Systems and methods for imaging a subject

Abstract

A method and system for acquiring image data of a subject is disclosed. The image data can be collected using an imaging system in a selected manner and / or motion. More than one projection can be combined to generate and create a selected view of the subject.

Description

Technical Field

[0001] The present disclosure relates to imaging a subject, and more particularly to a system for acquiring image data for producing selected views of a subject. Background Art

[0002] This section provides background information related to the present disclosure which is not necessarily prior art.

[0003] A subject, such as a human patient, can undergo a procedure. The procedure can include a surgical procedure to correct or enhance the subject's anatomical structure. Enhancement of the anatomical structure can include various procedures, such as mobilization or enhancement of bones, insertion of an implant (i.e., an implantable device), or other appropriate procedures.

[0004] A surgeon can perform a procedure on a subject based on images of the subject's projections. Images can be generated using an imaging system such as a magnetic resonance imaging (MRI) system, a computed tomography (CT) system, fluoroscopy (e.g., a C-arm imaging system), or other suitable imaging system. Summary of the Invention

[0005] This section provides a general summary of the disclosure, and is not a comprehensive disclosure of its full scope or all of its features.

[0006] According to various embodiments, a system for acquiring image data of a subject using an imaging system may use x-rays. The subject may be a living patient (e.g., a human patient). The subject may also be an inanimate subject, such as a housing, a shell, etc. The imaging system may include a movable source and / or a detector movable relative to the subject.

[0007] The imaging system can include a movable source and / or detector to create multiple projections of a subject. The multiple projections can be acquired in a linear path of movement of the source and / or detector. The multiple projections can then be combined, for example by stitching them together, to produce or form a long view (also referred to as a long film). The long view can be a two-dimensional view of the subject.

[0008] In various embodiments, the imaging system can acquire multiple projections at different viewing angles relative to the subject. The different viewing angles may occur due to parallax effects between different x-ray paths through the subject from a single source to the detector. The parallax effect can allow different views of the same location on the subject. The parallax effect can be formed because the filter has multiple slits or slots through which the x-rays pass and impinge on the detector. Therefore, movement of the source and / or detector relative to the subject can allow acquisition of multiple projections through the subject that include parallax effects. Due to the movement of the source and / or detector, the multiple projections can then be stitched together to form multiple long views of the subject.

[0009] Further areas of applicability will become apparent from the description provided herein.The description and specific examples in this summary are intended for purposes of illustration only and are not intended to limit the scope of the present disclosure. BRIEF DESCRIPTION OF THE DRAWINGS

[0010] The drawings described herein are for illustrative purposes only of selected embodiments and not all possible implementations, and are not intended to limit the scope of the present disclosure.

[0011] Figure 1 is an environmental view of the imaging system in the operating room;

[0012] Figure 2 is a detailed schematic diagram of an imaging system having a dual energy source system;

[0013] Figure 3 is a perspective view of an optical filter assembly according to various embodiments;

[0014] Figure 4A is an exploded view of a slot filter assembly according to various embodiments;

[0015] Figure 4B is a top plan view of a slot filter body according to various embodiments;

[0016] Figure 4C yes Figure 4B A cross-sectional view of the slot filter body around line 4C;

[0017] Figure 5A and Figure 5B is a schematic illustration of a slot filter assembly relative to a source and a detector;

[0018] Figure 6 is a flow chart for executing a long view or long film image according to various embodiments;

[0019] Figure 7 A detailed flow chart that is part of the long view approach;

[0020] Figure 8 is a schematic illustration of acquiring multiple projections in an intermediate image according to various embodiments;

[0021] Figure 9A is a schematic illustration of the focal plane relative to a slot filter assembly;

[0022] Figure 9B is a schematic illustration of the registration of the intermediate images;

[0023] Figure 10 is a schematic illustration of the formation of a long view with a weighting function; and

[0024] Figure 11 is a Gaussian graph plotted against intensity for a detector with fan-shaped x-rays.

[0025] Corresponding reference characters indicate corresponding parts throughout the several views of the drawings. DETAILED DESCRIPTION

[0026] Example embodiments will now be described more fully with reference to the accompanying drawings.

[0027] refer to Figure 1 , shows a schematic diagram of an operating room 20. A user 24, such as a surgeon, may perform surgery on a subject, such as a patient 28. The subject may be placed on a support, such as a table 32 (support), for selected portions of the procedure. Table 32 does not interfere with image data acquisition by imaging system 36. While performing the procedure, user 12 may use imaging system 36 to acquire image data of patient 28, allowing the selected system to generate or create images to assist in performing the procedure. Images generated using the image data, such as models (e.g., three-dimensional (3D) images), long views, single projection views, etc., may be generated using the image data and displayed as images 40 on a display device 44. Display device 44 may be part of and / or connected to a processor system 48, which may include an input device 52 (e.g., a keyboard) and a processor 56, which may include one or more processors or microprocessors integrated with processor system 48, and selected types of non-transitory and / or transient memory 58. A connection 62 may be provided between processor 56 and display device 44 for data communication, allowing display device 44 to be driven to display or show image 40. Processor 56 may be any suitable type of processor, such as a general purpose processor that executes instructions contained in a program or a special purpose processor such as an application specific integrated circuit.

[0028] The imaging system 36 may comprise a system sold by Medtronic Navigation, Inc. having a place of business in Louisville, CO, USA. Imaging system. Imaging System The imaging system 36 or other suitable imaging system may be used during the selected procedure, such as the imaging systems described in US Patent Publications 2012 / 0250822, 2012 / 0099772, and 2010 / 0290690, all of which are incorporated herein by reference.

[0029] When for example containing When imaging the system 36, the imaging system 36 may include a mobile cart 60 that includes a controller and / or control system 64. The control system 64 may include a processor and / or processor system 66 (similar to the processor 56) and a memory 68 (e.g., non-transitory memory). The memory 68 may include various instructions that are executed by the processor 66 to control the imaging system 36 (including various parts of the imaging system 36).

[0030] The imaging system 36 may include further additional parts, such as an imaging gantry 70 in which an active unit (also referred to as an assembly) 74 and a detector unit (also referred to as an assembly) 78 are positioned. The gantry 70 is movably connected to the mobile cart 60. The gantry 70 may be O-shaped or annular, wherein the gantry 70 is substantially annular and includes walls that form a volume in which the source unit 74 and the detector 78 can move. The mobile cart 60 may also be mobile and may be moved from one operating room to another operating room and or another room. The gantry 70 may be movable relative to the cart 60, as further discussed herein. This allows the imaging system 36 to be mobile and movable relative to the subject 28, thereby allowing it to be used in multiple locations and with multiple procedures without requiring capital expenditure or space dedicated to a fixed imaging system.

[0031] Processor 66 may be a general purpose processor or a special purpose processor. Memory 68 may be a non-transitory memory, such as a rotating disk or solid-state non-volatile memory. In various embodiments, the memory system may contain instructions to be executed by processor 66 to perform functions and determine results, as discussed herein.

[0032] In various embodiments, imaging system 36 may include an imaging system that acquires images and / or image data by emitting x-rays and detecting the interaction and / or attenuation of the x-rays with subject 28. Thus, x-ray imaging may be one imaging modality. It should be understood that other imaging modalities are also possible.

[0033] Thus, the imaging system 36 including the source unit 74 may be an x-ray emitter that may emit x-rays that pass through the patient 28 for detection by the detector 78. As will be appreciated by those skilled in the art, the x-rays emitted by the source unit 74 may be emitted in a cone along a selected primary vector 94 and detected by the detector 78, as shown in FIG. Figure 2 The source unit 74 and the detector 78 may also be collectively referred to as a source / detector unit 98 , particularly where the source unit 74 is generally diametrically opposed (eg, 180 degrees apart) to the detector 78 within the gantry 70 .

[0034] The imaging system 36 can be moved, in whole or in part, relative to the subject 28. For example, the source unit 74 and the detector 78 can be moved 360° around the patient 28. The movement of the source / detector unit 98 within the gantry 70 can allow the source unit 74 to remain approximately 180° relative to the detector 78 (e.g., with a fixed internal gantry or rotor or movement system). Therefore, unless otherwise disclosed, the detector 78 can be referred to as moving around the subject 28 (e.g., in a circular or spiral shape), and it should be understood that the source unit 74 remains relative to the subject.

[0035] Additionally, the gantry 70 can be equidistantly moved (also referred to as "swinging" relative to the subject 28 generally in the direction of arrow 100) about an axis 102, such as by the cart 60. Figure 1 The gantry 34 can also be tilted relative to the long axis 106 of the patient 28 as indicated by arrow 110. When tilted, the plane of the gantry 70 can be tilted or form a non-orthogonal angle with the long axis 106 of the subject 28.

[0036] The gantry 70 can also be moved longitudinally along the long axis 106 in the direction of arrow 114 relative to the subject 28 and / or the cart 60. Furthermore, the cart 60 can be moved to move the gantry 70. Furthermore, the gantry 70 can be moved up and down relative to the cart 30 and / or the subject 28 generally in the direction of arrow 118, generally transverse to the long axis 106 and parallel to the axis 102.

[0037] Imaging system 36 is movable in whole or in part to allow positioning of source / detector unit (SDU) 98 relative to subject 28. Imaging system 36 can be precisely controlled to move SDU 98 relative to subject 28 to produce accurate image data of subject 28. Imaging system 36 can be connected to processor 56 via connection 120, which can include a wired or wireless connection or physical medium transfer from imaging system 36 to processor 56. Thus, image data collected using imaging system 36 can be transferred to processor 56 for navigation, display, reconstruction, etc.

[0038] As discussed herein, source unit 74 may include one or more x-ray sources for imaging subject 28. In various embodiments, source unit 74 may include a single source that may be powered by more than one power source to generate and / or emit x-rays having different energy characteristics. Additionally, more than one x-ray source may be source unit 74 that may be powered to emit x-rays having different energy characteristics at selected times.

[0039] According to various embodiments, the imaging system 36 can be used with non-navigation or navigation procedures. In a navigation procedure, a localizer and / or digitizer, including either or both of the optical localizer 130 and / or the electromagnetic localizer 138, can be used to generate a field and / or receive and / or transmit signals within a navigation domain relative to the subject 28. The navigation space or navigation domain relative to the subject 28 can be registered with the image 40. As understood in the art, correlation allows for registration of the navigation space defined within the navigation domain and the image space defined by the image 40. A patient tracker or dynamic reference frame 140 can be connected to the subject 28 to allow for dynamic registration and maintain registration of the subject 28 with the image 40.

[0040] The patient tracking device or dynamic reference frame 140 and the instrument 144 can then be tracked relative to the subject 28 to allow for navigation procedures. The instrument 144 can include a tracking device, such as an optical tracking device 148 and / or an electromagnetic tracking device 152, to allow the instrument 144 to be tracked using either or both of the optical locator 130 or the electromagnetic locator 138. The navigation / detection interface device 158 can communicate (e.g., wired or wireless) with the instrument 144 (e.g., via communication line 156), with the electromagnetic locator 138 (e.g., via communication line 162), and / or with the optical locator 130 (e.g., via communication line 166). The navigation / detection interface device 158 can also communicate with the processor 56 via communication line 168 and can transmit information (e.g., signals) about various items connected to the navigation / detection interface device 158. It should be understood that any communication link can be wired, wireless, a physical medium transmission or mobile, or any other suitable communication. However, a suitable communication system may be equipped with corresponding positioners to allow tracking of instrument 144 relative to subject 28, thereby allowing the tracked position of instrument 144 relative to image 40 to be illustrated for performing the procedure.

[0041] Those skilled in the art will appreciate that device 144 can be any suitable device, such as a cardiac or vascular stent, a spinal implant, a neural stent or stimulator, an ablation device, or the like. Device 144 can be an interventional device, or can include or be an implantable device. Tracking device 144 allows the position (including x, y, z position and orientation) of device 144 relative to subject 28 to be viewed using registered image 40 without requiring direct viewing of device 144 within subject 28.

[0042] In addition, the imaging system 36, such as the gantry 70, can include an optical tracking device 174 and / or an electromagnetic tracking device 178 for tracking with the corresponding optical positioner 130 and / or electromagnetic positioner 138. Thus, the imaging system 36 can be tracked relative to the subject 28, and the instrument 144 can also be tracked to allow initial, automatic, or continued registration of the subject 28 relative to the image 40. Registration and navigation procedures are discussed in the above-incorporated U.S. Patent No. 8,238,631, which is incorporated herein by reference. After the instrument 144 is registered and tracked, an icon 180 can be displayed relative to the image 40, including overlaid on the image 40.

[0043] Continue to refer Figure 2 According to various embodiments, the source unit 74 may include a single x-ray tube 190 that may be connected to a switch 194 that may interconnect a first power source 198 via a connection or power line 200. As described above, x-rays may be emitted from the x-ray tube 190 generally in a cone toward the detector 78 and generally in a direction from the x-ray tube 190 as indicated by arrow, beam arrow, beam, or vector 94. As will be appreciated by those skilled in the art, the switch 194 may switch the tube 190 on or off to emit x-rays having selected characteristics. Vector 94 may be a central vector or ray within the beam 90 of x-rays. The x-ray beam may be emitted as a cone or other suitable geometric shape. Vector 94 may include a selected line or axis associated with further interactions of the beam, such as interaction with a filter component, as further discussed herein.

[0044] Subject 28 may be positioned within vector 94 of x-rays to allow acquisition of image data of subject 28 based on emission of x-rays in the direction of vector 94 toward detector 78 .

[0045] The x-ray tube 190 may be used to generate two-dimensional (2D) x-ray projections of the subject 28, including a selected portion of the subject 28 or any region, zone, or volume of interest, based on x-rays impinging on or being detected on a 2D or flat panel detector, such as the detector 78. The 2D x-ray projections may be reconstructed as discussed herein to generate and / or display a three-dimensional (3D) volumetric model of the subject 28, the selected portion of the subject 28, or any region, zone, or volume of interest. As discussed herein, the 2D x-ray projections may be image data acquired using the imaging system 36, and the 3D volumetric model may be generated or modeled from the image data.

[0046] For reconstructing or forming a 3D volumetric image, suitable algebraic techniques include expectation maximization (EM), ordered subset EM (OS-EM), simultaneous algebraic reconstruction techniques (SART), and total variation minimization (TVM), as generally understood by those skilled in the art. Applications for performing 3D volume reconstruction based on 2D projections allow for efficient and complete volume reconstruction. Generally, the algebraic techniques may include an iterative process to perform a reconstruction of subject 28 for display as image 40. For example, pure or theoretical image data projections, such as those generated from an atlas or stylized model of a "theoretical" patient, may be repeatedly altered until the theoretical projection image matches the acquired 2D projection image data of subject 28. The stylized model may then be appropriately modified to form a 3D volumetric reconstructed model of the acquired 2D projection image data of the selected subject 28 and may be used for surgical procedures, such as navigation, diagnosis, or planning. The theoretical model may be associated with the theoretical image data to construct the theoretical model. In this manner, a model or image 40 may be constructed based on the image data of subject 28 acquired using imaging system 36.

[0047] Continue to refer Figure 2 , the source unit 74 can include various elements or features that can be moved relative to the x-ray tube 190. In various embodiments, for example, the collimator 220 can be positioned relative to the x-ray tube 190 to help form the cone relative to the subject 28. The collimator 220 can include various features, such as movable components that can help position one or more filters within the beam 90 of the cone of x-rays before reaching the subject 28. In addition, as further discussed herein, various filters can be used to shape the x-ray beam before reaching the subject 28, such as to shape the beam 90 into a selected shape. In various embodiments, as discussed herein, the x-rays can be formed into a thin fan or plane to reach and pass through the subject 28 and be detected by the detector 78.

[0048] Thus, the source unit 74 including the collimator 220 may include a filter assembly 224. The filter assembly 224 may include one or more portions that allow the filter to be moved relative to the x-ray tube 190 to shape and / or position the x-rays before reaching the subject 28. For example, referring to Figure 3 , filter assembly 224 can include a platform 228. Platform 228 can be positioned relative to x-ray tube 190 and can substantially block all x-rays and / or define the start of cone beam 90 as the x-rays pass through platform exposure opening 232. Platform opening 232 can be an opening or passage through platform 228 that allows x-rays to exit x-ray tube 190 and form cone beam 90.

[0049] like Figure 3As shown, the filter holding assembly 240 can include a movable filter holder or step 244. The filter step 244 can include one or more filter holding locations, such as an open filter portion 246, a first filter or solid filter element 250, and a third or slotted filter assembly 260, as discussed further herein. The filter step 244 can be movable on one or more tracks, such as a first track 264 and a second track 266. The filter step 244 can be coupled to one or more carrier components, such as a ladder cart, including a first carrier 268 that moves along the first track 264 and a second carrier 270 that moves along the second track 266. It should be understood that opposing or opposed carrier components can also be provided to ensure smooth and / or selective planar movement of the filter step 244, thereby including a third carrier 274 and a fourth carrier 276. 264, 266. The third carrier 274 and the fourth carrier 276 can be resting on respective rails 264, 266 as can the first carrier 268 and the second carrier 270. Thus, the filter ladder 244 can be generally moved in the direction of the double-headed arrow 280 to selectively position the open filter portion 246, the solid filter member 250, or the slot filter assembly 260 relative to the aperture or passage opening 232 to allow x-rays to form the beam 90 or otherwise impinge on the subject 28, as further discussed herein. The filter assembly 224 can be used to enhance the emission of x-rays from the x-ray tube 190 to aid in generating images or image data of the subject 28, as further discussed herein.

[0050] The filter carriers or filter ladders 244 can be moved by a selected mechanism, such as a servo or drive motor associated with the respective carriers 268, 270, 274, 276, or other suitable mechanism. Movement of the filter ladders 244 can be controlled by the user 24, for example, through manual input and / or instructions provided to the imaging system 26. For example, the control system 64 can execute selected instructions to move the filter ladders 244 in a selected manner. Furthermore, the control system 64 can move the filter ladders 244 at selected times based on selected inputs, such as inputs from the user 24, regarding a selected image or image data to be acquired of the subject 28. Thus, the filter assembly 224 can be controlled by the control system 64 and / or any other suitable controller, such as the processor system 48.

[0051] refer to Figure 4A 、 Figure 4B and Figure 4C, showing the slot filter assembly 260 in more detail. The slot filter assembly 260 can include a filter assembly formed from one or more components. However, it should be understood that the slot filter assembly can be formed from a single component including only the body 352, as discussed further herein. In various embodiments, the slot filter assembly 260 includes a slot filter component 300 that can be sandwiched or placed between a first component or sheet 304 and a second component or second layer 308. However, it should be understood that the slotted component is not placed between the first component 304 and the second component 308. Both the first component 304 and the second component 308 can be placed on a single side and / or combined into a single component placed on a single side of the slot filter component 300. However, in various embodiments, the first component 304 and the second component 308 are solid and help ensure that the slots 340, 344, 348 (discussed further herein) remain free of debris.

[0052] The first sheet 304 can be formed from a selected material, such as substantially pure aluminum (i.e., pure aluminum commonly available to those skilled in the art), an aluminum alloy, or other suitable aluminum material. The top member 304 can include a first side (or outer side) 312 and a second side (bottom or contact side) 314. The first side 312 and the second side 314 can be substantially planar. The second side 314 can contact the first side 320 of the slot filter member 300. The second side 314 can be adhered to the first side 320, for example, using a selected adhesive or bonding member, such as adhesive transfer tape. The thickness or distance between the first side 312 and the second side 314 can be from about 0.01 inches to about 0.05 inches, including about 0.02 inches (about 0.5 millimeters (mm)).

[0053] The second layer 308 can include a first surface 324, which can be an exterior surface, and a second surface (or interior surface) 326. The second surface 326 can contact the bottom or second side 330 of the slot filter component 300. However, the second layer 308 can include or be formed as a bi-material structure formed from an aluminum portion 309 (formed from the same or similar aluminum material as described above) and a copper portion 310 (e.g., substantially pure copper). In various embodiments, the first portion can be 0.5 mm thick 1100 series aluminum bonded to 0.1 mm 99% pure copper using a selected material, such as Scotch brand adhesive 924. However, the entire second layer can have a thickness of approximately 0.01 to approximately 0.05 inches, including approximately 0.02 inches (approximately 0.5 millimeters (mm)). The sheet 304 and the second layer 308 will typically have parameters that are generally coextensive with the edges of the slot filter component 300.

[0054] The slot filter component 300 may include dimensions, as discussed further herein. The slot filter component 300 may be formed from a selected material, such as tungsten carbide having a selected amount of tungsten, for example, a minimum of approximately 90% tungsten. In various embodiments, the tungsten carbide is ANSI grade C2 tungsten carbide. For example, the tungsten carbide may be TECHMET grade TMK-22 tungsten carbide having approximately 94% tungsten carbide and 6% cobalt. In various embodiments, the grain size of the tungsten carbide component may be on the micron or submicron scale, for example, from approximately 0.5 microns to approximately 2 microns, including from approximately 1.0 microns to approximately 1.4 microns, and further including approximately 1.2 microns. The slot filter component 300 also includes a selected number of slots or slits formed through the slot filter component 300, such as a first slot 340, a second or middle slot 344, and a third slot 348. When the slots 340, 344, 348 are positioned above the opening 232 of the platform 228, they can be used to shape a selected x-ray beam, volume, or region, such as a sector. As described above, and further herein, the slot filter assembly 260 can be used to generate or shape an x-ray beam relative to the subject 28 to collect image data thereof.

[0055] Typically, the slot filter assembly 260 can be positioned so that the first sheet 304 is positioned away from the subject 28 and generally closer to the x-ray source (e.g., the x-ray tube 190). Thus, x-rays can generally pass through the slot filter assembly 260 in the direction of vector (or arrow) 94, first engaging the first layer of components 304 and finally engaging or passing through the second layer of components 308. Typically, the slot filter assembly 300 will block all or substantially all x-rays that pass through the first sheet 304, except for x-rays that pass through the slots 340, 344, 348. Thus, x-rays that pass through the slot filter assembly 260 and reach the detector 78 are limited to only those x-rays that pass through the slots 340, 344, 348. However, it should be understood that the components 304, 308 mentioned above can be positioned relative to the slot filter assembly 300 in any suitable manner. Additionally, the materials selected for the first component 304 and the second layer 308 may help refine and / or select the spectral content of the x-rays passing through the slot filter assembly 260 .

[0056] The slot filter assembly 260 includes a slot filter component 300, as described above. Figure 4B and 4C, the slot filter assembly 300 includes various features, including slots 340, 344, and 348. The slot filter assembly 300 includes a body 352 through which the slots 340, 344, and 348 are formed. The body 352 can have a selected thickness 354, which can be from about 0.01 inches to about 1 inch, including about 0.01 inches to about 0.1 inches, and further including about 0.07 inches to about 0.1 inches, and further about 0.09 inches (about 2.2 millimeters). It should be understood that the thickness 354 of the body 352, alone or in combination with the other filter layers 304 and 308, can be used to shape or limit the x-rays that pass through the slot filter assembly 260. The body 352 can have other dimensions for various purposes; however, these dimensions can be based on the size of the opening 232, the size of the filter assembly 224, or other appropriate constraints. However, in various embodiments, the body 352 can include a length dimension 356 between the terminal ends of about 0.5 inches to about 2 inches, and further including about 1.4 inches (35 mm). The width dimension 360 can be about 0.1 inches to about 2 inches, and further including about 0.9 inches (22 mm). The body 352 of the slot filter component 300 can include various configurations, such as a chamfered or angled corner 364 that can form an angle of about 45 degrees relative to the terminal end of the body 352. Again, it should be understood that the slot filter assembly 260 can include various configurations for fitting into a selected imaging system (e.g., the imaging system 36), and the specific shape of the exterior can be based on the configuration of the imaging system 36. However, the thickness 354 can be selected to ensure that minimal or no x-ray radiation passes through the slot filter assembly 260 other than through the slots 340, 344, 348.

[0057] Continue to refer Figure 4A and Figure 4B , and with particular reference to Figure 4C , the main slot filter body 352 has a thickness 354. The thickness 354 is defined by or between two sides 320 and 330. In various embodiments, the first side 320 can be the surface closest to the x-ray radiation source, while the second side 320 can be the surface closest to the subject 28. It should be understood that these surfaces can also be referred to as the top side 320 and the bottom side 330, respectively. However, it should be understood that the top and bottom are merely exemplary and are not intended to limit the absolute position of the body 352.

[0058] The body 352, which includes three slots, includes a middle slot 344 and two edge slots 340, 348. As discussed further herein, each slot is formed between and through the two sides 320, 330. Each of the three slots can be formed through the body 352 in a suitable manner, such as by electrical discharge machining or other suitable tool (e.g., a router or punch). It will also be understood that the slots can be forged or otherwise cut into the body 352. However, near or at the first side 320, each of the three slots 340, 344, 348 is formed by two respective side walls, such as, for example, a first slot 340 is formed between side walls 370 and 374; a second slot 344 is formed between side walls 378, 382; and a third slot 348 is formed between side walls 386 and 390. It will be understood that as Figure 4C As shown, the sidewalls extend between the two ends 357 and 358 of the body 352. The sidewalls of each of the slots 340, 344, 348 are generally spaced equidistantly along the length of the respective slot and are substantially parallel. In addition, the slot walls are generally straight and parallel relative to each other. However, it will be appreciated that certain tools may result in slightly different dimensions for various portions of the slot, such as the entry or exit cuts to start or end the slot. However, each of the slots 340, 344, 348 is generally formed to have a dimension 398 of about 0.001 inches to about 0.1 inches, including about 0.009 inches to about 0.03 inches, and further including about 0.025 inches to about 0.01 inches, and further including about 0.02 inches (about 0.5 mm). For each slot, the width 398 of the slots 340, 344, 348 can be substantially the same, typically the dimension between the inner surfaces of the respective opposing walls of the respective slots.

[0059] The respective walls forming the respective slots at the first side 320 can each have a center located between the respective walls. For example, the slot 340 can have a centerline or axis 400, the second slot 344 can have a center axis 404, and the third slot 348 can have a center axis 408. Each of the axes 400, 404, 408 can be a point located centered between the respective walls and substantially perpendicular to the first side 320. The center points or axes 400, 404, 408 are generally or substantially perpendicular to the two sides 320, 330 and can be separated by a selected distance, such as distance 412. The distance 412 between each slot can be the same and can be approximately 0.01 inches to approximately 1 inch, and further approximately 0.1 inches to approximately 4 inches, and further approximately 0.318 inches to approximately 0.322 inches (8.0 mm to approximately 8.2 mm) apart. The distance 412 can be selected based on various parameters, such as the size of the body 352, the size of the opening 232 in the filter platform 228, or other appropriate considerations. Thus, the distance 412 can be selected based on various parameters. However, it will be appreciated that the spacing 412 between the respective slots 340, 344, 348 can be selected substantially precisely for various imaging collection techniques and / or stitching, as discussed further herein.

[0060] As described above, the respective central axes 400, 404, 408 are defined or can be defined by a point located at the center between the respective walls at the first side 320 and substantially orthogonal to the first side 320. The central or second slot 344 can have sidewalls 378, 382 that are substantially parallel to the central axis 404 and substantially perpendicular to the first side 320. Thus, the central axis 404 can extend through the body 352 substantially parallel to the sidewalls 378, 382. Thus, the distance or width 398 can be substantially divided in half or split by the central axis 404.

[0061] However, edge slots 340 and 348 may have respective central axes 420 and 424 that extend substantially parallel to respective sidewalls 370, 374 and 386, 390, rather than perpendicular to first side 320. Central axes 420, 424 may form an angle relative to respective centerpoint axes 400, 408. For example, first slot 340 having centerline axis 420 may form angle 428 relative to centerpoint axis 400. Angle 428 may be from about 5 degrees to about 10 degrees, further from about 6 degrees to about 8 degrees, and further from about 7 degrees. Centerline axis 424 may also form angle 432 relative to centerpoint axis 408. Angle 432 may be from about 5 degrees to about 10 degrees, further from about 6 degrees to about 8 degrees, and further from about 7 degrees. Thus, angles 428, 432 may be substantially similar to or identical to the interior angle between respective centerlines 420, 424 and centerpoint axes 400, 408. The angles 428 , 432 may also be formed relative to either side 320 , 330 , as the centerpoint axis is substantially perpendicular to the sides 320 , 330 .

[0062] Angles 428, 432 can help allow x-rays to Figure 4C Schematically illustrated are the passages from the x-ray tube 190 through the respective slots 340, 344, 348 without any or significant distortion due to interaction with the respective side walls 370, 374, 379, 382, ​​386, 390. Figure 4C As shown and described above, x-rays can be emitted from the x-ray tube 190 in a substantially conical shape. Thus, x-rays traveling substantially perpendicular to the first side 320 will pass through the central slot 344 along the central axis 404 without substantial or any interaction with the sidewalls 378, 382. Similarly, due to the respective angles 428, 432, x-rays near the edges of the cone-shaped beam 90 can pass through the edge slots 340, 348 without substantial interaction with the respective sidewalls 370, 374, 386, 390 due to the respective angles 428, 432.

[0063] According to various embodiments, the slot filter assembly 300 of the slot filter assembly 260 can allow for the formation of three x-ray sectors or x-ray regions due to the respective slots 340, 344, 348, including a first sector 440, a second sector 444, and a third sector 448. The three sectors formed by the slot filter assembly 260, including the slot filter assembly 300, filter x-rays from the x-ray tube 190 except for the regions of the slots 340, 344, 348. In other words, the slot filter assembly 260 filters x-rays from the x-ray tube 190 and allows the x-rays to pass through the slots 340, 344, 348 to form the sectors 440, 444, 448. In various embodiments, the slot filter assembly 260, such as the slot filter assembly 300, is located a distance 450 from the x-ray tube 190. The distance 450 may be from about 50 mm to about 100 mm, including from about 60 mm to about 80 mm, further including from about 68 mm to about 72 mm.

[0064] As discussed further herein, the three sectors 440, 444, 448 allow for the generation of selected image projections due to the imaging area on the detector 78. Furthermore, due to the angles 428, 432, as described above, the first sector 440 and the third sector 448 are substantially undistorted by the interaction of x-rays with the body 352. It should also be understood that the numbering of the slots 340, 344, 348 and the corresponding sectors 440, 444, 448 is provided solely for clarity of the present discussion and is not intended to require any particular order. Furthermore, it should be understood that the body 352 may include a selected number of slots, such as fewer than three or more than three, and three are shown and discussed for purposes of the present disclosure. However, it should be understood that the three slots 340, 344, 348 allow for the generation of long views in an efficient and rapid manner, as discussed further herein. Including a different number of selected slots may allow for the generation of different numbers of intermediate images, as discussed herein, but this is not required.

[0065] As described above, the slot filter assembly 260 may be used in the imaging system 36 to acquire images of the subject 28. Figure 2 , the SDU 98 can be moved around the subject 28 within the gantry 70. It should be understood that the SDU 98 can be moved in any suitable manner, and that the imaging system 36 is exemplary. However, in various embodiments, the SDU can be rotated from a first position to a second position, for example, about 90 degrees apart. For example, Figure 2As shown, a first position of the SDU 98 may include the source unit 74, which directs x-rays along a cone of beams 90 for the detector 78, which may be generally oriented in an anteroposterior (AN) direction relative to the subject 28. The SDU 98 may be rotated 90 degrees so that the source is in a second source position 74' and the detector may be moved to a different position, such as a second detector position 78'. The SDU 98 may be located in either or both positions and may form a line scan of the subject 28.

[0066] The line scan may include moving the gantry 70 including the SDU 98 along the long axis 106 of the subject 28, which may also be referred to as the Z axis or Z direction of the imaging system 36, generally in the direction of the double-headed arrow 114, as shown. Figure 1 Thus, detector 78 can be moved in a linear direction, essentially only along the Z axis in the direction of double-headed arrow 114. The acquired image data can be used to form a long film or long view of subject 28, wherein image data is acquired at one or both of the positions of detectors 78, 78', as shown. Figure 2 As discussed further herein, the use of the slot filter assembly 260 can be used to generate multiple views along the Z axis.

[0067] like Figure 4C As shown and further referenced Figure 5A and Figure 5B , the slot filter assembly 260 can be used to form three sectors 440, 444, 448 that reach or have attenuation detected by the detector 78. Each of the sectors 440, 444, 448 directly or have attenuation that impinges or contacts the detector 78 in a substantially narrow location or area. Figure 5B As shown, the detector 78 may include a plurality of excitable or detector regions (or detector portions) 460. The detector regions 460 may also be referred to as pixels and may relate to a single picture element (pixel) shown in the image 40 on the display device 44.

[0068] The entire beam 90 from the source unit 74 may have an area that will excite or strike the entire surface of the detector 78. However, the individual sectors 440, 444, 448 typically only strike a narrow band of pixels in the detector area 460. It should be understood that the number of pixels excited may encompass the entire width 464 of the detector 78, but be limited to a selected length 468 of the detector. For example, assuming no object or subject is within the path of the x-rays (e.g., an air scan), the respective sectors 440, 444, 448 may strike approximately 10 to approximately 100 pixels. However, the number of pixels excited in the dimension 468 on the detector 78 may be enhanced or adjusted based on the distance of the detector 78 from the slot filter assembly 260, the width of the slots (340, 344, 348), or other appropriate considerations. However, as Figure 5A and Figure 5B As shown, each of the respective sectors 440, 444, 448 will impinge upon the detector 78 at a substantially narrow location and excite pixels along a length 468 that may be along substantially the entire width 464 of the detector 78. As discussed herein, the width of the slot 398 that results in a length of pixels 468 being excited (e.g., generating image data) limits or eliminates parallax distortion within the portion of an image collected by an imaging system using the slot filter assembly 300.

[0069] In addition, if Figure 5A and Figure 5B As shown, three sectors 440, 444, 448 can strike detector 78 substantially simultaneously from a single position of x-ray tube 190 along the Z-axis generally in the direction of double-headed arrow 114. Thus, detector 78 can output three different images or image data for three different x-ray positions at each single position of x-ray tube 190. However, movement of x-ray tube 190 of source unit 74 generally in the direction of double-headed arrow 114 can generate up to three views along the Z-axis, as discussed further herein. Each of sectors 440, 444, 448 can be separated by a selected distance, which can also be an angular distance 472.

[0070] The imaging system 36 can be used to generate images of the subject 28 for various purposes. As described above, images of the subject 28 can be generated to perform surgery on the subject 28, such as spinal fusion and / or implants associated with or ancillary to spinal fusion. Thus, in various embodiments, the user 24 can evaluate the subject 28 by viewing and evaluating the images of the subject 28 to determine the placement of a selected implant, such as a pedicle screw. Thus, the imaging system 36 can be used to acquire images of the subject 28. The imaging system 36 can be used to acquire one or more projections. As described above, the detector 78 detects x-rays that pass through the subject 28 or are attenuated by the subject. However, typically the detector 78 detects a single projection at a time. The imaging system 36, including the control system 64, can generate a long film or long view of the subject 28 by accumulating (e.g., stitching) multiple projections of the subject 28, alone or in combination with the processor system 48. In various embodiments, the imaging system 36 can therefore be operated to acquire multiple images.

[0071] Turn reference Figure 6 , a method 500 for acquiring an image, such as a long view of a subject 28, is shown. The method 500 may include or begin at a start block 510. The method 500 may then include positioning the subject 28 at a block 514. Positioning the subject 28 at block 514 may include positioning the subject 28, which may be a human patient, on the table 32 relative to the imaging system 36. Furthermore, as described above, the imaging system 36 may be a mobile imaging system, and thus positioning the subject 28 at block 514 may include moving the imaging system 36 relative to the subject 28. In particular, positioning the subject 28 may include positioning the subject 28 relative to the center or isocenter of the imaging system 36, such as within the gantry 70 and between the source unit 74 and the detector 78.

[0072] After positioning subject 28 in block 514, acquisition parameters may be set or entered in block 518. The input acquisition parameters may include a selected view length of subject 28, a desired or selected resolution, specific motion parameters for imaging system 36, or other suitable input parameters. For example, user 24 may enter the length or number of vertebrae to be imaged. Control system 64 may then determine the amount of motion, such as the length along the axial direction of the patient's long axis 106 and the direction of double-headed arrow 114. Furthermore, user 24 may choose to acquire image data that can be reconstructed into a three-dimensional model, as discussed herein. Thus, user 24, either manually or automatically via control system 64 or other suitable control or processor system, may determine to acquire images of subject 28 along at least the AP and lateral views to allow for reconstruction of a three-dimensional model. It will also be appreciated that only selected two-dimensional views of subject 28 may be acquired or selected, and thus only a single line scan may be acquired. It will also be appreciated that imaging system 36 may be used to acquire any suitable type of image of subject 28, and that the use of line scans for long views is merely exemplary. However, a line scan of subject 28 can be acquired by moving SDU 98 in a generally linear manner or direction from a starting point to an end point. In various embodiments, an AP view can be collected in a first direction along arrow 114 and SDU 98 can be rotated 90 degrees to collect a side view on a return path of the same length along arrow 114.

[0073] After the acquisition parameters are set in block 518, projections of the subject are acquired in block 522. The acquisition of projections may include acquiring slot or sector projections in a line scan of the subject 28. The acquisition of projections may include acquiring three sector projections at multiple locations along the line path of the source and detector and SDU 98, such as along the long axis 106 of the subject 28. The number of acquisitions may be selected based on the quality desired or selected for the final long view, including ensuring proper focus, minimizing or eliminating distortion (e.g., edge distortion), or other appropriate considerations.

[0074] After the projections are acquired in block 522, reconstruction of a long view, also known as a long film, is performed in block 526. The reconstruction of the long view may include various sub-steps and sub-algorithms, as discussed further herein, to form a selected reconstruction, such as a long view of the subject 28. The reconstruction may include various features, such as ensuring proper focus, iterating through multiple projections, etc. The multiple projections may then be stitched together to form a long view, either sequentially or to provide multiple long views, as discussed herein.

[0075] The long view can then optionally be saved in block 530. Saving the long view in block 530 can involve saving the long view in any suitable memory, such as imaging system memory 68 and / or processing system memory (non-transitory and / or transient memory 58). It is understood that saving the long view is optional and not required. The long view can then be displayed on a selected display device, such as display device 44, in block 534. Image 40 can include the long view reconstructed in block 536 or only the long view reconstructed in block 526. However, the display of the image in block 534 can also be used to illustrate the position of instrument 144, such as with the instrument icon or representation 180 discussed above.

[0076] Method 500 may then end at end block 540. Ending at block 540 may include stopping the operation of imaging system 36 and allowing the procedure to continue, as described above. In various embodiments, acquisition of the long view may be used to plan surgery on subject 28, such as prior to surgery or in the operating room during an intermediate step of the procedure. In addition, the long view may be acquired for various purposes, such as during the construction of a surgical step (e.g., placement of a first pedicle screw or other appropriate number of pedicle screws) or other steps. Thus, ending at block 540 may end the acquisition of the projections and reconstruction of the long view for display and use by user 24 or other appropriate user.

[0077] Continue to refer Figure 1-6 , and additionally refer to Figure 7 , Figure 6 The reconstruction of the long view shown in block 526 may include the following: Figure 7 The various sub-steps and / or sub-parts shown. Figure 7 The details of the long view reconstruction in block 526 are shown and may be incorporated into the above method 500. Thus, the method 500 may include the following: Figure 7 subsection shown.

[0078] Continue to refer Figure 7, the reconstruction of the long view (also referred to herein as the reconstructed long view) generally includes portions or sub-portions, as shown in block 526. It should be understood that various features and steps can be included as instructions, such as with an algorithm, that are executed by one or more processors or processor systems. For example, the imaging system processor 66 and / or the processor system 48 having the processor 56 can execute instructions to generate the long view based on the multiple projections acquired from block 522. As described above, the operation of the imaging system 36 can acquire multiple projections in block 522, for example, using the slot filter assembly 260. Thus, the imaging system 36 can generate projections based on the x-rays detected by the detector 78. Inputting the acquired projections in block 550 can initiate the reconstruction process shown in block 526. As discussed above and herein, the input of projections from three slots is exemplary and more or less is possible.

[0079] X-ray projections can be acquired at detector 78 using each of the three slots to produce a corresponding sector 440, 444, 448. Figure 7 , and additionally refer to Figure 8, each of the three sectors 440, 444, and 448 will produce three separate series of images or projections 560, 564, 568, respectively. Each series of projections includes multiple projections acquired substantially simultaneously. For example, the first series 560 may include a first image slice 560i acquired at the same location on the SDU 98 as the first images 564i and 568i of each of the corresponding sectors 440, 444, 448. As the SDU 98 moves in a selected direction, such as along the long axis 106 in the direction of arrow 114, multiple projections are acquired through each slot for each of the sectors 440, 444, 448. Thus, three series of projections 560, 564, 568 are acquired as a result of the movement of the imaging system 36 along the selected line scan. These series of projections 560, 564, 568 are the input projections from each of the three slots in block 550. As further discussed herein, while each slot and corresponding sector 440, 444, 448 is used to generate a corresponding series of projections 560, 564, 568, all image projections can be used to generate the long view reconstructed in block 526. Thus, the input from the x-ray projections of all three slots in 550 can include input from all three series of projections 560, 564, 568, which can be analyzed or evaluated individually in various portions of the reconstruction of block 526 and then combined to form the final long view, as further discussed herein. Due at least in part to the width of the slot 398 and the corresponding length 468 excited on the detector, each of the image slices used for each of the series (e.g., 560i, 564i, and 569i) is generally and / or substantially free of parallax distortion. Thus, due to the slice width 398, the slices can be sharper and have less error or distortion.

[0080] The procedure in block 526 also includes inputting a motion profile of the imaging system 36 in block 578. The input of the motion profile of the imaging system in block 578 may include distance traveled, time for distance traveled, distance between projection acquisitions, and other motion information about the imaging system 36. As discussed herein, the motion profile information may be used to determine and evaluate the relative positions of projections used for reconstruction.

[0081] After the x-ray projections are input from block 550, the focal plane may be set, for example, arbitrarily at a selected axis or line such as focal plane (fp) = 0 in block 590. fp = 0 may be defined as the isocenter of the imaging system 36. Figure 7 and Figure 8 , fp may be defined relative to the portion being imaged, such as the spine 28s of the subject 28. FP=0 may be an arbitrary position and is used to stitch or put together a series of projections in block 600 into a selected intermediate image for each slot.

[0082] like Figure 8 As shown, generating an intermediate image at the selected FP can generate an intermediate image for each of the series 560, 564, 568. Thus, a first intermediate image 610 can be generated based on the first series of projections 560. A second intermediate image 614 can be based on the series of projections 564 and a third intermediate image 618 can be based on the third series of projections 568. Each of the intermediate images 610, 614, 618 can be stitched together using well-known techniques such as image blending, registration, and view manipulation. These can include blending portions of closely matching images (e.g., determined to be similar portions) to achieve continuity. Registration involves matching or identifying identical portions of two or more images. As discussed herein, manipulation allows for altering different images or portions thereof.

[0083] As the SDU 98 moves relative to the subject 28, a plurality of projections, also referred to as image data portions, are captured in each series (e.g., the first series 560) at a selected rate. Figure 8 As shown, subject 28 may include spine 28s. For example, as SDU 98 moves, sector 440 moves a selected distance, such as 1 centimeter (cm) per projection acquisition. Thus, each of the image projections, such as image projection 560i, may be the width of sector 440 on the detector, and second image projection 560ii may be 1 cm from first image projection 560i and also the width of sector 440 on detector 78. A selected amount of overlap may occur between the two image projections 560i and 560ii, allowing them to be stitched together into an intermediate projection or image 610, as is known in the art. Thus, each of the series of projections 560, 564, 568 (each of which may include a portion of image data) may be stitched together at a corresponding focal plane to produce intermediate images 610, 614, 618. As described above, the focal plane may be initially set to zero or arbitrarily set to zero, which is typically the isocenter of imaging system 36 at which the plurality of projections 560, 564, 568 are acquired.

[0084] After generating an intermediate image at FP=0 for each slot in block 600, registration of the intermediate images for each slot and determination of the translation d occurs in block 680. Figure 7 And refer to Figure 9A and Figure 9B , the intermediate image is generated based on multiple projections caused by the movement of SDU 98. Figure 9A As shown, a schematic diagram of a first movement or distance d1 is shown. d1 can be the d discussed above. d1 is the distance that the source unit 74 can move from the first position 74i to the second position 74ii. Therefore, the narrow filter assembly 260 can also move from the first position 260i to the second position 260ii. Figure 9A As shown, the second sector 444 at the first position of the slot filter 260i and the first sector 440 at the second position of the slot filter 260ii may intersect or cross at the focal plane FP=1.

[0085] like Figure 9B As shown, the source unit 74 can be moved from the second position 74ii to the third position 74iii, and the slot filter can be moved from the second position 260ii to the third position 260iii, respectively. In this movement, a distance d2 may occur. Figure 9B The illustrated movement may include the middle or second sector 444 intersecting the first sector 440 at the second focal plane FP = 2. It is also understood that each of the other corresponding sectors may intersect at different locations, and the illustration of two sectors is merely exemplary. The discussion of the other sectors will not be repeated, but will be understood by those skilled in the art.

[0086] The location of the intersection of the sectors at the point being imaged (i.e., the distance from the x-ray tube 190) may depend on the location of the object being imaged, such as the spine 28s, from the x-ray tube 190. It will be appreciated by those skilled in the art that even if the isocenter of the imaging system 36 is moved along the long axis 106, the spine 28s may not be straight or extend along a line substantially parallel to the long axis 106 of the subject 28. Thus, as Figure 9A and Figure 9B As shown, the focal plane FP can be moved between different positions of the source unit 74 and the slot filter assembly 260. Thus, the first distance d1 can be different from the distance d2 and can also change the focal plane of the image or projection acquired with the imaging system 36. However, the first intermediate image generated in block 600 can assume that the focal plane is at the isocenter of the imaging system 36.

[0087] Continue to refer Figure 9A And refer to Figure 9B , showing a first intermediate image 610 and a second intermediate image 614. Intermediate images may include all intermediate images, including intermediate images 610, 614, and 618, and only first intermediate image 610 and second intermediate image 614 are discussed for clarity of the present discussion. However, intermediate images 610 and 614 may be registered with each other to determine or generate a registered image 640.

[0088] Registered image 640 may include a first end 644 that is equal to a first end 648 of first intermediate image 610 and a second end 654 that is equal to a second end 660 of second intermediate image 614. Thus, registered image 640 may be a composite or superposition of first intermediate image 610 and second intermediate image 614. In particular, an overlap region 664 may be determined or identified between first intermediate image 610 and second intermediate image 614. Overlap region 664 may be identified, for example, through feature-based registration, mutual information-based registration, or other suitable registration or image matching methods.

[0089] like Figure 9B As shown, second intermediate image 614 has second end 660 that is a distance 668 from second end 670 of first intermediate image 610. Distance 668 can be used or identified as a displacement distance d of the imaging system and can be used to change or determine the focal plane of each intermediate image, or the mutual focal plane of the intermediate images. Thus, distance d can be determined in block 680 due to registered image 640 determined by registering first intermediate image 610 and second intermediate image 614.

[0090] After determining the distance d, which may be a translation distance and is consistent with the slot filter spacing (e.g., distance 412), the focal plane, and the region of interest in the subject to be imaged (e.g., an anatomical region of interest, such as a particular vertebra or spinous process of a vertebra), in block 680, an updated focal plane FP containing the distance d may be prepared in block 684. The distance d, as Figure 9B As shown, the distance may be related to the distance adjustment used to achieve alignment of registration elements (e.g., spinous processes) between two or more intermediate images (e.g., images 610 and 614) to produce registered image 640. Additionally, the distance between the slots, such as distance 412, may be used to determine the translation distance d to achieve registered image 640. Even at the same location of slot filter assembly 260, image portions acquired through different slots are at different locations along the subject.

[0091] An updated FP based on the above analysis, including the location of the portion of interest (e.g., an anatomical structure of interest) within the subject, may then be input or iterated to generate an updated intermediate image using the updated FP in block 690. The iterative updated FP used to generate the updated image may account for the location of the subject or region of interest from the source unit 74 between two different intermediate images (e.g., image portions). Generation of the updated intermediate image may be substantially similar to generation of the intermediate image in block 600, except that the focal plane has been updated based on the determined translation d. Thus, since the focal plane is determined based on the translation of the image, the focus of the intermediate image may be increased or refined, as determined above, such as Figure 9BThe updated images generated in block 690 may then be combined in a combination of the intermediate images and the weighting function in block 700. As discussed above and herein, the inclusion of three intermediate images based on three slots is merely exemplary, and more or fewer slots may be permitted or used.

[0092] However, before generating the combination in block 700, a determination may be made in block 692 whether to further update the intermediate image. For example, at least two iterations may occur to determine whether a selected minimum value has been reached. If the minimum value has not been reached, further iterations may occur. Regardless of the determination, a decision may be made in block 692 whether to further update fp. If an update is made, a "yes" path 694 may be followed, the fp position may be updated in block 684, and the process may iterate. If further updates are not desired or selected, a "no" path 696 may be followed to combine the three intermediate images in block 700.

[0093] Continue to refer Figure 7 And refer to Figure 10 The intermediate images updated in block 690 may include a first updated intermediate image 610u, a second updated intermediate image 614u, and a third updated intermediate image 618u. As described above, each of the three intermediate images 610u, 614u, and 618u may then be combined to produce a first or initial long view or long film image 704.

[0094] The generation or merging of various intermediate images (e.g., each of the three intermediate images 610u, 614u, and 618u) can include various steps and features. In various embodiments, when generating each of the three intermediate images 610u, 614u, and 618u, initial deformations of various features can be performed. As described above, each of the three intermediate images 610u, 614u, and 618u can be generated based on multiple projections. Thus, each of the three intermediate images 610u, 614u, and 618u can include similar or identical features (e.g., vertebrae). The amount of deformation used to generate each of the three intermediate images 610u, 614u, and 618u can be determined and used in further merging procedures.

[0095] According to various embodiments, a weighting function 710 may be used to assist in the combination of updated intermediate images 610u, 614u, and 618u to produce the initial long view image 704. The weighting function 710 is used in Figure 10. A first weighting function for first sector 440w illustrates that, due to the position of sector 440, pixels or image portions may be weighted more heavily toward the leftmost portion of the long view. Middle or center sector 444 may have function 444w, which, due to the position of sector 444, weights pixels in the middle of long view 704 from updated image 614u more heavily. Finally, due to the position of sector 448 within long view 704, sector 448 may have function 448w to weight pixels at the far right or end. It should be understood that other suitable stitching functions may be used to generate initial long view 704, and that weighting function 710 is merely exemplary. Furthermore, greater weight may be assigned to intermediate images 610u, 614u, and 618u selected to exhibit the least distortion when generating the long view. Furthermore, selected distortions, such as geometric distortions, may be applied when generating the long view.

[0096] In various embodiments, the initial long view 704 may be output as a long view or long view in block 720. The long view output in block 720 may be saved, for example, saved in block 530 and / or displayed in block 532, as described above. Figure 6 However, in various embodiments, various normalizations and / or processing may be applied to the initial long view 704 before the long view is output in block 720, such as for image enhancement and / or clarity.

[0097] Continue to refer Figure 7 Various procedures may be performed before the final 2D long film or long view image is output in block 720. After the three intermediate images are combined with the weighting function, various processing steps may be performed before the long view image is displayed and / or saved. For example, air normalization may be applied in block 730 and / or further post-processing may be applied for visualization in block 740.

[0098] Air normalization can account for or minimize the effects of the slot filter assembly 260. Figure 5A and Figure 5B As shown, a sector, such as sector 448, contacts or impinges on detector 78 for a length distance 468. Distance 468 is a small fraction of detector 78. Furthermore, due to the narrow size of sector 448, the number of pixels contacting detector 78 is small, and the image or pixel intensity may drop rapidly from the peak intensity pixel or point 744, for example, at a value of Figure 11 Gaussian method shown.

[0099] 744 can be at the center of sector 448, e.g., at the center of distance 468 at a pixel or point on detector 78. Within five pixels from the center pixel (i.e., a width of 10 pixels, including the peak intensity pixel), an intensity drop of approximately 25% (e.g., the 6th pixel may have an intensity of approximately 75% of the peak intensity pixel 744) can be observed in pixels outside of the 10 pixels centered about the pixel with peak intensity 744. Within 10 pixels from the center pixel (i.e., a width of 20 pixels, including the peak intensity pixel), an intensity drop of approximately 66% (e.g., the intensity of the 11th pixel may have an intensity of approximately 33% of the peak intensity pixel 744) is observed. Thus, the narrow band of pixels can include all or substantially all of the intensity due to sector 448. It should be understood that each of the other sectors 440, 444 can include or have similar pixel intensity drops.

[0100] 700 , the image is normalized in the reconstruction to reduce or eliminate distortion that might otherwise be observed. For example, when stitching together multiple narrow images, such as image 460i with image 460ii, if normalization does not occur, the edges of the images may be substantially light or have almost no pixel intensity relative to the center pixel. Without masking and normalization, when stitched or combined, the combined images may have a "moiré effect" that can be seen in the stitched image. Due to the variation in pixel intensity across the multiple stitched images, where the amount of pixel intensity drop is significant across a narrow band or width of pixels, the moiré effect may alternate between dark and light bands.

[0101] Further post-processing for visualization may occur in block 740. Various post-processing may include any suitable post-processing to aid in visualization of the combined image from block 700. For example, in various embodiments, normalization or histogram averaging of the image (e.g., of pixel intensities) may occur. For example, the final reconstruction may divide the stitched pixel values ​​by the cumulative pixel values ​​to help reduce or minimize large variations between high-contrast and low-contrast areas in the combined image from block 700. Thus, the image may be prepared for viewing through further post-processing in block 740. Post-processing may include, but is not limited to, enhancing anatomical features, highlighting anatomical features (e.g., masking), sharpening edges, and the like.

[0102] Thus, in view of the above, imaging system 36 can be used to acquire multiple projections of subject 28. Multiple projections of subject 28 can be acquired in a linear manner, such as in a first line scan in the AP (anterior to posterior) direction and a second line scan in the lateral direction. The multiple projections can then be stitched or combined into a single long view or long film view of subject 28. Various intermediate steps, such as those discussed above, can be performed to help perform or produce a single long view. For example, multiple slots in a filter can be used to produce multiple intermediate images, which are then ultimately stitched together to form a single long view. However, imaging system 36 can be used to produce a long view of subject 28.

[0103] Furthermore, each slot in slot filter assembly 260 can allow for the acquisition of a different "view" of subject 28 during a scan of subject 28. For example, each of the three sectors 440, 444, and 448 acquires a projection at a single location on SDU 98. Thus, the perspective of subject 28 may be different in each view. Thus, according to various known techniques, a three-dimensional model of subject 28 can be reconstructed using multiple views of subject 28 acquired even during a line scan of the subject. As described above, a line scan of the subject can be a substantially linear movement, e.g., approximately parallel to the long axis 106 of subject 28. Thus, SDU 98 may not rotate around subject 28 during the acquisition of a line scan. However, multiple projections from various perspectives can be used to reconstruct a three-dimensional model of subject 28 using a single line scan or two line scans (e.g., an AP and a lateral line scan). These multiple projections from various perspectives can also be used to locate items or features in high-contrast objects, such as bony anatomy or implants. Local locations from each of more than one slot projection can also be used to generate a three-dimensional model of the imaged subject. As understood in the art, the different positions in the plane determined in each projection can be used to generate a 3D model.

[0104] The foregoing description of the embodiments is provided for the purpose of illustration and description. The above description is not intended to be exhaustive or to limit the present invention. The individual elements or features of a particular embodiment are generally not limited to the particular embodiment, but are interchangeable where applicable and can be used in selected embodiments, even if not specifically shown or described. The individual elements or features of a particular embodiment can also be changed in many ways. Such variations are not considered to depart from the present invention, and all such modifications are intended to be included within the scope of the present invention.

[0105] It should be understood that the various aspects disclosed herein can be combined in combinations different from those specifically presented in the specification and drawings. It should also be understood that, depending on the instance, certain actions or events of any of the processes or methods described herein may be performed in different sequences, may be added, combined, or omitted entirely (e.g., all described actions or events may not be necessary for performing these techniques). In addition, for the purpose of clarity, although certain aspects of the present disclosure are described as being performed by a single module or unit, it should be understood that the technology of the present disclosure may be performed by a combination of units or modules associated with, for example, a medical device.

[0106] In one or more examples, the described techniques may be implemented in hardware, software, firmware, or any combination thereof. If implemented in software, the functions may be stored as one or more instructions or codes on a computer-readable medium and executed by a hardware-based processing unit. A computer-readable medium may include a non-transitory computer-readable medium, which corresponds to a tangible medium, such as a data storage medium (e.g., RAM, ROM, EEPROM, flash memory, or any other medium that can be used to store desired program code in the form of instructions or data structures and that can be accessed by a computer).

[0107] Instructions may be executed by one or more processors, such as one or more digital signal processors (DSPs), general-purpose microprocessors, application-specific integrated circuits (ASICs), field-programmable logic arrays (FPGAs), or other equivalent integrated or discrete logic circuits. Thus, the term "processor," as used herein, may refer to any of the foregoing structures or any other physical structure suitable for implementing the described techniques. Furthermore, the techniques may be fully implemented in one or more circuits or logic elements.

Claims

1. A method of creating a long view image of a subject, comprising: positioning an image detector at a first position relative to the subject; emitting x-rays from a source, the image detector detecting the emitted x-rays; using a slot filter assembly to split the emitted x-rays from the source into at least a first independent x-ray beam portion having a first beam area and a second independent x-ray beam portion having a second beam area, the slot filter assembly comprising a first slot and a second slot, the x-rays passing through the slot filter assembly being split into the first x-ray beam portion and the second x-ray beam portion; moving the image detector from the first position to a second position along a path relative to the subject; collecting a first plurality of image data portions with the first x-ray beam portion and a second plurality of image data portions with the second x-ray beam portion at a plurality of intermediate positions between the first position and the second position; determining an overlapping region of the first plurality of image data portions and the second plurality of image data portions; generating an intermediate image based on the determined overlap between each of the image data portions; as well as The long view image is displayed based at least in part on the generated intermediate image.

2. The method of claim 1 , wherein the plurality of image data portions are collected at the plurality of intermediate locations, the method further comprising: The emitted x-rays and / or attenuation of the emitted x-rays are detected at the image detector. The method of claim 2 , wherein emitting x-rays from the sources comprises emitting x-rays from a single source.

4. The method according to any one of claims 1 to 3, further comprising: selecting a portion of the subjects; as well as A motion profile is determined for said collecting said plurality of image data portions at said plurality of intermediate locations.

5. The method of claim 1 , wherein the plurality of image data portions are collected at the plurality of intermediate locations, the method further comprising: At least a first sub-plurality of image data portions based on the first x-ray beam portion and a second sub-plurality of image data portions based on the second x-ray beam portion are collected at each intermediate position of the plurality of intermediate positions.

6. The method of claim 1 , wherein dividing the emitted x-rays from the source into at least the first x-ray beam portion and the second x-ray beam portion further comprises: The emitted x-rays are passed through a slot filter to impinge at least the first x-ray beam portion and the second x-ray beam portion onto the image detector.

7. The method according to claim 6, further comprising: moving the source and the image detector together; The collected plurality of image data portions includes a first sub-plurality of image data portions based on the first x-ray beam portion and a second sub-plurality of image data portions based on the second x-ray beam portion.

8. The method according to claim 1, further comprising: moving the image detector along the path in a first orientation relative to the subject; as well as moving the image detector along the path in a second orientation relative to the subject; wherein the first orientation is different from the second orientation.

9. The method of claim 1 , wherein dividing the emitted x-rays from the source into at least the first x-ray beam portion and the second x-ray beam portion further comprises: dividing the emitted x-rays into at least a third x-ray beam portion and the first x-ray beam portion and the second x-ray beam portion; as well as The emitted x-rays are passed through a slot filter having at least a first slot, a second slot, and a third slot.

10. The method according to claim 9, further comprising: At least a first sub-plurality of image data portions based on the first x-ray beam portion, a second sub-plurality of image data portions based on the second x-ray beam portion, and a third sub-plurality of image data portions based on the third x-ray beam portion are collected at each of the plurality of intermediate positions.

11. The method of claim 10 , wherein generating the intermediate image based on the determined overlap between each of the image data portions, the method further comprising: generating a first intermediate image based on the first sub-plurality of image data portions based on the first x-ray beam portion; generating a second intermediate image based on the second sub-plurality of image data portions based on the second x-ray beam portion; as well as A third intermediate image is generated based on the third sub-plurality of image data portions based on the third x-ray beam portion.

12. The method according to claim 11, further comprising: registering said first sub-plurality of image data portions; registering the second sub-plurality of image data portions; as well as The third sub-plurality of image data portions are registered.

13. An imaging system for producing a long view image of a subject, comprising: an image detector operable to be positioned at a first position relative to a subject and a second position relative to the subject, wherein the image detector is operable to collect a plurality of image data portions at at least the first position, the second position, and a plurality of intermediate positions between the first position and the second position; a single source configured to emit x-rays toward the image detector; an imager movement system operable to move the image detector between the first position and a second position along a path relative to the subject; an image processor operable to execute instructions to: determining overlapping regions between at least a sub-plurality of the plurality of image data portions, and generating an intermediate image based on the determined overlap between at least a sub-plurality of the plurality of image data portions; as well as a display device operable to display an image based at least in part on the generated intermediate image; a substantially solid member having at least a first through slot and a second through slot; wherein the substantially solid member blocks the emitted x-rays from reaching the detector or the subject; Substantially only the x-rays pass through the first through slot and the second through slot, so as to split the x-ray beam into at least a first beam portion and a second beam portion, so as to reach the subject or the detector.

14. The system of claim 13, wherein the detector is operable to detect emitted x-rays and / or attenuation of the emitted x-rays.

15. The system of claim 13, wherein substantially only x-rays passing through the first and second through-slots form at least a first imaging portion and a second imaging portion at each of the plurality of intermediate positions.

16. The system of claim 15, wherein the imager movement system is configured to move the single source and the image detector substantially relative to each other along the path.

17. The system of claim 13, wherein the image detector is movable from a first orientation relative to the subject to a second orientation relative to the subject.

18. The system of claim 13, further comprising: a substantially solid member having at least a first through slot, a second through slot, and a third through slot; wherein the substantially solid member blocks the emitted x-rays from reaching the detector or the subject; Substantially only the x-rays passing through the first through-slot, the second through-slot, and the third through-slot reach the subject or the detector.

19. The system according to claim 13, A memory system is configured to store at least the plurality of image data portions or the intermediate images.

20. A method of creating a long view image of a subject, comprising: positioning an image detector at a first position relative to the subject; dividing and forming a single emitted x-ray beam into at least a first beam having a first beam region, a second beam having a second beam region, and a third beam having a third beam region, each of the first, second, and third beam regions being a beam region independent of the single emitted x-ray beam; moving the image detector and the single emitted x-ray beam along a path relative to the subject from the first position to a second position; collecting a first plurality of image data portions based on the first beam as the image detector moves to a plurality of intermediate positions between the first position and the second position; collecting a second plurality of image data portions based on the second beam as the image detector moves to the plurality of intermediate positions between the first position and the second position; collecting a third plurality of image data portions based on the third beam as the image detector moves to the plurality of intermediate positions between the first position and the second position; generating a first intermediate image based on the collected first plurality of image data portions; generating a second intermediate image based on the collected second plurality of image data portions; as well as A third intermediate image is generated based on the collected third plurality of image data portions.

Images