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Conventional MR images, such as T1-weighted spin echo images, T2-weighted turbo-spin echo images and fluid-attenuated inversion recovery images, were obtained before acquisition of the diffusion tensor images.

3D magnetization prepared rapid acquisition of gradient echo images and T2WI were acquired.

Functional images consisted of echo-planar image (EPI) volumes sensitive to gradient-echo BOLD contrast in the axial orientation (TE = 30 ms, TR = 2500 ms).

Effects of turbulence on signal intensity in gradient echo images.

With BOLD MRI, the local magnetic field disturbances induced by the relatively high magnetic susceptibility of deoxygenated hemoglobin are exploited, which provides T2 contrast on spin echo images [ 64] and T2* contrast on gradient echo images [ 55].

Three sets of echo-planar images of the whole head were acquired.

MRI systems had 1.5-T static field strengths and were capable of acquiring single spin-echo images with minimum spin-echo times of at most 6 ms.

Then, the three echo images of each scan were combined into single images by calculating the weighted sum of the three echo times.

Furthermore, because the frontopolar cortex is located in the vicinity of air-filled spaces of the nasal cavity, the corresponding magnetic susceptibility differences at the air tissue or bone tissue interface result in severe distortions and regional signal losses in long-TE gradient-echo images, particularly for ultrafast imaging techniques such as echo-planar imaging at a high magnetic field.

If in doubt, the in-phase gradient echo images are often helpful because the fatty portion of angiomyolipomas will be hyperintense, whereas renal clear cell carcinomas are generally hypo- or isointense [ 6, 46].

In-phase and opposed phase T1 W gradient echo images are useful for the evaluation of fatty infiltration of lesions.