Distributed x-ray tube, distributed x-ray source assembly, and imaging system

Abstract

The application provides a distributed X-ray tube, a distributed X-ray source assembly and an imaging system. The distributed X-ray tube comprises: a tube shell comprising a front plate, a back plate and two end plates, the front plate and the back plate respectively extend along a first direction, the two end plates respectively intersect the first direction, the front plate is provided with a radiation window for radiation emission, and the two end plates are oppositely arranged along the first direction; a vacuum cavity, the vacuum cavity is at least partially surrounded by the tube shell; an anode, the anode is located in the vacuum cavity, the anode comprises a plurality of target points, the anode is configured to generate a plurality of X-ray beams from the plurality of target points, and the plurality of target points are arranged at intervals along the first direction. At least one end plate comprises a cavity outer side surface located on a side of the end plate away from the vacuum cavity, the cavity outer side surface comprises an outer side end surface and a forward clearance surface, in a second direction, the forward clearance surface is closer to the front plate than the outer side end surface; in the first direction, the forward clearance surface is recessed inward in a direction close to the vacuum cavity relative to the outer side end surface.

Description

Technical Field

[0001] This invention relates to the field of X-ray tube and radiation imaging technology, and more specifically, to a distributed X-ray tube, a distributed X-ray source assembly, and an imaging system based on a distributed X-ray source. Background Technology

[0002] As a core component of static CT systems, distributed X-ray tubes integrate arrayed cathode assemblies and linear anodes, typically housed in a hexagonal cuboid vacuum chamber structure. Due to the need to maintain ultra-high vacuum and implement complex electrical controls, the top, bottom, and back plates of the chamber often contain a high density of ion pumps, exhaust pipes, cooling circulation systems, and numerous high-voltage leads. Constrained by this dense peripheral layout, the mechanical mounting structure of the X-ray tube often needs to be located on end plates at both ends of the chamber, or fixed using complex clamping structures.

[0003] However, traditional hexahedral end structures face irreconcilable physical contradictions when constructing L-shaped or multi-segment arc-shaped spliced ​​X-ray source assemblies: on the one hand, to withstand the enormous atmospheric pressure load and provide reliable threaded installation depth, the end plate needs to retain a considerable physical thickness, which directly occupies space in the length direction, resulting in a large focal distance and imaging blind zone when adjacent X-ray tubes are spliced; on the other hand, limited by the electric field distribution of the internal high-voltage anode, the inner wall of the end plate needs to maintain sufficient vacuum insulation distance from the high-potential anode tip, limiting the possibility of thinning the end plate. In addition, if the mounting point is moved to the long side to avoid the end, the positioning error will be amplified due to the distance of the mounting point from the focal point, making it difficult to meet the stringent alignment accuracy requirements of static CT systems. Summary of the Invention

[0004] In view of the above, an embodiment of the present invention in a first aspect provides a distributed X-ray tube, comprising: a tube housing, the tube housing including a front plate, a back plate and two end plates, the front plate and the back plate extending along a first direction, the two end plates intersecting the first direction, the front plate having a ray window for ray emission, the back plate being disposed opposite to the front plate along a second direction, the two end plates being disposed opposite to each other along the first direction, the first direction and the second direction intersecting; a vacuum chamber, the vacuum chamber being at least partially surrounded by the tube housing; and an anode located in the vacuum chamber, the anode including a plurality of target points, the anode being configured to generate multiple X-ray beams from the plurality of target points, the plurality of target points being spaced apart along the first direction, wherein at least one of the end plates includes an external side surface located on the side of the end plate away from the vacuum chamber, the external side surface including an outer end face and a forward clearance surface, in the second direction, the forward clearance surface being closer to the front plate relative to the outer end face; in the first direction, the forward clearance surface being recessed inward relative to the outer end face towards the vacuum chamber.

[0005] In one exemplary embodiment, at least one of the end plates includes an inner side surface located on the side of the end plate near the vacuum cavity, at least a portion of the inner side surface being formed as an inner arc surface convex toward the outer end face.

[0006] In one exemplary embodiment, the anode includes a male end tip located at the end of the anode in the first direction, and at least a portion of the male end tip is provided with a convex arc surface protruding toward the outer end face.

[0007] In an exemplary embodiment, the vacuum cavity includes a first cavity and two second cavities located on either side of the first cavity along the first direction, at least a portion of each of the two second cavities being configured to bulge toward the inner arc surface; and the anode includes two anode tips located on either side of the anode in the first direction, and the two anode tips are respectively located in the two second cavities.

[0008] In one exemplary embodiment, the plurality of target points includes two edge target points respectively close to the two end plates in the first direction, and the two edge target points are respectively located in the two second cavities.

[0009] In one exemplary embodiment, at least a portion of the inner side surface of the cavity includes a spherical surface, the center of which is located in the region where the male end tip is located.

[0010] In one exemplary embodiment, the male end is a spherical end, and the center of the male end coincides with the center of the adjacent inner surface of the cavity.

[0011] In one exemplary embodiment, the minimum distance between the inner side of the cavity and the outer end face in the first direction is greater than or equal to 1 mm.

[0012] In an exemplary embodiment, the forward clearance surface is connected between the outer end face and the front plate, and the minimum distance between the forward clearance surface and the inner side of the cavity is greater than or equal to 1 mm.

[0013] In one exemplary embodiment, the forward clearance surface extends along a first plane, which is inclined relative to the first direction.

[0014] In one exemplary embodiment, the angle between the first plane and the first direction is 30° to 75°.

[0015] In one exemplary embodiment, the forward clearance surface is an arc-shaped surface.

[0016] In one exemplary embodiment, the arc axis of the forward clearance surface passes through the geometric center of the inner side surface of the cavity.

[0017] In an exemplary embodiment, the forward clearance surface is a spherical surface with a first origin as its center, and the first origin coincides with the center of the adjacent inner surface of the cavity.

[0018] In one exemplary embodiment, the outer side of the cavity further includes a rear side located near the back plate, the rear side being coplanar with the back plate.

[0019] In an exemplary embodiment, the distributed X-ray tube further includes a mounting connection portion located on the rear side surface. The mounting connection portion includes at least two mounting connection positions, which are spaced apart along a third direction on the rear side surface. The third direction is perpendicular to the second direction and the first direction, respectively.

[0020] In one exemplary embodiment, at least one of the end plates further includes a weight-reducing groove formed on the outer side of the cavity near the back plate, the weight-reducing groove being located between two adjacent mounting connection positions.

[0021] An embodiment of the second aspect of the present invention provides a distributed X-ray source assembly comprising at least two distributed X-ray tubes as described above.

[0022] In one exemplary embodiment, at least two adjacent distributed X-ray tubes are arranged at a predetermined angle, and the forward clearance surfaces of the end plates of at least two adjacent distributed X-ray tubes cooperate with each other.

[0023] In one exemplary embodiment, the target points of at least two adjacent distributed X-ray tubes are arranged perpendicularly to each other.

[0024] In one exemplary embodiment, the distributed X-ray source assembly includes at least three distributed X-ray tubes arranged sequentially, the envelope formed by the arrangement directions of the target points of the at least three distributed X-ray tubes being arc-shaped, and the forward clearance surfaces of the end plates of any two adjacent distributed X-ray tubes cooperating with each other.

[0025] In one exemplary embodiment, at the splice of at least two adjacent distributed X-ray tubes, the spacing between adjacent target points of two adjacent anodes is less than the maximum thickness of the endplates of each distributed X-ray tube in the first direction.

[0026] In one exemplary embodiment, at least two of the distributed X-ray tubes are arranged in a straight line along a first direction, with the end plates of two adjacent distributed X-ray tubes connected together and their forward-facing clearance surfaces facing each other.

[0027] An embodiment of the present invention in a third aspect provides an imaging system based on a distributed X-ray source, comprising: a radiation source, the radiation source including a distributed X-ray tube as described above or a distributed X-ray source assembly as described above; and a detector disposed opposite to the radiation source to form a scanning area between the radiation source and the detector. Attached Figure Description

[0028] The above and other objects, features and advantages of the present invention will become more apparent from the following description of embodiments of the invention with reference to the accompanying drawings, in which:

[0029] Figure 1 This is a schematic diagram of a traditional distributed X-ray tube.

[0030] Figure 2 This is a schematic diagram illustrating the displacement deviation of a traditional distributed X-ray tube installed with a top and bottom plate.

[0031] Figure 3 This is a simulation analysis diagram of the electrostatic field of a traditional distributed X-ray tube;

[0032] Figure 4 This is a schematic diagram of the structure of a distributed X-ray tube according to an embodiment of the present invention;

[0033] Figure 5This is a simulation analysis diagram of the electrostatic field of a distributed X-ray tube according to an embodiment of the present invention;

[0034] Figure 6 This is a cross-sectional view of a distributed X-ray tube according to some exemplary embodiments of the present invention;

[0035] Figure 7 This is a cross-sectional view of a traditional distributed X-ray tube;

[0036] Figure 8 This is a schematic diagram of the structure of an imaging system including a distributed X-ray source assembly according to some exemplary embodiments of the present invention;

[0037] Figure 9 This is a schematic diagram of the structure of an imaging system that includes traditional distributed X-ray source components;

[0038] Figure 10 This is a schematic diagram of the structure of an imaging system including a distributed X-ray source assembly according to some other exemplary embodiments of the present invention;

[0039] Figure 11 This is a schematic diagram of the structure of an imaging system that includes traditional distributed X-ray source components;

[0040] Figure 12 This is a schematic diagram of the structure of an imaging system including a distributed X-ray source assembly according to some further exemplary embodiments of the present invention;

[0041] Figure 13 This is a schematic diagram of the structure of an imaging system that includes traditional distributed X-ray source components;

[0042] Figure 14 This is a schematic diagram of the structure of the end plate of a distributed X-ray tube according to some embodiments of the present invention, viewed from one perspective.

[0043] Figure 15 This is a schematic diagram of the end plate of a distributed X-ray tube according to some embodiments of the present invention, viewed from another perspective;

[0044] Figure 16 This is a cross-sectional view of the end plate of a distributed X-ray tube taken from one position according to some embodiments of the present invention;

[0045] Figure 17 This is a cross-sectional view of the end plate of a distributed X-ray tube taken from another location according to some embodiments of the present invention;

[0046] Figure 18 This is a first enlarged structural diagram of the mounting connection position of a distributed X-ray tube according to some embodiments of the present invention;

[0047] Figure 19This is a second enlarged structural diagram of the mounting connection position of a distributed X-ray tube according to some embodiments of the present invention;

[0048] Figure 20 This is a schematic diagram of the structure of the end plate of a distributed X-ray tube according to some other embodiments of the present invention, viewed from one perspective.

[0049] Figure 21 This is a schematic diagram of the end plate of a distributed X-ray tube according to other embodiments of the present invention, viewed from another perspective.

[0050] Figure 22 This is a cross-sectional view of the end plate of a distributed X-ray tube according to other embodiments of the present invention;

[0051] Figure 23 This is a schematic diagram of the structure of the end plate of a distributed X-ray tube according to some embodiments of the present invention, viewed from one perspective.

[0052] Figure 24 This is a schematic diagram of the end plate of a distributed X-ray tube according to some embodiments of the present invention, viewed from another perspective; and

[0053] Figure 25 This is a cross-sectional view of the end plate of a distributed X-ray tube according to some embodiments of the present invention. Detailed Implementation

[0054] To enable those skilled in the art to better understand the technical solutions of this invention, the technical solutions of the embodiments of this invention will be clearly and completely described below with reference to the accompanying drawings. Obviously, the described embodiments are only some embodiments of this invention, and not all embodiments. Based on the embodiments of this invention, all other embodiments obtained by those skilled in the art without creative effort should fall within the scope of protection of this invention.

[0055] The terminology used herein is for the purpose of describing particular embodiments only and is not intended to limit the invention. The terms “comprising,” “including,” etc., as used herein indicate the presence of the stated features, steps, operations, and / or components, but do not exclude the presence or addition of one or more other features, steps, operations, or components.

[0056] All terms used herein (including technical and scientific terms) have the meanings commonly understood by those skilled in the art, unless otherwise defined. It should be noted that the terms used herein are to be interpreted in a manner consistent with the context of this specification, and not in an idealized or overly rigid way.

[0057] When using expressions such as "at least one of A, B, and C," the meaning should generally be interpreted according to the understanding of someone skilled in the art. For example, "a system having at least one of A, B, and C" should include, but is not limited to, systems having A alone, having B alone, having C alone, having A and B, having A and C, having B and C, and / or having A, B, and C. Similarly, when using expressions such as "at least one of A, B, or C," the meaning should generally be interpreted according to the understanding of someone skilled in the art. For example, "a system having at least one of A, B, or C" should include, but is not limited to, systems having A alone, having B alone, having C alone, having A and B, having A and C, having B and C, and / or having A, B, and C.

[0058] X-ray tubes, as the core device for generating X-rays, are used in fields such as industrial non-destructive testing, public safety inspections, and medical imaging diagnostics. From a basic structural perspective, an X-ray tube is typically a highly integrated vacuum electronic device, with its core components including a vacuum-sealed cavity, a cathode system, and an anode system. During operation, the free electron beam generated by the cathode filament or electron emitter is accelerated by the high-voltage electric field applied between the cathode and anode, gaining extremely high kinetic energy and striking the anode target. The electron kinetic energy is instantly converted into X-ray photons and heat energy. Because the generation, acceleration, and controlled movement of free electrons require an extremely high vacuum environment to avoid scattering of the electron beam by gas molecules and high-voltage breakdown, the vacuum-sealed cavity is not only the mechanical support for the components but also the physical barrier maintaining the high-vacuum environment. Simultaneously, to achieve high-voltage feed and signal control, multiple electrically penetrating connectors insulated from the shell are required on the cavity wall, and low-attenuation-rate X-ray windows are also needed in specific directions to extract the generated X-rays. This combination of vacuum, high-voltage insulation, electro-optics, thermal and mechanical structure determines that the structural design of the X-ray tube itself has extremely high sealing complexity.

[0059] With the development of static CT technology, distributed X-ray tubes (0100) with multiple independent focal points are increasingly being adopted. The three-dimensional imaging technology enabled by the distributed X-ray tube (0100) allows CT equipment to break free from the traditional slip-ring rotation structure, achieving ultra-high-speed, high-definition imaging. To accommodate the arrayed cathode components and corresponding linear anode targets, a reference... Figure 1 , Figure 7 , Figure 9 , Figure 11 , Figure 13As shown, the traditional distributed X-ray tube 0100 adopts a straight-line extended hexahedral prism-shaped vacuum cavity structure. This structure has become the mainstream choice in the industry mainly based on the following layout logic: one side of the cavity (usually called the front plate 0111) needs to have a large area of ​​long strip-shaped X-ray window 0117 to draw out the X-rays. To avoid obstruction, other components usually cannot be placed on this side; and in order to maintain the ultra-high vacuum degree under the huge internal volume and solve the problem of high power heat dissipation, the ion pump 0420, exhaust pipe 0430, anode cooling circulation system 0410 and a large number of anode lead terminals 0440 need to be densely arranged on the top plate 0115, bottom plate 0116 or back plate 0112 of the cavity. This high-density component arrangement means that the long sides (front, back, top, and bottom) of the vacuum chamber are almost completely occupied, which forces the mechanical installation and fixing interface 01132 of the distributed X-ray tube 0100 to be designed on the end plates 0113 at both ends, or to be fixed by a complex C-shaped connecting frame 01133 holding the top plate 0115 and the bottom plate 0116 in the very few gaps.

[0060] Research has revealed that while theoretically reducing the thickness of end plate 0113 can narrow the gap, in engineering practice, it faces a severe structural and electric field contradiction: On the one hand, end plate 0113, as the sealing component of the vacuum cavity, bears a huge atmospheric pressure load. Simply thinning end plate 0113 to shorten the gap will fail to meet structural strength requirements, leading to deformation or even vacuum leakage; furthermore, a thin end plate 0113 cannot provide sufficiently deep mounting threaded holes, leaving no place to install the mounting structure. On the other hand, an even greater constraint comes from the distribution pattern of the high-voltage electric field. Distributed X-ray tubes 0100 typically use linear long anodes, with their ends at extremely high potentials (e.g., above 100kV). According to electrostatic field theory, right-angled or angular structures will lead to severe electric field distortion and concentration. (See also...) Figure 3 , Figure 7 , Figure 9 , Figure 11 , Figure 13 As shown, the existing hexahedral right-angled endplate 0113 structure requires a sufficiently large vacuum insulation distance between the anode and the inner wall of the endplate 0113 to ensure the insulation safety between the anode high voltage and the ground potential cavity. This means that the inner wall of the endplate 0113 needs to be far away from the anode tip. In other words, in the traditional distributed X-ray tube 0100, the endplate 0113 itself needs to be relatively thick, and the distance between the target point closest to the endplate 0113 and the endplate 0113 needs to be sufficiently large.

[0061] Based on this, traditional distributed X-ray tubes 0100 encounter insurmountable physical bottlenecks in stitching applications pursuing higher imaging quality, and simple structural optimization is extremely difficult. When constructing static CT systems with linear, L-shaped, gate-shaped, or multi-segment linear-fitted-circle configurations, the endplate 0113 itself needs to be relatively thick, and the distance between the target point closest to the endplate 0113 and the endplate 0113 needs to be sufficiently large. Therefore, in adjacent distributed X-ray tubes 0100, the distance between the target point near the endplate of one distributed X-ray tube 0100 and the target point near the endplate of another distributed X-ray tube 0100 is relatively large, resulting in a large missing angle in the imaging viewpoint, i.e., a large blind zone or dead zone in the imaging viewpoint, which is detrimental to forming high-quality images. For example, as... Figure 9 As shown, when multiple traditional distributed X-ray tubes 0100 are spliced ​​together to form a linear X-ray source assembly, the distance between the rightmost target point of the left distributed X-ray tube 0100 and the leftmost target point of the right distributed X-ray tube 0100 is relatively large, resulting in a large missing angle in the imaging view. For example, as... Figure 11 As shown, when multiple traditional distributed X-ray tubes 0100 are spliced ​​together to form an L-shaped X-ray source assembly, the distance between the rightmost target point of the upper distributed X-ray tube 0100 and the uppermost target point of the right distributed X-ray tube 0100 is relatively large, resulting in a large missing angle in the imaging view. For example, as... Figure 13 As shown, when multiple traditional distributed X-ray tubes 0100 are spliced ​​together to form a multi-segment linearly fitted circular X-ray source assembly, the distance between the rightmost target point of the upper distributed X-ray tube 0100 and the leftmost target point of the upper right distributed X-ray tube 0100 is relatively large, resulting in a large missing angle of imaging view; the distance between the rightmost target point of the upper right distributed X-ray tube 0100 and the topmost target point of the right distributed X-ray tube 0100 is also relatively large, resulting in a large missing angle of imaging view.

[0062] Furthermore, research has revealed that attempting to alter the installation method, such as shifting the fixed installation point to the center of the extended edge of the distributed X-ray tube 0100 (e.g., top plate 0115 / bottom plate 0116), will trigger a leverage amplification effect: see reference [link to relevant documentation] Figure 1 and Figure 2 As shown, the C-type connector 01133 is connected to the top plate 0115 and the bottom plate 0116 of the distributed X-ray tube 0100, that is... Figure 2The two fulcrums are the mounting points of the C-type connector 01133. Due to the large aspect ratio of the distributed X-ray tube 0100, the distance from the mounting point to the anode end constitutes a long lever arm. Limited by the dense component arrangement on the top plate 0115 and bottom plate 0116, the installation space is extremely limited, resulting in a restricted installation span and extremely difficult position adjustment for the C-type connector 01133. In this structure, if one of the mounting points experiences a slight displacement from its intended position due to installation accuracy or machining tolerances, according to the lever principle, this small input error will be amplified many times by the long lever arm, causing a displacement deviation at the anode end located at the end of the lever arm several times greater than the installation error. This results in the anode focal array being severely deviated from the preset optical path center, failing to meet the stringent requirements of static CT systems for focal alignment accuracy. Moreover, due to the narrow space around the installation area, once such a deviation amplified by the lever effect occurs, it is difficult for technicians to effectively compensate for this end position offset by fine-tuning the C-type connector 01133, making the assembly and calibration of the entire machine extremely uncontrollable.

[0063] To address at least one aspect of the above-mentioned problems, embodiments of the present invention provide a distributed X-ray tube 100, a distributed X-ray source assembly, and an imaging system based on a distributed X-ray source tube.

[0064] Combined with reference Figure 4 and Figure 6 As shown, the distributed X-ray tube 100 may include: a tube housing 110, a vacuum chamber 120, a cathode, and an anode 130.

[0065] The tube housing 110 may include a front plate 111, a back plate 112, a top plate 115, a bottom plate 116, and two end plates 113.

[0066] It should be noted that, unless otherwise specified, the spatial relationships such as front, back (or back), left, right, top (or top), and bottom (or bottom) are described in the context of the normal working or normal use of the X-ray tube. For example, the side where the X-ray window is located is called the front side of the X-ray tube, and the side opposite to the side where the X-ray window is located is called the back side or back side of the X-ray tube. Based on the viewing angle of the X-ray tube facing the observer when it is working normally, the left side of the observer corresponds to the left side of the X-ray tube, the right side of the observer corresponds to the right side of the X-ray tube, the upper side of the observer's line of sight corresponds to the upper or top side of the X-ray tube, and the lower side of the observer's line of sight corresponds to the lower or bottom side of the X-ray tube.

[0067] It should also be noted that, for ease of description, this paper constructs a spatial coordinate system based on the first direction, the second direction, and the third direction, for example, as shown below. Figure 4As shown, there are three directions: a first direction F, a second direction E, and a third direction G. Any two of these directions intersect each other, for example, they are perpendicular to each other. For example, the first direction F can be left-right, the second direction E can be front-back, and the third direction G can be up-down.

[0068] It should be understood that the descriptions of spatial relationships such as front, back (or back), left, right, top (or top), bottom (or bottom) and directions such as first direction, second direction and third direction in this document are merely exemplary expressions used to facilitate the description of embodiments of the present invention and should not be construed as limiting the present invention.

[0069] like Figure 4 and Figure 6 As shown, the front plate 111, back plate 112, top plate 115 and bottom plate 116 extend along the first direction F, the back plate 112 and the front plate 111 are arranged opposite each other along the second direction E, the two end plates 113 are arranged opposite each other along the first direction F, and the top plate 115 and the bottom plate 116 are arranged opposite each other along the third direction G.

[0070] The front plate 111, back plate 112, top plate 115, and bottom plate 116 constitute the main structure of the tube housing 110 in the length dimension. The first direction F is the longitudinal axis direction or length extension direction of the distributed X-ray tube 100. The front plate 111 and back plate 112, and the top plate 115 and bottom plate 116, respectively, serve as two opposing main wall plates, extending parallel to this direction and defining the required elongated physical profile of the distributed X-ray tube 100. Two end plates 113 intersect the first direction F, meaning the two end plates 113 are located at opposite ends of the tube housing 110 in the first direction F. The two end plates 113 connect the longitudinally extending ends of the front plate 111 and back plate 112, and the top plate 115 and bottom plate 116, respectively, thereby enclosing the cylindrical structure formed by these longitudinal wall plates into a complete enclosed space. For example, this enclosed space can be a vacuum chamber 120. It should be understood that the vacuum chamber 120 is at least partially surrounded by the tube housing 110.

[0071] For example, in conjunction with reference Figure 4 and Figure 6The front panel 111 is provided with a radiation window for the radiation to be emitted. The top panel 115, bottom panel 116, and back panel 112 are equipped with an ion pump 420, an exhaust pipe 430, an anode cooling circulation system, and multiple anode / cathode high-voltage lead terminals 440. That is, in the distributed X-ray tube 100, in order to maintain the ultra-high vacuum environment within the vacuum chamber 120 and meet the high-power operation requirements, vacuum maintenance and heat dissipation components are required. For example, the ion pump 420 for adsorbing free gases, the exhaust pipe 430 for initial vacuuming, the anode cooling circulation system, and the multiple anode / cathode high-voltage lead terminals 440 need to be centrally arranged on the main wall panels other than the front panel 111. As mentioned above, this high-density component stacking leaves almost no flat space on the main wall panels such as the top panel 115, bottom panel 116, and back panel 112 for installing mechanical mounting structures, making it difficult to implement traditional side-clamp or bracket-type mounting schemes, or causing the aforementioned leverage effect error due to the mounting point being far from the end.

[0072] In embodiments of the present invention, both the cathode and anode 130 are located within a vacuum cavity 120. The cathode can be configured to extract electron beams from multiple locations, and the anode 130 is configured to generate multiple X-ray beams from multiple target points 131, which are spaced apart along a first direction F. Exemplarily, the cathode may include emitters arranged in an array along the first direction F, capable of controllably emitting multiple independent electron beams within the vacuum cavity 120; the anode 130 may include an elongated metal target (e.g., a tungsten target) extending along the first direction F. When the electron beams are accelerated under a high-voltage electric field and bombard specific locations on the anode 130, X-ray source points can be formed; these source points are referred to as "target points." Since the emitters of the cathode are arranged in an array, correspondingly, the multiple target points 131 are spaced apart along the first direction F on the anode 130, thereby forming a linearly arranged target point array. By controlling the operation of different emitters, multiple target points 131 can emit beams in the first direction F without moving the distributed X-ray tube 100, thereby achieving scanning imaging at multiple angles.

[0073] Combined with reference Figure 4 and Figure 6At least one end plate 113 may include an external side surface 1131 located on the side of the end plate 113 away from the vacuum cavity 120. The external side surface 1131 may include an outer end face 1132 and a forward clearance surface 1133. The outer end face 1132 is perpendicular to the first direction F. In the second direction E, the forward clearance surface 1133 is closer to the front plate 111 relative to the outer end face 1132. In the first direction F, the forward clearance surface 1133 is recessed inward relative to the outer end face 1132 towards the vacuum cavity 120. That is, the forward clearance surface 1133 is a space clearance structure deliberately formed by the end plate 113 on the front side (i.e., the side closer to the front plate 111) to avoid interference with adjacent devices. In some exemplary embodiments, the solid material in the area where the forward clearance surface 1133 is located is partially removed, so that the front contour of the end plate 113 is no longer flush with the outer end face 1132, but is recessed towards the vacuum cavity 120.

[0074] It should be noted that, in the first direction F, the forward clearance surface 1133 is recessed inward relative to the outer end face 1132 towards the vacuum cavity 120. This can be understood as: the forward clearance surface 1133 includes a first end or first endpoint connected to the outer end face 1132 (e.g., Figure 6 The upper end or upper endpoint of the forward clearance surface 1133 shown in the figure) and the second end or second endpoint of the connecting front plate 111 (e.g. Figure 6 The lower end or lower endpoint of the forward-facing air-avoiding surface 1133 shown in the figure), in the first direction F, the second end or second endpoint is closer to the vacuum cavity 120 or the anode 130 than the first end or first endpoint.

[0075] Combined with reference Figure 4 , Figure 6 , Figure 8 , Figure 10 and Figure 12 The distributed X-ray source assembly 200 may include at least two distributed X-ray tubes 100. The at least two distributed X-ray tubes 100 may be spliced ​​to form different configurations, such as straight lines, L-shapes, gate shapes, mouth shapes, polygons, multi-segment straight-fitted circular arcs, etc.

[0076] It should be noted that, in this document, some different configurations and different numbers of X-ray tubes included in the distributed X-ray source assembly are described by way of example. However, these are merely illustrative descriptions and are not intended to limit the implementation of the present invention. In the embodiments of the present invention, at least two distributed X-ray tubes 100 can be spliced ​​together to form distributed X-ray source assemblies 200 with different numbers and configurations. That is, the embodiments of the present invention do not impose any particular limitation on the configuration of the distributed X-ray source assembly 200 and the number of distributed X-ray tubes 100 it includes.

[0077] Combined with reference Figure 4 , Figure 6 , Figure 8 , Figure 10 and Figure 12 As shown, an inwardly contracting forward-facing clearance structure is formed on the outer side of the end plate 113 of the distributed X-ray tube 100, allowing adjacent distributed X-ray tubes 100 to complementarily fit together using the space released by the forward-facing clearance structure. This structural design physically removes the solid material that would otherwise prevent adjacent distributed X-ray tubes 100 from approaching, thereby significantly reducing the geometric distance between adjacent target points 131 of the anodes 130 at adjacent edges of two adjacent distributed X-ray tubes 100 without changing the necessary vacuum insulation distance between the anode 130 inside the vacuum chamber 120 and the inner wall of the end plate 113, and while maintaining sufficient solid thickness on the back of the end plate 113 to ensure vacuum safety sealing and provide installation strength. This effectively reduces the loss of imaging viewpoints at the splicing points and eliminates imaging blind spots, thus facilitating the acquisition of more complete, continuous, and low-artifact multi-view or static CT scan images.

[0078] In some exemplary embodiments, such as Figure 8 As shown, the distributed X-ray source assembly 200 may include at least two distributed X-ray tubes 100, which may be arranged sequentially in a straight line along a first direction F, with the end plates 113 of adjacent distributed X-ray tubes 100 abutting each other. Through the forward-facing clearance structure of the end plates 113, the end plates of adjacent distributed X-ray tubes 100 can achieve close "face-to-face" contact. Because the thickness of the end plate 113 itself is reduced, and the distance between the target point closest to the end plate 113 and the end plate 113 is reduced, the distance between the edge target points of adjacent distributed X-ray tubes 100 is reduced. For example, in... Figure 8 In the exemplary embodiment shown, when two distributed X-ray tubes 100 are spliced ​​together to form a linear distributed X-ray source assembly 200, the distance between the rightmost target point of the left distributed X-ray tube 100 and the leftmost target point of the right distributed X-ray tube 100 is small, resulting in a smaller missing angle of the imaging view, which is beneficial to improving imaging quality. (Comparison Reference) Figure 6 , Figure 7 , Figure 8 and Figure 9 In the relevant technology, at least two conventional distributed X-ray tubes 0100 are arranged in a straight line, and the distance between the anode ends 0132 of the anodes 0130 of two adjacent conventional distributed X-ray tubes 0100 is significantly greater than the distance between the anode ends 132 of two adjacent distributed X-ray tubes 100.

[0079] Combined with reference Figure 4 , Figure 6 , Figure 10 and Figure 12 The forward-facing clearance structure design of the end plate 113 creates a forward-facing clearance space, allowing the end plate of one distributed X-ray tube 100 to be embedded into the forward-facing clearance space of the end plate of the other distributed X-ray tube 100 when two distributed X-ray tubes 100 need to be arranged adjacent to each other at a certain angle (such as L-shaped vertical splicing or obtuse-angle arc splicing), or the forward-facing clearance surfaces 1133 of the two distributed X-ray tubes 100 to be tightly fitted face-to-face. In some exemplary embodiments, such as Figure 10 As shown, the forward clearance surface 1133 can be constructed as an inclined plane, in which case two adjacent inclined surfaces can fit tightly together face to face to achieve an L-shaped joint. In some other exemplary embodiments, such as Figure 12 As shown, the forward clearance surface 1133 can be constructed as a smoothly transitioned arc surface or spherical surface, in which case adjacent distributed X-ray tubes 100 can be joined together at a flexible angle like a ball joint.

[0080] In some exemplary embodiments, such as Figure 10 As shown, the distributed X-ray source assembly 200 may include at least two distributed X-ray tubes 100, which may be arranged at a predetermined angle, with at least a portion of the end plates 113 of adjacent distributed X-ray tubes 100 abutting each other. Through the forward-facing clearance structure of the end plates 113, the end plates of adjacent distributed X-ray tubes 100 can achieve a close "corner-to-corner" contact. Because the thickness of the end plates 113 themselves is reduced, and the distance between the target point closest to the end plate 113 and the end plate 113 is reduced, the distance between the edge target points of adjacent distributed X-ray tubes 100 is reduced. For example, in... Figure 10 In the exemplary embodiment shown, when two distributed X-ray tubes 100 are spliced ​​together to form an L-shaped distributed X-ray source assembly 200, the distance between the rightmost target point of the upper distributed X-ray tube 100 and the uppermost target point of the right distributed X-ray tube 100 is small, resulting in a smaller missing angle of the imaging view, which is beneficial to improving the imaging quality.

[0081] In some exemplary embodiments, such as Figure 12As shown, the distributed X-ray source assembly 200 may include at least two distributed X-ray tubes 100, which may be arranged at a predetermined angle, with at least a portion of the end plates 113 of adjacent distributed X-ray tubes 100 abutting. For example, the distributed X-ray source assembly 200 may include three distributed X-ray tubes 100, which may be arranged at a predetermined angle, with at least a portion of the end plates 113 of adjacent distributed X-ray tubes 100 abutting, forming a multi-segment linear-fitted arc-shaped X-ray source assembly. Through the forward-facing clearance structure of the end plates 113, the end plates of adjacent distributed X-ray tubes 100 can achieve close "corner-to-corner" contact. Due to the reduced thickness of the end plates 113 themselves, and the reduced distance between the target point closest to the end plate 113 and the end plate 113, the distance between the edge target points of adjacent distributed X-ray tubes 100 is reduced. For example, in Figure 12 In the exemplary embodiment shown, the distance between the rightmost target point of the upper distributed X-ray tube 100 and the leftmost target point of the upper right distributed X-ray tube 100 is small, resulting in a smaller missing angle of the imaging view; the distance between the rightmost target point of the upper right distributed X-ray tube 100 and the uppermost target point of the right distributed X-ray tube 100 is also small, resulting in a smaller missing angle of the imaging view. In this way, it is beneficial to improve the imaging quality.

[0082] Combined with reference Figure 8 , Figure 10 and Figure 12 An imaging system based on a distributed X-ray source may include a detector 300 and a radiation source. The detector 300 and the radiation source may be positioned opposite each other to form a scanning area 310 between the radiation source and the detector 300. The radiation source may include a distributed X-ray tube 100 or a distributed X-ray source assembly 200. The space enclosed or defined by the detector 300 and the radiation source constitutes the scanning area 310. During scanning imaging, the object to be detected (e.g., a baggage or a part of the human body) may be located in the scanning area 310. The distributed X-ray tube 100, as a basic radiation generating unit, has target points 131 of its anode 130 spaced along a first direction F, which can controllably generate multiple beams of X-rays directed towards the scanning area 310 to acquire scanning data of the object to be detected.

[0083] In some exemplary embodiments, the X-ray source in the imaging system may include a X-ray source assembly formed by spatially stitching together multiple distributed X-ray tubes 100 to expand the scanning field of view or provide multiple projection angles. In this imaging system, the forward-facing clearance of the distributed X-ray tubes 100 can significantly reduce the lack of angle at the stitching points of the distributed X-ray source assembly, which is beneficial for achieving a near-full coverage scan of the object to be detected within the scanning area 310.

[0084] Reference Figure 6 , Figure 16 , Figure 17 , Figure 22 and Figure 25 In some exemplary embodiments, at least one end plate 113 includes an inner surface 1134 located on the side of the end plate 113 near the vacuum cavity 120, and at least a portion of the inner surface 1134 is formed as an inner arc surface convex toward the outer end face 1132. In some specific embodiments, the inner arc surface may be constructed as a curved surface structure that gradually concaves toward the center and extends outward from the periphery of the inner surface 1134. The convexity of the inner arc surface may be manifested as a cylindrical extension based on an axis parallel to the first direction F, or as a hemispherical or ellipsoidal extension centered at a point on a straight line parallel to the first direction F.

[0085] Accordingly, refer to Figure 6 In some exemplary embodiments, the vacuum cavity 120 may include a first cavity 121 and two second cavities 122, the two second cavities 122 being located on both sides of the first cavity 121 along a first direction F, and at least a portion of each of the two second cavities 122 being configured to bulge toward the inner arc surface.

[0086] like Figure 1 and Figure 3 As shown, in the existing X-ray tube with a hexahedral square structure, in order to prevent high voltage breakdown, the inner wall of the flat end plate 0113 needs to maintain a large distance from the anode end, resulting in a longer cavity size of the X-ray tube.

[0087] like Figure 4 , Figure 5 and Figure 6 As shown, in some embodiments of the present invention, the end plate 113 has an outwardly protruding inner arc surface, that is, a receiving space, such as a second cavity 122, is "carved out" inside the solid material of the end plate 113. This allows for a sufficiently large vacuum insulation distance between the anode 130 and the inner side 1134 of the end plate 113, thus meeting the creepage distance and breakdown voltage requirements. Furthermore, this design significantly reduces the solid thickness of a portion of the end plate 113, thereby reducing the ineffective physical volume of the vacuum cavity 120 at its end. It should be further noted that the rear region of the end plate 113, where it is not "carved out," retains its original thickness, allowing for the provision of sufficiently deep mounting threaded holes on the end plate 113. This also reduces the length of the distributed X-ray tube 100 in the first direction F. Furthermore, the thinning of the front region allows adjacent distributed X-ray tubes 100 to be physically closer, compressing the size of the edge dead zone and further reducing the loss of imaging angle.

[0088] Reference Figure 6 In some exemplary embodiments, the anode 130 includes a male end 132, which is located at the end of the anode 130 in a first direction F. At least a portion of the male end 132 is provided with a convex arc surface protruding towards the outer end face 1132. In some specific embodiments, the anode 130 may be an elongated columnar or prismatic structure extending along the first direction F, and the male end 132 is the end of this structure in the first direction F. The convex arc surface may be constructed as a smoothly transitioned hemispherical surface, parabolic surface, or rounded surface, and its protrusion direction is consistent with the first direction F, directly pointing towards the inner arc surface of the end plate 113.

[0089] According to electrostatic field theory, in a vacuum and high-pressure environment, sharp edges can lead to a high concentration of charge, forming an extremely strong local electric field (i.e., the tip effect), which can easily cause arcing or breakdown. In the embodiments of this invention, the anode end 132 is designed as a smoothly transitioned convex arc surface, allowing it to form an approximately concentric mating relationship with the inner arc surface of the end plate 113. Figure 5 As shown, this geometric fit enables a more uniform electric field distribution on the surface of the anode tip 132, resulting in a smooth equipotential surface distribution and eliminating electric field distortion points. Thus, under the same applied voltage, the required theoretical insulation distance is minimized, allowing the inner arc surface of the end plate 113 to be physically closer to the anode tip 132, providing an electrical basis for the compactness of the length dimension of the distributed X-ray tube 100 in the first direction F.

[0090] Combined with reference Figure 3 and Figure 5 In embodiments of the present invention, by making the outer cavity surface 1131 include a forward clearance surface 1133, that is, by removing at least a portion of a corner of the end plate 113, a compact distributed X-ray source can be achieved, which is beneficial for splicing multiple distributed X-ray sources. In this case, the inner cavity surface 1134 of the end plate 113 is changed from a plane to an inner arc surface, and an X-ray tube with an inner arc surface design (see reference) Figure 5 ) and ray tubes with an inner plane design (see reference) Figure 3 The extreme values ​​of the electric field strength are basically the same, which means that the stability of the X-ray tube is not sacrificed while saving the internal space of the cavity. It should be noted that in the embodiments of the present invention, the inner side surface 1134 of the end plate 113 can be designed first by simulation calculation, and then the outer side surface 1131 of the cavity can be designed based on the inner side surface 1134 of the end plate 113 and the required thickness.

[0091] See example 4. Figure 6 , Figure 8 , Figure 10 and Figure 12The anode 130 may include two anode terminals 132, which are located on both sides of the anode 130 in the first direction F.

[0092] In some exemplary embodiments, such as Figure 5 , Figure 8 , Figure 10 and Figure 12 As shown, the two male end caps 132 can be located in the two second cavities 122 respectively.

[0093] In some specific embodiments, the first cavity 121 constitutes the main body of the vacuum cavity 120, used to accommodate the main body of the cathode array and the anode 130; the second cavity 122 is the relatively smaller portion located at both ends. The space of the second cavity 122 is defined by the recess of the inner arc surface of the end plate 113. The protrusion of the second cavity 122 can be a hemispherical protrusion as a whole, or it can protrude only in a local area corresponding to the axis of the anode 130. In the embodiments of the present invention, the two anode ends 132 are respectively located in the two second cavities 122, which means that the anode ends 132 are actually located within the thickness range of the end plate 113. Compared with the conventional design where the anode ends 132 are located in the first cavity 121, in the embodiments of the present invention, the space formed by the recess of the end plate 113 (i.e., the second cavity 122) is fully utilized to accommodate the high-voltage components, so that the effective length of the vacuum cavity 120 in the first direction F (i.e., the length including the focal array) can be closer to the total physical length of the vacuum cavity 120. In this way, the problem of excessively long "dead zones" caused by end insulation and sealing structures in traditional structures is solved, allowing the effective radiation generation area to extend to the outermost edge of the tube shell.

[0094] Reference Figure 8 , Figure 10 and Figure 12 In some exemplary embodiments, the plurality of target points 131 may include two edge target points 1311 respectively located near the two end plates 113 in the first direction F, and the two edge target points 1311 are respectively located in the two second cavities 122. In some specific embodiments, the edge target points 1311 refer to the two X-ray source points located at both ends of the focal array of the anode 130. These two target points 131 are not located inside the first cavity 121, but are disposed inside the second cavity 122, and these two target points 131 are adjacent to the convex arc surface region of the anode end head 132.

[0095] In some exemplary embodiments, such as Figure 6 As shown, both male end caps 132 can be located in the first cavity 121, that is, the two male end caps 132 can be located outside the two second cavities 122.

[0096] Reference Figure 14 , Figure 16 , Figure 20 , Figure 22 , Figure 23 and Figure 25 In some exemplary embodiments, at least a portion of the inner side surface 1134 may include a spherical surface, and the center of the sphere of the inner side surface 1134 may be located in the region where the male end head 132 is located.

[0097] For example, the inner surface 1134 is a spherical concave cavity constructed following the curvature characteristics of a geometric sphere. The spatial position of the center of the sphere of the inner surface 1134 is located within the spatial volume occupied by the anode end 132, or adjacent to the front end of the anode end 132, that is, the inner surface 1134 forms a uniform envelope structure around the anode end 132. The fact that the center of the sphere of the inner surface 1134 falls into the region where the anode end 132 is located minimizes the rate of change of distance from the inner surface 1134 to the surface of the anode 130, that is, it utilizes the spherical symmetry to optimize the electric field distribution. In this way, the vacuum insulating medium in all directions can be efficiently utilized within the limited end space, avoiding breakdown caused by excessively close local distances or volume waste caused by excessively large local distances, and reserving a large internal safety margin for subsequent "slimming down" of the external structure.

[0098] Reference Figure 5 and Figure 6 In some exemplary embodiments, the anode end 132 is a spherical end, with the center of the sphere coinciding with the center of the adjacent cavity inner side 1134. Exemplarily, the concentric anode end 132 and cavity inner side 1134 constitute a "concentric spherical shell" model. Studies have shown that in this model, the electric field lines between the two electrodes can diverge uniformly radially, and the equipotential surfaces are a series of approximately concentric spherical surfaces. This means that the vacuum insulation gap between the surface of the anode 130 and the cavity inner side 1134 is a constant value equal in all directions. This constant value can be the theoretical minimum distance to meet the withstand voltage requirements. Compared to non-concentric or non-spherical structures, this eliminates any possible electric field concentration points, allowing the cavity inner side 1134 of the end plate 113 to be pushed to a limit position close to the surface of the anode 130 during the design phase, thereby fundamentally compressing the physical dimensions of the distributed X-ray tube 100 in the first direction F.

[0099] Reference Figure 16 , Figure 17 , Figure 22 and Figure 25 In some exemplary embodiments, the minimum distance between the inner side surface 1134 and the outer end surface 1132 in the first direction F is greater than or equal to 1 mm.

[0100] Research and development have revealed that, in conjunction with reference Figure 8 , Figure 10 and Figure 12 The minimum distance between the inner side surface 1134 and the outer end face 1132 in the first direction F can determine the minimum wall thickness (i.e., minimum axial wall thickness) of the end plate 113 in the first direction F. The minimum wall thickness of the end plate 113 in the first direction F can determine the physical limit of the length of the blind zone, that is, the size of the missing angle can be determined. In the embodiments of the present invention, the structure bearing the mechanical connection load is moved to the side where the back plate 112 is located, so that the front end face of the end plate 113 no longer bears the main torque, but only needs to bear atmospheric pressure. Moreover, due to the use of the arc or spherical structure, the compressive strength of the inner side surface 1134 is better than that of the plane. Through these structural designs, the wall thickness between the inner side surface 1134 and the outer end face 1132 can be reduced, for example, reduced to 1 mm, so that the anode tip and the edge target point can be close to the physical edge of the tube shell. Thus, in the scenario where multiple distributed X-ray tubes are spliced ​​to form a X-ray source assembly, the interval between the edge target points in two adjacent X-ray tubes can be smaller, that is, the missing angle can be reduced.

[0101] Reference Figure 16 , Figure 17 , Figure 22 and Figure 25 In some exemplary embodiments, the forward clearance surface 1133 is connected between the outer end face 1132 and the front plate 111, and the minimum distance between the forward clearance surface 1133 and the inner side surface 1134 is greater than or equal to 1 mm.

[0102] Research and development have revealed that, in conjunction with reference Figure 8 , Figure 10 and Figure 12 The minimum distance between the forward clearance surface 1133 and the inner side surface 1134 determines the minimum wall thickness of the end plate 113 in the front corner region. Whether the inward reduction is due to a chamfered angle, an arc, or a spherical surface, the depth of the inward reduction is limited by the boundary of the vacuum cavity 120. By controlling the normal distance between the forward clearance surface 1133 and the inner side surface 1134 to be greater than or equal to 1 mm, a thin-walled shell structure with uniform thickness can be formed. This design, combined with the aforementioned minimum axial wall thickness, allows for thin-walled construction of both the front and sides of the end plate 113. The rear of the end plate 113 retains a thick structure coplanar with the back plate 112 for rigid support and threaded hole connections, while the thin shell at the front serves only as a vacuum sealing structure. This differentiated wall thickness distribution design allows the anodes of two adjacent distributed X-ray tubes 100 to be separated by only two thin metal shells when multiple distributed X-ray tubes are spliced ​​together at a preset angle to form a radiation source assembly. This results in a smaller distance between the edge target points in the two adjacent X-ray tubes, thus reducing the lack of angle.

[0103] Reference Figure 4 , Figure 15 , Figure 16 , Figure 17 , Figure 22 and Figure 25 In some exemplary embodiments, the forward clearance surface 1133 extends along a first plane, which is inclined relative to a first direction F. In some specific embodiments, the first plane is a virtual reference plane that obliquely cuts into the front plate 111 from the outer end face 1132 of the end plate 113. It should be noted that the actual physical shape of the forward clearance surface 1133 is not limited to a plane. The forward clearance surface 1133 can be a straight inclined plane coinciding with the first plane, a circular arc cylindrical surface tangent to the first plane, or a concentric sphere with the aforementioned center as the origin. It should be noted that regardless of the specific shape, it follows the geometric law of inward contraction along the first plane.

[0104] In some exemplary embodiments, the angle between the first plane and the first direction F can be 30° to 75°, for example, the angle can be 30°, 35°, 45°, 55°, 60°, 75°, etc. Research has found that the selection of this angle range is based on an engineering balance between splicing efficiency and structural reliability. If the angle is greater than 75°, less material is removed, and although the wall thickness is easily guaranteed, the front edge cannot be effectively removed, resulting in significant physical interference during splicing. If the angle is less than 30°, a larger portion is removed, leading to an excessively short transition area between the forward clearance surface 1133 and the front plate 111, and the compression of the internal space is not significant. An angle within the range of 30° to 75° ensures sufficient welding sealing area while maximizing the removal of excess material obstructing splicing, achieving a better compact splicing effect.

[0105] Reference Figures 20 to 22 In some exemplary embodiments, the forward clearance surface 1133 can be an arc-shaped surface. Exemplarily, the arc-shaped surface is constructed as a curved structure that smoothly transitions from the outer end face 1132 to the surface of the front plate 111, with a cross-section exhibiting an arc segment. Studies have found that the forward clearance surface 1133 with an arc shape has better compressive strength. Since the vacuum cavity 120 is under high vacuum and subjected to atmospheric pressure externally, sharp edges or the transition points between straight surfaces and planes are prone to stress concentration. The arc-shaped surface design conforms to the stress distribution flow lines of the shell, enhancing the structural rigidity of thin-walled areas.

[0106] Furthermore, referring to Figure 12 In the scenario of splicing multiple tubes to fit an arc, the included angle between adjacent distributed X-ray tubes 100 may be slightly adjusted as the fitting radius changes. The forward clearance surface 1133 with an arc shape provides a wider tangential fitting range than a plane, so that adjacent distributed X-ray tubes 100 can maintain a good streamlined fit at different angles, reducing dead angle gaps.

[0107] In some exemplary embodiments, the arc axis of the forward clearance surface 1133 passes through the center of the sphere of the inner cavity side surface 1134; that is, the arc-shaped surface of the forward clearance surface 1133 can be constructed around the center of the sphere of the inner cavity side surface 1134. In this way, the forward clearance surface 1133 and the inner cavity side surface 1134 form an approximately "coaxial cylindrical shell" relationship, ensuring that the wall thickness of the shell is uniform in the radial direction around the center of the sphere, and achieving a good envelopment of the internal space by the outer contour while ensuring the insulation safety distance.

[0108] Reference Figures 23 to 25 In some exemplary embodiments, the forward clearance surface 1133 can be a spherical surface centered at a first origin. For example, the first origin can coincide with the center of the adjacent inner cavity surface 1134. That is, the front part of the end plate 113 forms a spherical shell portion with uniform wall thickness. In this spherical shell portion, the interior is a spherical cavity accommodating the male end tip, and the exterior is a concentric spherical forward clearance surface 1133, separated by a metal wall of uniform thickness. In this way, all unnecessary angular material is removed in terms of physical volume, achieving miniaturization of the front part of the end plate 113. In terms of splicing freedom, the spherical surface allows adjacent distributed X-ray tubes 100 to fit tightly at any angle like a "ball-and-socket joint," which is particularly suitable for the construction of static CT arrays with irregular geometries. In addition, the concentric spherical shell structure has good stability when subjected to uniform external atmospheric pressure and can maintain long-term vacuum sealing reliability.

[0109] Reference Figure 4 , Figure 6 , Figures 14 to 16 , Figures 20 to 21 , Figures 23 to 24 In some exemplary embodiments, the external cavity side 1131 may further include a rear side 1135 located near the back plate, and the rear side 1135 may be coplanar with the back plate 112. The distributed X-ray tube 100 may also include a mounting connection portion 140, which may be located on the rear side 1135. In some specific embodiments, the rear side 1135 may be an area on the back of the end plate 113 that is not designed with clearance. The rear surface of the end plate 113 does not protrude from the back contour of the tube housing, maintaining the overall flatness of the X-ray tube.

[0110] Alternatively, in some other exemplary embodiments, the rear side 1135 may not be coplanar with the back plate 112. For example, the rear side 1135 may form an inclined surface with the back plate 112, or the rear side 1135 may be parallel to the back plate 112.

[0111] For example, the mounting connection 140 may include a threaded hole, which can be directly machined into the rear side surface 1135, which has a relatively large thickness. In an embodiment of the invention, the front portion of the end plate 113 is thinned to facilitate splicing, while the rear portion of the end plate 113 serves as the mechanical connection. By positioning the mounting connection 140 coplanar with the back plate, the corner solid material at the junction of the end plate 113 and the back plate 112 is utilized. This not only provides a large wall thickness to ensure the thread engagement depth but also does not extend beyond the outer end face 1132 of the end plate 113 in the first direction F, thereby providing a robust mechanical connection interface without sacrificing compactness.

[0112] Combined with reference Figure 4 , Figure 6 , Figures 14 to 16 , Figures 18 to 19 , Figures 20 to 21 , Figures 23 to 24 In some exemplary embodiments, the mounting connection portion 140 may include at least two mounting connection positions 141, which are spaced apart along a third direction G on the rear side surface 1135. For example, the at least two mounting connection positions 141 are respectively located near the corner areas of the top plate 115 and the bottom plate 116. In embodiments of the present invention, the mounting connection portion 140 provided on the rear side surface 1135 of the end plate 113 includes at least two independent connection positions, and these two connection positions are spaced apart along a third direction G. In this way, the upper and lower corners of the end plate 113 welded or connected to the top plate 115 and the bottom plate 116 can be used as connection anchor points. It should be understood that these two corners are areas with high rigidity in the ray tube. Through the spaced arrangement, a torsional mechanical structure can be formed, effectively locking the degree of freedom of the end plate 113. Furthermore, the positions of the two mounting connection points in the first direction F are basically consistent with the position of the anode end head. In this way, the adjustment action of the external frame can be accurately transmitted to the target array of the anode 130, which can eliminate the aforementioned lever amplification error and improve the accuracy and stability of the distributed X-ray tube when aligning the target.

[0113] Combined with reference Figure 4 , Figure 6 , Figures 14 to 15 , Figures 17 to 19 , Figures 20 to 22 , Figures 23 to 25In some exemplary embodiments, at least one weight-reducing groove 1136 may be formed on the side of the outer cavity surface 1131 of the end plate 113 near the back plate 112, and the at least one weight-reducing groove 1136 is located between two adjacent mounting connection positions 141. Exemplarily, between the two mounting connection positions 141 on the rear side surface 1135 of the end plate 113 (i.e., the middle region of the rear of the end plate 113), a portion of the material is removed by milling or casting to form an inwardly recessed groove or cavity. It should be understood that the depth of the weight-reducing groove 1136 can be controlled within a range that does not affect the internal vacuum seal wall thickness. Studies have found that the stress around the mounting connection positions 141 is mainly concentrated in the corner areas, while the material in the middle region between the mounting connection positions 141 mainly serves a connecting function, and stress concentration does not occur. Therefore, without compromising the overall rigidity of the end plate 113, removing material from the intermediate area between the mounting connection positions 141 can effectively reduce the weight of a single distributed X-ray tube 100, which helps to quickly establish thermal equilibrium when the X-ray tube is operating at high power, thus achieving a dual improvement in lightweighting and structural efficiency.

[0114] Return to reference Figure 8 , Figure 10 and Figure 12 In the distributed X-ray source assembly 200 provided in the embodiments of the present invention, by providing at least two distributed X-ray tubes 100, the forward clearance surface 1133 allows adjacent distributed X-ray tubes 100 to be angularly fitted with a small gap. In an exemplary embodiment, referring to reference... Figure 10 and Figure 12 As shown, at least two adjacent distributed X-ray tubes 100 are arranged at a predetermined angle, and the forward clearance surfaces 1133 of the end plates 113 of at least two adjacent distributed X-ray tubes 100 are in contact with each other. Exemplarily, the forward clearance surface 1133 may be located in the front corner region of the end plate 113, i.e., in the transition region connecting the front plate 111 and the outer end face 1132. In related technologies, when two conventional distributed X-ray tubes 0100 approach each other at a predetermined angle, referring to... Figure 11 , Figure 13 The traditional right-angle endplate 0113 structure causes geometric interference at the front corner region, forcing a large safety gap to be maintained between the two X-ray tubes. In the embodiment of the present invention, when the two distributed X-ray tubes 100 approach each other at a preset angle, in conjunction with reference to... Figure 10 , Figure 12Because of the inwardly contracting forward clearance surface 1133, the interference region is removed. The ends of two adjacent distributed X-ray tubes 100 can be fitted together in a manner where "forward clearance surface 1133" is paired with "forward clearance surface 1133" or "forward clearance surface 1133" is paired with "sidewall". This fitting method allows the edge target points inside the two distributed X-ray tubes 100 to be spatially close to each other, thereby forming a nearly continuous X-ray coverage field at the splicing point, which greatly reduces the loss of imaging perspective caused by mechanical obstruction.

[0115] Continue to refer to Figure 10 In some exemplary embodiments, the target points 131 of at least two adjacent distributed X-ray tubes 100 are arranged perpendicularly to each other, and the forward clearance surfaces 1133 of the end plates 113 of at least two adjacent distributed X-ray tubes 100 are adjacent to each other and fit together. Exemplarily, the perpendicular arrangement of the target points 131 of at least two adjacent distributed X-ray tubes 100 can be used to construct an L-shaped, gate-shaped, or mouth-shaped X-ray source assembly for a rectangular channel security inspection machine. In this X-ray source assembly, the angle between the first direction F of the two distributed X-ray tubes 100 is 90 degrees. To achieve an approximately seamless fit, the forward clearance surface 1133 can be constructed as a planar slope, and the angle between the first plane containing the planar slope and the first direction F is 45°. In this case, the 45° slopes of the two adjacent distributed X-ray tubes 100 are exactly parallel to each other and closely fitted, forming a diagonal seam. Since the anode 130 has extended into the second cavity 122 of the end plate 113, this 45° fit allows the target point spacing at the vertical corner to reach a small value that meets the physical limit, compared with the reference. Figure 6 , Figure 7 , Figure 10 and Figure 11 In related technologies, the anodes 0130 of two conventional distributed X-ray tubes 0100 extend perpendicularly to each other, and the distance between the anode ends 0132 of the two conventional distributed X-ray tubes 0100 is significantly greater than the distance between the anode ends 132 of two adjacent distributed X-ray tubes 100. The distributed X-ray source assembly provided in this embodiment of the invention can effectively eliminate the imaging blind zone at the corner of the rectangular channel.

[0116] Continue to refer to Figure 12In some exemplary embodiments, the distributed X-ray source assembly 200 may include at least three distributed X-ray tubes 100 arranged sequentially. The envelope formed by the arrangement directions of the target points 131 of the at least three distributed X-ray tubes 100 is arc-shaped, and the forward clearance surfaces 1133 of the endplates 113 of any two adjacent distributed X-ray tubes 100 are fitted together. Exemplarily, this arrangement can be used to fit the annular scanning architecture of static CT. In this X-ray source assembly, the included angle between adjacent distributed X-ray tubes 100 can be an obtuse angle. To accommodate this variable obtuse angle fitting, the forward clearance surface 1133 can be constructed as an arc-shaped surface or a sphere, or as a sloping plane with a large inclination angle. When an arc-shaped surface or a sphere is used, the end contact of adjacent distributed X-ray tubes 100 is similar to the tangential contact of a ball joint or a cylindrical hinge, which allows the distributed X-ray tubes 100 to freely adjust the fitting angle within a certain angle range, thereby maintaining close contact of the endplates. This structure ensures that the target arrays of adjacent distributed X-ray tubes 100 remain connected end-to-end when fitting circles of different diameters. (Comparison reference) Figure 6 , Figure 7 , Figure 12 and Figure 13 In related technologies, the envelope formed by the extension directions of the anodes 0130 of at least three conventional distributed X-ray tubes 0100 is arc-shaped, and the distance between the anode ends 0132 of two adjacent conventional distributed X-ray tubes 0100 is significantly greater than the distance between the anode ends 132 of two adjacent distributed X-ray tubes 100. The distributed X-ray source assembly provided in this embodiment of the invention can effectively eliminate the imaging blind zone at the corner of the rectangular channel, thereby significantly reducing annular artifacts.

[0117] In some exemplary embodiments, at the splicing point of at least two adjacent distributed X-ray tubes 100, the distance between the edge target points 1311 of two adjacent anodes 130 can be less than the maximum thickness of the end plate 113 of each distributed X-ray tube 100 in the first direction F. It should be noted that the maximum thickness of the end plate 113 of each distributed X-ray tube 100 in the first direction F can represent the physical thickness reserved on the back side of the end plate 113 (near the back plate 112) for providing the mounting connection portion 140; the distance between the edge target points 1311 of two adjacent anodes 130 can represent the straight-line distance between the edge target point 1311 at the end of the previous distributed X-ray tube 100 and the edge target point 1311 at the front of the next distributed X-ray tube 100. In embodiments of the present invention, since the end plate adopts a design that is thinner at the front and thicker at the back, the distance at the splicing point can be mainly limited by the wall thickness of the forward clearance surface 1133 at the front of the end plate. In other words, while ensuring high-strength installation, the front splicing spacing (e.g., the spacing between edge target points 1311) can be smaller than the rear wall thickness of the end plate, which is conducive to achieving a balance between connection strength and splicing gap.

[0118] Optionally, in some other exemplary embodiments, at the splice of at least two adjacent distributed X-ray tubes 100, the spacing between the edge target points 1311 of two adjacent anodes 130 may be greater than or substantially equal to the maximum thickness of the end plate 113 of each distributed X-ray tube 100 in the first direction F.

[0119] Combined with reference Figure 6 and Figure 8 In the distributed X-ray source assembly 200, at least two distributed X-ray tubes 100 can be arranged sequentially along a first direction F, with the end plates 113 of adjacent distributed X-ray tubes 100 connected and their forward clearance surfaces 1133 facing each other. In this distributed X-ray source assembly 200, the outer end faces 1132 of the end plates 113 of adjacent distributed X-ray tubes 100 abut against each other. Since each distributed X-ray tube 100 is provided with a first cavity 121 and a second cavity 122 protruding from the end, as well as a corresponding external forward clearance surface 1133, the edge target point 1311 of the anode 130 has penetrated into the thickness space of the end plate 113 (i.e., located in the second cavity 122). (See reference for comparison.) Figure 7 and Figure 9 In an embodiment of the present invention, the distance between the edge target points 1311 of two adjacent distributed X-ray tubes 100 in the first direction F is significantly shortened. The wall thickness reduction design of the forward clearance surface 1133 allows the radiation coverage areas of the two adjacent distributed X-ray tubes 100 to be brought as close as possible, thereby reducing the missing angle.

[0120] Those skilled in the art will understand that the features described in the various embodiments of the present invention can be combined and / or combined in various ways, even if such combinations or combinations are not explicitly described in the present invention. In particular, the features described in the various embodiments of the present invention can be combined and / or combined in various ways without departing from the spirit and teachings of the present invention. All such combinations and / or combinations fall within the scope of the present invention.

Claims

1. A distributed X-ray tube, characterized in that, include: The tube housing includes a front plate, a back plate, and two end plates. The front plate and the back plate extend along a first direction, and the two end plates intersect the first direction. The front plate is provided with a ray window for ray emission. The back plate is disposed opposite to the front plate along a second direction, and the two end plates are disposed opposite to each other along the first direction. The first direction and the second direction intersect. A vacuum chamber, which is at least partially surrounded by the tube housing; as well as An anode, located within the vacuum cavity, comprises a plurality of target points configured to generate multiple beams of X-rays from the target points, the target points being spaced apart along the first direction. Wherein, at least one of the end plates includes an outer side surface located on the side of the end plate away from the vacuum cavity, the outer side surface including an outer end face and a forward clearance surface, in the second direction, the forward clearance surface is closer to the front plate relative to the outer end face; in the first direction, the forward clearance surface is recessed inward relative to the outer end face toward the vacuum cavity.

2. The distributed X-ray tube according to claim 1, characterized in that, At least one of the end plates includes an inner side surface located on the side of the end plate near the vacuum cavity, and at least a portion of the inner side surface is formed as an inner arc surface convex toward the outer end face.

3. The distributed X-ray tube according to claim 2, characterized in that, The anode includes a male end tip, which is located at the end of the anode in the first direction, and at least a portion of the male end tip is provided with a convex arc surface protruding toward the outer end face.

4. The distributed X-ray tube according to claim 3, characterized in that, The vacuum cavity includes a first cavity and two second cavities, the two second cavities being located on either side of the first cavity along the first direction, and at least a portion of each of the two second cavities being configured to bulge toward the inner arc surface; and The anode includes two anode ends, which are located on opposite sides of the anode in the first direction and are located in the two second cavities.

5. The distributed X-ray tube according to claim 4, characterized in that, The plurality of target points include two edge target points that are respectively close to the two end plates in the first direction, and the two edge target points are respectively located in the two second cavities.

6. The distributed X-ray tube according to claim 4 or 5, characterized in that, At least a portion of the inner side surface of the cavity includes a spherical surface, and the center of the sphere of the inner side surface of the cavity is located in the region where the male end tip is located.

7. The distributed X-ray tube according to claim 6, characterized in that, The male end is a spherical end, and the center of the male end coincides with the center of the adjacent inner side of the cavity.

8. The distributed X-ray tube according to any one of claims 2-5 and 7, characterized in that, The minimum distance between the inner side of the cavity and the outer end face in the first direction is greater than or equal to 1 mm.

9. The distributed X-ray tube according to claim 8, characterized in that, The forward clearance surface is connected between the outer end face and the front plate, and the minimum distance between the forward clearance surface and the inner side of the cavity is greater than or equal to 1 mm.

10. The distributed X-ray tube according to any one of claims 1-5, 7 and 9, characterized in that, The forward clearance surface extends along a first plane, which is inclined relative to the first direction.

11. The distributed X-ray tube according to claim 10, characterized in that, The angle between the first plane and the first direction is 30°~75°.

12. The distributed X-ray tube according to claim 6, characterized in that, The forward clearance surface is an arc-shaped surface.

13. The distributed X-ray tube according to claim 12, characterized in that, The arc axis of the forward-facing clearance surface passes through the geometric center of the inner side of the cavity.

14. The distributed X-ray tube according to claim 6, characterized in that, The forward clearance surface is a spherical surface with a first origin as its center, and the first origin coincides with the center of the adjacent inner surface of the cavity.

15. The distributed X-ray tube according to any one of claims 1-5, 7, 9 and 11-14, characterized in that, The outer side of the cavity also includes a rear side located near the back plate, the rear side being coplanar with the back plate.

16. The distributed X-ray tube according to claim 15, characterized in that, The distributed X-ray tube further includes a mounting connection part located on the rear side. The mounting connection part includes at least two mounting connection positions, which are arranged at intervals along a third direction on the rear side. The third direction is perpendicular to the second direction and the first direction, respectively.

17. The distributed X-ray tube according to claim 16, characterized in that, At least one of the end plates further includes a weight-reducing groove, which is formed on the outer side of the cavity near the back plate, and the weight-reducing groove is located between two adjacent mounting connection positions.

18. A distributed X-ray source assembly, characterized in that, It includes at least two distributed X-ray tubes as described in any one of claims 1 to 17.

19. The distributed X-ray source assembly according to claim 18, characterized in that, At least two adjacent distributed X-ray tubes are arranged at a predetermined angle, and the forward clearance surfaces of the end plates of at least two adjacent distributed X-ray tubes cooperate with each other.

20. The distributed X-ray source assembly according to claim 19, characterized in that, The target points of at least two adjacent distributed X-ray tubes are arranged perpendicularly to each other.

21. The distributed X-ray source assembly according to claim 19, characterized in that, The distributed X-ray source assembly includes at least three distributed X-ray tubes arranged sequentially. The envelope formed by the arrangement directions of the target points of the at least three distributed X-ray tubes is arc-shaped, and the forward clearance surfaces of the end plates of any two adjacent distributed X-ray tubes cooperate with each other.

22. The distributed X-ray source assembly according to any one of claims 18 to 21, characterized in that, At the junction of at least two adjacent distributed X-ray tubes, the distance between adjacent target points of two adjacent anodes is less than the maximum thickness of the endplates of each distributed X-ray tube in the first direction.

23. The distributed X-ray source assembly according to claim 18, characterized in that, At least two of the distributed X-ray tubes are arranged in a straight line along a first direction, with the end plates of two adjacent distributed X-ray tubes connected together and their forward-facing clearance surfaces facing each other.

24. An imaging system based on a distributed X-ray source, characterized in that, include: X-ray source, said X-ray source comprising a distributed X-ray tube as described in any one of claims 1 to 17 or a distributed X-ray source assembly as described in any one of claims 18 to 23; and A detector is disposed opposite to the radiation source to form a scanning area between the radiation source and the detector.

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