CMR-FT was performed using dedicated software provided by TomTec Imaging Systems (2D CPA MR, Cardiac Performance Analysis, Version 1.1.2.36) and Circle Cardiovascular Imaging (Tissue Tracking, cvi42). For the purposes of this paper the different software tools are referred to as “TomTec” and “Circle”. Identical short axis sections were analysed at apical, mid-ventricular, and basal levels to compare short-axis-derived global LV Ecc and Err (based on all three analysed sections) alongside the time-to-peak (TPK) strain duration. Short-axis CMR images were analysed at rest and with 10 and 20 μg/kg/min dobutamine, respectively. Myocardial torsion was calculated from the rotational raw data provided with the TomTec software using an in-house-developed post-processing tool as recently described by the authors' group.15 (link) The model underlying this assessment makes use of linear interpolation and takes standardized rotational measurements at 25 and 75% LV locations after the analysis of a whole LV short axis stack. In this model the most apical section showing LV cavity at end-systole is considered at the 0% LV location and the most basal section including a complete circumference of myocardium at end-systole is considered at the 100% LV location. In comparison to TomTec, Circle commercially provides torsion measurements within its software interface. This is done by manually choosing an apical and basal section. In order to allow accurate comparisons between vendors, apical and basal sections at the closest distance to 25% and 75% LV locations were chosen.
With both types of software LV endocardial and epicardial borders were manually delineated in all analysed sections with the initial contour set at end-diastole. In case of insufficient tracking, as defined by apparent deviations of the contours from the endocardial and epicardial borders, contours were manually corrected and the algorithm reapplied. The tracking was repeated three times in all sections. One single observer analysed all data using both types of software. Intra-observer variability was derived from the repetition of the analysis after 4 weeks. The analysis of a second skilled observer for both types of software was used to assess interobserver reproducibility.
Reported results are based on the average of three analysis repetitions (R3). To study the impact of repeated measurements on reproducibility, the reproducibility derived from results based on a single repetition (R1), averaged results for two (R2) and three repetitions (R3) were compared with each other.
With both types of software LV endocardial and epicardial borders were manually delineated in all analysed sections with the initial contour set at end-diastole. In case of insufficient tracking, as defined by apparent deviations of the contours from the endocardial and epicardial borders, contours were manually corrected and the algorithm reapplied. The tracking was repeated three times in all sections. One single observer analysed all data using both types of software. Intra-observer variability was derived from the repetition of the analysis after 4 weeks. The analysis of a second skilled observer for both types of software was used to assess interobserver reproducibility.
Reported results are based on the average of three analysis repetitions (R3). To study the impact of repeated measurements on reproducibility, the reproducibility derived from results based on a single repetition (R1), averaged results for two (R2) and three repetitions (R3) were compared with each other.
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