A patient imaging system for creating visual representations for analysis includes an imaging source and a patient support disposed proximate the imaging source configured to receive and support the patient. An imaging device is disposed adjacent to the patient support and incorporates at least one detector, one or more slats cooperating with the at least one detector and a collimator disposed between the one or more slats and patient support having a plurality of links adjustably positionable on the collimator. The plurality of links receive and support imaging plates that may be adjusted to provide a variety of image settings such that the imaging device and imaging source define a pre-determined imaging volume in an imaging region for the patient positioned in the imaging system.

A radiation imaging system that is capable of controlling a radiation generating apparatus and a radiation detector based on communication between a first control application and a second control application is provided. The radiation imaging system comprises a holding unit configured to hold a plurality of processing requests transmitted from the second control application, a determination unit configured to determine whether the plurality of processing requests held in the holding unit are processing requests to be continuously executed, and a control right obtaining unit configured to obtain a control right to control an imaging control unit of the first control application that performs the control in order to continuously process the processing requests.

A scintillation crystal can include a cesium halide that is co-doped with thallium and another element. In an embodiment, the scintillation crystal can include CsX:Tl, Me, where X represents a halogen, and Me represents a dopant selected from the group consisting of chromium (Cr), zirconium (Zr), cobalt (Co), manganese (Mn), cadmium (Cd), dysprosium (Dy), thulium (Tm), tantalum (Ta), and erbium (Er), the dopant concentration of the element selected from the group consisting of chromium (Cr), zirconium (Zr), cobalt (Co), manganese (Mn), cadmium (Cd), dysprosium (Dy), thulium (Tm), tantalum (Ta), and erbium (Er) in the scintillation crystal is in a range of 1×10.sup.−7 mol % to 0.5 mol %. In a particular embodiment, the scintillation crystal may have a cesium iodide host material, a first dopant including a thallium cation, and a second dopant including a cation.

A radiation detector provides improved time-resolution under consideration of an incident of a multiple scattering event. An individual comparator 11 extracts a pulse from the detection element 3a through a total circuit 12 and converts to the time data. In addition, each detection element 3a comprises the total circuit 12. that outputs the pulse totaling the output of each detection element 3a, and the total comparator 13 that converts the pulses output from the total circuit 12 to the time data. According to the aspect of the present invention, the time data suitable from each discriminated event is processed, so that the emission-time of fluorescence can be more accurately determined.

When two detector panels are rotationally moved around the entire circumference of a region of interest and projection images of the region of interest are captured during the rotational movement, the respective detector panels are moved along the tangential direction of the rotational movement to a position where the union of the capturing ranges of the projection images captured by the respective detector panels covers the entire region of interest. The projection images captured by the respective detector panels are used to reconstruct a transaxial image of the region of interest.

Provided is a method of fabricating a detector array that includes preparing a plurality of slabs of an optical medium of an imaging device, forming a plurality of optical boundaries within at least one of the slabs of optical medium, where the plurality of optical boundaries defining a 1×N array of non-contiguous, independent light-redirecting regions within the at least one slab, arranging the plurality of slabs into a stack with a reflective layer defined between each adjacent slab and affixing the positions of the plurality of slabs with respect to each other. A detector array formed using the method is also provided.

The following relates to noise filtering in nuclear imaging systems. In one aspect, a fully automatic noise filtering system is provided in a nuclear imaging device. In some embodiments, a filter parameter selection engine is applied to an image environment of a medical image to calculate an image filter configuration for the medical image wherein the image environment includes values for one or more of an imaging subject of the medical image, an imaging device used to acquire the medical image, and a medical context of the medical image.

Disclosed herein is an image sensor comprising: a plurality of packages arranged in a plurality of layers; wherein each of the packages comprises an X-ray detector mounted on a printed circuit board (PCB); wherein the packages are mounted on one or more system PCBs; wherein within an area encompassing a plurality of the X-ray detectors in the plurality of packages, a dead zone of the packages in each of the plurality of layers is shadowed by the packages in the other layers.

A nuclear detector, comprises a scintillation crystal array including a plurality of scintillation crystal bars of the same size arranged closely and in sequence, a light guide, and a photodetector array including a plurality of photodetectors arranged in sequence. The photodetectors have a cross-sectional area greater than that of the scintillation crystal bars, and the light guide includes a top surface coupled to the scintillation crystal array, an opposed bottom surface coupled to the photodetector array and a side surface. The light guide has a thickness in a range of 0.1 mm to 40 mm. The light guide further includes a slit adjacent to an edge of the light guide, and the slit is configured to extend from the top surface toward the bottom surface of the light guide and the slit has a depth in a range of 0.1 to 0.5 times the thickness of the light guide.

The invention is an imaging device comprising detector and collimator element (144) applied e.g. in a SPECT. In the imaging device according to the invention the collimator element comprises—one or more first pinholes (146a, 148a) being focussed on a central field of view (141), the one or more first pinholes (146a, 148a) being adapted for projecting the central field of view (141) on one or more respective first imaging regions (52) being non-overlapping with any other imaging regions;—one or more second pinholes (148b) being focussed on a central field of view (141), the one or more second pinholes (148b) being adapted for projecting the central field of view (141) on one or more respective second imaging regions (56);—one or more second pinholes (148c) being focussed on a primary field of view (142) comprising the central field of view (141), the one or more third pinholes (148c) being adapted for projecting the primary field of view (142) on one or more respective third imaging regions (58) overlapping with at least one second imaging region (56). The invention is furthermore a tomographic apparatus (e.g. a SPECT) comprising the imaging device. (FIG. 13).