The purpose of this work was to develop and evaluate a novel deep learning-based framework termed Reference-free Latent map-eXtracting MANTIS (Relax-MANTIS) for efficient MR parameter mapping. Our approach incorporated end-to-end CNN mapping, the concept of cyclic loss to enforce data fidelity and without the need of explicit training references. Our results demonstrated that the proposed framework produced accurate and robust T1 mapping in knee and low-SNR lung UTE MRI. The good quantitative agreement to the reference method suggests that Relax-MANTIS allows potentially accelerated quantitative mapping without modifications of scan protocol and sequence for high-resolution knee and whole lung T1 quantification.
(a) Quantitative Imaging: The Relax-MANTIS framework (Figure 1) performs a learning process to estimate latent parameter maps, for instance, T1 and proton density images $$$ I_{0}$$$, using CNN mapping and the known MR signal model for the parameters of interest. Like MANTIS, the CNN mapping was implemented for converting the VFA image data directly to the T1 and $$$ I_{0}$$$ maps. However, Relax-MANTIS relaxes the requirement for the use of reference quantitative maps as supervised learning, but ensures that the extracted parameter maps from end-to-end CNN mapping produce estimated images matching the VFA images (i.e. model-augmented data consistency). The training objective is to learn parameters and using the generator CNN, $$$C(i|T_{1},I_{0})$$$: $$\hat{T_{1}},\hat{I_{0}}=argmin_{T_{1},I_{0}}(E_{i\sim domain(i)}[\sum_{j=1}^N\parallel S_{j}(C(i|T_{1},I_{0}))-i^{j} \parallel_{1}])$$ where $$$i$$$ are input VFA images, $$$i^{j}$$$ is the input image at the $$$j^{th}$$$ FA, $$$N$$$ is the total number of FAs, $$$S_{j}(\cdot)$$$ is the MR signal model, denotes the $$$l_{1}$$$ norm, $$$E$$$ is the expectation operator.
(b) Network Implementation: We used U-Net as convolutional encoder/decoder for performing the end-to-end CNN mapping4. The network was trained on an Nvidia GeForce GTX 1080Ti card using adaptive gradient descent optimization with a learning rate of 0.0001 for 300 epochs.
(c) Evaluation: Two image datasets were used as follows. 1) 34 spoiled gradient echo VFA healthy knee data sets (30/4 for training and evaluation) at 3.0T (GE Discovery MR750): 16cm FOV, 3 FAs = 3°, 7° and 18°, TR/TE = 4.9/2.3 ms, 3mm thickness, 256×256×32 matrix. 2) 12 low-SNR (10.9±2.9) 3D radial UTE VFA5 data sets of the healthy lungs (9/3 for training and evaluation) with full chest coverage at 1.5T (GE SignHDx): 32cm FOV, 5 FAs = 2°, 4°, 6°, 10° and 14°, TR/TE=2.86/0.08 ms, ~30,000 projections per FA, and total scan time=~14 minutes. Due to the inherently low proton density in lung, the two additional FAs (6°and 14°) were acquired to solve for T1 using standard non-negative least-squares fitting (NNLS)6. All UTE images were reconstructed at 1.25mm isotropic resolution (320×356×320 matrix) and registered to the UTE at 10° FA for each subject. For both knee and lung data, parameter maps were also calculated using standard NNLS and the widely used maximum likelihood variable projection method (VPM) with a grid search estimator7,8.
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