A radiological image conversion panel 2 is provided with a phosphor 18 containing a fluorescent material that emits fluorescence by radiation exposure, in which the phosphor includes, a columnar section 34 formed by a group of columnar crystals which are obtained through columnar growth of crystals of the fluorescent material, and a non-columnar section 36, the columnar section and the non-columnar section are integrally formed to overlap in a crystal growth direction of the columnar crystals, and a thickness of the non-columnar section along the crystal growth direction is non-uniform in a region of at least a part of the non-columnar section.

In one embodiment, there is provided detector for an inspection system, including at least one first scintillator configured to, in response to interaction with a pulse of inspection radiation, re-emit first light in a first wavelength domain, at least one second scintillator configured to, in response to interaction with the pulse of inspection radiation, re-emit second light in a second wavelength domain different from the first wavelength domain, and at least one first sensor configured to measure the first light and the second light.

A detector includes a first detection layer (114.sub.1) and a second detector layer (114.sub.2). The first and second detection layers include a first and second scintillator (204, 704.sub.1) (216, 704.sub.2), a first and second active photosensing region (210, 708.sub.1) (220, 708.sub.2), a first portion (206, 726.sub.1) of a first substrate (208, 706.sub.1), and a second portion (218, 726.sub.2) of a second substrate (208, 706.sub.2). An imaging system (100) includes a radiation source (110), a radiation sensitive detector array (108) comprising a plurality of multi-layer detectors (112), and a reconstructor (118) configured to reconstruct an output of the detector array and produces an image. The detector array includes a first detection layer and a second detector layer with a first and second scintillator, a first and second active photosensing region, a first portion of a first substrate, and a second portion of a second substrate.

An X-ray detector and an X-ray image system using the same are disclosed. The X-ray image system comprises an X-ray generator irradiating X-rays to an object to be photographed; an X-ray detector including a first photoelectric converter receiving X-rays transmitted the object and converting the X-rays in to a first electric signal and a second photoelectric converter converting the X-rays in to a second electric signal; a first image processor processing a first image of the object on the basis of the first electric signal of the X-ray detector; a second image processor processing a second image of the object on the basis of the second electric signal of the X-ray detector; a display module displaying the first and second processed images of the object; and a controller controlling the X-ray generator, the X-ray detector, the first and second image processors and the display module.

A laminated fluorescent sensor includes a sealable sensor housing and an optical sensing system embedded inside the sensor housing. The optical sensing system includes a light source (7), a short wave pass filter (8), an air chamber (10), a sensing unit, a long wave pass filter set (12) and an optical signal collecting unit from top to bottom all of which are coaxially set. The optical signal collecting unit is connected with a signal processing system (14); the sensor housing has air inlets (2, 201) and an air pumping port (3), the air inlets (2, 201) are communicated with the air chamber (10) through an air intake passage, the air chamber (10) is communicated with the air pumping port (3) through an air pumping passage. The laminated fluorescent sensor is compact and easy to be arrayed for simultaneously detecting two or more detected objects, has a high signal-to-noise ratio, is applicable in quick detection of micro-trace chemicals including but not limited to explosives and narcotics, provides great detection effects, has distinctly distinguishable signal responses to objects not being detected and to objects being detected, and provides stable and accurate detection.

A photoelectric detection structure and a preparation method, the structure comprises a first scintillator layer used for absorbing low-energy X rays and converting the X rays into visible light; a second scintillator layer used for absorbing high-energy X rays and converting the X rays into visible light; and a first visible light sensor located between the first scintillator layer and the second scintillator layer and used for converting visible light penetrating through the first scintillator layer and visible light reflected by the second scintillator layer into charges and storing the charges into the first visible light sensor. The method comprises providing a substrate, preparing layers layer by layer on the substrate through a semiconductor manufacturing process to form a first visible light sensor, forming a first scintillator layer on a first surface of the first visible light sensor and then forming a second scintillator layer on a second surface of the first visible light sensor.

The invention provides a novel arrangement of photon sensors on a scintillation-crystal based gamma-ray detector that takes advantage of total internal reflection of scintillation light within the scintillation detector substrate. The present invention provides improved spatial resolution including depth-of-interaction (DOI) resolution while preserving energy resolution and detection efficiency, which is especially useful in small-animal or human positron emission tomography (PET) or other techniques that depend on high-energy gamma-ray detection. Moreover, the new geometry helps reduce the total number of readout channels required and eliminates the need to do complicated and repetitive cutting and polishing operations to form pixelated crystal arrays as is the standard in current PET detector modules.

Embodiments include a device, comprising: a column line; a plurality of pixels; each pixel coupled to the column line; a comparator having an input coupled to the column line and configured to compare a signal from the column line to a threshold; and control logic coupled to the pixels and configured to selectively couple each pixel to the column line after a sampling period for each pixel.

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.

An active matrix substrate 1 has a plurality of detection circuitry. The detection circuitry includes a photoelectric conversion layer 15, a first electrode 14a and a second electrode 14b which interpose the photoelectric conversion layer 15 therebetween, a first insulating film 105, and a second insulating film 106. The first insulating film 105 covers a part of the photoelectric conversion layer 15, and has an opening 105a on the photoelectric conversion layer 15. The second insulating film 106 is provided on the first insulating film 105, and has an opening 106a having a width greater than that of the first insulating film 105. The second electrode 14b is in contact with the photoelectric conversion layer 15 in the first opening 105a, and is in contact with the first insulating film 105 and the second insulating film 106.