Ben Statton1,2, Joely Smith3,4, Mary E Finnegan3,4, Rebecca A Quest3,4, and Matthew Grech-Sollars3,5
1Imperial College London, London, United Kingdom, 2Medical Research Council, London Institute of Medical Sciences, London, United Kingdom, 3Department of Imaging, Imperial College Healthcare NHS Trust, London, United Kingdom, 4Department of Bioengineering, Imperial College London, London, United Kingdom, 5Department of Surgery and Cancer, Imperial College London, London, United Kingdom
Synopsis
Magnetic Resonance Fingerprinting (MRF) is a technique which
produces multiple parametric maps during a single fast acquisition.
Before MRF can be adopted clinically, quantitative values derived from these
maps must be proven accurate and reproducible over a range of T1 and T2 values
and temperatures. The aim of this study was to investigate the accuracy and reproducibility
of T1and T2 values derived from two different methods of MRF compared to
conventional quantitative maps using the ISMRM/NIST system phantom.
Introduction
Magnetic Resonance Fingerprinting (MRF) is a
technique which produces multiple parametric maps during a single fast acquisition1.
Before MRF can be adopted clinically, quantitative values derived from these
maps must be proven accurate and reproducible over a range of T1 and T2 values
and temperatures. The aim of this study was to investigate the accuracy and reproducibility
of T1and T2 values derived from two different methods of MRF compared to
conventional quantitative maps using the ISMRM/NIST system phantom.Methods
This study was performed on the ISMRM/NIST
system phantom using a 3T Magnetom Prisma scanner (Siemens Healthcare,
Erlangen, Germany) and a 64-channel head/neck coil. The protocol comprised a 2D multi-echo spin
echo (MESE: TR 3520ms, TE: 24ms, 48ms, 72ms, 96ms, 120ms, 144ms and 168ms,
1x1x5mm voxels)2, a 3D VIBE with 6 different flip angles (VFA: TR 10ms, TE
1.43ms, FA: 2°, 8°,12°,15°, 20° and 26°, 1x1x5mm voxels)3, a prototype implementation
of a 2D FISP MRF with 1x1x5mm voxels and spiral read-out using
1500 measurements (MRF-1500) and 3000 measurements (MRF-3000)4. Each of these four
sequences was performed twice during each session and then this same protocol
was repeated nine times over the course of two months.
The phantom was stored in the scanner room. Before
each scanning session the temperature of the deionized water within the phantom
was measured using digital thermometer.
The phantom was then placed in the coil within the scanner for 30
minutes before acquisition to reduce the effects of the liquid motion.
The mean and standard deviation (SD) of each
sphere was measured from a circular region of interest (ROI) of 80 voxels manually
drawn to avoid edges on the T1 and T2 maps. As the B1 field correction in the current
implementation of the MRF sequence is only accurate above a T1 relaxation time
of 400ms, only those spheres with a value greater than this were included in
the analysis5.
The repeatability of the T1 and T2 measurements
from each of the methods, expressed as the coefficient of variation, was calculated
as the ratio of the standard deviation to the mean of the T1 and T2 values over
all the scanning sessions. The mean bias and limits of agreement (LoA) between the
T1 and T2 values derived from each of the methods was assessed by Bland Altman
analysis. Correlation between
temperature of the phantom and T2 and T1 values was also performed.Results
The mean, standard deviation and coefficient
of variation for each of the methods is summarized in Table 1 and examples for
two spheres of T1 and T2 shown in Figures 1 and 2 respectively.
Bland-Altman analysis (Figure 3) revealed a
mean bias for T1 measurements between the MRF-1500 and the VFA of 113ms (95% LoA,
-50ms to 277ms), between the MRF-3000 and the VFA of 109ms (95% LoA, -46ms to
256ms) and between the MRF-1500 and MRF-3000 of 3.8ms (95% LoA, -16.6ms to
24.3ms). The mean bias for T2 measurements between the MRF-1500 and MESE was
13ms (95% LoA, -37ms to 63ms), between the MRF-3000 and MESE of 14ms (95% LoA, -29ms
to 57ms) and between the MRF-1500 and MRF-3000 of -1ms (95% LoA, -13ms to
11ms).
There was a statistically significant
correlation between the measured T1 and the temperature of the phantom for sphere
2 (T1=1398ms) for the VFA (R2=0.46, p<0.05)), the MRF-1500 (R2=0.67,
p<0.05) and the MRF-3000 (R2=0.53, p<0.05) (Figure 4a).
Noticeably there was a steeper slope for the VFA (31x) compared to the MRF-1500
(18.6x) and MRF-3000 (17.2x). For sphere 3 (T1=998.3) there was a statistically
significant correlation between the measured T1 and the temperature for the VFA
(R2=0.31, p=0.01) but not for either of the MRF methods (Figure 4b). There was no significant correlation found between
the temperature and any of the other T1 values derived from conventional
mapping technique or MRF, neither was there any significant correlation between
the temperature and the derived T2 values for any of the techniques (examples
Figure 4c,d).Discussion
MRF derived T1 values in the range 1838ms to
509ms varied less than 2.1%, and T2
values in the range 645ms to 31ms varied less than 5% in 9 sessions over two
months using the ISMRM/NIST system phantom. The T2 measurements had greater variation
than the T1 measurements which agrees with previously published results6.
Agreement between the two MRF techniques was excellent,
suggesting that the use of the 1500 dictionary could be more practical in
clinical practice as it can be acquired in half the time and is a significantly
quicker to reconstruct. The T1 values derived from the MRF were less
susceptible to temperature variations than the VFA method, especially at the T1
values which would be encountered clinically in the brain. This finding would
need to be studied more thoroughly in future work.Conclusion
MRF is a highly reproducible method for T1
and T2 mapping with seemingly less temperature variation than conventional
methods. There is very little difference in derived T1 and T2 values from the
MRF method using the 1500 dictionary and that using the 3000 dictionary.Acknowledgements
The authors would like to acknowledge funding from
the Imperial CRUK Centre and the Imperial NHS Imaging Department. Thanks also
to the Imperial MRI Physics Collective, Iulius Dragonu and Mathias Nittka,
Siemens Healthineers, UK and Germany.References
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