- Poster presentation
- Open Access
High-resolution spin-echo Cardiac Diffusion-Weighted MRI with motion compensated Convex Optimized Diffusion Encoding (CODE)
© Aliotta et al. 2016
- Published: 27 January 2016
- Apparent Diffusion Coefficient
- Cardiac Motion
- Cardiac Phasis
- Diffusion Weight
- Sequence Constraint
Cardiac Diffusion Weighted MRI (cDWI) has the potential to characterize myocardial infarction (MI) without contrast. However, the clinical utility of cDWI has been limited by severe sensitivity to cardiac motion that manifests as signal dropouts which corrupt measures of myocardial diffusivity. This can be managed by carefully timing the diffusion encoding gradients (GDiff) to a quiescent diastolic phase, but this approach is burdensome and highly sensitive to heart-rate changes. More recently, motion compensated (MOCO) diffusion encoding gradients with nulled first (M1) and second (M2) moments have demonstrated good robustness to cardiac motion (Stoeck, MRM 2015, Nguyen, MRM 2013) but they necessarily increase the echo time (TE) compared to monopolar encoding (MONO), which reduces SNR and/or limits spatial resolution. We have developed a MOCO cDWI sequence that employs Convex Optimized Diffusion Encoding (CODE) to reduce bulk motion sensitivity and shorten TE compared to existing MOCO schemes.
G Diff Design: CODE gradients were calculated using convex optimization to determine the M1 and M2 nulled GDiff waveform that minimizes TE while conforming to hardware (GMax = 80 mT/m and SRMax = 50 T/m/s) and pulse sequence constraints. Imaging: Healthy volunteers (N = 5) were scanned on a 3.0T scanner (Siemens Prisma) after providing written informed consent for an IRB approved study. High resolution cDWI were acquired in the left ventricular (LV) short-axis with b = 350 s/mm2, 1.5 × 1.5 × 5.0 mm spatial resolution, 2x GRAPPA acceleration, three orthogonal diffusion encoding directions and three signal averages in a single 15-heartbeat breath hold. Both MONO (TE/TR = 67 ms/1R-R) and CODE encoding (TE/TR = 76 ms/1R-R) were acquired, but MOCO (TE = 94 ms) was not. All cDWI were acquired at eight subject-specific cardiac phases distributed across systole and diastole. Reconstruction and Data Analysis: Apparent diffusion coefficient (ADC) maps were reconstructed at each phase. Motion corrupted voxels were identified by ADC values exceeding 3.0 × 10-3mm2/s (the diffusivity of free water at 37°C, a thermodynamic upper bound for soft tissues) in the LV. The mean LV ADC and the percentage of motion corrupted LV voxels were then calculated at each phase. Statistical analyses were performed using t-tests with Holm-Sidak post hoc corrections.
CODE cDWI significantly improved robustness to cardiac motion compared to MONO cDWI. CODE cDWI also permits M1 and M2 moment nulling with a shorter TE than existing MOCO cDWI methods.
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