Various methods and systems are provided for x-ray tube conditioning for a computed tomography imaging method. In one embodiment, x-ray may be generated in an x-ray tube of a radiation source prior to a diagnostic scan to warmup the x-ray tube to a desired temperature for the diagnostic scan. The power delivered to the x-ray tube during warmup may be adjusted in a closed loop system based on an initial temperature of the x-ray tube and the desired temperature for the diagnostic scan. During tube warmup, by placing a blocking plate coupled to a collimator blade in a path of the x-ray beam, the x-ray beam may be blocked from exiting a collimator.

A positron emission tomography (PET) assembly includes an annular housing and an annular scintillator disposed within the annular housing. The annular scintillator includes an annular, substantially continuous crystal scintillator tube configured to absorb ionizing radiation and to emit light energy. A plurality of photo detectors are annularly disposed around the annular scintillator within the annular housing and configured to detect the emitted light energy.

The present disclosure provides systems and methods for create a scanning pencil beam of x-rays and the air cooling of the system. The system has an enclosure with an x-ray beam source disposed therein. An x-ray wheel having or holding an x-ray attenuating ring is disposed proximate to an end of the enclosure and is configured and disposed to rotate the x-ray attenuating ring and form a scanning pencil beam. The system has at least one air inlet and air outlet and at least one air moving device configured and disposed to move air through the air inlet and the air outlet and to air cool the x-ray system.

A computer tomograph operates by rigidly arranged x-ray tubes, which are components of emitter-detector elements, which form an emitter-detector ring opened by relocating one emitter-detector element. Each x-ray tube includes a cathode emitting electrons, and an anode arrangement having an anode. Each cathode has an orientation angle relative to the geometrical center axis of the computer tomograph. A tangential plane on the focal spot of the anode has a surface normal, which includes an anode angle with the center axis. X-ray radiation emitted from the focal spot is directed in a center radiation angle to an x-ray detector axially offset relative to the x-ray tubes. The quotient from the sum of the orientation angle, radiation angle and anode angle is between two ninths and two. Each cathode, interacting with an electrode arrangement of the x-ray tubes, produces a focal spot on one of selectable positions on the anode arrangement.

The present application discloses an X-ray scanner having an X-ray source arranged to emit X-rays from source points through an imaging volume. The scanner may further include an array of X-ray detectors which may be arranged around the imaging volume and may be arranged to output detector signals in response to the detection of X-rays. The scanner may further include a conveyor arranged to convey an object through the imaging volume in a scan direction, and may also include at least one processor arranged to process the detector signals to produce an image data set defining an image of the object. The image may have a resolution in the scan direction that is at least 90% as high as in one direction, and in some cases two directions, orthogonal to the scan direction.

Disclosed is a ceramic shielding apparatus including at least one shield made of a ceramic material and provided inside or outside an X-ray tube to shield radiation; and supports configured to support the shield. According to such a configuration, disadvantages of conventional shielding materials such as lead can be addressed, so that a shield apparatus having excellent shielding properties while being harmless to the human body can be provided.

The present disclosure relates to a system for PET imaging. The system may include a first device and a second device. The first device may include a first scanning channel. The second device may include a second scanning channel connected to the first scanning channel, a heat generating component, and a cooling assembly configured to cool the heat generating component, wherein the cooling assembly may include an inlet chamber and a return chamber, the heat generating component may be closer to a first side of the second device than at least one of the inlet chamber or the return chamber, and the first side of the second device may face the first device.

An imaging system based on an imaging device and/or a cooling system is provided. The imaging system may include a control module, an imaging device, and/or a cooling system. The imaging device may include a first portion and a second portion. The cooling system may include a cooling module configured to generate a cooling medium, and/or a cooling medium passage configured to spread the cooling medium. The cooling medium passage may belong to a closed loop. At least part of the cooling system may be located within the imaging device such that the cooling medium may be in direct contact with the at least part of the imaging device.

The present disclosure relates to a system for PET imaging. The system may include a first device and a second device. The first device may include a first scanning channel. The second device may include a second scanning channel connected to the first scanning channel, a heat generating component, and a cooling assembly configured to cool the heat generating component, wherein the cooling assembly may include an inlet chamber and a return chamber, the heat generating component may be closer to a first side of the second device than at least one of the inlet chamber or the return chamber, and the first side of the second device may face the first device.

The present disclosure relates to a detector apparatus. The detector apparatus may include a detecting module, an electronics module and a cooling assembly. The detecting module may be configured to detect radiation rays emitted from a subject and generate electrical signals in response to detection of radiation rays. The electronics module may be configured to process the electrical signals generated by the detecting module. The cooling assembly may be configured to cool the detecting module and the electronics module. The cooling assembly may include a first layer and a second layer. The first layer may be thermally connected with the detecting module, and the second layer may be thermally connected with the electronics module.