72 mm birdcage volume coil

Orbital contents of a minke whale (Balaenoptera acutorostrata, USNM 593554 L,R) and a sperm whale (Physeter macrocephalus, USNM 594183 R) were scanned with a GE Signa HDxt 3 T clinical MRI (General Electric Medical Systems, Milwaukee, WI) with a quadrature knee/ft coil (GE) at the Department of Radiology in the Howard University Hospital, Washington, D.C. Images of orbital contents of a Risso’s dolphin (Grampus griseus, USNM 594001 L), a melon-headed whale (Peponocephala electra, USNM 550008 R), and a sperm whale (USNM 594183 L) were acquired with a Bruker AVANCE III 7 T research MRI (Bruker BioSpin, Billerica, MA) using a 72 mm birdcage volume coil (Bruker Biospin) and a 90 mm quadrature volume coil (RAPID Biomedical, Rimpar, Würzburg, Germany) at the Department of Radiology, Howard University College of Medicine, Washington, D.C. Anatomic scans were acquired using T1- and T2-weighted fast spin echo sequences. Structures of the orbit in the MRI were identified and confirmed during dissection of the same specimens following the MRI scanning.

In order to visualize the fine structure of the ultrasound lesions,
ex vivo canine prostate samples were imaged with a 9.4
Tesla Bruker BioSpec 33-cm horizontal bore scanner with a Bruker 72-mm birdcage
volume coil (Billerica, MA). Samples were submerged in Fluorinert (3M Co., St.
Paul, MN) and oriented to approximately replicate the in vivoorientation for the supine canines. Imaging protocols were tested on a phantom
prior to prostate imaging. Fast low-angle shot (FLASH) tri-pilot images were
acquired in three orthogonal planes to verify correct positioning of the sample
and determine angulation of axial slices for subsequent scans. T₁W
and T₂W images were acquired, and sequences for T₁,
T₂, and ADC mapping were performed as outlined in Table 2. ADC maps were computed from
diffusion-weighted images by fitting to an exponential decay as described
above.³⁷ T₁maps were computed from variable-TR rapid acquisition with refocused echoes (VTR
RARE) images by fitting each voxel magnitude in a least squares sense to an
exponential recovery.^{43 (link)}Similarly, T₂ maps were computed from multi-slice mutli-echo (MSME)
images by fitting each voxel magnitude in a least squares sense to an
exponential decay.^{44 (link)}