BAOSONG WU1, Charles Rogers III1, Sajad Hosseinnezhadian1, Yonghyun Ha1, Kartiga Selvaganesan1, Gigi Galiana1, and R. Todd Constable1
1Department of Radiology and Biomedical Imaging, Yale University, NEW HAVEN, CT, United States
Synopsis
This
work describes methods and systems to implement Bloch-Siegert(BS) spatial
encoding using simultaneous transmit and receive in low-field MRI. The key
challenge is to reduce coupling power in receiver chains so that the
on-resonance signal can be acquired during the off-resonance irradiation. The
developments include combining filters and coil decoupling methods. Together
these methods suppress irradiation leakage more than 60dB which, for an
anticipated offset B1 field of 60 dBm, allows for spatial encoding in low-field MRI
device.
Introduction
Recently,
there has been interest in low-field MRI devices for applications in
point-of-care diagnostics1. Our group is developing an approach
that combines a ramp-able and nonuniform electromagnet for polarization and
slice selection, as well as RF encoding to replace gradients for in-plane
encoding2. This not only
eliminates the need for additional gradient amplifiers but also provides silent
scanning and elimination of claustrophobia associated with cylindrical magnet
geometries.
Single point BS encoding3, as a
novel RF encoding technique, was developed by Kartäusch for RF fields that generate
linear phase modulation. Our group2,4 has been working on BS
encoding for arbitrary nonlinear RF fields using an array of coils that would
simultaneously irradiate off-resonance and detect signal on-resonance. This
approach corresponds to using BS RF pulses like readout gradients, which would increase
the time efficiency by orders of magnitude.
However, to avoid saturating the preamplifier due to large coupling
power on receive channels, special hardware for this NMR/MRI device must be
developed. In this work, filters and coil decoupling methods are combined to
address this problem and make such a system feasible.Methods
The open
MRI system (Figure 1) was built, including electromagnet, a copper shield layer,
a volume coil and a 3x3 array coil. For spatial encoding that uses BS
shift, a subset of coils in the array generate encoding patterns across the
slice by playing off-resonance pulses at 870kHz, while other coils in the array
simultaneously receive signal on resonance at 1MHz.
The coupling parameter S12 between coils is a function
of the irradiation and detection frequencies. In experiments using simultaneous
transmit and receive, the harmonic components in RF pulses increase coupled
voltage on the detection coils when the harmonic components are close to the
detection frequency. To reduce these harmonic components, we have built a low-pass
filter into the transmit chain (Figure 2). Filters were also used in each receive
channel to reduce off-resonance component in signal. Figure 3 is a graph illustrating
S12 results of the high-pass ellipse filter (KR Electronics Inc.) which shows
steep roll-off characteristics around 870kHz, and the insertion loss is around
0.2db at 1MHz.
Filtering
efforts alone, may not sufficiently attenuate off-resonance components in the
receive path. Appropriate decoupling techniques in the array also must be used.
In addition to geometric decoupling, inductive decoupling which is insensitive
to frequency was exploited to build the frequency-switchable array coils (Figure
1 and 2). Coupling is adjusted by inductors for adjacent coils, while small
loops connected by coaxial cables are used to reduce coupling between coils
that do not overlap. These were used to acquire conventional receive signal at Larmor frequency(1MHz) as well as to generate offset fields at 870kHz.Results
Figure
4 shows the mutual coupling achieved when each coil was tuned and matched to 50
Ohm at 1MHz. However, coupling levels are different when coils are switched to
different frequencies. For example, S12 is -40.8 at 1MHz measured by VNA with
transmit power 0dBm when coil #7 and coil #1 are on and off resonance (1MHz and
870kHz), respectively. Measurements were taken using the array coil in Fig.2
and a high-pass filter in Fig.3, and those results are summarized in Fig.5. For
example, when off-resonance pulses at 870kHz, corresponding to 1kW(60dBm), are
applied on coil #7, the coupled power on coil #1 and coil #4 are 6.2dBm and
-0.8dBm, respectively. After running through high-pass filter, the residual powers
are -26.7dBm and -31.3dBm, which is consistent with the reported filter
characteristics in Fig.3. In this way, a low-noise preamplifier(LNA) (Advanced
Research Receiver, P0.5-30/20VD) in the first stage, which has the maximum
input power 2dBm, would not be saturated, making simultaneous transmit/receive
BS spatial encoding possible.Conclusion and Discussion
We
present a design for an MRI device using BS nonlinear spatial encoding. It was
successfully shown that the strategies combining coil decoupling and filters help
to reduce coupling power and remove the off-resonance signal, such that BS
encoding radiation can be applied while detecting the on-resonance signal
simultaneously. This development allows BS
encoding to be applied in the same manner as a readout gradient, thereby
increasing the efficiency of this spatial encoding technique by orders of
magnitude.Acknowledgements
We would
like to thank the help of Terence Nixon and Scott McIntyre.
References
[1]Sarty
G E and Vidarsson L. Magnetic resonance imaging with RF encoding on curved natural slices.
Magnetic resonance imaging. 2018; 46: 47-55.
[2]Constable
R T, et al. Design of a novel class of open MRI devices with nonuniform Bo,
field cycling, and RF spatial encoding. In: ISMRM.;2019. p. 113.
[3]
Kartäusch R, et al. Spatial phase encoding exploiting the Bloch–Siegert shift
effect. Magnetic Resonance Materials in Physics Biology and Medicine. 2014;
27(5): 363-371.
[4] Wu B,
et al. RF encoding using a simultaneous transmit and receive system. In: ENC.; 2019.