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.

Micrometer-scale x-ray photodetectors that utilize a flexible array of photodiodes wrapped around the circumference of a scintillator core are provided. The photodetectors use dense and flexible pixelated arrays of photodiodes disposed around the circumference of a crystalline scintillator to provide highly compact photodetectors with high spatial, temporal, and energy resolution.

Embodiments are directed generally to an ionizing-radiation beamline monitoring system that includes a vacuum chamber structure with vacuum compatible flanges through which an incident ionizing-radiation beam enters the monitoring system. Embodiments further include at least one scintillator within the vacuum chamber structure that can be at least partially translated in the ionizing-radiation beam while oriented at an angle greater than 10 degrees to a normal of the incident ionizing-radiation beam, a machine vision camera coupled to a light-tight structure at atmospheric/ambient pressure that is attached to the vacuum chamber structure by a flange attached to a vacuum-tight viewport window with the camera and lens optical axis oriented at an angle of less than 80 degrees with respect to a normal of the scintillator, and at least one ultraviolet (UV) illumination source facing the scintillator in the ionizing-radiation beam for monitoring a scintillator stability comprising scintillator radiation damage.

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. 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.

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 transmissive ionizing-radiation beam monitoring system includes an enclosure structure with at least one ultra-thin window to an incident ionizing-radiation beam, where the ultra-thin window is highly transmissive to ionizing-radiation. Embodiments include at least one thin or ultra-thin scintillator within the enclosure structure that is substantially directly in an incident ionizing-radiation beam path and transmissive to the incident radiation beam, and at least one ultraviolet (UV) illumination source within the enclosure structure facing the scintillator. Embodiments include at least one machine vision camera within the enclosure structure located out of an incident ionizing-radiation beam path and including a camera body and lens having a projection of its optical axis oriented at an angle of incidence of 4535 degrees to a surface of the scintillator.

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.

An echo-scintigraphic probe for medical applications and the method of merging images. It is constituted by the union of an ultrasound probe suitably integrated, both in geometric terms, and in terms of image processing, with a scintigraphic probe or gamma camera (3). With a single application of said probe, one is able to provide a double image of the object under examination. The ultrasound probe is housed in the head, above the plane of the collimator and kept projecting to favor the direct contact with the body part of the patient to be examined. The collimator is able to obtain images of the biodistribution of a radiolabelled drug by radiation with frontal incidence, maintaining the characteristics of the ultrasound probe. The probe is applicable to both clinical diagnosis and intraoperative diagnosis of cancer with the use of radio tracers. A guided diagnostic method is disclosed that realizes a functional integration of a pair of ultrasound and scintigraphic images concurrently obtained by the echo-scintigraphic probe.

A transmissive ionizing-radiation beam monitoring system includes an enclosure structure including an entrance window and an exit window to an incident ionizing-radiation beam, where the entrance window and the exit window are highly transmissive. The system further includes a thin scintillator within the enclosure structure that is directly in an incident ionizing-radiation beam path and transmissive to the incident radiation beam and an ultraviolet (UV) illumination source within the enclosure structure facing the scintillator for internal system calibration. Embodiments further include a UV photosensor within the enclosure structure positioned to monitor and calibrate the UV illumination source and a machine vision camera within the enclosure structure that includes a lens which views the scintillator through a close proximity mirror including a folded optical axis system located to a side of the scintillator.