Techniques are provided for x-ray sensing for intraoral tomography. A methodology implementing the techniques according to an embodiment includes detecting an x-ray pulse based on energy received at one or more pixels of a pixel array. The method also includes integrating the energy received at each of the pixels of the array of pixels, in response to the detection, wherein the energy received at each of the pixels is associated with the x-ray pulse. The method further includes multiplexing readouts of analog signals from the array of pixels into two or more parallel channels. The method further includes simultaneously converting (or otherwise in parallel) the analog signals of each of the channels into digital signals and storing the digital signals in memory as frames of data. The method may further include, for example, transmitting the frames of data from the memory, over a Universal Serial Bus, to an imaging system.

Techniques are provided for x-ray image data monitoring and signaling for patient safety. A methodology implementing the techniques according to an embodiment includes integrating energy associated with a received x-ray pulse at an array of pixels. The method also includes multiplexing a readout of the integrated energy from the array of pixels, as analog signals, into channels, and performing analog to digital conversion of the analog signals of the channels into digital signals. The method further includes generating an error indicator in response to determining that a calculated mean of the digital signals is either greater than an upper threshold value associated with saturation or less than a lower threshold value associated with underexposure. The method further includes transmitting the error indicator over a Universal Serial Bus, to an imaging system, to terminate transmission of further x-ray pulses.

A radiation detector can include a scintillator having opposing end surfaces and a plurality of discrete photosensors disposed on an end surface of the scintillator. In an embodiment, the photosensors are disposed at the corners or along the peripheral edge of the end surface, as opposed to being disposed at the center of the end surface. In an embodiment, the plurality of discrete photosensors may cover at most 80% of a surface area of the end surface of the scintillator and may not cover a center of the end surface of the scintillator. In a further embodiment, an aspect ratio of the monolithic scintillator can be selected to improve energy resolution.

Provided are a system and method for combining detector signals. In one exemplary embodiment, the system includes the detector, a plurality of ASICs where each ASIC may receive an electric signal from the detector and generate a position signal and an energy signal based on the received electric signal, a combiner that may combine a position signal output from a first ASIC and a position signal output from a second ASIC to generate a combined position signal, and combine an energy signal output from the first ASIC and an energy signal output from the second ASIC to generate a combined energy signal, and an analog-to-digital converter that may receive the combined position signal and the combined energy signal and generate digitized image data for the first ASIC and the second ASIC based thereon.

An electronic cassette has a detection panel (light detection substrate) in which pixels for accumulating electric charges corresponding to radiation are arranged. The electronic cassette includes two gate control circuits that control an operation of a gate drive circuit, a power supply circuit that supplies power to the gate control circuits, a first wiring line, and a second wiring line. The first wiring line connects the power supply circuit and each of two gate control circuits to each other, and supplies each of two gate control circuits with the power supplied from the power supply circuit. The second wiring line connects two gate control circuits to each other. The power supplied from the power supply circuit to one of two gate control circuits is diverted to the other, through the second wiring line.

A radiation detector has reflection materials that segment a scintillator array to respective areas, a first accumulator 41, which adds multiple signals amplified by amplifiers 30 in the area segmented by the reflection materials, per area segmented by the reflection materials, a first trigger generation circuit 42, that generates a trigger of the signals added by the first accumulator, per area segmented by the reflection materials. When the signals are added, the superimposition of the inherent noises of each amplifier 30 can be reduced as much as the area segmented by the reflection materials, so that the signal noise can be reduced by increasing the S/N (signal/noise) ratio. The signals (timing signals) are respectively and separately generated based on each trigger in the different area to each other and converged by the encoder 50, so that probability of pileup (multiple pileups) can be reduced and an accurate timing signal can be obtained.

A digital radiographic detector includes redundant bonding pads formed on the array substrate and electrically connected to the array of photosensors. A plurality of COFs are each electrically connected to one of the bonding pads. A repair may be performed by removing a bond pad and reconnecting a corresponding COF to a redundant bond pad. A PCB including array read out electronics is electrically connected to the plurality of COFs.

Among other things, a detector unit for a detector array of a radiation imaging modality is provided. In some embodiments, the detector unit comprises a radiation detection sub-assembly and an electronics sub-assembly. The electronics sub-assembly comprises electronic circuitry, embedded within a molding compound, configured to digitize analog signals yielded from the radiation detection sub-assembly and/or to otherwise process such analog signals. The electronics sub-assembly also comprises a substrate, such as a printed circuit board, configured to route signals between the electronic circuitry and a photodetector array of the radiation detection sub-assembly and/or to route signals between the electronic circuitry and digital processing components, such as an image generator, for example.

According to embodiment, an X-ray computed tomography apparatus includes an X-ray tube, an X-ray detector including a scintillator generating scintillation light upon incidence of X-ray photons and a photodetection element, a peak value detector detecting peak values corresponding to X-ray photons based on an output signal from the element, processing circuitry determining an attenuation characteristic of the light by each X-ray photon and an output decreased characteristic of the element, based on the values and time when each peak value was detected, correcting the detected values according to the characteristics, a counter counting the X-ray photons corresponding to the respective corrected peak values, wherein the processing circuitry reconstructs a medical image based on an output from the counter.

An organic charge integrating device is presented. The organic charge integrating device includes a thin film transistor (TFT) array, a first electrode layer disposed on the TFT array, an organic photoactive layer disposed on the first electrode layer, and a second electrode layer disposed on the organic photoactive layer. The organic photoactive layer has a thickness in a range from about 700 nanometers to about 3 microns. An organic x-ray detector is presented. An imaging system including the organic x-ray detector is also presented.