Sigrun Roat1, Martin Vít2,3, Stefan Wampl1, Albrecht Ingo Schmid1, and Elmar Laistler1
1Center for Medical Physics and Biomedical Engineering, Medical University of Vienna, Vienna, Austria, 2IKEM, Institute for Clinical and Experimental Medicine, Praha, Czech Republic, 3Technical University of Liberec, Liberec, Czech Republic
Synopsis
Cardiac 31P MRS is a powerful noninvasive tool in the
assessment of myocardial energy metabolism, but it is inherently
limited by low SNR, which can be mitigated by increasing B0. In
order to fully exploit the SNR gain, elaborate RF coil development is
necessary. In this work we compare the performance of a standard single loop
coil with an optimized 3-element array in simulation and
measurement.
We validated the superior performance of the array experimentally, with a
2.2-fold SNR increase in localized spectroscopy, and in simulation yielding a
1.7 and 2.2 times higher PE and SE for the array, respectively.
Introduction
Cardiac
phosphorous (31P) magnetic resonance
spectroscopy (MRS) is a powerful noninvasive tool in the assessment of myocardial energy metabolism. Metabolites such as ATP and PCr are readily
detectable in 31P spectra and their relative and absolute
concentrations are strong indicators of cardiac dysfunction with ischemic
events as a major cause. 31P MRS is inherently limited by low SNR, which
can be mitigated by increasing B0. In order to fully exploit the SNR
gain, elaborate RF coil development is necessary due to increased magnetic
field inhomogeneities, RF non-uniformities and power deposition constraints associated
with the increased static magnetic field. In this study we compare the
performance of a commercially available standard single loop 31P
coil with a specifically optimized 3-element 31P array in simulation
and measurement.Methods
3-element coil
implementation: Suitable
RF coil designs for the 31P array were investigated via 3D
electromagnetic simulation in a comprehensive simulation study (1), resulting in a theoretical
superiority of a 3 element array design with an element size of 9.4x14.1 cm2
positioned centered over the heart. To increase electromagnetic coupling
of the RF coil, the 31P array was constructed out of flexible litz
wire (∅=2 mm) and a fixed overlap for
nearest neighbor decoupling. 1H and 31P coil cross talk
is minimized by replacing every second segmenting capacitor by an LCC trap (2), resulting in three traps per
element. Performance of the 31P array was tested on the bench
measuring S-parameters for 5 human volunteers (3m/2f) using a vector network
analyzer (E5071C, Agilent, Santa Clara, CA, USA).
3D electromagnetic
simulation (EMS):
Both RF coils were simulated in XFdtd 7.5. (Remcom, State College, PA, USA). The
single loop has a diameter of 140 mm, according to the vendor’s user manual,
and an assumed wire thickness of 1.5 mm. An RF co-simulation approach was used
to enable fast tuning and matching in ADS (Keysight Technologies, Santa Rosa,
CA, USA) (3) by replacing all lumped elements in
the 3D EMS with 50Ω
voltage sources. Realistic loss estimations for capacitances, and solder joints
were modeled as series resistances. Both RF coils were loaded with two
realistic human body models (“Duke” & “Ella”, Virtual Family, IT’IS Foundation, Zurich, Switzerland). Post-processing of 3D EM data and
co-simulation results was performed in Matlab 2017b (Mathworks, Natick, MA, USA). The simulation
setup of both coils can be seen in Fig. 1.
MR measurements: All MR measurements were conducted
on a 7 T MR scanner (Siemens Magnetom, Erlangen, Germany). The coils were
loaded by a phantom with dimensions of 23x28x38 cm3 containing saline
solution (σ ≈ 0.5 S/m, ε ≈ 80) with 1.57 g/L K2HPO4 and 0.14 g/L KH2PO4.
The RF coils were positioned centrically with respect to the phantom which was
located in the isocenter of the scanner. In this setup 31P images as
well as localized spectra were acquired. 31P imaging sequence: TrueFISP,
TR/TE = 8/4 ms, 4 slices (20mm), 96 avg. 31P spectroscopy sequence:
STEAM, TR/TE = 3000/13.4 ms, TD = 6.9 ms, voxel size 5 x 2 x 5 cm3,
16 avg, voxel location: 7 cm from phantom wall (see Fig. 2). The
voxel was set at this distance to match the
coil-heart distance in reality.Results
Bench measurements show sufficient matching and
isolation between array elements (Sii ≤ -19.9 dB and Sij
≤ -14.9 dB averaged over 5 volunteers). MR
measurements show a 2.2-fold SNR within the voxel of interest (see. Fig. 2) and
an overall higher coverage of the top part of the phantom (see. Fig. 2 top),
when comparing the 3-element array with the single loop. The simulation results
can be seen exemplarily for a transversal slice through the heart for each of
the simulation setups in Figure 3 and are summarized in Table 1. The averaged values over “Duke” and “Ella” for
power efficiency (PE) and SAR efficiency (SE) shows a 1.7 and 2.2 fold higher PE and SE,
respectively, for the 3-element array.Discussion and Conclusion
In
this work we present preliminary results of the implementation of a dedicated
flexible 1H-31P RF coil for cardiac MRS investigations at
7 T. Comparison with a commercially available standard loop coil shows superior
performance of the developed 3-element array in simulation and measurement. The
results shown within this work justifies very well the additional effort that
has to be undertaken when designing and building array coils vs single loops.Acknowledgements
This work was funded by
the Austrian Science
Fund (FWF) grants P28059 and P28867References
1. Goluch-Roat S, Vit M, Schmid AI, Laistler E.
Simulation comparison of 28 different 31P arrays for cardiac MR spectroscopy at
7 T. In: Proceedings of the ISMRM 2019.
2. Meyerspeer M, Roig ES, Gruetter R, Magill AW. An improved trap design for decoupling multinuclear RF
coils. Magn Reson Med 2013;00 doi: 10.1002/mrm.24931.
3.
Kozlov M, Turner R. Fast MRI coil analysis based on 3-D electromagnetic and RF
circuit co-simulation. J Magn Reson 2009;200:147–52 doi:
10.1016/j.jmr.2009.06.005.