A radiation detector (16) having a first detector layer (24) and a second detector layer (26) encircles an examination region (14). Detectors of the first layer include scintillators (72) and light detectors (74), such as avalanche photodiodes. The detectors of the second detector layer (26) include scintillators (62) and optical detectors (64). The scintillators (72) of the first layer have a smaller cross-section than the scintillators (62) of the second layers. A group, e.g., nine, of the first layer scintillators (72) overlay each second group scintillator (62). In a CT mode, detectors of the first layer detect transmission radiation to generate a CT image with a relatively high resolution and the detectors of the second layer detect PET or SPECT radiation to generate nuclear data for reconstruction into a lower resolution emission image. Because the detectors of the first and second layers are aligned, the transmission and emission images are inherently aligned.

A detector ring has a first unit and a second unit that are rotatably movable and an auxiliary unit movable in a central axis direction. The auxiliary unit is moved in the central axis direction relative to the units. The detector ring forms into a C shape to form a clearance. Subsequently, the first unit and the second unit are rotatably moved to move the clearance of the detector ring to a position distant from a support member. A patient can be introduced from the clearance. The detector ring is returned to an annular shape in the reverse sequence of the above one with the patient introduced. A annihilation radiation pairs can be detected from all directions to take a tomographic image, and a functional image with higher image quality than that of a conventional configuration can be obtained.

A PET detecting module may include a scintillator array configured to receive a radiation ray and generate optical signals in response to the received radiation ray. The scintillator array may have a plurality of rows of scintillators arranged in a first direction and a plurality of columns of scintillators arranged in a second direction. A first group of light guides may be arranged on a top surface of the scintillator array along the first direction. The light guide count of the first group of light guides may, be less than the row count of the plurality of rows of scintillators. A second group of light guides may be arranged on a bottom surface of the scintillator array. The light guide count of the second group of light guides may be less than the column count of the plurality of columns of scintillators.

A PET detecting device may include a plurality of detection modules and a processing engine. Each of the plurality of detection modules may include a scintillator array, one or more photoelectric converters, one or more energy information determination circuits and a time information determination circuit. The scintillator array may interact with a plurality of photons at respective interaction points to generate a plurality of optical signals. The one or more photoelectric converters may convert the plurality of optical signals to one or more electric signals that each include an energy signal and a time signal. The one or more energy information determination circuits may generate energy information based on the one or more energy signals. The time information determination circuit may generate time information based on the one or more time signals. The processing engine may generate an image based on the energy information and the time information.

A system and method for the measurement of radiation emitted from an in-vivo administered radioactive analyte is presented. Gamma radiation sensors may be used to determine the proper or improper administration of a radioactive analyte. In some cases, the system utilizes computer program code executable by a computer processor that performs the steps of receiving signal data, accessing reference data, and comparing the signal data to the reference data to determine a likelihood of improper administration of the radioactive analyte to the subject.

Described is a directional gamma detector including a detection probe and a handgrip, wherein the detection probe includes: a supporting rod and a detection head coupled or integrated with a first end of the supporting rod. The detection head includes a plurality of detection elements distinct from each other for simultaneously detecting gamma rays directed in different directions and including at least one scintillation crystal and a corresponding first electronic conversion circuitry. Each detection element is associated with a respective collimator. The handgrip is equipped internally with a second electronic circuitry for converting the signals. The detection probe, and in particular a second end of the supporting rod, is reversibly connectable to the handgrip by a mechanical connector equipped with electrical contacts for transferring the signals from the first electronic conversion circuitry to the second electronic conversion circuitry.

Detector designs and systems for enhanced radiographic imaging with integrated detector systems incorporate one or more of Compton and nuclear medicine imaging, PET imaging and x-ray CT imaging capabilities. Detector designs employ one or more layers of detector modules comprised of edge-on or face-on detectors or a combination of edge-on and face-on detectors which may employ gas, scintillator, semiconductor, low temperature (such as Ge and superconductor) and structured detectors. Detectors may implement tracking capabilities and may operate in a non-coincidence or coincidence detection mode.

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 dual mode radiation detector comprising an x-ray detector layer to convert incident x-ray radiation into x-ray electrical data, said x-ray detector forming an incident face of said dual mode radiation detector, a collimator disposed below the x-ray detector layer, and a gamma photon detector layer disposed below the collimator to convert incident gamma photons into gamma photon electrical data.

A system and method for the measurement of radiation emitted from an in-vivo administered radioactive analyte. Gamma radiation sensors may be used to determine the proper or improper administration of a radioactive analyte. In some cases, the system employs a sensor having a scintillation material to convert gamma radiation to visible light, which enables embodiments of the sensor to be ex vivo. A light detector converts the visible light to an electrical signal. This signal is amplified and is processed to measure the captured radiation. Temperature of the sensor may be recorded along with this radiation measurement for temperature compensation of ex vivo embodiments. The sensor enables collection of sufficient data to support separate application to predictive models, background comparisons, or change analysis.