Abstract: Disclosed embodiments include devices, systems, and methods for real time marker less tumor tracking (RMTT). In various embodiments, the RMTT embodiments use positron emission tomography (PET) and time of flight data to determine a 3D position of the tumor. The 3D position of the tumor may be continuously determined multiple times per section during a radiation therapy session to track the position of a moving tumor in real time. The real time tumor tracking data may be used to position a radiation source to deliver radiation directly to the tumor at all times during radiation therapy to improve the effectiveness of radiation treatments.

Abstract: A method and system for generating a hybrid positron emission tomography (PET) scanner are disclosed herein. An imaging system receives, from the hybrid PET scanner, a first set of image data of an object corresponding to high-resolution, low-sensitivity image data. The imaging system receives, from the hybrid PET scanner, a second set of image data of the object corresponding to low-resolution, high-sensitivity image data. The imaging system converts the second set of image data from low-resolution, high-sensitivity image data to high-resolution, high-sensitivity image data. The imaging system combines the high-resolution, high-sensitivity image data with the high-resolution, low-sensitivity image data. The imaging system generates an image of an object based on the combined high-resolution, high-sensitivity image data and the high-resolution, low-sensitivity image data, or high-resolution, high-sensitivity image data only.

Abstract: A three-dimensional PET detector of a type having a scintillation crystal and first and second photosensitive detectors arranged one at each opposite end face of the crystal for detecting scintillation interactions within the crystal is calibrated to determine a depth-of-interaction (DOI) function thereof by irradiating the crystal to cause a predetermined distribution of interactions along a depth axis of the crystal, and applying probability theory to signal data collected by the two photosensitive detectors. The method provides a DOI function that indicates DOI position as a function of a signal ratio R obtained from the signal data.

Abstract: Methods and systems for calibrating a positron emission tomography (PET) system are provided. The method includes determining at least one non-acquisition time period for the PET system. The method further includes automatically acquiring calibration data during the at least one non-acquisition time period.

Abstract: Methods and systems for controlling a positron emission tomography (PET) system are provided. The method includes receiving timing information from a PET system during an imaging scan using the PET system. The method further includes processing the received timing information and timing bias information relating to the PET system to control the PET system.

Abstract: A three-dimensional PET detector of a type having a scintillation crystal and first and second photosensitive detectors arranged one at each opposite end face of the crystal for detecting scintillation interactions within the crystal is calibrated to determine a depth-of-interaction (DOI) function thereof by irradiating the crystal to cause a predetermined distribution of interactions along a depth axis of the crystal, and applying probability theory to signal data collected by the two photosensitive detectors. The method provides a DOI function that indicates DOI position as a function of a signal ratio R obtained from the signal data.

Abstract: Methods and systems for controlling a positron emission tomography (PET) system are provided. The method includes receiving timing information from a PET system during an imaging scan using the PET system. The method further includes processing the received timing information and timing bias information relating to the PET system to control the PET system.

Abstract: Methods and systems for calibrating a positron emission tomography (PET) system are provided. The method includes determining at least one non-acquisition time period for the PET system. The method further includes automatically acquiring calibration data during the at least one non-acquisition time period.

Abstract: A detector includes a first position sensitive radiation detector having a first radiation sensitive area and a second radiation insensitive area. The detector further includes a first scintillator having a first decay time, located adjacent to the first radiation sensitive area and a second scintillator having a second decay time different than the first decay time, located adjacent to the second radiation insensitive area and being optically coupled to the first scintillator.

Abstract: A detector includes a first position sensitive radiation detector having a first radiation sensitive area and a second radiation insensitive area. The detector further includes a first scintillator having a first decay time, located adjacent to the first radiation sensitive area and a second scintillator having a second decay time different than the first decay time, located adjacent to the second radiation insensitive area and being optically coupled to the first scintillator.

Abstract: A detector for use in a dedicated PET scanner for cancer applications, particularly breast cancer applications, using a LSO scintillator, a lightguide coupling arrangement, and an efficient way to construct the scintillator array, which provides a flexible imaging system for breast cancer applications with high sensitivity and high spatial resolution in a compact, cost effective, design.

Abstract: A detector for use in a dedicated PET scanner for cancer applications, particularly breast cancer applications, using a LSO scintillator, a lightguide coupling arrangement, and an efficient way to construct the scintillator array, which provides a flexible imaging system for breast cancer applications with high sensitivity and high spatial resolution in a compact, cost effective, design.

Abstract: A gamma ray detection and locating system comprising an array of scintillator crystals connected to a multichannel photomultiplier tube by discrete optical fibers, each fiber connecting a single crystal to a corresponding specific location on the face of the photomultiplier tube. Also described is an improved system for identifying the location of specific electrodes in the photomultiplier tube receiving electrons generated by photons flowing from the crystal along the fiber to the tube.