Subsystem X-ray Source Module

Abstract

The modular X-ray imaging system includes an application-specific module, a base unit in communication with the application-specific module, and a mechanical support configured to support the X-ray application-specific module, wherein the base unit and the application-specific module are configured to communicate via wired and / or wireless communication.

Description

[Technical field]

[0001] CROSS-REFERENCE TO RELATED APPLICATIONS / PRIORITY CLAIMS This application claims the benefit of and priority to U.S. Provisional Patent Application No. 63 / 341,580, filed May 13, 2022, and U.S. Provisional Patent Application No. 63 / 296,551, filed January 5, 2022, the entire contents of which are incorporated herein by reference.

[0002] This disclosure relates to system designs for x-ray imaging equipment, including digital radiography, fluoroscopy, tomography, and computed tomography (CT). [Background technology]

[0003] X-ray imaging is a primary technology for medical diagnosis, surgical guidance, and industrial imaging, providing operators with the ability to non-destructively image the contents of objects. Systems are currently fully integrated with all of their components built into the respective systems, including computers, data acquisition systems (DAS), X-ray sources, X-ray detectors, high voltage power supplies, and cooling. For systems with 3D imaging, such as tomosynthesis and computed tomography, the system also includes a means to move the X-ray source and detector, such as a motor, a significant rigidity gantry to provide precise movement, and / or a method to maintain the connection to the X-ray source and collect data from the X-ray detector under motion, such as slip rings. Integrated systems have fundamentally limited portability due to their large size and weight, and have high costs for each individual system component (over $100,000 per system, and sometimes over $1 million per system). Summary of the Invention

[0004] An aspect of the present disclosure provides a modular x-ray imaging system including an application-specific module, a base unit, and a mechanical support. The application-specific module includes an imaging ring configured to image a patient, a sensor configured to provide positioning data to enable positioning of the imaging ring relative to the patient, a motor configured to position the imaging ring based on the sensed position, and a controller for controlling the output of a plurality of x-ray sources. The imaging ring includes a plurality of x-ray sources configured to generate and emit beams including an x-ray spectrum, one or more collimators configured to limit the span of the x-ray beam, one or more filters configured to selectively attenuate and / or block low energy rays during x-ray imaging, and one or more x-ray detectors configured to detect x-rays generated by the plurality of x-ray sources. The base unit communicates with the application-specific module. The base unit includes a first power supply having an output voltage greater than 10 kV, a second power supply having an output voltage less than 10 kV configured to turn on and off each individual x-ray source of the plurality of x-ray sources, a processor, and a memory. The memory includes instructions stored thereon that, when executed by the processor, cause the modular x-ray imaging system to position the imaging ring based on the sensor and capture imaging data. The mechanical support is configured to support the imaging ring.

[0005] In aspects of the present disclosure, the base unit may further include a battery. The base unit may be configured to operate solely on battery power with a portion of the battery capable of being changed during operation to maintain battery power longer than the total capacity of the battery.

[0006] In aspects of the present disclosure, the base unit can be configured to move independently of the remainder of the X-ray imaging system.

[0007] In another aspect of the present disclosure, the base unit may be configured to simultaneously connect to, control, and power multiple application-specific modules.

[0008] In aspects of the present disclosure, the system may further include a second application-specific module configured to provide a convertible computed tomography (CT) that can operate vertically or laterally and at any angle in between.

[0009] In aspects of the present disclosure, the application specific module may be operated as at least one of a vertical CT or a horizontal CT.

[0010] In an aspect of the disclosure, when operating in a lateral direction, the system may further include an x-ray transparent table configured to support a patient with the x-ray transparent table supported by at least two points on different halves of the table, each having an opening for a region of interest for imaging.

[0011] In an aspect of the disclosure, the second application specific module may further include a motorized control, an imaging ring including a controller, multiple x-ray sources, one or more anti-scatter grids, an x-ray detector, and communication electronics, a motorized track configured to move the motorized control and the imaging ring, and a sensor configured to position the imaging ring relative to the patient. The motorized control may provide mechanical alignment of the ring to the patient.

[0012] In another aspect of the disclosure, the motorized truck can be configured to move the second application-specific module a distance that is greater than the desired imaging field of view and less than the length of the entire body.

[0013] In aspects of the present disclosure, the motorized track can be configured to rotate about an axis perpendicular to the surface in contact with the mechanical support to change direction of motion.

[0014] In aspects of the present disclosure, the motorized control may be further configured to move the imaging ring in the xy-plane of the patient using at least one linear degree of motion and at least one angular degree of freedom.

[0015] In another aspect of the disclosure, the system may further include a dynamic anti-scatter grid or a moving anti-scatter grid with multiple x-ray sources to optimally remove scatter from each x-ray source.

[0016] In aspects of the present disclosure, application-specific modules may be configured to be adjusted in height and / or rotation relative to the normal of the mounting surface of the application-specific module.

[0017] In aspects of the disclosure, the system may further include at least one wired or wireless connection between the application-specific module and the base unit having at least one high voltage connection above 10 kV configured to connect a high voltage power supply to the application-specific module, and at least one or more low voltage connections below 10 kV configured to connect the application-specific module between a power supply configured to power the motor, a low voltage power supply, and a processor to provide control of the X-ray source and communication between the data acquisition system and sensors controlling the positioning of the application-specific module.

[0018] An aspect of the present disclosure provides an X-ray source alignment device including an imaging ring including a plurality of individually packaged X-ray sources configured to emit a beam including an X-ray spectrum, a second sensor configured to provide positioning data to enable positioning of the imaging ring relative to a patient, a motorized controller configured to provide mechanical alignment of the imaging ring to the patient based on the positioning data, and a motorized track configured to move the motorized controller and the imaging ring based on the positioning data.

[0019] In aspects of the present disclosure, the multiple individually packaged x-ray sources can include at least one focal spot configured for imaging.

[0020] In aspects of the present disclosure, the multiple individually packaged x-ray sources may further include a filter configured to reduce the intensity of one or more wavelengths from the x-ray spectrum.

[0021] In aspects of the present disclosure, the multiple individually packaged x-ray sources may further include a collimator configured to direct the x-ray beam.

[0022] In aspects of the disclosure, the x-ray source alignment device may include a sensor configured to determine the positioning of the imaging ring relative to the patient.

[0023] In another aspect of the disclosure, a modular x-ray imaging system includes an application-specific module, a base unit configured to communicate with and power the application-specific module, and a mechanical support. The application-specific module includes a vertically positionable imaging ring configured to image a patient, a processor, and a memory. The base unit and the application-specific module are configured to communicate in at least one of a wired and / or wireless manner. The memory includes instructions stored thereon that, when executed by the processor, cause the modular x-ray imaging system to position the imaging ring and capture imaging data. The mechanical support is configured to support the vertically positionable imaging ring.

[0024] Further details and aspects of the present disclosure are described in more detail below with reference to the accompanying drawings.

[0025] A better understanding of the features and advantages of the present disclosure will be obtained by reference to the following detailed description that sets forth illustrative aspects, in which the principles of the disclosure are utilized, and the accompanying drawings of which: [Brief description of the drawings]

[0026] [Figure 1] 1 shows a schematic diagram of a modular X-ray system according to the present disclosure. [Diagram 2] 2 illustrates an example block diagram of a base unit of the system of FIG. 1 in accordance with the present disclosure. [Diagram 3] 2 illustrates an imaging ring of the system of FIG. 1 in accordance with the present disclosure. [Figure 4] 4 illustrates a diagram of the imaging ring of FIG. 3 in accordance with the present disclosure. [Diagram 5] FIG. 2 illustrates the system of FIG. 1 in a lateral configuration in accordance with the present disclosure. [Figure 6] FIG. 1 illustrates a mobile screening system according to the present disclosure. [Figure 7] FIG. 2 is an illustration of an inverse geometry computed tomography (IGCT) for use in the system of FIG. 1 in accordance with the present disclosure. [Figure 8] 8 illustrates an exemplary X-ray source for use with the IGCT of FIG. 7 in accordance with the present disclosure. [Figure 9] FIG. 1 illustrates a side perspective cross-sectional view of an exemplary 2×32 X-ray source array showing the individual components arranged in accordance with the present disclosure. [Figure 10] 10 illustrates a side perspective cross-sectional view of the 2×32 X-ray source of FIG. 9, including portions of the chassis, in accordance with the present disclosure. [Figure 11] 10 shows a block diagram of an exemplary connection between the X-ray source and other subsystems of FIG. 9 in accordance with the present disclosure. DETAILED DESCRIPTION OF THE PREFERRED EMBODIMENTS

[0027] The present disclosure relates to methods for constructing X-ray systems, including 2D, tomosynthesis, and computed tomography (CT).

[0028] 1 shows a modular X-ray imaging system 10. The modular X-ray imaging system 10 generally includes a base unit 100, application-specific modules 110, and mechanical support 120 for the application-specific modules 110. The base unit 100 and the application-specific modules 110 communicate via connections 130. Some of the connections 130 can be wired or wireless. In aspects, the modular X-ray imaging system 10 can be converted between an upright type (FIG. 1) and conventional imaging with a patient lying in bed (FIG. 5).

[0029] The mechanical support 120 is used to support the application specific module 110. This mechanical support 120 can be mounted to the ground or can be designed to be temporary for easy transport to improve portability. The mechanical support 120 has the ability to adjust the height of the application specific module 110 or allow the application specific module 110 to be rotated, allowing the vertical system to be converted into a lateral system.

[0030] In an embodiment, the base unit 100 may include an X-ray source 102. The base unit 100 may include a small-scale X-ray source including a field emitter using sharpened silicon nanowires, a vacuum package, and a target anode. The X-ray source may include a focusing mechanism and / or a metal plate that protects the field emitter array from ions. The X-ray source is programmable (e.g., when used in an array). The X-ray source is high performance due to the nature of the X-ray source (vacuum transistor). The X-ray source is compact (volume 10 times smaller than conventional X-ray sources) and batch manufacturable using conventional silicon manufacturing techniques.

[0031] In aspects, the modular X-ray imaging system 10 may include a second application-specific module configured for a convertible CT that can operate vertically or laterally and at any angle in between.

[0032] 2, the base unit 100 includes a processor 150, a display 160, a high voltage power supply 170, a low voltage power supply 180, a motor power supply 190, a battery 200, and a battery power supply 210. In various aspects of the present disclosure, the processor 150 may include any suitable type of computing device, for example, a laptop, a desktop, a mobile device, and / or a server. The processor 150 may include any type of suitable processor, such as, but not limited to, a digital signal processor, a microprocessor, an ASIC, a graphics processing unit (GPU), a field programmable gate array (FPGA), or a central processing unit (CPU). The processor 150 may include a memory for executing instructions that cause the system to perform various functions.

[0033] The high voltage power supply 170 may provide a voltage greater than 10 kV. The low voltage power supply 180 may provide a voltage less than 10 kV. The low voltage power supply 180 may be configured to turn on and off each individual X-ray source 34 (e.g., X-ray tube) of the multiple X-ray sources 34 (FIG. 3). The X-ray source(s) 34 are configured to emit a beam that includes an X-ray spectrum. The motor power supply 190 is configured to power one or more mechanical motors. The base unit 100 may include multiple connections 220, 230 for connecting different power sources and communications to one or more application-specific modules based on low or high voltage requirements. The base unit 100 may be designed to be portable and rugged with a battery 200 as a temporary power source and may have a battery power supply 210 that allows charging from a wall outlet. This allows the system to operate completely on its own power in the event of a power interruption or in the event of field operation. Some of the batteries may be replaceable to allow system power to be replenished in the event of a power outage exceeding its internal battery capacity.

[0034] The connections 130 between the application-specific module(s) 110 and the base unit 100 may be provided at different voltages that may need to be separated based on the purpose. One or more high voltage connections (above 10 kV) 230 connect the high voltage power supply 170 to the application-specific modules, depending on the requirements, and at least one or more low voltage (below 10 kV) connections 220 connect the motor power supply 190, the low voltage power supply 180, and between the processor 150 and the application-specific modules 110 to provide communication between the data acquisition system 292 and the sensors 280 that control the X-ray source 34 and the positioning of the application-specific modules 110 (FIG. 3). Wireless communication may be used to communicate some information between the processor 150 and different parts of the application-specific modules 110 to reduce the total number of connections.

[0035] Referring to FIG. 3, an application-specific module 110 is shown. The application-specific module can be any subsystem module designed for any x-ray imaging modality, such as 2D digital radiography, tomosynthesis (e.g., chest and breast tomosynthesis), or computed tomography. The application-specific module 110 includes application-specific components (e.g., a CT module, a tomosynthesis module, and / or a digital radiography module). The application-specific module 110 generally includes an imaging ring 270, a sensor 280, and a motorized control 260. In an embodiment, the application-specific module 110 can include a motorized control 260 and a motorized track 250 for moving the imaging ring 270. The motorized control 260 can be further configured to control the movement of the imaging ring 270 in the xy-plane of the patient using at least one linear degree of motion and / or at least one angular degree of freedom. The application-specific module 110 can be configured to be adjusted in height and / or rotation relative to a normal to a mounting surface of the application-specific module 110.

[0036] The motorized track 250 may be configured to move the application specific module 110 a distance that is greater than the desired imaging field of view, but less than the entire body length of the patient P. The motorized track 250 may be further configured to rotate about an axis perpendicular to the surface in contact with the mechanical support 120 to change the direction of movement.

[0037] The imaging ring 270 is configured to capture images. The imaging ring 270 includes a controller 290, multiple x-ray sources 34, one or more anti-scatter grids 16, a data acquisition system 292, an x-ray detector 36 (e.g., photon counting or energy integrating), a communication system 294, and a sensor 280 for positioning the imaging ring 270 (FIG. 4). The anti-scatter grid 16 is configured to limit the amount of scattered radiation reaching the detector, thereby improving the amount of x-ray images. The one or more anti-scatter grids 16 may include a dynamic anti-scatter grid or a moving anti-scatter grid with multiple x-ray sources to optimally remove scatter from each x-ray source 34.

[0038] The imaging ring 270 may further include components associated with the X-ray source 34, such as an X-ray collimator 296 and / or an X-ray filter 298. The communication system 294 is configured for communication between the application specific modules 110 and the base unit 100 (FIG. 1). The X-ray collimator 296 is generally disposed near the X-ray source 34 to limit the span of the X-ray beam. The X-ray filter 298 is configured to selectively attenuate or block low energy rays during X-ray imaging.

[0039] The motorized control 260 is configured to provide the motion for imaging and automatically capture the correct image. The motorized control 260 may provide mechanical alignment of the ring to the patient P. The sensor 280 is configured to sense position data and to enable positioning of the patient P relative to the imaging ring 270.

[0040] The controller 290 is configured to control the output x-ray source 34 (FIG. 4). The controller 290 may include any type of suitable processor, such as, but not limited to, a digital signal processor, a microprocessor, an ASIC, a graphics processing unit (GPU), a field programmable gate array (FPGA), or a central processing unit (CPU). The controller 290 may include memory for executing instructions that cause the system to perform various functions.

[0041] The imaging ring 270 is moved along the z-axis or length of the patient P to capture images with a sufficient field of view through the motorized track 250. The motorized track 250 has a range of motion that is greater than the desired image field of view, but less than the full length of the patient P's body. The motorized track 250 is used when the field of view requirement is greater than the field of view provided by the x-ray detector 36. The motorized control 260 can enable a combination of motions to position the imaging ring 270 in an optimal orientation relative to the patient P. The motorized control 260 can handle motions in the xy plane through a combination of motions in the x-direction and one or more of the angular directions θ, ψ, and Φ, the axes of motion being shown in FIG. 3. The imaging ring 270 includes a sufficient number of x-ray sources 34 to meet the power requirements of the desired scan and has a sufficient angular range to be considered as a computed tomography by both the x-ray sources and the x-ray detector 36. One or more anti-scatter grids 16 (FIG. 4) are configured to reduce x-ray scatter. The anti-scatter grid 16 may be dynamic or movable to adjust based on which x-ray source is currently operating. Finally, a sensor 280, such as a camera, may be used to optimally position the imaging ring relative to the patient P.

[0042] This design change is made possible by using "static" imaging for 3D imaging, where multiple x-ray sources 34 illuminate a detector array consisting of x-ray detector elements 36 that are larger than the field of view of the individual x-ray sources 62; an example of a static CT layout is shown in FIG. 4. This system replaces a single x-ray tube and the detector array is moved relative to the patient, which requires strong mechanical support to move components that are generally heavier than 1000 kg. The elimination of movement, multiple components, and the difference in size and weight of the x-ray sources allows the x-ray imaging system to be split into smaller components. This design change allows multiple x-ray systems to utilize a common base unit, reducing the cost, size, weight, and footprint of the overall combined system, and allowing for greater portability by requiring only parts of the system to be transported at one time. The base unit can be transported to a location that already has application-specific modules installed, or alternatively, new application-specific modules can be brought in if additional capacity is required.

[0043] A computed tomography system can be realized using this system design that benefits from the modularity or separation of the individual components and the reduction in overall weight of the application-specific modules. The modularity and separation of the individual components allows the system to be transported in separate parts that can be moved more easily and in smaller vehicles. The reduction in weight allows for a convertible CT that can operate as a vertically oriented CT (FIG. 5) or a horizontally oriented CT (FIG. 1), scanning at a conventional lateral angle or at an angle θ between the vertical and lateral directions.

[0044] Operation as a vertical CT allows the operator to save on footprint since the room no longer needs to support the length of the patient, thus saving on room and CT bed area costs. While the CT is operating in a traditional lateral configuration, the X-ray transparent table 240 supports the patient with the table supported by at least two points, each in a different half of the table with an opening for the region of interest for imaging. A table with two support points is made possible by the fact that the bed does not need to accommodate patient movement relative to the ring, can be portable in form factor (e.g., folded), can support more weight, and is less expensive.

[0045] Referring to FIG. 6, a diagram illustrating an example of a mobile screening system 600 is shown. The mobile screening system 600 may include a truck and a mammography 610 and / or a computed tomography system 620. The mobile screening system 600 includes two or more imaging modalities. The mobile screening solution comprises a vehicle (e.g., a truck or a bus) that includes an X-ray imaging device, additional equipment, and a shield. The mobile screening system has the advantage of reducing the overall cost of ownership of the system, which is a key challenge for performing mobile medical imaging. Another advantage of a mobile screening system with two or more imaging modalities such as the one described is that 1) the mobile screening system improves the profitability of the operator by up to 40% by saving personnel, hardware, and / or maintenance costs, 2) the mobile screening system improves patient convenience by allowing patients to be screened for more than one disease, and 3) the mobile screening system reduces the overall infrastructure required to maintain (one bus vs. the total number of individual buses). The modular X-ray imaging system 10 may be used as an upright and modular CT system in accordance with the present disclosure. The upright and modular CT systems can be used for mobile screening (Figure 6) and / or fixed screening.

[0046] Stationary CT systems break the traditional trade-off between the rotation speed of the x-ray tube and detector pair around the gantry compared to the patient imaging speed. This requires the gantry to rotate at an increasing speed for reduced detector size or increased scanning speed. Stationary CT's electronic rastering allows the rotation of the "gantry" to be orders of magnitude faster compared to conventional CT, enabling faster scanning with smaller detectors and saving costs or allowing higher throughput imaging for the same system specifications.

[0047] FIG. 7 is a diagram of an inverse geometry computed tomography for use in the system of FIG. 1. The disclosed technology provides a geometric layout to fix the fundamental tradeoff between detector size and field of view, which is the use of inverse geometry imaging, where multiple x-ray sources illuminate different areas of the desired image onto a smaller detector, and the images are stitched together to form the desired field of view. This fundamentally changes the cost equation for building any x-ray imaging system. For CT systems: the cost of the x-ray source module and detector area should be optimized for a given field of view. Inverse geometry x-ray imaging can be used for 2D x-ray imaging or tomosynthesis and computed tomography, and shows clear advantages such as reduced dose, improved image quality by reducing cone beam artifacts, and reduced detector size required for a given field of view, thereby reducing detector cost. The reduction in cost and detector area can also be used to offset other increases in cost, such as more expensive detectors that are photon energy sensitive or have improved spatial resolution, as well as other systems inverse geometry, such as stationary CT or CT performed without moving parts. The disclosed technique offers advantages over previous demonstrations of inverse geometry systems in which a single vacuum chamber was used with multiple x-ray sources integrated together, creating the challenges listed above. In FIG. 7, an array of x-ray sources illuminates a small detector that captures a portion of the field of view. A complete field of view is formed when all x-ray sources illuminate the detector, and images are stitched together. The array of x-ray sources and the detector rotate synchronously with each other, and images are taken at every angle theta.

[0048] The disclosed technology provides a solution for effectively implementing inverse geometry by generating high performance, compact, and inexpensive x-ray sources. High x-ray flux and fast on / off times (less than about 100 μs) are required for the main challenges of high performance CT and inverse geometry CT. A tight x-ray source pitch is necessary to minimize the size of the detector because x-ray images must overlap to obtain the desired x-ray flux in a particular region of the image. Finally, the cost of each source must be low to favor cost optimization between x-ray source and detector size. These characteristics are addressed in the disclosed technology.

[0049] 8-10, a subsystem X-ray source module 800 is shown. The subsystem X-ray source module 800 generally includes multiple individually packaged X-ray sources 810 with one or more focal spots, one or more filters 820, collimators 830, and / or X-ray source alignment devices 840. Each X-ray source 810 includes two types of connections: an electrical connection between the emitter and gate of a field emission electron source 860 with a controller, and an electrical connection between a high voltage power supply 850 (e.g., voltages greater than about 10 kVolts) and an anode designed to accelerate electrons to generate X-rays through Bremsstrahlung. Bremsstrahlung is electromagnetic radiation produced by the deceleration of a charged particle when deflected by another charged particle, typically an electron by an atomic nucleus. The X-ray source may have a physical or electronic indicator 870 to indicate to an operator if the X-ray source needs to be replaced. The connection to the anode may also carry a coolant to actively remove heat generated from electrons colliding with the anode. Individualized x-ray sources 810 (e.g., x-ray tubes) and their components are repeated to form the array of x-ray sources required for inverse geometry CT. These individual components are then interconnected through high voltage and cooling interconnects 900 and a common low voltage connection 880 (FIG. 9). These connections are through a common high voltage and cooling output and a common low voltage connection to a leak-proof outer case or chassis 890 (FIG. 10).

[0050] 9 and 10, the entire subsystem X-Ray source module 800 may be electrically isolated by immersing the connections and the X-Ray source in an insulating dielectric fluid. This fluid and all subcomponents are contained through a leak-proof outer case that drains and fills the subsystem module with the dielectric fluid, provides electrical connections between the X-Ray source, controller, and high voltage power supply, and makes one or more connections to provide the insulating dielectric fluid for cooling the anode.

[0051] FIG. 11 shows a block diagram of the connections between the subsystem X-Ray module 800 and other subsystems such as a high voltage supply 920 (greater than about 10 kilovolts), a cooling pump 830, and a controller 840.

[0052] Multiple x-ray source subsystems 800 may be located on the same system and connected to one or more high voltage power supplies 820, cooling pumps 830, and a controller 840. By utilizing multiple x-ray source subsystems 800, the speed of movement for the system 800 may be eliminated for stationary imaging or reduced for conventional CT reducing the mechanical engineering requirements for such a system 800. The controller 840 is configured to independently control each x-ray source 810. Each x-ray source 800 has an independent calibration profile that is applied to both the x-ray source and detector images. The calibration ensures that each x-ray source 810 is outputting the proper dose, and the detector side calibration mitigates any minor misalignment between the x-ray source 810 and the detector. The proper dose may be determined using a scout x-ray image or using other sensors that provide the necessary information to estimate the overall dose. The cumulative x-ray flux emitted by the x-ray source 810 is dynamic as a function of both position and time. The x-ray flux profile can be adjusted by changing the power of each x-ray source 810 or the amount of time each x-ray source 810 is on.

[0053] Particular embodiments of the present disclosure may include some, all, or none of the above advantages and / or one or more other advantages that will be readily apparent to one of ordinary skill in the art from the drawings, descriptions, and claims contained herein. Moreover, although certain advantages are recited above, various embodiments of the present disclosure may include all, some, or none of the recited advantages and / or other advantages not specifically recited above.

[0054] The aspects disclosed herein are examples of the present disclosure and may be embodied in various forms. For example, although a particular aspect of the present disclosure is described as a separate aspect, each of the aspects of the present disclosure may be combined with one or more of the other aspects of the present disclosure. The specific structural and functional details disclosed herein should be interpreted as non-limiting, as a basis for claims, and as a representative basis for teaching a person skilled in the art to employ the present disclosure in substantially any appropriately detailed structure. Similar reference numbers may refer to similar or identical elements throughout the description of the drawings.

[0055] The phrases "in an aspect," "in aspects," "in various aspects," "in some aspects," or "in other aspects" can each refer to one or more of the same or different example aspects provided in this disclosure. A phrase in the form "A or B" means "(A), (B), or (A and B)." A phrase in the form "at least one of A, B, or C" means "(A), (B), (C), (A and B), (A and C), (B and C), or (A, B and C)."

[0056] It should be understood that the foregoing description is merely illustrative of the present disclosure. Those skilled in the art may devise various alternatives and modifications without departing from the present disclosure. Accordingly, the present disclosure is intended to embrace all such alternatives, modifications, and variations. The embodiments described with reference to the accompanying drawings are presented only to illustrate specific examples of the present disclosure. Other elements, steps, methods, and techniques that are substantially different from those described above and / or in the appended claims are also intended to be within the scope of the present disclosure.

[0057] Although several embodiments of the present disclosure are shown in the drawings, it is not intended that the disclosure be limited thereto, as the disclosure is within the scope of the art and the specification is intended to be read in the same manner. Therefore, the above description should not be interpreted as limiting, but merely as exemplifications of particular embodiments. Those skilled in the art will envision other modifications within the scope and spirit of the claims appended hereto.

Claims

1. 1. A modular x-ray imaging system comprising: an application specific module including an imaging ring, a sensor, a motor, and a controller configured to image a patient; a base unit in communication with the application specific module; a mechanical support configured to support the imaging ring; Including, The imaging ring is a plurality of x-ray sources configured to generate and emit beams comprising an x-ray spectrum; one or more collimators configured to limit the span of the x-ray beam; one or more filters configured to selectively attenuate and / or block low energy radiation during x-ray imaging; one or more x-ray detectors configured to detect x-rays produced by the plurality of x-ray sources; Including, the sensor is configured to provide positioning data to enable positioning of the imaging ring relative to the patient; the motor is configured to position the imaging ring based on a sensed position; the controller is for controlling an output of the plurality of X-ray sources; The base unit includes: a first power supply having an output voltage greater than 10 kV; a second power supply having an output voltage less than 10 kV configured to turn on and off each individual X-ray source of the plurality of X-ray sources; A processor; a memory containing stored instructions; Including, The instructions, when executed by the processor, cause the modular X-ray imaging system to position the imaging ring based on the sensor and capture imaging data.

2. the base unit further includes a battery; 2. The x-ray imaging system of claim 1, wherein the base unit is configured to operate solely on battery power with a portion of the battery being able to be changed during operation to maintain battery power longer than the total capacity of the battery.

3. The x-ray imaging system of claim 1 , wherein the base unit is configured to move independently of the remainder of the x-ray imaging system.

4. The X-ray imaging system of claim 1 , wherein the base unit is configured to simultaneously connect to, control and power multiple application-specific modules.

5. 10. The X-ray imaging system of claim 1, further comprising a second application-specific module configured to provide a convertible computed tomography (CT) that can operate vertically or laterally and at any angle in between.

6. The X-ray imaging system of claim 1 , wherein the application specific module is operated as at least one of a vertical CT or a horizontal CT.

7. 6. The X-ray imaging system of claim 5, wherein when operating in a lateral direction, the system further comprises an X-ray transmission table configured to support a patient with the X-ray transmission table supported by at least two points in different halves of the table, each of which has an opening for a region of interest for imaging.

8. The second application specific module comprises: An electric control unit; an imaging ring including a controller, a plurality of x-ray sources, one or more anti-scatter grids, an x-ray detector, and communication electronics; a motorized track configured to move the motorized control and the imaging ring; a sensor configured to determine a positioning of the imaging ring relative to the patient; Further comprising: The x-ray imaging system of claim 5 , wherein the motorized control provides mechanical alignment of the imaging ring to the patient.

9. The X-ray imaging system of claim 8 , wherein the motorized truck is configured to move the second application-specific module a distance that is greater than a desired imaging field of view and less than a total body length of the patient.

10. The x-ray imaging system of claim 8 , wherein the motorized track is configured to rotate about an axis perpendicular to a surface in contact with the mechanical support to change direction of motion.

11. The electric control unit is The X-ray imaging system of claim 8 , further configured to control movement of the imaging ring in an xy-plane of the patient using at least one linear degree of motion or at least one angular degree of freedom.

12. 10. The x-ray imaging system of claim 1, further comprising at least one of a dynamic anti-scatter grid or a moving anti-scatter grid having multiple x-ray sources to optimally eliminate scatter for each x-ray source.

13. The X-ray imaging system of claim 1 , wherein the application-specific module is configured to be adjusted in height and / or rotation relative to a normal to a mounting surface of the application-specific module.

14. A data acquisition system; at least one of a wired or wireless connection between the application specific module and the base unit; Further comprising: At least one of the wired connection unit and the wireless connection unit is at least one high voltage connection, greater than 10 kV, configured to connect the first power source to the application specific module; At least one low voltage connection less than 10 kV; Including, 9. The X-ray imaging system of claim 8, wherein the at least one low voltage connection is configured to connect between the power source configured to power the motor, the second power source, and the processor to the application-specific module to provide communication between a control unit of the X-ray source, the data acquisition system, and the sensor that controls the positioning of the application-specific module.

15. 1. An X-ray source alignment apparatus comprising: an imaging ring including a plurality of individually packaged x-ray sources configured to emit a beam including an x-ray spectrum; a sensor configured to provide positioning data to enable positioning of the imaging ring relative to a patient; a motorized control configured to provide mechanical alignment of the imaging ring to the patient based on the positioning data; a motorized track configured to move the motorized control and the imaging ring based on the positioning data; 1. An X-ray source alignment apparatus comprising:

16. 16. The x-ray source alignment apparatus of claim 15, wherein the plurality of individually packaged x-ray sources includes at least one focal spot configured for imaging.

17. 20. The x-ray source alignment apparatus of claim 16, wherein the plurality of individually packaged x-ray sources further comprises a filter configured to reduce intensity of one or more wavelengths from the x-ray spectrum.

18. 20. The x-ray source alignment apparatus of claim 17, wherein the plurality of individually packaged x-ray sources further comprises a collimator configured to direct the x-ray beam.

19. The x-ray source alignment device of claim 14 further comprising a second sensor configured to determine a positioning of the imaging ring relative to the patient.

20. 1. A modular x-ray imaging system comprising: Application-specific modules; a base unit configured to communicate with and power the application-specific module; Mechanical support and Including, The application specific module comprises: a vertically positionable imaging ring configured to image the patient; A processor; a memory containing stored instructions; Including, The instructions, when executed by the processor, cause the modular x-ray imaging system to position the imaging ring and capture imaging data; the mechanical support is configured to support the vertically positionable imaging ring; A modular X-ray imaging system, wherein the base unit and application-specific modules are configured to communicate in at least one of a wired and / or wireless manner.

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