Arrhythmia is often a significant challenge to acquiring diagnostic quality cardiac MRI. While discarding atypical cardiac cycles can exclude short-lived arrhythmic events, such as premature ventricular contractions (PVCs), this fails for atrial fibrillation (Afib), where subjects have an irregular cardiac cycle pattern. Harnessing the potential of the XD-GRASP MRI technique to reconstruct continuously acquired data with cardiac and respiratory phase as extra dimensions, we propose to additionally classify cardiac cycles for Afib patients according to their preload state, and simultaneously reconstruct the different types of arrhythmic cycles in a five-dimensional image space.
Patients underwent free-breathing continuous acquisition, using a steady-state free precession sequence, with golden-angle radial sampling scheme, for a single-slice mid-ventricular short axis cine. Imaging was performed on a 1.5T scanner (Aera, Siemens, Erlangen, Germany), TR/TE=2.8/1.4ms, FOV=320×320mm2, 128 readout points per spoke, spatial resolution 2×2mm2, slice thickness 8mm, acquisition time 2min.
Breathing and cardiac motion-related signals were separately extracted from the image data, after a "real-time" KWIC reconstruction.4 Cardiac signal was derived from an automatically detected region around the heart. The breathing motion signal was extracted from an automatically determined image block with strongest periodic signal in the breathing range (0.2-0.4Hz). Data was grouped into 5 respiratory phases using probabilistic k-means, which minimizes the intra-class variance.
Classifying cardiac cycles by length of RR interval is common but suboptimal, as it may group together cycles with different cardiac state. It was shown that, in Afib, cardiac function can be predicted by previous cycle dynamics.5 Since the P wave is absent, the amount of preload of the LV is mainly determined by the length of diastole during the previous cardiac cycle (LD). The preload is, in turn, correlated with the next cycle’s ejection fraction. Based on this observation, we use LD-dependent preload as a measure of self-similarity for cardiac cycles in Afib, which ensures a similar blood pool size for corresponding cardiac cycles. Cardiac cycles were thus classified by their preload state, computed as LD (Fig.2.). The number of distinct classes was heuristically determined from the LD distribution (3 to 6). To facilitate joint multidimensional reconstruction, reconstructed cardiac cycles were equally resampled into 15 cardiac phases.
After rebinning data in the three extra dimensions (cardiac phase, arrhythmic cycle type, and respiratory phase), each reconstructed image frame has a variable degree of undersampling (30 to 80 spokes per frame). Joint reconstruction was performed using XD-GRASP by iterative optimization.3 The optimal “sparsifiable” multidimensional image $$$d$$$ for all acquired data $$$y$$$ was found by:$$d=argmin\parallel E(d)-y\parallel_2+\lambda_1\phi_d\parallel T_1(d)\parallel_1+\lambda_2\phi_d\parallel T_2(d) \parallel_1w_2+\lambda_3\phi_d\parallel T_3(d)\parallel_1$$where $$$E$$$ is the sampling function (including coil sensitivities), $$$T_{1,2,3}$$$ are total variation functions computed separately over the cardiac, respiratory, and cardiac cycle type dimensions, as sparsity transforms, and $$$\lambda_{1,2,3}$$$ are regularizing parameters. The probabilistic result of k-means classification was used to implement weighted view sharing along the respiratory dimension $$$w_2$$$, for the highly undersampled respiratory states. To account for the variable undersampling, the additional $$$\phi_d=1/n_s$$$ weighting term is inversely proportional to the number of spokes $$$n_s$$$ in each frame.
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