Aw volume share 5

The 64-slice multidetector-row computed tomography (MDCT) scanner generates 0.75 mm image slices that can be reconstructed into 1.0 mm image data. Image processing analysis was performed using a 3D volume rendering (VR) technique with the Extended Brilliance Workspace (EBW) software. The MIP images were evaluated using VITAL Image Management System (VIMS, Vitrea^® 2). The selected VR image (based on small-vessel extraction technology) was evaluated using AW VolumeShare 5, GE Medical Systems.

Postprocessing of the MRI data was interactively performed using the integrated registration function of a standard workstation (AW VolumeShare 5; GE Healthcare, Waukesha, WI, USA). Slabs of 18 mm thickness were generated by maximum intensity projection (MIP) of Volume-T1 with 3D PC-MRA or CE-MRA. A total of 40 facial arteries of 20 anonymized patients were evaluated using 3D PC-MRA and CE-MRA. Further, MRA diagnosis and image quality for the visualization of facial arteries were assessed by two board-certified radiologists with 11- and 7-year experience in evaluating MRA images, respectively, who were blinded to patient information and imaging technique. The radiologists rated the diagnostic and image qualities of facial arteries using a four-point scale: 0 = poor quality of facial arteries with nondiagnostic quality (Fig. 1a); 1 = questionable or partial visualization of facial arteries with nondiagnostic quality (Fig. 1b); 2 = partial visualization of facial arteries with diagnostic quality (Fig. 1c); and 3 = good to excellent image with diagnostic quality (Fig. 1d).Fig. 1

Examples of the image quality of 3D phase contrast magnetic resonance angiography (3D PC-MRA) to visualize the facial artery courses based on four-point score.0 = poor (a); 1 = questionable (b); 2 = adequate (c); and 3 = good (d). Green arrows indicate the facial artery course

A whole-body PET/CT system with time-of-flight capability (Discovery 690; GE
Healthcare, Waukesha, WI, USA) was used for the ¹⁸F-FDG-PET/CT
acquisition. The patients were instructed to fast for at least six hours and
were required to have a blood glucose level ≤ 180 mg/dL before injection
of the ¹⁸FDG (≤ 3.7 MBq/kg of body weight). Image acquisition
was initiated approximately 60 min after injection of the radiotracer, and
images were acquired from the mid-skull to the mid-thigh. The metabolic activity
at the primary tumor site, before and after nCRT, was recorded by using the
following parameters: SUV_max, SUV_mean, TLG, and MTV. Those
values were calculated by a single nuclear medicine physician using a radiology
workstation (AW VolumeShare 5; GE Healthcare). The SUV thresholds used in order
to define the boundaries of the lesions were established by visual analysis. The
total volume of interest that circumscribed the metabolic area was calculated
automatically by the dedicated software.

Before the PET/CT test, the rats and nude mice were fasted for 8 h and were water‐free for 4 h. Following isoflurane inhalation anaesthesia, each rat and nude mouse was injected intraperitoneally with 18F‐FDG 4.2 MBq/kg and then fixed in the prone position on the micro‐positron emission tomography (PET)/computed tomography (CT) scanning bed (Discovery 690/Elite; GE Healthcare), using AW Volume Share 5 software (France) to collect static images for 20 min. The scanning parameters were as follows: Voltage, 120 kV; current, 260 μA; pitch, 0.561; rotation speed, 0.5 s/cycle; layer thickness, 3.75 mm; interval, 3.75 mm; matrix 512 × 512; FOV, 50 × 50 cm; subsequent PET scan; parameters for each rat or a nude mouse scans two beds, each bed is collected for 2.5 min. CT was used for attenuation correction and iterative reconstruction to obtain 47 frames of PET cross‐sectional images. The CT and PET image data were transferred to the AW Volume Share 5 workstation, and the coronal, sagittal, cross‐sectional and three‐dimensional CT and PET scans and their fusion images were obtained. Two PET/CT rapporteurs read the PET/CT images using double‐blind method, the tumour and normal tissue ROI was delineated, and the SUVmax was measured.

A preoperative MRI was performed with a Siemens Trio 3.0T scanner using a 32-channel brain coil. The technical protocol was T2 FSE coronal (TR/TE 7520/114 ms, in-plane resolution 0.5 × 0.4 mm, slice thickness 3 mm), 3D T1 mp2rage (T/RTE 5000/2.89, in-plane resolution 1 × 1 mm, slice thickness 1 mm), DTI (TR/TE 8000/84, in-plane resolution 2 × 2 mm, slice thickness 2 mm, 30 diffusion directions), and 3D FLAIR (TR/TE 5000/419, in-plane resolution 0.9 × 0.9 mm, slice thickness 0.9 mm).
Postoperative CT was performed with a Siemens Somatom Definition Flash (Siemens, Erlangen, Germany). Slice thickness was 1.25 mm.
Preoperative high-resolution 3D sequences obtained at 3T and postoperative CT series were fused using commercially available software (Integrated Registration, AW Volume Share 5, GE Healthcare). Maximum intensity projections (MIP), multi-planar reformatting (MPR) and volume rendering (VR) were performed for better localization of the electrodes. Fused images illustrated location of microelectrode arrays (not performed for patient H3, H6 and H7 Supplementary Figure S1, Table 2).