Ming Lu1,2, Junzhong Xu1,2, Sandeep S. Arora3, John C. Gore1,2, and Xinqiang Yan1,2
1Vanderbilt University Institute of Imaging Science, Vanderbilt University Medical Center, Nashville, TN, United States, 2Department of Radiology and Radiological Sciences, Vanderbilt University Medical Center, Nashville, TN, United States, 3Department of Radiology and Biomedical Imaging, Yale University School of Medicine, New Haven, CT, United States
1Vanderbilt University Institute of Imaging Science, Vanderbilt University Medical Center, Nashville, TN, United States, 2Department of Radiology and Radiological Sciences, Vanderbilt University Medical Center, Nashville, TN, United States, 3Department of Radiology and Biomedical Imaging, Yale University School of Medicine, New Haven, CT, United States
Based on our
simulation results, the Capacitor-Terminated Coaxial (CTC) coil is the best
candidate for prostate imaging where a wearable, size-optimized, high-density array
is desired.
Figure 4 A
and B: Simulated receive sensitivity (B1-) maps in the central axial
slice of a cuboid phantom (15x30x15 cm3), with one coil set to 1W input
(active) and the other coil terminated with the preamplifier loading (passive).
The B1- distortion due to non-perfect decoupling can be easily observed in the
residual B1- maps calculated by subtracting the baseline B1- of a single coil.
C and D: Plots of normalized B1- values at the 10-cm-deep region (white dotted
circle in Figures 4A and B).
Figure 5 Illustration
of an example of a 29-element high-density over-overlapped coil array focusing
on prostate imaging. A: Planar unfold view. B and C:
Three-dimensional view.
