Image Reconstruction (including machine learning)
Omer B. Demirel, MSc
PhD Candidate
University of Minnesota
Minneapolis, Minnesota, United States
Omer B. Demirel, MSc
PhD Candidate
University of Minnesota
Minneapolis, Minnesota, United States
Chi Zhang
PhD Candidate
University of Minnesota, Minnesota, United States
Burhaneddin Yaman, BSc
PhD
University of Minnesota
Saint Paul, Minnesota, United States
Steen Moeller, PhD
Assistant Professor
University of Minnesota
Minneapolis, Minnesota, United States
Chetan Shenoy, MBBS, MS
Associate Professor of Medicine
University of Minnesota
Minneapolis, Minnesota, United States
Sebastian Weingartner, PhD
Assistant Professor
Delft University of Technology
Delft, Zuid-Holland, Netherlands
Tim Leiner, MD, PhD
Professor of Radiology
Mayo Clinic
Rochester, Minnesota, United States
Mehmet Akcakaya, PhD
Associate Professor
University of Minnesota
Minneapolis, Minnesota, United States
Theory: The inverse problem for simultaneous multi-slice (SMS) imaging [1] is given as xSMS = arg minxSMS ||ySMSΩ-ESMSΩxSMS||2 + ℜ(xSMS) where ySMSΩ is acquired SMS k-space, Ω is the undersampling pattern, ESMSΩ is MR encoding operator, xSMS is readout concatenated slices of images, and ℜ(.) is a regularizer. Variable splitting is used [4] for solving this, alternating between data-fidelity incorporating MRI physics, and implicit regularization using neural networks. Recently, zero-shot self-supervised PG-DL (ZS-SSDU) [5] was proposed for subject-specific training without a ground truth or training database. ZS-SSDU splits measurements ySMSΩ into three disjoint sets θ, Λ, and Γ. θ enforces data-fidelity in the PG-DL network. Λ defines a k-space loss [4], and Γ is used as k-space validation loss for early stopping [5] to avoid overfitting (Fig. 1). Further, a multi-mask approach was used as data augmentation, partitioning Ω\Γ into K disjoint pairs (θk,Λk). Experiments: Free-breathing first-pass perfusion was acquired at 3T on 2 subjects, with outer volume suppression [2], SMS=3, uniform in-plane R=4, resolution=1.7×1.7mm2, temporal resolution=116ms. A 3D unrolled PG-DL network was implemented for subject-specific regularization across all time-frames using ZS-SSDU (Fig. 1). 20% of Ω was randomly selected for Γ. K=100 partitions were used for the remainder. Training was stopped once k-space validation loss increased [5]. Comparisons were made to split-slice GRAPPA (SP-SG) and locally-low rank (LLR) regularized reconstruction. Images were assessed by an experienced reader on a 4-point scale (1:best, 4:worst) for aliasing artifacts, SNR, blurring, and overall quality [4].
Results: Figs. 2 and 3 show results from 2 different subjects. SP-SG suffers from noise amplification. LLR reconstruction reduces noise but leaves residual artifacts. Proposed subject-specific PG-DL eliminates noise and aliasing artifacts, yielding high-quality images across time-frames. Image readings align with these observations.
Conclusion: Proposed subject-specific PG-DL leads to improved perfusion CMR, particularly in later time-frames with limited SNR.