23 results about "Pet scanner" patented technology

A PET scanner includes gamma-ray detector rings that form a bore through which an imaging subject is translated, a length of the bore defining an axial length of the PET scanner, the gamma-ray detector rings being movable along the axial length, the gamma-ray detector rings including gamma-ray detector modules therein, and processing circuitry configured to receive PET data associated with a plurality of transaxial slices of the imaging subject, the PET data including a first set of spatial information and timing information corresponding to a first data acquisition period for the gamma-ray detector modules in a first axial position and a second set of spatial information and timing information corresponding to a second data acquisition period for the gamma-ray detector modules in a second axial position, and reconstruct a PET image based on the first set of spatial and timing information and the second set of spatial and timing information.

A positron emission tomography (PET) scanner is provided having a plurality of detector subsystems, including processing circuitry to determine, for each detector subsystem of the plurality of detector subsystems, a singles count loss correction factor of the detector subsystem; determine, for each detector subsystem pair of a plurality of pairs of the detector subsystems, a coincidence count loss correction factor for the detector subsystem pair; calculate a scanner coincidence count loss correction factor for the PET scanner based on the coincidence count loss correction factors determined for the plurality of pairs of the detector subsystems; and reconstruct an image based on the calculated scanner count loss correction factor and scan data acquired from a scan of a patient performed using the PET scanner.

A PET scanner system is provided having a PET scanner gantry configured to deliver uniformly distributed cooling air to a plurality of detectors housed therein. The PET scanner gantry includes a cooling air delivery manifold comprising: a patient tunnel portion; and a front funnel portion. The front funnel portion includes an annular inner wall defining an inlet opening for the patient tunnel portion; and a plenum having an annular structure for carrying a flow of pressurized cooling air received from a remote source, supplementing the pressurized cooling air with an ambient air supply, and directing the pressurized cooling air to the plurality of detectors.

A method for determining a convolution kernel for an iterative statistical algorithm based on a continuous-to-continuous data model. The method is used for image reconstruction from radiation measurements obtained in emission tomography, specifically in a Time-of-Flight Positron Emission Tomography (TOF PET) scanner. The presented method is a non-list-mode solution that reduces the computational complexity of the reconstruction problem, improves the resolution of reconstructed images, reduces the radiation dose absorbed by patients during TOF PET examinations, and / or shortens the measurement acquisition time without significantly compromising the quality of the diagnostic images. Notably, the quality of the functional images remains at the same level. These improvements are achieved by designing the convolution kernel to account for the statistical properties of the measurement signals registered during the TOF PET scanner's acquisition process.

A novel method is disclosed for obtaining transmission scan data in a PET scanner by incorporating one or more stationary gamma ray sources that provide forward scattered gamma photons that can be used as transmission imaging radiation.

The application relates to the technical field of image processing, and discloses a PET image enhancement method and device, computer equipment and a storage medium. The method comprises the following steps: acquiring a PET image to be reconstructed and measurement data, wherein the measurement data refers to sinogram data formed after signal data collected by a PET scanner is subjected to attenuation and scattering correction; and finally, based on the PET image, the sinogram data, a trained convolutional neural network and an EM fidelity algorithm, the PET image is reconstructed to obtain a target PET image. According to the application, a convolutional neural network for denoising is first trained based on a diffusion model theory on a high-quality (a high-quality PET image of a conventional dose) image, and then based on the trained model, high-quality image reconstruction is performed under the guidance of the PET image to be reconstructed and an EM fidelity algorithm.

A method and a system for limiting coincidence data includes detecting a plurality of coincidence events during a scan of a subject with a detector array of a positron emission tomography (PET) scanner, wherein the PET scanner includes a plurality of detector rings disposed along a longitudinal axis of the PET scanner, and each detector ring includes a plurality of detectors. The method also includes limiting data associated with the plurality of coincidence events from the scan so that the data varies in a radial extent relative to a center of a field of view of the scan.

The disclosure relates to a device and positron emission tomography (PET) scanner for acquiring a PET image and a system for generating the PET image. The disclosure describes a device that may have one or more moveable portions. The device may comprise an upper portion and a lower portion. The upper portion and lower portion define a cavity for a patient. At least one of the upper portion or the lower portion may be movable. The upper and lower portions may comprise a cap and wings, respectively, At least one of the caps and / or wings may comprise one or more detection modules. The wings may also move with respect to a corresponding cap.

Systems, methods, and devices provide data correction for positron emission tomography (PET) examinations using an external, supplemental radioactive source. The supplemental radioactive source is formed of a uniformly distributed radionuclide. The uniformly distributed radionuclide is positioned in a support structure which is positioned into an inner bore of a PET scanner and secured in place by a friction fit, or directly integrated into the PET system. A transmission source control system moves the one or more 2024 / 059537 transmission sources into the support structure for performing the PET examination (e.g., using a hydraulic system). The transmission source control system also retracts the one or more transmission sources back into a source storage device upon completing the PET examination. Various data correction algorithms use the first PET signal data, originating from a radiotracer injected in the patient, and second PET signal data, originating from the uniformly distributed radionuclide.

The present disclosure relates to reconstructing positron emission tomography (PET) images. The approach may involve receiving measured sinogram data from one or more scans by a PET scanner. The measured sinogram data may represent measured projections from the PET scanner. The approach may involve performing forward rendering to generate a rendered sinogram. Forward rendering may comprise sampling a number of positions corresponding to each crystal detector in a plurality of crystal detectors. The positions may define lines of response (LORs) between crystal pairs. The approach may involve performing inverse rendering based on the measured sinogram data and the rendered sinogram. Inverse rendering may comprise applying auto-differentiation for gradient-based optimization. The rendering may be performed iteratively to update pixel values of an emission image until a stopping criterion. A reconstructed PET image based on the updated emission image may be output following the stopping criterion being satisfied.

The present disclosure relates to a device for use in a PET scanner, comprising a base configured to be worn around a head of a subject, wherein the base comprises three or more radioactive point sources which are non-pure positron emitters which simultaneously emit a positron that annihilates into two back-to-back gamma photons with 511 keV and into an additional gamma photon of different energy. The present disclosure further relates to a controller for a PET scanner configured to receive data from one or more photon detectors, and to determine positions of the radioactive point sources based on the sensor events. The present disclosure further relates to a PET scanner, to methods for monitoring movements of a head of a subject in a PET scanner and to methods for scanning a brain of a subject.

A method for determining a convolution kernel for an iterative statistical algorithm based on a continuous-to-continuous data model for image reconstruction from radiation measurements obtained in emission tomography, specifically in a Positron Emission Tomography (PET) scanner. The method improves the resolution of reconstructed images, reduces the radiation dose absorbed by patients during PET examinations, and / or shortens the measurement acquisition time without significant loss in the quality of the diagnostic images obtained. Specifically, the quality of the functional images remains at the same level. These improvements are achieved through the design of the convolution kernel, which takes into account the statistical properties of the measurement signals registered during the acquisition process in the PET scanner.

The application relates to a sensor data processing module including a plurality of integrated circuit devices each configured to receive and process sensor data, in particular sensor data from a PET scanner, at least some of the integrated circuit devices each comprising: at least one data input for receiving measurement data from at least one sensor; at least one data input for receiving a plurality of sensor events from at least one other integrated circuit device, wherein each sensor event comprises at least a time information and an event information; and at least one data output for sending one or more sensor events; wherein the integrated circuit devices each comprise one or more FIFO buffers for temporarily storing one or more sensor events and the integrated circuit devices are each configured: to create one or more sensor events from the measurement data, wherein each sensor event comprises at least a time information and an event information; and to process the sensor events queued in the one or more FIFO buffers by sorting the sensor events located at the front of the queues at least based on the time information; and wherein at least two of the plurality of integrated circuit devices are connected such that the data output of one integrated circuit device is connected to the data input of at least one other integrated circuit device.

Systems and methods for estimating mean randomness include: acquiring list pattern data describing true and delayed coincidences detected by a positron emission tomography (PET) scanner during a scan of an object; determining, based on the list pattern data, delayed coincidences including said crystals for each crystal of the PET scanner and for each of a plurality of time periods of the scan; for each crystal, determining a single event rate associated with each time period based on the delayed coincidences determined for the crystal within the time period; for each time period, determining an estimated mean randomness for each of a plurality of crystal pairs based on the single event rate associated with the time period for each crystal of the crystal pair; and reconstructing an image of the object based on the estimated mean randomness for each time period and the detected true coincidences.

Various systems and computer-implemented methods for background radiation-based attenuation correction are disclosed. First set of nuclear scan data and first background radiation data are received, the first set of nuclear scan data including first scan data associated with a first imaging modality having a long axis field of view, and a first background radiation attenuation map is generated by applying a trained machine learning model to the first background radiation data. First set of attenuation corrected scan data is generated by performing attenuation correction of the first scan data based on only the first background radiation attenuation map, and a first image is reconstructed from the first set of attenuation corrected scan data. The disclosed background radiation-based attenuation correction can be used for longer duration scans, repeated scans, and / or low dose clinical applications, such as pediatric applications, theranostics, and / or other suitable applications.

A PET imaging system includes BGO crystals that generate Cherenkov photons in response to excitation by photons from positron annihilation events and photosensors configured to detect the Cherenkov photons and generate signals indicative thereof, an LOR determiner configured to identify, based on the signals, coincident photon pairs along each LOR, a TOF determiner configured to determine a timing resolution for each of the coincident photon pair along each LOR, an accuracy determiner configured to bin the LORs, based on the timing resolutions, into at least higher accuracy TOF LORs and lower accuracy TOF LORs, a reconstructor configured to reconstruct the higher accuracy TOF LORs using models and generate volumetric image data, and a model adjuster configured to adjust at least one model of the models based on the volumetric image data. The reconstructor is configured to reconstruct at least a subset of the LORs using the updated models.

This invention belongs to the field of nuclear medicine imaging technology, specifically relating to a PET myocardial blood flow quantitative optimization method, including the following steps: determining the shortest effective acquisition time: for specific types of research subjects and pathophysiological states, the injection time is determined through experimental analysis. 18 After F-Flurpiridaz, the shortest effective acquisition time required to achieve stable myocardial blood flow (MBF) quantification is achieved; an optimized acquisition protocol is implemented; image reconstruction and MBF quantification are performed based on the optimized acquisition time; results are verified and reported. This invention significantly improves scanning and quantification efficiency: by shortening the effective acquisition time by 2-7 minutes, the occupancy time of the PET scanner can be substantially reduced while ensuring data quality, increasing equipment turnover and enabling more subjects to be examined within the same time period.

Provided is a medical imaging scanner system such as a PET scanner system having a patient bed pallet that is provided with at least one multi-axis motion sensor for monitoring the movement of the patient bed pallet and detecting any deviation in the orientation of the patient bed pallet from a predetermined desired orientation during the movement.

A device for the detection of gamma rays to be used primarily in a PET scanner is based on a scintillator heterostructure combining the high stopping power of scintillators commonly used in PET scanners (such as L(Y)SO, BGO, etc.) and fast scintillators based on polymers loaded with fast emitting dyes or nanocrystals, or thin layers of nanocrystals or multiple quantum well structures. While the metascintillator block is read out in the monolithic or semi-monolithic arrangement, the fast scintillator is segmented so that it is read out by less photodetectors. The particular arrangement of this detector module allows combining all the important features of a high-performance Time-of-Flight PET (TOFPET) detector module, i.e. a high photoelectric detection efficiency for the gamma rays, a precise 3D information (including the depth of interaction DOI) of the gamma ray conversion in the module, good energy resolution and superior timing resolution.

To provide a PET detector system that overcomes defects and is cost-efficient.SOLUTION: This disclosure relates to a device including a cavity formed by a plurality of rails, the plurality of rails being connected at predetermined intervals around a first support and a second support, and at least one particle detection device being operably connected to each rail of the plurality of rails. This disclosure also relates to a scanner including the device and a processor.SELECTED DRAWING: Figure 1

The present disclosure relates to a device for use in a PET scanner, comprising a base configured to be worn around a head of a subject, wherein the base comprises three or more radioactive point sources which are non-pure positron emitters which simultaneously emit a positron that annihilates into two back-to-back gamma photons with 511 keV and into an additional gamma photon of different energy. The present disclosure further relates to a controller for a PET scanner configured to receive data from one or more photon detectors, and to determine positions of the radioactive point sources based on the sensor events. The present disclosure further relates to a PET scanner, to methods for monitoring movements of a head of a subject in a PET scanner and to methods for scanning a brain of a subject.

A method for improving a quality of a transmission scan signal from forward scattered gamma-photons within a positron emission tomography (PET) scanner's field of view (FOV) by applying time-of-flight (TOF) consideration to a transmission imaging scan using stationary gamma-ray sources (130) comprised of the PET scanner (200), the PET scanner (200) further comprises a PET detector ring assembly (100) within a gantry (210), and a patient tunnel (T), wherein the gamma-ray sources (130) are positioned behind the PET detector ring assembly (100) away from the patient tunnel (T) and between a pair of the detector electronic assemblies (110), the method comprises: (a) calculating (410) the TOF for scattered photons, which are photons from the gamma-ray sources (130) that have undergone Compton scatter in a first scintillator crystal in a first detector block (214a), to reach a second scintillator crystal in a second detector block (214b), based on a distance between the two scintillator crystals (214a, 214b); (b) defining (420) a time window, where the time window has a width centered around the calculated TOF; (c) measuring (430) TOF of actual scattered gamma-photons (12) originating from the first scintillator crystal with a scan target object in the PET scanner's FOV; (d) comparing (440) the measured TOF from (c) against the calculated TOF to identify the measured TOF that are within the time window; and (e) identifying (450) the forward scattered gamma-photons corresponding to those measured TOF that are within the time window as transmission source events originating from the Compton scattering in the first scintillator crystal, thereby discriminating a transmission type data from gamma emitting annihilation events within the scan target object and random events.

An apparatus for reconstructing a positron emission tomography (PET) image, comprising processing circuitry configured to extract, from raw data obtained from a PET scanner, energy data and timing data associated with a plurality of annihilation events, the extracted energy data and the extracted timing data for each annihilation event corresponding to interactions between each of a pair of gamma rays generated by each annihilation event and one or more gamma ray detectors of the PET scanner, classify each annihilation event based on respective extracted energy data and respective extracted timing data, determine, for each annihilation event and based on a calculated timing resolution of the annihilation event, a width of a time-of-flight kernel, and reconstruct, by processing circuitry, the PET image based on the obtained raw data from the PET scanner and the determined width of the time-of-flight kernel associated with each annihilation event.