Arineta Ltd.

Koninklijke Philips Corporation N.v.

Olga Shapiro

Ehud Dafni

David Ruimi

Naor Wainer

Simha Levene

Ami Altman

Rodney Arnold Mattson

Rafi Brada

A CT scanner with scatter correction device and a method for scatter correction are provided. The method comprises positioning shields for shielding some of the CT detector elements from direct X ray radiation, while allowing scattered radiation to arrive at said shielded elements; measuring scatter signals from said shielded elements, indicative of scattered radiation intensity; and correcting for scatter by subtracting scatter intensity values estimated from said measured scatter signals from signals measured by unshielded detector elements.

X ray imaging system with scatter radiation correction and method of using same

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 method for calibration of a CT comprises sequentially positioning a phantom having a non-circular cross section and a length commensurate with the extent of a detector at a plurality of positions between an X ray source and the detector array or sequentially positioning a plurality of generally similar phantoms or sequentially positioning a same phantom at a plurality of positions between the X ray source and detector array of the CT scanner; acquiring calibration attenuation data for X rays that have been attenuated by traversing the phantom positioned at each of the plurality of positions; and calculating calibration corrections for CT scanner scan data from the calibration attenuation data.

Method for calibration of a CT scanner

A CT scanner includes a first X-ray beam source, and a second X-ray beam source. With such an apparatus, first source is used to monitor buildup of an injected contrast agent in a selected region of interest relative to a patient and at least the second source is used to perform diagnostic scanning when the buildup of the contrast agent reaches a desired level.

CT scanner using injected contrast agent and method of use

A CT scanner with scatter correction device and a method for scatter correction are provided. The method of correcting CT images from artifacts caused by scattered radiation comprises affixing to the non-rotating frame of the CT gantry a plurality of shields for shielding some of the CT detector elements from direct X ray radiation, while allowing scattered radiation to arrive at said shielded elements; measuring scatter signals from said shielded elements, indicative of scattered radiation intensity; and correcting for scatter by subtracting scatter intensity values estimated from said measured scatter signals from signals measured by unshielded detector elements.

CT scanner with scatter radiation correction and method of using same

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

X-rays from an x-ray tube ( ) pass through an examination region ( ) and are detected by a single or two-dimensional x-ray detector ( ). The x-ray detector ( ) includes an array ( ) of photodiodes, CCD devices, or other opto-electrical transducer elements. A matching array ( ) of transparent scintillator crystals, e.g., CdWO , is supported on and optically coupled to the photoelectric transducer array. A layer ( ) of a high efficiency scintillator with a good spectral match with the opto-electrical transducer array but with limited light transmissiveness is optically coupled to the transparent scintillator array. The layer ( ) is preferably zinc selenide ZnSe (Te). Electrical signals from the transducer array are reconstructed ( ) into an image representation and converted into a human-readable display ( ). To reduce cross-talk, the zinc selenide layer is etched with pits ( ), sliced into strips ( &prime;), cut into rectangles ( &Prime;), or has channels ( ) cut into it. Scatter grids ( ) are advantageously received in the channels. Alternately, the zinc selenide can be powdered, encased in a transparent binder, and applied as a coating layer ( &Prime;&prime;) to the individual transparent scintillator elements.

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Haifa, Israel

Olga Shapiro