Gemini tf pet ct scanner

Manufactured by Philips

Sourced in United States, Netherlands

The Gemini TF PET/CT scanner is a medical imaging device that integrates positron emission tomography (PET) and computed tomography (CT) technologies. It is designed to provide high-quality images for diagnostic and treatment planning purposes.

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Lab products found in correlation

18f flutemetamol, by GE Healthcare (1 mentions) Ingenuity tf pet ct scanner, by Philips (1 mentions) Discovery ste pet ct scanner, by GE Healthcare (1 mentions) Discovery 690 pet ct scanner, by GE Healthcare (1 mentions) Discovery pet ct 600 scanner, by GE Healthcare (1 mentions) Biography mct pet ct scanner, by Siemens (1 mentions) Mimneuro application, by MIM Software (1 mentions)

Close spelling variants of this product

Gemini TF (74 citations) Gemini TF PET/CT (31 citations) Gemini TF-64 PET/CT scanner (28 citations) GEMINI PET/CT scanner (8 citations) Gemini TF scanner (7 citations) CT scanners (6 citations) Gemini TF 16 PET/CT scanner (6 citations) PET/CT scanner (4 citations) Gemini Astonish TF 16 PET/CT scanner (4 citations) Gemini TF CT scanner (2 citations)

23 protocols using gemini tf pet ct scanner

PET/CT Halo Artifact Evaluation

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A Gemini TF PET/CT scanner (Philips Healthcare, Cleveland, OH, USA) was used for all imaging [16 (link)]. The coincidence and energy windows were used at their fixed settings of 3.8 ns and 460–665 keV, respectively. The acquisition was in three-dimensional mode only.
We conducted the patient and phantom studies to investigate the presence, rate, and underlying mechanisms of halo-artifact generation by using different scatter correction techniques as follows. (1) The frequency of halo-artifact generation was investigated using the ¹⁸F-FDG PET images with a standard scatter correction based on the TF-SSS using 4-mm voxel μ-maps (TFS 4-mm). (2) We performed phantom studies to evaluate the effects of a urine catheter and different scatter correction techniques, i.e., TF-SSS with 2-mm voxel μ-maps (TFS 2-mm) and the MC-SSS using 4-mm voxel μ-maps (MCS 4-mm). (3) We conducted an analysis of the patients’ data to determine whether the use of TFS 2-mm and/or MCS 4-mm can eliminate the artifacts in the clinical images.

Magota K., Numata N., Shinyama D., Katahata J., Munakata Y., Maniawski P.J., Kobayashi K., Manabe O., Hirata K., Tateishi U., Kudo K, & Shiga T. (2020). Halo artifacts of indwelling urinary catheter by inaccurate scatter correction in 18F-FDG PET/CT imaging: incidence, mechanism, and solutions. EJNMMI Physics, 7, 66.

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Sequential 18F-FDG and NaF PET/CT Imaging

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All patients underwent sequential ¹⁸F-FDG PET/CT and NaF PET/CT at baseline and 8 weeks post-treatment. One hour after injection with 185–370 MBq (5–10 mCi) of FDG, imaging was acquired on a Gemini TF PET/CT scanner (Philips Healthcare, Amsterdam, The Netherlands) from the base of the skull to the upper thigh. Immediately, after acquisition of the FDG PET/CT scan, patients were injected with 111–185 MBq (3–5 mCi) of NaF; 1 h after NaF injection, imaging was performed on the same PET/CT scanner from the vertex of the skull to the feet.
Low-dose CT transmission scans were obtained (120 kVp, 60 mAs, 0.75-s rotation time, 1.438 pitch, and 5-mm axial slice thickness) for attenuation correction and localization. Emission PET images were obtained at 2 min per bed position with 22 overlapping slices per bed. PET images were reconstructed using the Gemini TF default reconstruction algorithm: BLOB-OS-TF, a 3-dimensional ordered-subset iterative time-of-flight reconstruction technique using 3 iterations, 33 subsets, and 4 × 4 × 4 mm voxels. Imaging review and analysis were performed using a MIM workstation version 6.5.6 (MIM Software Inc., Cleveland, OH).

Lim I., Lindenberg M.L., Mena E., Verdini N., Shih J.H., Mayfield C., Thompson R., Lin J., Vega A., Mallek M., Cadena J., Diaz C., Mortazavi A., Knopp M., Wright C., Stein M., Pal S., Choyke P.L, & Apolo A.B. (2019). 18F-Sodium fluoride PET/CT predicts overall survival in patients with advanced genitourinary malignancies treated with cabozantinib and nivolumab with or without ipilimumab. European Journal of Nuclear Medicine and Molecular Imaging, 47(1), 178-184.

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FDG-PET/CT Brain Imaging Protocol

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A resting 18F-FDG PET/CT scan was performed after intravenous injection of ~150 MBq of FDG using a Gemini TF PET-CT scanner (Philips Medical Systems) as described elsewhere (43 (link)). The scan started 30 min after an intravenous injection of the tracer and the scan duration was 12 min. FDG-PET images for each patient were manually reoriented using SPM12. The images were then spatially normalized, smoothed (with a 14 mm FWHM Gaussian filter) and analyzed. Patient data were compared to 34 healthy control subjects (age range 19–70 years, 15 women). SPM analysis identified brain regions with decreased and relatively preserved metabolism in each patient compared to healthy control subjects (global normalization was performed by proportional scaling). The resulting set of voxel values for each contrast, constituting a statistical parametric map of the t-statistics (SPM{t}), was transformed to the unit normal distribution (SPM{Z}) and thresholded at voxel-wise p < 0.05 FWE-corrected and at p < 0.001 uncorrected.

Aubinet C., Murphy L., Bahri M.A., Larroque S.K., Cassol H., Annen J., Carrière M., Wannez S., Thibaut A., Laureys S, & Gosseries O. (2018). Brain, Behavior, and Cognitive Interplay in Disorders of Consciousness: A Multiple Case Study. Frontiers in Neurology, 9, 665.

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Optimized PET/CT Imaging Protocols

Cited 1 time

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All PET/CT scans were obtained with a Gemini TF PET/CT scanner (Philips Healthcare, Cleveland, OH, USA). Patients fasted for 6 h or more. A low-dose CT during normal breathing for attenuation correction was performed, followed by a whole-body [¹⁸F]FDG PET scan 60 min after tracer injection. Thirty minutes later, a second whole-body PET acquisition was performed. After the second PET scan, a second low-dose CT was done for attenuation correction. This procedure was repeated within 3 days of the first study. All PET data were normalised and corrected for scatter and random events, dead time, attenuation, and decay. Two reconstruction protocols were applied to the PET images. The first reconstruction followed EARL compliant guidelines for tumour imaging [22 (link)], while the second included resolution modelling with PSF [23 (link), 24 (link)] as implemented by the scanner vendor.

Kolinger G.D., Vállez García D., Kramer G.M., Frings V., Smit E.F., de Langen A.J., Dierckx R.A., Hoekstra O.S, & Boellaard R. (2019). Repeatability of [18F]FDG PET/CT total metabolic active tumour volume and total tumour burden in NSCLC patients. EJNMMI Research, 9, 14.

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PET Imaging of Amyloid and Tau Biomarkers

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¹⁸F-Flutemetamol was obtained from General Electric (GE, Risø, Denmark), and the scanning procedures have been described previously [23] (link). In brief, the patients received 196 ± 2 MBq ¹⁸F-Flutemetamol via an intravenous injection in the antecubital vein. On a separate day, a subset (n = 5) of the patients received an average of 372 ± 2 MBq ¹⁸F-AV-1451. The radiosynthesis of AV-1451 has been described previously [24] (link). The PET data were acquired on a Philips Gemini TF PET-CT scanner as 4 × 5 minute dynamic time frames, 80–100 minutes postinjection.

Hansson O., Palmqvist S., Ljung H., Cronberg T., van Westen D, & Smith R. (2018). Cerebral hypoperfusion is not associated with an increase in amyloid β pathology in middle-aged or elderly people. Alzheimer's & Dementia, 14(1), 54-61.

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Whole-Body PET/CT Phantom Study

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DIRECT reconstructions were also tested and compared using a whole-body patient study acquired on our clinical Philips Gemini TF PET/CT scanner. The subject had a BMI of 26, and 90-s scans per bed position were performed one hour post-injection of 15-mCi (555 MBq) of [F-18]-fluorodeoxyglucose. List-mode data from separately acquired 10-mm spheres scanned in air were merged with the patient’s data to create emulated lesions with a standardized uptake value (SUV) of 10. Six spheres were inserted into the liver and lung for a total of 12 emulated lesions (El Fakhri et al., 2011 (link); Surti et al., 2011 (link); Daube-Witherspoon et al., 2014 (link)). Separate reconstructions were performed for each frame, and the reconstructed images were then combined together post-reconstruction. Each acquired frame data contained on average 48M prompts, 26M delays, and a 37% scatter fraction. The axial acceptance angle of the used data was limited to ±7 degrees, limiting the number of the used prompts to about 29M per frame with approximately 8M true counts per frame. The list-mode data (prompts and delays) were deposited into histo-images, and correction data were generated using the same histo-image geometry and parameters as for the measured phantom.

Matej S., Daube-Witherspoon M.E, & Karp J.S. (2016). Analytic TOF PET reconstruction algorithm within DIRECT data partitioning framework. Physics in medicine and biology, 61(9), 3365-3386.

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PET/CT Acquisition Protocol for FDG Imaging

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PET/CT acquisitions were performed 79+/-9 [range: 59–90] minutes following intravenous injection of 3 MBq/kg of FDG. Serum glucose level was <1.4 g/L at the time of injection for all patients. All FDG-PET/CT images were acquired using a Gemini TF PET/CT scanner (Philips Medical Systems, Netherlands). The Gemini TF is a TOF-capable, fully 3-dimensional PET scanner together with a 16-slice Brilliance CT scanner. CT images were obtained without contrast media injection using the following settings: 120 KV, 100 mA, collimation 16×1.5 mm, pitch of 0.69, slice thickness of 3 mm and increment of 1.5 mm. PET images were reconstructed using a BLOB-OS-TF list-mode iterative algorithm with 2 iterations and 33 subsets. A single scatter-simulation model was used for scatter correction [11] (link) and attenuation correction was performed based on the CT. No post-reconstruction smoothing filter was used. The image voxel size was 4 mm×4 mm×4 mm for PET and 1.17 mm×1.17 mm×1.5 mm for CT. SUVs were calculated from the reconstructed activity concentration values and normalized to body weight.

Soussan M., Orlhac F., Boubaya M., Zelek L., Ziol M., Eder V, & Buvat I. (2014). Relationship between Tumor Heterogeneity Measured on FDG-PET/CT and Pathological Prognostic Factors in Invasive Breast Cancer. PLoS ONE, 9(4), e94017.

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Quantifying Cerebral Glucose Uptake via 18F-FDG-PET

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Resting 18F-FDG-PET acquisition was performed about 30 min after intravenous injection of approximately 150 MBq radioactive labeled glucose (Gemini TF PET-CT scanner, Philips Medical Systems) in order to quantify cerebral glucose uptake. A low dose CT was acquired prior the 12-min emission scan and used for attenuation correction. PET images were reconstructed using the iterative LOR RAMLA algorithm and correction for dead-time, random events and scatter were applied.
Preprocessing and statistical analysis were done in the Statistical Parametric Mapping toolbox (SPM12, www.fil.ion.ucl.ac.uk/spm) implemented in MATLAB (R2017a). Preprocessing was done as described previously (Stender et al., 2014 (link)). Briefly, images were manually reoriented according to the SPM12 FDG-PET template, spatially normalized (using a template for patients and controls) and smoothed (with a 14 mm FWHM Gaussian kernel).

Annen J., Blandiaux S., Lejeune N., Bahri M.A., Thibaut A., Cho W., Guger C., Chatelle C, & Laureys S. (2018). BCI Performance and Brain Metabolism Profile in Severely Brain-Injured Patients Without Response to Command at Bedside. Frontiers in Neuroscience, 12, 370.

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Whole-body FDG-PET/CT Imaging Protocol

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Whole-body FDG-PET scans were perfomed as described using the Philips Gemini TF PET/CT scanner (Philips Medical Systems B.V., Eindhoven, The Netherlands). Patients were prepared by a 6-h fast, as serum glucose levels had to be <150 mg/dl prior to glucose tracer administration. At 60 min after the intravenous injection of 3.7 MBq/kg (0.1 mCi/kg) ¹⁸F-FDG (Monrol, Eczacıbaşı, İstanbul, Turkey), PET/CT was performed. Subsequently, an emission scan was recorded in three-dimensional mode following CT for 2 min per position. PET and CT images were examined in the cross-sectional planes view and in the rotating maximum-intensity projection. FDG uptake in the tumor and lymph nodes were semiquantified using maximum SUV (SUVmax).

Cerci S.S., Bozkurt K.K., Eroglu H.E., Cerci C., Erdemoglu E., Bulbul P.T., Cetin M., Cetin R., Ciris I.M, & Bulbul M. (2016). Evaluation of the association between HIF-1α and HER-2 expression, hormone receptor status, Ki-67 expression, histology and tumor FDG uptake in breast cancer. Oncology Letters, 12(5), 3889-3895.

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PET-CT Imaging Protocol for [18F]FDG Uptake

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PET and low-dose CT images were performed simultaneously using Gemini TF PET-CT scanner (Phillips, Cleveland, USA). Pre- and post-treatment parameters of the imaging process were identical. Patients fastened at least 6 h before administration of [¹⁸F]FDG. Serum glucose concentration was measured right before the injection of the radiopharmaceutical. Acquisition started ca. 60 min after intravenous injection of [¹⁸F]FDG. The mean activity of the radiotracer was 3.7 MBq/kg of body weight. The scans were scattered and randomly corrected and reconstructed using OSEM reconstruction (MTX = 256 × 256). The field of view (FOV) was 18 cm with a slice thickness of 5 mm. After administration of [¹⁸F]FDG, patients were resting in a darkened room at room temperature.

Burchardt E., Bos-Liedke A., Serkowska K., Cegla P., Piotrowski A, & Malicki J. (2023). Value of [18F]FDG PET/CT radiomic parameters in the context of response to chemotherapy in advanced cervical cancer. Scientific Reports, 13, 9092.

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