Koninklijke Philips Corporation N.V.

Ami Altman

Simha Levene

Naor Wainer

Dagobert Michel De Leeuw

Olga Shapiro

Cornelis Reinder Ronda

Rodney Arnold Mattson

Eliav Itzhak Haskal

Eliav Itshak Haskal

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.

Imaging measurement system with a printed photodetector array

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.

Imaging measurement system with a printed organic photodiode array

A radiation detector () includes a two-dimensional array of upper scintillators (&#x3c4;) which is disposed facing an x-ray source () to convert lower energy radiation events into visible light and transmit higher energy radiation. A two-dimensional array of lower scintillators () is disposed adjacent the upper scintillators (&#x3c4;) distally from the x-ray source () to convert the transmitted higher energy radiation into visible light. Upper and lower photodetectors () are optically coupled to the respective upper and lower scintillators () at an inner side () of the scintillators (). An optical element () is optically coupled with the upper scintillators (&#x3c4;) to collect and channel the light from the upper scintillators (&#x3c4;) into corresponding upper photodetectors (&#x3c4;).

Detector array for spectral CT

A radiation detector () includes a two-dimensional array of upper scintillators (&#x3c4;) which is disposed facing an x-ray source () to convert lower energy radiation into visible light and transmit higher energy radiation. A two-dimensional array of lower scintillators (B) is disposed adjacent the upper scintillators (&#x3c4;) distally from the x-ray source () to convert the transmitted higher energy radiation into visible light. Respective active areas () of each upper and lower photodetector arrays (B) are optically coupled to the respective upper and lower scintillators (B) at an inner side () of the scintillators (B) which inner side () is generally perpendicular to an axial direction (Z). Interference filters () may be deposited on the active areas () of the associated upper and lower photodetectors (B) to restrict radiation wavelengths received by the upper and lower photodetectors (B) to wavelengths emitted by the respective upper and lower scintillators (B). The upper scintillators (&#x3c4;) may include at least one of ZnSe(Te) and YAG(Ce).

Double decker detector for spectral CT

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

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Tel Aviv, Israel

Ami Altman