Compact X-ray devices, systems and methods for tomosynthesis, fluoroscopy and stereotactic imaging

Abstract

Compact x-ray devices, systems and methods for capturing in tomosynthesis, two-dimensional radiography, fluoroscopy and stereotactic imaging modes. In some embodiments, a compact x-ray imaging system includes an x-ray source array including spatially distributed x-ray foci; and a digital area x-ray detector. In some embodiments, the imaging system includes an electronic switching device configured to cycle the imaging modes of the system. In some embodiments, the imaging system includes a mechanical support configured to enable the position and orientation of the x-ray source array and the digital area x-ray detector to be adjusted so that the patient's upper and lower extremities can be imaged using various imaging modes while the positions of the multiple spatially distributed x-ray foci remain unchanged relative to the position of the digital area x-ray detector.

Description

[0001] CROSS-REFERENCE TO RELATED APPLICATIONS

[0002] This application claims priority to U.S. Provisional Patent Application Serial No. 62 / 774,649, filed on December 3, 2019, the entire disclosure of which is incorporated herein by reference. Technical Field

[0003] The subject matter disclosed herein relates to x-ray imaging. More particularly, the subject matter disclosed herein relates to a compact x-ray imaging system that can perform multiple functions, including digital tomosynthesis, fluoroscopy, and stereotactic imaging. Background Art

[0004] Trauma to the extremities (e.g. wrist, ankle or limbs) is very common and affects all populations. It constitutes a major public health problem. Standard radiography remains the fundamental imaging tool. However, as a two-dimensional (2D) imaging modality, it lacks sensitivity and specificity. It is well known that the misdiagnosis rate is high, especially for non-displaced fractures of the navicular and talus and erosions caused by rheumatoid arthritis.

[0005] Misdiagnosis leads to overtreatment and unnecessary loss of productivity and quality of life, including being in an immobilization dressing for 6-12 weeks. A missed fracture may result in chronic, nonunion fractures and / or early arthritis of the joint that may require surgery.

[0006] Fractures occult to radiography often result from obscuration by adjacent anatomical structures. Obscuration can be reduced by three-dimensional (3D) imaging modalities. Computed tomography (CT), magnetic resonance imaging (MRI), SPECT / CT, and bone scanning are known to have better specificity and sensitivity than radiography, but these methods are more expensive and generally unavailable. Only 14% of emergency care centers offer CT scanning, however, 80% of emergency care centers offer fracture care. CT scanning also exposes patients to a much higher radiation dose than 2D radiography. Bone scanning increases radiation exposure from radionuclide injection and cannot be performed until more than 72 hours after fracture.

[0007] Arthritis is a disease with high morbidity and socioeconomic costs. Rheumatoid arthritis (RA) is an autoimmune disease affecting 1.0% of the global population, with women being affected more frequently than men. It is characterized by a proliferative, highly vascularized synovitis leading to bone erosions, cartilage damage, joint destruction and long-term disability. Osteoarthritis (OA) is a chronic, debilitating disease of the joints characterized by degenerative changes in bone, cartilage, menisci, ligaments and synovial tissues and is the fourth largest source of non-fatal health burden, living with disability accounting for 3% of total life expectancy.

[0008] Radiography has traditionally been used for the diagnosis, staging and follow-up of patients with arthritis, as well as for assessing the effectiveness of treatment in individual patients. The main advantages of radiography are short examination time, low cost and easy access. However, there are also considerable disadvantages, such as low sensitivity for detecting bone erosions, especially in patients with early arthritis. The detectability of pathological findings is limited by the overlap of structures, as three-dimensional (3D) structures are projected into 2D images in radiography.

[0009] Tomosynthesis is a quasi-3D imaging modality that uses a series of limited-angle projection images to produce a 3D representation of the scanned object. It provides depth information and eliminates structural overlap at roughly the same cost as CT and with significantly lower radiation dose. It is now widely used clinically for breast cancer detection with significantly higher sensitivity and accuracy than digital mammography.

[0010] Several recent scientific studies have shown that tomosynthesis is superior to x-ray radiography for orthopedic imaging. In a clinical study of 30 RA patients, it was found that the sensitivity for detecting bone erosions in the hand and wrist was increased by about 20% when using tomosynthesis compared with radiography, with only a relatively small increase in radiation dose compared with radiography. For patients with early RA, the median erosion score was significantly higher when tomosynthesis was performed on the hand and wrist compared with radiography. In a separate clinical study of 100 patients with acute wrist trauma, it was found that "the diagnostic value of tomosynthesis was superior to that of standard radiography" (emphasis added) (M. Ottenin, A. Jacquot, O. Grospretre et al., "Evaluation of the diagnostic performance of tomosynthesis in wrist fractures", American Journal of Roentgenology, 198: 180-186 (2012)).

[0011] The study further concluded that tomosynthesis has a role to play in the diagnosis of fractures of the wrist alongside standard radiography due to its low cost, extremely low levels of radiation required, its speed, and efficient integration into the workflow. Specifically for scaphoid fractures, it provides a more reliable diagnosis and reduces the need for other expensive imaging methods.

[0012] Figure 1A commercially available tomosynthesis scanner 100 is shown. An exemplary tomosynthesis scanner 100 acquires projection images required for reconstruction by mechanically moving a large single beam x-ray tube 110 mounted on a motorized arm 120 over a long distance while performing x-ray exposure. Due to the movement of the tube, currently available tomosynthesis scanners 100 obtain images with fuzzy spatial resolution and detection sensitivity is lower than the sensitivity that the mode can inherently provide. In addition, tomosynthesis scanners 100 are large and require a dedicated imaging room. An example of an indoor tomosynthesis scanner is the VolumeRAD scanner commercially available from General Electric (GE). The device uses a rotating anode x-ray tube 110 mounted on a motorized arm 120 to scan an angular span of approximately 40 degrees, during which approximately 60 projection images are taken. An area detector (such as, for example, a flat panel detector) is placed behind the patient. Typical source-to-imager distances are between and including approximately 100 cm and 180 cm.

[0013] C-arm and mini C-arm 2D fluoroscopy devices are used for image guidance during plastic surgery. Fluoroscopy devices use x-ray radiation from a single focal point to form a 2D image. It operates in either continuous or pulsed mode. In continuous fluoroscopy mode, the x-ray radiation is always on and the image is typically displayed at 30 frames per second. In pulsed fluoroscopy mode, the x-ray radiation is emitted in pulses and the image is typically displayed at 15 frames per second. This is compared to about 100cm-180cm for a conventional C-arm, such as Figure 2 The miniature C-arm device shown has a small source to imager distance, typically on the order of about 40 cm.

[0014] An example of a commercially available miniature C-arm fluoroscopy device is the Fluoroscan InSight Mini C-arm Extremities Imaging System. The miniature C-arm is attractive for clinical applications for a number of reasons. It takes up less space, which is valuable in overcrowded operating rooms. It is mobile and can be easily manipulated. In addition, the shorter source-to-imager distance shown reduces scattered radiation to the operator.

[0015] In order to achieve a certain resolution at a reduced source-to-imager distance, a micro-c-arm device typically uses a micro-focus x-ray tube operating at a low tube current. For example, a fluorescent scanning endoscopy micro-c-arm system uses an x-ray tube having a focal spot size of about 0.045 mm, a tube peak kilovolt range between about 40 kVp and 75 kVp, and a tube current between about 0.02 mA and 0.1 mA. It has a maximum output of about 0.1 mA at 75 kVp. The detector pixel size is about 0.075 mm x 0.075 mm.

[0016] However, there are currently no miniature C-arm imaging devices that can perform both fluoroscopic imaging and tomosynthesis imaging simultaneously. While this could in principle be achieved by mechanically rotating the x-ray tube along the C-arm or mechanically rotating the x-ray tube and detector pair, there are several technical limitations that make this approach infeasible. In particular, in order to complete a tomosynthesis scan within a clinically acceptable time and cover reasonable angular scans, the x-ray focus motion blur would have to be an order of magnitude larger than the intrinsic focus size of the microfocus x-ray tube, which severely degrades the imaging quality. Summary of the invention

[0017] The subject matter of the present application discloses a compact x-ray device that can perform tomosynthesis imaging, fluoroscopy imaging, and stereotactic imaging at high resolution at the point of care in orthopedic and radiology clinics. As non-limiting examples, some contemplated uses of the device disclosed below include diagnostic and interventional imaging of human limbs in orthopedic and radiology clinics. It is contemplated that the device disclosed herein can be used for other imaging applications, including veterinary imaging.

[0018] According to the present disclosure, a system and method for compact x-ray imaging are provided. On the one hand, a compact x-ray imaging system is provided. In some embodiments, the compact x-ray imaging system includes an x-ray source array and a digital area x-ray detector, the x-ray source array including a plurality of spatially distributed x-ray focal spots; a collimation assembly connected to an exit window of the x-ray source array, the collimation assembly configured to substantially collimate x-ray radiation generated from each of the plurality of spatially distributed x-ray focal spots to a surface of the digital area x-ray detector; an electronic switching device, comprising: a high voltage power supply, a current source, a switch (which is configured to sequentially connect the current source to a plurality of field emission cathodes of the compact x-ray imaging device one at a time at a preset current value, so as to achieve the desired effect without requiring the x-ray source array or the digital area x-ray detector to be used. The compact x-ray imaging system comprises a first processor and / or circuit configured to synchronize detector data acquisition with x-ray exposure from a plurality of spatially distributed x-ray foci; and a mechanical support configured to enable the position and orientation of an x-ray source array and a digital area x-ray detector to be adjusted so that tomosynthesis can be used to image an upper and lower extremity of a patient in a non-load-bearing position or a load-bearing position; wherein the compact x-ray imaging system is configured to operate in multiple imaging modes.

[0019] In some embodiments, the compact x-ray imaging system is configured to operate in a tomosynthesis imaging mode or a pulsed fluoroscopy mode.

[0020] In some embodiments, the compact x-ray imaging system is configured such that, when the x-ray imaging device is operated in a tomosynthesis imaging mode, a scanning x-ray beam is electronically generated by sequentially activating x-ray beams from a plurality of spatially distributed x-ray focal spots without moving an x-ray source array, a digital area x-ray detector, or a patient so as to acquire one or more desired projection images for tomosynthesis reconstruction; and the compact x-ray imaging system is configured such that, when the x-ray imaging device is operated in a pulsed fluoroscopy imaging mode, x-ray radiation generated from a central focus of the plurality of spatially distributed x-ray focal spots is pulsed at approximately 5 to 30 pulses per second, and for each x-ray pulse, an image of the scanned object is formed and displayed to produce an x-ray image of the object.

[0021] In some embodiments, the compact x-ray imaging system is configured to operate in a stereotactic mode.

[0022] In some embodiments, the compact x-ray imaging system is configured such that when the x-ray imaging device is operated in a stereotactic mode, two discrete focal spots among a plurality of spatially distributed x-ray focal spots are activated to emit x-ray radiation, resulting in the formation and display of two projection images from two different angles.

[0023] In another aspect, a method for performing x-ray imaging using a compact x-ray imaging device is provided. In some embodiments, the method includes: providing an x-ray source array having a plurality of spatially distributed x-ray focal spots and a digital area x-ray detector; using a collimation assembly connected to an exit window of the x-ray source array, substantially collimating x-ray radiation generated from each of the plurality of spatially distributed x-ray focal spots to a surface of the digital area x-ray detector; providing an electronic switching device including: a high voltage power supply, a current source, a switch, and a trigger including one or more first processors and / or circuits; positioning and orienting the x-ray source array and the digital area x-ray detector to adjust to enable tomosynthesis in a non-load bearing position The invention relates to a method of imaging an upper limb and a lower limb of a patient in a compact x-ray imaging device and a load-bearing position while the positions of multiple spatially distributed x-ray foci remain unchanged relative to the position of a digital area x-ray detector; sequentially connecting current sources to multiple field emission cathodes of a compact x-ray imaging device one at a time at preset current values ​​to produce one or more projection images for tomosynthesis reconstruction without requiring any mechanical movement of the x-ray source array or the digital area x-ray detector; and synchronizing detector data acquisition with x-ray exposure from the multiple spatially distributed x-ray foci; wherein the compact x-ray imaging system is configured to operate in multiple imaging modes.

[0024] On the other hand, a miniature C-arm X-ray imaging system is provided. In some embodiments, the miniature C-arm X-ray imaging system includes a carbon nanotube-based microfocus X-ray source array and a digital area X-ray detector mounted on the miniature C-arm, wherein the carbon nanotube-based microfocus X-ray source array includes a plurality of spatially distributed microfocus X-ray focal spots; a collimation assembly connected to an exit window of the microfocus X-ray source array, wherein the collimation assembly is configured to substantially collimate X-ray radiation generated from each of the plurality of spatially distributed microfocus X-ray focal spots to a surface of the digital area X-ray detector; and an electronic switching device, which includes: a high voltage power supply, a current source, a switch, and a trigger, wherein the switch is configured to be switched at a preset voltage. A trigger is provided for sequentially connecting current sources, one at a time, to multiple field emission cathodes of a miniature C-arm x-ray imaging device to produce one or more projection images for tomosynthesis reconstruction without requiring any mechanical movement of a microfocused x-ray source array or a digital area x-ray detector, the trigger comprising one or more processors and / or circuits configured to synchronize detector data acquisition with x-ray exposure from multiple spatially distributed microfocused x-ray foci; wherein the miniature C-arm x-ray device is configured to operate in a three-dimensional tomosynthesis imaging mode, a fluoroscopy mode, or a stereotactic mode.

[0025] In another aspect, a method for performing x-ray imaging using a miniature c-arm x-ray imaging system is provided. In some embodiments, the method includes: providing a miniature C-arm x-ray imaging system having a carbon nanotube-based microfocus x-ray source array having a plurality of spatially distributed microfocus x-ray focal spots and a digital area x-ray detector mounted on the miniature C-arm; substantially collimating x-ray radiation generated from each of the plurality of spatially distributed microfocus x-ray focal spots onto a surface of the digital area x-ray detector using a collimation assembly connected to an exit window of the microfocus x-ray source array; providing an electronic switching device including: a high voltage power supply, a current source, a switch, and a trigger including one or more processors and / or circuits; sequentially connecting the current source to a plurality of field emission cathodes of the miniature C-arm x-ray imaging device one at a time at a preset current value to generate one or more projection images for tomosynthesis reconstruction without requiring any mechanical movement of the microfocus x-ray source array or the digital area x-ray detector; and synchronizing detector data acquisition with x-ray exposure from the plurality of spatially distributed microfocus x-ray focal spots; wherein the miniature C-arm x-ray device is configured to operate in a three-dimensional tomosynthesis imaging mode, a fluoroscopy mode, or a stereotactic mode.

[0026] While certain aspects of the presently disclosed subject matter have been set forth above and may be achieved in whole or in part by the presently disclosed subject matter, other aspects will become apparent when described in conjunction with the accompanying drawings, as best described hereinafter. BRIEF DESCRIPTION OF THE DRAWINGS

[0027] The features and advantages of the present subject matter will be more readily understood from the following detailed description, which should be read in conjunction with the accompanying drawings, which are given by way of illustrative and non-limiting examples only, in which:

[0028] Figure 1 is a schematic diagram of a conventional commercially available tomosynthesis scanner;

[0029] Figure 2 is a schematic diagram of a conventional miniature C-arm X-ray imaging device according to commercially available equipment;

[0030] Figure 3A , Figure 3B , Figure 3C , Figure 3D is a schematic diagram of an exemplary x-ray imaging system according to some embodiments of the present disclosure;

[0031] 4A and 4B are schematic diagrams of a curved carbon nanotube (CNT) x-ray source and a linear shaped CNT x-ray source;

[0032] Figure 5 is a schematic diagram of a movable miniature C-arm x-ray imaging system according to some embodiments of the present disclosure;

[0033] Figure 6 and Figure 7 is a schematic diagram of an exemplary arrangement of various components of an x-ray imaging system according to some embodiments of the present disclosure;

[0034] Figure 8 shows a simulation performed to demonstrate the system resolution of an exemplary x-ray imaging system of some embodiments of the present disclosure;

[0035] Fig. 9 is a schematic diagram of an exemplary desktop x-ray imaging system according to another embodiment of the present disclosure;

[0036] Fig. 10A shows an exemplary projection image captured by a conventional imaging system that does not capture the same detail as systems and devices according to some embodiments of the present disclosure. Fig. 10B shows a reconstructed slice image captured by the apparatus of the present disclosure; and

[0037] Fig.11A and Fig. 11BExemplary tomosynthesis reconstructed slice images captured at various aspects by an exemplary system of the present disclosure are shown. DETAILED DESCRIPTION

[0038] The subject matter of the present disclosure includes compact x-ray devices for imaging at the point of care in non-limiting examples. The devices disclosed herein can be used for a variety of functions. They can be used for diagnostic tomosynthesis imaging, providing functions similar to large indoor tomosynthesis devices, but with a smaller footprint (i.e., taking up less physical space in the examination room / operating room). The devices of the present disclosure can also be used for interventional purposes, providing image guidance for surgery and other procedures. In some embodiments, the devices can be used in tomosynthesis imaging mode, 2D radiography mode, fluoroscopy mode, or stereotactic mode.

[0039] Figure 3A One possible embodiment of the subject matter disclosed herein is shown. In some embodiments, the x-ray imaging device 300 shown in FIG. 3 is a compact x-ray tomosynthesis device, including an x-ray source array 310 and a digital area x-ray detector 320, the x-ray source array including a plurality of spatially distributed x-ray focal spots (not shown in this view). In some embodiments, as a non-limiting example, the digital area x-ray detector 320 is positioned opposite and parallel to the x-ray source array 310 to record an image. In some embodiments, the x-ray imaging device 300 includes a beam limiting device or collimation assembly (not shown in this view) connected to an exit window of the x-ray source array 310. In some embodiments, the collimation assembly is configured to substantially collimate the x-ray radiation generated from each of the plurality of spatially distributed x-ray focal spots to a surface of the digital area x-ray detector 320. In some embodiments, for example and without limitation, the digital area x-ray detector 320 can be a flat-panel type area detector.

[0040] In some embodiments, the plurality of spatially distributed x-ray foci includes two spatially distributed x-ray foci, or more than two spatially distributed x-ray foci. In some embodiments, each of the plurality of spatially distributed x-ray foci is micro-focused, having a spot size between about 0.01 mm and 0.3 mm and including about 0.01 mm and 0.3 mm. For example, but not limited to, in some embodiments, the spot size of each of the foci may be between about 0.1 mm and 0.2 mm and including about 0.1 mm and 0.2 mm. For example, but not limited to, in some embodiments, the spot size of each of the foci may be about 0.1 mm. In some embodiments, at least one of the plurality of spatially distributed x-ray foci is micro-focused, having a spot size between about 0.01 mm and 0.3 mm and including about 0.01 mm and 0.3 mm. In some embodiments, the plurality of spatially distributed x-ray foci are positioned in a plane substantially perpendicular to the plane in which the digital area x-ray detector 320 is positioned. In some embodiments, the plurality of spatially distributed focal spots of the x-ray source array are positioned in a plane that is substantially parallel to the plane in which the digital area x-ray detector 320 is positioned.

[0041] To electronically generate the scanning x-ray beam, in some embodiments, the x-ray imaging device 300 further includes an electronic switching device 330, which includes: a high voltage power supply, a current source, and a switch. In some embodiments, the high voltage power supply and the current source are configured to supply power to the x-ray imaging device 300, including supplying power to the x-ray source array 310. In some embodiments, the switch is configured to sequentially connect the current source to one or more field emission cathodes of the x-ray source array 310. In some embodiments, the current source is sequentially connected to one or more field emission cathodes of the x-ray source array 310 one at a time at a certain preset current value, the preset current value being between about 0.05 mA and 20 mA and including about 0.05 mA and 20 mA, to generate one or more projection images for tomosynthesis reconstruction without requiring any mechanical movement of the x-ray source array 310 or the digital area x-ray detector 320.

[0042] In some embodiments, the electronic switching device 330 further comprises a trigger or triggering mechanism to synchronize detector data acquisition with x-ray exposure from a plurality of spatially distributed x-ray foci. In some embodiments, as a non-limiting example, the trigger may comprise one or more first processors and / or circuits configured to synchronize detector data acquisition with x-ray exposure from a plurality of spatially distributed x-ray foci. In some embodiments, the electronic switching device 330 is configured to operate the high voltage power supply at more than one energy level during a single imaging sequence, such that projection images acquired at different anode energy levels may be combined to produce a contrast enhanced 2D radiographic image and / or a 3D tomosynthesis image.

[0043] In some embodiments, the x-ray imaging device 300 can be mounted on or secured to a movable cart 332. In some further embodiments, the x-ray imaging device 300 can include a mechanical support 334 configured to adjust the position and orientation of the x-ray source array 310 and the digital area x-ray detector 320 so that (for non-limiting example) tomosynthesis can be used to image the upper and lower extremities of a patient in a non-load bearing position or a load bearing position. In some embodiments, imaging can be performed while the positions of multiple spatially distributed x-ray foci remain unchanged relative to the digital area x-ray detector 320. In some embodiments, the x-ray imaging device 300 of the present disclosure is configured to operate in a tomosynthesis imaging mode, a pulsed fluoroscopy mode, or a stereotactic mode.

[0044] In some embodiments, the x-ray imaging device 300 includes one or more central processors configured to switch between imaging modes. In some embodiments, the central processor may be embedded in, or part of, or otherwise control the electronic switching device 330. For example, but not limited to, the x-ray imaging device 300 may include a processor that automatically or after receiving some input from a user switches imaging modes and controls the x-ray source array 310 and the digital area x-ray detector 320 and various other devices in the x-ray imaging device 300. In some embodiments, the central processor is configured to switch imaging modes between tomosynthesis imaging mode, 2D radiography mode, fluoroscopy mode, or stereotactic mode. In this regard, the central processor may be configured to control the x-ray source array 310 and the digital area x-ray detector 320 and various other devices according to the description herein.

[0045] In some embodiments, when the x-ray imaging device 300 is operated in a tomosynthesis imaging mode, a scanning x-ray beam is generated by sequentially and electronically activating x-ray beams from a plurality of spatially distributed x-ray focal spots without moving the x-ray source array 310, the digital area x-ray detector 320, or the patient (not shown in this view) to acquire all projection images required for tomosynthesis reconstruction. In an embodiment, this is achieved by connecting the current sources of the electronic switching device 330 to the field emission cathodes in the x-ray source array 310 one at a time at a preset current value, thereby generating x-ray radiation from the plurality of spatially distributed x-ray focal spots to produce projection images. In some embodiments, the preset current value is set to between and including about 0.05 mA and 20 mA.

[0046] In some embodiments, the x-ray imaging device 300 further includes one or more second processors, a non-transitory computer-readable medium, and a tomosynthesis image reconstruction algorithm configured to reconstruct the projection images into a stack of tomosynthesis images. In some embodiments, the x-ray imaging device 300 further includes an observation screen, such as a monitor 336, or other display that allows a user or physician to observe images generated by the x-ray imaging device. In some embodiments, for example but not limited to, to increase the speed of tomosynthesis reconstruction, the x-ray imaging device 300 includes a graphics processing unit (GPU). In some embodiments, the x-ray imaging device 300 includes a display, such as a monitor 336, or a separate display from the host computer, such as a graphics processing unit (GPU). Figure 3B Mount to the wall as shown or as Figure 3C Other screens are shown mounted on separate movable carts (as a non-limiting example).

[0047] refer to Figure 3A In some embodiments, when the x-ray imaging device 300 is operated in a 2D radiography mode, x-ray radiation generated from one or more of a plurality of spatially distributed x-ray foci is used to generate a single two-dimensional x-ray image or one or more two-dimensional fluoroscopy images.

[0048] In some embodiments, when the x-ray imaging device 300 is operated in a fluoroscopic imaging mode, preferably a pulsed fluoroscopic mode, x-ray radiation generated from one of a plurality of spatially distributed x-ray focal spots is used to generate a plurality of images. In some embodiments, the x-ray imaging device 300 is configured to pulse radiation originating from one x-ray focal spot. In some embodiments, a central x-ray focal spot among a plurality of spatially distributed x-ray focal spots is utilized, and the radiation beam is pulsed using the central focal spot. In some embodiments, an x-ray focal spot is pulsed at a rate ranging from about 5 to 30 pulses per second. In some embodiments, the central x-ray focal spot is pulsed at a pulse rate ranging from about 5 to 30 pulses per second. In some embodiments, for each x-ray pulse (relative to the central x-ray focal spot or another single x-ray focal spot), an image of the scanned object is formed and displayed to generate an x-ray image or x-ray video of the scanned object.

[0049] In some embodiments, when the x-ray imaging device 300 is operated in a stereotactic imaging mode, x-ray radiation from a plurality of discrete focal points in a plurality of spatially distributed x-ray focal points is used to form and display a plurality of projection images from a plurality of different viewing angles. In some embodiments, the stereotactic imaging mode uses two discrete focal points in a plurality of spatially distributed x-ray focal points to form and display two projection images from two different viewing angles. In some embodiments, mechanical movement of the x-ray source array 310 is not required. In some embodiments, the image produced when the x-ray imaging device 300 is operated in a stereotactic imaging mode may be, for example, but not limited to, a two-dimensional or three-dimensional image.

[0050] In some embodiments of the present disclosure, the x-ray source array 310 is an x-ray array based on carbon nanotubes (CNTs). The CNT x-ray source array uses an array of independently controllable CNT field emitters to generate electrons at room temperature, where the electrons are accelerated to bombard the anode to generate x-rays. In some embodiments of the present disclosure, the CNT field emitters are connected to an electronic switching device 330. By electronically switching the independent CNT cathodes on and off, a scanning x-ray beam can be generated from different viewing angles to collect multiple projection images required for tomosynthesis reconstruction without any mechanical movement. FIG. 4A shows an x-ray source operating using this principle. In some embodiments, such as, for example but not limited to, as shown in FIG. 4A, the CNT x-ray source array 310 can be arranged in a curved manner. However, in some embodiments, the CNT x-ray source array 310 is not necessarily shaped in a curved manner, but can be straight or linear. This straight or linear shape of the CNT x-ray source array 310 is shown in FIG. 4B. Furthermore, both CNT x-ray source arrays 310 depicted in FIGS. 4A and 4B may be commercially available, for example but not limited to, from XinRay Systems, LLC.

[0051] With CNTs, electrons are generated at room temperature using field emission. By applying a potential difference across a very sharp object, electrons can be generated at the tip of the sharp object. One requirement for x-ray imaging with modern x-ray tubes and CNTs includes focusing each electron source. With CNTs, field-emitted electrons are already partially focused during the emission process, and therefore smaller focusing structures are also required. In 2002, Zhou and colleagues demonstrated that CNTs can be used as effective field emitters for x-ray sources because of their atomically sharp tips and high mechanical stability. In addition, the required turn-on voltage is significantly reduced compared to existing attempts with diamond tips and tungsten tips. CNT x-ray sources can be positioned very close to allow the formation of multi-beam x-ray sources for various applications.

[0052] In some embodiments, the x-ray imaging device 300 of the present disclosure includes between about five and about sixty, and including, independently controllable CNT emitters as electron sources. In some embodiments, the x-ray source array has a monopole design. In some embodiments, the anode voltage of the x-ray source array has an anode voltage between about 0 kV and 120 kV, and includes about 0 kV and 120 kV, and the x-ray tube current is between about 0.05 mA and 20 mA, and includes about 0.05 mA and 20 mA. In some embodiments, the x-ray focus has a spatial distribution of a line, a circle, a 2D array, or any other 2D or 3D geometric structure configuration.

[0053] Figure 3DA more detailed example of the electronic switching device 330 is shown. In some embodiments, the electronic switching device 330 may include a high voltage power supply 340, a current source 342, a switch 344, a trigger including one or more first processors 346, one or more second processors 348, and a central processor 350, as described herein. In some embodiments, the high voltage power supply 340 is configured to provide power to various components of the x-ray imaging device 300 of the present disclosure, such as, but not limited to, the x-ray source array 310 and the digital area x-ray detector 320. In some embodiments, the current source 342 is configured to be connected to a plurality of field emission cathodes of the compact x-ray imaging device one at a time at a preset current value through the switch 344 to produce one or more projection images for tomosynthesis reconstruction without requiring any mechanical movement of the x-ray source array 310 or the digital area x-ray detector 320.

[0054] In some embodiments, the switch 344 is configured to connect the current source 342, as described herein. In some embodiments, a trigger including one or more first processors 346 is configured to synchronize detector data acquisition with x-ray exposure from multiple spatially distributed x-ray foci. In some embodiments, the one or more first processors 346 may be located in the electronic switching device 330 or in any other suitable portion of the x-ray imaging device 300, as described herein. In some embodiments, the one or more second processors 348 include a non-transitory computer-readable medium and a tomosynthesis image reconstruction algorithm configured to reconstruct the projection image into a stack of tomosynthesis images. In some embodiments, the one or more second processors 348 are configured to automatically register non-load bearing images and load bearing images to generate load-induced structural deformation / displacement of the patient's limb. In some embodiments, the one or more second processors 348 are configured to automatically register images before contrast injection and images after contrast injection to generate contrast-enhanced images of the patient's limb.

[0055] In some embodiments, the central processor 350 is configured to switch the x-ray imaging device 300 between imaging modes. In some embodiments, the central processor 350 may include a processor that automatically or after receiving some input from a user switches the imaging mode and controls the x-ray source array 310 and the digital area x-ray detector 320 and various other devices in the x-ray imaging device 300. In some embodiments, the central processor is configured to switch the imaging mode between a tomosynthesis imaging mode, a 2D radiography mode, a fluoroscopy mode, or a stereotactic mode. In this regard, the central processor may be configured to control the x-ray source array 310 and the digital area x-ray detector 320 and various other devices according to the description herein. In some embodiments, the central processor 350 may be connected or communicated with one or more first processors 346, one or more second processors 348, or any other various components to receive data to be displayed or output on a monitor 336 or other device. For example, but not limitation, one or more second processors 348 may be configured to process and reconstruct tomosynthesis images and send them to a central processor 350, which is configured to display the images on a monitor 336. Additionally, in some embodiments, detector 320 and any processor of x-ray imaging device 300 may send captured images (using any imaging mode) and send to central processor 350 for display on monitor 336.

[0056] Figure 5 Another embodiment of the miniature C-arm X-ray imaging device 400 of the present disclosure is shown, which includes a mechanical support structure that enables the position and orientation of the X-ray source and detector pair as a whole to be adjusted so that, for example, but not limited to, upper and lower extremities can be imaged in a non-load-bearing position or a load-bearing position. Figure 5 The miniature C-arm x-ray imaging device 400 may include many of the same electronic components as the previously described x-ray imaging devices, including processors, switching devices, monitors, etc. In some embodiments of the present disclosure, the mechanical support is a miniature C-arm 404, which is commercially used, for example, but not limited to, for fluoroscopy. In some embodiments, the mechanical support may include or include a mechanized arm or other mechanized structure. In some embodiments, the mechanical support may be a non-mechanized arm or other non-mechanized structure. In some embodiments, the mechanical support may be a Figure 5 Movable support arm shown.

[0057] In some embodiments, the mechanical support may include a mini (min) C-arm 404 connected to an adjustable extendable support arm 406, which is attached or mounted to a support structure, such as, for example but not limited to, a mobile cart 402 or other mobile or non-mobile device. In some embodiments, the adjustable extendable support arm 406 is configured to extend and retract and / or rotate so that a user of the x-ray imaging device 400 can move the x-ray source array 310 and the digital area x-ray detector 320 to approach a portion of the patient's body for imaging. In some embodiments, one or more second processors of the mini C-arm x-ray imaging device 400 are configured to automatically register non-load bearing images and load bearing images to generate load-induced structural deformation / displacement of the patient's limb. In some embodiments, one or more second processors are configured to automatically register pre-contrast injection images and post-contrast injection images to generate contrast-enhanced images of the patient's limb.

[0058] One or more processors of the miniature C-arm X-ray imaging device 400, such as a first processor, a second processor and / or a central processor, can all be positioned in any suitable location on the miniature C-arm X-ray imaging device 400, including in a housing 408, which may also include an electronic switching unit as described above with reference to FIG. 3 .

[0059] In some embodiments, Figure 5 The miniature C-arm X-ray imaging device 400 includes a carbon nanotube-based microfocus X-ray source array having a plurality of spatially distributed microfocus X-ray focal points, and a digital area X-ray detector mounted on the miniature C-arm. In addition, Figure 5 The miniature C-arm X-ray imaging device is configured to operate in a 3D tomosynthesis imaging mode, a fluoroscopy mode, and / or a stereotactic mode, as described herein. In some embodiments, the miniature C-arm X-ray imaging device 400 includes a central processor configured to control an electronic switching unit that switches between various imaging modes, as described herein.

[0060] The geometrical arrangement 600 of some embodiments of an x-ray imaging device is shown in FIG. Figure 6, wherein the x-ray source array 310 and the digital area x-ray detector 320 are in a parallel geometry relative to each other. To reduce the size of the imaging device, in some embodiments, the source-to-imager distance (SID) 614 of the system can be between about 40 cm and 60 cm and include about 40 cm and 60 cm, similar to the source-to-imager distance used in a miniature c-arm device. Reducing the SID 614 also has the following benefits: a) reducing the x-ray tube power required for exposure; b) reducing radiation exposure to the operator; and c) reducing the size and weight of the imaging system. However, reducing the SID 614 has an adverse effect on the system resolution. The spatial resolution of the imaging system is determined by factors including the focal spot size of the x-ray source array 310, the pixel size of the digital area x-ray detector 320, and the magnification factor. The magnification factor is the ratio of the SID 614 to the source-to-object distance (SOD) 616, the source being the x-ray source array 310, and the object being the scanned object 630.

[0061] In order to achieve the high spatial resolution required for diagnostic imaging at different magnification factors, in one embodiment of the present disclosure, a microfocus x-ray source array 310 is used. In some embodiments, for example but not limited to, the source array is a CNT-based microfocus x-ray source array. In some embodiments, the size of the x-ray focal spots 612 in the x-ray source array 310 (only 3 focal spots are marked by arrows for clarity) is preferably about 0.1 mm or less. To obtain depth resolution, in some embodiments, the angular scan 618 covered by the x-ray source array 310 is between about 10 degrees and 50 degrees and includes about 10 degrees and 50 degrees. In some embodiments, the angular scan (i.e., angular coverage) 618 of the x-ray source array 310 is about 40 degrees, and the SID 616 is about 40 cm. In some embodiments, in the case of a linear x-ray source array, this would require the line formed by the x-ray focal spots 612 to be equal to about 2*tan(20 degrees)*40 cm or about 29 cm.

[0062] In some embodiments of the present disclosure, the x-ray source array 310 includes between about 10 and 40 cathodes, each cathode producing an x-ray beam having a defined focal spot size from a corresponding focal spot 612 on an anode, arranged to be between about 10 and 40 focused focal spots 612, inclusive. In some embodiments, the CNT x-ray source array 310 includes about 30 spatially distributed microfocus x-ray focal spots 612, each focal spot 612 having an average focal spot size of, for example, a full width at half maximum (FWHM) of about 0.1 mm. In some embodiments, the x-ray source array 310 operates within an energy range between about 0 kVp and 120 kVp, inclusive. In one embodiment, the x-ray source array 310 operates within an energy range between about 40 kVp and 80 kVp, inclusive, to image, for example, but not limited to, a limb.

[0063] In some embodiments, the CNT-based microfocus x-ray source array 310 uses an electrostatic focusing structure to focus the electron beam for a small area on the x-ray anode. A non-limiting example of an electrostatic focusing structure is an Einzel-type electrostatic focusing lens. The construction of a single-beam CNT microfocus x-ray tube with an Einzel-type electrostatic focusing lens is described in the publication "Carbon nanotube based microfocus field emission x-ray source for microcomputed tomography", Appl. Phys. Lett, 89, 103111 (2006); Zejian Liu et al., and U.S. Pat. No. 7,826,595, the disclosures of which are incorporated herein by reference in their entirety.

[0064] In some embodiments, the x-ray photon output from the x-ray source array 310 depends on the size of the x-ray focal spot 612. Reduction in the size of the focal spot 612 limits the maximum tube power and, therefore, the generated x-ray fluence. For a microfocus x-ray source with a fixed anode, the x-ray tube current is typically less than 1 mA when the x-ray tube voltage is about 70 kVp and the x-ray focal spot 612 size is less than 0.1 mm.

[0065] For x-ray imaging, image quality, and in particular the image signal-to-noise ratio (SNR), depends on the amount of x-ray photons received by the x-ray detector 320, which depends on the incident dose. For tomosynthesis imaging of the human wrist, total incident doses between about 0.2 mGy and 0.3 mGy are typically used in the published literature. An experiment with a CNT x-ray source array according to the present disclosure designed for dental imaging showed that at a 40 cm SID 614 and an x-ray tube voltage of about 70 kVp, the x-ray radiation generation rate was about 0.4 mGy / mAs. At an x-ray tube voltage of about 50 kVp, this rate is expected to decrease to 0.2 mGy / mAs. Therefore, with a 40 cm SID device, the source current required to image the human wrist at 50 kVp is about 1 mA. Assuming the microfocus source array is operated at 50 kVp and 0.5 mA tube current, the total x-ray exposure required is 2 seconds for a dose of 1 mAs. If there are 20 projection images, and the detector frame rate is 4 frames per second, the total detector readout time is 5 seconds, and the total scan time of the example device is 7 seconds for tomosynthesis imaging of the human wrist. In comparison, General Electric's current commercial indoor digital tomosynthesis scanner takes about 10 seconds to perform a tomosynthesis scan. This shows that the example device of the present disclosure can perform a tomosynthesis scan in a similar, if not significantly shorter, time than currently available large indoor scanners.

[0066] In some embodiments of the present disclosure, Figure 7 As shown, the x-ray imaging device 300 may include a beam limiting device, such as a collimation assembly 702, which is configured to constrain the x-ray radiation from each x-ray focal spot to the surface of the digital area x-ray detector 320 in accordance with the requirements of the IEC standard. In some embodiments, the collimation assembly 702 may be, for example, but not limited to, one or more collimators. In some embodiments, the collimation assembly 702 is connected to the exit window of the x-ray source array 310 and is configured to substantially collimate or constrain the x-ray radiation generated from each and every one of the plurality of spatially distributed focal spots 612 to the surface of the digital area x-ray detector 320.

[0067] In some embodiments, the collimation assembly 702 includes a primary collimator and a secondary collimator, wherein the primary collimator includes a plurality of apertures, and each of the plurality of apertures is configured to allow radiation from a corresponding x-ray focal point 612A to pass therethrough. In other words, in some embodiments, a first aperture is fixed to or aligned with a single corresponding x-ray focal point 612A, and the first aperture is configured to allow only radiation from the corresponding x-ray focal point 612A to pass therethrough. Although in Figure 7Without the aperture visible in the view of FIG. 7 , lines 704 and 706 illustrate how radiation from each x-ray focal spot 612A and 612B, respectively, is collimated and focused onto digital x-ray detector 320 .

[0068] Figure 8 Included are several graphs showing simulations performed to demonstrate the system resolution of an example x-ray imaging device of the present disclosure. The simulations were run to demonstrate the system resolution of an x-ray source at different distances from an x-ray detector.

[0069] Using desktop equipment, such as Fig. 9 The tabletop apparatus 900 shown demonstrates the feasibility of the operation of the apparatus disclosed herein above. A pre-existing short CNT x-ray source array 310 and a flat panel detector 320 are mounted on a mechanical support 910. In addition, the tabletop apparatus 900 includes a set of legs 908 for further supporting the tabletop apparatus 900. The source array is translated to a total of 3 positions so as to cover 40 degrees at a 40 cm SID. Lines 902, 904, and 906 show the angle of the x-ray beam as it propagates toward the detector 320. A cadaver specimen was imaged at 55 kVp using 21 projections. The image was reconstructed using an iterative algorithm.

[0070] An example image reconstructed by a desktop device (or other device according to the disclosure herein) is shown in Fig. 10B Shown in. Fig. 10A An example projection image of a cadaver wrist captured using a different device than the present disclosure is shown. It was captured using conventional methods. Fig. 10A The image in (captured using the method of the present disclosure) Fig. 10B When compared with the images in Fig. 10A method) cannot be implemented Fig. 10B As indicated by the reference numerals, Fig. 10B The reconstructed slice images in Fig. 10A The joint space and injury are not visible on the projection image in 1000.

[0071] Fig.11A and Fig. 11B Another demonstration of the apparatus of the present disclosure is shown, where two different images are at different depths or heights. Fig.11A Depicted is a tomosynthetic reconstructed slice from the wrist of the specimen in the plane of the capitate. Fig. 11B Depicted are tomosynthetic reconstructed slices of the same wrist at the hook of the hamate and the palmar aspect of the scaphoid.

[0072] Some of the subject matter disclosed herein can be implemented in software or using software in combination with hardware and / or firmware. For example, the subject matter described herein can be implemented in software executed by a processor or processing unit. In an exemplary embodiment, the subject matter described herein can be implemented using a computer-readable medium having computer-executable instructions stored thereon that control the computer to perform steps when executed by the processor of the computer. Exemplary computer-readable media suitable for implementing the subject matter described herein include non-transitory devices, such as disk storage devices, chip storage devices, programmable logic devices, and application-specific integrated circuits. In addition, the computer-readable medium implementing the subject matter described herein can be located on a single device or computing platform, or can be distributed on multiple devices or computing platforms.

[0073] Without departing from the spirit and essential features of the present subject matter, the present subject matter may be embodied in other forms. Therefore, the described embodiments should be considered to be illustrative and not restrictive in all respects. Although the present invention has been described according to certain preferred embodiments, other embodiments apparent to those of ordinary skill in the art are also within the scope of the present invention.

Claims

1. A compact x-ray imaging system, include: an x-ray source array including a plurality of spatially distributed x-ray foci and a digital area x-ray detector; a collimation assembly coupled to an exit window of the x-ray source array, the collimation assembly configured to collimate x-ray radiation generated from each of a plurality of spatially distributed x-ray foci onto a surface of the digital area x-ray detector; Electronic switching equipment, including: High voltage power supply; Current source; a switch configured to sequentially connect the current source to a plurality of field emission cathodes of the compact x-ray imaging system one at a time at preset current values ​​to produce one or more projection images for tomosynthesis reconstruction without requiring any mechanical movement of the x-ray source array or the digital area x-ray detector; and a trigger comprising one or more first processors and / or circuits configured to synchronize detector data acquisition with x-ray exposure from the plurality of spatially distributed x-ray foci; and a mechanical support configured to enable the position and orientation of the x-ray source array and digital area x-ray detector to be adjusted to enable imaging of an upper and lower extremity of a patient in a non-load bearing position or a load bearing position using tomosynthesis; wherein the compact x-ray imaging system is configured to operate in multiple imaging modes, Wherein, the mechanical support is a micro C-shaped arm; wherein, when the x-ray imaging system is operated in a tomosynthesis imaging mode of the plurality of imaging modes, a scanning x-ray beam is electronically generated by sequentially activating x-ray beams from the plurality of spatially distributed x-ray focal spots without moving any of the x-ray source array, the digital area x-ray detector, or the patient so as to acquire one or more desired projection images for tomosynthesis reconstruction; and Wherein, when the x-ray imaging system operates in a pulsed fluoroscopy imaging mode among the multiple imaging modes, the x-ray radiation generated from the central focus of the multiple spatially distributed x-ray focuses is pulsed at 5 to 30 pulses per second, and for each x-ray pulse, an image of the scanned object is formed and displayed to generate an x-ray image of the object.

2. The compact x-ray imaging system according to claim 1, in, The x-ray imaging system is configured to operate in the tomosynthesis imaging mode or in the pulsed fluoroscopy mode.

3. The compact x-ray imaging system according to claim 1, in, The plurality of imaging modalities includes a stereotactic mode.

4. The compact x-ray imaging system according to claim 3, in, When the compact x-ray imaging system is operated in the stereotactic mode, two discrete focal spots of the plurality of spatially distributed x-ray focal spots are activated to emit x-ray radiation, resulting in the formation and display of two projection images from two different angles.

5. The compact x-ray imaging system according to claim 1, in, The collimation assembly includes a primary collimator and a secondary collimator; The primary collimator comprises a plurality of apertures, wherein each aperture of the plurality of apertures is configured to allow radiation from a corresponding x-ray focal spot to pass therethrough.

6. The compact x-ray imaging system according to claim 1, in, The x-ray source array includes between five and sixty, inclusive, independently controllable carbon nanotube emitters as electron sources; wherein the x-ray source array has a monopolar design with an anode voltage between 0 kV and 120 kV, inclusive, and an x-ray tube current between 0.05 mA and 20 mA, inclusive; and The spatial distribution of the focal spots is a line, a circle, a 2D array or any other 2D or 3D geometric structure configuration.

7. The compact x-ray imaging system according to claim 1, in, At least one of the plurality of x-ray focal spots is microfocused with a spot size between and including 0.01 mm and 0.3 mm.

8. The compact x-ray imaging system according to claim 7, in, The plurality of x-ray focal spots of the x-ray source array are positioned in a plane perpendicular to a plane in which the digital area x-ray detector is positioned.

9. The compact x-ray imaging system according to claim 7, in, The plurality of x-ray focal spots of the x-ray source array are positioned in a plane parallel to a plane in which the digital area x-ray detector is positioned.

10. The compact x-ray imaging system according to claim 1, in, The electronic switching device is configured to operate the high voltage power supply at more than one energy level during a single imaging sequence so that projection images acquired at different anode energy levels can be combined to produce contrast-enhanced two-dimensional (2D) radiography images and three-dimensional (3D) tomosynthesis images.

11. The compact x-ray imaging system of claim 1 , further comprising one or more second processors and a non-transitory computer readable medium including executable instructions; in, The one or more second processors are configured to automatically register the non-load bearing images and the load bearing images to generate load-induced structural deformation and / or displacement of the limb in the upper limb or lower limb of the imaged patient.

12. The compact x-ray imaging system of claim 1, further comprising one or more second processors and a non-transitory computer readable medium including executable instructions; in, The one or more second processors are configured to automatically register the pre-contrast injection image and the post-contrast injection image to generate a contrast-enhanced image of an upper or lower extremity of the imaged patient.

13. A method for performing x-ray imaging using a compact x-ray imaging system, the method include: providing an x-ray source array having a plurality of spatially distributed x-ray focal spots and a digital area x-ray detector on a mechanical support, the mechanical support enabling the position and orientation of the x-ray source array and the digital area x-ray detector to be adjusted; collimating x-ray radiation generated from each of the plurality of spatially distributed x-ray foci onto a surface of the digital area x-ray detector using a collimation assembly connected to an exit window of the x-ray source array; An electronic switching device is provided, the electronic switching device comprising: High voltage power supply; Current source; Switcher; and a trigger comprising one or more first processors and / or circuits; positioning and orienting the x-ray source array and digital area x-ray detector to enable imaging of an upper extremity and a lower extremity of a patient in a non-load bearing position or a load bearing position using tomosynthesis, wherein a relative position between the plurality of spatially distributed x-ray focal spots and the digital area x-ray detector remains unchanged during positioning and orienting the x-ray source array and digital area x-ray detector; sequentially connecting the current source to a plurality of field emission cathodes of a compact x-ray imaging system one at a time at preset current values ​​to produce one or more projection images for tomosynthesis reconstruction without requiring any mechanical movement of the x-ray source array or digital area x-ray detector; and synchronizing detector data acquisition with x-ray exposure from the plurality of spatially distributed x-ray focal spots; Wherein, the mechanical support is a micro C-shaped arm; wherein the compact x-ray imaging system is configured to operate in a plurality of imaging modes; wherein, when the x-ray imaging system is operated in a tomosynthesis imaging mode, a scanning x-ray beam is electronically generated by sequentially activating x-ray beams from the plurality of spatially distributed x-ray focal spots without moving any of the x-ray source array, the digital area x-ray detector, or the patient to acquire one or more desired projection images for tomosynthesis reconstruction; and Wherein, when the x-ray imaging system is operated in a pulsed fluoroscopy imaging mode, the x-ray radiation generated from the central focus of the multiple spatially distributed x-ray foci is pulsed at 5 to 30 pulses per second, and for each x-ray pulse, an image of the scanned object is formed and displayed to generate an x-ray image of the object.

14. A miniature C-arm X-ray imaging system, include: a carbon nanotube-based microfocus x-ray source array comprising a plurality of spatially distributed microfocus x-ray focal spots and a digital area x-ray detector mounted on a miniature c-arm; a collimation assembly coupled to an exit window of the microfocus x-ray source array, the collimation assembly configured to collimate x-ray radiation generated from each of the plurality of spatially distributed microfocus x-ray foci onto a surface of a digital area x-ray detector; as well as Electronic switching equipment, including: High voltage power supply; Current source; a switch configured to sequentially connect the current source to a plurality of field emission cathodes of a miniature C-arm x-ray imaging system one at a time at preset current values ​​to produce one or more projection images for tomosynthesis reconstruction without requiring any mechanical movement of the microfocus x-ray source array or the digital area x-ray detector; and a trigger comprising one or more processors and / or circuits configured to synchronize detector data acquisition with x-ray exposure from the plurality of spatially distributed microfocused x-ray foci; Wherein, the miniature C-arm X-ray imaging system is configured to operate in a 3D tomosynthesis imaging mode, a fluoroscopy mode, and a stereotactic mode.

15. A method for performing X-ray imaging using a miniature C-arm X-ray imaging system, include: A miniature C-arm X-ray imaging system is provided, which includes a carbon nanotube-based microfocus X-ray source array having a plurality of spatially distributed microfocus X-ray focal spots and a digital area X-ray detector mounted on the miniature C-arm; collimating x-ray radiation generated from each of the plurality of spatially distributed microfocus x-ray foci onto a surface of a digital area x-ray detector using a collimation assembly coupled to an exit window of the microfocus x-ray source array; An electronic switching device is provided, the electronic switching device comprising: High voltage power supply; Current source; Switcher; and a trigger comprising one or more processors and / or circuits; sequentially connecting current sources to a plurality of field emission cathodes of a miniature C-arm x-ray imaging system one at a time at preset current values ​​to produce one or more projection images for tomosynthesis reconstruction without requiring any mechanical movement of the microfocus x-ray source array or digital area x-ray detector; and synchronizing detector data acquisition with x-ray exposure from the plurality of spatially distributed microfocused x-ray foci; Wherein, the miniature C-arm X-ray imaging system is configured to operate in a 3D tomosynthesis imaging mode, a fluoroscopy mode, and a stereotactic mode.

Images