Daniel Wenz1 and Rolf Gruetter1,2,3,4
1Center for Biomedical Imaging - Animal Imaging and Technology (CIBM-AIT), Ecole Polytechnique Fédérale de Lausanne (EPFL), Lausanne, Switzerland, 2Laboratory of Functional and Metabolic Imaging (LIFMET), Ecole Polytechnique Fédérale de Lausanne (EPFL), Lausanne, Switzerland, 3Department of Radiology, University of Lausanne, Lausanne, Switzerland, 4Department of Radiology, University of Geneva, Geneva, Switzerland
Synopsis
Shortening dipole antennas using dielectric materials provides an
opportunity to design very high-channel count dipole arrays which should boost
signal-to-noise ratio and enable higher acceleration factors in parallel MRI at
7.0 Tesla. In this study, we compare different dipole antennas shortened using
D2O. We demonstrate, that the height of the dielectric block becomes
a critical design parameter when there is no direct contact between the block
and the sample and what we know about dielectric block design should be
revisited. Our results indicate, that miniaturizing dipole antennas, and employing them in an 8-channel configuration, is feasible without
significant performance decrease.
Introduction
Dipole antennas (DA) are inevitable to achieve the ultimate intrinsic
signal-to-noise ratio (UISNR) in ultrahigh field (UHF) MRI1. DA
arrays, which are built of high number of channels, can provide higher acceleration
factors in parallel MRI and higher SNR2,3,4,5. For this purpose, the
DA geometry requires some modifications. One of the approaches is to shorten DA
using high-dielectric constant εr medium6,7,8. Unfortunately, the sizes of dielectric blocks
(DB) used in previous investigations were rather large. Those reports have followed
what Raaijmakers et al. have suggested in their landmark paper6,
i.e. that the height of DB should be bigger than ¼ of λ. This condition seems to be
true when there is direct contact between DB and the sample. However, when DB
has a higher dielectric constant εr (e.g. 80), and a small, 5-mm air gap is present between DB and the
sample, the electromagnetic field (EMF) pattern changes substantially and there
is no efficient RF power delivery to the sample. In this study, we investigate transmit
field (B1+) produced by four different DA designs immersed
in heavy water (D2O) by conducting EMF simulations and MR phantom
experiments. We also compare in simulations three types of DA arrays including
one that is comprised of a miniaturized version of one of the elements.Methods
Electromagnetic field (EMF) and specific absorption rate (SAR)
simulations were performed in spherical (diameter=85mm) and cubic phantom (size=300x300x200mm3),
conductivity σ=0.4 S/m, dielectric permittivity εr=80) using Sim4Life (ZMT AG,
Switzerland). Three different single elements were investigated: RA-S, B-T7,
SSAD8. DB dimensions were: RA-S (97.5x47.6x28.6mm3), B-T (155x70x25mm3), SSAD (160x70x50mm3).
RA-S geometry was scaled from 6 according to the higher εr (80 instead of 36). The elements were built of
acrylic glass boxes filled with D2O. Since our goal at this stage
was a qualitative comparison, acrylic glass was not included in our
simulations. Phantom experiments were conducted on a 7.0 Tesla head-only system
(Magnetom, Siemens Healthineers, Erlangen, Germany) and phantom images, which are related to transmit field, were obtained using SA2RAGE imaging technique9. The geometry of
miniaturized B-T (B-T-m) was arbitrarily modified: 105x60x5mm3.
RA-S, SSAD, B-T and B-T-m were used in 8-channel DA arrays that were driven in a
circularly polarized (CP) mode (phase increment/element=45°).Results
Figure 1 shows that B1+ distribution in cubic and
spherical phantom is substantially different between setup A (direct contact,
no air gap) and B (5-mm air gap). In setup B, the magnetic field does not propagate
down towards the sample and is contained within DB. As a result, a dramatic
decrease in B1+ (B1+/√Pin) and SAR
(B1+/√SAR10g) efficiency
is observed (Figure 1 and 2). Phantom measurements are in rough agreement with
simulations (experimental conditions were slightly different). The observed
effect is associated with the height of DB. The resulting EM field was also
related to the phantom's geometry. Only element
B-T (shortest distance between the antenna feed and the bottom of DB) performs
well despite the air gap. In setup A, B1+ efficiency is
not proportional to the DB height, but rather finds its optimum around 12.5 cm
(Figure 3). However, even higher DB (height=22.5cm) can produce efficient B1+.
Scattering parameter matrix (Figure 4) was analyzed for setup A and B (DB
height=20cm). It indicates that such high DB has at least several dielectric
modes in setup B. Miniaturized version of B-T in an 8-channel configuration,
provides higher B1+ efficiency in superficial region and
only 3% lower B1+ efficiency in the center of the phantom
than 8-channel B-T array.Discussion and Conclusion
We showed, that performance of DA, which are shortened using too high
DB, can be completely degraded when a small air gap is present between DB and
the phantom. This effect disappears when the distance between the feed of DA
and the bottom of DB is reduced. Our observations disagree with what was
reported previously, i.e. that the height should be at least ¼ λ. This condition remains
true when there is direct contact between the block and the sample. Direct
contact between DB and the sample leads to smooth EM wave propagation, and an optimal
DB height to maximize B1+ efficiency at given depth can
be found. This is not the case when there is a sufficiently small air gap
between DB and the phantom. We conclude that this effect can be related to a
coupled dielectric mode of DB. This hypothesis is yet to be fully confirmed in future experiments. Our work has important implications for DA design using
dielectric materials especially for brain UHF-MRI. It is rarely the case that
direct contact between DB and volunteer's head can be achieved. We also extended our work,
and showed in simulations, that significant reductions in overall size of DB
are possible without substantial B1+ efficiency decrease
in 8-channel array configuration. This is very promising for high-channel count,
receive-only dipole or loop/dipole arrays. There is a broad range of available,
low loss dielectric materials with higher εr
which could be considered in future DB design optimizations, and their
potential benefits for UHF-MRI should be investigated.Acknowledgements
No acknowledgement found.References
1. Lattanzi R, et al., Approaching ultimate intrinsic signal-to-noise
ratio with loop and dipole antennas. Magn Reson Med. 2018 Mar;79(3):1789-1803.
2. Roemer PB, et al., The NMR phased array. Magn Reson Med. 1990
Nov;16(2):192-225.
3. Sodickson DK, Manning WJ, Simultaneous acquisition of spatial
harmonics (SMASH): fast imaging with radiofrequency coil arrays. Magn Reson
Med. 1997 Oct;38(4):591-603.
4. Pruessmann KP, et al., SENSE: sensitivity encoding for fast MRI. Magn
Reson Med. 1999 Nov;42(5):952-62.
5. Griswold MA, et al., Generalized autocalibrating partially parallel
acquisitions (GRAPPA). Magn Reson Med. 2002 Jun;47(6):1202-10.
6. Raaijmakers AJ, et al., Design of a radiative surface coil array
element at 7 T: the single-side adapted dipole antenna. Magn Reson Med. 2011
Nov;66(5):1488-97.
7. Winter L, et al., Design and evaluation of a hybrid radiofrequency
applicator for magnetic resonance imaging and RF induced hyperthermia:
electromagnetic field simulations up to 14.0 Tesla and proof-of-concept at 7.0
Tesla. PLoS One. 2013 Apr 22;8(4):
8. Sanchez JD, et al., Radiative MRI coil design using parasitic
scatterers: MRI Yagi. IEEE Transactions on Antennas and Propagation, 2018 66(3),
1570-1575.
9. Eggenschwiler F, et al., SA2RAGE: a new sequence for fast B1+
-mapping. Magn Reson Med. 2012 Jun;67(6):1609-19.