1507 results about "Radiation imaging" patented technology

The invention provides methods and apparatus for detecting radiation including x-ray photon (including gamma ray photon) and particle radiation for radiographic imaging (including conventional CT and radiation therapy portal and CT), nuclear medicine, material composition analysis, container inspection, mine detection, remediation, high energy physics, and astronomy. This invention provides novel face-on, edge-on, edge-on sub-aperture resolution (SAR), and face-on SAR scintillator detectors, designs and systems for enhanced slit and slot scan radiographic imaging suitable for medical, industrial, Homeland Security, and scientific applications. Some of these detector designs are readily extended for use as area detectors, including cross-coupled arrays, gas detectors, and Compton gamma cameras. Energy integration, photon counting, and limited energy resolution readout capabilities are described. Continuous slit and slot designs as well as sub-slit and sub-slot geometries are described, permitting the use of modular detectors.

Apparatus and methods are provided comprising an implantable non-hydraulic ring that encircles and provides a controllable degree of constriction to an organ or duct and an external control that powers and controls operation of the ring. The ring includes a rigid dorsal periphery that maintains a constant exterior diameter, and a compliant constriction system that reduces intolerance phenomena. A high precision, energy efficient mechanical actuator is employed that is telemetrically powered and controlled, and maintains the ring at a selected diameter when the device is unpowered, even for extended periods. The actuator provides a reversible degree of constriction of the organ or duct, which is readily ascertainable without the need for radiographic imaging. Methods of use and implantation also are provided.

The present invention provides radiation detectors and methods, including radiation detection devices having beam-oriented scintillators capable of high-performance, high resolution imaging, methods of fabricating scintillators, and methods of radiation detection. A radiation detection device includes a beam-oriented pixellated scintillator disposed on a substrate, the scintillator having a first pixel having a first pixel axis and a second pixel having a second pixel axis, wherein the first and second axes are at an angle relative to each other, and wherein each axis is substantially parallel to a predetermined beam direction for illuminating the corresponding pixel.

An object hereof is to restrain occurrence of artifact in an acquired radiation image with comparatively simple configuration without providing wiring between a radiation source and a radiation imaging apparatus to thereby obtain a radiation image with extremely good quality. Therefore, a controller selectively carries out real read operation of reading an electric signal obtained by activating a drive circuit from a signal processing circuit unit in case of detecting X-ray irradiation with an X-ray detecting circuit and dummy read operation of reading an electric signal obtained by activating a drive circuit from a signal processing circuit unit in case of detecting X-ray non-irradiation with an X-ray detecting circuit; discontinues the dummy read operation at the time of detecting the start of X-ray irradiation with the X-ray detecting unit in dummy read operation; and starts real read operation at the time of detecting the finish of X-ray irradiation with the X-ray detecting unit.

A radiation imaging apparatus includes a radiation detecting unit and an image-display controlling unit. The radiation detecting unit has radiation detectors, arranged in a two-dimensional array, for detecting radiation transmitted through an object as electrical signals. The image-display controlling unit radiographs radiation images of the object, detected as the electrical signals by the radiation detecting unit, at a predetermined frame rate as continuous images in a plurality of frames and displays a processed image given by subtracting an m-th image from an (m+1)-th image in synchronous with either the m-th image or the (m+1)-th image that does not undergo the subtraction in a display, where m is a natural number.

A lamp emits pulse-shaped visible light when a wait period begins. If a radiation emission switch is not pressed in the wait period, X-ray radiation is not emitted from an X-ray source, and no charges are accumulated in photoelectric conversion elements of an X-ray imaging apparatus. In a non-read period, although signals are sequentially read from the photoelectric conversion elements, an output signal does not change. When the radiation emission switch is pressed in synchronization with a radiation-induced signal in a certain wait period, the X-ray source emits X-rays. After irradiation of X-rays, a photoelectric conversion period transitions to an actual read period. In the photoelectric conversion period, X-rays are emitted and transmitted X-ray information of a patient are accumulated in the photoelectric conversion elements of the X-ray imaging apparatus. In the actual read period, the accumulated information is read.

Radioimaging methods, devices and radiopharmaceuticals therefor.

The invention intends to be able to adequately perform a gain correction. Hence, at the time of radiographing an object, a gain correction of the object image is performed based on a gain correction image (XRc1) derived by performing a light reset. On the other hand, at the time of radiographing an object, when a light reset is not performed, a gain correction of the object image is performed based on a gain correction image (XRc2) derived without performing the light reset.

An X-ray imaging system includes first to third absorption gratings. Initially, the third absorption grating is disposed in a Z axis orthogonal to a detection surface of a FPD, and the position of the third absorption grating is adjusted in θx and θy directions based on a dose of X-rays having passed through the third absorption grating. Then, the first absorption grating is disposed in the Z axis so as to produce a moiré pattern. The position of the first absorption grating is adjusted in the θx and θy directions so that a frequency of the moiré pattern detected by the FPD becomes uniform. Then, the position of the first absorption grating is adjusted in a Z or θz direction so that the FPD loses the detection of the moiré pattern. After that, the second absorption grating is aligned in a like manner as the first absorption grating.

An x-ray and gamma-ray radiant energy imaging device is disclosed having a temperature sensitive semiconductor detector substrate bump-bonded to a semiconductor CMOS readout substrate. The temperature sensitive, semiconductor detector substrate utilizes Tellurium compound materials, such as CdTe and CdZnTe. The bump bonds are formed of a low-temperature, lead-free binary solder alloy having a melting point between about 100° C. and about 180° C. Also described is a process for forming solder bumps utilizing the low-temperature, lead-free binary solder alloy, to prevent damage to temperature sensitive and potentially brittle detector substrate when assembling the imaging device.

It is made possible that, in accordance with a plurality of radiographing modes such as the still image radiographing mode and the moving image radiographing mode, the outputs both in the irradiation period and in the non-irradiation period are made to fall within the dynamic range of the radiographing system, whereby an accurate, high-S/N-ratio X-ray radiographic image is obtained. For that purpose, in accordance with the plurality of radiographing modes, an arithmetic operation unit adjusts a power source to control voltage to be applied to a reading circuit unit or an Analogue-Digital conversion unit, such that, in each of the radiographing modes, both an electric signal in the X-ray irradiation period and an electric signal in the X-ray non-irradiation period fall within the dynamic ranges of the reading circuit unit and the Analogue-Digital conversion unit.

When performing an offset correction, without lowering an image quality of the radiographed image data, a prompt radiographing is realized. Hence, a memory 105 stores a first image data for offset correction generated by performing an interlace scanning of the driving lines of odd rows only in a driving circuit unit 103. A memory 106 stores a second image data for offset correction generated by performing the interlace scanning of the driving lines of even row only in the driving circuit unit 103. A processing unit 108 synthesizes the first image data for offset correction and the second image data for offset correction, thereby to generate an image data for offset correction of one frame portion, and an arithmetic operation unit 109 performs an arithmetic operation processing on the radiation image data stored in a memory 107 by using the image data for offset correction of one frame portion synthesized and generated, thereby to perform the offset correction of the radiation image data.

A radiation imaging apparatus is capable of taking a moving picture by acquisition by a reading circuit of a plurality of radiation image signals on the basis of a plurality of successive times of irradiation of a radiation detector with radiation rays. The radiation detector has a two-dimensional array of pixels. In a period between a start of an n-th time of irradiation with radiation rays and a start of an (n+1)-th time of irradiation with radiation rays, where n is a natural number, a controller switches an operation status of an analog-to-digital converter that converts electric signals read by the reading circuit into digital signals so that power consumption of the analog-to-digital converter is reduced.

A phase contrast radiation imaging apparatus is includes a radiation source, a diffraction grating, and a radiation image detector. The radiation image detector is equipped with a charge generating layer that generates electric charges when irradiated with radiation, and charge collecting electrodes that collect the electric charges. The charge collecting electrodes are linear electrode groups, constituted by linear electrodes which are arranged at a constant period and are electrically connected to each other, provided to have different phases from each other. Thereby, use of a conventional amplitude diffraction grating is obviated.