Disentangling Signal propagation and Noise-related Effects in the Presence of High Permittivity Materials via Ideal Current Patterns
Manushka V. Vaidya1,2,3, Christopher M. Collins1,2,3, Daniel K. Sodickson1,2,3, Giuseppe Carluccio1,2, and Riccardo Lattanzi1,2,3

1Center for Advanced Imaging Innovation and Research (CAI2R), Department of Radiology, New York University School of Medicine, New York, NY, United States, 2Bernard and Irene Schwartz Center for Biomedical Imaging, Department of Radiology, New York University School of Medicine, New York, NY, United States, 3Sackler Institute of Graduate Biomedical Sciences, New York University School of Medicine, New York, NY, United States

Synopsis

There is no single mechanism to describe how high permittivity materials (HPMs) improve signal-to-noise ratio when placed between radiofrequency coils and the object. We separately investigated the effects of HPMs on signal propagation and sample noise by studying ideal current patterns, the corresponding optimal electric (E) field and a signal-only propagation model. Our results suggest that phase changes in the ideal current patterns with HPMs are primarily due to signal-propagation effects while their increase in size is due to reduced E field penetration into the sample, which allows larger current patterns that maximize signal reception with a limited noise penalty.

PURPOSE

Signal-to-noise ratio (SNR) can be improved by placing high permittivity materials (HPM) (εr>80) between a radio-frequency (RF) coil and the object1,2. However, the beneficial effect of HPMs on the relative balance between coil signal and noise sensitivity has not been elucidated. To gain physical insight, our work analyzes the effects of HPMs on ideal current patterns3, corresponding to the ultimate intrinsic SNR (UISNR) at a voxel of interest. Ideal current patterns cover a larger region in the presence of HPMs4, but it is unclear whether this is primarily due to signal propagation effects through the HPM layer, or a consequence of reduced sample noise ($$$\int_{}^{} \sigma E\cdot E^{\star}dv$$$). Our objective is to interpret these findings by studying ideal current patterns, the corresponding optimal electric (E) fields, and a signal-only propagation model.

METHODS

1) Ideal current patterns: An in-house simulation framework based on dyadic Green’s functions (DGF) was used to calculate the ideal current patterns3 corresponding to the UISNR at a voxel 3.4cm from the center of a sphere at 7T (Fig. 1). A mode expansion order of 60 was used to ensure convergence. Calculations were repeated in the presence and absence of a HPM layer surrounding the object with εr = 1000.

2) Signal-only propagation model: A circularly polarized local magnetic field source at the operating frequency (Fig. 1) was modeled to simulate a precessing spin at the voxel of interest using numerical simulation software (CST, 2015). The corresponding tangential E field, which may be associated with a putative detector current pattern well matched to the precessing spin’s field, and hence well suited for efficient signal reception, was calculated on a curved spherical surface (Fig. 1) to investigate the effects of signal propagation through HPMs. Approximately one million mesh cells were used. An accuracy of -50 dB was used to ensure convergence.

3) Optimal E fields: The optimal net E field generated by the ideal current patterns was calculated (Fig.5) and its spatial distribution was investigated to test the hypothesis that reduced E field penetration, and consequently reduced sample noise is associated with larger ideal current patterns.

RESULTS AND DISCUSSION

Size and phase of the ideal current patterns changed depending on the thickness of the HPM layer (Fig. 2). This suggests that the SNR-optimal diameter of a surface coil changes in the presence of HPMs. The tangential E field in the signal model exhibited a different phase delay depending on the HPM thickness (Fig. 3), but there was no appreciable change in size (Fig 4), suggesting that signal-propagation delay in the HPMs affects the phase, but not the size, of the ideal current patterns. Other factors must contribute to the phase changes in the ideal current patterns, since they could not be predicted exactly by the HPM thickness. For example, the patterns in Fig 2B (λ/4 HPM thickness) should be delayed by 90o (figure-eight shape) from those in Fig. 2A, but they are delayed by 180o (loop with inverted current direction). This could be due to the fact that the ideal current patterns cover a larger area, adding to the effective distance. While the ideal current patterns alternate between a localized loop and figure-eight3, the tangential E fields appear as distributed loops that sweep across the surface. This difference is because the ideal current patterns are optimized to maximize signal at the voxel of interest while minimizing received noise, whereas the tangential E field is simply the field produced by precessing spins at the voxel. The optimal E fields associated with the ideal current patterns showed that particular thicknesses of the HPM layer limited the propagation of the E field, consequently reducing sample noise (Fig. 5). Reduced E fields within the sample (Fig. 5B,E) correspond to larger loops in the ideal current patterns (Fig. 2B,E), indicating that larger loops can maximize the received signal when E field attenuation reduces sample noise penalty. The patterns of concentric loops with mutually opposite directions (Fig 2D) could be an effect of SNR optimization5, or due to a standing wave or resonance-like behavior6 observed in the optimal E fields (Fig 5D), but further investigation is needed.

CONCLUSIONS

Our results demonstrate that the phase changes observed in the ideal current patterns are likely due to signal propagation effects within the HPM, while the increase in size of the ideal current patterns is a consequence of reduced E field penetration into the sample for different HPM thicknesses. Our results provide an intuitive understanding of the signal and noise sensitivity changes and the optimal radius for coils in the presence of HPMs.

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

1.Webb AG. Dielectric Materials in Magnetic Resonance. Concepts in Magnetic Resonance Part A 2011;38A(4):148-184.

2.Yang QX, Wang J, Wang J, Collins CM, Wang C, Smith MB. Reducing SAR and enhancing cerebral signal-to-noise ratio with high permittivity padding at 3 T. Magnetic Resonance in Medicine 2011;65(2):358-362.

3. Lattanzi R, Sodickson DK. Ideal current patterns yielding optimal signal-to-noise ratio and specific absorption rate in magnetic resonance imaging: computational methods and physical insights. Magn Reson Med 2012;68(1):286-304.

4. Vaidya MV, Haemer G, Carluccio G, Novikov DS, Sodickson DK, Collins CM, Wiggins GC, Lattanzi R. Ideal current patterns correspond to larger surface coils with use of high permittivity materials Proc Intl Soc Mag Reson Med 2015:p.3109.

5. King SB, Ryner LN, Tomanek B, Sharp JC, Smith ICP. MR spectroscopy using multi-ring surface coils. Magnetic Resonance in Medicine 1999;42(4):655-664.

6. Haemer GG, Collins CM, Sodickson DK, Wiggins GC. Discovering and working around effects of unwanted resonant modes in high permittivity materials placed near RF coils. Proc Intl Soc Mag Reson Med 2015:p.0859.

Figures

Figure 1: Voxel of interest (red X) is located 3.4cm from the center of spherical sample (gray) surrounded by HPM (blue)(A). HPM thickness ranged from 0.8cm to 3.2cm (λ/4-λ in HPM). Ideal current patterns and tangential E fields of a synthetic dipole (B) were calculated on a spherical surface (dotted line).

Figure 2: Ideal current patterns for a voxel of interest change in size and direction (red) for different thicknesses of the HPM. In D, concentric loops with opposite direction are observed. Ideal current patterns in B, C are out of phase and E,F are in phase with A.

Figure 3: Tangential E fields produced by a local circularly-polarized field source at the voxel of interest demonstrate a phase delay for cases with the HPM layer. Tangential E fields in Fig E are phase delayed by approximately 90o w.r.t A, and fields in Fig H are in-phase with A.

Figure 4: The size of the distributed loops in the tangential E field plots does not change noticeably for cases with and without an HPM. Tangential E fields in Fig B were manually advanced in phase by approximately 90o in order to align the loop at the same position as in Fig A, for visual comparison.

Figure 5: The optimal E fields, which are the weighted combination of the DGF basis fields using the same weights that result in UISNR (matrix size of 128x128; slice x = 0), demonstrate that cases with less E field penetration (B,D,E) correspond to larger ideal current patterns in Fig 2:B,D,E.



Proc. Intl. Soc. Mag. Reson. Med. 24 (2016)
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