Abstract: When compensating for truncated patient scan data acquired by a multi-modal PET/CT or PET/MR imaging system (14, 16), such as occurs when a patient is larger than a field of view for an anatomical imaging device, a segmented contour of a non-attenuation-corrected (NAC) PET image is used to identify a contour of the truncated region. An appropriate tissue type is used to fill in truncated regions of a truncated CT or MR image for the attenuation map. The corrected attenuation map is then used to generate an attenuation-corrected PET image of the patient or a region of interest. Alternatively, the system can be employed in PET/CT or PET/MR imaging scenarios where two modalities are performed sequentially (e.g., not simultaneously), and thus the contour derived from the PET scan can be compared to the CT or MR image to infer potential subject motion between the PET and CT or MR scans.

Abstract: A gamma ray detection system includes a plurality of detector modules having a same length, where each detector module is configured to detect gamma rays generated from positron annihilation events. A first detector module of the plurality of detector modules is shifted by a predetermined distance in an axial direction from a second detector module of the plurality of detector modules that is adjacent to the first detector module, where the predetermined distance is less than the length of the detector modules.

Abstract: A hybrid imaging system and a patient bed for same are disclosed. The hybrid imaging system includes a magnetic resonance scanner and a second modality imaging system spaced apart from the magnetic resonance scanner by a gap. In some embodiments, the gap is less than seven meters. The patient bed is disposed at least partially in the gap between the magnetic resonance scanner and the second modality imaging system, and includes a linearly translatable patient support pallet aligned to be selectively moved into an examination region of the magnetic resonance scanner for magnetic resonance imaging and into an examination region of the second modality imaging system for second modality imaging. In some embodiments, a linear translation range of the linearly translatable pallet is less than five times a length of the patient support pallet along the direction of linear translation.

Abstract: A diagnostic imaging device includes detector elements (16) for detecting ?-rays indicative of nuclear decay events. The detected ?-rays are used to produce lines of response (LORs) (46), which are time stamped (20) and stored in list mode. The LORs are reconstructed (34) into an image. An image analysis processor (38) analyzes the image for motion artifacts and iteratively adjusts an event transform processor (30) to transform selected LORs to minimize the motion artifacts. If the transformed LOR (50) does not correspond with a pair of detector elements (16), closest detector elements (52, 54) are determined. Candidate LORs (62) are created between the closest and neighboring detector elements. An event location (40) on an LOR (46) is determined from the time-of-flight (TOF) information and then transformed (47) to generate a transformed event location (48).

Abstract: A PET imaging system includes a measurement subsystem, a data acquisition subsystem, and a reconstruction subsystem. The measurement subsystem detects deflection in a patient pallet, and generates deflection information based on the detected deflection. The data acquisition subsystem receives the deflection information from the measurement subsystem and PET measurement data corresponding to a plurality of coincidence events from a PET scanner, and communicates the received deflection information and PET measurement data to the reconstruction subsystem. The reconstruction subsystem includes a processor that reconstructs a PET scan image using the deflection information and the PET measurement data communicated by the data acquisition subsystem.

Abstract: An imaging system, including (1) a CT scanner configured to scan an object arranged on a patient pallet; (2) a PET scanner, including a first detector portion, including first detector elements, arranged circumferentially around the patient pallet, the first detector portion having a predetermined axial extent and transaxially subtending less than 360 degrees with respect to a central axis of the scanner; and a second detector portion, including second detector elements, arranged separately from and opposing the first detector portion, wherein the second detector elements are of a different type than the first detector elements, and the second detector portion is configured to be movable radially and circumferentially around the object; and (3) an acquisition subsystem configured to acquire first event data from the first detector portion and to acquire second event data from the second detector portion.

Abstract: Methods, systems and apparatuses for processing data associated with nuclear medical imaging techniques are provided. Data is ordered in LUT's and memory structures. Articles of manufacture are provided for causing computers to carry out aspects of the invention. Data elements are ordered into a plurality of ordered data groups according to a spatial index order, and fetched and processed in the spatial index order. The data elements include sensitivity matrix elements, PET annihilation event data, and system and image matrix elements, the data grouped in orders corresponding to their processing. In one aspect geometric symmetry of a PET scanner FOV is used in ordering the data and processing. In one aspect a system matrix LUT comprises total number of system matrix elements equal to a total number of image matrix elements divided by a total number of possible third index values.

Abstract: A positron emission tomography (PET) scanner system, including a detector that acquires PET event information, the detector being configured to move during acquisition of the PET event information; a first motion unit that acquires first event information of a position of a patient bed, the patient bed being configured to move during acquisition of the PET event information; a second motion unit that acquires second event information of the detector; an event collector that generates an event list of events that includes the PET event information, the first event information, and the second event information; and a list-mode reconstructing unit that reconstructs an image by processing the generated event list.

Abstract: An apparatus for treating an aqueous medium containing microorganisms comprises an intake for receiving the aqueous medium containing microorganisms. A pressure differential inducer is associated to the intake so as to receive the aqueous medium containing microorganisms with a desired level of gas saturation. The pressure differential inducer is actuatable to expose the aqueous medium containing microorganisms with a desired level of gas saturation to accelerations so as to cause cell wall rupture of the microorganisms. An outlet is associated with the pressure differential inducer for outletting the treated aqueous medium containing ruptured microorganism cells and contents. The treated aqueous medium containing ruptured cell wall of the microorganisms is disposed of and/or recycled.

Abstract: A method of imaging a region of interest (ROI) in an object, the ROI having an axial extent greater than an axial FOV of a PET scanner. The method includes determining a number of overlapping scans of the PET scanner necessary to image at least the axial extent of the ROI, wherein each scan has a same axial length equal to the axial FOV, and each scan overlaps an adjacent scan by a predetermined overlap percentage of the axial length of each scan. The method includes determining a total amount of excess scanning length of the scans based on the number, the axial extent of the ROI, and the axial FOV, and determining a new overlap percentage so that a new total amount of excess scanning length is zero.

Abstract: A diagnostic imaging device includes detector elements (16) for detecting y-rays indicative of nuclear decay events. Pairs of concurrently detected ?-rays define lines of response (LORs) which are collected, time stamped, and compiled in list-mode. In tissue perfusion studies, it is beneficial to use the data that concurrently maximizes contrast and signal-to-noise ratio in the reconstructed images. Using the list-mode data, events in an adjustable temporal window (33) are reconstructed and the reconstructed images are analyzed to determine a figure of merit based on contrast and signal-to-noise properties of the image. By iteratively adjusting the temporal window, extending its start point (36) backwards in time, and repeating the reconstructing, analyzing, and adjusting steps, an image with an optimal figure of merit is obtained.

Abstract: When correcting attenuation in a nuclear image (e.g., PET or SPECT), an MR-based attenuation correction (AC) map (16) is generated using MR image data (14) of a subject (60). The subject (60) is then placed in a nuclear imaging device with a radioactive point or line source (18, 18?) from which transmission data is measured as the patient is imaged. In order to resolve ambiguity between air voxels and bone voxels in the MR-based AC map (16), estimated transmission data (24) is generated from the AC map and compared to the measured transmission data (22) from the point or line source. An error is iteratively calculated for the estimated and measured transmission data, and attenuation values of the AC map (16) are refined to minimize the error. The refined AC map (32) is used to correct attenuation in collected nuclear data (41) which is reconstructed into an attenuation corrected image (99) of the patient.

Abstract: When performing positron emission tomography (PET) scanning and image reconstruction, a primary PET system (10) with a primary PET detector array (12) is used to image a patient or subject, and a secondary PET detector array (14) is coupled to the system at specific input points to mitigate unnecessary duplication of system components. The primary system (10) provides PET data processing and reconstruction for the secondary array (14), in addition to the first array (12). An adjustable array (120) includes radially movable detectors (122) and stationary detectors (124) with different crystal resolutions. The movable detectors (122) are alternately positioned with the stationary detectors (124) at a first radius to form a large detector ring, or are positioned at a second, smaller radius without the stationary detectors (124) to form a small detector ring.

Abstract: An apparatus includes a scanner (102, 104) and a scanning motion monitor (100). A motion modeler (116) uses data from the scanning motion monitor (100) and the scanner (102, 104) to generate a motion model which describes motion of a region of interest of an object. A treatment planner (112) uses image data from the scanner (102, 104) to establish a treatment plan for the object. A treatment device 114, which operates in conjunction with a treatment motion monitor (108), uses the motion model to compensate for motion of the object during application of the treatment.

Abstract: A digital photosensor that includes a photomultiplier tube (PMT) including a power distribution circuit, the PMT outputting an analog signal in response to received light; an analog-to-digital converter (ADC) to receive the analog signal and to generate a digital signal; and a non-transitory memory storing manufacturing parameters of the PMT and operational parameters of the PMT, the operational parameters being calculated by a parameter calculation unit during operation of the PMT, wherein the PMT, the ADC, and the memory are integrated into a single housing

Abstract: A positron emission tomography (PET) detector module includes an array of scintillation crystal elements and a plurality of photosensors arranged to at least partially cover the array of scintillation crystal elements. The photosensors are configured to receive light emitted from the array of scintillation crystal elements. The module includes a transparent adhesive arranged between the array of scintillation crystal elements and the plurality of photosensors. The transparent adhesive extends directly from a surface of at least one of the scintillation crystal elements to a surface of at least one of the photosensors and is configured to distribute the light emitted from one of the scintillation crystal elements to more than one of the photosensors. A method of manufacturing the module includes various steps utilizing a fixture. A PET scanner uses multiple modules arranged circumferentially around an area to be scanned.

Abstract: A digital photosensor that includes a photomultiplier tube (PMT) including a power distribution circuit, the PMT outputting an analog signal in response to received light; an analog-to-digital converter (ADC) to receive the analog signal and to generate a digital signal; and a non-transitory memory storing manufacturing parameters of the PMT and operational parameters of the PMT, the operational parameters being calculated by a parameter calculation unit during operation of the PMT, wherein the PMT, the ADC, and the memory are integrated into a single housing.

Abstract: A positron emission tomography scanner system that includes detector modules arranged adjacent to one another to form a cylindrical detector ring. Each of the detector modules includes an array of scintillation crystal elements, a plurality of photosensors arranged to cover the array of crystal elements and configured to receive light emitted from the array of crystal elements, and a fiber optics plate arranged between the array of scintillation crystal elements and the plurality of photosensors, the fiber optics plate including a plurality of fibers configured to guide the light emitted from the scintillation crystal to the plurality of photosensors.

Abstract: A positron emission tomography scanner system that includes detector modules arranged adjacent to one another to form a cylindrical detector ring. Each of the detector modules includes an array of scintillation crystal elements, a plurality of photosensors arranged to cover the array of crystal elements and configured to receive light emitted from the array of crystal elements, and a fiber optics plate arranged between the array of scintillation crystal elements and the plurality of photosensors, the fiber optics plate including a plurality of fibers configured to guide the light emitted from the scintillation crystal to the plurality of photosensors.

Abstract: When employing hygroscopic scintillation crystals (32) in a nuclear detector (e.g., PET or SPECT), Silicon photo-multiplier (SiPM) sensors (34) are coupled to each scintillation crystal (32) to improve scintillation event detection and reduce scatter. The crystals (32) and sensors (34) are hermetically sealed in a detector housing (50) using a sealant layer (51). Electrical contacts (60) from each sensor (34) extend through the sealant layer (51) or are bused together such that the bus extends through the sealant layer (51). In this manner, hygroscopic scintillation crystals (e.g., LaBr, NaI, etc.) are protected from humidity and light scatter is reduced by direct coupling of the sensors (34) and crystals (32).