James Timothy Grist1,2, Esben S Hansen3, Juan D Sanchez4, Mary A McLean5, Frank Riemer6, Rolf F Schulte7, Jan Henrik Ardenkjaer-Larsen4, Christoffer Laustsen3, and Ferdia A Gallagher6
1Unviesity of Cambridge, Cambridge, United Kingdom, 2University of Birmingham, Birmingham, United Kingdom, 3Aarhus University, Aarhus, Denmark, 4Technical University of Denmark, Copenhagen, Denmark, 5Cancer Research UK, Cambridge Institute, University of Cambridge, Cambridge, United Kingdom, 6University of Cambridge, Cambridge, United Kingdom, 7GE Healthcare, Munich, Germany
Synopsis
Hyperpolarized 13C MRI is an emerging clinical technique
to probe metabolism. Calibration of transmit gain and centre frequency is
challenging, due to the low endogenous 13C signal. Pre-scan is
typically performed by adding an external phantom for reference, however this
is challenged by the shim volume inside the subject and the RF coil excitation
and receptions profiles. We demonstrate the ability to use the sodium-23
resonance to accurately prescan prior to 13C experiments, using single
tuned 13C coils in a 3T MRI system. This provides an important workflow
improvement for the adoption of hyperpolarized 13C imaging into
clinical practise.
Introduction
Hyperpolarized carbon-13 MRI is a powerful, clinical technique to
probe in vivo metabolism, and recent studies
have demonstrated the technique in the brain, heart, and in cancer (1–4) The calibration of the system centre frequency and radiofrequency power is commonly achieved using external phantoms
but errors in this calibration will significantly affect data quality. Previous
work has assessed the use of dual tuned 23Na/13C coils to
calibrate 13C experiments as part of the prescan (5,6) and here we develop this idea by using
dedicated commercially available 13C coils to provide this data. Here
we show that the sodium-23 resonance can be reliably used to calibrate clinical
systems prior to data acquisition using dedicated, clinically available, 13C
tuned coils providing all the necessary system parameters for successful data
acquisition. Methods
System centre frequency and transmit gain (TG) estimation
Four cylindrical phantoms filled with saline (150-17 mMoL-1
NaCl) with a urea phantom (8 MoL-1) on top were placed in the
scanner (3T, HDx, GE Healthcare, WI) with either two 13C tuned 8-channel
paddle coils or a single loop receive coil placed either side of the phantom or
on top of the phantom, respectively. A Helmholtz loop transmitter (clamshell)
was used for B1 transmission. The 13C urea and 23Na
centre frequency and TG were acquired using a pulse-acquire Bloch-Siegert
acquisition (hard pulse, pulse width = 0.5 ms, repetition time (TR) = 2 s, echo
time (TE) = 0.5 ms, flip angle (FA) = 90 degrees)(7). The ratiometric difference in centre
frequency between 23Na/1H and 13C-urea were
averaged over all experiments. The difference in TG (dB) between 23Na
and 13C was calculated for all experiments. A linear fit between the
TG at different loading states per nuclei was calculated.
In vivo experiments
Six female Danish land pigs were placed supine in the scanner. The
single loop coil was placed on the biceps femoris muscle of the right lower
limb, and used for acquisition with a 13C-lactate (4MolL-1)
phantom placed in the FOV of the coil. The 23Na and 13C
centre frequency were recorded, as well as the TG required for 23Na
and 13C as described above before data acquisition (partially
self-refocusing since pulse, spectral bandwidth = 5 kHz, number of samples =
2048, TR = 1 s, 128 time points, FA = 12 degrees, slice thickness = 40 mm). Spectral
data were post-processed using matching pursuit fitting and kinetic modelling as
well as calculating ratiometric results (lactate:pyruvate,
bicarbonate:pyruvate) (8). Kinetic and ratiometric results were
averaged over all experiments, and a linear correlation between kPL and lactate:pyruvate was performed.
All processing and statistical analysis was performed in Matlab (2018a, The
Mathworks, MA).
Coil profile estimation
The RF amplifier was disabled and a noise only acquisition
performed with the 8-channel paddle coils to calculate the noise covariance
matrix at both 13C and 23Na frequencies.
Transmit B1 Simulations
Simulations of the clamshell B1+ performance at both 13C
and 23Na frequencies was performed (CST, Darmstad, Germany) and the
ratio between 13C and 23Na B1+ fields (T)
computed.
Results
System f0 and TG calibration can be performed with the 23Na
resonance for 13C experiments
The ratiometric difference in 23Na and 13C
Urea f0 at 3T was 1.05180 ± 0.00001, with the mean difference in TG
for 23Na and 13C was 10.4 +/- 0.6 dB. Simulated B1+
profiles agreed with this (Figure 2), with a predicted difference in 10.4 +/- 0.2 dB between 23Na
and 13C. There was no significant correlation between saline
loading and TG (R2 < 0.1, p > 0.05). Simulations showing the
transmit B1 field at the 13C and 23Na frequencies can be
found in Figure 2A and B, respectively; Figure 2C shows the ratiometic
difference between the two.
13C coil element noise coupling increases at 23Na
frequency
Noise correlation between the 8 channels in the paddle coil
revealed good linearity at 13C frequency, however increased
off-diagonal correlation was observed at 23Na f0, shown
in Figure 3A and B, respectively.
In vivo hyperpoalrized 13C experiments
are successful using a 23Na prescan
Using the 23Na prescan, hyperpolarized 13C
MRS was successfully performed from the musculature of six pigs. The frequency
scaling constant between 23Na and [1-13C] pyruvate was 1.05179
± 0.00001. Kinetic analysis revealed a mean kPL
of 0.007 +/- 0.002 s-1 and correlated with lactate:pyruvate ratio (R2
= 0.9, p = 0.01). Example summed spectra are seen in Figure 4.
Discussion
This study has provided the translational step required to
provide a clinical pipeline for successful, accurate, prescan measures for hyperpolarized
13C experiments using the 23Na resonance. Due to the high
natural abundance of 23Na in vivo, combined with the low frequency
difference at 3T, it is possible to utilise this technique with dedicated,
commercially available, coils – providing the translation step required for
clinical application and uptake of this technique.Acknowledgements
This study was funded by the Lundbeck Foundation, Medical Research Council, Cancer Research UK, and the Little Princess Trust.References
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