Available literature values for T1 are approximately

400 ms, 600 ms, 800 ms and 1100 ms at 1 T, 1.5 T, 1.9 T and 3 T, respectively [16] and [21]. Our value of T1 of 1656 ms measured at 7 T confirms the overall trend of increasing T1 with field strength. For T2, there appears to be little change with field strength. The observed fall in T1 and T2 with the number of freeze–thaw cycles also confirms previous reports [16] and [17], although only the T1 values for two and four cycles reached statistical significance. Available PF-02341066 cell line literature values for myocardial T1 are 1300 ms in rat at 4.7 T [22] and 952 ms in mouse at 9.4 T [23], rather lower than our PVA Cryogel phantoms. However, our primary design goal was to generate realistic myocardial motion rather than exact matching of relaxation times. Use of a pure sinusoidal flow from the pump resulted in eventual collapse

of the phantom at “end systole,” so that an offset sinusoid was used. In practice, the amplitude and degree of offset were adjusted until the phantom operated without collapse. The use of an offset sinusoid would seem to imply an overall net flow towards the phantom. However, since no leaks were evident downstream of the pump, we conclude that the pump itself was not 100% efficient and that there was some backflow through it. The phantoms http://www.selleckchem.com/products/Everolimus(RAD001).html exhibited smooth cyclic behavior with suitable pump settings, and the walls were highly visible in the Rebamipide MR images. As can be seen from Fig. 2 and Fig. 3 and Table 1, the dynamic range of diameters achieved was broadly similar to in vivo measurements except that the rat phantom had a larger inner diameter (and hence thinner walls) than a real rat heart (Fig. 2). Thin walls were necessary to ensure sufficient distensibility. The dynamic performance of the mouse phantom dimensions agreed very well with in vivo behavior, although some asymmetry of wall thickness is apparent in Fig. 3. A limitation of the current phantoms is that their geometry is very simplified compared with real rodent hearts, but it is sufficient for imaging in the short-axis view routinely used in assessment of cardiac function [24]. Modeling

of complex rotation and shortening movements was beyond the scope of the current work. The pattern of fluid flow within the phantom is quite different from blood flow in real hearts, but in this work, the objective was to mimic LV dimensions and not blood flow. Specifically, the phantoms were subsequently used to implement and test the kt-Broad-use Linear Acquisition Speed-up Technique [25] for accelerated cardiac imaging (data not shown). Refinements beyond the scope of the current work could include the addition of rotation and “respiratory” motions, the incorporation of metabolites in the phantom walls for the development of MR spectroscopic techniques, and the use of a fully programmable pump to enable asymmetric timing of the cardiac cycle.