Embodiments provide a stationary X-ray source for a multisource X-ray imaging system for tomographic imaging. The stationary X-ray source includes an array of thermionic cathodes and, in most embodiments a rotating anode. The anode rotates about a rotation axis, however the anode is stationary in the horizontal or vertical dimensions (e.g. about axes perpendicular to the rotation axis). The elimination of mechanical motion improves the image quality by elimination of mechanical vibration and source motion; simplifies system design that reduces system size and cost; increases angular coverage with no increase in scan time; and results in short scan times to, in medical some medical imaging applications, reduce patient-motion-induced blurring.

Some embodiments include an x-ray source, comprising: an anode; a field emitter configured to generate an electron beam; a first grid configured to control field emission from the field emitter; a second grid disposed between the first grid and the anode; and a middle electrode disposed between the first grid and the anode wherein the second grid is either disposed between the first grid and middle electrode or between the middle electrode and the anode.

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.

A system, comprising: a vacuum enclosure; an anode support structure penetrating the vacuum enclosure and including a plurality of first cooling passages; and an anode disposed within the vacuum enclosure, coupled to and supported by the anode support structure, and including: a target; and a plurality of second cooling passages; wherein: each of the second cooling passages is coupled to a corresponding first cooling passage; and the anode is coupled to the anode support structure on a side of the anode different from a side of the anode including the target and different from axial ends of the anode on a major axis of the anode.

Provided are an on-chip miniature X-ray source and a method for manufacturing the same. The on-chip miniature X-ray source includes: an on-chip miniature electron source; a first insulating spacer provided on an electron-emitting side of the on-chip miniature electron source, where the first insulating spacer has a cavity structure; and an anode provided on the first insulating spacer, where a closed vacuum cavity is formed between the on-chip miniature electron source and the anode. The on-chip miniature X-ray source has the advantages of stable X-ray dose, low working requirements for vacuum, fast switch response, capability of integration and batch fabrication, and can be used in various types of small and portable X-ray detection, analysis and treatment devices.

Some embodiments include an x-ray source, comprising: an anode; a field emitter configured to generate an electron beam; a first grid configured to control field emission from the field emitter; a second grid disposed between the first grid and the anode; a third grid disposed between the first grid and the anode; and a middle electrode disposed between the first grid and the anode wherein the second grid is either disposed between the first grid and middle electrode or between the middle electrode and the anode; wherein the third grid is a mesh grid.

Embodiments include a system, comprising: a vacuum enclosure; an anode support structure penetrating the vacuum enclosure and including a plurality of first cooling passages; and an anode disposed within the vacuum enclosure, coupled to and supported by the anode support structure, and including: a target; and a plurality of second cooling passages; wherein: each of the second cooling passages is coupled to a corresponding first cooling passage; the anode is coupled to the anode support structure on a side of the anode different from a side of the anode including the target and different from axial ends of the anode on a major axis of the anode; and the anode is a linear anode.

An X-ray radiator and an X-ray assembly are disclosed. The X-ray radiator according to an embodiment has an evacuated X-ray tube housing, mounted to be rotatable about a rotation axis, the X-ray tube housing including an anode and an electron source. The anode is arranged within the X-ray tube housing non-rotatably relative to the X-ray tube housing and is configured to generate X-ray radiation via electrons impacting upon a focal spot of the anode, the electron source being mounted substantially stationary within the X-ray tube housing relative to the rotation axis. The electron source has a main emitter and at least one subsidiary emitter for emitting electrons. The electron emission of the main emitter and/or of the at least one subsidiary emitter is controllable such that a spatial movement of the focal spot due to a movement of the electron source is reduced.

A stationary in-vivo grating-enabled micro-CT (computed tomography) architecture (SIGMA) system includes CT scanner control circuitry and a number of imaging chains. Each imaging chain includes an x-ray source array, a phase grating, an analyzer grating and a detector array. Each imaging chain is stationary and each x-ray source array includes a plurality of x-ray source elements. Each imaging chain has a centerline, the centerlines of the number of imaging chains intersect at a center point and a first angle between the centerlines of a first adjacent pair of imaging chains equals a second angle between the centerlines of a second adjacent pair of imaging chains. A plurality of selected x-ray source elements of a first x-ray source array is configured to emit a plurality of x-ray beams in a multiplexing fashion.

An x-ray generating unit includes an x-ray tube that is substantially transparent to x-rays and that defines a vacuum therein. A cathode is disposed within the x-ray tube and defines a plurality of spaced apart cavities. An anode is spaced apart from the cathode and includes a material that emits x-rays when impacted by electrons. A plurality of filaments is each disposed in a different one of the cavities defined by the cathode and each is electrically coupled to the cathode. Each filament emits a focused electron beam directed to a different predetermined spot on the anode upon application of a predetermined voltage between the cathode and the anode, thereby causing the anode to generate x-rays.