Chathura Kumaragamage1, Henk M De Feyter1, Peter B Brown1, Scott McIntyre1, Terence W Nixon1, and Robin A de Graaf1
1Radiology and Biomedical Imaging, Yale University, New Haven, CT, United States
Synopsis
At high
magnetic field strengths (≥3T), the utility of MRSI is impeded by challenges
such as increased B1 field heterogeneity, increased RF power requirements
for reduced chemical shift displacement errors (CSDE), and water/lipid
contamination. In this work, the utilization of gradient modulated (GOIA) RF
pulses, is investigated, with elliptical localization with pulsed second order
fields (ECLIPSE) for MRSI. A 15 kHz GOIA pulse based ECLIPSE double-spin-echo
MRSI sequence was developed. In vivo data demonstrate that the GOIA based MRSI
method provides full-intensity metabolite spectra in edge of the brain voxels,
and undetectable extracranial lipid signals within or outside the brain.
Introduction
Proton Magnetic Resonance Spectroscopic
Imaging (MRSI) is a powerful technique that can map the metabolic profile in
the human brain, non-invasively. At high magnetic field strengths (≥ 3T), MRSI is
presented with a number of technical challenges including, lipid and water
contamination, increased B1 field heterogeneity, and increased RF power
deposition to reduce chemical shift displacement errors (CSDE).
Elliptical
localization with pulsed second order fields (ECLIPSE1) for MRSI has
recently been demonstrated for robust (> 100-fold) lipid suppression, while providing
high brain coverage relative to cubical localization and low power requirements
compared to traditional 8-slice OVS2. The objectives of this work
were to further improve ECLIPSE by reducing CSDE through the use of gradient-modulated
GOIA3 pulses without significantly increasing RF power deposition.Methods
The
GOIA RF pulse was derived from an AFP-HS4 pulse (Figure 1, dotted line) of 6.66
ms duration and 3.0 kHz bandwidth. Given the amplitude and gradient
modulations, the GOIA frequency modulation was calculated for a 15 kHz
bandwidth (Figure 1, solid line) as previously described3. In order to
achieve 99.5% inversion efficiency, the GOIA RF pulse needed to be executed
with 25% more amplitude (Figure 1A).
All MR experiments were performed on a 4T
magnet (Magnex Scientific Ltd.) interfaced to a Bruker Avance III HD
spectrometer running ParaVision 6 (Bruker, Billerica, MA, USA). A within-brain
B1+ optimized, 8-element Tx/Rx volume coil was used with a ± 30% and ± 60% B1+
variation within the brain and extracranial region, respectively.
The ECLIPSE system1 is a
home-built, unshielded gradient insert consisting of Z2, X2Y2, and XY second
order spherical harmonic magnetic fields with efficiencies of 5.48, 2.58 and
2.76 Hz/cm2/A, respectively, driven by three independent 100A Techron 7780
current amplifiers (Techron, Elkhart, IN, USA) interfaced to a home-built
multi-channel gradient controller4. The minimum and implemented rise
times of the ECLIPSE magnetic fields are 660 and 1150 µs, respectively. A water
reference MRSI was acquired and used for receiver amplitude and phase
correction, as well as B0 eddy current compensation.
An ECLIPSE based adiabatic double-spin-echo sequence1
was implemented with GOIA RF pulses, for B1 insensitive inner volume
selected MRSI (see Figure 2). The gradient modulation was applied to the
higher-order Z2, X2Y2 and XY ECLIPSE gradients, as well as on the linear X and
Y gradients needed for in-plane translations. GOIA modulation of the B0 field
was implemented as a RF phase modulation. A
seven-pulse VAPOR-style water suppression sequence was optimized using Gaussian
pulses (10ms, 200Hz BW), as indicated in Figure 2. The MRSI phase encoding gradients were
superimposed on the spoiler gradients (3 ms 20 mT/m), sampling a 17 x 21 matrix
for a 1 mL nominal volume resolution.Results
Figure
3 compares the CSD in a two-compartment water-vegetable oil phantom when the 3
kHz AFP-HS4 and 15kHz GOIA pulses were used with ECLIPSE localization. Considering
water-fat chemical shift to be 600Hz at 4T, the CSD in (A-D) is 0.90cm, -0.90cm,
0.18cm, and -0.18cm respectively, which is in agreement with the apparent CSD
in experimental data. A radially decreasing gradient field in the X-Y plane is
generated for negative second order fields, and results in a smaller ROI for
up-field lipid signals (see Figure 3B,D) relative to water. This convention was
used for all subsequent MRSI acquisitions.
Figure
4 compares the CSD for an elliptical ROI selection with ECLIPSE generated with AFP-HS4
and GOIA pulses in a metabolite phantom. The dotted lines that extend from (D) -
(B) and (E) - (C) indicate the edge of the NAA methyl (2.01 ppm) and creatine methylene
(3.93ppm) metabolic maps, respectively for the GOIA pulse ROI. The small
water-creatine chemical shift difference leads to near-identical ROIs for both
acquisitions. However, the circa 2.7 ppm water-NAA chemical shift difference
leads to a significantly smaller ROI for the low-bandwidth AFP- HS4 pulse. When
comparing voxel locations [2, 5, 8] the reduction in NAA intensity is evident,
with the AFP-HS4 pulse, and is minimal with the GOIA based acquisition.
Figure 5 illustrates
an in vivo MRSI acquisition with GOIA pulses used for elliptical ROI selection
with ECLIPSE. The elliptical ROI results in the water-NAA CSD to be 1.5mm and 1.9mm
in the x and y direction at ROI edge voxels, respectively. Furthermore, the
transition zone (Mz/M0 = 0.9 to -0.9) to bandwidth zone ratio for the GOIA
(HS4) pulse is ~3%, which results in full intensity brain spectra along the ROI
edge, and negligible perturbation of extracranial lipid resonances in the
adjacent voxels as illustrated in Figure 5.Conclusions
ECLIPSE-based
IVS provides high-quality lipid suppression in MRSI. However, like all IVS
methods it is sensitive to large CSDs during low bandwidth RF pulses.
GOIA-ECLIPSE has been shown here to maintain excellent lipid suppression, while
minimizing CSDs to 1.9 mm and providing high 2D brain coverage. The five-fold
bandwidth improvement comes with a modest (~25%) increase in RF amplitude,
making GOIA-ECLIPSE an attractive method for high-field MRSI.Acknowledgements
This
research was supported by NIH grant R01- EB014861.References
[1] de
Graaf RA, Brown PB, De Feyter HM, McIntyre S, Nixon TW. Elliptical localization
with pulsed second-order fields (ECLIPSE) for robust lipid suppression in
proton MRSI. NMR in biomedicine 2018;31(9):e3949.
[2] Henning
A, Schar M, Schulte RF, Wilm B, Pruessmann KP, Boesiger P. SELOVS: brain MRSI localization
based on highly selective T1- and B1- insensitive outer-volume suppression at
3T. Magn Reson Med 2008;59(1):40-51.
[3] Tannus
A, Garwood M. Adiabatic pulses. NMR in biomedicine 1997;10(8):423–434.
[4] Nixon
TW, McIntyre S, de Graaf RA. The design and implementation of a 64 channel
arbitrary gradient waveform controller. Proc Int Soc Magn Reson Med.
2017;25:969.
[5] Tayari N, Heerschap A, Scheenen T,
Kobus T. In vivo MR spectroscoping imaging of the prostate, from application to
interpretation. Anal Biochem. 2017;529:158-170.