A time correction device for a PET system, comprises a detector ring, a ring-shaped prosthesis, and detection, data acquisition, data coincidence, time shift calculation, data correction application modules. Center of the ring-shaped prosthesis overlaps with axial and radial center of the detector ring. The detection module is located in ring-shaped prosthesis. Center of the detection module is at the center of the ring-shaped prosthesis. The data acquisition module comprises data gathering and energy filtering modules connected to each other. The data gathering module comprises detectors and the detection module. The energy filtering module connects to the data gathering module receiving single-event time information. The data coincidence module is connects to the energy filtering module receiving the single-event time information. Time shift calculation module connects to the data coincidence module providing a shift value of the detectors. The data correction application module applies the shift value to the PET system.

Various methods and systems are provided for stationary CT imaging. In one embodiment, an imaging system comprises a chamber shaped to enclose a subject to be imaged, a support surface disposed within the chamber and shaped to maintain the subject in an upright position, and an annular imaging unit encircling the chamber and having a fixed angular orientation to the chamber, the annular imaging unit including a distributed x-ray unit and a detector array arranged opposite to each other across the chamber. The imaging system may image the subject without rotation of the annular imaging unit.

An apparatus and a method for correcting for signal variations in pixels of a main photoelectric conversion element in a radiation detection apparatus due to focal spot position drifts. Edge reference detectors are positioned next to a main detector, in a fan beam coverage but outside a scan field of view. The signal variations of the edge reference detectors under an anti-scatter-grid shadow are used to estimate a real-time focal spot movement, which is used to estimate a shadow/signal variation on the main detector that are in the scan field of view.

Imaging systems and methods are provided for scanning a patient’s head using a portable CT scanner. An imaging assembly can comprise a portable scan board on which a patient is positioned, and a corresponding portable CT scanner positioned and locked onto the portable scan board. The portable CT scanner and the portable scan board can form a portable CT scanning assembly capable of rotating an X-ray source and corresponding X-ray detector around the patient’s head to transmit X-rays through the patient’s head at one or more angles, while translating across the portable scan board to scan one or more portions of the patient’s head. A composite image reconstructed based on the rotational and translational scanning is generated representing one or more interior aspects of the patient’s head.

A PET system for a PET/MRI machine is disclosed. The PET system includes a PET detector assembly arranged to form a single gap aligned with the high-density support structure assembly and the shielded cable assembly that run along the patient bed in the PET/MRI machine. The PET detector arrangement maximizes the allowable diameter of the PET system within the MR magnet and ensures that the high-density material does not interfere with image acquisition. Further, various image reconstruction techniques compatible with the PET detector arrangement are described.

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.

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

A C-Arm X-ray imaging system using multiple pulsed X-ray sources in motion to perform efficient and ultrafast 3D radiography is presented. X-ray sources mounted on a structure in motion to form an array. X-ray sources move simultaneously relative to an object on a pre-defined arc track at a constant speed as a group. Each individual source can also move rapidly around its static position in a small distance. When a source has a speed that is equal to group speed but with opposite moving direction, the source at one C-arm end and X-ray flat panel detector at other C-arm end are activated through an external exposure control unit so that source stay momentarily standstill. The C-arm provides 3D X-ray scan imaging over a wide sweep angle and in different position by rotation. The X-ray image can be analyzed by an artificial intelligence module for real-time diagnosis.

An X-ray imaging system using multiple pulsed X-ray sources to perform highly efficient and ultrafast 3D radiography is presented. There are multiple pulsed X-ray sources mounted on a structure in motion to form an array of sources. The multiple X-ray sources move simultaneously relative to an object on a pre-defined arc track at a constant speed as a group. Electron beam inside each individual X-ray tube is deflected by magnetic or electrical field to move focal spot a small distance. When focal spot of an X-ray tube beam has a speed that is equal to group speed but with opposite moving direction, the X-ray source and X-ray flat panel detector are activated through an external exposure control unit so that source tube stay momentarily standstill equivalently. 3D scan can cover much wider sweep angle in much shorter time and image analysis can also be done in real-time.

An X-ray imaging system using multiple pulsed X-ray sources in motion to perform high efficient and ultrafast 3D radiography using an X-ray flexible curved panel detector is presented. There are multiple pulsed X-ray sources mounted on a structure in motion to form an array of sources. The sources move simultaneously relative to an object on a predefined arc track at a constant speed as a group. Each individual X-ray source can move around its static position at a small distance. When an individual source has a speed equal to group speed, but with opposite moving direction, the individual source and detector are activated. This allows source to stay relatively standstill during activation. The operation results in reduced source travel distance for each individual source. 3D radiography image data can be acquired with much wider sweep angle in much shorter time, and image analysis can also be done in real-time.