject’s abdomen (Fig.
1a, magenta) was wirelessly transmitted from the iPRES-W coil element to
the AP, then recorded on a computer outside the scanner room. Results
The iPRES-W coil element
modifications did not significantly impact the SNR with or without wireless
transmission of the respiratory data (Fig. 2). Wireless shimming
significantly reduced the B0 field inhomogeneity (-41%) and the
geometric distortions in the spin-echo EPI images (Fig. 3, green arrows). The B0 shimming performance can be further improved by implementing iPRES into all
coil elements. Additionally, the wirelessly transmitted respiratory signal was similar
with or without simultaneous MR image acquisition and wireless localized B0 shimming (Fig. 4). Discussion and Conclusion
These results
demonstrate that the dual-stream iPRES-W head coil array can perform
simultaneous image acquisition and wireless data transfer for multiple
applications, specifically, for wireless localized B0 shimming and
respiratory tracking. In future applications, the respiratory signal can be
used to perform dynamic shimming with the iPRES coil elements and correct for
respiration-induced B0 variations, which has previously been done
using wired rather than wireless connections5. In addition, the
integrated RF/wireless coil design can be used for wireless data transfer in
other applications, such as cardiac monitoring or field monitoring with NMR
probes. Acknowledgements
This work was in part supported by GE Healthcare, grants R21 EB024121,
R01 NS075017, R01 EB028644, and S10 OD021480 from the National Institutes of
Health, and the Duke-Coulter Translational Partnership.
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