Koninklijke Philips Corporation N.v.

Picker International, Inc.

Picker Corporation

Other

Koninklijke Philips Electronics N.v.

Rodney Arnold Mattson

Randall Peter Luhta

Marc Anthony Chappo

Carl J Brunnett

Brian E Harwood

Theodore A Resnick

Chris Vrettos

Gordon D DeMeester

Jerome R Cox, Jr

Heang K Tuy

Pieter Gerhard Roos

Donald L Snyder

William Charles Brunnett

Dominic J Heuscher

Todd J Krochta

Richard A Sones

Jeffrey Harold Yanof

Lester Donald Miller

Simha Levene

James E Burke

Donald E Negrelli

Olga Shapiro

Karen L Lauro

Robert E Levar

Ami Altman

Sung-Cheng Huang

Andrew J Ivan, Jr

Narasimharao Koka

P Gerhard Roos

Paula I Patel

David A Wilcox

Leslie J Williams

Randall P Lutha

Chris John Vrettos

William C Brunnett

A one-dimensional multi-element photo detector includes a photodiode array with a first upper row of photodiode pixels and a second lower row of photodiode pixels. The photodiode array is part of the photo detector. A scintillator array includes a first upper row and a second lower row of scintillator pixels. The first upper and second lower rows of scintillator pixels are respectively optically coupled to the first upper and second lower rows of photodiode pixels. The photo detector also includes readout electronics, which are also part of the photo detector. Electrical traces interconnect the photodiode pixels and the readout electronics.

Spectral imaging detector

A method includes obtaining a photosensor substrate () having two opposing major surfaces. One of the two opposing major surfaces includes at least one photosensor row () of at least one photosensor element (), and the obtained photosensor substrate has a thickness equal to or greater than one hundred microns. The method further includes optically coupling a scintillator array () to the photosensor substrate. The scintillator array includes at least one complementary scintillator row () of at least one complementary scintillator element (), and the at least one complementary scintillator row is optically coupled to the at least one photosensor row () and the at least one complementary scintillator element is optically coupled to the at least one photosensor element. The method further includes thinning the photosensor substrate optically coupled to the scintillator producing a thinned photosensor substrate that is optically coupled to the scintillator and that has a thickness on the order of less than one hundred microns.

An imaging system () includes a radiation source () that emits radiation from a focal spot () in a direction of an examination region. The imaging system further includes a beam shaper (), located between the focal spot and the examination region, that shapes an x-ray transmission profile of the radiation emitted from the source and incident on the beam shaper such that the radiation leaving the beam shaper has a pre-determined transmission profile.

X-ray beam transmission profile shaper

An imaging detector () includes a scintillator array () including a scintillator element () and a material () and a photosensor array () including a detector element () having a light sensitive region () and a non-sensitive region (). The light sensitive region is separated from the scintillator element by a gap, the light sensitive region is in one-to-one mechanical alignment with the scintillator element, and the non-sensitive region is in mechanical alignment with the material. The detector further includes structure () that includes one or more material free channels. The structure is located between the non-sensitive region and the material and not between the light sensitive region and the scintillator element. An optical adhesive () is located in the gap, filling the entire gap, and mechanically and optically coupling the light sensitive region and the scintillator element.

Imaging detector

A one-dimensional multi-element photo detector () includes a photodiode array () with a first upper row of photodiode pixels and a second lower row of photodiode pixels. The photodiode array () is part of the photo detector (). A scintillator array () includes a first upper row and a second lower row of scintillator pixels. The first upper and second lower rows of scintillator pixels are respectively optically coupled to the first upper and second lower rows of photodiode pixels. The photo detector () also includes readout electronics (), which are also part of the photo detector (). Electrical traces () interconnect the photodiode pixels and the readout electronics ().

A detector tile () of an imaging system () includes a photosensor array () and electronics () electrically coupled to the photosensor array (), wherein the electronics includes a dose determiner () that determines a deposited dose for the detector tile () and generates a signal indicative thereof. In one non-limiting instance, this signal is utilized to correct parameters such as gain and thermal coefficients, which may vary with radiation dose.

Radiation dose based imaging detector tile parameter compensation

A radiation detector module () particularly well suited for use in computed tomography (CT) applications includes a scintillator (), a photodetector array (), and signal processing electronics (). The photodetector array () includes a semiconductor substrate () having a plurality of photodetectors and metalization () fabricated on non-illuminated side of the substrate (). The metalization routes electrical signals between the photodetectors and the signal processing electronics () and between the signal processing electronics () and an electrical connector ().

Radiation detector array

An imaging system () includes a radiation source () that emits radiation that traverses an examination region () and a detection system () that detects radiation that traverses the examination region () and generates a signal indicative thereof. The detection system () includes a first detector array (-) and a second detector array (-). The first and second detector arrays (-) are separately distinct detector arrays and at least one of the detector arrays (-) is moveable with respect to the radiation beam. A reconstructor () reconstructs the signal and generates volumetric image data indicative thereof.

Multi-detector array imaging system

A radiation sensitive detector array includes a plurality of detector modules () extending along a z-axis direction and aligned along an x-axis direction with respect to the imaging system (). At least one of the detector modules () includes a module backbone () and at least one detector tile (). The at least one detector tile () is coupled to the module backbone () through a non-threaded fastener (). The at least one detector tile () includes a two-dimensional detector () and a two-dimensional anti-scatter grid () that is focused at a focal spot () of an imaging system ().

Detector array with pre-focused anti-scatter grid

A radiographic imaging apparatus () comprises a primary radiation source () which projects a beam of radiation into an examination region (). A detector () converts detected radiation passing through the examination region () into electrical detector signals representative of the detected radiation. The detector () has at least one temporally changing characteristic such as an offset B(t) or gain A(t). A grid pulse means () turns the primary radiation source () ON and OFF at a rate between 1000 and 5000 pulses per second, such that at least the offset B(t) is re-measured between 1000 and 5000 times per second and corrected a plurality of times during generation of the detector signals. The gain A(t) is measured by pulsing a second pulsed source () of a constant intensity (XRef) with a second pulse means (). The gain A(t) is re-measured and corrected a plurality of times per second during generation of the detector signals.

Pulsed x-ray for continuous detector correction

An ionizing radiation detector module () includes a detector array (), a memory (), signal processing electronics (), a communications interface (), and a connector (). The memory contains detector performance parameters () and detector correction algorithms (). The signal processing electronics () uses the detector performance parameters () to correct signals from the detector array () in accordance with the detector correction algorithms ().

Smart radiation detector module

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.

GOS ceramic scintillating fiber optics x-ray imaging plate for use in medical DF and RF imaging and in CT

A radiation detector for a computed tomography scanner includes a plurality of radiation detector modules. Each detector module includes an anti-scatter module, at least one radiation absorbing mask and a detector subassembly module. The anti-scatter module includes radiation absorbing anti-scatter plates. The detector subassembly module includes a substrate and an array of detector elements. The radiation absorbing mask is a photoetched grid, formed of a radiation absorbing material and is positioned between the anti-scatter module and the detector elements of array. The strip of the grid, that is parallel to the anti-scatter plates, is wider than each anti-scatter plate. The detector module is aligned with a spatial focus by inserting the alignment pins into the alignment openings of the radiation absorbing mask and the alignment openings of the detector subassembly module.

Radiation mask for two dimensional CT detector

A radiation detector module includes a scintillator () arranged to receive penetrating radiation of a computed tomography apparatus (). The scintillator produces optical radiation responsive to the penetrating radiation. A detector array () is arranged to convert the optical radiation into electric signals. Electronics () are arranged on a side of the detector array opposite from the scintillator in a path of the penetrating radiation. A radiation shield (') is disposed between the detector array and the electronics to absorb the penetrating radiation that passes through the scintillator. The radiation shield includes openings (&#x2032;) that communicate between the detector array and the electronics. Electrical feedthroughs (&#x2032;) pass through the radiation shield openings and electrically connect the detector array and the electronics.

Growing community of inventors

Mentor, OH, United States of America

Rodney Arnold Mattson