Various methods and systems are provided for computed tomography imaging. In one embodiment, a method includes acquiring, with an x-ray detector and an x-ray source coupled to a gantry, a three-dimensional image volume of a subject while the subject moves through a bore of the gantry and the gantry rotates the x-ray detector and the x-ray source around the subject, inputting the three-dimensional image volume to a trained deep neural network to generate a corrected three-dimensional image volume with a reduction in aliasing artifacts present in the three-dimensional image volume, and outputting the corrected three-dimensional image volume. In this way, aliasing artifacts caused by sub-sampling may be removed from computed tomography images while preserving details, texture, and sharpness in the computed tomography images.

The disclosure is directed to a device that includes a cavity formed by a plurality of rails, the plurality of rails connected to both a first support and a second support, each at predetermined intervals about a circumference of the first support and the second support; and at least one particle detection device operably connected to each rail of the plurality of rails. The disclosure is also directed to a scanner that includes the device, and a processor.

A method for adaptive coincidence data processing is provided. The method includes detecting positron annihilation events with a detector array of a positron emission tomography (PET) scanner, wherein the PET scanner includes multiple detector rings disposed along a longitudinal axis of the PET scanner, and each detector ring includes multiple detectors. The method also includes, within a given time period, dynamically adjusting a number of positron annihilation events accepted and transmitted to acquisition circuitry for processing utilizing a numerical difference in detector rings along the longitudinal axis between a first detector and a second detector detecting respective annihilation photons from a positron annihilation event.

Gamma ray detection system comprising a detection module assembly including at least two detection modules configured for positron emission tomography (PET) scanning of a target zone, each detection module comprising a plurality of stacked scintillator plates each having a major surface oriented to generally face the target zone and lateral minor surfaces defining edges of the scintillator plates, a plurality of photon sensors being mounted against said edges layer photon sensor 18a configured to detect a scintillation event in the scintillator plate from a gamma ray incident on the major surface. The gamma ray detection system is further configured to function as a Compton camera, at least one scintillator plate that is not the scintillator plate closest to the target zone being configured as an absorber scintillator plate for said Compton camera.

A method for compensating motion in positron emission tomographic, PET, data comprising coincident lines of response from positron-emitting position markers, includes: detecting a slippage of one or more of the position markers; determining slippage correction parameters based on the detected slippage; and applying motion correction to the PET data by taking into account the slippage correction parameters, thereby obtaining a motion-compensated PET data.

Described herein are systems and methods for positioning a radiation source with respect to one or more regions of interest in a coordinate system. Such systems and methods may be used in emission guided radiation therapy (EGRT) for the localized delivery of radiation to one or more patient tumor regions. These systems comprise a gantry movable about a patient area, where a plurality of positron emission detectors, a radiation source are arranged movably on the gantry, and a controller. The controller is configured to identify a coincident positron annihilation emission path and to position the radiation source to apply a radiation beam along the identified emission path. The systems and methods described herein can be used alone or in conjunction with surgery, chemotherapy, and/or brachytherapy for the treatment of tumors.

A diagnostic imaging system utilizing a reduced crystal design pattern is utilized to image a subject and collect event data. The reduced crystal design pattern includes filled crystal locations and empty crystal locations. A processor accounts for empty crystal locations by selecting windows that include nearest neighbor filled crystal locations. The nearest neighbor filled crystal locations include event data which is averaged by the processor and assigned to the empty crystal location. A weighted average based on distance or event strength is incorporated.

A channel multiplexing method for reading array detector signals includes: dividing array detectors into M groups, at least two detectors being in each group; array coding the read channel to read M row signals and N column signals, which means when a signal is outputted at the detector in row a, column b, the signals of row a and column b are outputted correspondingly; connecting the readout signals of-the row and the column to different positions of two transmission lines respectively; determining the source row number and column number of the signal on the basis of the time difference between the time of signal reaching two ends of the transmission line, and marking the source detector from which the signal is generated on the basis of two time differences of the row signal and the column signal.

A combined scintillation crystal includes: at least one scintillation crystal A module and a scintillation crystal B module. The scintillation crystal A module and the scintillation crystal B module are scintillation crystal modules with different performances. The scintillation crystal A module comprises at least one scintillation crystal A, and the scintillation crystal B module comprises at least one scintillation crystal B. The sensitivity of the scintillation crystal A is lower than the sensitivity of the scintillation crystal B, and the light output ability of the scintillation crystal A is higher than the light output ability of the scintillation crystal B. The scintillation crystal B module includes a ray incidence plane for receiving rays, and the at least one scintillation crystal module A is arranged at the outer side of the ray incidence plane of the scintillation crystal B module.

Multiple interactions, such as Compton scattering, inside a PET detector are used to predict an incident photon's direction for identifying true coincidence events versus scatter/random coincidence events by creating a cone shaped shell projection defining a range of possible flight directions for the incident photon. The disclosed techniques can be used as prior information to improve the image reconstruction process. The disclosed techniques can be implemented in a LYSO/SiPM-based layer stacked detector, which can precisely register multiple interactions' 3D position.