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.

Disclosed herein is a radiological instrument (100, 200, 300, 400, 600, 700, 800) comprising at least one pulse shaper circuit (102) configured for a direct conversion radiation detector (108). The at least one pulse shaper circuit comprises an amplifier (110). The pulse shaper further comprises a feedback circuit (118) connected in parallel with the amplifier; a first switching unit (120) connected in series with the feedback circuit; a second switching unit (122) connected in parallel with the amplifier; a discriminator circuit (124) that provides a discriminator signal (128) when the output exceeds a controllable signal threshold; and a control unit (124) for controlling the first switching unit and the second switching unit, wherein the control unit controls the second switching unit such that a substantial part of the signal is integrated, when the second switching unit is closed.

Disclosed herein is a radiological instrument (100, 200, 300, 400, 600, 700, 800) comprising at least one pulse shaper circuit (102) configured for a direct conversion radiation detector (108). The at least one pulse shaper circuit comprises an amplifier (110). The pulse shaper further comprises a feedback circuit (118) connected in parallel with the amplifier; a first switching unit (120) connected in series with the feedback circuit; a second switching unit (122) connected in parallel with the amplifier; a discriminator circuit (124) that provides a discriminator signal (128) when the output exceeds a controllable signal threshold; and a control unit (124) for controlling the first switching unit and the second switching unit, wherein the control unit controls the second switching unit such that a substantial part of the signal is integrated, when the second switching unit is closed.

Described herein is the use of a biased suitable ferrimagnetic crystal or suitable ferromagnetic crystal, for example, a hexaferrite ferrimagnetic semiconductive crystal for detection of the radiation on GHz frequencies. Specifically, the frequency of either ferromagnetic or multidomain resonance of the hexaferrite semiconductor crystal can be changed as a result of electric current flow and the value of current can be calculated based on the frequency shift measurement. This principle can be used for radiation detection.

According to one embodiment, a radiation detector includes first and second resin members, a detection part, a wiring part, and a controller. The first resin member includes first and second partial regions, and a third partial region between the first and second partial regions. The second resin member includes fourth and fifth partial regions. The detection part is provided between the first and fourth partial regions. The detection part includes a first conductive layer, a second conductive layer provided between the first conductive layer and the fourth partial region, and an organic semiconductor layer provided between the first and second conductive layers. The wiring part is provided between the third and fifth partial regions. The wiring part includes first and second wiring layers. The controller is fixed to the second partial region. The controller is electrically connected with the first and second wiring layers.

In general, an X-ray imaging apparatus according to one embodiment includes an X-ray tube, an X-ray detector, and processing circuitry. The processing circuitry is configured to obtain correction-target data that includes component deterioration resulting from a transient response of the X-ray detector, and to output, based on the obtained correction-target and a model that outputs data in which component deterioration resulting from a transient response is reduced based on an input of data that includes component deterioration resulting from a transient response, corrected data in which the component deterioration resulting from the transient response of the X-ray detector is reduced.

A detection device for detecting at least the occurrence and location of occurrence of sensor element signals that are generated by sensor elements, includes an array of detector element circuits each generating a element row output and at least one element column output. The detection device determines, for each row of detector element circuits, at least a first row summation signal corresponding to a sum of the element row outputs of the detector element circuits of this row, and a row address signal indicating that the first row summation signal crosses a threshold. The detection device also determines, for each column of detector element circuits, at least a first column summation signal corresponding to a sum of the element column outputs of the detector element circuits of this column, and a column address signal indicating that the first column summation signal crosses a threshold.

Disclosed is a photosensitive component, including: an intrinsic layer; a first doped layer provided on a light incident side of the intrinsic layer; and a second doped layer provided on a light exit side of the intrinsic layer; the intrinsic layer, the first doped layer and the second doped layer are all doped with a dopant, and silicon ions are injected into the intrinsic layer, the first doped layer and the second doped layer. An X-ray detector and a display device are further disclosed.

Various aspects include methods compensating for Compton scattering effects in pixel radiation detectors. Various aspects may include determining whether gamma ray detection events occurred in two or more detector pixels within an event frame, determining whether the gamma ray detection events occurred in detector pixels within a threshold distance of each other in response to determining that gamma ray detection events occurred in two or more detector pixels within the event frame, and recording the two or more gamma ray detection events as a single gamma ray detection event having an energy equal to the sum of measured energies of the two or more gamma ray detection events located in a detector pixel having a highest measured energy in response to determining that the gamma ray detection events occurred in detector pixels within the threshold distance of each other.