Abstract: A solid-state imaging apparatus includes a pixel array in which a plurality of pixels are arranged, wherein the pixel array has a region formed from one of an electrical conductor and a semiconductor to which a fixed electric potential is supplied, each pixel includes a photoelectric converter, a charge-voltage converter which converts charges generated by the photoelectric converter into a voltage, and an amplification unit which amplifies a signal generated by the charge-voltage converter by a positive gain and outputs the amplified signal to an output line, and the output line comprising a shielding portion arranged to shield at least part of the charge-voltage converter with respect to the region.

Abstract: A method and an apparatus for measuring the dose, the dose rate and/or the composition of radiation is disclosed. In the method, a detector means is exposed to a radiation environment, the detector means comprising an array of radiation sensing detector elements. The detector means is switched in a sensitive state for the duration of a sensitive time period, and during said sensitive time period, an interaction pattern generated by individual radiation quanta interacting with one or more of the detector elements is recorded. The duration of the sensitive time period can be precisely adapted to the intensity of the radiation that has to be recorded. The interaction pattern is analyzed to distinguish individual radiation quanta received during the sensitive time period, and a radiation category is assigned to each of the distinguished radiation quanta based on its corresponding interaction pattern.

Abstract: A radiation detecting apparatus comprises: a first detector that detects incidence of radiation; a plate-shaped detection substrate including a second detector that detects an incident position of the radiation to at least the first detector, and a first terminal that is electrically connected to the second detector; a wiring substrate including a second terminal and an external terminal that is electrically connected to the second terminal; and a connecting member that electrically connects the first terminal and the second terminal. The first terminal is arranged at one end of a main surface of the plate-shaped detection substrate. The detection substrate is mounted on the wiring substrate such that the main surface is substantially perpendicular to the wiring substrate in a state that the one end faces the wiring substrate. The first detector is arranged opposite to the main surface of the detection substrate.

Abstract: A scintillator array and method for making the same are provided. The array comprises a bi-layer reflector further comprising a conformal smoothing layer and a mirror layer. The bi-layer reflector does not comprise an intervening reducing agent or adhesion layer and/or comprises aluminum. Further, the mirror layer may be deposited via gas phase metallization, allowing application to tightly confined spaces. A detector array comprising the scintillator array is also provided.

Abstract: An imaging detector includes processing electronics with a thermal coefficient about equal to a negative of a summation of thermal coefficients of a photosensor array and a scintillator array of the detector. In another instance, the imaging detector includes an A/D converter that alternately converts first charge corresponding to impinging radiation into a first signal and second charge corresponding to decaying charge into a second signal and a logic unit that corrects the first signal based on the second signal. In another instance, the imaging detector includes an A/D converter, an integrator offset voltage signal determiner, and a logic unit, wherein the determiner induces an electrical current via an off-set voltage, the A/D converter measures the current, and the logic unit calculates a resistance of the photosensor array based on the reference voltage and the measured current.

Abstract: A solid-state imaging device according to an embodiment includes a plurality of signal output units. Each of the plurality of signal output units includes an input terminal electrode group including terminal electrodes for inputting a reset signal, a hold signal, a horizontal start signal, and a horizontal clock signal and an output terminal electrode for providing an output signal. The solid-state imaging device further includes common lines that are provided across the plurality of signal output units. A terminal electrode for the reset signal and a terminal electrode for the hold signal are connected to the corresponding common lines through the corresponding switches.

Abstract: The present invention provides a radiation detecting element and a radiographic imaging device that may reliably detect radiation even when a region where radiation is irradiated is set narrowly. Namely, in the radiation detecting element and the radiographic imaging device of the present invention, plural pixels including radiographic imaging pixels and plural radiation detection pixels are disposed in a matrix in a detection region that detects radiation.

Abstract: A light transmitting element such as a scintillating element (50) or an optic fiber (50?) has side surfaces coated with a metamaterial (62) which has an index of refraction less than 1 and preferably close to zero to light transmitted in the light transmitting element. A photonic crystal (80) or metamaterial layer optically couples a light output face of the light transmitting element with a light sensitive element (52), such as a silicon photomultiplier (SiPM). A thin metal layer (64) blocks optical communication between adjacent scintillating elements (50) in a radiation detector (22), such as a radiation detector of a nuclear imaging system (10).

Abstract: The present invention provides a radiation detecting element and a radiographic imaging device that may reliably detect irradiation of radiation even when a region where radiation is irradiated is set narrowly. Namely, the present invention provides a radiation detection element and a radiographic imaging apparatus, in which radiographic imaging pixels and radiation detection pixels are provided at intersecting portions of scan lines and signal lines.

Abstract: A radiation detection apparatus comprising semiconductor substrates each having a first surface on which a photoelectric conversion portion is formed and a second surface opposite to the first surface; a scintillator layer, placed over the first surfaces of the semiconductor substrates, for converting radiation into light; and an elastic member, placed between a base and the second surfaces, for supporting the second surfaces of the semiconductor substrates such that the first surfaces of the semiconductor substrates are flush with each other is provided. In measurement of the elastic member as a single body, an amount of stretch of a cubic specimen in a direction parallel to the first surface when being compressed in a direction perpendicular to the first surface is smaller than an amount of stretch of the specimen in the direction perpendicular to the first surface when being compressed in the direction parallel to the first surface.

Abstract: Embodiments of radiographic imaging apparatus and methods for operating the same can include a first scintillator, a second scintillator, a plurality of first photosensitive elements, and a plurality of second photosensitive elements. The plurality of first photosensitive elements receives light from the first scintillator and has first photosensitive element characteristics chosen to cooperate with the first scintillator properties. The plurality of second photosensitive elements are arranged to receive light from the second scintillator and has second photosensitive element characteristics different from the first photosensitive element characteristics and chosen to cooperate with the second scintillator properties. Further, the first scintillator can have first scintillator properties and the second scintillator can have second scintillator properties different from the first scintillator properties.

Abstract: A nuclear medicine imaging apparatus according to an embodiment includes a gradation width storage, an estimating unit, and an image generating unit. The gradation width storage is configured to store the gradation width of an image determined by the temporal resolution of a detector. The estimating unit is configured to estimate the spatial position of a positron on the basis of the spatial position of a set of detectors and a set of detection times. The image generating unit is configured to allocate pixel value to pixels corresponding to the gradation width around the estimated spatial position such that a spatial resolution corresponding to the temporal resolution is reflected on a line linking the set of detectors, thereby generating an image.

Abstract: A method for estimating the start time of an electronic pulse generated in response to a detected event, for example the start time for pulses received in response to photon detection in positron emission tomography, includes providing a detector that detects an external event and generates an electronic analog pulse signal. A composite reference pulse curve is calculated to represent analog pulse signals generated by the detector. Upon receiving an analog pulse signal, it may be filtered, and then digitized, and normalized based on the area of the digital signal. Using at least one point of the normalized digital pulse signal, the composite reference pulse curve shape is used to estimate the pulse start time.

Abstract: A PET scanner (10) includes a ring of detector modules (16) encircling an imaging region (18). Each of the detector modules includes one or more sensor avalanche photodiodes (APDs) (34) that are biased in a breakdown region in a Geiger mode. The sensor APDs (34) output pulses in response to light from a scintillator corresponding to incident photons. A reference APD (36) also biased in a breakdown region in a Geiger mode is optically shielded from light and outputs a voltage that is measured by an analog to digital converter (44). Based on the measurement, a bias control feedback loop (42) directs a variable voltage generator (48) to adjust a bias voltage applied to the APDs (34, 36) such that a difference (86) between a voltage of a break-down pulse (68) and a preselected logic voltage level (70) is minimized.

Abstract: A neutron image detection method is disclosed, which collects a fluorescent light generated by a neutron incident at a designated position interval in one-dimensional geometry and determines an incident position of the neutron by detecting the collected fluorescent light, in which the fluorescent light is detected by a photon counting method; a pulse signal generated by an individual output photon is extracted on the basis of a clock signal generated with the same time interval as the time width of the pulse signal generated by a single photon; a count-value distribution is obtained in terms of incident position as variable determined by a single neutron incident by counting the pulse signal output; and a neutron incident position is determined by calculating a median point on the basis of the obtained count-value distribution.

Abstract: A detector for a nuclear imaging system includes a scintillator including an array of scintillator elements and a light guide including a grid which defines light guide elements. Light from scintillations in the scintillation crystal in response to received radiation, passes through the light guide and strikes light sensitive elements of a light sensitive element array. The light sensitive element array includes larger elements in an array in the center surrounded by smaller light sensitive elements located in a peripheral array around the central array.

Abstract: An X-ray radiation detector (100) consists of an arrangement with photodetector elements (12) and a scintillator layer (14) on the same. It is assumed in an exemplary fashion that the scintillator layer (14) subjects an input signal, which describes an object to be imaged, to a convolution with a modulation transfer function. The effect of this can be cancelled, particularly by obtaining a test X-ray image in advance, with the aid of which this modulation transfer function, or a similar variable providing information on the modulation transfer function, is established. If use is made of photodetectors that are based on CMOS technology, use can be made of a particularly thick scintillator layer made of gadolinium oxysulfide, which absorbs a particularly large amount of X-ray radiation. High-contrast X-ray images are obtained in this fashion.

Abstract: A monolithic integrated radiation detector includes a photodetector and a scintillator deposited directly on the photodetector. Preferably the photodetector is silicon and the scintillator is a rare earth phosphor. The rare earth phosphor is crystal lattice matched to the silicon by a transitional layer epitaxially grown therebetween.

Abstract: An X-ray detector of an X-ray CT apparatus has a plurality of collimators, a plurality of scintillators, a plurality of photodiodes and a light guide. The plurality of collimators collimate an X-ray. The plurality of scintillators respectively emit fluorescence based on the X-ray from the plurality of collimators. The plurality of photodiodes respectively convert the fluorescence from the plurality of scintillators into the electric signal. The light guide has such a shape as to guide the fluorescence emitted from the plurality of scintillators respectively to the plurality of photodiodes while focusing the fluorescence toward the plurality of photodiodes.

Abstract: An X-ray detector of an X-ray CT apparatus has a collimator, a plurality of scintillators, a light reflector and a plurality of photodiodes. The collimator has a threshold plate with a thickness Wc to eliminate scattered radiation from an X-ray. The plurality of scintillators emit light based on the X-ray. The light reflector is provided in a gap between adjacent scintillators of the plurality of scintillators. The plurality of photodiodes convert the light of each of the plurality of scintillators into the electric signal. The thickness Wc of the threshold plate mounted on the X-ray incident side of the adjacent scintillators, and a thickness Ws of the gap has a relationship shown in a following expression: Wc?Ws.

Abstract: When detecting photons in a computed tomography (CT) detector, a sensor (10, 38) includes a photodiode that is switchable between liner and Geiger operation modes to increase sensing range. When signal to noise ratio (SNR) is high, a large bias voltage is applied to the photodiode (12) to charge it beyond its breakdown voltage, which makes it sensitive to single photons and causes it to operate in Geiger mode. When a photon is received at the photodiode (12), a readout transistor (18) senses the voltage drop across the photodiode (12) to detect the photon. Alternatively, when SNR is low, a low bias voltage is applied to the photodiode (12) to cause it to operate in linear mode.

Abstract: In order to provide a particle radiotherapy apparatus with high sensitivity for detecting annihilation radiation pairs, an elliptic detector ring of a particle radiotherapy apparatus according to this invention makes rotating movement relative to a top board. Specifically, with rotation about a base axis of a first ring and a second ring, the elliptic detector ring makes rotating movement in a state of being tilted relative to the first ring. Incidentally, the elliptic detector ring cannot be disposed in a position to interfere with travel of this particle beam. According to the construction of this invention, the elliptic detector ring is tilted relative to the top board, and besides makes rotating movement relative to the top board. Since the elliptic detector ring can be moved away from the particle beam by rotating the elliptic detector ring, it is possible to provide the particle radiotherapy apparatus which can detect annihilation radiation while emitting the particle beam.

Abstract: A cardiac imaging system employing dual gamma imaging heads co-registered with one another to provide two dynamic simultaneous views of the heart sector of a patient torso. A first gamma imaging head is positioned in a first orientation with respect to the heart sector and a second gamma imaging head is positioned in a second orientation with respect to the heart sector. An adjustment arrangement is capable of adjusting the distance between the separate imaging heads and the angle between the heads. With the angle between the imaging heads set to 180 degrees and operating in a range of 140-159 keV and at a rate of up to 500kHz, the imaging heads are co-registered to produce simultaneous dynamic recording of two stereotactic views of the heart. The use of co-registered imaging heads maximizes the uniformity of detection sensitivity of blood flow in and around the heart over the whole heart volume and minimizes radiation absorption effects.

Abstract: A one-dimensional multi-element photo detector (120) includes a photodiode array (122) with a first upper row of photodiode pixels and a second lower row of photodiode pixels. The photodiode array (122) is part of the photo detector (120). A scintillator array (126) includes a first upper row and a second lower row of scintillator pixels. The first upper and second lower rows of scintillator pixels are respectively optically coupled to the first upper and second lower rows of photodiode pixels. The photo detector (120) also includes readout electronics (124), which are also part of the photo detector (120). Electrical traces (512) interconnect the photodiode pixels and the readout electronics (124).

Abstract: The present technology provides for an fluorescent detector that is configured to detect light emitted for a probe characteristic of a polynucleotide. The polynucleotide is undergoing amplification in a microfluidic channel with which the detector is in optical communication. The detector is configured to detect minute quantities of polynucleotide, such as would be contained in a microfluidic volume. The detector can also be multiplexed to permit multiple concurrent measurements on multiple polynucleotides concurrently.

Abstract: According to some aspects, a device comprising a plurality of cameras arranged in an array, each of the plurality of cameras producing a signal indicative of radiation impinging on the respective camera, the plurality of cameras arranged such that the field of view of each of the plurality of cameras at least partially overlaps the field of view of at least one adjacent camera of the plurality of cameras, to form a respective plurality of overlap regions, an energy conversion component for converting first radiation impinging on a surface of the energy conversion component to second radiation at a lower energy that is detectable by the plurality of cameras, and at least one computer for processing the signals from each of the plurality cameras to generate at least one image, the at least one processor configured to combine signals in the plurality of overlap regions to form the at least one image is provided.

Abstract: A radiation detector includes a sensor panel including a photodetector and peripheral circuitry, the photodetector includes a two-dimensional array of photoelectric conversion elements arranged on a substrate, the peripheral circuitry is electrically connected to the photoelectric conversion elements and is disposed on the periphery of the photodetector; a scintillator layer is disposed on the photodetector of the sensor panel, the scintillator layer converts radiation into light that is detectable by the photoelectric conversion elements; a scintillator protection member covers the scintillator layer; and a sealing resin seals the scintillator layer, the sealing resin is disposed between the sensor panel and the scintillator protection member on the periphery of the scintillator layer; the sealing resin is disposed on top of the peripheral circuitry; and particles containing a radiation-absorbing material are dispersed in the sealing resin.

Abstract: When employing hygroscopic scintillation crystals (32) in a nuclear detector (e.g., PET or SPECT), Silicon photo-multiplier (SiPM) sensors (34) are coupled to each scintillation crystal (32) to improve scintillation event detection and reduce scatter. The crystals (32) and sensors (34) are hermetically sealed in a detector housing (50) using a sealant layer (51). Electrical contacts (60) from each sensor (34) extend through the sealant layer (51) or are bused together such that the bus extends through the sealant layer (51). In this manner, hygroscopic scintillation crystals (e.g., LaBr, NaI, etc.) are protected from humidity and light scatter is reduced by direct coupling of the sensors (34) and crystals (32).

Abstract: An imaging apparatus for x-rays includes a scintillator, overlying an array of imaging pixels on a substrate, and at least one trigger pixel array externally peripheral to the array of imaging pixels on the substrate such that the trigger pixel array is not substantially overshadowed by the scintillator from incident x-ray radiation. A layer substantially impervious to light but transparent to x-rays overlays the trigger pixel array, such that the trigger pixels are unresponsive to light but triggered by direct hits from incident x-ray photons.

Abstract: CT scanning of transportation containers is performed by generating X-rays at various points at the opposite sides of the containers, detecting the X-rays passing through the containers, and analyzing the data received to determine the presence of contraband. The X-rays are generated by modulating a magnetic field through which a high-energy electron beam passes to deflect the beam successively to different targets positioned around the sides of the container, while the electron beam source remains stationary. The X-rays are detected by an array of cells using X-ray responsive storage phosphor material to emit light which is sent to analyzing and comparing equipment. The targets and detectors and the cargo container are moved relative to one another to scan a selected volume of the container.

Abstract: An apparatus and associated method for gamma ray detection that improves the timing resolution is provided. A crystal of interaction in a scintillation crystal array emits scintillation light in response to interaction with a gamma ray. The scintillation light is detected by one or more photomultiplier tubes. Each photomultiplier tube that detects the scintillation light detects the light at a different time. The apparatus determines the location of the gamma ray interaction and uses the location of the interaction to generate correction times for each waveform generated by the photomultiplier tubes. The waveforms are corrected with the correction timings and combined to extract a time of arrival estimate for the gamma ray. Noise thresholding is also used to select waveforms having low noise for combination to extract the time of arrival estimate.

Abstract: A radiation detector (24) includes a two-dimensional array of upper scintillators (30?) which is disposed facing an x-ray source (14) to convert lower energy radiation into visible light and transmit higher energy radiation. A two-dimensional array of lower scintillators (30B) is disposed adjacent the upper scintillators (30?) distally from the x-ray source (14) to convert the transmitted higher energy radiation into visible light. Respective active areas (94, 96) of each upper and lower photodetector arrays (38?, 38B) are optically coupled to the respective upper and lower scintillators (30?, 30B) at an inner side (60) of the scintillators (30?, 30B) which inner side (60) is generally perpendicular to an axial direction (Z).

Abstract: A photoelectric conversion device is provided and includes: a photoelectric conversion panel in which light detection portions each having a charge storage portion storing light as electric charges are two-dimensionally arranged; a reading control unit that reads the electric charges stored in the charge storage portions of the photoelectric conversion panel for each reading signal line; and a reset unit that is connected to the reading signal lines and discharges residual charges of the charge storage portions for each reading signal line. The reading control unit and the reset unit are arranged at different end portions of the photoelectric conversion panel.

Abstract: A radiation detector includes an array of detector pixels each including an array of detector cells. Each detector cell includes a photodiode biased in a breakdown region and digital circuitry coupled with the photodiode and configured to output a first digital value in a quiescent state and a second digital value responsive to photon detection by the photodiode. Digital triggering circuitry is configured to output a trigger signal indicative of a start of an integration time period responsive to a selected number of one or more of the detector cells transitioning from the first digital value to the second digital value. Readout digital circuitry accumulates a count of a number of transitions of detector cells of the array of detector cells from the first digital state to the second digital state over the integration time period.

Abstract: A digital radiographic detector has a scintillator element having a particulate phosphor dispersed within a binder composition, wherein the binder composition is a pressure-sensitive adhesive, wherein the particulate phosphor emits light corresponding to a level of incident radiation. There is an array of photosensors wherein each photosensor in the array is energizable to provide an output signal indicative of the level of emitted light that is received. The scintillator element bonds directly to, and in optical contact with, either the array of photosensors or an array of optical fibers that guide light to the array of photosensors.

Abstract: A digital radiographic detector having a radiation sensing element with a particulate material dispersed within a binder composition, wherein the binder composition includes a pressure-sensitive adhesive, wherein the particulate material, upon receiving radiation of a first energy level, is excitable to emit radiation of a second energy level, either spontaneously or in response to a stimulating energy of a third energy level. There is an array of photosensors, each photosensor in the array energizable to provide an output signal indicative of the level of emitted radiation of the second energy level that is received. The radiation sensing element bonds directly to, and in optical contact with, either the array of photosensors or an array of optical fibers that guide light to the array of photosensors.

Abstract: A gamma ray detector for detecting a gamma ray emitted from a target of measurement includes: an organic scintillator for detecting Compton electrons resulting from a gamma ray emitted from the target of measurement; an inorganic scintillator for detecting a Compton gamma ray; and photodetector modules for detecting light generation in the corresponding scintillators. Light generation signals from the organic and inorganic scintillators are synchronously measured, and a detection window of a gamma ray is generated. Thus, an inexpensive radiation diagnostic device of an ultra-high S/N ratio and low cost is provided.

Abstract: A gamma ray detector module that includes at least one crystal element arranged in a plane, a plurality of light sensors arranged to cover the at least one crystal element and to receive light emitted from the at least one crystal element, and a light guide arranged between the at least one crystal element and the light sensors, the light guide being optically connected to the at least one crystal element. Further, the light guide includes a narrow portion that positions at least one light sensor of the plurality of light sensors closer to the at least one crystal element than other light sensors of the plurality of light sensors. In addition, the light guide may include an angled recessed portion that positions another light sensor at an oblique tilt angle with respect to the plane of the at least one crystal element.

Abstract: In an X-ray line sensor 1, a scintillator layer 24 that absorbs X-rays in a low-energy range and emits light and a scintillator layer 26 that absorbs X-rays in a high-energy range and emits light are brought in contact with each other, and further, the thickness of the scintillator layer 24 on the front side is thinner than that of the scintillator layer 26 on the rear side. These make the amount of mismatch small between a light emitting position P1 in the scintillator layer 24 and a light emitting position P2 in the scintillator layer 26 to X-rays in the low-energy range and X-rays in the high-energy range entered at the same angle from the front side, so that at this time, light emitted by the scintillator layer 24 and light emitted by the scintillator layer 26 are detected by a photo-detecting section 16 and a photo-detecting section 23 facing each other.

Abstract: Disclosed is a multi-channel array radiation detector that can provide high-definition and high-resolution CT photo-images. The radiation detector has semiconductor photo-detecting elements arranged lengthwise and breadth-wise in a lattice manner and scintillator elements arranged on them one-to-one. The scintillator elements have thin metal light-reflecting material layers formed on side surfaces of the scintillator elements, and a radiation shielding material layer composed of resin blended with heavy metal element particles is filled in between adjacent metal light-reflecting material layers.

Abstract: A method and system for nuclear imaging normally involve detection of energy by producing at most two or three bursts of photons at a time in response to events including incident gamma radiation. F number of sharing central groups of seven photodetectors, depending on the photodetector array size, is arranged in a honeycomb array for viewing zones of up to F bursts of optical photons at a time for each continuous detector and converting the bursts of optical photons into signal outputs, where each of the central groups is associated with a zone. This enables the detector sensitivity to be increased by as much as two orders of magnitude, and to exchange some of this excess sensitivity to achieve spatial resolution comparable to those in CT and MRI, which would be unprecedented. Signal outputs that are due to scattered incident radiation are rejected for each of the central groups to reduce image blurring, thereby further improving image quality.

Abstract: A portable radiographic image capturing device has: an image capturing unit at which is provided a radiation surface onto which radiation is irradiated at a time of capturing a radiographic image, and that captures a radiographic image expressed by radiation irradiated onto the radiation surface, and that incorporates therein a radiation detector that outputs electric signals expressing a captured radiographic image; and a control unit that is connected to the image capturing unit, and that incorporates therein a controller that controls image capturing operations of the radiation detector, and that can be changed between an expanded state in which the radiation surface is exposed to an exterior and a housed state in which the control unit covers the radiation surface.

Abstract: An emission tomography detector module and an emission tomography scanner are disclosed. In at least one embodiment, the emission tomography detector modules includes a scintillator to capture an photon, the scintillator emitting a scintillating light on capturing the photon; a first type of solid-state photodetector to detect the scintillating light; and a second type of solid-state photodetector to detect the scintillating light, wherein the first type of solid-state photodetector and the second type of solid-state photodetector are different with respect to a detecting property.

Abstract: A vacuum vessel is configured by hermetically joining a faceplate to one end of a side tube and a stem to the other end via a tubular member. A photocathode, a focusing electrode, dynodes, a drawing electrode, and anodes are arranged within the vacuum vessel. The dynodes and the anodes have a plurality of channels in association with each other. The drawing electrode is placed on electrically-conductive supporting pins penetrating the stem. The dynodes are stacked with insulating members interposed between one another. Since the supporting pins and the insulating members are arranged coaxially, each electrode can be fixed by applying pressure in z-axis direction. At the same time, emission of light between the anodes and the drawing electrode can be suppressed, thereby enabling noise to be reduced.

Abstract: An image sensor has a plurality of pixels, each pixel including a photoelectric converter and a pixel circuit for processing signals from the photoelectric converter and outputting processed signals and a scanning circuit, disposed between the photoelectric converters, included in each of at least two adjacent pixels among a plurality of pixels aligned in a single direction. An edge pixel accommodates, in order from an edge of the image sensor toward an interior, a predetermined empty region, a photoelectric converter and a pixel circuit. There is at least one position at which two adjacent pixels, the first of the two pixels accommodating, in order, a pixel circuit, a photoelectric converter and predetermined empty region, the second accommodating, in order, a predetermined empty region, a photoelectric converter and a pixel circuit. The scanning circuit is disposed in the predetermined empty region between the two adjacent pixels.

Abstract: A radiation detecting apparatus includes: a sensor panel that has a substrate, and has a plurality of pixels each of which has a photoelectric conversion element for converting light into an electric signal, arranged on the substrate; and a scintillator layer arranged on a reverse side of the pixels with respect to the substrate, wherein the scintillator layer contains an activator added in a main ingredient, and has a higher concentration of the activator in a peripheral area than in a center area, in a surface direction of the scintillator layer.

Abstract: An X-ray detector for a tomography device is disclosed, including a plurality of detector elements, each including a photodiode and a scintillator fixed to the optically active surface of the photodiode by a connecting medium. In at least one embodiment, the optically active surface of the photodiode has a nanostructure, which forms a transition region having gradually progressing refractive indices between a refractive index of the connecting medium and a refractive index of the photodiode. Reflections at the optical transition of connecting medium/photodiode and also optical crosstalk to adjacent detector elements are greatly reduced in this way. Such an X-ray detector therefore has a higher luminous efficiency, with which a signal-to-noise ratio and a spatial resolution of the X-ray detector are improved. At least one embodiment of the invention additionally relates to a method for producing an X-ray detector having the properties mentioned.

Abstract: A water Cerenkov-based neutron and high energy gamma ray detector and radiation portal monitoring system using water doped with a Gadolinium (Gd)-based compound as the Cerenkov radiator. An optically opaque enclosure is provided surrounding a detection chamber filled with the Cerenkov radiator, and photomultipliers are optically connected to the detect Cerenkov radiation generated by the Cerenkov radiator from incident high energy gamma rays or gamma rays induced by neutron capture on the Gd of incident neutrons from a fission source. The PMT signals are then used to determine time correlations indicative of neutron multiplicity events characteristic of a fission source.

Abstract: An X-ray detector for detecting X-ray comprises a photodetector and a scintillator layer formed of a fluorescent material coated on a light receiving surface of the photodetector, the fluorescent material converting X-ray into light.

Abstract: A photodiode comprising: a first semiconductor layer having a first conductivity type; a second semiconductor layer having a second conductivity type that is opposite to the first conductivity type of the first semiconductor layer; and a third semiconductor layer interposed between the first semiconductor layer and the second semiconductor layer, wherein an edge of the first semiconductor layer is inset from an edge of the second semiconductor layer.