Ferran Prados1,2, Bhavana S Solanky2, Patricia Alves Da Mota2, Manuel Jorge Cardoso1, Wallace J Brownlee2, Niamh Cawley2, David H Miller2, Xavier Golay3, Sebastien Ourselin1, and Claudia Angela Michela Gandini Wheeler-Kingshott2,4
1Translational Imaging Group, Medical Physics and Biomedical Engineering, University College London, London, United Kingdom, 2NMR Research Unit, Queen Square MS Centre, Department of Neuroinflammation, UCL Institute of Neurology, University College London, London, United Kingdom, 3Brain Repair & Rehabilitation, UCL Institute of Neurology, University College London, London, United Kingdom, 4Brain Connectivity Center, C. Mondino National Neurological Institute, Pavia, Italy
Synopsis
Quantitative sodium magnetic resonance imaging (23Na-MRI) enables the non-invasive measurement of in vivo total 23Na concentration (TSC) in the human brain. This involves a complex process of reconstructing datasets acquired to calculate a TSC map. Quantitative TSC map calibration relies on external reference phantoms with known concentration for linear calibration. This commonly involves manually segmenting the phantoms by trained raters, hindering automatic image analysis, and presenting a bottleneck in the TSC computation. We propose to substitute the manual segmentation by OPAL, a novel, fast, robust and reliable technique for segmenting sodium phantoms that allows fully-automatic reconstruction of TSC maps.Introduction
Quantitative
sodium magnetic resonance imaging (23Na-MRI) enables the non-invasive
measurement of in vivo total 23Na concentration (TSC) in the human
brain1.
This involves a complex process of reconstructing datasets acquired
to calculate a TSC map2.
Quantitative TSC map calibration relies on external reference
phantoms with known concentration for linear calibration3.
This commonly involves manually segmenting the phantoms by a trained
rater, hindering automatic analysis of the images, and presenting a
bottleneck in the TSC map computation. Moreover, the manual segmentation
of the sodium phantoms reduces reproducibility due to intra-rater and
inter-rater variability.
Here
we propose to substitute the manual segmentation with an automated
method. Recently, it has been demonstrated that the Optimitzed
PatchMatch Label fusion algorithm3
(OPAL) has an excellent performance in terms of segmentation accuracy
and computation time when compared with recently published methods4.
By introducing OPAL into our pipeline for phantom segmentation, we
aim to make the processing of TSC maps more time efficient and
reproducible.
Methods
Protocol:
10 healthy controls
and 14 Multiple Sclerosis (MS) patients were scanned on a 3T Philips
Achieva. They underwent two protocols in the same session using: 1) A
proton scan using a 32-channel
head coil, which included a PD/T2
(1x1x3 mm3)
and a 3DT1-weighted (1x1x1 mm3)
scans; 2) 23Na scan using a fixed-tuned 23Na transmit/receive coil
(Rapid Biomedical), which included a 3D-Cones UTE sequence4
(3x3x3 mm3)
and a 1H
PD/T2w sequence. Two 4% agar phantoms with 40 and 80 mM NaCl were
placed on either head side for calibration5.
Manual
phantom segmentation:
Three observers manually outlined both phantoms in all participants
using JIM (Xinapse systems); the time needed to manually segment the
phantoms was about 30 minutes per subject. Additionally, white matter
(WM) lesions were marked by an experienced observer from the PD
images.
Automatic
phantom segmentation:
OPAL3
was used to automatically detect the phantoms. The template library
was composed of 24 sodium images and the associated manual phantom
segmentations from the manual step. In order to increase the size of
the library, all the scans were left-right flipped, increasing the
template library to 48 samples. For each subject a leave-one-out
technique was used, where the manual segmentation for that particular
subject was omitted from the library. OPAL was used with the
parameters suggested by Ta et al. The time needed for detecting both
phantoms was <0.5 seconds.
Processing:
Probabilistic brain tissue segmentation was performed over the 3DT1
images using GIF6.
The segmentation masks were registered to the 23Na TSC maps. A set of
symmetric affine registrations7
were computed and concatenated. Masks were resampled to sodium space
with linear interpolation using a point-spread function8
to preserve mask continuity. The registration steps were: the 3DT1
and pseudo-T1 images (PDw-T2w images9)
were registered, the transformation between T2w and 1H
PD/T2w was calculated, and finally 1H
PD-T2w was registered to TSC map.
Partial
volume correction:
With the aim of
removing the cerebrospinal fluid (CSF) sodium contribution in the
tissues, we used a voxel-wise modified partition-based correction
method10.
Statistics:
The mean and standard deviation of grey matter (GM), cortical grey
matter (CGM), deep grey matter (DGM) and WM 23Na values were
calculated using both manually segmented phantoms and their automatic
segmentations. Two-tailed t-tests were used to look for differences
between pipelines for each tissue class in controls and patients. In
addition, for each method TSC differences between patients and
controls were assessed.
Results
and Discussion
The
new fully-automatic pipeline obtains non-significantly different
means in healthy controls, while significantly higher means in
patients as well as a lower standard deviation (both groups),
demonstrating it obtains more informative TSC maps (Table 1 and 2).
The difference between patients and controls becomes more significant
with the new fully automatic pipeline for each tissues class (Table
3). Finally, the new pipeline saves 30 minutes per subject comparing with manual
computation time.
Conclusion
We
have introduced a novel fast, robust and reliable technique for
segmenting sodium phantoms that allows fully-automatic reconstruction
of TSC maps. The new automatic pipeline has shown less variability
and hence higher sensitivity to changes in
23Na concentration. This
will enable less user-dependent variation on the results and faster
processing of large batches of data.
Acknowledgements
NIHR
BRC UCLH/UCL High Impact Initiative, EPSRC
(EP/H046410/1,EP/J020990/1,EP/K005278), MRC (MR/J01107X/1), UK MS
Society and Brain Research Trust. References
1)
Thulborn, Radiology, 1999 2)
Atkinson, Int J Imag Syst Technol, 2012 3) Christensen, MRM 1996 4) Ta, MICCAI, 2014 5) Riemer, MAGMA,
2014 6) Cardoso, IEEE-TMI, 2015 7) Modat, JMI, 2014 8)
Cardoso, MICCAI, 2015 9) Hickman, MS Journal, 2002 10) Paling,
Brain, 2014