Patent Application
20120106710
The subject matter disclosed herein relates to the thermal regulation of components within an X-ray tube, and more specifically to heat transfer between the anode and the rotary mechanism to which the anode is attached.
A variety of diagnostic and other systems may utilize X-ray tubes as a source of radiation. In medical imaging systems, for example, X-ray tubes are used in projection X-ray systems, fluoroscopy systems, tomosynthesis systems, and computer tomography (CT) systems as a source of X-ray radiation. The radiation is emitted in response to control signals during examination or imaging sequences. The radiation traverses a subject of interest, such as a human patient, and a portion of the radiation impacts a detector or a photographic plate where the image data is collected. In conventional projection X-ray systems the photographic plate is then developed to produce an image which may be used by a radiologist or attending physician for diagnostic purposes. In digital X-ray systems a digital detector produces signals representative of the amount or intensity of radiation impacting discrete pixel regions of a detector surface. In CT systems a detector array, including a series of detector elements, produces similar signals through various positions as a gantry is displaced around a patient.
The X-ray tube is typically operated in cycles including periods in which X-rays are generated, interleaved with periods in which the X-ray source is allowed to cool. In X-ray tubes having rotating anodes, the large amount of heat that is generated at the anode during electron bombardment can limit the amount of electron beam flux suitable for use. Such limitations may lower the overall flux of X-rays that are generated by the X-ray tube. The generated heat may be removed from the anode through various features, such as coolant and other X-ray tube components. One example is the transfer of heat through the shaft. Unfortunately, inefficient heat transfer to the shaft may not allow continuous operation of the X-ray tube, and may also result in unsuitable X-ray tube temperatures, which can reduce the expected useful life of the tube. There is a need, therefore, for an approach for limiting overheating of X-ray tubes. Specifically, it is now recognized that there is a need for improved heat transfer between components of an X-ray tube.
In one embodiment, an X-ray tube is provided. The X-ray tube generally includes a fixed shaft, a rotating bearing sleeve disposed about the fixed shaft and configured to rotate with respect to the fixed shaft via a rotary bearing, an electron beam target disposed about the bearing sleeve and configured to rotate with the bearing sleeve, and a thermally conductive, deformable metallic gasket disposed between the target and the bearing sleeve and configured to conduct heat between the target and the bearing sleeve in operation.
In another embodiment, an X-ray tube is provided that generally includes a fixed shaft, a rotating bearing sleeve disposed about the fixed shaft and configured to rotate with respect to the fixed shaft via a rotary bearing, an electron beam target disposed about the bearing sleeve and configured to rotate with the bearing sleeve, a thermally conductive gasket disposed between the target and the bearing sleeve and configured to conduct heat between the target and the bearing sleeve in operation, and a particle trap disposed radially around the gasket.
In a further embodiment, a method for making an X-ray tube is provided. The method generally includes disposing a rotating bearing sleeve about a fixed shaft, disposing an electron beam target about the bearing sleeve, the electron beam target being rotatable with the bearing sleeve during operation, and disposing a thermally conductive gasket between the target and the bearing sleeve to conduct heat between the target and the bearing sleeve in operation.
These and other features, aspects, and advantages of the present invention will become better understood when the following detailed description is read with reference to the accompanying drawings in which like characters represent like parts throughout the drawings, wherein:
The present embodiments are directed towards enhanced heat conduction within an X-ray tube. Specifically, the present embodiments provide a deformable gasket that allows enhanced heat conduction between an X-ray target and a bearing supporting the target in rotation. The gasket may also allow for limited target displacement relative to a surface at which the target is attached to the bearing. In allowing such controlled displacement, pulling of the bearing by the target during rotation, and the resulting increase in the gap between the rotational and stationary components, may be avoided. A particle trap may also be provided to mitigate particle migration out of the joint formed between the X-ray target, the gasket, and the bearing.
The anode assembly 12 generally includes a rotor 18 and a stator outside of the X-ray tube 10 (not shown) at least partially surrounding the rotor 18 for causing rotation of an anode 20 during operation. The anode 20 is supported in rotation by a bearing 22, which may be a ball bearing, spiral groove bearing, or similar bearing. In general, the bearing 22 includes a stationary portion 24 and a rotary portion 26 to which the anode 20 is attached. Additionally, as illustrated, the X-ray tube 10 includes a hollow portion 28 through which a coolant, such as oil, may flow. The bearing 22 and its connection to the anode 20 are described in further detail below with respect to
The front portion of the anode 20 is formed as a target disc having a target or focal surface 30 is formed thereon. During operation, as the anode 20 rotates, the focal surface 30 is struck by an electron beam 32. The anode 20 may be manufactured of any metal or composite, such as tungsten, molybdenum, copper, or any material that contributes to Bremsstrahlung (i.e., deceleration radiation) when bombarded with electrons. The anode surface material is typically selected to have a relatively high refractory value so as to withstand the heat generated by electrons impacting the anode 20. During operation of the X-ray tube 10, the anode 20 may be rotated at a high speed (e.g., 100 to 200 Hz) to spread the thermal energy resulting from the electron beam 32 striking the anode 20. Further, the space between the cathode assembly 14 and the anode 20 may be evacuated in order to minimize electron collisions with other atoms and to maximize an electric potential. In some X-ray tubes, voltages in excess of 20 kV are created between the cathode assembly 14 and the anode 20, causing electrons emitted by the cathode assembly 14 to become attracted to the anode 20.
The electron beam 32 is produced by the cathode assembly 14 and, more specifically, a cathode 34 that receives one or more electrical signals via a series of electrical leads 36. The electrical signals may be timing/control signals that cause the cathode 34 to emit the electron beam 32 at one or more energies and at one or more frequencies. The cathode 34 includes a central insulating shell 38 from which a mask 40 extends. The mask 40 encloses the leads 36, which extend to a cathode cup 42 mounted at the end of the mask 40. In some embodiments, the cathode cup 42 serves as an electrostatic lens that focuses electrons emitted from a thermionic filament within the cup 42 to form the electron beam 32.
As control signals are conveyed to cathode 34 via leads 36, the thermionic filament within cup 42 is heated and produces the electron beam 32. The beam 32 strikes the focal surface 30 of the anode 20 and generates X-ray radiation 46, which is diverted out of an X-ray aperture 48 of the X-ray tube 10. The direction and orientation of the X-ray radiation 46 may be controlled by a magnetic field produced outside of the X-ray tube 10 or by electrostatic means at the cathode 34. The field produced may generally shape the X-ray radiation 46 into a focused beam, such as a cone-shaped beam as illustrated. The X-ray radiation 46 exits the tube 10 and is generally directed towards a subject of interest during examination procedures.
As noted above, the X-ray tube 10 may be utilized in systems where the X-ray source is displaced relative to a patient, such as in CT imaging systems where the source of X-ray radiation rotates about a subject of interest on a gantry. Accordingly, it may be desirable that the X-ray tube 10 produce a suitable flux of X-rays so as to avoid noise generated from insufficient X-ray penetration while the X-ray tube 10 is in motion. To achieve such suitable X-ray flux, the X-ray tube 10 may generally include, as mentioned above, a number of features that are configured to allow the dispersion of thermal energy as the anode 20, which produces X-rays and thermal energy when bombarded with the electron beam 32, begins to heat during use. One feature to control such heat buildup in X-ray tubes is a rotating anode. Further, in accordance with the present approaches, one or more features may be placed proximate to the anode 20 to facilitate heat transfer from the anode 20 to other components of the X-ray tube 10.
The anode 20, which generally has an annular shape with an annular opening proximate its center, is disposed about the bearing sleeve 62 in such a way so as to cause rotation of the anode 20 when the bearing sleeve 62 rotates. According to present embodiments, a gasket 70 is disposed between the anode 20 and the bearing sleeve 62. The gasket 70, in a general sense, is configured to facilitate the transfer of thermal energy from the anode 20 to the bearing sleeve 62 as the anode 20 heats as a result of electron bombardment. Further, the gasket 70 may also transfer heat from the bearing sleeve 62 to the anode 20, such as in embodiments where rotation of the SGB 60 is utilized to generate thermal energy. To allow such heat transfer, the gasket 70 is disposed between an axial face 72 of a shoulder 74 of the bearing sleeve 62. Such placement may be advantageous to allow heat to be removed from the bearing sleeve 62 by coolant that circulates within a coolant flow path 76 of the fixed shaft 64.
The gasket 70 may be constructed from or include any number of materials capable of thermal energy transmission. In accordance with an embodiment of the present disclosure, the gasket 70 may have a thermal conductivity of at least 100 Watts per Kelvin per meter (W·K−1·m−1). In some embodiments, the thermal conductivity may be between about 200 and 500 W·K−1·m−1, or at least about 900, 1000, 3000, 4000, or 5000 W·K−1·m−1. As an example, the gasket 70 may include a ceramic material, a composite or nano-composite material, graphite, or a metal. Metals that may be utilized in accordance with present embodiments may include noble metals that are able to deform, yet substantially retain their shape, at the temperatures experienced during usage of the X-ray tube 10. For example, the noble metal may be silver (Ag), copper (Cu), gold (Au), platinum (Pt), or alloys or mixtures thereof.
The gasket 70 is advantageously deformable so as to allow the gasket 70 to fill any asperities in the surfaces of the anode 20 and the axial face 72 of the bearing sleeve 62. Further, the deformability of the gasket 70 helps to account for the flatness of the surfaces of the anode 20 and the bearing sleeve 62. The gasket 70 may be sized based on the particular dimensions of the components of the X-ray tube 10 and other design considerations. To allow suitable thermal conduction, the thickness, in the longitudinal direction (i.e., the direction defined by the axis of SGB 60) of the gasket 70 may be sized anywhere between approximately 1 micron (e.g., 1, 2, 3, 5, or 10 microns) and approximately 10 millimeters (mm) (e.g., 1, 2, 3, 5, or 10 mm) Further, the gasket 70 may only partially extend up the axial face 72 of the bearing sleeve 62, may be substantially flush with the diametrical extent of the axial face 72, or may extend beyond the axial face 72.
It should be noted that, even at the operating temperatures of the X-ray tube 10, which may approach or exceed about 400° C., there is no appreciable metallurgical bond between the gasket 70 and the anode 20 or the bearing sleeve 62. Such a lack of a metallurgical bond may allow axial growth (i.e., in the longitudinal direction) of the anode 20 as it begins to heat upon electron bombardment without causing the anode 20 to pull on the shoulder 74 of the bearing sleeve 62. Such pulling may cause the gap size of the SGB 60 to increase, which decreases the load that the SGB 60 may support during gantry rotation. Accordingly, the lack of pulling on the bearing sleeve 62 allows the SGB 60 to remain substantially cylindrical without appreciable deformation. This may allow rotation of the gantry at higher speeds than would be otherwise suitable, which can decrease the time needed for examination sequences and overall radiation exposure to the patient or subject of interest.
As noted above, the gasket 70 may be constructed from soft materials that are able to deform so as to allow slight movement of the anode 20 during operation of the X-ray tube 10. It may therefore be appreciated that as the X-ray tube 10 is utilized, small particulates of the gasket 70 may be removed, for example as a result of shear forces applied by either or a combination of the anode 20 or the shoulder 74 of the bearing sleeve 62. Such particulates may, in certain situations, be detrimental to the operation of the X-ray tube 10. For example arcing caused by the particulates (e.g., when the particulates are struck by the electron beam 32) may occur, and/or the vacuum within the tube 12 may be decreased due to the increased presence of particulates.
Accordingly, the present approaches also provide features that are configured to trap particulates generated from the gasket 70. If a liquid metal is used in the joint between the target and bearing sleeve, this feature will also serve to trap the liquid metal from the joint. An embodiment of the X-ray tube 10 including such features is illustrated in
As illustrated, the particle trap 80 includes a circumferential recess 82 that is configured to collect gasket particulates and/or liquid metal. The circumferential recess 82 may assume any number of shapes and/or sizes, as depicted in
During operation, the anode 20 and, via protrusion therefrom, the particle trap 80 rotate with respect to the fixed shaft 64. The gasket 70 and the bearing sleeve 62 also rotate with respect to the fixed shaft 64. Therefore, in situations where particulates are formed from the gasket 70, the particulates are directed towards the circumferential recess 82 of the particle trap 80 via centrifugal force, which allows the particle trap 80 to maintain the vacuum, and, therefore, the voltages within the X-ray tube 10. In this way, rotation of the SGB 60 contains the particulates within the particle trap 80.
As noted above,
In a similar embodiment, the particle trap 80 may not have a circumferential recess 82, as noted above.
In accordance with another aspect of the present disclosure,
After performing the acts represented by block 102, a thermally conductive gasket is disposed about the bearing sleeve (block 104). The thermally conductive gasket, as noted above, is configured to transfer heat between an electron beam target (i.e., an anode) and the bearing sleeve. Accordingly, an electron beam target (i.e., an anode) is then disposed about the bearing sleeve (block 106). While the method 100 is illustrated as disposing the gasket on the bearing sleeve prior to disposing the target on the bearing sleeve, it should be noted that the gasket may be disposed thereon after the target. As an example, the gasket may have a slit that allows it to be pulled over the bearing sleeve. As an example, the electron beam target and the gasket may have an annular shape with an annular opening in their respective centers that are configured to receive the bearing sleeve.
After performing the acts represented by blocks 102-106 as well as any other X-ray tube manufacturing processes, the X-ray tube may be utilized. In use, the bearing (e.g., the SGB) is rotated (block 108), followed by bombardment of the electron beam target with an electron beam (block 110). As noted above with respect to
This written description uses examples to disclose embodiments of the invention, including the best mode, and also to enable any person skilled in the art to practice the invention, including making and using any devices or systems and performing any incorporated methods. The patentable scope of the invention is defined by the claims, and may include other examples that occur to those skilled in the art. Such other examples are intended to be within the scope of the claims if they have structural elements that do not differ from the literal language of the claims, or if they include equivalent structural elements with insubstantial differences from the literal languages of the claims.
