Abstract: A radiation detector (24) includes a two-dimensional array of upper scintillators (30?) which is disposed facing an x-ray source (14) to convert lower energy radiation events into visible light and transmit higher energy radiation. A two-dimensional array of lower scintillators (30B) is disposed adjacent the upper scintillators (30?) distally from the x-ray source (14) to convert the transmitted higher energy radiation into visible light. Upper and lower photodetectors (38?, 30B) are optically coupled to the respective upper and lower scintillators (30?,30B) at an inner side (60) of the scintillators (30?,30B). An optical element (100) is optically coupled with the upper scintillators (30?) to collect and channel the light from the upper scintillators (30?) into corresponding upper photodetectors (38?).

Abstract: A radiation-sensitive detector includes a photosensor layer with one or more photosensor dixels and a composite scintillator layer with one or more scintillator dixels optically coupled to the photosensor layer. The composite scintillator layer is formed from a mixture including a scintillator material having a first refractive index corresponding to a first wavelength and a photo-resist used in micro-electromechanical systems production, having a second refractive index corresponding to the first wavelength. The first and second refractive indices are substantially matched, and the composite scintillator layer produces light having the first wavelength and that is indicative of x-radiation detected thereby.

Abstract: A radiation-sensitive detector includes a photosensor elements (122) and a scintillator (116) optically coupled to the photosensor element (122). The scintillator (116) includes a powdered scintillator and a resin mixed with the powdered scintillator. The refractive index mismatch between the powdered scintillator and the resin is less than 7%. In one non-limiting instance, the composite scintillator material may be used to form fiber optic leaves arranged as a high-resolution detector array in conventional or spectral CT.

Abstract: A radiation-sensitive detector includes a photosensor layer with one or more photosensor dixels and a composite scintillator layer with one or more scintillator dixels optically coupled to the photosensor layer. The composite scintillator layer is formed from a mixture including a scintillator material having a first refractive index corresponding to a first wavelength and a photo-resist used in micro-electromechanical systems production, having a second refractive index corresponding to the first wavelength. The first and second refractive indices are substantially matched, and the composite scintillator layer produces light having the first wavelength and that is indicative of x-radiation detected thereby.

Abstract: Low cost large area photodetector arrays are provided. In a first embodiment, the photodetectors comprise an inorganic photoelectric conversion material formed in a single thick layer of material. In a second embodiment, the photodetectors comprise a lamination of several thin layers of an inorganic photoelectric conversion material, the combined thickness of which is large enough to absorb incoming x-rays with a high detector quantum efficiency. In a third embodiment, the photodetectors comprise a lamination of several layers of inorganic or organic photoelectric conversion material, wherein each layer has a composite scintillator coating.

Abstract: An imaging system includes a macro organic photodiode array with rows and columns of printed photodiodes. The array may be bendable for easy manufacture and assembly on a curved support within an imaging system. Two or more layers of photodiodes may be provided for use in a spectral CT imaging system or as slices.

Abstract: A host lattice modified GOS scintillating material and a method for using a host lattice modified GOS scintillating material is provided. The host lattice modified GOS scintillating material has a shorter afterglow than conventional GOS scintillating material. In addition, a radiation detector and an imaging device incorporating a host lattice modified GOS scintillating material are provided.

Abstract: A radiation detector (24) includes a two-dimensional array of upper scintillators (30?) which is disposed facing an x-ray source (14) to convert lower energy radiation into visible light and transmit higher energy radiation. A two-dimensional array of lower scintillators (30B) is disposed adjacent the upper scintillators (30?) distally from the x-ray source (14) to convert the transmitted higher energy radiation into visible light. Respective active areas (94, 96) of each upper and lower photodetector arrays (38?, 38B) are optically coupled to the respective upper and lower scintillators (30?, 30B) at an inner side (60) of the scintillators (30?, 30B) which inner side (60) is generally perpendicular to an axial direction (Z).

Abstract: A system comprises a radiation source (110), including a anode (112) and a cathode (114), a high voltage generator (202) that generates a source voltage that is applied across the anode (112) and cathode (114), wherein the source voltage accelerates electrons from the cathode (114) towards the anode (112), and a modulation wave generator (204) that generates a modulation voltage wave having a non-zero amplitude, which is combined with and modulates the source voltage between at least two different voltages.

Abstract: The invention relates to a light-reflecting material (240) of a radiation detector (200), which also comprises photo-detecting elements (220) and imaging elements (250) adjacent to the photo-detecting elements. Typically, epoxy resin is used as the light-reflecting material. According to the invention, a tough, pliable resin may be used for the photo-detecting elements. This has the advantage of reducing thermal stresses inside the radiation detector, thus reducing the risk of delamination due to e.g. temperature shifts. Moreover, the tough, pliable resin preferably also has a low refractive index, which may increase the scattering co-efficient of the resin as compared to epoxy resin, which has a refractive index of 1.58. The layer thickness of a low-refractive index resin may thereby be reduced as compared to the layer thickness of epoxy resin for a given level of optical crosstalk. Preferable resins are silicon resins and resins of thermoplastic fluoropolymers.

Abstract: A radiation-sensitive detector includes a photosensor elements (122) and a scintillator (116) optically coupled to the photosensor element (122). The scintillator (116) includes a powdered scintillator and a resin mixed with the powdered scintillator. The refractive index mismatch between the powdered scintillator and the resin is less than 7%. In one non-limiting instance, the composite scintillator material may be used to form fiber optic leaves arranged as a high-resolution detector array in conventional or spectral CT.

Abstract: A radiation detector (24) includes a two-dimensional array of upper scintillators (30?) which is disposed facing an x-ray source (14) to convert lower energy radiation events into visible light and transmit higher energy radiation. A two-dimensional array of lower scintillators (30B) is disposed adjacent the upper scintillators (30?) distally from the x-ray source (14) to convert the transmitted higher energy radiation into visible light. Upper and lower photodetectors (38?, 30B) are optically coupled to the respective upper and lower scintillators (30?,30B) at an inner side (60) of the scintillators (30?,30B). An optical element (100) is optically coupled with the upper scintillators (30?) to collect and channel the light from the upper scintillators (30?) into corresponding upper photodetectors (38?).

Abstract: A radiation-sensitive detector (120) includes a scintillator array (124) coupled with a photosensor array (140) via an adhesive laminate (144). The photosensor (140) has a plurality of dixels (136). The adhesive laminate (144) includes a material free region that extends through the adhesive laminate (144) from the scintillator array (124) to the photosensor array (140) and that is located between a pair of adjacent dixels (136).

Abstract: A radiation-sensitive detector includes a photosensor layer with one or more photosensor dixels and a composite scintillator layer with one or more scintillator dixels optically coupled to the photosensor layer. The composite scintillator layer is formed from a mixture including a scintillator material having a first refractive index corresponding to a first wavelength and a photo-resist used in micro-electromechanical systems production, having a second refractive index corresponding to the first wavelength. The first and second refractive indices are substantially matched, and the composite scintillator layer produces light having the first wavelength and that is indicative of x-radiation detected thereby.

Abstract: A radiation detector (24) for an imaging system includes a two-dimensional array (50) of nondeliquescent ceramic scintillating fibers or sheets (52). The scintillating fibers (52) are manufactured from a GOS ceramic material. Each scintillating fiber (52) has a width (d2) between 0.1 mm and 1 mm, a length (h2) between 0.1 mm and 2 mm and a height (h8) between 1 mm and 2 mm. Such scintillating fiber (52) has a height (h8) to cross-sectional dimension (d2, h2) ratio of approximately 10 to 1. The scintillating fibers (52) are held together by layers (86, 96) of a low index coating material. A two-dimensional array (32) of photodiodes (34) is positioned adjacent and in optical communication with the scintillating fibers (52) to convert the visible light into electrical signals. A grid (28) is disposed by the scintillating array (50). The grid (28) has the apertures (30) which correspond to a cross-section of the photodiodes (34) and determine a spatial resolution of the imaging system.

Abstract: An x-ray detector array (102) includes a plurality of detector elements or dixels (100). Each detector element includes a first scintillator (1061) a second scintillator (1062), a first photodetector (1101), and a second photodetector (1102). The first and second photodetectors (1101, 1102) are disposed at the side of the respective first and second scintillators (1061, 1062). The photodetectors (1101, 1102) of a plurality of detector elements (100) are carried by a circuit board (103) such as a thin flexible circuit.

Abstract: A radiation detector (24) includes a two-dimensional array of upper scintillators (30?) which is disposed facing an x-ray source (14) to convert lower energy radiation into visible light and transmit higher energy radiation. A two-dimensional array of lower scintillators (30B) is disposed adjacent the upper scintillators (30?) distally from the x-ray source (14) to convert the transmitted higher energy radiation into visible light. Respective active areas (94, 96) of each upper and lower photodetector arrays (38?, 38B) are optically coupled to the respective upper and lower scintillators (30?, 30B) at an inner side (60) of the scintillators (30?, 30B) which inner side (60) is generally perpendicular to an axial direction (Z).

Abstract: An X-ray collimator for collimating X-rays from an X-ray source that illuminate an array of columns and rows of X-ray detectors, the collimator having a first side that faces the X-ray source and a second side opposite the first side that faces the detector array, the collimator comprising: a plurality of strips formed from an X-ray absorbing material, wherein each strip is corrugated so that it has rectangular and/or square corrugations; and means for maintaining the plurality of strips one next to the other with the corrugations of one strip aligned with corrugations of an adjacent strip to form an array of rows and columns of square/and or rectangular wells corresponding to the X-ray detectors in the array.

Abstract: A radiation detector (24) for an imaging system includes a two-dimensional array (50) of nondeliquescent ceramic scintillating fibers or sheets (52). The scintillating fibers (52) are manufactured from a GOS ceramic material. Each scintillating fiber (52) has a width (d2) between 0.1 mm and 1 mm, a length (h2) between 0.1 mm and 2 mm and a height (h8) between 1 mm and 2 mm. Such scintillating fiber (52) has a height (h8) to cross-sectional dimension (d2, h2) ratio of approximately 10 to 1. The scintillating fibers (52) are held together by layers (86, 96) of a low index coating material. A two-dimensional array (32) of photodiodes (34) is positioned adjacent and in optical communication with the scintillating fibers (52) to convert the visible light into electrical signals. A grid (28) is disposed by the scintillating array (50). The grid (28) has the apertures (30) which correspond to a cross-section of the photodiodes (34) and determine a spatial resolution of the imaging system.

Abstract: An x-ray tube (16) suitable for use in a computed tomography (CT) scanner (10) includes an envelope (42) which defines an evacuated chamber. An anode (40) and a cathode assembly (70) are disposed within the chamber. The anode defines a target area (56) which is struck by electrons (52) emitted by a filament (54) of the cathode assembly and emits x-rays (46). The target area lies partially on a first annular portion (80) which is disposed at first angle (a) relative to a plane perpendicular to an axis of rotation (R) of the anode, and partially on a second portion (82,120) which is radially spaced from the first portion and disposed at a second angle (?), relative to the plane. The second angle is greater than the first angle. The portions of different slope allow the x-ray tube to take advantage of a shallow angle, while minimizing the heel effect.