Gang Chen1,2,3, Riccardo Lattanzi1,2, Daniel Sodickson1,2, and Graham Wiggins1,2
1The Center for Advanced Imaging Innovation and Research (CAI2R), Department of Radiology, New York University School of Medicine, New York, NY, United States, 2The Bernard and Irene Schwartz Center for Biomedical Imaging, Department of Radiology, New York University School of Medicine, New York, NY, United States, 3The Sackler Institute of Graduate Biomedical Science, New York University School of Medicine, New York, NY, United States
Synopsis
Coil designs motivated by the ideal current patterns
corresponding to the Ultimate Intrinsic SNR (UISNR) have been used to
boost central SNR at 3T and 7T. For a cylindrical phantom and a current
distribution defined on a concentric cylindrical surface, the ideal current
pattern for optimal central SNR includes both divergence-free and curl-free
components. While loops are exclusively divergence-free, recent work has shown
that electric dipole antennae include both divergence-free and curl-free current
components. Here we explore in simulation whether arrays with an increasing
number of electric dipole antennas can approach UISNR in the center of a head-sized
phantom at 7T, and investigate selected practical design considerations.Introduction
Coil designs motivated by the ideal current patterns
corresponding to the Ultimate Intrinsic SNR (UISNR) have been used to
boost central SNR at 3T and 7T [1-5]. For a cylindrical phantom and a current
distribution defined on a concentric cylindrical surface, the ideal current
pattern for optimal central SNR includes both divergence-free and curl-free
components [6, 7]. At low field, divergence-free current patterns saturate the
UISNR and arrays with an increasing number of loops can approach the UISNR [8-10].
While loops are exclusively divergence-free, recent work has shown that
electric dipole antennae include both divergence-free and curl-free current
components [11,12]. Here we explore in simulation whether arrays with an
increasing number of electric dipole antennas can approach UISNR in the center
of a head-sized phantom at 7T, and investigate selected practical design
considerations.
Methods
FDTD simulations were performed with Microwave
studio (CST, Darmstadt, Germany). Dipole
arrays with various numbers of elements were simulated using 4 mm diameter rods,
placed 10 mm away from a 20 cm diameter cylindrical phantom (εr =
52.5, σ = 0.5642 S/m) [Fig 1(a-e)]. All dipole arrays were limited to a 20 cm
area along the z direction to ensure
a fair comparison between arrays. In the two-row 32-element design, each
element was shortened to 16 cm and nearest neighbors were offset along z, to
reduce coupling and maintain the 20 cm range [Fig 1(d)]. Similar strategies were
applied to the 24- and 48-element arrays with three rows, where each dipole was
shortened to 9cm [Fig 1(c, e)]. All elements were tuned to 297.2 MHz with inductors
close to the feed points.
For comparison, a three-row 48-element loop array
was simulated for an identical phantom [Fig 1(f)]. The width and length of each
loop element was adjusted to achieve geometric decoupling with neighboring coils.
The length was also adjusted to fit three rows into the 20 cm range along the z direction. Three capacitors were
distributed evenly along each element. All elements were tuned to 297.2 MHz.
In practice, the use of inductors to shorten
dipoles introduces extra resistance into the array, particularly for very short
dipoles, which may result in reduced SNR. To model this effect, we repeated the
simulations including a model for the extra resistance (R) of the inductors. We calculated R on the bench using the Q value measured when the inductor was
combined with a capacitor into a resonant LC circuit, such that $$$ R=2 \pi f L/Q $$$.
UISNR values were calculated using a full-wave electrodynamic
simulation tool based on a current mode expansion and dyadic Green’s functions
[6]. Separate UISNR optimizations were repeated including only curl-free, only divergence-free,
and all current modes.
Results
Figure 2 shows optimally combined SNR (i.e., matched
filter combination including noise covariance matrix) for a transverse slice
through the center of the phantom. The 48-element dipole array resulted in the highest
central SNR among the six designs, with 28% higher SNR at the center than the
48-element loop array.
All dipole arrays
were found to exceed the UISNR for either divergence-free components or
curl-free components at the center of the phantom, and the 48-element dipole
array achieved 95% of UISNR for all currents (Figure 3). The 32-element
array is the only 2-row design studied, which may account for its low SNR. When
inductor losses were included in the simulations (Figure 4), the performance of
the 48-element dipole array dropped to 87% of UISNR for all currents. When SNR
was reconstructed using a sum-of-squares combination of the array elements
without incorporation of the noise covariance matrix, due to lower
inter-element coupling the 24-element dipole array outperformed the 48-element
design (Figure 5), achieving 82% of the UISNR for all currents, and still exceeding
the UISNR for divergence-free currents alone.
Discussion
Recent work has shown that the current pattern in an
electric dipole antenna includes both curl-free and divergence-free components.
This is supported by our simulation results showing that the SNR of dipole
arrays can surpass the UISNR for either curl-free or divergence-free currents. We
showed that, theoretically, a dense dipole array with the proper configuration could
closely approach the central UISNR for all-currents, outperforming considerably
any conceivable loop array for head imaging at 7T. However, in practice, inductor
losses and inter-element coupling may limit gains with high element counts.
Future work will include constructing a dense array of dipole antennas to
confirm our predictions that loops are not needed for 7T head imaging.
Acknowledgements
This work was supported by the Center for
Advanced Imaging Innovation and Research (www.cai2r.net),
a NIBIB Biomedical Technology Resource Center (NIH P41 EB017183). References
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