Navid Pourramzangandji1, Christopher Sica2, Byeong-Yeul Lee3, Hannes Wiesner3, Maryam Sarkarat4, Michael Lanagan4, Xiao-Hong Zhu3, Wei Chen3, and Qing Yang1
1Department of Neurosurgery, PennState University College of Medicine, Hershey, PA, United States, 2Department of Radiology, PennState University College of Medicine, Hershey, PA, United States, 3CMRR, Department of Radiology, University of Minnesota, Minneapolis, MN, United States, 4Department of Engineering Science and Mechanics, Pennsylvania State University, State College, PA, United States
Synopsis
We
investigated the effect of ultrahigh dielectric constant (uHDC) materials on
reducing the noise and enhancing B1 efficiency at 78-MHz for low-γ nuclear applications (23Na and 13C at 7T or 61-MHz for 17O
at 10.5 T). By employing uHDC materials, the conservative E-field can be
reduced in the sample, which makes the non-conservative field dominant and
increases the transmit efficiency and receive sensitivity. We calculated the
normalized noise level and extracted the B1+ efficiency map for baseline (no uHDC)
and when uHDC is used, and show experimentally that noise level is reduced
considerably in the presence of the UHDC material.
Introduction
It
was shown previously that RF B1 field can be enhanced several folds in the sample
by induced strong displacement current in high dielectric constant (uHDC)
materials next to the sample 1, 2. The displacement current in uHDC materials
is produced by non-conservative E field by the coil. However, the E field by
the RF coils in the sample consists of both conservative and non-conservative
components (Eq. 1), both of which produce losses and generate noises in a
conductive sample 3.
$$\overrightarrow{E}=\overrightarrow{E}_{Conservative}+\overrightarrow{E}_{Non-Conservative}=-\overrightarrow{\triangledown\phi}-j\omega\overrightarrow{A} (1)$$
where φ is the electric scalar potential, is the vector
potential, and ω is the
angular frequency. Since one
of the properties of UHDC material is partial shielding the conservative E-field,
in this investigation, we studied the effect of suppression of noise level by
the uHDC materials via shielding the conservative E-field at 78 MHz (23Na
and 13C at 7T or 61 MHz for 17O at 10.5T). We demonstrate
that this de-noising effect of HDC material could synergistically enhance the
SNR further by the induced displacement current in the material.Methods
Simulation setup: We performed the simulation in CST
Microwave Studio as a full-wave simulation software. The setup (Fig.1) includes
a 15 cm diameter coil shaped from a copper wire, a cylindrical uHDC disk, and a
cylindrical water phantom placed on top of the uHDC disk. The thickness and
diameter of the uHDC disk is chosen as 2.1 cm and 8 cm, respectively. The water
phantom is filled within a container with the diameter of 9 cm and height of 11
cm. The phantom has the relative permittivity εr=80 and conductivity of σ=1.5
S/m. The coil diameter is chosen 15 cm so that the tuning and matching of the
coil at the desired frequency (78.6 and 61 MHz) is easier. To perform our
investigation, we studied the field at employing high relative permittivity
values of the HDC material at εr = 6000, and compared the noise level
and the B1+ efficiency.
Electric field map: has been extracted and compared for
the 1) coil only (without uHDC disk and phantom), 2) coil and phantom in the coil
center (baseline), and 3) the coil with phantom in the center on top of the HDC
disk.
SNR gain and Noise Level (NL): The SNR is calculated from the
signal produced by the coil over the noise level calculated from Roemer et al. 3, which can also be presented as the dissipated power within the phantom. In
this work we calculated the normalized noise level (NNL) over the average value
of the B1 field within the phantom (Eq. 2).
$$ NNL=\sqrt{\frac{\int_{}^{}\sigma|E|^{2}dv }{avg(|B_{1}^+|^{2})}} (2)$$
where
σ is the conductivity of the phantom, and E is the electric field. The
integration is performed in the whole volume of the phantom.
B1+ Efficiency: The B1 field is decomposed into two
counter rotating fields in the transvers plane, B1+ and B1-. Then the efficiency
is calculated by dividing the B1+ over the square root of the dissipated power
within the phantom. Results and Discussion
The vector plots in Fig.2a shows that the E-field
in the sample region for coil-only case consists of a set of parallel lines indicating
a conservative field. In the presence of
the phantom (Fig. 2b) the E-field vectors in the phantom follow circular lines,
indicating the field is dominantly non-conservative, while outside the sample E-field
is dominantly conservative. The conservative E-field is produced by the surface
charges of the coil and phantom. The E-field intensity is also decreased within
the phantom. However, in the presence of the uHDC disk we see the non-conservative
E-field is enhanced, which in turn, creates displacement current and induces a much
stronger B1 field in the sample. The line plot in Fig.2d shows the conservative
field is reduced by the uHDC disk, which leads to a significant reduction of the
noise level. Figure 3a shows the calculated and experimental normalized noise
level, the noise level is reduced by approximately 50% with the uHDC disk of
that of baseline. Figure 3b shows the experimental results of 17O
MRSI noise levels between baseline and in the presence of the uHDC disk. This denoising
effect which were achieved through a reduction of the conservative E-field
contribution by the uHDC disk. Figure 4 also shows the B1+ efficiency maps
without and with uHDC disk. As we see, the B1 efficiency is enhanced
substantially by using the uHDC disk. Conclusion
With computer modeling and experimental
measurements under an identical setup, we demonstrated that, in addition to B1
field enhancement by the induced displacement current, the uHDC material can
also shield the conservative E-field in the sample. This property leads to a
prominent denoising effect. This effect
can immediately benefit imaging of 23Na and 13C at 7T and 17O at 10.5T.Acknowledgements
This
work was supported in part by NIH grants of U01 EB026978, R24 MH106049, R01
CA240953, S10 RR026783 and P41 EB027061. References
[1] Yang, Q.X. et al., JMRI, 2013. 38(2).
[2]
Rupprecht, S., et al., Magnetic Resonance in Medicine, 2017. 79(5).
[3] Roemer,
P. B., et al., Magnetic Resonance in Medicine, 1990, 16(2)