- Oral presentation
Exploring intrinsic MR signal relaxation in acute RF ablation lesions using T2 mapping and IR-SSFP CINE imaging
Journal of Cardiovascular Magnetic Resonancevolume 15, Article number: O87 (2013)
Cardiac MR has been used successfully in RF ablation therapies for arrhythmias, both for procedural planning and for post-ablation lesion imaging. Non-enhanced imaging, though it has a lower SNR, has advantages over Gd-enhanced techniques mainly because contrast kinetics and dosage issues are avoided. Previously T2-weighted imaging was found to be more sensitive than T1-weighted imaging . In this study, we performed non-enhanced T2 mapping and an inversion-prepared SSFP CINE imaging to characterize intrinsic relaxation behavior in acute lesions.
Using approved animal protocols, 15 ablation lesions were created using irrigated catheters, on the endocardium of the left ventricle in 8 healthy pig models under X-ray and Carto-XP guidance. After transferring the animal to the MR suite, we performed T2 mapping using a multi-echo Fast-Spin-Echo (MEFSE) sequence  and T1* characterization using a 2RR-IR-SSFP CINE method . Both MEFSE and IRSSFP were done within 30-60 mins of creating the lesions. Then Gd-DTPA (Magnevist, 0.2 mmol/kg) was injected and late-Gd-enhancement (LGE) scans were done multiple times from 10-60 min after contrast injection. The animals were then sacrificed and the hearts were preserved for pathology.
MEFSE images were fitted using a standard 2-parameter fit for M0 and T2. The M0 term here is a function of both true M0 and T1, because it was a single-RR (RR = 700 ms) sequence. IRSSFP signal recovery is determined by T1* (dependent on both T1 and T2). Ablation extent was confirmed by LGE and pathology. The T2 and M0 maps and IRSSFP images were then analyzed using an ROI based analysis to compare the signal in 3 zones (ablation lesion, adjacent edema and remote tissue).
The T2 and relative M0 values are given in Table 1. On T2-maps there was a broad area of increased T2 in and around the ablation, likely due to edema; this area was much larger than lesion extent on pathology . However the M0-maps seem to correspond closely with the actual border of ablation. Contrast in T1*-weighted IRSSFP images also clearly depicted the actual border of the ablation seen on pathology . T1* is about 315ms in the remote zone while in ablation zone it was significantly lower at 270ms.
The M0 and T2 maps appear to depict actual lesion area and edema respectively. T1*-weighted IRSSFP generally gives more robust visualization of the ablation lesion within a breath-hold. The high signal of the lesion core in T1 and T1*-weighted images might be due to methemoglobin, which is created upon heating blood . In summary, T1-weighting seems to delineate the acute lesion core while T2-weighting seems to depict the overlying edema.
We gratefully acknowledge support from GE Healthcare, the Ontario Research Fund, and Canadian Institutes of Health Research.
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