Abstract: A direct radiation converter is disclosed. In at least one embodiment, the direct radiation converter is operated using a direct conversion element having a temperature of at least 38° C. and at most 55° C., and designed for detecting X-ray radiation.

Abstract: X-ray security inspection machine (10) comprising an X-ray tunnel (40); a conveyor means (50) for conveying an article through the tunnel; an X-ray source for irradiating the article; and an X-ray detection means for detecting X-rays transmitted through the article. In one aspect, the detection means comprises a photodetector array module (20) actuatable between a first stowed configuration and a second deployed configuration. In a second aspect, the detection means comprises a first unit having a first photodetector array (22); and a second unit, having a second photodetector array (24), offset with respect to the first unit. The units are moveable relative to one another between a first arrangement where the arrays overlap to a first degree and a second arrangement where they overlap to a second, lower degree; preferably zero. Also, a conveyor belt-tracking device (100) comprising a guide frame (104) to receive the conveyor belt (116) and substantially to restrict its motion to a predetermined direction.

Abstract: A CT detector capable of energy discrimination and direct conversion is disclosed. The detector includes multiple layers of semiconductor material with the layers having varying thicknesses. The detector is constructed to be segmented in the x-ray penetration direction so as to optimize count rate performance as well as avoid saturation. The detector also includes variable pixel pitch and a flexible binning of pixels to further enhance count rate performance.

Abstract: The invention is directed at an apparatus (10), an imaging device and a method for detecting X-ray photons, in particular photons (32, 34) in a computer tomograph. Photons (32, 34) are converted into an electrical pulse and compared against a threshold using a discriminator (20). The electrical network (12) performing these functions comprises a switching element (28), that can modify the electrical path (22) along which the process signals travel. The trigger signal (VT) for actuating the switching element (28) is derived from an electrical state of the electrical path (22). If a pulse associated to a photon (32, 34) is detected, the switching element (28) is actuated in order to avoid that the processing of the charge pulse stemming from a first photon (32) is affected by a subsequent second photon (34).

Abstract: An x-ray CT system that generates tomographic phase contrast or dark field exposures, has at least one grating interferometer with three grating structures arranged in series in the radiation direction, with a modular design of the second and third grating structures. The distance between the first grating structure of the x-ray source and the second grating structure (fashioned as a phase grating) of the respective grating/detector modules is adapted, depending on the fan angle, corresponding to a period of the grating structure of the x-ray source projected onto the grating detector module at a respective fan angle (?i).

Abstract: An electron beam computed tomography system is provided that uses a cone beam geometry to generate truly three-dimensional images. The required cone beam projections can be obtained using a single sweep of the electron beam along the target ring (20). The target ring (20) is non-planar and shaped roughly like a ?th segment of the boundary curve of a saddle. The resulting source trajectory satisfies Tuy's completeness condition with respect to a sizeable volume of interest around the isocenter of the system. The detector (28) has a large area and is built from a plurality of small, brick-shaped detector modules (32), which are placed side by side along a detector trajectory that is a mirror image, through the isocenter, of the source trajectory. Owing to the special shapes of the target ring and the detector strip, a cone-beam of x-rays starting from the target ring and heading towards the opposite segment of the detector strip is not blocked by other portions of the detector.

Abstract: A method is disclosed for detecting X-ray radiation from an X-ray emitter. In at least one embodiment of the method, an electric pulse with a pulse amplitude characteristic of the energy of a quantum is generated when a quantum of the X-ray radiation impinges on a sensor, wherein a number of threshold energies are predetermined. When the pulse amplitude corresponding to the respective energy is exceeded, a signal is emitted each time the pulse amplitude corresponding to a respective threshold energy is exceeded. At least one embodiment of the method permits reliable and high-quality imaging, even in image regions with high X-ray quanta rates. To this end, at least one of the threshold energies is predetermined such that it is higher than the maximum energy of the X-ray spectrum emitted by the X-ray emitter.

Abstract: Medical imaging may be accomplished with a high photoconductive gain at a relatively low operating voltage by employing a black silicon photodetector and integrating CMOS components with elements of the photodetector.

Abstract: A diagnostic imaging system includes a magnetic resonance imaging scanner (10) for imaging an organ of interest, a reformatting processor (70) for constructing reformatted images corresponding to a scout image in different coordinate systems, and a graphical user interface (62) for displaying acquired images and reformatted images to an associated user. An imaging processor (60) causes the scanner (10) to acquire a base sparse scout image of an organ of interest in a standard coordinate system, causes the reformatting processor (70) to generate one or more reformatted images from the sparse scout image in coordinate systems other than the standard coordinate system, determines a diagnostic imaging coordinate system aligned with the organ of interest using the base sparse scout image and the one or more reformatted images, and causes the scanner (10) to acquire one or more diagnostic images of the organ of interest in the diagnostic imaging coordinate system.

Abstract: An X-ray CT imaging apparatus includes an X-ray generating section, an X-ray image capturing section, a supporting section, a holding section, a rotation driving section, and an X-ray controlling section, wherein the X-ray generating section generates an X-ray cone beam, the X-ray image capturing section detects the X-ray cone beam having passed through an object, the supporting section supports the X-ray generating section and the X-ray image capturing section with the object positioned therebetween, the holding section holds the object, the rotation driving section rotates the supporting section relatively to the object, and the X-ray controlling section alleviates an influence of a high X-ray absorption region, present inside the object, in the X-ray image capturing section by means of a control model formed based upon information on the high X-ray absorption region.

Abstract: An X-ray examination apparatus includes a scanning X-ray source for outputting X-rays, a sensor base which is attached with a plurality of X-ray sensors and which rotates about a rotation axis, and an image acquiring control mechanism for controlling rotation angle of the sensor base and acquisition of image data from the X-ray sensors. With respect to each X-ray sensor, the scanning X-ray source moves the X-ray focal position of the X-ray source to each starting position of the X-ray emission set so that the X-ray transmits through a predetermined examination area of an examination target and enters each X-ray sensor, and emits the X-rays. The image control acquiring control mechanism acquires image data detected by the X-ray sensors, and a calculation unit reconstructs an image of the examination area based on the image data.

Abstract: The invention relates to a CT imaging system for determining the flow of a substance within an object, wherein the CT imaging system comprises a polychromatic X-ray source and an energy-resolving X-ray detector for obtaining detection signals depending on the X-ray radiation after passing through the object. A calculation unit (12) determines a k-edge 5 component of the substance from the detection signals, and a reconstruction unit (13) reconstructs a time series of k-edge image from the determined k-edge component. A flow determination unit (14) determines flow values indicative for the flow within the object from the time series of k-edge images.

Abstract: The invention relates to radiation-and-detection system comprising a radiation unit (2) for alternately illuminating a detection unit (6) with radiation of a first emanating region (15) at first time intervals and with radiation of a second emanating region (16) at second time intervals, wherein first detection values are detected at the first time intervals and second detection values are detected at the second time intervals. The radiation-and-detection system is calibrated with respect to the influence of the radiation of the second emanating region (16) to the first detection values and with respect to the influence of the radiation of the first emanating region (15) to the second detection values.

Abstract: A compression subsystem for a computed tomography system compresses projection data to for efficient data transfer and storage. The compression includes detecting edges in the projection data corresponding to the object being imaged to set boundaries for compression operations. The edge detection compares difference samples to positive and negative thresholds to determine the boundaries. The projection samples or the difference samples are compressed between the boundaries. The boundaries are encoded and included in the compressed data. The compressed samples are decompressed prior to image reconstruction processing. Decompression includes decoding the compressed samples and the boundary values. This abstract does not limit the scope of the invention as described in the claims.

Abstract: A method of calibrating a computed tomography system includes the steps of mounting a scan geometry defining tool on a rotating object positioning unit of a computer tomography scanner. The scan geometry defining tool has structure of precisely measured dimensions. A beam is directed from an x-ray source of the computed tomography system through the structure of the scan geometry defining tool. A detected image after absorption of the x-ray from the scan geometry defining tool is analyzed, and utilized to determine a distance from the x-ray source spot location to the center of rotation of the object positioning unit. A beam is also directed from the x-ray source through a system performance test standard tool and analyzes a number of electronic and computer performance characteristics. The analyzed characteristics can be compared to expected characteristics to provide feedback on the operation of electronic and computer functions within the computed tomography system.

Abstract: A radiographic imaging apparatus includes a radiation detector (16) and a radiation source (12) which projects a non-parallel beam of radiation into field of view (14). A footprint of each voxel (v) which is projected on the detector (16) is corrected based on the position of the voxel (v) in the field of view (14) in relation to the radiation detector (16) and the radiation source (12). The contributions from substantially parallel redundant projections are further combined based on a fractional distance frac from a center point (82) of the voxel (v) to a center of each of the adjacent redundant projections.

Abstract: An X-ray detection technology capable of suppressing a decrease in a signal-to-noise ratio derived from external noise even in a case where it is hard to intercept electromagnetic-wave noise, and offering a wide dynamic range is realized, and an X-ray imaging device utilizing the technology is provided. An electromagnetic-wave noise signal to be mixed in a signal detected by an X-ray detector 2 is inferred from electromagnetic-wave noise signals measured by reference detectors 10A and 10B according to the method of least squares. Noise removal calculation is performed in order to minimize the decrease in a signal-to-noise ratio derived from the electromagnetic-wave noise.

Abstract: Spectral CT systems require cheap detectors with high energy resolution. According to an aspect of the present invention, a computer tomography apparatus comprises a detector element which is segmented into a plurality of sub-pixels. Each sub-pixel has at least two thresholds and counting channels, wherein the second threshold for each sub-pixel varies over the nominal detector element. This may provide for an improved energy-resolved photon counting.

Abstract: A CT scanner and method are designed to scan a preselected portion of a patient's lower abdomen. The scanner may include a source and detector array designed to rotate about a rotation axis oriented substantially parallel to or coincident with the hips of the a patient so that a scanning plane does not pass through the patient's pelvic bones Higher-resolution image CT images can be achieved by using a detector array of the type used for digital radiography. The presence of prostatic cancer can be detected by first injecting the patient with a material including a high contrast material for X-ray imaging and a material for binding the high contrast material to a specific biological site if present in the preselected portion of the lower abdomen of the patient; and generating a CT image of the preselected portion of the lower abdomen.

Abstract: An X-ray computed tomography apparatus includes an X-ray tube (101) which generates X-rays, a multi-channel X-ray detector (103) which detects X-rays transmitted through an object to be examined, a rotating frame (102) which is equipped with the X-ray tube and the X-ray detector, a reconstruction unit (114) which reconstructs an image on the basis of an output from the X-ray detector, and a control unit (121) which alternately shifts the X-ray focal spot of the X-ray tube along the rotating direction on the anode by a distance +? and a distance ?? for each view. The distance ? is set to ? = S ? ? O ? ? D · tan ( ? ? ? ? 2 ) where SOD is the distance between the X-ray tube and the rotation center, and ?? is the angle difference between adjacent views, such that X-ray focal spots in the adjacent views overlap each other at almost the same position.

Abstract: A system and methods for characterizing an inspected object on the basis of attenuation determined from pair-wise illuminated voxels. A beam of penetrating radiation characterized by a propagation direction and an energy distribution is scanned relative to an object, while scatter detectors with collimated fields-of-view detect radiation scattered by each voxel of the inspected object that is intercepted by the incident beam of penetrating radiation. By calculating the attenuation of penetrating radiation between pairs of voxels illuminated sequentially by the incident beam, a tomographic image is obtained characterizing the three-dimensional distribution of attenuation in the object of one or more energies of penetrating radiation, and thus of various material characteristics.

Abstract: An X-ray imaging apparatus includes an imaging unit which is rotatable relative to a platform about a shaft portion perpendicular to an X-ray detecting surface, so as to change the orientation relative to a subject.

Abstract: A radiation converter is disclosed. In at least one embodiment, the converter is for x-ray or gamma radiation and includes a multiplicity of scintillation elements which are separated from one another by separating septa. To reduce cross-talk between adjacent scintillation elements, the separating septa have a layer structure. The layer structure includes two backscatter layers, between which an absorber layer which is essentially opaque to the radiation, to scatter radiation and/or scintillation light is disposed.

Abstract: A computed tomography system includes a plurality of radiation sensitive detector elements (100) which generate a time varying signal indicative of x-ray photons received by the various detector elements (100). Photon counters (24) count the photons received by the various detector elements (24). Event-driven energy determiners (26) measure the total energy of the received photons. A mean, energy calculator (46) calculates a mean energy of the photons received by the various detector elements (100) during a plurality of reading periods.

Abstract: A unified quality assurance technique to verify alignment of a radiation treatment delivery system. In one embodiment, a radiation treatment source is instructed to move to a preset source position. An image of the radiation treatment source at its actual source position is generated and compared against a reference image to determine whether the radiation treatment source correctly achieved the preset source position. In one embodiment, a positioning system is instructed to move a target detector to a preset target position. An image of the target detector at its actual target position is generated and compared against a reference target image to determine whether the positioning system correctly achieved the preset target position.

Abstract: A computed tomographic imaging system is provided for generating computed tomography images. The computed tomographic system includes a processor configured to access image data encoding X-ray projections at a detector position and a plurality of X-ray source beam focal spot positions and to align pixel values for the projections in a direction of deviation of the positions. The processor is also configured to determine a correction factor for at least one of the projections based upon the aligned pixel values and upon a sum of the projections and to correct the pixel values for the at least one of the projections based upon the correction factor.

Abstract: In an X-ray CT scanner having an X-ray tube which applies an X-ray spreading in a body axis direction of a subject, and an X-ray detector having a wide imaging range which detects the X-ray passed through the subject and converts the detected X-ray into an electric signal, a desired image creation time is set by use of a specific CT value curve in a console input unit before scanning with the X-ray. After the scanning, data of the CT value change curve is generated based on the obtained projection data. An image creation range in the generated change curve is determined based on an image creation range set in the console input unit, and the image creation is performed in the image creation unit based on the determined image creation time.

Abstract: A computed tomography system includes a radiation sensitive detector element (100) which provides outputs (DL, DH) indicative of the radiation detected in at least first and second energies or energy ranges. Energy resolving photon counters (26) further classify the detector signals according to their respective energies. Correctors (24) correct the classified signals, and a combiner (30) combines the signals according to a combination function to generate outputs (EL, EH) indicative of radiation detected in at least first and second energies or energy ranges.

Abstract: The present invention relates to an apparatus (10) for counting X-ray photons (12, 14). The apparatus (10) comprises a sensor (16) adapted to convert a photon (12, 14) into a charge pulse, a processing element (18) adapted to convert the charge pulse (51) into an electrical pulse (53) and a first discriminator (20) adapted to compare the electrical pulse (53) against a first threshold (TH1) and to output an event (55) if the first threshold (TH1) is exceeded. A first counter (22) counts these events (55), unless counting is inhibited by a first gating element (24). The first gating element (24) is activated when the first discriminator (20) outputs the event (55), and it is deactivated, when the processing of a photon (12, 14) is found to be complete or about to be completed by a measurement or by the knowledge about the time that it takes to process a photon (12, 14) in the processing element (18). By activating and deactivating the first counter (22) pile-up events, i.e.

Abstract: A method is disclosed for image reconstruction of an object with the aid of at least one-dimensional projections of the object into a three-dimensional volume image data record, it being possible to generate the projections by at least one detector/source system with reference to different positions and angles relative to the object, and at least two projections forming a reconstruction volume in an overlap region as basis for a backprojection of the projections into the three-dimensional volume image data record, in particular computed tomography. An apparatus for carrying out the method is further disclosed. In at least one embodiment, supplemented reconstruction volumes are generated by supplementing reconstruction volumes, covered only partially by projections, by way of virtual projections that are derived from volume image data records.

Abstract: A CT scanner includes a pair of shields to protect an operator from x-rays from the CT scanner. The CT scanner has a gantry that provides structural support and housing for the components including an x-ray source and a detector arranged on the gantry to face one another. Lead shields are located on opposing sides of the x-ray source and extend between the x-ray source and the detector. The CT scanner further includes a computer located on an opposing side of the gantry from the x-ray source and the detector. The lead shields rotate with the gantry and prevent the x-ray from reaching the operator while the CT scanner is in operation.

Abstract: It is described an integrated circuit design and a method to fabricate the same for a high-efficiency, low-noise, position sensitive X-ray detection in particular for medical applications. The device (350) is based on deep recesses (354) filled with an X-ray sensitive scintillator material. A shallow first electrode (360) is formed on the surface of the substrate (352) sidewalls separating two neighboring recesses (354). This sidewall electrode (360) in combination with particular frontside wafer electrode (363) structure results in a full depletion of the entire device (350) and a removal of signal charge towards the low capacitance readout electrode (363). The described integrated circuit element (350) ensures high and not depth dependent light collection efficiency.

Abstract: A method for single photon counting transmission computed tomography (CT) is described. The method is based on an apparatus consisting of a radiation source and detectors on an opposite side of the subject from the source. The radiation source is for example an X-ray tube. The detectors are independently connected to parallel, fast, low-noise processing electronics capable of recording and counting individual X-ray photons at very high rate. In one embodiment of the invention, said detector is made of a scintillator coupled to a photodetector. The photodetector can be an avalanche photodiode (APD).

Abstract: The invention relates to a medical X-ray imaging apparatus comprising a frame part, an X-ray source for producing X-rays, radiation receiving means for detecting radiation transmitted through an object, and support means for supporting the X-ray source and the receiving means in positions on opposite sides of the object. The support means are connected to the frame part so as to rotate around the axis of rotation provided with actuator means for rotating the said support means around the said axis of rotation. The apparatus makes possible both panoramic imaging and CT imaging, as selected by the operator. The X-ray apparatus comprises means for adjusting the ratio of enlargement so as to be optimal for each method of imaging used respectively.

Abstract: The present invention is a directed to a non-pixelated scintillator array for a CT detector as well as an apparatus and method of manufacturing same. The scintillator array is comprised of a number of ceramic fibers or single crystal fibers that are aligned in parallel with respect to one another. As a result, the pack has very high dose efficiency. Furthermore, each fiber is designed to direct light out to a photodiode with very low scattering loss. The fiber size (cross-sectional diameter) may be controlled such that smaller fibers may be fabricated for higher resolution applications. Moreover, because the fiber size can be controlled to be consistent throughout the scintillator array and the fibers are aligned in parallel with one another, the scintillator array, as a whole, also is uniform. Therefore, precise alignment with the photodiode array or the collimator assembly is not necessary.

Abstract: An x-ray computed tomography apparatus has a stationary x-ray detector that at least partially surrounds the examination volume in one plane and a stationary device for generation of x-ray radiation. The device for generation of x-ray radiation is composed of an x-ray source that extends annularly around the examination volume over an angle of at least 180° as well as one or more light scanning units with which an x-ray focus moving along the x-ray source can be generated on the x-ray target by scanning of the x-ray source with a light beam, from which x-ray target an x-ray beam is directed through the examination volume onto respective, momentarily opposite detector elements of the stationary x-ray detector. The computed tomography apparatus has one or more light scanning units are arranged and fashioned outside of a central ring axis of the x-ray source such that only an angle range <360° is respectively scanned with each light scanning unit without crossing the ring axis.

Abstract: Computed tomography (CT) systems and related methods involving forward collimation are provided are provided. In this regard, a representative method involving forward collimation of X-rays includes: emitting X-rays from a housing in which an X-ray source is mounted; collimating the X-rays downstream of the housing; and directing the collimated X-rays at a target.

Abstract: The present invention is directed to a method and apparatus of multi-energy data acquisition. An imaging system is also provided and includes a number of HF electromagnetic energy filters. The filters include at least a first and a second filter wherein the first filter is positioned in a path of HF electromagnetic energy when an HF electromagnetic energy source is energized to a first voltage and the second filter is positioned in the path of HF electromagnetic energy when the HF electromagnetic energy source is energized to a second voltage.

Abstract: A CT detector capable of energy discrimination and direct conversion is disclosed. The detector includes multiple layers of semiconductor material with the layers having varying thicknesses. The detector is constructed to be segmented in the x-ray penetration direction so as to optimize count rate performance as well as avoid saturation. The detector also includes variable pixel pitch and a flexible binning of pixels to further enhance count rate performance.

Abstract: A radiological imaging apparatus of the present invention comprises an image pickup device and a medical examinee holding device that is provided with a bed. The image pickup device includes a large number of radiation detectors and radiation detector support plates. A large number of radiation detectors are mounted around the circumference of a through-hole and arranged in the axial direction of the through-hole. The radiation detectors are arranged in three layers formed radially with respect to the center of the through-hole and mounted on the lateral surfaces of the radiation detector support plates. Since the radiation detectors are not only arranged in the axial direction and circumferential direction of the through-hole but also arrayed in the radial direction, it is possible to obtain accurate information about a ?-ray arrival position in the radial direction of the through-hole (the positional information about a radiation detector from which a ?-ray image pickup signal is output).

Abstract: A computer tomography system has a stationary x-ray tube, that has an anode ring and at least one cathode ring, that extends through 360° in a system plane perpendicular to a system axis, and a vacuum region that is at least partially delimited by a light-permeable and/or infrared-permeable vacuum window is provided between the anode ring and the at least one cathode ring. A support frame is rotatable around the system axis parallel to the system plane, on which are arranged, in at least one angle position, a system with at least one laser for local activation of electron emission at the at least one cathode ring, and a filter and/or collimator set, and a radiation detector opposite the filter and collimator set.

Abstract: A computer tomograph system comprises a rotating part for accommodating at least one X-ray tube and a detector arrangement, and a stationary part rotatably supporting the rotating part, and comprising a DC-to-AC converters for generating an alternating current for supplying current to a conductor arrangement. To supply energy to the rotating part, the rotating part comprises at least one inductive coupler for engaging, exclusively in dependence upon position, with a section of the entire length of the conductor arrangement, and for coupling electrical energy out of the conductor arrangement. Alternatively, the conductor arrangement may be disposed on the rotating part, and the inductive coupler may be disposed on the stationary part.

Abstract: A computer tomography apparatus (200) for examination of an object of interest (207), the computer tomography apparatus (200) comprising detecting elements (223) adapted to detect, as detecting signals, electromagnetic radiation scattered from an object of interest (207) in an energy-resolving manner, and a combination unit (225) adapted to combine detecting signals detected by different detecting elements (223) such as to reduce the amount of data to be processed for determining structural information concerning the object of interest (207).

Abstract: A computer tomography device is provided. The computer tomography device includes a rotating part and a stationary part. The rotating part has an X-ray tube for radiographing an object to be examined with X-rays and a detector for detecting the X-rays transmitted through the object. A stationary part has a data processing device for evaluating the detected measuring results, and a transmitter for supplying the X-ray tube and/or the detector and other rotating consumers with supply voltage by contactless transmission of electric power between the stationary and the rotating part. The transmitter is designed for contactless data transmission between the stationary part and the rotating part in addition to the contactless transmission of electrical power.

Abstract: Imaging apparatus comprises a radiation source arranged to generate a divergent imaging beam and an associated radiation detector mounted on a C-arm which can rotate. A first drive is arranged to move the radiation source and the detector relative to a subject in a scanning direction to generate output signals from the detector, thereby performing a scan generating image data containing distortion in a direction transverse to the scanning direction. A second drive is arranged to rotate the C-arm, to change the orientation of the radiation source in a direction transverse to the scanning direction incrementally between repeated scans, thereby to generate a plurality of sets of image data.

Abstract: A detector arrangement (10) for detecting and transferring detector signals to a processing unit is described. This detector arrangement is provided in particular for use in a computer tomograph for high-resolution detection of X-rays, the processing unit being in the form of a central processing unit or buffer memory (Z) on a rotatable portion of a gantry (1). To transfer the detector signals with the minimum number of contacts or plug-in connectors also in the case of a high-resolution detector arrangement (10), this comprises at least one detector module having a plurality of individual detector elements as well as an electrical unit having an electro-optical transducer for processing the signals of the detector elements and for generating optical detector module output signals.

Abstract: A radiological imaging apparatus of the present invention comprises an image pickup device and a medical examinee holding device that is provided with a bed. The image pickup device includes a large number of radiation detectors and radiation detector support plates. A large number of radiation detectors are mounted around the circumference of a through-hole and arranged in the axial direction of the through-hole. The radiation detectors are arranged in three layers formed radically with respect to the center of the through-hole and mounted on the lateral surfaces of the radiation detector support plates. Since the radiation detectors are not only arranged in the axial direction and circumferential direction of the through-hole but also arrayed in the radial direction, it is possible to obtain accurate information about a ?-ray arrival position in the radial direction of the through-hole (the positional information about a radiation detector from which a ?-ray image pickup signal is output).

Abstract: A Multi-Energy Computed Tomography (MECT) System is provided. The system includes a radiation source rotatable about a patient, a radiation detector, and a computer coupled to the radiation source and the radiation detector wherein the computer is configured to receive data regarding a first energy spectrum of a scan of a head of the patient, receive data regarding a second energy spectrum of a scan of the head, and generate an image using the received data.

Abstract: An optical tomographic imaging device and the like which suppress influence in the case of a measuring beam being truncated by an iris, and can ensure reliability of a tomographic image which is acquired, when imaging the tomographic image of a retina in an eyeground of an examined eye. An optical tomographic imaging device is configured to have an observation unit observing a state of irradiating an examined object with the measuring beam, and imaging a state of the measuring beam being incident on the examined object as an observation image, a recording unit recording the observation image by linking the observation image with a tomographic image by the optical tomographic imaging device, and an evaluating unit evaluating reliability of the tomographic image which is linked with the observation image based on the observation image imaged in the observation unit.

Abstract: In some embodiments, an optical mask for a CT detector is disclosed. In some embodiments, the mask is intercalated between a photodiode array and a scintillator array forming the CT detector. In some embodiments, the optical mask may extend along one or more axes and differentially absorbs and/or reflects light emitted from the scintillators at edges of photodiodes forming the diode array, with less absorption or reflection at edges of tiled die forming the diode array than in central portions of each of the die. Through selective absorption and/or reflection, transference of light photons from a scintillator to the photodiode corresponding to a neighboring scintillator is spatially modified, at least partially compensating for spatial differences in crosstalk signals between adjacent pairs of photodiode/scintillator cell elements. This reduction in differential crosstalk reduces artifacts in a reconstructing data descriptive of internal portions of a subject, which improves diagnostic value of the data.