A radiation shield assembly includes a shield configured to block radiation and a rail assembly configured to position the shield in between the radiation table and a radiation source. The shield is movable between a retracted position and an extended position along a length of the rail assembly. In the extended position, the shield extends along a portion of a radiation table and blocks radiation from the radiation source to the portion of the radiation table. In the retracted position, the shield exposes at least some of the portion of the radiation table to the radiation.

In a case in which an imaging mode continuously acquiring a plurality of energy subtraction images is performed, a radiation source control unit of a control device performs radiation source control for performing a one-shot imaging operation, in which only one of first radiation and second radiation is emitted, at least once for one two-shot imaging operation in which the first radiation and the second radiation are continuously emitted. In a case in which the imaging mode is performed, a detector control unit performs detector control to direct a radiation detector to output a first radiographic image based on the first radiation and a second radiographic image based on the second radiation.

To optimize image quality and/or sensitivity, a Compton camera is adaptable. The scatter and/or catcher detectors may move closer to and/or further away from a patient and/or each other. This adaptation allows a balancing of image quality and sensitivity by altering the geometry.

A method is for producing a grid-like beam collimator. In an embodiment, the method includes printing a suspension, including a binder and metal particles, in several stacked layers to build a layer stack with a grid structure including a number of crossing webs, and removing the binder from the layer stack. In an embodiment, the printing includes applying a curable liquid stiffening material at least on a surface of the grid structure, and curing the curable liquid stiffening material after the applying.

An overall full-angle coincidence brain PET detector (1) and an overall apparatus, said detector (1) comprising a plurality of PET detection modules (7), each PET detection module (7) consisting of PET detection crystals (10), a photoelectric sensor array (8) and light guides (9), and all the PET detection crystals (10) being arranged towards the inner cavity. The plurality of PET detection modules (7) form a detection chamber (3) having an opening (4), each of the length, width and height of an inner cavity of the detection chamber (3) is no greater than 35 to 50 cm, and the opening (4) of the detection chamber (3) is located at the lower side of the detection chamber (3). The cross-sectional area at the opening (4) is greater than the maximum cross-sectional area of a head (2) in the horizontal direction. Except for the opening (4), all the PET detection modules (7) are non-detachably connected together. All the cross-sectional areas of gaps between the plurality of PET detection modules (7) are less than ½ to ⅓ of the area of the smallest one of the PET detection crystals (10). At least 75% to 80% of a true coincidence event occurring at the center of the detection chamber (3) is detected by the plurality of PET detection modules (7).

Arrangement to reduce a time until a first image is displayed, to reduce a standby time until the next imaging is started, and to uniformize a time interval in a case where a plurality of images are displayed. An X-ray CT device detects a dose of an X-ray, a storage unit that preserves image data, a calculation unit that generates, as the image data, projection data on the basis of the X-ray data in parallel to an imaging process in the scanner, preserves the projection data, notifies a display control unit of preservation information, performs a reconstruction process, a display unit that displays an image generated per the X-ray data, and the display control unit that controls a display timing of a reconstructed image to be displayed on the display unit on the basis of the preservation information and the reconstruction information.

An X-ray imaging system is provided. The X-ray imaging system includes an X-ray radiation source, an X-ray detector, and a C-arm. The C-arm has the X-ray radiation source disposed on a first end and the X-ray detector disposed on a second end opposite the first end. The X-ray imaging system also includes a motorized system configured to rotate the C-arm about three different rotational axes.

A full-angle coincidence PET detector array, comprising the following components: a plurality of PET detection modules (2), wherein each of the PET detection modules (2) is composed of PET detection crystals (7), a photosensor array (5) and a light guide (6); and the plurality of PET detection modules (2) are adjacent to each other to form an integrally closed detection chamber. A full-angle coincidence PET detection method, comprising the following steps: 1) the step of assembling the detection chamber; 2) the step of placing a detection object; and 3) the step of acquiring an image. The cross-sectional area of all voids is smaller than the area of the smallest of the PET detection crystals (7) when the detection chamber is in a closed state; and the integrally closed detection chamber is of a cylindrical shape, a capsular shape, an ellipsoidal shape or a regular polygonal prism shape.

A device may include a base, a transmission assembly, and a response assembly. The transmission assembly may be configured to move a component of a medical device. The transmission assembly may include a cable and a wheel connected to the base. An end of the cable may be connecting to a part of the component of the medical device. The response assembly may be connected to the transmission assembly. The response assembly may be configured to generate a response in response to a break of the cable.

A specimen radiography system may include a controller and a cabinet. The cabinet may include an x-ray source, an x-ray detector, and a specimen drawer disposed between the x-ray source and the x-ray detector. The specimen drawer may be automatically positionable along a vertical axis between the x-ray source and the x-ray detector.