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.

Apparatus, techniques and systems are described for facilitating identification of a target area during a probe-guided radio-localization surgical procedure. The described apparatus, techniques and systems can be used to implement a nuclear-uptake mode controller integrated into a probe to allow a user to instantly switch between multiple nuclear-uptake modes directly from the probe hand-piece. For example, a nuclear-uptake mode controller integrated into the probe can be used to instantly switch between a high-sensitivity nuclear-up-take mode and a high-resolution nuclear-uptake mode to effectively identify the target area in the presence of interfering nuclear signals by better matching the probe's nuclear detection parameters to a search task for that target area.

A dual mode radiation detector includes an x-ray detector layer configured to convert incident x-ray radiation into x-ray electrical data, where the x-ray detector forms an incident face of the dual mode radiation detector. The dual mode radiation detector further includes 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.

The present invention relates to a water dosimetry device using X-ray induced ultrasonic waves, in which a medical X-ray linear accelerator and an ultrasonic transducer are combined to construct a medical X-ray linear accelerator-based ultrasound imaging device, so that a radiation-absorbed dose in water when X-rays irradiate the water is measured in real time.

The invention relates to a combined detector (660) comprising a gamma radiation detector (100) and an X-ray radiation detector (661). The gamma radiation detector (100) comprises a gamma scintillator array (101.sub.x, y), an optical modulator (102) and a first photodetector array (103.sub.a, b) for detecting the first scintillation light generated by the gamma scintillator array (101.sub.x, y). The optical modulator (102) is disposed between the gamma scintillator array (101.sub.x, y) and the first photodetector array (103.sub.a, b) for modulating a transmission of the first scintillation light between the gamma scintillator array (101.sub.x, y) and the first photodetector array (103.sub.a, b). The optical modulator (102) comprises at least one optical modulator pixel having a cross sectional area (102) in a plane that is perpendicular to the gamma radiation receiving direction (104). The cross sectional area of each optical modulator pixel (102) is greater than or equal to the cross sectional area of each photodetector pixel (103.sub.a, b).

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.

Apparatus, techniques and systems are described for facilitating identification of a target area during a probe-guided radio-localization surgical procedure. The described apparatus, techniques and systems can be used to implement a nuclear-uptake mode controller integrated into a probe to allow a user to instantly switch between multiple nuclear-uptake modes directly from the probe hand-piece. For example, a nuclear-uptake mode controller integrated into the probe can be used to instantly switch between a high-sensitivity nuclear-uptake mode and a high-resolution nuclear-uptake mode to effectively identify the target area in the presence of interfering nuclear signals by better matching the probe's nuclear detection parameters to a search task for that target area.

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 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 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.