Disclosed are a Li.sup.+ doped metal halide scintillation crystal with a zero-dimensional perovskite structure, a preparation method and use thereof. The scintillation crystal has a chemical formula of Cs.sub.3-xCu.sub.2I.sub.5:xLi, where x is in a range of 0.003 to 0.3. The method for preparing the scintillation crystal comprises the steps of: weighting and fully mixing a CuI powder, a CsI powder and a LiI powder in a molar ratio of 2:(3-x):x in an inert atmosphere to obtain a mixed powder, and growing into the scintillation crystal from the mixed powder by Bridgman Stockbarger method. After excited, the scintillation crystal could emit a broadband blue light in a range of 350-550 nm, with an intensity much higher than that of the original pure component crystal. The existence of Li.sup.+ further expands the application of the scintillation crystals from X/γ-ray detection to neutron detection.

Scintillator materials, as well as related systems, and methods of detection using the same, are described herein. The scintillator material composition may comprise a Tl-based scintillator material. For example, the composition may comprise a thallium-based halide. Such materials have been shown to have particularly attractive scintillation properties and may be used in a variety of applications for detection radiation.

Disclosed herein are variations of megavoltage (MV) detectors that may be used for acquiring high resolution dynamic images and dose measurements in patients. One variation of a MV detector comprises a scintillating optical fiber plate, a photodiode array configured to receive light data from the optical fibers, and readout electronics. In some variations, the scintillating optical fiber plate comprises one or more fibers that are focused to the radiation source. The diameters of the fibers may be smaller than the pixels of the photodiode array. In some variations, the fiber diameter is on the order of about 2 to about 100 times smaller than the width of a photodiode array pixel, e.g., about 20 times smaller. Also disclosed herein are methods of manufacturing a focused scintillating fiber optic plate.

Disclosed herein are variations of megavoltage (MV) detectors that may be used for acquiring high resolution dynamic images and dose measurements in patients. One variation of a MV detector comprises a scintillating optical fiber plate, a photodiode array configured to receive light data from the optical fibers, and readout electronics. In some variations, the scintillating optical fiber plate comprises one or more fibers that are focused to the radiation source. The diameters of the fibers may be smaller than the pixels of the photodiode array. In some variations, the fiber diameter is on the order of about 2 to about 100 times smaller than the width of a photodiode array pixel, e.g., about 20 times smaller. Also disclosed herein are methods of manufacturing a focused scintillating fiber optic plate.

To obtain a neutron detector capable of measuring high dose neutrons with high neutron/gamma-ray discrimination ability and high efficiency.

A scintillator 10 has a layered structure in which a phosphor layer 11 and a light transmission layer 12 are alternatelylaminatedin z direction. The phosphor layer 11 is made of a phosphor material emitting fluorescent light by absorbing neutrons, the material being, for example, a scintillator material used in neutron detectors having alreadybeen known. The light transmission layer 12 is made of a material highly transmitting fluorescent light emitted by the phosphor materialand only slightlyabsorbingneutrons. In the scintillator 10, when neutrons and gamma-ray photons enter it, luminescence intensity (pulse height) due to neutrons is significantly different from that due to gamma-ray photons. It makes it easy to discriminate between outputs due to the two kinds of radiations.

To obtain a neutron detector capable of measuring high dose neutrons with high neutron/gamma-ray discrimination ability and high efficiency.

A scintillator 10 has a layered structure in which a phosphor layer 11 and a light transmission layer 12 are alternatelylaminatedin z direction. The phosphor layer 11 is made of a phosphor material emitting fluorescent light by absorbing neutrons, the material being, for example, a scintillator material used in neutron detectors having alreadybeen known. The light transmission layer 12 is made of a material highly transmitting fluorescent light emitted by the phosphor materialand only slightlyabsorbingneutrons. In the scintillator 10, when neutrons and gamma-ray photons enter it, luminescence intensity (pulse height) due to neutrons is significantly different from that due to gamma-ray photons. It makes it easy to discriminate between outputs due to the two kinds of radiations.

The present specification provides a detector for an X-ray imaging system. The detector includes at least one high resolution layer having high resolution wavelength-shifting optical fibers, each fiber occupying a distinct region of the detector, at least one low resolution layer with low resolution regions, and a single segmented multi-channel photo-multiplier tube for coupling signals obtained from the high resolution fibers and the low resolution regions.

Device for detecting neutrons with ionization chamber and with optical transduction comprising a plurality of optical cavities, each accommodating the free end of an optical fiber.

The invention relates to a device (1) for detecting neutrons comprising at least one sealed ionization chamber (2) and with optical transduction with a plurality of cavities whose operation is each based on optical transduction using an optical fiber whose free end is within the cavity, which allows multipoint neutron-flux measurement, the measurement points being axially distributed.

A dosimeter includes a housing and a printed circuit board positioned within the housing. A silicon photomultiplier is operably connected to the printed circuit board. A scintillator formed of Ce-activated lithium aluminosilicate glass is positioned on the silicon photomultiplier. An optical coupling is positioned between the scintillator and the silicon photomultiplier, and an optical reflector surrounds the scintillator.

A dosimeter includes a housing and a printed circuit board positioned within the housing. A silicon photomultiplier is operably connected to the printed circuit board. A scintillator formed of Ce-activated lithium aluminosilicate glass is positioned on the silicon photomultiplier. An optical coupling is positioned between the scintillator and the silicon photomultiplier, and an optical reflector surrounds the scintillator.