Sebastian Mueller1, Felix Glang1, Klaus Scheffler1,2, and Moritz Zaiss1,3
1High-field Magnetic Resonance Center, Max Planck Institute for Biological Cybernetics, Tuebingen, Germany, 2Department of Biomedical Magnetic Resonance, Eberhard Karls University Tuebingen, Tuebingen, Germany, 3Department of Neuroradiology, University Hospital Erlangen, Erlangen, Germany
Synopsis
The pH
value is of major importance for most physiological processes and may change
due to altered metabolism in pathologies. In the present work, we exploit the inherent
dependency of CEST MR data on pH with a new approach: train neural networks
to map voxel-by-voxel from multi-B1+ CEST spectra to pH value. Measurements
were performed in homogenate of pig brain tissue at 9.4T ultra high field. Prediction
of absolute pH values was possible and predictions were stable against inhomogeneity
in B1+. We hope this proof of concept might be a first small step towards high-resolution
3D pH maps in vivo.
Introduction
The
pH value is of importance for nearly all physiological processes in vivo and it
is often altered in pathologies due to altered metabolism – for example in
tumors or in ischemic stroke. To be able to generate a 3D pH map with
reasonable spatial resolution is thus of great interest in MRI. One way to
access pH noninvasively in vivo with high precision is 31P MR spectroscopy (1). However, 31P MRS suffers from low signal and
thus relatively poor spatial resolution. In 1H CEST MRI the pH value is an
inherent property of all measured signals since it catalyzes the exchange rates
(2) which can be exploited for pH mapping (3). Moreover, the signal of 1H CEST is much higher
compared to 31P. However, at in vivo conditions the pH dependency of the CEST signal
is rather complex and not easy to model. In the present work, we aim to extract
the pH value from CEST data by training a neural network (NN) to predict pH
values from multi-B1 CEST spectra acquired in post mortem pig brain at 9.4T as
an in-vivo-like tissue sample.Methods
All
measurements were performed at a 9.4T human whole body MR scanner (Siemens
Healthineers, Erlangen, Germany) with a custom-built 18/32 Tx/Rx head coil (4) applying a 3D-GRE sequence (5) (TE/TR=1.91/3.76ms, FOV=147x120x40mm³, ROxPEx3D=96x78x8;
690Hz/pix; in PE: GRAPPA=2). CEST measurements were performed for 112
saturation offsets at three different nominal B1+ values (0.4, 0.6, 0.9 µT)
with 150x15ms Gaussian pulses at DC=50% (recovery times/M0=5/12s).
Four interleaved WASABI (6) measurements were added. Samples were prepared
from fresh pig brain provided by the local slaughterhouse (no animals killed
only for the purpose of this work). Vessels, brain stem and penumbra were
removed before homogenate was produced. The pH value in the homogenate was
adjusted using 1M NaOH and HCl and measured using a pH electrode (inoLab pH
720, WTW, Weilheim, Germany). A deep feed-forward neural network (NN), with
probabilistic output layer for uncertainty quantification, was trained voxel-by-voxel
on data sets that contained CEST spectra of three different B1+, and the absolute
B1+ values obtained by WASABI. Target pH values for the NN were determined with
the pH electrode for each sample. For testing the NN, additional samples with
slightly different pH values compared to the training set were created and
measured with the exact same MRI protocol.Results
Investigation
of different NN architectures showed that two layers with 100 neurons each were
suitable for the given task with dropout rate during training set to 10%. The
calibration mean squared error as suggested by Kendall et al. (7) was found to be below 5% for the optimized NN
architecture. The
NN was able to predict pH with an average deviation <0.1 pH (maximum
deviation <0.2 pH) in phantoms that were not contained in the training set.
In Figure 1A, the corresponding pH ground truth and NN prediction values are
shown for seven samples. The
predicted pH values match the ground truth well, as indicated by the slope
(+1.2812; ideal: 1.0) shown in Figure 2A. The same network trained on 25°C data was also
applied to additional test samples measured at 37°C. This increased the
average prediction error by a factor of 2.4, however, the relative pH contrast
between the samples was still predicted correctly (Figure 1B/2B).
The spatial distribution of predicted
pH values was homogeneous within single samples (Figure 2CD) and on average
spatial std/mean was 8%. The B1+ values differed by 21% with the same metric. Figure 3 shows scatter
plots and correlation coefficients for predict pH against measured relative
B1+. Only weak correlation (in 5 of 7 cases significant with P<0.05) was
seen with min/max/average correlation coefficients of -0.4991/0.3526/0.0031 for
different samples. Thus, the NN is robust against B1+ inhomogeneity. Indeed
the largest absolute correlation coefficient was observed for a sample that had
a 2.2 times smaller T1 (≈840ms)
as contained in training data (mean±std:
(1872±27)ms).Discussion
The pH-deepCEST NN was able to predict pH values of unknown
samples with high accuracy. Interestingly, the network also generalized to
samples with different temperature as contained in the learning data set, and
could predict pH differences accordingly; still the absolute pH value was
biased. Nevertheless, other parameters such as T1, T2 and especially
concentration were kept constant and their influence on the predictions must be
further evaluated since they would spatially differ in vivo and alter CEST MRI
spectra. For example, it was observed that T1 might introduce some bias. Still, being able to exploit 1H CEST MRI data to predict pH
values would strongly increase spatial resolution as compared to spectroscopic
imaging; in addition clinical translation of such a pH mapping might be simpler
for a 1H-based MRI method.Conclusion
The
derived results can be seen as proof of principle for the application of neural
networks to predict absolute pH values based on 1H CEST MRI data of brain
tissue.Acknowledgements
The financial support of the Max
Planck Society, German Research Foundation (DFG, grant ZA 814/2-1), and
European Union’s Horizon 2020 research and innovation programme (Grant Agreement
No. 667510) is gratefully acknowledged.References
1. Moon RB, Richards JH. Determination of
Intracellular pH by 31P Magnetic Resonance. J. Biol. Chem. 1973;248:7276–7278.
2. Englander SW, Downer NW, Teitelbaum H.
Hydrogen Exchange. Annual Review of Biochemistry 1972;41:903–924 doi:
10.1146/annurev.bi.41.070172.004351.
3. Zhou J, Payen J-F, Wilson DA,
Traystman RJ, van Zijl PCM. Using the amide proton signals of intracellular
proteins and peptides to detect pH effects in MRI. Nature Medicine
2003;9:1085–1090 doi: 10.1038/nm907.
4. Avdievich NI, Giapitzakis I-A, Bause
J, Shajan G, Scheffler K, Henning A. Double-row 18-loop transceive–32-loop receive
tight-fit array provides for whole-brain coverage, high transmit performance,
and SNR improvement near the brain center at 9.4T. Magnetic Resonance in
Medicine 2019;81:3392–3405 doi: 10.1002/mrm.27602.
5. Zaiss M, Ehses P, Scheffler K.
Snapshot‐CEST: Optimizing spiral‐centric‐reordered gradient echo acquisition
for fast and robust 3D CEST MRI at 9.4 T. NMR in Biomedicine 2018;31 doi:
10.1002/nbm.3879.
6. Schuenke P, Windschuh J, Roeloffs V,
Ladd ME, Bachert P, Zaiss M. Simultaneous mapping of water shift and B1
(WASABI)-Application to field-Inhomogeneity correction of CEST MRI data. Magn
Reson Med 2017;77:571–580 doi: 10.1002/mrm.26133.
7. Kendall A, Gal Y.
What Uncertainties Do We Need in Bayesian Deep Learning for Computer Vision?
In: Guyon I, Luxburg UV, Bengio S, et al., editors. Advances in Neural
Information Processing Systems 30. Curran Associates, Inc.; 2017. pp.
5574–5584.