Rock Hadley1, Henrik Odeen2, Robb Merrill2, Sam Adams2, Viola Rieke2, Allison Payne2, and Dennis Parker2
1Radiology and Imaging Sciences, University of Utah, Salt Lake City, UT, United States, 2University of Utah, Salt Lake City, UT, United States
Synopsis
This work evaluates screens with different hole size in
their ability to pass ultrasound and their ability to shield RF in a Transcranial
MR guided Focused Ultrasound experiment.
Hydrophone and radiation force balance studies were used to measure
attenuation and peak pressure when passing ultrasound through the screens
compared to water-only measurements.
Electromagnetic simulations and MRI experiments were performed to
measure RF shielding effectiveness of the screens by comparing their ability to
change known artifacts in a transcranial transducer compared to a solid
conductor.
Introduction
The ground plane of focused ultrasound transducers often distorts
the imaging (B1) RF field. For example, the
RF field patterns in the hemispherical transducer in one commercially available
3 Tesla Transcranial Magnetic Resonance guided Focused Ultrasound (TcMRgFUS) system
(Exablate, Insightec, Isreal), causes an artifactual low signal band of near
the transducer focal point (see Figure 1), reducing temperature measurement accuracy.
We have demonstrated recently that this band can be shifted or eliminated and
the SNR at the ultrasound focus can be greatly increased by applying a screen
that blocks RF magnetic fields while being transparent to the 650-kHz
ultrasound field. Here we study the performance of RF screens of different mesh
sizes for applications where RF energy must be blocked and ultrasound energy
passed. Methods
Screens of different hole sizes
were evaluated with hydrophone and Radiation Force Balance (RFB) testing for
ultrasound attenuation and beam spreading. RF electromagnetic properties were
compared using simulations and verified with MR experiments.
Screens
included a commercial Bronze wire screen with 2-mm hole size and several tinned
copper wire screens that were made in-house with 1-, 2-, 3-, and 4-cm hole sizes,
(see figure 2). All were 30awg wire.
Hydrophone and RFB measurements
were made using a 256-element 14.4x9.8-cm
aperture ultrasound transducer (Image
Guided Therapy, Pessac, France/Imasonic, Voray-sur-l'Ognon, France) with a 10-cm focal length and
operating at 940-kHz. Hydrophone scans
were performed at the focal point plane with screens positioned 4-cm from the
focal spot.
Electromagnetic simulations were
performed using CST Studio Suiteâ
(CST). The Insightec neuro transducer
was modeled as a solid 30-cm diameter semi-spherical conductive ground plane filled
with water. Screens of 24-cm diameter were positioned at 8-cm from the water surface. A 16-rung birdcage coil created a 123-MHz circularly
polarized excitation field. Maximum B1- values were used to analyze
trends in screening effectiveness vs. mesh size with comparison to a simulated
solid copper disk (0.25-mm thick) used as the simulation gold standard.
MR imaging studies were performed to
determine the ability of the screens of different hole sizes to change the
original transducer artifact. Screens
were cut to 24-cm diameter and positioned in an Insightec neuro transducer
oriented in the upward facing preclinical position. The transducer was filled with tap water and
screens were positioned 7.5-cm deep on a plastic support resting on the bottom
of the transducer. Axial and sagittal
GRE images (TR/TE/Flip=123/4/70°)
were acquired for each screen and compared with images using an aluminum disk (gold
standard).
Results
Results for the hydrophone studies (Table
1) show the 2-mm commercial screen had approximately 7% attenuation at 940-kHz
compared to water-only. The screens with
mesh size 2-cm or larger had less than 1% attenuation and were essentially ultrasound
transparent.
RFB data (Table 2) confirms the
hydrophone results showing that 99% of the power is transmitted through a
screen with a hole size of at least 2-cm.
Simulations results, (Figure 3),
demonstrated artifacts that are problematic in 3T imaging with this transducer
geometry and the way these artifacts change with mesh hole size. Rather than eliminate artifacts caused by
this transducer, the goal of this study was to compare RF screening
capabilities of different screens with the solid copper or aluminum disk. These results show that the 1-cm mesh creates
a fairly effective RF screen and provides an imaging result similar to the copper
disk. The screens with larger mesh sizes
progressively let more RF energy through the screen and the original artifact progresses
to its original position as mesh size increases.
The MR imaging results (Figure 4) demonstrate
similar trends as the simulation results. It can be seen that the 2-mm mesh closely
approximates the aluminum disk, however, with a mesh size of 2-cm and larger,
the original artifact begins to return, indicating an increasing
ineffectiveness at RF screening with larger mesh size compared to a solid
conductor.
Discussion
The ultrasound through
transmission and the RF simulation and MRI experiments demonstrate the effects
of a screen mesh size in ultrasound transmission and RF screening in an MRgFUS
environment. In comparing the RF
screening capabilities of the different screens relative to a solid copper or
aluminum disk, these results show that
the 1cm mesh creates a fairly effective RF screen and provides an imaging
result similar to the solid disk. The
screens with larger mesh sizes progressively let more RF energy through the
screen and the original artifact progresses to its original position as mesh
size increases. These results indicate that a mesh size of 2-cm or greater is nearly
transparent to ultrasound at 950kHz and that a mesh size of 1-2-cm or smaller provides
similar RF shielding properties as a solid conductor.
It’s important to note that ultrasound
transmission results are frequency dependent and a smaller hole size may
perform better for ultrasound transparency in a lower frequency transducer.Conclusion
Given the tradeoff between the use
of larger screen mesh for better ultrasound transmission and smaller mesh size
for RF screening, these results indicate that a mesh size on the order of 1-2-cm
may be the best compromise for US transmission and RF screening purposes for
ultrasound at 940-kHz and 3Tesla MRI (123-MHz), respectively.
Acknowledgements
Mark H. Huntsman Endowed Chair at the University of Utah and NIH grant 1R01 EB028316References
No reference found.