An X-ray detector assembly includes a polymeric substrate having a lower surface and an upper surface, and an X-ray detector disposed on the upper surface of the polymeric substrate. The X-ray detector includes a thin-film-transistor array disposed on the substrate, an organic photodiode disposed on the thin-film-transistor array, and a scintillator disposed on the organic photodiode. A metal barrier extends substantially over the lower surface of the polymeric substrate.

The invention achieves preventing from moisture penetration into an imaging panel without deterioration in detection accuracy of scintillation light. An imaging panel includes an active matrix substrate having a plurality of pixels each provided with a photoelectric conversion element, a scintillator provided on a surface of the active matrix substrate, a damp-proof material covering the active matrix substrate and the scintillator, and an adhesive layer bonding the damp-proof material to the scintillator and the active matrix substrate. The active matrix substrate includes a first flattening film overlapped in a planar view with the scintillator and configured as a photosensitive resin film. The first flattening film is entirely disposed, in a planar view, inside an adhesive layer region provided with the adhesive layer.

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 imaging system. The imaging system can comprise: a scintillator structure; and an electronic device engaged with the scintillator structure, wherein: the scintillator structure can comprise: a scintillator support layer; and a scintillator layer; the scintillator support layer can comprise: a first substantially non-planar surface; and a second substantially non-planar surface, the first substantially non-planar surface can be approximately parallel to the second substantially non-planar surface; the electronic device can comprise a device substrate and one or more active sections; the device substrate can comprise a first surface and a second surface opposite the first surface of the device substrate; the one or more active sections are at the second surface of the device substrate; and the second surface of the device substrate and the one or more active sections can conform to the second surface of the scintillator layer. Other embodiments are described herein.

An imaging detector is provided that includes a continuous NaI crystal, a glass plate, an array of SiPMs, and an array of concentrators. The continuous NaI crystal defines a reception side and a detection side. The glass plate is disposed on the detection side of the continuous NaI crystal, and is interposed between the detection side of the continuous NaI crystal and the array. The array of concentrators corresponds to the array of SiPMs, and is interposed between the array of SiPMs and the glass plate. Each concentrator has a reception side opening that is larger than a detection side opening, with the detection side opening disposed proximate to a corresponding SiPM.

A radiation detection apparatus may include a scintillator to emit scintillating light in response to absorbing radiation, a photosensor to generate an electronic pulse in response to receiving the scintillating light, and a reflector surrounding the photosensor. The photosensor may be coupled to a wiring board and the reflector may be coupled to the wiring board. The radiation detection apparatus can be more compact and more rugged as compared to radiation detection apparatuses that include a photomultiplier tube.

A protection film covering a scintillator has at least a plurality of metal atoms, an oxygen atom, and a hydrophobic functional group, a certain metal atom of the plurality of metal atoms is bonded to the other metal atom of the plurality of metal atoms through the oxygen atom, the hydrophobic functional group has a carbon atom, and the carbon atom is bonded to any one of the plurality of metal atoms.

A radiation detector has a photoelectric conversion element array having a light receiving unit and a plurality of bonding pads; a scintillator layer stacked on the photoelectric conversion element array; a resin frame formed on the photoelectric conversion element array so as to pass between the scintillator layer and the bonding pads away from the scintillator layer and the bonding pads and so as to surround the scintillator layer; and a protection film covering the scintillator layer and having an outer edge located on the resin frame; a first distance between an inner edge of the resin frame and an outer edge of the scintillator layer is shorter than a second distance between an outer edge of the resin frame and an outer edge of the photoelectric conversion element array; the outer edge and a groove are processed with a laser beam.

A flexible digital radiographic detector with a flexible multi-layered core including a two-dimensional array of photo-sensitive cells, a flexible enclosure enveloping the multi-layered core to facilitate conforming the radiographic detector to a curved surface. A shaped flexible sleeve can receive the digital radiographic detector to conform the detector against a surface of a preselected structure.

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.