Integrated computed tomography rotating base with integrated drive system

Abstract

A rotating component (50) for a gantry (12) of a computed tomography (CT) imaging system (10) includes a one-piece structure (56) configured to be coupled to an imaging component. The one-piece structure (56) includes a drive device (92) integrated on the one-piece structure (56) configured to drive the one-piece structure (56) and the imaging component in rotation in response to a driving force.

Description

Background Art

[0001] The subject matter disclosed herein relates to imaging systems, and more particularly, to an integrated computed tomography (CT) rotating base with an integrated drive system.

[0002] Non-invasive imaging techniques allow images of a patient's internal structures or features to be obtained without performing an invasive procedure on the patient. Specifically, such non-invasive imaging techniques rely on various physical principles (such as differential transmission of X-rays through a target volume or reflection of sound waves) to acquire data and construct an image or otherwise represent the observed internal features of a patient.

[0003] For example, in computed tomography (CT) and other X-ray based imaging techniques, X-ray radiation passes across a subject of interest (such as a human patient) and a portion of the radiation impacts a detector that collects image data. In digital X-ray systems, photodetectors generate signals representing the amount or intensity of radiation that strikes discrete pixel regions of the detector surface. The signals can then be processed to generate an image that can be displayed for viewing. In a CT imaging system, a detector array comprising a series of detector elements generates similar signals through various locations as the gantry moves around the patient.

[0004] The gantry of a CT imaging system includes a rotating portion and a fixed portion. Specifically, in a CT imaging system, the rotating portion of the gantry is traditionally used to rotate an X-ray source (e.g., an X-ray tube) and a detector component around an imaging volume, wherein a patient is positioned in the imaging volume during scanning. The X-ray tube, collimator, and detector form key image chain components of a CT imaging system. These subsystems or components, which are mechanically mounted on the CT gantry base (i.e., the rotating portion), are positioned in the X-ray beam path for forming an image. The CT gantry base includes bearings that are individually coupled to a large and heavy disc-shaped gear pulley system driven by a motor that rotates the CT gantry base (and the image chain components). All of these components require a great deal of time and effort to be individually coupled via a large number of bolted assemblies and subassemblies. Summary of the invention

[0005] Certain embodiments commensurate with the scope of the originally claimed subject matter are summarized below. These embodiments are not intended to limit the scope of the claimed subject matter, but rather, these embodiments are intended only to provide a brief overview of possible forms of the subject matter. In fact, the subject matter may include a variety of forms that may be similar to or different from the embodiments described below.

[0006] In one embodiment, a rotating component of a gantry for a computed tomography (CT) imaging system is provided. The rotating component includes a single-piece structure configured to be coupled to an imaging component. The single-piece structure includes a drive device integrated on the single-piece structure and configured to drive the single-piece structure and the imaging component to rotate in response to a driving force.

[0007] In another embodiment, a computer tomography (CT) imaging system is provided. The CT imaging system includes a frame, the frame including a fixed component and a rotating component, the rotating component being coupled to the fixed component via a bearing. The rotating component includes a structure configured to be coupled to the imaging component. The structure includes a first annular structure and a second annular structure. The structure also includes a plurality of cross bars, which are arranged between the first annular structure and the second annular structure and are coupled to both the first annular structure and the second annular structure. The plurality of cross bars are spaced apart relative to each other in a circumferential direction relative to the axis of rotation of the structure. The first annular structure includes a plurality of mounting holes, the plurality of mounting holes being configured to enable the structure to be directly coupled to the bearing without the need to align the structure with the bearing.

[0008] In another embodiment, a rotating component of a rack for a computed tomography (CT) imaging system is provided. The rotating component includes a single-piece structure, which is configured to be coupled to the imaging component and rotate around an axis. The single-piece structure also includes a first annular structure and a second annular structure. The single-piece structure also includes a plurality of crossbars, which are arranged between the first annular structure and the second annular structure and are coupled to both the first annular structure and the second annular structure. The plurality of crossbars are spaced apart relative to each other in a circumferential direction relative to the axis. The single-piece structure also includes a housing, which is integrated on the second annular structure and is configured to install a collimator in the housing, an X-ray source is installed on a side of the housing opposite to the position where the collimator is configured to be installed, and both the X-ray source and the collimator can be coupled to and disengaged from the housing in a mutually exclusive manner. BRIEF DESCRIPTION OF THE DRAWINGS

[0009] These and other features, aspects, and advantages of the subject matter disclosed herein will be better understood when the following detailed description is read with reference to the accompanying drawings, in which like characters refer to like parts throughout the several views, and in which:

[0010] Figure 1 is a combined pictorial view and block diagram of a computed tomography (CT) imaging system as discussed herein;

[0011] Figure 2 is a perspective view of a CT rotating base according to aspects of the present disclosure;

[0012] Figure 3According to various aspects of the present disclosure Figure 2 The front view of the CT rotating base in;

[0013] Figure 4 According to various aspects of the present disclosure Figure 2 Rear view of the CT rotating base in FIG.

[0014] Figure 5 According to various aspects of the present disclosure Figure 2 Side view of the CT rotating base in;

[0015] Figure 6 According to various aspects of the present disclosure Figure 2 Side view of the CT rotating base in Figure 5 lateral sides in the middle);

[0016] Figure 7 According to various aspects of the present disclosure Figure 2 A bottom view of the housing of the CT rotating base;

[0017] Figure 8 According to various aspects of the present disclosure Figure 7 A perspective view of the housing in FIG.

[0018] Fig. 9 According to various aspects of the present disclosure Figure 2 A front view of the extension of the CT rotating base;

[0019] Fig.10 According to various aspects of the present disclosure Figure 2 A perspective view of the drive device of the CT rotating base;

[0020] Fig.11 According to various aspects of the present disclosure Figure 2 A perspective view of a CT rotating base coupled to various components;

[0021] Fig.12 In accordance with various aspects of the present disclosure, Figure 2 A stress diagram performed on a CT rotating base and an enlarged portion of the stress diagram;

[0022] Fig.13 In accordance with various aspects of the present disclosure, Figure 2 Deflection diagram of the deformation performed on the CT rotating base in FIG.

[0023] Fig.14 is a side view of a CT rotating base according to aspects of the present disclosure. DETAILED DESCRIPTION

[0024] One or more specific embodiments will be described below. In order to provide a concise description of these embodiments, not all features of an actual implementation are described in the specification. It should be understood that in the development of any such actual implementation, as in any engineering or design project, many implementation-specific decisions must be made to achieve the developer's specific goals, such as complying with system-related and business-related constraints that may vary from implementation to implementation. In addition, it should be understood that such development efforts may be complex and time-consuming, but are still routine tasks for design, fabrication, and manufacturing for ordinary technicians who benefit from this disclosure.

[0025] When introducing elements of various embodiments of the present subject matter, the articles "a," "an," "the," and "said" are intended to indicate that there are one or more elements. The terms "comprising," "including," and "having" are intended to be inclusive, and mean that there may be additional elements in addition to the listed elements. Furthermore, any numerical examples in the following discussion are intended to be non-limiting, and thus the additional numerical values, ranges, and percentages are within the scope of the disclosed embodiments.

[0026] Although various aspects of the following discussion are provided in the context of medical imaging, it should be understood that the technology disclosed in the present invention is not limited to such medical contexts. In fact, the examples and explanations are provided in such medical contexts only to facilitate explanation by providing examples of realistic specific implementations and applications. However, the technology disclosed in the present invention can also be used in other contexts, such as non-destructive inspection of manufactured parts or goods (i.e., quality control or quality review application scenarios) and / or image reconstruction of non-invasive inspection of packages, boxes, suitcases, etc. (i.e., security inspection or screening application scenarios). In general, the technology disclosed in the present invention can be used in any imaging or screening context or image processing or photography field, in which a group or class of collected data undergoes a reconstruction process to generate an image or volume.

[0027] The present disclosure provides an embodiment of an integrated computed tomography CT rotating base (e.g., a rotating drum) with a drive device and a mounting interface for image chain components (e.g., an X-ray tube, a collimator, a detector), which are integrated into a single component (e.g., a single part, a single piece, or a single structure). The CT rotating base is a rotating component of the gantry. The CT rotating base includes a single-piece structure that is used to accommodate and / or mount multiple components of the imaging chain. The single-piece structure can be manufactured by machining, forging, molding, casting, welding, or any three-dimensional (3D) printing process, or any combination of these processes. The CT rotating base also includes a drive device that is integrated on the single-piece structure and is configured to drive the single-piece structure and the imaging components to rotate in response to a driving force (e.g., from a pulley or belt coupled to a motor).

[0028] The CT rotating base includes a cylindrical shape. In some embodiments, the rotating base may have different shapes. Specifically, the one-piece structure includes a first annular member or part or structure, a second annular member or part or structure, and a plurality of cross bars, which are arranged between the first annular structure and the second annular structure and coupled to both the first annular structure and the second annular structure. The plurality of cross bars are spaced apart from each other in the circumferential direction relative to the rotation axis of the one-piece structure or the CT rotating base. The drive device is located on the surface of the outer periphery of the first annular structure (e.g., the outer surface away from the rotation axis). In some embodiments, the drive device may include teeth or grooves. In some embodiments, the drive device may be flat.

[0029] The one-piece structure includes an independent mounting structure integrated on the one-piece structure, and the independent mounting structure is configured to mount the imaging component on the one-piece structure. For example, the one-piece structure includes a plurality of detector mounting structures located on the second annular structure. Specifically, the flat extension extends in a radial direction away from the axis of rotation, and the outer periphery of the second annular structure has a plurality of detector mounting structures. Each detector mounting structure is configured to directly mount (i.e., there is no intermediate interface (e.g., detector rail) between the X-ray detector module and the detector mounting structure) a corresponding X-ray detector module of the X-ray detector assembly. The one-piece structure also includes another mounting structure (e.g., a housing) located on the second annular structure (e.g., in a surface of the second annular structure away from the first annular structure). The housing is configured to mount a collimator in the housing (e.g., on a side of the housing facing the detector assembly). The housing is also configured to mount an X-ray source (e.g., an X-ray tube) on a side of the housing opposite to the position where the collimator is configured to be mounted (i.e., the side away from the detector assembly). The housing is also configured to enable both the X-ray source and the collimator to be coupled to and detached from the housing in a mutually exclusive manner. The modularity of the imaging components (e.g., the X-ray tube, collimator, and detector assembly) on the CT rotating base minimizes beam-on-window (BOW) alignment of the X-ray tube and detector, thereby reducing the overall time required for alignment at the customer site. In addition, integrating the mounting structure of the collimator avoids the need for additional bulky components that are typically coupled to the base to form a collimator housing.

[0030] In addition to the mounting structure, the CT rotating base also has mounting structures for other components. For example, the CT rotating base has a mounting structure (e.g., a flat extension) that is integrated on the second annular structure for coupling to a power source (e.g., an electrical housing and a power source) of the CT imaging system. In addition, the CT rotating base includes a plurality of mounting holes that are located on (and extend through) the first annular structure, and the plurality of mounting holes enable the single-piece structure to be directly coupled to a bearing of the frame (which is coupled to a fixed component of the frame) without the need to align the single-piece structure with the bearing of the frame (i.e., without the need to center the rotating base relative to the bearing).

[0031] In addition, the contoured geometry of the CT rotating base provides a self-balancing rotor system. In other words, when all imaging components (and other components) are coupled to the CT rotating base, there is no need to couple balancing weights to the rotating components of the gantry to counterbalance the CT rotating base. In some embodiments, one or more balancing sheets can be coupled to the single-piece structure to facilitate self-balancing, thereby taking into account changes in weight and center of gravity between parts. In some embodiments, the balancing sheets can be separate from the single-piece structure. In some embodiments, the balancing sheets can be integrated with the single-piece structure.

[0032] The disclosed CT rotating base significantly reduces the number of bolted joints and assemblies (and other components) on the rotating base, and thus achieves better structural integrity. In addition, due to the reduced number of these bolted joints and assemblies, the disclosed rotating base is significantly lighter than a typical rotating base (e.g., about 40% weight reduction) while still achieving a high strength construction. The construction of the CT rotating base is configured to evenly distribute stress with minimal deformation. The disclosed rotating base construction is scalable and can be adapted for other CT platforms. For example, the depth of the single-piece structure between the first annular structure and the second annular structure can be adjusted.

[0033] The disclosed CT rotating base provides a built-in drive device for many types of drive devices, which does not require any additional or intermittent independent drive devices that are usually required to use the rotating base to transmit motion from the drive to the frame. In addition, the unified drive solution for the rotating base provides plug-and-play fit for the entire structure, avoiding any misalignment of the drive drive system, while also enhancing the motion performance and reliability of the drive system. The disclosed CT rotating base with an integrated drive device avoids the need for the assembly alignment process of the drive wheel and the frame rotating base.

[0034] Taking into account the foregoing and referring to Figure 1, a computed tomography (CT) imaging system 10 is shown by way of example. The CT imaging system 10 includes a gantry 12. The gantry 12 has an X-ray source 14 that projects a beam of X-rays 16 toward a detector assembly 15 on the opposite side of the gantry 12. The X-ray source 14 projects the X-ray 16 beam through a pre-patient collimator assembly 13, which determines the size and shape of the X-ray 16 beam. The detector assembly 15 includes a collimator assembly 18 (post-patient collimator assembly), a plurality of detector modules 20 (e.g., detector elements or sensors), and a data acquisition system (DAS) 32. The plurality of detector modules 20 detect the projected X-rays that pass through a subject or object 22 being imaged, and the DAS 32 converts the data into digital signals for subsequent processing. Each detector module 20 in a conventional system generates an analog electrical signal that represents the intensity of the incident X-ray beam and, therefore, the intensity of the beam that is attenuated when the incident X-ray beam passes through the subject or object 22. During a scan to acquire x-ray projection data, the gantry 12 and components mounted thereon are rotated about a center of rotation 25 (eg, isocenter) to collect attenuation data from multiple viewing angles relative to the imaging volume.

[0035] The rotation of the gantry 12 and the operation of the X-ray source 14 are controlled by a control system 26 of the CT imaging system 10. The control system 26 includes an X-ray controller 28, which provides power and timing signals to the X-ray source 14; a collimator controller 29, which controls the aperture length and width of the pre-patient collimator 13 (and therefore, the size and shape of the beam of X-rays 16); and a gantry motor controller 30, which controls the rotation speed and position of the gantry 12. An image reconstructor 34 receives sampled and digitized X-ray data from the DAS 32 and performs high-speed image reconstruction. The reconstructed image is applied as input to a computer 36, which stores the image in a storage device 38. The computer 36 also receives commands and scanning parameters from an operator via a console 40. An associated display 42 allows the operator to observe the reconstructed image and other data from the computer 36. The computer 36 uses the commands and parameters provided by the operator to provide control signals and information to the DAS 32, the x-ray controller 28, the collimator controller 29, and the gantry motor controller 30. In addition, the computer 36 operates a table motor controller 44, which controls a motorized table 46 to position the subject 22 and the gantry 12. Specifically, the table 46 moves portions of the subject 22 through a gantry opening or aperture 48.

[0036] Figures 2 to 6 Different views of a CT rotating base 50 (eg, a drum) are shown. The CT rotating base 50 is a gantry (eg, Figure 1The CT rotating base 50 is a rotating component of the gantry 12 in the embodiment of the present invention, which is configured to be disposed within the housing of the gantry. The CT rotating base 50 is configured to be coupled to the fixed component via a bearing within the housing of the gantry. The CT rotating base 50 is configured to rotate in a circumferential direction 52 around a rotation axis 54.

[0037] The CT rotating base 50 is made of a single-piece structure 56. The single-piece structure 56 can be manufactured by machining, forging, molding, casting, welding, or any three-dimensional (3D) printing process, or any combination of these processes. The single-piece structure 56 can be made of aluminum, steel, or other metals or metal alloys. In some embodiments, the weight of the single-piece structure 56 can be about 56 kilograms (kg). In some embodiments, the weight of the single-piece structure 56 can be about 40% less than a typical CT rotating base.

[0038] The single-piece structure 56 has a cylindrical shape. The single-piece structure 56 includes a first annular member or portion or structure 58 and a second annular member or portion or structure 60. The single-piece structure 56 also includes a plurality of structural members or crossbars 62, which are arranged between the first annular structure and the second annular structure and are coupled to both the first annular structure and the second annular structure. The plurality of crossbars 62 are spaced relative to each other in a circumferential direction 52 relative to the rotation axis 54 of the single-piece structure 56 or the CT rotating base 50. The plurality of crossbars 62 are configured to minimize deflection and minimize stress. The construction of the CT rotating base 50 (i.e., the single-piece structure 56) is scalable and can be adapted for use with other CT platforms. The width 63 of the plurality of crossbars 62 (e.g., as shown in Figure 5 and Figure 6 Specifically, the width 63 of the plurality of crossbars 62 may be adjusted based on the configuration of the CT imaging system. Thus, the depth 65 (e.g., shown in FIG. 1 ) of the one-piece structure 56 between the first annular structure 58 and the second annular structure 60 in the direction 80 may also be adjusted based on the configuration of the CT imaging system. Figure 5 and Figure 6 The depth 65 of the one-piece structure minimizes the gantry depth. It should be noted that the shape and / or arrangement of the CT rotating base 50 and / or the components of the CT rotating base 50 may be different from Figures 2 to 6 For example, the position and angle of the crossbar 62 (eg, relative to the rotation axis of the CT rotating base 50) may be different, such as Fig.14 shown.

[0039] return Figures 2 to 6, the second annular structure 60 includes an outer periphery 64. The second annular structure 60 includes a first flat extension 66 (integral with the one-piece structure 56) and the outer periphery 64 of the second annular structure 60, the first flat extension extending in a radial direction 68 away from the rotation axis 54 (e.g., orthogonal to the rotation axis 54) and the outer periphery 64 of the second annular structure 60. The second annular structure 60 also includes a second flat extension 70 (integral with the one-piece structure 56) and the outer periphery 64 of the second annular structure 60, the second flat extension 70 extending in a radial direction 68 away from the rotation axis 54 (e.g., orthogonal to the rotation axis 54).

[0040] like Figure 4 As shown, the width 71 of the first annular structure 58 in the radial direction 68 may be constant in the circumferential direction 52. Figure 3 As shown, the width 73 of the second annular structure 60 in the radial direction 68 may vary in the circumferential direction 52. Figure 3 and Figure 4 As shown, at each corresponding point or location in the circumferential direction 52 , the width 73 may be equal to or greater than the width 73 .

[0041] The second annular structure 60 includes a separate mounting structure 72 for mounting the imaging component to the single-piece structure 56. The separate mounting structure 72 includes a housing 74 for mounting both an X-ray source (e.g., an X-ray tube) and a collimator. The housing 74 includes a first side 76 and a second side 78. The housing 74 is configured for mounting the collimator on the second side 78 (which faces the detector assembly when coupled to the single-piece structure 56) within the housing 74. The housing 74 is also configured to mount the X-ray source on the first side 76 (i.e., the side facing away from the detector assembly) of the housing 74, which is opposite to the location where the collimator is configured to be mounted. The housing 74 is also configured to enable both the X-ray source and the collimator to be coupled to and detached from the housing 74 in a mutually exclusive manner.

[0042] The independent mounting structure 72 also includes a plurality of detector mounting structures 79 located on the second planar extension 70. Each detector mounting structure 79 is configured to directly mount (i.e., without an intermediate interface (e.g., a detector rail) between the X-ray detector module and the detector mounting structure) a corresponding X-ray detector module of the X-ray detector assembly. As shown, the plurality of detector mounting structures 79 extend away from the first annular structure 58 and the second planar extension 70 in a direction 80 (parallel to the rotation axis 54). The arrangement of the plurality of detector mounting structures 79 may vary. Figure 2 In some embodiments, the detector mounting structure 79 is configured for indirect mounting of the X-ray detector module via a detector rail mounted on the detector mounting structure 79 .

[0043] The modularity of the imaging components (e.g., X-ray tube, collimator, and detector assembly) on the CT rotating base 50 minimizes the beam-on-window (BOW) alignment of the X-ray tube and detector, thereby reducing the overall alignment time at the manufacturing site and the customer site. In addition, the integration of the collimator mounting structure (e.g., housing 74) avoids the need for additional bulky components that are typically coupled to the base to form a collimator housing.

[0044] The first planar extension 66 serves as a mounting structure for a power source (e.g., an electrical housing and a power source) of the CT imaging system to be coupled to the single-piece structure 56. Specifically, the first planar extension 66 includes a plurality of holes 81 disposed on a surface 83 of the first planar extension 66 that faces away from the rotation axis 54 in the radial direction 68 (e.g., Figure 6 The plurality of holes enable the power supply to be mounted to the one-piece structure 56. The first flat extension 66 also includes a plurality of holes 82 for mounting a balancing sheet on a surface 84 (e.g., facing away from the first annular structure 58). The balancing sheet can assist the CT rotating base 50 in self-balancing as it rotates with all components coupled to it.

[0045] The second flat extension 70 also serves as a mounting structure for additional components. Figure 2 As shown, the second planar extension 70 includes a plurality of holes 86 for coupling a plate to a surface 88 (eg, facing away from the first annular structure 58) of the second planar extension 70. The plate may be coupled to an additional component (eg, a DAS).

[0046] The second annular structure 60 includes a plurality of holes 89 that enable a generator (e.g., a high voltage generator) to be mounted to the single-piece structure 56. Specifically, the plurality of holes 89 enable a bracket to be coupled to the second annular structure 60 and the generator to be coupled to the bracket. The generator provides power to the X-ray source.

[0047] The first annular structure 58 includes a plurality of holes 90 (e.g., mounting holes) spaced along the first annular structure 58 in the circumferential direction 52. The plurality of holes 90 enables the one-piece structure 56 to be directly coupled to a bearing of the frame (which is coupled to a stationary component of the frame) (via the first annular structure 58) without requiring the one-piece structure 56 to be aligned with the bearing of the frame (i.e., without requiring the rotating base 50 to be centered relative to the bearing).

[0048] The one-piece structure 56 also includes a drive device 92, which is integrated on the one-piece structure 56 and is configured to drive the one-piece structure 56 and the imaging component to rotate in response to a driving force (e.g., from a pulley or belt coupled to a motor). The drive device 92 is located on a surface 94 (e.g., an outer surface away from the rotation axis 54) of the outer periphery 96 of the first annular structure 58. As shown, the surface 94 of the drive device 92 is flat or smooth. In some embodiments, the drive device 92 may include a groove. In some embodiments, the drive device 92 may include teeth (e.g., gear teeth). The built-in drive device does not require any additional or intermittent independent drive devices that are usually required to use a rotating base to transfer motion from the drive to the frame. In addition, the unified drive solution for the rotating base 50 provides plug-and-play cooperation for the entire structure, avoiding any misalignment of the drive drive system, while also enhancing the motion performance and reliability of the drive system. In addition, the integrated drive device 92 avoids the need for an assembly alignment process of the drive wheel and the frame rotating base.

[0049] The profile geometry of the one-piece structure 56 provides a self-balancing rotor system. In other words, when all imaging components (and other components) are coupled to the CT rotating base 50, there is no need to couple balancing weights to the rotating components of the gantry to counterbalance the CT rotating base 50. In some embodiments, one or more balancing sheets can be coupled to the one-piece structure 56 to facilitate self-balancing. In some embodiments, the balancing sheets can be separate from the one-piece structure 56. In some embodiments, the balancing sheets can be integrated with the one-piece structure 56.

[0050] Figure 7 and Figure 8 yes Figure 2 1 and 10. As shown, the housing 74 is configured to mount both an X-ray source (e.g., an X-ray tube) and a collimator. The housing 74 includes a top wall 98 having a first side 76 and a second side 78. The housing 74 also includes a pair of walls 100, 102 flanking the top wall 98. The pair of walls 100, 102 extend in a radial direction 68 toward the rotation axis 54 (see FIG. Figure 2 ). Walls 98, 100, 102 define a space 104. The housing 74 is configured for mounting a collimator on a second side 78 (which faces the detector assembly when coupled to the single-piece structure 56) within the space 104 of the housing 74. The housing 74 includes a plurality of holes 106 for coupling the collimator.

[0051] The housing 74 is also configured to mount the X-ray source on a second side 78 of the housing 74 (i.e., the side facing away from the detector assembly), which second side is opposite to where the collimator is configured to be mounted. The wall 98 includes a plurality of holes 108 for coupling the X-ray source to the first side 76. The wall 98 also includes a plurality of recesses 110 on the second side 78 for receiving the X-ray source. The wall 98 also includes an aperture 112 for an X-ray beam emitted by the X-ray source. The housing 74 is also configured to enable both the X-ray source and the collimator to be coupled to and removed from the housing 74 in a mutually exclusive manner.

[0052] Fig. 9 yes Figure 2 00140 . A front view of an extension (second flat extension 70) of the CT rotating base 50 in FIG. 10 . As described above, the second flat extension 70 (integral to the one-piece structure 56) extends in a radial direction 68 away from the rotation axis 54 (e.g., orthogonal to the rotation axis 54) and the outer periphery 64 of the second annular structure 60. The second flat extension 70 includes a plurality of detector mounting structures 79 located on the second flat extension 70. Each detector mounting structure 79 is configured for directly mounting (i.e., without an intermediate interface (e.g., a detector rail) between the X-ray detector module and the detector mounting structure) a corresponding X-ray detector module of the X-ray detector assembly. As shown in FIG. Figure 2 As shown, a plurality of detector mounting structures 79 extend in a direction 80 (parallel to the rotation axis 54) away from the first annular structure 58 and the second flat extension 70. As described above, the second flat extension 70 also serves as a mounting structure for additional components. The second flat extension 70 includes a plurality of holes 86 for coupling a plate to a surface 88 of the second flat extension 70 (e.g., away from the first annular structure 58). The plate can be coupled to an additional component (e.g., a DAS).

[0053] Fig.10 yes Figure 2 0048 . A perspective view of the drive device 92 of the CT rotating base 50 in FIG. As described above, the one-piece structure 56 also includes the drive device 92, which is integrated on the one-piece structure 56. The drive device is configured to drive the one-piece structure 56 and the imaging component to rotate in response to a driving force (e.g., from a pulley or belt coupled to a motor). The drive device 92 is located on a surface 94 (e.g., an outer surface facing away from the rotation axis 54) of the outer periphery 96 of the first annular structure 58. As shown, the drive device 92 includes teeth 114 (e.g., gear teeth). In some embodiments, the drive device 92 may include grooves. In some embodiments, the drive device 92 may be flat (e.g., as Figures 2 to 6 shown).

[0054] Fig.11 is coupled to each component Figure 2 A perspective view of the CT rotating base 50 in FIG. Fig.11 As shown, the collimator 13 (e.g., a pre-patient collimator assembly) is disposed within the housing 74. The housing 74 also includes an X-ray source 14 (e.g., an X-ray tube) mounted to the housing 74. As shown, the collimator 13 is mounted on one side (e.g., Figure 7 and Figure 8 The X-ray source 14 is mounted on an opposite side of the top of the housing 74 (e.g., Figure 7 and Figure 8 As described above, the housing 74 is also configured to enable both the X-ray source 14 and the collimator 13 to be coupled to and detached from the housing 74 in a mutually exclusive manner.

[0055] In addition, if Fig.11 As shown, the detector assembly 15 is directly coupled to the surface 88 on the second planar extension 70. Specifically, the plurality of detector modules 20 of the detector assembly 15 are connected to the second planar extension 70 via the detector mounting structure (e.g., Figure 2 The detector mounting structure 79 in the embodiment of the present invention is directly coupled to the surface 88. The detector module 20 is directly coupled to the second extension portion 70 without an intermediate interface (eg, a detector rail) between the detector module 20 and the second extension portion 70.

[0056] Furthermore, if Fig.11 As shown, the plate 116 is coupled to the second planar extension 70 (eg, via Fig. 9 The DAS 32 is mounted on the plate 116. Further, a power supply 118 (e.g., an electrical housing and a power supply) for the CT imaging system is mounted on the first planar extension 66 (e.g., Figure 6 Multiple holes 81 on the surface 83 in it).

[0057] Furthermore, if Fig.11 As shown, a generator 117 (eg, a high voltage generator) is mounted on the second annular structure 60. Specifically, the generator 117 is coupled to the second annular structure 60 via a bracket 119. The bracket 119 is directly coupled to the second annular structure 60.

[0058] As shown, the one-piece structure 56 of the CT rotating base 50 is coupled to the fixed component 120 via the bearing 122. Specifically, the first annular structure 58 is coupled to the bearing 122 (e.g., via Figure 2The plurality of holes 90 enables the one-piece structure 56 to be directly coupled to the bearing 122 (via the first annular structure 58) without the need to align the one-piece structure 56 with the bearing 122 (i.e., without the need to center the CT rotating base 50 relative to the bearing 122).

[0059] As shown, the motor 124 is coupled to the stationary component 120. A belt or pulley 126 is coupled to the motor 124 and disposed about the drive device 92. The drive device 92 drives the one-piece structure 56 and the imaging component to rotate in response to a driving force (e.g., from the pulley or belt 126 coupled to the motor 124).

[0060] The profile geometry of the one-piece structure 56 provides a self-balancing rotor system. In other words, when all imaging components (and other components) are coupled to the CT rotating base 50, there is no need to couple a balancing weight to the rotating component 120 of the gantry to counterbalance the CT rotating base 50. In some embodiments, one or more balancing sheets may be coupled (e.g., directly or indirectly) to the one-piece structure 56 to facilitate self-balancing. Fig.11 As shown, the first balancing sheet 128 is coupled to the first planar extension 66 (eg, via Figure 2 86 in the plate 116). Additionally, a second balancing sheet 130 is coupled to the plate 116 (which is coupled to the second flat extension 70). In certain embodiments, the balancing sheet can be separate from the one-piece structure 56. In certain embodiments, the balancing sheet (e.g., balancing sheet 128) can be integrated with or on the one-piece structure 56.

[0061] The construction of the CT rotating base 50 is configured to evenly distribute stress with minimal deformation. Specifically, the plurality of crossbars 62 are configured to minimize deflection and stress. Fig.12 Shown in Figure 2 FIG. 1 is a stress graph 132 performed on the CT rotating base 50 in FIG. 1 and an enlarged portion 134 of the stress graph 132. As shown, the stress is evenly distributed throughout the single-piece structure 56 of the CT rotating base 50. Fig.13 Shown in Figure 2 Deflection diagram 136 of the deformation performed on the CT rotating base 50. As shown, the single-piece structure 56 undergoes minimal deformation.

[0062] The technical effects of the disclosed embodiments include providing an integrated CT rotating base with a drive device and a mounting interface for image chain components (e.g., X-ray tube, collimator, detector), which are integrated into a single component (e.g., a single part, a single piece, or a single structure). The technical effects of the disclosed embodiments also include significantly reducing (e.g., reducing by about 40%) the rotating portion of the CT gantry. The technical effects of the disclosed embodiments also include reducing the time and effort spent during assembly (e.g., by avoiding the need to perform runout alignment of the driven pulley relative to the center of rotation). The technical effects of the disclosed embodiments also include enabling the X-ray tube and collimator assemblies to be assembled to and disassembled from the CT rotating base in a mutually exclusive manner. The technical effects of the disclosed embodiments also include improving the structural integrity of the CT rotating base (e.g., by reducing the number of bolted joints and assemblies). The technical effects of the disclosed embodiments also include directly mounting the detector module (i.e., without interface connection components) on the CT rotating base.

[0063] Reference is made to the technology presented and claimed herein and applied to physical and specific examples of a practical nature that clearly improves upon the present state of the art and, therefore, is not abstract, intangible, or purely theoretical. In addition, if any claim appended to the end of this specification contains one or more elements designated as "means for [performing] the function of ..." or "steps for [performing] the function of ...," it is intended that such elements be interpreted under 35 U.S.C. § 112(f). However, for any claim containing elements designated in any other manner, it is not intended that such elements be interpreted under 35 U.S.C. § 112(f).

[0064] This written description uses examples to disclose the subject matter, including the best mode, and also to enable those skilled in the art to practice the subject matter, including making and using any devices or systems and performing any included methods. The patentable scope of the subject matter 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 insignificant differences from the literal language of the claims.

Claims

1. A rotating component (50) for a gantry (12) of a computed tomography (CT) imaging system (10), the rotating component comprising: A single-piece structure (56) is configured to be coupled to an imaging component, wherein the single-piece structure (56) includes a driving device (92), which is integrated on the single-piece structure (56) and is configured to drive the single-piece structure (56) and the imaging component to rotate in response to a driving force.

2. The rotating component (50) according to claim 1, wherein the one-piece structure (56) includes an independent mounting structure (72), which is integrated on the one-piece structure (56) and is configured to mount the imaging component on the one-piece structure (56).

3. The rotating component (50) according to claim 2, wherein the imaging component comprises an X-ray source (14), a collimator (13) and an X-ray detector assembly (15).

4. The rotating component (50) according to claim 3, wherein the independent mounting structure (72) includes a plurality of detector mounting structures (79), wherein each detector mounting structure (79) of the plurality of detector mounting structures (79) is configured to mount an X-ray detector module (20) of the X-ray detector assembly (15).

5. The rotating component (50) according to claim 3, wherein the independent mounting structure (72) includes a housing (74), and the housing is configured to mount the collimator (13) in the housing (74).

6. The rotating component (50) according to claim 5, wherein the housing (74) is configured to mount the X-ray source (14) on a side (76) of the housing (74) opposite to the position where the collimator (13) is configured to be mounted.

7. The rotating component (50) according to claim 6, wherein the housing (74) is configured to enable both the X-ray source (14) and the collimator (13) to be coupled to and detached from the housing (74) in a mutually exclusive manner.

8. The rotating component (50) of claim 1, wherein the single-piece structure (56) is configured to mount a power source (118) of the CT imaging system (10).

9. The rotating component (50) of claim 1, wherein the single-piece structure (56) is configured to self-balance while rotating.

10. A rotating component (50) according to claim 1, wherein the one-piece structure (56) includes a first annular structure (58), a second annular structure (60), and a plurality of cross bars (62), wherein the plurality of cross bars are arranged between the first annular structure (58) and the second annular structure (60) and are coupled to both the first annular structure and the second annular structure, wherein the plurality of cross bars (62) are spaced apart relative to each other in a circumferential direction (52) relative to a rotation axis (54) of the one-piece structure (56).

11. The rotating component (50) of claim 10, wherein the drive device (92) is located on a surface (94) of an outer periphery (96) of the first annular structure (58).

12. The rotating component (50) of claim 10, wherein the first annular structure (58) includes a plurality of mounting holes (90), the plurality of mounting holes being configured to enable the one-piece structure (56) to be directly coupled to a bearing (122) of the frame (12) without aligning the one-piece structure (56) with the bearing (122) of the frame (12).

13. A computer tomography (CT) imaging system (10), the computer tomography imaging system comprising: A frame (12), the frame comprising a fixed component (120) and a rotating component (50), the rotating component being coupled to the fixed component (120) via a bearing (122), wherein the rotating component (50) comprises a structure (56) configured to be coupled to an imaging component, and wherein the structure (56) comprises: a first annular structure (58); a second annular structure (60); and a plurality of cross bars (62) disposed between and coupled to the first annular structure (58) and the second annular structure (60), wherein the plurality of cross bars (58) are spaced relative to one another in a circumferential direction (52) relative to an axis of rotation (54) of the structure (56); and The first annular structure (58) includes a plurality of mounting holes (90) configured to enable the structure (56) to be directly coupled to the bearing (122) without aligning the structure (56) with the bearing (122).

14. The CT imaging system (10) of claim 13, wherein the structure (56) comprises a single-piece structure (56).

15. The CT imaging system (10) according to claim 14, wherein the single-piece structure (56) includes a driving device (92), which is integrated on the single-piece structure (56) and is configured to drive the single-piece structure (56) and the imaging component to rotate in response to a driving force.

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