An array substrate for a digital X-ray detector, a digital X-ray detector including the same, and a method for manufacturing the same are disclosed. The array substrate reduces a step difference of a PIN diode, removes a bent part from a lower part to reduce characteristic deterioration of the PIN diode, and increases the size of a formation region of the PIN diode to increase a fill factor. To this end, the array substrate allows a source region of an active layer included in a thin film transistor to be in surface contact with a lower electrode of the PIN diode, and disposes the lower electrode over a planarized source region or a base substrate, such that a step difference of the PIN diode is reduced and fill factor is improved.

According to one embodiment, a photoelectric conversion element includes a first conductive layer, a second conductive layer, and an intermediate layer provided between the first conductive layer and the second conductive layer. The intermediate layer includes a first semiconductor region and a second semiconductor region. The first semiconductor region is of an n-type, and the second semiconductor region is of a p-type. The first semiconductor region includes at least one selected from the group consisting of fullerene and a fullerene derivative. The second semiconductor region includes at least one selected from the group consisting of quinacridone and a quinacridone derivative. A ratio of a weight of the second semiconductor region per unit volume to a weight of the first semiconductor region per unit volume in the intermediate layer is greater than 5.

An image acquiring device includes a camera that scans radiation passing through a subject in one direction and captures an image of the radiation to acquire an X-ray image, a scintillator layer provided on the camera to convert X-rays into light, and a control device that executes noise removal processing of removing noise from the X-ray image. The camera includes N (N is an integer equal to or greater than 2) pixels arrayed in a direction orthogonal to the one direction to detect the light and output detection signals, and a readout circuit that outputs the X-ray image by outputting the detection signal for each of the N pixels. The scintillator layer includes P (P is an integer equal to or greater than 2) scintillator units disposed separately to correspond to the N pixels and a separation unit disposed between the P scintillator units.

A positron emission tomography (PET) scanner may include a plurality of gamma radiation detector modules arranged to form a detector ring. Each detector module may include an array of elongated scintillation crystals. With respect to the detector ring, each elongated scintillation crystal includes a proximal end-face, two axially oriented lateral faces, two transaxially oriented lateral faces, and a distal end-face radially oriented into the detector ring to receive a gamma photon. An array of photosensors is positioned along a first of the axially oriented lateral faces of each elongated scintillation crystal to detect scintillation photons. A reflective material is positioned on the proximal end-face, the distal end-face, the transaxially oriented lateral faces, and a second of the axially oriented lateral faces of each elongated scintillation crystal to internally reflect scintillation photons. In various embodiments, a dual-channel processing circuit provides distinct timing and energy signals from the photosensors.

A dynamic X-ray detecting panel, an X-ray detector including the same, and a method of driving an X-ray detector are disclosed. The method of driving the X-ray detector is a method of driving a dynamic X-ray detector including the X-ray detecting panel. The X-ray detecting panel includes multiple pixels arranged in a matrix, each of the pixels includes a readout thin film transistor, a reset thin film transistor, and a photodiode, and line reset, window time, and readout proceed with respect to the multiple pixels in each row.

A positron emission tomography imaging system (100) includes a plurality of detector elements (130.sub.1..i) and a plurality of compute elements (140.sub.1..j). Each compute element (140.sub.1..j) comprises one or more of the detector elements (130.sub.1..i), and the compute elements (140.sub.1..j) are arranged around the bore (110) of the PET imaging system. Each compute element (140.sub.1..j) includes a first communication path (160.sub.1..j) coupling the compute element to an adjacent compute element in a5circumferential direction around the bore, and a second communication path (170.sub.1..e) coupling the compute element to a non-adjacent compute element in the circumferential direction. Each computeelement (140.sub.1..j) includes a processor configured to receive the event data generated by its one or more detector elements (130.sub.1..i), and to communicate the event data to the processor of its adjacent computeelement, and to the processor of its non-adjacent compute element, via its first communication path10(160.sub.1..j), and via its second communication path (170.sub.1..j), respectively.

A flat pixel (20) is a single unit composing a radiation detector and is configured so as to be divided into at least four subpixels (21) such that even if a prescribed number of subpixels (21) are removed from each pixel (20) in order of largest effective area, the centroid (51) of the effective area of the entirety of the remaining subpixels (21) is positioned within a similar-shape region (30) having the same centroid (50) as the pixel (20) and having sides of lengths that are half those of the pixel (20).

A semiconductor photomultiplier (SPM) device is described. The SPM comprises a plurality of photosensitive elements, a first electrode arranged to provide a bias voltage to the photosensitive elements, a second electrode arranged as a biasing electrode for the photosensitive elements, a plurality of quench resistive elements each associated with a corresponding photosensitive element, a plurality of output loads; a first node of each output load is common to one of the photosensitive elements and the corresponding quench element; and a third electrode provides an output signal from the photosensitive elements; the third electrode is coupled to a second node of the respective output loads; the outputs loads fully or partially correct an overshoot of the output signal on the third electrode.

The present disclosure relates to a detection device and electronic equipment, in which a detection accuracy of minute light can be improved. A detection device includes: a pixel array portion in which a plurality of first pixels including a photoelectric conversion unit, and a plurality of second pixels not including a photoelectric conversion unit, are arranged; and a driving unit configured to drive the first pixel and the second pixel. The present technology, for example, can be applied to a light detector, a radiation counter device performing radiation counting by using the light detector, and a biological examination device using the light detector, such as a flow cytometer.

An electromagnetic radiation detection device comprises a matrix having a plurality of N rows divided into a plurality of M columns of cells, each cell comprising a plurality of diode segments responsive to electromagnetic radiation incident on said device. A scan driver provides a plurality of N scan line signals to respective rows of said matrix, each for enabling charge values from cells of a selected row of said matrix to be read. A reader reads a plurality of M variable charge value signals from respective columns of said matrix, each corresponding to a cell within a selected row of said matrix. Each diode segment is connected to a drive voltage sufficient to operate each diode segment in avalanche multiplication Geiger mode; and connected in series with an avalanche quenching resistor to said reader.