Abstract:
A medical imaging method comprising generating a radiation at a first energy level by a radiation source, generating a radiation at a second energy level different from the first energy level by the radiation source, emitting the generated radiations at an output of the radiation source towards a detector, and blocking or diverting the emitted radiations during at least one intermediate phase during which the radiation source switches in a transient way from one of the first energy level and the second energy level to the other of the first energy level and the second energy level.
Abstract:
A computed tomography apparatus (10) includes spaced radiation sources (82, 84), such as anodes, which each propagate a cone-beam of radiation (40, 50) into an examination region (14). A detector (22) detects radiation which has passed through the examination region. An attenuation system (55) interposed between the radiation sources and the examination region for cone-angle dependent filtering of the cone beams. The attenuation system allows rays which contribute little to a reconstructed image to be attenuated more than rays which contribute more.
Abstract:
According to one embodiment, there is provided an X-ray tube target. The X-ray tube target has a structure in which a carbon base material is bonded with an Mo base material or Mo alloy base material with a joint layer. The joint layer includes an MoNbTi diffusion phase, an NbTi alloy phase, an Nb-rich phase and a ZrNb alloy phase when the ratios of components in the joint layer are detected by EPMA.
Abstract:
The aim of the invention is to produce an x-ray computed tomography arrangement in which there is no axial offset between the path of the focal spot and the x-ray detector arc. Said aim is achieved by: —arranging the x-ray detector arc and the target around the examination cross-section within a radiation plane such that the x-ray focal spots generated by the deflected electron beam of the electron beam generator lie within an axial plane, the radiation plane, along with the active detector elements; —disposing the x-ray detector arc behind the target in a radial direction such that each imaginary x-ray extending from a focal spot position on the target to a detector element of the x-ray detector arc penetrates the target, which lies in front of the point of incidence on the x-ray detector arc in the direction of radiation, in the area in which the target and the x-ray detector arc angularly overlap; —producing the target from a target member which is preferably made of a material that has a low atomic number and great heat storage capacity or thermal conductance; —applying an electron-decelerating material layer, preferably made of a refractory material that has a high atomic number, to the side of the target member which faces the electron beam.
Abstract:
According to one embodiment, there is provided an X-ray tube target. The X-ray tube target has a structure in which a carbon base material is bonded with an Mo base material or Mo alloy base material with a joint layer. The joint layer includes an MoNbTi diffusion phase, an NbTi alloy phase, an Nb-rich phase and a ZrNb alloy phase when the ratios of components in the joint layer are detected by EPMA.
Abstract:
The object of the present invention is a mount for a rotating target, roughly disk-shaped and perforated at its center. The mount is made of a material which a structurally hardened nickel-based superalloy. The mount is disk-shaped with a narrower area at its periphery, and the narrow peripheral area and the thick area surrounding the central orifice are separated by a discontinuous area whose slope is between 3° and 10°, with the thickness ratio between the narrow peripheral area and the thick area surrounding the central orifice being between 1.5 and 3. The superalloy is an Inconel that has undergone a structural hardening treatment after machining. At least one of the mount's surfaces is coated with an emissive coating used to discharge heat through thermal radiation.
Abstract:
An X-ray tube anode assembly and an X-ray tube assembly are disclosed that include an X-ray target and a drive assembly configured to provide an oscillatory motion to the X-ray target. The drive assembly is configured to provide an oscillatory motion to the target assembly.
Abstract:
A collimator includes a first plate having an aperture therein, the aperture configured to allow passage of a beam of x-rays from a source of a multi-spot source therethrough, and a second plate parallelly positioned with respect to the first plate and configured to receive and attenuate a first portion of the beam of x-rays passing through the aperture in the first plate, the second plate having an aperture therein configured to non-concentrically overlap the aperture in the first plate, to receive a second portion of the beam of x-rays passing through the aperture in the first plate, and to allow passage of the second portion of the beam of x-rays therethrough. A portion of the aperture in the first plate and a portion of the aperture in the second plate form a composite aperture parallel to the beam of x-rays, the composite aperture configured to allow passage of the second portion of the beam of x-rays through the first and second plates.
Abstract:
In a focus detector arrangement and method for an x-ray apparatus for generating projection or tomographic phase-contrast images of an examination subject, a beam of coherent x-rays is generated by an anode that has areas of different radiation emission characteristics arranged in bands thereon, that proceed parallel to grid lines of a phase grid that is used to generate the phase-contrast images.
Abstract:
An X-ray generator comprises a container (1) for maintaining a high vacuum or low pressure gas atmosphere internally, a hemimorphic crystal (4), temperature raising/lowering means (3, 5-7), and a metal target (8) for generating X-rays. In this X-ray generator the metal target (8) has a pointed protrusion protruding toward the hemimorphic crystal (4). When X-rays are generated by raising/lowering the temperature of the hemimorphic crystal (4) by using the temperature raising/lowering means (3, 5-7), the intensity of an electric field formed between the hemimorphic crystal (4) and the metal target (8) increases at the pointed end of the protrusion and thus the intensity of X-rays generated through collision of electrons against the metal target (8) increases. Consequently, an X-ray generator employing a hemimorphic crystal, which is capable of generating X-rays with practically sufficient intensity can be provided.