Accelerated higher resolution industrial radiography

Abstract

An example industrial radiography system allows higher resolution 2D radiographs to be generated using an accelerated higher resolution radiography process. An accelerated higher resolution radiography process uses pixel (e.g., grayscale) values from one or more lower resolution 2D radiographs to set pixel values for a first portion of higher resolution radiograph pixels of a higher resolution 2D radiograph. The remaining portion of the higher resolution radiograph pixel is set based on the analysis of the first portion. The accelerated higher resolution radiography process is faster than a more conventional process because the accelerated higher resolution radiography process requires a smaller number of lower resolution radiographs captured, thus saving time and / or reducing wear of the radiographic camera while still providing high quality higher resolution 2D radiographs.

Description

[0001] CROSS-REFERENCE TO RELATED APPLICATIONS

[0002] This application claims priority to and the benefit of U.S. Provisional Patent Application No. 63 / 521,159, filed on June 15, 2023, entitled “Accelerated Higher Resolution Industrial Radiography,” the entire contents of which are incorporated herein by reference. Technical Field

[0003] The present disclosure relates generally to industrial radiography and, more particularly, to accelerated, higher resolution industrial radiography. Background Art

[0004] Industrial radiography systems are used to acquire two-dimensional (2D) radiographic images of components used in industrial applications. Such industrial applications may include, for example, aerospace, automotive, electronics, medical, pharmaceutical, military and / or defense applications. The 2D radiographic images may be reviewed to inspect the part(s) for cracks, flaws and / or defects that may or may not be normally visible to the human eye.

[0005] By comparing such a system with the present disclosure set forth in the remainder of this application with reference to the accompanying drawings, the limitations and disadvantages of conventional and traditional methods will become clear to those skilled in the art. Summary of the invention

[0006] The present disclosure is directed to accelerated higher resolution industrial radiography substantially as shown in and / or described in conjunction with at least one of the accompanying drawings and as more fully set forth in the claims.

[0007] These and other advantages, aspects and novel features of the present disclosure will be more fully understood from the following detailed description and drawings, as well as details of illustrated examples of the disclosure. BRIEF DESCRIPTION OF THE DRAWINGS

[0008] Figure 1 An example of an industrial X-ray radiograph according to aspects of the present disclosure is shown.

[0009] Figure 2 It is a diagram showing various aspects of the present disclosure. Figure 1 Block diagram of an example X-ray radiography system of an industrial X-ray radiography machine.

[0010] Figure 3a to Figure 3b It is a display of various aspects according to the present disclosure Figure 2 A flow chart of example operations of an accelerated higher resolution radiography process of an X-ray radiography system.

[0011] Figure 4 It is a display of various aspects according to the present disclosure Figure 1 An example detector pixel grid of an X-ray detector 108 of an industrial X-ray radiograph.

[0012] Figure 5a to Figure 5b An example radiograph pixel grid is shown in accordance with aspects of the present disclosure.

[0013] Figure 6 It is shown how the example pixel grid of FIG. 3 may be shifted to different detector locations by an amount less than a sub-pixel in accordance with aspects of the present disclosure.

[0014] Figure 7 It is a display of various aspects according to the present disclosure Figure 1 Different example detector positions for an X-ray detector 108 of an industrial X-ray radiograph.

[0015] Figure 8a to Figure 8b Demonstrates how to use various aspects of the present disclosure Figure 5a The different lower resolution radiograph pixels of the different lower resolution 2D radiographs in the image are combined to set Figure 5b An example of pixel values ​​for a first portion of pixels of a higher resolution radiograph in a higher resolution 2D radiograph.

[0016] The drawings are not necessarily drawn to scale. Where appropriate, the same or similar reference numbers are used to refer to similar or identical elements in the drawings. For example, a reference number with a letter (e.g., lower resolution 2D radiograph 500a, higher resolution 2D radiograph 500b) represents an instance of the same reference number (e.g., 2D radiograph 500) without the letter. DETAILED DESCRIPTION

[0017] Some examples of the present disclosure relate to industrial radiography systems that use an accelerated sub-pixel sampling process to generate higher resolution 2D radiographs with more details than normal radiographs. In some examples, pixel (e.g., grayscale) values ​​in lower resolution radiograph pixels from one or more lower resolution 2D radiographs are used to set the pixel values ​​of a first portion of higher resolution radiograph pixels in a higher resolution 2D radiograph. Then, the pixel values ​​of the remaining portion of the higher resolution pixels can be set based on an analysis of the pixel values ​​from the first portion of the higher resolution radiograph pixels. This technique of using a lower resolution 2D radiograph to directly set only a portion of the higher resolution pixels instead of setting all pixels means that fewer lower resolution 2D radiographs need to be captured, thereby saving time and / or reducing wear compared to some other more traditional techniques, while still providing high quality higher resolution 2D radiographs. When generating and / or combining several higher resolution 2D radiographs to form a three-dimensional (3D) radiographic volume, model and / or image, the time saved (and / or reduced wear) using the accelerated sub-pixel sampling process is even more significant.

[0018] Some examples of the present disclosure relate to a non-transitory computer-readable medium comprising machine-readable instructions that, when executed by a processing circuit system, cause the processing circuit system to perform the following actions: capture a lower resolution radiograph of a sample using radiation emitted by a radiation emitter and detected by a radiation detector, the sample being positioned between the radiation emitter and the radiation detector in a radiation path of the radiation; and generate a higher resolution radiograph of the sample based on the lower resolution radiograph, the higher resolution radiograph comprising more pixels than the lower resolution radiograph, the higher resolution radiograph having higher resolution pixels, and the higher resolution radiograph being generated by setting first higher resolution pixel values ​​for a first portion of higher resolution pixels based on lower resolution pixel values ​​of the lower resolution radiograph, and setting remaining higher resolution pixel values ​​for a remaining portion of the higher resolution pixels of the higher resolution radiograph using an analysis of the first higher resolution pixel values ​​for the first portion of the higher resolution pixels.

[0019] In some examples, the lower resolution radiograph includes a first lower resolution radiograph of the sample when the radiation detector is in a first detector position and the sample is in a sample orientation relative to the radiation emitter or the radiation detector, the lower resolution pixel values ​​include a first lower resolution pixel value, and the non-transitory computer readable medium further includes machine readable instructions that, when executed by the processing circuit system, cause the processing circuit system to perform the following actions: when the radiation detector is in a second detector position and the sample is in the sample orientation, capture a second lower resolution radiograph of the sample, wherein the first higher resolution pixel value of the first portion of the higher resolution pixels is set based on the first lower resolution pixel value of the first lower resolution radiograph and the second lower resolution pixel value of the second lower resolution radiograph.

[0020] In some examples, the radiation detector includes a detector surface including a plurality of detector pixels, each of the plurality of detector pixels having a detector pixel size defined by a detector pixel width along a first detector axis and a detector pixel height along a second detector axis perpendicular to the first detector axis, the second detector position being offset from the first detector position by a first distance along the first detector axis or by a second distance along the second detector axis, the first distance being less than the detector pixel width, or the second distance being less than the detector pixel height. In some examples, the non-transitory computer-readable medium further includes machine-readable instructions that, when executed by the processing circuit system, cause the processing circuit system to perform the following actions: move the radiation detector from the first detector position to the second detector position using the positioning system. In some examples, the non-transitory computer-readable medium further includes machine-readable instructions that, when executed by the processing circuit system, cause the processing circuit system to display a visual representation of the higher resolution radiograph on a display screen.

[0021] In some examples, the non-transitory computer-readable medium further includes machine-readable instructions that, when executed by the processing circuitry, cause the processing circuitry to apply enhancement to the higher resolution pixels of the higher resolution radiograph. In some examples, the non-transitory computer-readable medium further includes machine-readable instructions that, when executed by the processing circuitry, cause the processing circuitry to construct a three-dimensional higher resolution radiographic volume using the higher resolution radiograph and one or more additional higher resolution radiographs.

[0022] Some examples of the present disclosure relate to an industrial radiography imaging system, the industrial radiography imaging system comprising: a radiation emitter, the radiation emitter being configured to emit radiation along a radiation path; a radiation detector positioned in the radiation path of the radiation, the radiation detector being configured to detect the radiation emitted by the radiation emitter; a sample support positioned between the radiation emitter and the radiation detector, the sample support being configured to support a sample at a sample position in the radiation path of the radiation; and an image acquisition system, the image acquisition system comprising: a processing circuit system and a memory circuit system, the memory circuit system comprising machine-readable instructions that, when executed by the processing circuit system, cause the processing circuit system to perform the following Action: Capturing a lower resolution radiograph of the sample using radiation detected by a radiation detector, and generating a higher resolution radiograph of the sample based on the lower resolution radiograph, the higher resolution radiograph including more pixels than the lower resolution radiograph, the higher resolution radiograph having higher resolution pixels, and the higher resolution radiograph being generated by setting first higher resolution pixel values ​​for a first portion of the higher resolution pixels based on lower resolution pixel values ​​of the lower resolution radiograph, and setting remaining higher resolution pixel values ​​for a remaining portion of the higher resolution pixels of the higher resolution radiograph using an analysis of the first higher resolution pixel values ​​for the first portion of the higher resolution pixels.

[0023] In some examples, the lower resolution radiograph includes a first lower resolution radiograph of the sample when the radiation detector is in a first detector position and the sample is in a sample orientation relative to the radiation emitter or the radiation detector, the lower resolution pixel values ​​include a first lower resolution pixel value, and the memory circuit system further includes machine readable instructions that, when executed by the processing circuit system, cause the processing circuit system to perform the following actions: when the radiation detector is in a second detector position and the sample is in the sample orientation, capture a second lower resolution radiograph of the sample, wherein the first higher resolution pixel value of the first portion of the higher resolution pixels is set based on the first lower resolution pixel value of the first lower resolution radiograph and the second lower resolution pixel value of the second lower resolution radiograph.

[0024] In some examples, the radiation detector includes a detector surface including a plurality of detector pixels, each of the plurality of detector pixels having a detector pixel size, the detector pixel size being defined by a detector pixel width along a first detector axis and a detector pixel height along a second detector axis perpendicular to the first detector axis, the second detector position being offset from the first detector position by a first distance along the first detector axis or by a second distance along the second detector axis, the first distance being less than the detector pixel width, or the second distance being less than the detector pixel height.

[0025] In some examples, the system further includes a positioning system configured to move the radiation detector from a first detector position to a second detector position. In some examples, the image acquisition system further includes a display screen configured to display a visual representation of the higher resolution radiograph. In some examples, the memory circuit system further includes machine readable instructions that, when executed by the processing circuit system, cause the processing circuit system to: apply enhancement to the higher resolution pixels of the higher resolution radiograph. In some examples, the memory circuit system further includes machine readable instructions that, when executed by the processing circuit system, cause the processing circuit system to: construct a three-dimensional higher resolution radiographic volume using the higher resolution radiograph and one or more additional higher resolution radiographs.

[0026] Some examples of the present disclosure relate to a method for accelerating the generation of higher resolution radiographs, the method comprising: capturing a lower resolution radiograph of a sample using radiation emitted by a radiation emitter and detected by a radiation detector, the sample being positioned between the radiation emitter and the radiation detector in a radiation path of the radiation; and generating a higher resolution radiograph of the sample based on the lower resolution radiograph via a processing circuit system, the higher resolution radiograph including more pixels than the lower resolution radiograph, the higher resolution radiograph having higher resolution pixels, and the higher resolution radiograph being generated by setting first higher resolution pixel values ​​for a first portion of higher resolution pixels based on lower resolution pixel values ​​of the lower resolution radiograph via the processing circuit system, and setting remaining higher resolution pixel values ​​for a remaining portion of the higher resolution pixels of the higher resolution radiograph using an analysis of the first higher resolution pixel values ​​for the first portion of the higher resolution pixels via the processing circuit system.

[0027] In some examples, the lower resolution radiograph includes a first lower resolution radiograph of the sample when the radiation detector is in a first detector position and the sample is in a sample orientation relative to a radiation emitter or a radiation detector, the lower resolution pixel values ​​include a first lower resolution pixel value, and the method further includes: when the radiation detector is in a second detector position and the sample is in the sample orientation, capturing a second lower resolution radiograph of the sample using the radiation detector, wherein the first higher resolution pixel value of the first portion of the higher resolution pixels is set based on the first lower resolution pixel value of the first lower resolution radiograph and the second lower resolution pixel value of the second lower resolution radiograph.

[0028] In some examples, the radiation detector includes a detector surface including a plurality of detector pixels, each of the plurality of detector pixels having a detector pixel size, the detector pixel size being defined by a detector pixel width along a first detector axis and a detector pixel height along a second detector axis perpendicular to the first detector axis, the second detector position being offset from the first detector position by a first distance along the first detector axis or by a second distance along the second detector axis, the first distance being less than the detector pixel width, or the second distance being less than the detector pixel height.

[0029] In some examples, the method further includes moving the radiation detector from the first detector position to the second detector position using the positioning system. In some examples, the method further includes applying enhancement to the higher resolution pixels of the higher resolution radiograph via the processing circuit system; and displaying a visual representation of the higher resolution radiograph on a display screen. In some examples, the method further includes constructing a three-dimensional higher resolution radiographic volume using the higher resolution radiograph and the one or more additional higher resolution radiographs via the processing circuit system.

[0030] Figure 1 An example industrial X-ray radiography machine 100 is shown. In some examples, the X-ray radiography machine 100 can be used to perform non-destructive testing (NDT), digital radiography (DR) scanning, computed tomography (CT), and / or other applications on a sample 102. In some examples, the sample 102 can be an industrial component and / or an assembly of components (e.g., an engine casting, a microchip, a bolt, etc.). In some examples, the sample 102 can be relatively small, so a more sophisticated, more detailed, and higher resolution radiography (e.g., radiographic imaging) process may be useful. Although primarily discussed in terms of X-rays for simplicity, in some examples, the industrial X-ray radiography machine 100 discussed herein can use radiation of other wavelengths (e.g., gamma rays, neutrons, etc.).

[0031] exist Figure 1 In an example of the present invention, the X-ray radiography machine 100 directs X-ray radiation 104 from an X-ray emitter 106 along a radiation path 105. The emitted radiation travels along the radiation path 105, passes through the sample 102, and then strikes (and / or is detected by) an X-ray detector 108. In some examples, the X-ray emitter 106 may include an X-ray tube configured to emit a cone or fan-shaped X-ray radiation. In some examples, the X-ray emitter 106 may emit X-ray radiation in an energy range of 20 kiloelectronvolts (keV) to 10 megaelectronvolts (meV).

[0032] In some examples, a two-dimensional (2D) digital radiograph (e.g., a radiographic image, an X-ray image, etc.) may be generated based on the X-ray radiation 104 incident on the X-ray detector 108. In some examples, the 2D radiograph may be generated by the X-ray detector 108 itself. In some examples, the 2D radiograph may be generated by the X-ray detector 108 in conjunction with a computing system 202 in communication with the X-ray detector 108 and / or the X-ray radiography machine 100 (see, e.g., Figure 2 )generate.

[0033] In some examples, 2D radiographs generated by the X-ray detector 108 (and / or associated computing system(s)) may be combined to form a three-dimensional (3D) radiographic volume and / or image. In some examples, 2D image slices of the 3D volume / image may also be formed. Although the terms "image" and / or "radiograph" are used herein as shorthand, it should be understood that "image" and / or "radiograph" may include representative data until the data is visually presented by one or more appropriate components (e.g., a display screen, a graphics processing unit, the X-ray detector 108, etc.).

[0034] In some examples, the X-ray detector 108 may include a flat panel detector (FDA), a linear diode array (LDA), and / or a lens-coupled scintillation detector. In some examples, the X-ray detector 108 may include a fluoroscopic detection system and / or a digital image sensor configured to indirectly receive an image via scintillation. In some examples, the X-ray detector 108 may be implemented using a sensor panel (e.g., a charge-coupled device (CCD) panel, a complementary metal oxide semiconductor (CMOS) panel, etc.) that is configured to directly receive X-rays and generate a digital image. In some examples, the X-ray detector 108 may include a scintillation layer / screen that absorbs X-rays and emits visible light photons, which are in turn detected by a solid-state detector panel (e.g., a CMOS X-ray panel and / or a CCD X-ray panel) coupled to the scintillation screen.

[0035] In some examples, the X-ray detector 108 (eg, a solid-state detector panel) may include detector pixels 404 (eg, see Figure 4 ). In some examples, the detector pixels 404 may correspond to portions of a scintillating screen. In some examples, the size of each detector pixel 404 may be in the range of tens to hundreds of microns. In some examples, the pixel size of the X-ray detector 108 may be in the range of 25 microns to 250 microns (e.g., 200 microns). In some examples, the detector pixels 404 may be arranged in a detector pixel grid 402 on the X-ray detector 108.

[0036] Figure 4 An example of a detector pixel grid 402 is shown, which is composed of a number of detector pixels 404. As shown, each detector pixel 404 has a pixel size determined by a pixel height (e.g., on the y-axis) and a pixel width (e.g., on the x-axis). In some examples, the x-axis can be approximately parallel (e.g., within 1-5 degrees) to one or more tracks 154 of the detector positioner 150 (described below with respect to Figure 1 In some examples, the y-axis can be substantially parallel to one or more posts 152 of the detector positioner 150 (discussed below). Figure 1 Discussion). Although the detector pixel 404 is Figure 4 In the example of , the detector pixels 404 are shown as squares with equal pixel height and pixel width, but in some examples, the detector pixels 404 can be rectangular with pixel height not equal to pixel width. For convenience, the term "pixel length" may be used in the following disclosure to refer to either / both pixel height and / or pixel width.

[0037] In some examples, when generating the 2D radiograph 500a, the 2D radiograph 500a is represented using an arrangement of radiograph pixels 504 (eg, a radiograph pixel grid 502) (see, e.g., Figure 5a ). In some examples, each 2D radiograph 500a captured using the X-ray detector 108 can have the same number (and / or same arrangement) of radiograph pixels 504 as the detector pixels 404 that the X-ray detector 108 has. In some examples, each radiograph pixel 504 can have an associated pixel (e.g., grayscale) value that is set based on radiation detected by the X-ray detector 108 in the vicinity of the corresponding detector pixel 404. Thereafter, the computing system 202 and / or the user interface (UI) 204 (see, e.g., Figure 2) can output a visual representation (e.g., an image) of the 2D radiograph 500a on a display screen (having its own display screen pixels) by appropriately arranging the same number of display screen pixels in the same manner as the radiograph pixels 504, wherein each display screen pixel has a display screen pixel value that is the same as (and / or related to, based on, etc.) the pixel value of the corresponding radiograph pixel 504.

[0038] Figure 5a A simple example of a 2D radiograph 500a is shown. Figure 5a In the example of , a 2D radiograph 500a is represented by a number of radiograph pixels 504a arranged in a radiograph pixel grid 502a. As shown, each radiograph pixel 504a in a given row (e.g., along the x-axis) of the radiograph pixel grid 502a has the same shade of gray, indicating a common pixel (e.g., grayscale) value for these radiograph pixels 504a. In contrast, each radiograph pixel 504a in a given column (e.g., along the y-axis) has a different shade of gray than each other radiograph pixel 504a in the column, indicating a different pixel (e.g., grayscale) value for each radiograph pixel 504a in the column.

[0039] In some examples, the size of each detector pixel 404 of the X-ray detector 108 may be a limiting factor in the resolution or detail of the 2D radiograph 500a captured by the X-ray detector 108 (and / or the associated computing system 202). This may be a problem when the sample 102 contains features that are finer (e.g., smaller / denseer, etc.) than the pixel size of the detector pixels 404 of the X-ray detector 108.

[0040] For example, a computer microchip may have very fine features that are smaller than the size of a detector pixel 404. Since each detector pixel 404 (and / or corresponding radiograph pixel 504a) can only have one pixel (e.g., grayscale) value, granularity differences that occur at scales (e.g., color and / or grayscale) that are smaller than the size of a detector pixel 404 may be lost. In such an example, sub-pixel (e.g., fewer than / smaller than a detector pixel 404) sampling is used to construct a higher resolution 2D radiograph 500b (see, e.g., Figure 5b) may be useful to construct a higher resolution 2D radiograph having higher resolution radiograph pixels 504b that are capable of expressing more detail than a lower resolution 2D radiograph 500a captured using the x-ray detector 108. As used herein, "sub-pixel sampling" refers to the process of constructing a higher resolution 2D radiograph 500b using several lower resolution 2D radiographs 500a captured at different detector positions of the x-ray detector 108, wherein each detector position is offset from at least one other detector position (and / or all other detector positions) by an amount of a sub-pixel (e.g., less than the pixel length of the detector pixel 404).

[0041] Figure 5b An example of a higher resolution 2D radiograph 500b is shown. Figure 5a As with the lower resolution 2D radiograph 500a in Figure 5b The higher resolution 2D radiograph 500b in FIG. 5 is represented by a number of higher resolution radiograph pixels 504b arranged in a radiograph pixel grid 502b. Figure 5a The lower resolution 2D radiograph 500a (and / or Figure 4 Compared to the detector pixel grid 402 in Figure 5b The higher resolution 2D radiograph 500b in FIG. 5 has a higher pixel density. Figure 5a The lower resolution 2D radiograph 500a (and / or Figure 4 Compared to the detector pixel grid 402 in Figure 5b The higher resolution 2D radiograph 500b in FIG. 5 is illustrated as having more (and smaller) higher resolution radiograph pixels 504b.

[0042] Specifically, Figure 5b The higher resolution 2D radiograph 500b shown in FIG. 4 has four times as many higher resolution radiograph pixels 504b as the lower resolution 2D radiograph pixel 500a has lower resolution radiograph pixels 504a (and / or detector pixels 404 of the detector pixel grid 402). In some examples, the number of higher resolution radiograph pixels 504b may be some other multiple (e.g., 2x, 6x, 8x, 10x, etc.) of the number of lower resolution radiograph pixels 504a (and / or detector pixels 404). Nonetheless, the two 2D radiographs 500 (and Figure 4 The detector pixel grids 402 in FIG. 4 are all illustrated as occupying (and / or representing) the same total area.

[0043] In some examples, the greater pixel density of the higher resolution 2D radiograph 500b may allow for a more detailed depiction of the sample 102 than the lower resolution 2D radiograph 500a. Figure 5a to Figure 5b , where both 2D radiographs 500a show a gradual progression from very light to very dark, but the higher resolution 2D radiograph 500b shows a finer, more gradual progression than the lower resolution 2D radiograph 500b.

[0044] exist Figure 1 In an example of the X-ray machine 100, the positioning system 199 includes a detector positioner 150, a sample positioner 110, and an emitter-detector positioner 150. In some examples, the detector positioner 150 is configured to move the X-ray detector 108 to different detector positions (e.g., for sub-pixel sampling). As shown, the detector positioner 150 includes two parallel posts 152 connected by two parallel rails 154. As shown, the X-ray detector 108 is held on the rails 154. In some examples, the X-ray detector 108 can be held on the rails 154 (and / or attached to the rails) by one or more intermediate supports.

[0045] In some examples, the detector positioner 150 can be configured to move the X-ray detector 108 along the track 154 toward and / or away from either of the posts 152. In some examples, the track 154 can be configured to move along and / or parallel to the posts 152 (e.g., upward and / or downward), thereby also moving the X-ray detector 108 along and / or parallel to the posts 152. Figure 1 , but in some examples, the detector positioner 150 may be more complex, similar to the x-translation stage 18, y-translation stage 20, detector mounting frame 26 and / or x / y-stage linear encoder 22 / 24 shown and described in the following patent: §371 U.S. Patent No. 9,459,217, dated September 30, 2015, and entitled "High-Resolution Computed Tomography", the entire contents of which are incorporated herein by reference.

[0046] In some examples, sample 102 can be moved by sample positioner 110. Figure 1In some examples, sample positioner 110 holds sample 102 in the path of X-ray radiation 104, between X-ray emitter 106 and detector 108. In some examples, sample positioner 110 may be configured to move sample 102 toward and / or away from X-ray emitter 106 and / or X-ray detector 108, thereby changing a geometric magnification (defined as the distance between X-ray emitter 106 and X-ray detector 108 divided by the distance between X-ray emitter 106 and sample 102). In some examples, sample positioner 110 may be configured to move and / or rotate sample 102 so that a desired portion and / or orientation of sample 102 is located in the path of X-ray radiation 104. In some examples, the sample positioner 110 can position the sample 102 at different angles / orientations relative to the X-ray emitter 106 and / or the X-ray detector 108 to obtain 2D radiographs 500a at different orientations, which can then be used to generate one or more three-dimensional (3D) images of the sample 102.

[0047] exist Figure 1 In the example of , the sample positioner 110 includes a rotatable clamp 112 on which the sample 102 is positioned. As shown, the rotatable clamp 112 is a circular plate. As shown, the rotatable clamp 112 is attached to a motorized spindle 116, by which the rotatable clamp 112 can be rotated around an axis defined by the spindle 116. In some examples, one or more alternative and / or additional rotation mechanisms may be provided.

[0048] exist Figure 1 In some examples, the rotatable fixture 112 is supported by a support structure 118. In some examples, the support structure 118 can be configured to translate the rotatable fixture 112 (and / or the sample 102) toward and / or away from the X-ray emitter 106 and / or the X-ray detector 108. In some examples, the support structure 118 can include one or more actuators configured to apply the translation(s).

[0049] Despite Figure 1 An example sample positioner 110 is shown in the example of FIG, but in some examples, a different sample positioner 110 can be used. For example, a robot object positioner can be used to translate and / or rotate the sample 102. Similarly, although in Figure 1In the example of 102 shown as a circular plate, in some examples, the rotatable clamp 112 may alternatively include a different clamp, such as a clip, a clasp, a clamp, and / or other retaining mechanism. In some examples, the X-ray emitter 106 and the X-ray detector 108 may alternatively rotate around the sample 102 instead of rotating the sample 102 via the rotatable clamp 112 (or a combination of the two) (for example, this may be helpful if the sample 102 is bulky).

[0050] exist Figure 1 In the example of , the X-ray machine 100 further includes an emitter-detector positioner 150. Figure 1 In the example of , the emitter-detector positioner 150 is depicted as a rotatable platform. In some examples, the emitter-detector positioner 160 is configured to move the X-ray emitter 106 and the X-ray detector 108 around the sample 102. Figure 1 In the example of FIG. 1 , the emitter-detector positioner 160 is shown as being raised above and connected to the X-ray emitter 106 and the X-ray detector 108, such as might occur when implemented using a gantry system.

[0051] In some examples, the emitter-detector positioner 160 may alternatively be implemented in a different manner, such as via a platform built into the floor of the X-ray machine 100, one or more robotic movers, a conveyor, and / or one or more other suitable devices. In some examples, the emitter-detector positioner 160 may be configured for rotation about different (e.g., horizontal, diagonal, etc.) axes, with the X-ray emitter 106 and / or the X-ray detector 108 being repositioned accordingly.

[0052] In some examples, one or more portions of sample positioner 110 (e.g., support structure 118) may be altered and / or omitted to facilitate use of (e.g., viewing of) X-ray emitter 106 and X-ray detector 108 while being moved about sample 102 by emitter-detector positioner 160. In some examples, emitter-detector positioner 160 may be configured to maintain the same geometric magnification of X-ray machine 100 while moving X-ray emitter 106 and X-ray detector 108 about sample 102. While much of the present disclosure discusses rotating sample 102 during accelerated, higher resolution radiography process 300, in some examples, X-ray emitter 106 and X-ray detector 108 may instead be rotated about sample 102, as discussed above.

[0053] Figure 2An example of an X-ray radiography system 200 is shown, which includes an X-ray radiography machine 100, for example, Figure 1 The X-ray radiography system 100 shown in FIG. As shown, the X-ray radiography system 200 also includes a computing system 202, a user interface (UI) 204, and a remote computing system 299. Figure 2 In the example shown, only one X-ray radiography machine 100, computing system 202, UI 204 and remote computing system 299 are shown, but in some examples, the X-ray radiography system 200 may include several X-ray radiography machines 100, computing systems 202, UI 204 and / or remote computing systems 299.

[0054] exist Figure 2 In the example of , the X-ray radiography system 100 has an emitter 106, a detector 108, and a positioning system 199 (including a sample positioner 110, a detector positioner 150, and an emitter-detector positioner 150) surrounded by a housing 199. As shown, the X-ray radiography system 100 is connected to and / or communicates with (multiple) computing systems 202 and (multiple) UIs 204. In some examples, the X-ray radiography system 100 can also communicate electrically with (multiple) remote computing systems 299. In some examples, the communication and / or connection can be electrical, electromagnetic, wired, and / or wireless.

[0055] exist Figure 2 In some examples, the UI 204 includes one or more input devices 206 and / or output devices 208. In some examples, the one or more input devices 206 may include one or more touch screens, mice, keyboards, buttons, switches, sliders, knobs, microphones, dials, and / or other electromechanical input devices. In some examples, the one or more output devices 208 may include one or more display screens, speakers, lights, tactile devices, and / or other devices. In some examples, a user can provide input to and / or receive output from (multiple) X-ray radiography cameras 100, (multiple) computing systems 202, and / or (multiple) remote computing systems 299 via (multiple) UIs 204.

[0056] In some examples, the UI(s) 204 can be part of the computing system 202. In some examples, the computing system 202 can implement one or more controllers of the X-ray radiography machine(s) 100. In some examples, the computing system 202 can constitute an image acquisition system of the X-ray radiography system 200 together with the UI(s) 204. In some examples, the remote computing system(s) 299 can be similar or identical to the computing system 202.

[0057] exist Figure 2 In the example of , the computing system 202 communicates (e.g., electrically) with (multiple) X-ray radiography machines 100, (multiple) UIs 204, and (multiple) remote computing systems 299. In some examples, the communication can be direct communication (e.g., through wired and / or wireless media) or indirect communication, for example, through one or more wired and / or wireless networks (e.g., local area networks and / or wide area networks). As shown, the computing system 202 includes a processing circuit system 210, a memory circuit system 212, and a communication circuit system 214 interconnected to each other via a common electrical bus.

[0058] In some examples, processing circuit system 210 may include one or more processors. In some examples, communication circuit system 214 may include one or more wireless adapters, wireless cards, cable adapters, line adapters, radio frequency (RF) devices, wireless communication devices, Bluetooth devices, devices compliant with IEEE 802.11, WiFi devices, cellular devices, GPS devices, Ethernet ports, network ports, lightning cable ports, cable ports, etc. In some examples, communication circuit system 214 may be configured to communicate via one or more wired media and / or protocols (e.g., (multiple) Ethernet cables, (multiple) Universal Serial Bus cables, etc.) and / or wireless media and / or protocols (e.g., near field communication (NFC), ultra-high frequency radio waves (commonly known as Bluetooth), IEEE 802.11x, Zigbee, HART, LTE, Z-Wave, Wireless HD, WiGig, etc.).

[0059] exist Figure 2 In some examples, the memory circuit system 212 includes and / or stores an accelerated higher resolution radiography process 300. In some examples, the accelerated higher resolution radiography process 300 can be implemented via machine-readable (and / or processor-executable) instructions stored in the memory circuit system 212 and / or executed by the processing circuit system 210. In some examples, the accelerated higher resolution radiography process 300 can be performed as part of a larger scanning and / or imaging process of the X-ray radiography system 200. Although some of the disclosure below discusses the accelerated higher resolution radiography process 300 performing certain actions, this should be understood as a simple form: that is, one or more components of the X-ray radiography system 200 (e.g., the processing circuit system 210, the communication circuit system 214, the UI 204, the radiography machine 100, etc.) perform (multiple) actions as part of the accelerated higher resolution radiography process 300.

[0060] In some examples, the accelerated higher resolution radiography process 300 can use sub-pixel sampling in conjunction with pixel analysis to generate one or more higher resolution 2D radiographs 500b faster than conventional sub-pixel sampling. While in some conventional sub-pixel sampling examples, several lower resolution 2D radiographs 500a are captured and the lower resolution radiograph pixels 504a of the lower resolution 2D radiographs are used to set the pixel values ​​of all higher resolution radiograph pixels 504b, in the accelerated higher resolution radiography process 300, the lower resolution radiograph pixels 504a are only used to set the pixel values ​​of the first portion of the higher resolution radiograph pixels 504b instead of all. The pixel values ​​of the remaining portion of the higher resolution radiograph pixels 504b are set using analysis of the pixel values ​​of the first portion of the higher resolution radiograph pixels 504b. Because only a portion of the pixel values ​​of the higher resolution pixels are set using the lower resolution 2D radiographs instead of all, fewer lower resolution 2D radiographs 500a need to be captured, thereby saving time and / or reducing wear and tear on the radiography machine 100 while still providing high quality higher resolution 2D radiographs.

[0061] Figure 3a is a flow chart illustrating example operations of the accelerated higher resolution radiography process 300. Figure 3a In the example of FIG. 3 , the accelerated higher resolution radiography process 300 begins at block 302 . At block 302 , the accelerated higher resolution radiography process 300 identifies one or more parameter values ​​that may be used during the accelerated higher resolution radiography process 300 .

[0062] In some examples, these parameter values ​​may include values ​​related to the type / size / geometry of the sample 102, the starting position / orientation / magnification of the sample 102, the target total rotation of the sample 102 (e.g., between 1-360 degrees, inclusive), the target rotation increment of the sample 102 (e.g., 1 degree, 5 degrees, etc.), the geometric magnification of the X-ray detector 108, the target higher resolution, the resolution, one or more target positions of the X-ray detector 108, one or more target position changes of the X-ray detector 108, one or more position change triggers of the X-ray detector 108, one or more target analyses, one or more shift correction techniques, and / or other relevant information. In some examples, the accelerated higher resolution radiography process 300 may prompt the user to enter one or more of these parameter values, for example, via the UI 204.

[0063] In some examples, the accelerated higher resolution radiography process 300 can automatically identify one or more of these parameter values ​​(e.g., if not provided by the UI 204). For example, if the target total rotation of the sample 102 remains unset, the accelerated higher resolution radiography process 300 can default to 360 degrees. In some examples, the accelerated higher resolution radiography process 300 can automatically identify one or more of these parameter values ​​based on one or more other parameter values. For example, the accelerated higher resolution radiography process 300 can identify an ideal (and / or default) geometric magnification value based on the resolution of the x-ray detector 108 and / or the target higher resolution, such as through a data structure (e.g., a lookup table, a database) stored in the memory circuit system 212 and / or a dynamic algorithm calculation.

[0064] exist Figure 3a In the example of , after block 302, the accelerated higher resolution radiography process 300 proceeds to block 304, where the accelerated higher resolution radiography process 300 arranges the X-ray detector 108, the X-ray emitter 106, and / or the sample 102 (e.g., via the positioning system 199) to present a starting view (e.g., orientation, magnification, or position) of the sample 102 (e.g., relative to the X-ray detector 108 and / or the X-ray emitter 106). In some examples, the starting view of the sample 102 can be determined based on one or more parameter values ​​input and / or determined at block 302. In some examples, the starting view places the sample 102 at a particular orientation relative to the X-ray detector 108 (and / or the X-ray emitter 106).

[0065] After block 302, the accelerated higher resolution radiography process 300 proceeds to block 306, where the accelerated higher resolution radiography process 300 moves the X-ray detector 108 (e.g., via the positioning system 199) to a first detector position. In some examples, the first detector position may be determined based on one or more parameter values ​​input and / or determined at block 302. In some examples, the accelerated higher resolution radiography process 300 may use one or more sensors (e.g., position sensor(s), angle sensor(s), etc.) of the radiography machine 100 to determine the position of the X-ray detector 108, and / or when the X-ray detector 108 has been properly positioned.

[0066] After block 306, the accelerated higher resolution radiography process 300 proceeds to block 308, where the accelerated higher resolution radiography process 300 captures a lower resolution 2D radiograph 500a based on the X-ray radiation 104 incident on the X-ray detector 108 while the X-ray detector 108 is in the first detector position and the sample 102 is in the starting view. In some examples, the sample 102 and / or the X-ray detector 108 (e.g., via the positioning system 199) remain stationary while the lower resolution 2D radiograph 500 is captured. In some examples, the lower resolution 2D radiograph 500a may be stored in the memory circuitry 212.

[0067] exist Figure 3a In the example of FIG. 3 , after block 308, the accelerated higher resolution radiography process 300 proceeds to block 310 where the accelerated higher resolution radiography process 300 determines whether the X-ray detector 108 should be moved to another detector position while the sample 102 is in the same view. In some examples, this determination may be made based on one or more parameter values ​​input and / or determined at block 302 and / or the number of times the X-ray detector 108 has been previously moved while the sample 102 is in the same view (and / or the number of times blocks 306-310 have been performed).

[0068] In some examples, the accelerated higher resolution radiography process 300 may use only one detector position while the sample 102 is in a given view. In some examples, the accelerated higher resolution radiography process 300 may use two or more detector positions while the sample 102 is in a given view. In some examples using more than one detector position, each detector position used by the accelerated higher resolution radiography process 300 when the sample 102 is in a given view may be offset from each other (or from at least one other) detector position when the sample 102 is in the given view by an amount that is less than the pixel length of the detector pixel 404 (e.g., less than the pixel width on the x-axis and / or the pixel height on the y-axis).

[0069] Figure 6 An example of how two detector positions can be offset from each other by an amount less than the detector pixel length is shown. Figure 6In the example of , two different detector pixel grids 402 of detector pixels 404 are shown, indicating two different positions of the x-ray detector 108. A first detector pixel grid 402a of detector pixels 404a is depicted using solid lines, while a second detector pixel grid 402b of detector pixels 404b is depicted using dashed lines. As shown, the two different detector pixel grids 402 are offset from each other by an amount less than a pixel length. Specifically, the position of the detector pixel grid 402b is offset from the position of the detector pixel grid 402a in the positive x-direction by half a detector pixel 404, and in the negative y-direction by half a pixel (resulting in an offset in the diagonal direction of less than one detector pixel 404). This offset of less than the pixel length of one detector pixel 404 can be referred to as a sub-pixel offset. Although for reasons of clarity and explanation, the detector pixel grids 402 are shown as being offset from each other in the diagonal direction, in some examples, the detector pixel grids 402 may be offset only in the x-axis or only in the y-axis.

[0070] Figure 7 An example of four different detector positions that are offset from each other by sub-pixels is shown: I, II, III, and IV. Figure 7 , the larger dashed rectangle represents the outer perimeter (and / or maximum range of motion) of the X-ray detector 108 at all different detector positions I, II, III, and IV. The X-ray detector 108 is shown as a smaller solid gray rectangle located at different detector positions I, II, III, and IV within the dashed rectangle. As shown, each detector position is offset from each other detector position by less than the detector pixel 404.

[0071] exist Figure 7 In the example of FIG. 1 , the first detector position (I) and the second detector position (II) of the X-ray detector 108 correspond to Figure 6 402a and 402b in the dashed line perimeter. With respect to the position within the dashed line perimeter, the X-ray detector 108 is located in the upper left corner at the first detector position (I) and in the lower left corner at the second detector position (II). The depicted third detector position (III) and fourth detector position (IV) are approximate mirror images of the first detector position (I) and the second detector position (II), respectively. With respect to the position within the dashed line perimeter, the X-ray detector 108 is located in the upper right corner at the third detector position (III) and in the lower right corner at the fourth detector position (IV).

[0072] exist Figure 3aIn the example of FIG. 1 , if the accelerated higher resolution radiography process 300 determines at block 310 that the X-ray detector 108 should be moved to a different detector position, the accelerated higher resolution radiography process 300 returns to block 306 and moves the X-ray detector 108 to the next detector position. For example, the first detector position may be Figure 7 The detector position shown is I, and the next detector position can be Figure 7 108 is moved to a different detector position, as discussed above. Blocks 306-310 continue to be executed until the accelerated higher resolution radiography process 300 determines at block 310 whether the X-ray detector 108 should not be moved to a different detector position.

[0073] In some examples, the number of detector positions used by the accelerated higher resolution radiography process 300 when the sample 102 is in a given view can be less than the number of higher resolution radiograph pixels 504b in the higher resolution 2D radiograph 500b divided by the number of lower resolution radiograph pixels 504a in the lower resolution 2D radiograph 500a. Thus, for example, when the number of higher resolution radiograph pixels 504b is four times the number of lower resolution radiograph pixels 504b (e.g., as Figure 5a to Figure 5b ), the number of detector positions used by the accelerated higher resolution radiography process 300 when the sample 102 is in a given view may be less than four. This is in contrast to some conventional sub-pixel sampling examples, where the x-ray detector 108 may be moved to Figure 7 The four positions (I, II, III, IV) shown in FIG.

[0074] If the accelerated higher resolution radiography process 300 determines at block 310 that the X-ray detector 108 should not be moved to a new detector position, the accelerated higher resolution radiography process 300 proceeds to block 312 where the accelerated higher resolution radiography process 300 determines (e.g., based on the parameter(s) identified at block 302) whether another view (e.g., orientation, magnification, or position) of the sample 102 is desired. For example, if a higher resolution three-dimensional (3D) radiographic volume, model, and / or image is to be constructed (e.g., using several higher resolution 2D radiographs 500a), the accelerated higher resolution radiography process 300 may determine that another orientation of the sample 102 is desired until the sample 102 has been rotated 360 degrees. In contrast, if only a single higher resolution 2D radiograph 500a is desired, the accelerated higher resolution radiography process 300 may determine that another orientation of the sample 102 is not desired. In another example, if several higher resolution 2D radiographs 500a are needed, the accelerated higher resolution radiography process 300 can determine that another orientation of the sample is needed, even if a 3D radiography volume is not constructed. In another example, the accelerated higher resolution radiography process 300 can determine that the parameters require a different magnification or position of the sample 102 (e.g., relative to the X-ray detector 108 or the X-ray emitter 106).

[0075] exist Figure 3a In the example of , if the accelerated higher resolution radiography process 300 determines that another view of the sample 102 is needed, the accelerated higher resolution radiography process 300 proceeds to block 314, where the accelerated higher resolution radiography process 300 moves the sample 102 and / or the X-ray emitter 106 and the X-ray detector 108 (e.g., via the positioning system 199) to place the sample 102 in the next view. In some examples, the next view of the sample 102 can be determined based on the current view of the sample 102 and / or one or more parameters identified at block 302. For example, the parameter(s) can identify a series of specific orientations of the sample 102, or incremental rotation degrees for changing the orientation of the sample 102 a certain number of times or until a final target orientation or rotation degree is reached. In some examples, the accelerated higher resolution radiography process 300 can use one or more sensors of the radiography machine 100 (e.g., position sensor(s), angle sensor(s), etc.) to determine a view of the sample 102 (e.g., relative to the X-ray emitter 106 and / or the X-ray detector 108) and / or when to obtain the next view of the sample 102.

[0076] After block 314, the accelerated higher resolution radiography process 300 returns to block 306, where the accelerated higher resolution radiography process 300 moves the X-ray detector 108 to another detector position. In some examples, this movement may be a sub-pixel movement (e.g., moving the X-ray detector 108 from detector position II back to detector position I, or from detector position II to detector position III or IV). In some examples, this movement may be skipped (e.g., keeping the X-ray detector 108 at detector position II).

[0077] Although in Figure 3a In the example of FIG. 3 , the detector position determination of block 310 is shown as controlling the inner loop, and the sample view determination of block 312 is shown as controlling the outer loop, but in some examples, this arrangement can be reversed. In the reversed case, blocks 306 and 314 can effectively swap positions, and blocks 310 and 312 can effectively swap positions. However, as discussed below, this reversal can make shift correction more difficult.

[0078] exist Figure 3a In the example of , blocks 306-314 continue to repeat until the accelerated higher resolution radiography process 300 determines that no further views of the sample 102 require capturing the lower resolution 2D radiograph 500a. Once this determination is made, the accelerated higher resolution radiography process 300 proceeds to block 316, where the higher resolution radiography process 300 performs shift correction on the captured lower resolution 2D radiograph 500a.

[0079] Shift correction refers to correction for unexpected and / or undesirable shifts in the radiation focal spot on the X-ray detector 108, which may occur over time, for example due to thermal effects. In some examples, such shifts in the focal spot may cause a shift in the viewing angle of the lower resolution 2D radiograph 500a. In some examples, the degree of shift that occurs during the time it takes to perform a 360-degree scan may be measured based on a comparison of two lower resolution 2D radiographs 500a taken at the beginning and end of a 360-degree scan, where for these two lower resolution 2D radiographs 500a, the X-ray detector 108 is in the same position and the sample 102 is in the same orientation (e.g., the sample 102 is rotated 0 degrees and rotated 360 degrees). In some examples, a corrective action may be determined based on the shift, and the corrective action may be applied to one or more lower resolution 2D radiographs 500a captured during the 360-degree scan to compensate for the shift. Such shift correction may improve the quality and / or consistency of the lower resolution 2D radiographs 500a. Since shift correction requires a full 360 degree scan (and / or rotation of sample 102), block 316 may be skipped if a full 360 degree scan (and / or rotation of sample 102) is not performed.

[0080] Conventional 360-degree sub-pixel sampling scans may not be able to utilize shift correction. This is because in conventional 360-degree sub-pixel sampling scans (e.g., 3D reconstruction), the X-ray detector 108 moves from a first detector position (e.g., detector position I) to a second detector position (e.g., detector position II) only after a full 360-degree scan (and / or a rotation of the sample 102) is completed. In addition, the shift of the focal spot may be different during different scans (and / or 360-degree rotations of the sample 102). Therefore, even if the shift is measured at the end of a first full scan when the X-ray detector 108 is at the first detector position (e.g., detector position I) and at the end of a second full scan when the X-ray detector 108 is at the second detector position (e.g., detector position II), the shift measured in the two scans may be significantly different. Therefore, the correction determined may be significantly different. If different corrections are applied to their corresponding sets of lower resolution 2D radiographs 500a and then the two sets of lower resolution 2D radiographs 500a are interlaced to generate higher resolution 2D radiographs 500b, image quality degradation, loss of detail, reduced clarity, blurring, distortion, artifacts and / or other negative consequences may occur.

[0081] In contrast, in the example, Figure 3aThe illustrated accelerated higher resolution radiography process 300 requires only one 360 ​​degree scan (and / or rotation of the sample 102) to be performed. All different detector positions of the X-ray detector 108 can be completed during one 360 ​​degree scan (and / or rotation of the sample 102).

[0082] Thus, for example, detector positions I and II may be used when the sample 102 is at 0 and 360 degrees of rotation. In such an example, the shift may be measured by comparing the lower resolution 2D radiographs 500a obtained at 0 and 360 degrees for detector positions I and / or II. And since the time difference between capturing the lower resolution radiographs 500a at detector positions I and II will be minimal, the difference in the measured offset and / or the determined correction should be minimal. In fact, in some examples, the shift may be measured only once to save time. Thus, the shift correction may be applied in the accelerated higher resolution radiography process 300, thereby improving the quality and / or consistency of the lower resolution 2D radiographs 500a.

[0083] exist Figure 3a In some examples, the accelerated higher resolution radiography process 300 generates one or more higher resolution 2D radiographs 500b after shift correction of the lower resolution 2D radiograph 500a, and / or sets pixel values ​​of the higher resolution 2D radiograph(s) 500b at block 350 during the accelerated higher resolution pixel setting process 350. In some examples, the pixel values ​​of the higher resolution radiograph pixels 504b are set using the pixel values ​​of the lower resolution radiograph pixels 504 of the lower resolution 2D radiograph(s) 500a captured at block 308.

[0084] Figure 3b is a flow chart illustrating an example operation of the accelerated higher resolution pixel setup process 350. As shown, the accelerated higher resolution pixel setup process 350 begins at box 352, where the accelerated higher resolution pixel setup process 350 identifies a particular view of the sample 102 for which the higher resolution 2D radiograph 500b is to be generated. In some examples, the particular view may be the lowest degree of rotation (e.g., 0 degrees, 1 degree, etc.) of the sample 102 for which the lower resolution 2D radiograph 500a was captured. After selecting a particular orientation at box 352, the accelerated higher resolution pixel setup process 350 generates a "blank" higher resolution 2D radiograph 500b (e.g., no pixel values ​​are set) for the particular orientation at box 354.

[0085] At box 356, the accelerated higher resolution pixel setting process 350 sets pixel values ​​for a first portion of higher resolution radiograph pixels 504b of the higher resolution 2D radiograph 500b. In some examples, the first portion of higher resolution radiograph pixels 504b may include fewer higher resolution radiograph pixels 504b than the total number of higher resolution radiograph pixels 504b in the higher resolution 2D radiograph 500b. In some examples, the number of higher resolution radiograph pixels 504b in the first portion is equal to the total number of higher resolution radiograph pixels 504b in the higher resolution 2D radiograph 500b divided by the total number of lower resolution radiograph pixels 504a in the lower resolution 2D radiograph 500b, multiplied by the number of lower resolution 2D radiographs 500a captured for the particular view at box 308.

[0086] In some examples, pixel values ​​for a first portion of the higher resolution radiograph pixels 504b are set based on the lower resolution 2D radiograph(s) 500a captured at block 308 for a particular view of the sample 102. Specifically, pixel values ​​for a first portion of the higher resolution radiograph pixels 504b are set based on pixel values ​​for lower resolution radiograph pixels 504a of the lower resolution 2D radiograph(s) 500a captured at block 308 for a particular view of the sample 102.

[0087] In some examples, each lower resolution radiograph pixel 504a of each lower resolution 2D radiograph 500a captured for a particular view at block 208 is used to set the pixel value of one higher resolution radiograph pixel 504b in the same region as the lower resolution radiograph pixel 504a. Figure 5a to Figure 5b , the lower resolution radiograph pixel 504a in the upper left corner of the lower resolution 2D radiograph 500a covers the same area as the four higher resolution radiograph pixels 504b in the upper left corner of the higher resolution 2D radiograph 500b. Thus, in some examples, the lower resolution radiograph pixel 504a in the upper left corner of the lower resolution 2D radiograph 500a will be used to set the pixel value of one of the four higher resolution radiograph pixels 504b in the upper left corner of the higher resolution 2D radiograph 500b.

[0088] In some examples, the detector position of the X-ray detector 108 when the lower resolution 2D radiograph 500a is captured can determine which of the higher resolution radiograph pixels 504b in the coverage area is set. For example, the upper left lower resolution radiograph pixel 504a of the lower resolution 2D radiograph 500a captured when the X-ray detector 108 is at the upper left detector position I can be used to set the upper left higher resolution radiograph pixel 504b in the higher resolution 2D radiograph 500b. As another example, the upper left lower resolution radiograph pixel 504a of the lower resolution 2D radiograph 500a captured when the X-ray detector 108 is at the lower right detector position II can be used to set the higher resolution radiograph pixel 504b diagonally adjacent to the upper left higher resolution radiograph pixel 504b in the higher resolution 2D radiograph 500b.

[0089] Figure 8a This positional relationship between the detector position and the pixel position is shown in Figure 8a In the example of , the gray lower resolution radiograph pixel 504a in the upper left corner of the dashed rectangle represents the upper left lower resolution radiograph pixel 504a of the lower resolution 2D radiograph 500a captured when the X-ray detector 108 is located at the upper left detector position I. The black lower resolution radiograph pixel 504a in the lower right corner of the dashed rectangle represents the upper left lower resolution radiograph pixel 504a of the lower resolution 2D radiograph 500a captured when the X-ray detector 108 is located at the lower right detector position II.

[0090] exist Figure 8a In the example of , the upper left corner higher resolution radiograph pixel 504b has the same gray color as the upper left corner lower resolution radiograph pixel 504a, indicating that the pixel (e.g., grayscale) value of the upper left corner higher resolution radiograph pixel 504b has been set (and / or set to be the same) according to the pixel value of the upper left corner lower resolution radiograph pixel 504a. Similarly, the lower right corner higher resolution radiograph pixel 504b has the same black color as the lower right corner lower resolution radiograph pixel 504a, indicating that the pixel (e.g., grayscale) value of the lower right corner higher resolution radiograph pixel 504b has been set (and / or set to be the same) according to the pixel value of the lower right corner lower resolution radiograph pixel 504a.

[0091] In some conventional sub-pixel sampling examples, the upper right and lower left higher resolution radiograph pixels 504b would similarly be set using lower resolution radiograph pixels 504a from lower resolution 2D radiographs 500a captured when the X-ray detector 108 was at upper right detector position III and lower left detector position IV. Figure 8a In the example of , the high resolution radiograph pixels 504b in the upper right and lower left corners are displayed as white to indicate that they are “blank,” having unset pixel values. While conventional sub-pixel sampling can set the pixel values ​​of all higher resolution radiograph pixels 504b based on the lower resolution radiograph pixels 504a, this requires capturing more of the lower resolution 2D radiographs 500a. In contrast, the higher resolution radiography process 300 (and / or the accelerated higher resolution pixel setting process 350) only sets the pixel values ​​of a first portion of the higher resolution radiograph pixels 504b. This technique of setting the pixel values ​​of only some, rather than all, of the higher resolution radiograph pixels 504b based on the lower resolution radiograph pixels 504a means that fewer lower resolution 2D radiographs 500a need to be captured, thereby saving a significant amount of time and requiring less movement of the X-ray detector 108 (which can reduce wear and tear).

[0092] Because fewer lower resolution 2D radiographs 500a were captured than were required to set the pixel values ​​for each higher resolution radiograph pixel 504a, after the pixel values ​​for a first portion of the higher resolution radiograph pixels 504b are set at block 356, the remaining portion of the higher resolution radiograph pixels 504b are left unset (and / or “blank”). Figure 8b This is depicted in FIG, where a first portion (e.g., half) of the higher resolution radiograph pixel 504b is assigned a gray or black color to indicate that its pixel value has been set, while the remainder (e.g., half) of the high resolution radiograph pixel 504b is white to indicate that it has no pixel value. Figure 3b In the example of , the pixel values ​​of the remainder of the higher resolution radiograph pixels 504 b are set at box 358 by the accelerated higher resolution pixel setting process 350 .

[0093] In some examples, the accelerated higher resolution pixel setting process 350 sets the pixel values ​​of the remaining portion of the higher resolution radiograph pixels 504b based on an analysis of the pixel values ​​of the first portion of the higher resolution radiograph pixels 504b. In some examples, the analysis can include and / or use some (e.g., bicubic, linear, bilinear, nearest neighbor, etc.) interpolation of the first portion of the high resolution radiograph pixels 504b that are nearby, adjacent, and / or surrounding. In this context, adjacent can refer to high resolution radiograph pixels 504b that are laterally adjacent along the x-axis, vertically adjacent along the y-axis, and / or diagonally adjacent along a diagonal axis that bisects the x-axis and the y-axis.

[0094] In some examples, the analysis may include and / or use artificial intelligence mechanisms. For example, the analysis may include and / or use one or more neural networks, clustering algorithms, and / or pattern matching techniques trained on and / or using a repository of previously captured lower resolution 2D radiographs 500a and / or higher resolution 2D radiographs 500b (e.g., stored in the memory circuitry 212).

[0095] Studies have shown that by using some analysis of the pixel values ​​of a first portion of the higher resolution radiograph pixels 504b to set the remaining high resolution radiograph pixels 504, the quality and / or quantity of detail in the higher resolution 2D radiograph 500b remains very high and / or is only slightly reduced. And the generation of the higher resolution 2D radiograph 500b is significantly faster because a smaller number of lower resolution 2D radiographs 500a need to be captured. In addition, the fewer lower resolution 2D radiographs 500a are captured, the less movement of the X-ray detector 108 (e.g., via the positioning system 199) may be required, which can reduce wear.

[0096] exist Figure 3b In the example of , the accelerated higher resolution pixel setup process 350 determines at block 360 whether there is another view of the sample 102 for which a higher resolution 2D radiograph 500b should be generated. If so, the accelerated higher resolution pixel setup process 350 iterates to the next view at block 352, and then loops through blocks 354 to 358 again for that view of the sample 102. If not, the accelerated higher resolution pixel setup process 350 ends, and the accelerated higher resolution radiography process 300 proceeds to block 318.

[0097] exist Figure 3a In the example of , the accelerated higher resolution radiography process 300 enhances one or more higher resolution 2D radiographs 500 generated during the accelerated higher resolution pixel setting process 350 at box 318. In some examples, the enhancement at box 318 may include deconvolution. In some examples, the enhancement may include and / or use one or more artificial intelligence mechanisms, such as those discussed above. Although shown as being performed at the end of the loop of boxes 306 to 314, in some examples, boxes 316, 350, and / or 318 may be performed after each loop of boxes 306 to 310.

[0098] After block 318, the accelerated higher-resolution radiography process 300 proceeds to block 320, where the accelerated higher-resolution radiography process 300 combines the higher-resolution 2D radiographs 500b into one or more higher-resolution 3D volumes (if necessary and / or possible). In some examples, the accelerated higher-resolution radiography process 300 may additionally acquire one or more specific slices of the higher-resolution 2D radiographs 500b from the higher-resolution 3D volume(s) (e.g., based on some user-selected or stored parameters). In some examples, the slice(s) may be different from any higher-resolution 2D radiographs 500b previously generated and / or acquired.

[0099] exist Figure 3b In the example of FIG. 3 , after block 320, the accelerated higher resolution radiography process 300 proceeds to block 322, where one or more (e.g., visual) representations of the higher resolution 3D volume and / or the higher resolution 2D radiograph 500 b may be output to a user via the output device(s) 208 of the UI 204 and / or stored in the memory circuitry 212. After block 322, the accelerated higher resolution radiography process 300 ends.

[0100] The X-ray radiography system 200 discussed herein allows for the generation of a higher resolution 2D radiograph 500b using an accelerated higher resolution radiography process 300. Specifically, the accelerated higher resolution radiography process 300 uses pixel (e.g., grayscale) values ​​from one or more lower resolution 2D radiographs 500a to set the pixel values ​​of a first portion of higher resolution radiograph pixels 504b of the higher resolution 2D radiograph 500b. The remainder of the higher resolution radiograph pixels 504b are set based on an analysis of the first portion. The accelerated higher resolution radiography process 300 is faster than a more conventional process because the accelerated higher resolution radiography process 300 requires a smaller number of lower resolution radiographs to be captured, thereby saving time and / or reducing wear and tear on the radiography machine 100 while still providing high quality higher resolution 2D radiographs 500b.

[0101] The method and / or system can be implemented with hardware, software or a combination of hardware and software. The method and / or system can be implemented in a centralized manner in at least one computing system, or the method and / or system can be implemented in a distributed manner with different elements spread over several interconnected computing systems and / or remote computing systems. Any type of computing system or other device adapted to perform the method described herein is suitable. A typical combination of hardware and software can be a general computing system with a program or other code, which controls the computing system when loaded and executed so that the computing system performs the method described herein. Another typical implementation can include a dedicated integrated circuit or chip. Some implementations can include a non-transient machine-readable (e.g., computer-readable) medium (e.g., a flash drive, an optical disk, a magnetic storage disk, etc.), which stores one or more instructions (multiple lines of code) executable by a machine, so that the machine performs the process described herein.

[0102] Although the present method and / or system has been described with reference to certain embodiments, it will be appreciated by those skilled in the art that various changes may be made and equivalents may be substituted without departing from the scope of the present method and / or system. In addition, many modifications may be made to adapt a particular situation or material to the teachings of the present disclosure without departing from the scope of the present disclosure. Therefore, the present method and / or system is not intended to be limited to the specific embodiments disclosed, but rather the present method and / or system will include all embodiments falling within the scope of the appended claims.

[0103] As used herein, "and / or" refers to any one or more of the items connected by "and / or" in a list. As an example, "x and / or y" refers to any element in the three-element set {(x), (y), (x, y)}. In other words, "x and / or y" means "one or both of x and y". As another example, "x, y and / or z" refers to any element in the seven-element set {(x), (y), (z), (x, y), (x, z), (y, z), (x, y, z)}. In other words, "x, y and / or z" means "one or more of x, y and z".

[0104] As used herein, the terms "eg," and "for example," introduce a list of one or more non-limiting examples, instances, or illustrations.

[0105] As used herein, the terms "coupled," "coupled to," and "coupled with" refer to structural and / or electrical connections, whether attached, attached, connected, joined, fastened, associated, and / or otherwise secured, respectively. As used herein, the term "attach" refers to attaching, coupling, connecting, joining, fastening, associated, and / or otherwise secured. As used herein, the term "connect" refers to attaching, attaching, coupling, joining, fastening, associated, and / or otherwise secured.

[0106] As used herein, the terms "circuit" and "circuitry" refer to physical electronic components (i.e., hardware) and any software and / or firmware ("code") that may configure, be executed by, and / or otherwise be associated with the hardware. As used herein, for example, a particular processor and memory may constitute a first "circuit" when executing a first one or more lines of code, and may constitute a second "circuit" when executing a second one or more lines of code. As used herein, a circuitry is "operable" and / or "configured" to perform a function when the circuitry includes the necessary hardware and / or code (if necessary) to perform the function, regardless of whether performance of the function is disabled or enabled (e.g., by a user-configurable setting, a factory adjustment, etc.).

[0107] As used herein, control circuitry may include digital circuit systems and / or analog circuit systems, discrete circuit systems and / or integrated circuit systems, microprocessors, DSPs, etc., located on one or more circuit boards forming part or all of a controller and / or software, hardware and / or firmware for controlling a welding process and / or devices such as a power supply or a wire feeder.

[0108] As used herein, the term "processor" refers to a processing device, apparatus, program, circuit, component, system and subsystem, whether implemented in hardware, software in tangible form or both, and whether or not it is programmable. As used herein, the term "processor" includes, but is not limited to, one or more computing devices, hard-wired circuits, signal modification devices and systems, devices and machines for controlling systems, central processing units, programmable devices and systems, field programmable gate arrays, application-specific integrated circuits, systems on chips, systems including discrete components and / or circuits, state machines, virtual machines, data processors, processing facilities, and any combination of the above components. The processor may be, for example, any type of general-purpose microprocessor or microcontroller, a digital signal processing (DSP) processor, an application-specific integrated circuit (ASIC), a graphics processing unit (GPU), a reduced instruction set computer (RISC) processor with an advanced RISC machine (ARM) core, etc. The processor may be coupled to a memory device and / or integrated with the memory device.

[0109] As used herein, the terms "memory" and / or "memory device" refer to computer hardware or circuitry for storing information for use by a processor and / or other digital device. The memory and / or memory device may be any suitable type of computer memory or any other type of electronic storage medium, such as read-only memory (ROM), random access memory (RAM), cache memory, compact disk read-only memory (CDROM), electro-optical memory, magneto-optical memory, programmable read-only memory (PROM), erasable programmable read-only memory (EPROM), electrically erasable programmable read-only memory (EEPROM), computer-readable media, etc. The memory may include, for example, non-transitory memory, non-transitory processor-readable medium, non-transitory computer-readable medium, non-volatile memory, dynamic RAM (DRAM), volatile memory, ferroelectric RAM (FRAM), first-in-first-out (FIFO) memory, last-in-first-out (LIFO) memory, stack memory, non-volatile RAM (NVRAM), static RAM (SRAM), cache, buffer, semiconductor memory, magnetic memory, optical memory, flash memory, flash memory card, compact flash memory card, memory card, secure digital memory card, micro card, mini card, expansion card, smart card, memory stick, multimedia card, picture card, flash memory device, subscriber identity module (SIM) card, hardware drive (HDD), solid state drive (SSD), etc. The memory may be configured to store code, instructions, applications, software, firmware and / or data, and may be external to the processor, internal to the processor, or both internal and external to the processor.

Claims

1. A non-transitory computer readable medium comprising machine readable instructions which, when executed by a processing circuit system, cause the processing circuit system to perform the following actions: capturing a lower resolution radiograph of a sample using radiation emitted by a radiation emitter and detected by a radiation detector, the sample being positioned between the radiation emitter and the radiation detector in a radiation path of the radiation; and A higher resolution radiograph of the sample is generated based on the lower resolution radiograph, the higher resolution radiograph comprising more pixels than the lower resolution radiograph, the higher resolution radiograph having higher resolution pixels, and the higher resolution radiograph is generated by: setting first higher resolution pixel values ​​for the first portion of the higher resolution pixels based on lower resolution pixel values ​​of the lower resolution radiograph, and Analysis of the first higher resolution pixel values ​​for the first portion of the higher resolution pixels is used to set remaining higher resolution pixel values ​​for a remaining portion of the higher resolution pixels of the higher resolution radiograph.

2. The non-transitory computer readable medium of claim 1, wherein: The lower resolution radiograph comprises a first lower resolution radiograph of the sample when the radiation detector is in a first detector position and the sample is in a sample orientation relative to the radiation emitter or the radiation detector, the lower resolution pixel values ​​comprise first lower resolution pixel values, the non-transitory computer readable medium further comprising machine readable instructions that, when executed by the processing circuitry, cause the processing circuitry to perform the following actions: capturing a second, lower resolution radiograph of the sample when the radiation detector is in the second detector position and the sample is in the sample orientation, wherein the first higher resolution pixel value of the first portion of the higher resolution pixels is set based on the first lower resolution pixel value of the first lower resolution radiograph and the second lower resolution pixel value of the second lower resolution radiograph.

3. The non-transitory computer readable medium of claim 2, wherein: The radiation detector comprises a detector surface comprising a plurality of detector pixels, each of the plurality of detector pixels having a detector pixel size defined by a detector pixel width along a first detector axis and a detector pixel height along a second detector axis perpendicular to the first detector axis, the second detector position being offset from the first detector position by a first distance along the first detector axis or by a second distance along the second detector axis, the first distance being less than the detector pixel width, or the second distance being less than the detector pixel height.

4. The non-transitory computer-readable medium of claim 3, further comprising machine-readable instructions that, when executed by the processing circuit system, cause the processing circuit system to: move the radiation detector from the first detector position to the second detector position using a positioning system.

5. The non-transitory computer-readable medium of claim 1, further comprising machine-readable instructions that, when executed by the processing circuitry, cause the processing circuitry to display a visual representation of the higher resolution radiograph on a display screen.

6. The non-transitory computer-readable medium of claim 1, further comprising machine-readable instructions that, when executed by the processing circuitry, cause the processing circuitry to apply enhancement to the higher resolution pixels of the higher resolution radiograph.

7. The non-transitory computer-readable medium of claim 1, further comprising machine-readable instructions that, when executed by the processing circuit system, cause the processing circuit system to construct a three-dimensional higher resolution radiographic volume using the higher resolution radiograph and one or more additional higher resolution radiographs.

8. An industrial radiography imaging system comprising: a radiation emitter configured to emit radiation along a radiation path; a radiation detector positioned in the radiation path of the radiation, the radiation detector configured to detect the radiation emitted by the radiation emitter; a sample support positioned between the radiation emitter and the radiation detector, the sample support configured to support a sample at a sample position in the radiation path of the radiation; as well as An image acquisition system, the image acquisition system comprising: processing circuitry, and memory circuitry comprising machine-readable instructions that, when executed by the processing circuitry, cause the processing circuitry to: capturing a lower resolution radiograph of the sample using the radiation detected by the radiation detector, and A higher resolution radiograph of the sample is generated based on the lower resolution radiograph, the higher resolution radiograph comprising more pixels than the lower resolution radiograph, the higher resolution radiograph having higher resolution pixels, and the higher resolution radiograph is generated by: setting first higher resolution pixel values ​​for the first portion of the higher resolution pixels based on lower resolution pixel values ​​of the lower resolution radiograph, and Analysis of the first higher resolution pixel values ​​for the first portion of the higher resolution pixels is used to set remaining higher resolution pixel values ​​for a remaining portion of the higher resolution pixels of the higher resolution radiograph.

9. The system of claim 8, wherein: The lower-resolution radiograph comprises a first lower-resolution radiograph of the sample when the radiation detector is in a first detector position and the sample is in a sample orientation relative to the radiation emitter or the radiation detector, the lower-resolution pixel values ​​comprise first lower-resolution pixel values, and the memory circuitry further comprises machine-readable instructions that, when executed by the processing circuitry, cause the processing circuitry to: capturing a second, lower resolution radiograph of the sample when the radiation detector is in the second detector position and the sample is in the sample orientation, wherein the first higher resolution pixel value of the first portion of the higher resolution pixels is set based on the first lower resolution pixel value of the first lower resolution radiograph and the second lower resolution pixel value of the second lower resolution radiograph.

10. The system of claim 9, wherein: The radiation detector comprises a detector surface comprising a plurality of detector pixels, each of the plurality of detector pixels having a detector pixel size defined by a detector pixel width along a first detector axis and a detector pixel height along a second detector axis perpendicular to the first detector axis, the second detector position being offset from the first detector position by a first distance along the first detector axis or by a second distance along the second detector axis, the first distance being less than the detector pixel width, or the second distance being less than the detector pixel height.

11. The system of claim 10, further comprising a positioning system configured to move the radiation detector from the first detector position to the second detector position.

12. The system of claim 8, wherein: The image acquisition system further includes a display screen configured to display a visual representation of the higher resolution radiograph.

13. The system of claim 8, wherein: The memory circuitry further includes machine-readable instructions that, when executed by the processing circuitry, cause the processing circuitry to: apply enhancement to the higher resolution pixels of the higher resolution radiograph.

14. The system of claim 8, wherein: The memory circuitry further includes machine readable instructions that, when executed by the processing circuitry, cause the processing circuitry to: construct a three-dimensional higher resolution radiographic volume using the higher resolution radiograph and one or more additional higher resolution radiographs.

15. A method for accelerating the generation of higher resolution radiographs, the method comprising: capturing a lower resolution radiograph of a sample using radiation emitted by a radiation emitter and detected by a radiation detector, the sample being positioned between the radiation emitter and the radiation detector in a radiation path of the radiation; as well as generating, via processing circuitry, a higher resolution radiograph of the sample based on the lower resolution radiograph, the higher resolution radiograph comprising more pixels than the lower resolution radiograph, the higher resolution radiograph having higher resolution pixels, and the higher resolution radiograph being generated by: setting, via the processing circuitry, first higher resolution pixel values ​​for a first portion of the higher resolution pixels based on lower resolution pixel values ​​of the lower resolution radiograph, and An analysis of the first higher resolution pixel values ​​for the first portion of the higher resolution pixels is used, via the processing circuitry, to set remaining higher resolution pixel values ​​for a remaining portion of the higher resolution pixels of the higher resolution radiograph.

16. The method of claim 15, wherein: The lower resolution radiograph comprises a first lower resolution radiograph of the sample when the radiation detector is in a first detector position and the sample is in a sample orientation relative to the radiation emitter or the radiation detector, the lower resolution pixel values ​​comprise first lower resolution pixel values, the method further comprising: capturing a second, lower resolution radiograph of the sample using the radiation detector when the radiation detector is in the second detector position and the sample is in the sample orientation, wherein the first higher resolution pixel value of the first portion of the higher resolution pixels is set based on the first lower resolution pixel value of the first lower resolution radiograph and the second lower resolution pixel value of the second lower resolution radiograph.

17. The method of claim 16, wherein: The radiation detector comprises a detector surface comprising a plurality of detector pixels, each of the plurality of detector pixels having a detector pixel size defined by a detector pixel width along a first detector axis and a detector pixel height along a second detector axis perpendicular to the first detector axis, the second detector position being offset from the first detector position by a first distance along the first detector axis or by a second distance along the second detector axis, the first distance being less than the detector pixel width, or the second distance being less than the detector pixel height.

18. The method of claim 17, further comprising moving the radiation detector from the first detector position to the second detector position using a positioning system.

19. The method of claim 15, further comprising: applying, via the processing circuitry, enhancement to the higher resolution pixels of the higher resolution radiograph; as well as A visual representation of the higher resolution radiograph is displayed on a display screen.

20. The method of claim 15, further comprising constructing, via the processing circuitry, a three-dimensional higher resolution radiographic volume using the higher resolution radiograph and one or more additional higher resolution radiographs.

Images