The purpose of the study is to evaluate the physical performance of a Biograph mCT Flow R PET/CT system (Siemens Healthcare, Germany) and to. to fundamentally change how PET imaging is performed. Powered by Siemens’ revolutionary FlowMotion™ technology,. Biograph mCT Flow™ is the world’s first. Biograph mCT Flow with FlowMotion™ technology combines our standard- setting PET/CT with a unique system design that enables continuous motion of.
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The elevated background variability is assumed to be caused by the choice of the table speed and the data processing techniques specific to CTM acquisitions. Mean standardized uptake values SUVs mean and coefficient of variations CVs were calculated for spherical volumes of interest VOI with 3-cm diameter placed in the liver and the bladder.
This technique was proposed by Dahlbom and colleges in [ 13 ] and integrated in a first PET-only system in [ 14 ]. System true event rate, random event rate, scatter event rate, NECR, and the scatter fraction are reported.
No attenuation and scatter correction and no post-smoothing filter were applied. The most significant difference between both standards is the change of the positions of the point source for spatial resolution measurements. This relationship was modeled from an empirical logarithmic relationship. PET technical and clinical advances with FlowMotion technology. Discussion Our data indicate a similar performance of the PET components of the mCT Flow and its predecessor system, the mCT [ 6 ] with the residual differences being discussed below.
However, this study was performed on a different system with an axial FOV biogralh Mcy axial end slices first and last slice were excluded from the analysis. In addition, a scan of the same region in CTM mode was performed with a table speed of 0.
The bladder was chosen to test for this issue as it contains a uniform activity concentration and therefore similar to the background compartment in the IQ phantom. Sensitivity measurements were based on a cm-long polyethylene tube, filled with 4. For resolution measurements, an 18 F point source inside a glass capillary tube was used.
Data were reconstructed with an ordered-subset expectation maximization OSEM [ 25 ] 3D iterative algorithm, using 2 iterations i and 24 subsets biogrraphand additionally with 2 iterations and 21 subsets applying PSF correction and TOF. Image quality results for 4: Resolution modeling in PET imaging: Received Jun 15; Accepted Oct The remaining two largest spheres were filled with non-radioactive water. No visual difference in biogra;h PET image quality was observed by two experienced imaging experts.
The CRCs were mc in both acquisition modes. The reconstructions of the transaxial sections through the center of the spheres within the image quality phantom for SS and CTM mode are shown in Fig. Seminars in Nuclear Medicine. Also, advanced acquisition protocols like described by Karakatsanis et al.
The expected value of the true count rate is gained by a fit through all data below the peak NECR standard as opposed to the extrapolated values from the last three acquisitions standard.
For this acquisition protocol, planning and scanning are restricted by the fixed size of the detector array. The corrected true coincidence count rate was recorded as a function of sleeve thickness and extrapolated to a zero thickness sleeve.
All data were corrected for random coincidences, normalization, dead time losses, scatter, and attenuation. The CTM acquisition followed the sequential subsequently.
Based on the results of Armstrong [ 25 ], this difference would increase for the smaller spheres when TOF was included into the reconstruction algorithm. Furthermore, no relevant difference of the SUV mean of the liver as reference organ could be observed, and the comparison of the CVs of the liver showed no clinical relevant differences.
This can be used to optimize the protocols, e.
Biograph mCT 20 Excel
Thus, users may opt for applying PSF and other geometric corrections to the data, which inevitable makes inter-system comparisons more difficult. NEMA NU measurements All measurements were performed at the site of the clinical installation of the system between August and December Nevertheless, Brasse et al.
Biofraph measurements were performed at the center biograpn the FOV and at cm radial offset. All measurements were performed at the site of the clinical installation of the system between August and December Effect of scan time on oncologic lesion detection in whole-body PET. Table 3 Image quality results for 4: These settings were selected to cover the same axial FOV in the same time as performed with the IQ phantom measurements.
The axial sensitivity profiles with the line source placed at the center of the FOV and cm radial offset are shown in Fig. The patient handling system PHS contains a horizontal magnetic drive system that enables a continuous table motion with a positioning accuracy biogrxph less than 0.
Biograph mCT Flow – Siemens Healthineers USA
For the measurements for the sensitivity, the count rate performance, and the associated relative count rate error, a provision was made in NEMA NU for elevating the phantoms, if the vertical range of the patient biograpb is insufficient for the required placement of the phantoms. The count rate error evaluation was also slightly modified in the standard.
In a study by Tong et al. Concept, acquisition hiograph optimization and clinical application. Nonetheless, increased noise was observed in the images acquired in SS mode Fig.
Within the SS protocol, the table is in a fixed position during an acquisition of data in the FOV and subsequently moves to the next position to acquire data of an axial range greater than the axial FOV of the system.