A digital radiographic detector includes a planar multi-layered core with a two-dimensional array of photo-sensitive cells. A five-sided, integrally formed, rigid enclosure having one open side is configured to receive the multi-layered core through the open side. The planar multi-layered core comprises a foam layer having a recessed pocket on one major side thereof shaped in the form of a metal ground plane positioned in the recessed pocket.

A scintillation crystal can include a rare earth silicate, an activator, and a Group 2 co-dopant. In an embodiment, the Group 2 co-dopant concentration may not exceed 200 ppm atomic in the crystal or 0.25 at % in the melt before the crystal is formed. The ratio of the Group 2 concentration/activator atomic concentration can be in a range of 0.4 to 2.5. In another embodiment, the scintillation crystal may have a decay time no greater than 40 ns, and in another embodiment, have the same or higher light output than another crystal having the same composition except without the Group 2 co-dopant. In a further embodiment, a boule can be grown to a diameter of at least 75 mm and have no spiral or very low spiral and no cracks. The scintillation crystal can be used in a radiation detection apparatus and be coupled to a photosensor.

Some embodiments include an electronic device. The electronic device includes a first scintillator layer, a transistor, and one or more device elements over the transistor, and the one or more device elements include a photodetector. Meanwhile, the first scintillator layer is monolithically integrated with at least one of the transistor or the one or more device elements. Other embodiments of related systems, devices, and methods are also disclosed.

An active matrix substrate includes a photoelectric conversion element 12, a first planarizing film 107, a first inorganic insulating film 108a, and a bias wire 16. The first planarizing film 107 covers the photoelectric conversion element 12 and has a first opening 107h at a position at which the first opening 107h overlaps with the photoelectric conversion element 12 in plan view. The first inorganic insulating film 108a has a second opening on an inner side of the first opening h and covers a surface of the first planarizing film 107. The bias wire 16 is provided on a first inorganic insulating film 108a and is connected to the photoelectric conversion element 12 via the second opening CH2.

Provided is a radiation detector including a substrate including a sensor unit layer having a plurality of pixels for accumulating electric charges generated depending on light converted from radiation in a pixel region of a flexible base material; a conversion layer that is provided on a surface side of the base material provided with the pixel region to convert the radiation into light; and a fixing member that is provided closer to the substrate side than the conversion layer to fix the sensor unit layer to the base material.

A flexible DR detector assembly bendable along one axis and not bendable along a second axis is used with an x-ray source for radiographic imaging of a human anatomy, veterinary anatomy, or industrial equipment.

A shock isolated gamma probe attenuates axial, lateral, and torsional shocks to a gamma sensor package. A gamma sensor is inserted into and fixed to a tubular cartridge. The cartridge is closed with a cap and keyed at the other end. The cartridge is inserted into a resilient sleeve having an extension at the closed end to conform to the key on the cartridge. The open end of the resilient sleeve is closed with a gasket. The sleeve/cartridge assembly are inserted into a tubular structure on a first chassis. The first chassis has a keying structure for the key and extension of the resilient on an end bulkhead. The cartridge and first chassis are resiliently engaged to attenuate shocks. A second bulkhead, on a second chassis, closes the open end of the tubular structure on the first chassis.

A scintillation crystal can include a rare earth silicate, an activator, and a Group 2 co-dopant. In an embodiment, the Group 2 co-dopant concentration may not exceed 200 ppm atomic in the crystal or 0.25 at % in the melt before the crystal is formed. The ratio of the Group 2 concentration/activator atomic concentration can be in a range of 0.4 to 2.5. In another embodiment, the scintillation crystal may have a decay time no greater than 40 ns, and in another embodiment, have the same or higher light output than another crystal having the same composition except without the Group 2 co-dopant. In a further embodiment, a boule can be grown to a diameter of at least 75 mm and have no spiral or very low spiral and no cracks. The scintillation crystal can be used in a radiation detection apparatus and be coupled to a photosensor.

A scintillation apparatus design is provided which eliminates the requirement of an optical window between the scintillator and the photosensitive device. The disclosed design provides significantly improved performance with a scintillator mounted directly to the photosensitive device. Improved light coupling between the scintillator and the photosensitive device is achieved. The present disclosure improves the light transmission to the photosensitive device (PSD) by direct coupling of the photosensitive device to the scintillator. By eliminating the need for an optical window, light loss due to the glass interface caused by the optical window likewise may be eliminated. The improvement of light transmission to the PSD improves the gamma ray energy resolution. The quality of the gamma spectroscopy is improved with this design. Furthermore, providing the means and method for evacuating the internal assembly significantly improves the reliability and lifespan of the detector assembly.

An active matrix substrate 1 includes a plurality of detection circuitry. The detection circuitry includes a photoelectric conversion layer 15, a pair of a first electrode 14a and a second electrode 14b, a protection film 106, and a bias line 16. The protection film 106 covers a side end part of the photoelectric conversion layer 15, and overlaps with at least a part of the second electrode 14b. The bias line 16 is provided on an outer side of the photoelectric conversion layer 15. An electrode portion of the second electrode 14b that overlaps with the bias line 16 has at least one electrode opening 141h. The bias line 16 is in contact with the electrode portion of the second electrode 14b on an outer side of the photoelectric conversion layer 15, and is in contact with the protection film 106 in the electrode opening 141h.