INTEGRATED COMPUTED TOMOGRAPHY ROTATING BASE WITH AN INTEGRATED DRIVE SYSTEM

A rotating component for a gantry of a computed tomography (CT) imaging system includes a single-piece structure configured to couple to imaging components. The single-piece structure comprises a drive mechanism integrated on the single-piece structure configured to drive rotation of the single-piece structure and the imaging components in response to a driving force.

BACKGROUND

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.

Non-invasive imaging technologies allow images of the internal structures or features of a patient to be obtained without performing an invasive procedure on the patient. In particular, such non-invasive imaging technologies rely on various physical principles, such as the differential transmission of X-rays through the target volume or the reflection of acoustic waves, to acquire data and to construct images or otherwise represent the observed internal features of the patient.

For example, in computed tomography (CT) and other X-ray based imaging technologies, X-ray radiation spans a subject of interest, such as a human patient, and a portion of the radiation impacts a detector where the image data is collected. In digital X-ray systems a photodetector produces signals representative of the amount or intensity of radiation impacting discrete pixel regions of a detector surface. The signals may then be processed to generate an image that may be displayed for review. In CT imaging systems, a detector array, including a series of detector elements, produces similar signals through various positions as a gantry is displaced around a patient.

A gantry of CT imaging system includes a rotating portion and a stationary portion. In particular, in CT imaging systems the rotating portion of the gantry is conventionally used to spin the X-ray source (e.g., X-ray tube) and detector components around the imaging volume in which the patient is positioned during a scan. The X-ray tube, collimator, and detector form the critical image chain components of the CT imaging system. These subsystems or components mechanically assembled on a CT gantry base (i.e., the rotating portion) are positioned in an X-ray beam path for image formation. The CT gantry base includes a bearing that is separately coupled to a large and heavy platter shaped gear pulley system driven by a motor that causes rotation of the CT gantry base (and the image chain components). All of these components are separately coupled via numerous bolted assemblies and sub-assemblies requiring a great deal of time and effort.

SUMMARY

In one embodiment, a rotating component for a gantry of a computed tomography (CT) imaging system is provided. The rotating component includes a single-piece structure configured to couple to imaging components. The single-piece structure includes a drive mechanism integrated on the single-piece structure configured to drive rotation of the single-piece structure and the imaging components in response to a driving force.

In another embodiment, a computed tomography (CT) imaging system is provided. The CT imaging system includes a gantry including a stationary component and a rotating component coupled to the stationary component via a bearing. The rotating component includes a structure configured to couple to imaging components. The structure includes a first annular structure and a second annular structure. The structure also includes a plurality of cross bars disposed between and 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 an axis of rotation of the structure. The first annular structure includes a plurality of mounting holes configured to enable the structure to be directly coupled to the bearing without needing to align the structure to the bearing.

In a further embodiment, a rotating component for a gantry of a computed tomography (CT) imaging system is provided. The rotating component includes a single-piece structure configured to couple to imaging components and to rotate about 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 cross bars disposed between and 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. The single-piece structure further includes an enclosure integrated on the second annular structure and configured for mounting a collimator within the enclosure, mounting an X-ray source on a side of the enclosure opposite from where the collimator is configured to be mounted, and enabling both the X-ray source and the collimator to be coupled to and to be decoupled from the enclosure mutually exclusive of each other.

DETAILED DESCRIPTION

While aspects of the following discussion are provided in the context of medical imaging, it should be appreciated that the disclosed techniques are not limited to such medical contexts. Indeed, the provision of examples and explanations in such a medical context is only to facilitate explanation by providing instances of real-world implementations and applications. However, the disclosed techniques may also be utilized in other contexts, such as image reconstruction for non-destructive inspection of manufactured parts or goods (i.e., quality control or quality review applications), and/or the non-invasive inspection of packages, boxes, luggage, and so forth (i.e., security or screening applications). In general, the disclosed techniques may be useful in any imaging or screening context or image processing or photography field where a set or type of acquired data undergoes a reconstruction process to generate an image or volume.

The present disclosure provides embodiments for an integrated computed tomography) CT rotating base (e.g., drum) with a drive mechanism and mounting interfaces for image chain components (e.g., X-ray tube, collimator, detector) integrated into a single component (e.g., single part, piece, or structure). The CT rotating base is the rotating component of a gantry. The CT rotating base includes a single-piece structure used to house and/or mount multiple components of the imaging chains. The single-piece structure may be manufactured via machining, forging, moulding, casting, weldment, or any three-dimensional (3D) printing process, or any combination of these processes. The CT rotating base also includes a drive mechanism integrated on the single-piece structure configured to drive rotation of the single-piece structure and the imaging components in response to a drive force (e.g., from a pulley or belt coupled to a motor).

The CT rotating base includes a cylindrical shape. In certain embodiments, the rotating base may have a different shape. In particular, the single-piece structure includes a first annular member or portion or structure, a second annular member or portion or structure, and a plurality of cross bars disposed between and 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 an axis of rotation of the single-piece structure or CT rotating base. The drive mechanism is located on a surface (e.g., outer surface facing away from the axis of rotation) of an outer perimeter of the first annular structure. In certain embodiments, the drive mechanism may include teeth or grooves. In certain embodiments, the drive mechanism may be flat.

The single-piece structure includes separate mounting structures integrated on the single-piece structure that are configured for mounting the imaging components on the single-piece structure. For example, the single-piece structure includes a plurality of detector mounting structures located on the second annular structure. In particular, a flat extension extends in a radial direction away from the axis of rotation and an outer perimeter of the second annular structure has the plurality of detector mounting structures. Each detector mounting structure is configured for directly mounting (i.e., without an intermediate interface (e.g., detector rail) between the X-ray detector module and the detector mounting structure) of a respective X-ray detector module of an X-ray detector assembly. The single-piece structure also includes another mounting structure (e.g., an enclosure) located on the second annular structure (e.g., in a surface of second annular structure facing away from the first annular structure). The enclosure is configured for mounting the collimator within the enclosure (e.g., on a side of the enclosure facing the detector assembly). The enclosure is also configured for mounting an X-ray source (e.g., X-ray tube) on a side of the enclosure opposite from where the collimator is configured to be mounted (i.e., side facing away from the detector assembly). The enclosure is also configured to enable both the X-ray source and the collimator to be coupled to and to be decoupled from the enclosure mutually exclusive of each other. The modularity of the imaging components (e.g., 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, thus, reducing the overall alignment time at the customer site. In addition, the integration of the mounting structure for the collimator eliminates additional bulky components that are normally coupled to the base to form the collimator housing.

Besides the mounting structures, the CT rotating base has mounting structures for other components. For example, the CT rotating base has a mounting structure (e.g., flat extension portion) integrated on the second annular structure for coupling to a power supply (e.g., electrical housing and power supply) of the CT imaging system. In addition, the CT rotating base includes a plurality of mounting holes located on (and extending through) the first annular structure that enable the single-piece structure to be directly coupled to a bearing of the gantry (which is coupled to a stationary component of the gantry) without needing to align the single-piece structure to the bearing of the gantry (i.e., no need for centering the rotating base with respect to the bearing).

In addition, a profile geometry of the CT rotating base provides for a self-balancing rotor system. In other words, a balance block does not need to be coupled to the rotating component of the gantry for counterbalancing the CT rotating base when all of the imaging components (and other components) are coupled to the CT rotating base. In certain embodiments, one or more balance sheets may be coupled to the single-piece structure to help with the self-balancing to account for part to part weight and center of gravity variation. In certain embodiments, the balance sheets may be separate from the single-piece structure. In certain embodiments, the balance sheets may be integrated with the single-piece structure.

The disclosed CT rotating base significantly reduces the number of bolted joints and assemblies (and other parts) on the rotating base and, thus provides better structural integrity. In addition, due to these reduced number of bolted joints and assemblies, the disclosed rotating base is significantly lighter (e.g., with an approximately 40 percent reduction in weight) than a typical rotating base while still providing a high strength configuration. The configuration of the CT rotating base is configured to uniformly distribute stress with minimal deformation. The disclosed rotating base is scalable in configuration and can be adapted for other CT platforms. For example, a depth of the single-piece structure between the first annular structure and the second annular structure may be adjusted.

The disclosed CT rotating base provides a built-in drive mechanism for many types of drive mechanisms that avoids needing any additional or intermittent separate driven provisions to transmit motion from the drive to the gantry that are typically required with rotating bases. In addition, the unified drive solution for the rotating base provides an entire structure with a plug and play fit that eliminates any misalignments that occur with a drive-driven system while also enhancing motion performance and reliability of the drive system. The disclosed CT rotating base having the integrated drive mechanism eliminates the assembly alignment process of a drive wheel with a gantry rotating base.

With the preceding in mind and referring toFIG.1, a computed tomography (CT) imaging system10is shown, by way of example. The CT imaging system10includes a gantry12. The gantry12has an X-ray source14that projects a beam of X-rays16toward a detector assembly15on the opposite side of the gantry12. The X-ray source14projects the beam of X-rays16through a pre-patient collimator assembly13that determines the size and shape of the beam of X-rays16. The detector assembly15includes a collimator assembly18(a post-patient collimator assembly), a plurality of detector modules20(e.g., detector elements or sensors), and data acquisition systems (DAS)32. The plurality of detector modules20detect the projected X-rays that pass through a subject or object22being imaged, and DAS32converts the data into digital signals for subsequent processing. Each detector module20in a conventional system produces an analog electrical signal that represents the intensity of an incident X-ray beam and hence the attenuated beam as it passes through the subject or object22. During a scan to acquire X-ray projection data, gantry12and the components mounted thereon rotate about a center of rotation25(e.g., isocenter) so as to collect attenuation data from a plurality of view angles relative to the imaged volume.

Rotation of gantry12and the operation of X-ray source14are governed by a control system26of CT imaging system10. Control system26includes an X-ray controller28that provides power and timing signals to an X-ray source14, a collimator controller29that controls a length and a width of an aperture of the pre-patient collimator13(and, thus, the size and shape of the beam of X-rays16), and a gantry motor controller30that controls the rotational speed and position of gantry12. An image reconstructor34receives sampled and digitized X-ray data from DAS32and performs high-speed image reconstruction. The reconstructed image is applied as an input to a computer36, which stores the image in a storage device38. Computer36also receives commands and scanning parameters from an operator via console40. An associated display42allows the operator to observe the reconstructed image and other data from computer36. The operator supplied commands and parameters are used by computer36to provide control signals and information to DAS32, X-ray controller28, collimator controller29, and gantry motor controller30. In addition, computer36operates a table motor controller44, which controls a motorized table46to position subject22and gantry12. Particularly, table46moves portions of subject22through a gantry opening or bore48.

FIGS.2-6illustrate different views of a CT rotating base50(e.g., drum). The CT rotating base50is a rotating component of a gantry (e.g., gantry12inFIG.1) that is configured to be disposed within a housing of the gantry. The CT rotating base50is configured to be coupled to a stationary component via a bearing within the housing of the gantry. The CT rotating base50is configured to rotate in a circumferential direction52about an axis of rotation54.

The CT rotating base50is made of a single-piece structure56. The single-piece structure56may be manufactured via machining, forging, moulding, casting, weldment, or any three-dimensional (3D) printing process, or any combination of these processes. The single-piece structure56may made of aluminum, steel, or other metal, or metal alloy. In certain embodiments, the single-piece structure56may weigh approximately 56 kilograms (kg). In certain embodiments, the single-piece structure56may weigh approximately 40 percent less than a typical CT rotating base.

The single-piece structure56has a cylindrical shape. The single-piece structure56includes a first annular member or portion or structure58and a second annular member or portion or structure60. The single-piece structure56also includes a plurality of structural members or cross bars62disposed between and coupled to both the first annular structure and the second annular structure. The plurality of cross bars62are spaced apart relative to each other in the circumferential direction52relative to the axis of rotation54of the single-piece structure56or the CT rotating base50. The plurality of cross bars62are configured to provide the lowest amount of deflection and the lowest amount of stress. The CT rotating base50(i.e., the single-piece structure56) is scalable in configuration and can be adapted for other CT platforms. A width63(e.g., shown inFIGS.5and6) of the plurality of cross bars62may vary. In particular, the width63of the plurality of cross bars62may be adjusted based on the configuration of the CT imaging system. Thus, a depth65(e.g., shown inFIGS.5and6) of the single-piece structure56in the direction80between the first annular structure58and the second annular structure60may also be adjusted based on the configuration of the CT imaging system. The depth65of single-piece structure minimizes the gantry depth. It should be noted that shape and/or arrangement of the CT rotating base50and/or the components of the CT rotating base50may vary from that depicted inFIGS.2-6. For example, the location and angle of the cross bars62(e.g., relative to an axis of rotation of the CT rotating base50) may be different as depicted inFIG.14.

Returning toFIGS.2-6, the second annular structure60includes an outer perimeter64. The second annular structure60includes a first flat extension portion66(integral to the single-piece structure56) that extends in a radial direction68(e.g., orthogonal to the axis of rotation54) away from the axis of rotation54and the outer perimeter64of the second annular structure60. The second annular structure60also includes a second flat extension portion70(integral to the single-piece structure56) that extends in the radial direction68(e.g., orthogonal to the axis of rotation54) away from the axis of rotation54and the outer perimeter64of the second annular structure60.

As depicted inFIG.4, a width71in the radial direction68of the first annular structure58may be constant in the circumferential direction52. As depicted inFIG.3, a width73in the radial direction68of the second annular structure60may vary in the circumferential direction52. As depicted inFIGS.3and4, the width73may be same or greater than the width73at each corresponding point or location in the circumferential direction52.

The second annular structure60includes separate mounting structures72for mounting imaging components to the single-piece structure56. The separate mounting structures72include an enclosure74for mounting both an X-ray source (e.g., X-ray tube) and a collimator. The enclosure74includes a first side76and a second side78. The enclosure74is configured for mounting the collimator within the enclosure74on the second side78(which faces the detector assembly when coupled to the single-piece structure56). The enclosure74is also configured for mounting the X-ray source on the first side76of the enclosure74opposite from where the collimator is configured to be mounted (i.e., side facing away from the detector assembly). The enclosure74is also configured to enable both the X-ray source and the collimator to be coupled to and to be decoupled from the enclosure74mutually exclusive of each other.

The separate mounting structures72also include a plurality of detector mounting structures79located on the second flat extension portion70. Each detector mounting structure79is configured for direct mounting (i.e., without an intermediate interface (e.g., detector rail) between the X-ray detector module and the detector mounting structure) of a respective X-ray detector module of an X-ray detector assembly. As depicted, the plurality of detector mounting structures79extend in a direction80(parallel with the axis of rotation54) away from both the first annular structure58and the second flat extension portion70. The arrangement of the plurality of detector mounting structures79may vary from that depicted inFIG.2. In certain embodiments, the detector mounting structure79is configured for indirect mounting of the X-ray detector modules via a detector rail mounted on the detector mounting structure79.

The modularity of the imaging components (e.g., X-ray tube, collimator, and detector assembly) on the CT rotating base50minimizes beam on window (BOW) alignment of the X-ray tube and detector, thus, reducing the overall alignment time at the manufacturing site and the customer site. In addition, the integration of the mounting structure (e.g., enclosure74) for the collimator eliminates additional bulky components that are normally coupled to the base to form the collimator housing.

The first flat extension portion66functions as a mounting structure for a power supply (e.g., electrical housing and power supply) of the CT imaging system to be coupled to the single-piece structure56. In particular, the first flat extension portion66includes a plurality of holes81on a surface83(as depicted inFIG.6) of the first flat extension portion66facing away from the axis of rotation54in the radial direction68. The plurality of holes enable the power supply to be mounted to the single-piece structure56. The first flat extension portion66also includes a plurality of holes82for mounting of a balance sheet on a surface84(e.g., facing away from the first annular structure58). The balance sheet may assist the CT rotating base50in self balancing when rotating with all of components coupled to it.

The second flat extension portion70also serves as a mounting structure for additional components. As depicted inFIG.2, the second flat extension portion70includes a plurality of holes86for coupling a plate on a surface88(e.g., facing away from the first annular structure58) of the second flat extension portion70. The plate may be coupled to additional components (e.g., DAS).

The second annular structure60includes a plurality of holes89to enable mounting of a generator (e.g., high voltage generator) to the single-piece structure56. In particular, the plurality of holes89enable a bracket to be coupled to the second annular structure60and the generator is coupled to the bracket. The generator provides power to the X-ray source.

The first annular structure58includes a plurality of holes90(e.g., mounting holes) spaced apart along the first annular structure58in the circumferential direction52. The plurality of holes90enable (via the first annular structure58) the single-piece structure56to be directly coupled to a bearing of the gantry (which is coupled to a stationary component of the gantry) without needing to align the single-piece structure56to the bearing of the gantry (i.e., no need for centering the rotating base50with respect to the bearing).

The single-piece structure56also includes a drive mechanism92integrated on the single-piece structure56that is configured to drive rotation of the single-piece structure56and the imaging components in response to a drive force (e.g., from a pulley or belt coupled to a motor). The drive mechanism92is located on a surface94(e.g., outer surface facing away from the axis of rotation54) of an outer perimeter96of the first annular structure58. As depicted, the surface94of the drive mechanism92is flat or smooth. In certain embodiments, the drive mechanism92may include grooves. In certain embodiments, the drive mechanism92may include teeth (e.g., gear teeth). The built-in drive mechanism avoids needing any additional or intermittent separate driven provisions to transmit motion from the drive to the gantry that are typically required with rotating bases. In addition, the unified drive solution for the rotating base50provides an entire structure with a plug and play fit that eliminates any misalignments that occur with a drive-driven system while also enhancing motion performance and reliability of the drive system. Also, the integrated drive mechanism92eliminates the assembly alignment process of a drive wheel with a gantry rotating base.

A profile geometry of the single-piece structure56provides for a self-balancing rotor system. In other words, a balance block does not need to be coupled to the rotating component of the gantry for counterbalancing the CT rotating base50when all of the imaging components (and other components) are coupled to the CT rotating base50. In certain embodiments, one or more balance sheets may be coupled to the single-piece structure56to help with the self-balancing. In certain embodiments, the balance sheets may be separate from the single-piece structure56. In certain embodiments, the balance sheets may be integrated with the single-piece structure56.

FIGS.7and8are different views of the enclosure74of the CT rotating base50inFIG.2. As noted, the enclosure74is configured for mounting both an X-ray source (e.g., X-ray tube) and a collimator. The enclosure74includes a top wall98having the first side76and the second side78. The enclosure74also includes a pair of walls100,102flanking the top wall98. The pair of walls100,102extend in the radial direction68toward the axis of rotation54(seeFIG.2). The walls98,100,102define a space104. The enclosure74is configured for mounting the collimator within space104of the enclosure74on the second side78(which faces the detector assembly when coupled to the single-piece structure56). The enclosure74includes a plurality of holes106for coupling the collimator.

The enclosure74is also configured for mounting the X-ray source on the second side78of the enclosure74opposite from where the collimator is configured to be mounted (i.e., side facing away from the detector assembly). The wall98includes a plurality of holes108for coupling the X-ray source to the first side76. The wall98also includes a plurality of recesses110on the second side78for receiving the X-ray source. The wall98further includes an aperture112for the X-ray beams emitted by the X-ray source. The enclosure74is also configured to enable both the X-ray source and the collimator to be coupled to and to be decoupled from the enclosure74mutually exclusive of each other.

FIG.9is a front view of an extension (second flat extension portion70) of the CT rotating base50inFIG.2. As noted above, the second flat extension portion70(integral to the single-piece structure56) extends in the radial direction68(e.g., orthogonal to the axis of rotation54) away from the axis of rotation54and the outer perimeter64of the second annular structure60. The second flat extension portion70includes the plurality of detector mounting structures79located on the second flat extension portion70. Each detector mounting structure79is configured for directly mounting (i.e., without an intermediate interface (e.g., detector rail) between the X-ray detector module and the detector mounting structure) of a respective X-ray detector module of an X-ray detector assembly. As depicted inFIG.2, the plurality of detector mounting structures79extend in the direction80(parallel with the axis of rotation54) away from both the first annular structure58and the second flat extension portion70. As noted above, the second flat extension portion70also serves as a mounting structure for additional components. The second flat extension portion70includes the plurality of holes86for coupling a plate on a surface88(e.g., facing away from the first annular structure58) of the second flat extension portion70. The plate may be coupled to additional components (e.g., DAS).

FIG.10is a perspective view of the drive mechanism92of the CT rotating base50inFIG.2. As noted above, the single-piece structure56also includes the drive mechanism92integrated on the single-piece structure56. The drive mechanism is configured to drive rotation of the single-piece structure56and the imaging components in response to a drive force (e.g., from a pulley or belt coupled to a motor). The drive mechanism92is located on the surface94(e.g., outer surface facing away from the axis of rotation54) of the outer perimeter96of the first annular structure58. As depicted, the drive mechanism92includes teeth114(e.g., gear teeth). In certain embodiments, the drive mechanism92may include grooves. In certain embodiments, the drive mechanism92may be flat (e.g., as depicted inFIGS.2-6).

FIG.11is a perspective view of the CT rotating base50inFIG.2coupled to various components. As depicted inFIG.11, the collimator13(e.g., pre-patient collimator assembly) is disposed within the enclosure74. The enclosure74also includes the X-ray source14(e.g., X-ray tube) mounted to the enclosure74. As depicted, the collimator13is mounted within the enclosure74on one side (e.g., second side78inFIGS.7and8). The X-ray source14is mounted on top of the enclosure74on an opposite side (e.g., first side76inFIGS.7and8). As noted above, the enclosure74is also configured to enable both the X-ray source14and the collimator13to be coupled to and to be decoupled from the enclosure74mutually exclusive of each other.

Also, as depicted inFIG.11, the detector assembly15is directly coupled to the surface88on the second flat extension portion70. In particular, a plurality of detector modules20of the detector assembly15is directly coupled to the surface88via detector mounting structures (e.g., detector mounting structures79inFIG.2) on the second flat extension portion70. The detector modules20are directly coupled to the second extension portion70without an intermediate interface (e.g., detector rail) between the detector modules20and second extension portion70.

Further, as depicted inFIG.11, a plate116is coupled to the second flat extension portion70(e.g., via plurality of holes86inFIG.9). The DAS32is mounted on the plate116. Even further, a power supply118(e.g., electrical housing and power supply) of the CT imaging system is mounted on the first flat extension portion66(e.g., the plurality of holes81on the surface83inFIG.6).

Still further, as depicted inFIG.11, a generator117(e.g., high voltage generator) is mounted on the second annular structure60. In particular, the generator117is coupled to the second annular structure60via a bracket119. The bracket119is directly coupled to the second annular structure60.

As depicted, the single-piece structure56of the CT rotating base50is coupled to a stationary component120via a bearing122. In particular, the first annular structure58is coupled to the bearing122(e.g., via the holes90inFIG.2). The plurality of holes90enable (via the first annular structure58) the single-piece structure56to be directly coupled to the bearing122without needing to align the single-piece structure56to the bearing122(i.e., no need for centering the CT rotating base50with respect to the bearing122).

As depicted, a motor124is coupled to the stationary component120. A belt or pulley126is coupled to the motor124and disposed about the drive mechanism92. The drive mechanism92drives rotation of the single-piece structure56and the imaging components in response to a drive force (e.g., from the pulley or belt126coupled to the motor124).

A profile geometry of the single-piece structure56provides for a self-balancing rotor system. In other words, a balance block does not need to be coupled to the rotating component120of the gantry for counterbalancing the CT rotating base50when all of the imaging components (and other components) are coupled to the CT rotating base50. In certain embodiments, one or more balance sheets may be coupled to the single-piece structure56(e.g., directly or indirectly) to help with the self-balancing. As depicted inFIG.11, a first balance sheet128is coupled to the first flat extension portion66(e.g., via holes86inFIG.2). Also, a second balance sheet130is coupled to the plate116(which is coupled to the second flat extension portion70). In certain embodiments, the balance sheets may be separate from the single-piece structure56. In certain embodiments, the balance sheets (e.g., balance sheet128) may be integrated with or on the single-piece structure56.

The configuration of the CT rotating base50is configured to uniformly distribute stress with minimal deformation. In particular, the plurality of cross bars62are configured to provide the lowest amount of deflection and the lowest amount of stress.FIG.12depicts a stress plot132and zoomed in portion134of the stress plot132performed on the CT rotating base50inFIG.2. As depicted, the stress is uniformly distributed across the single-piece structure56of the CT rotating base50.FIG.13depicts a deflection plot136for deformation performed on the CT rotating base50inFIG.2. As depicted, minimal deformation occurs in the single-piece structure56.

Technical effects of the disclosed embodiments include providing an integrated CT rotating base with a drive mechanism and mounting interfaces for image chain components (e.g., X-ray tube, collimator, detector) integrated into a single component (e.g., single part, piece, or structure). Technical effects of the disclose embodiments also include a significant reduction (e.g., approximately 40 percent reduction) in the rotating portion of the CT gantry. Technical effects of the disclosed embodiments further include a reduction in time and effort during assembly (e.g., by eliminating run out alignment of a driven pulley with respect to a center of rotation). Technical effects of the disclosed embodiments still further include enabling the X-ray tube and the collimator assembly to be assembled and disassembled to the CT rotating base mutually exclusive of each other. Technical effects of the disclosed embodiments yet further include improving structural integrity of the CT rotating base (e.g., via reduction in the number of bolted joints and assemblies). Technical effects of the disclosed embodiments further include providing for direct detector module mounting on the CT rotating base (i.e., without an interfacing component).