Accelerated high-resolution industrial radiography

Abstract

To provide industrial radiography.SOLUTION: Example industrial radiography systems allow generation of high-resolution 2D radiographs using an accelerated high-resolution radiograph process. The accelerated high-resolution radiograph process uses pixel (e.g., grayscale) values from one or more lower resolution 2D radiographs to set pixel values for a first portion of high-resolution radiograph pixels of a high-resolution 2D radiograph. A remaining portion of the high-resolution radiograph pixels are set on the basis of an analysis of the first portion. The accelerated high-resolution radiograph process is faster than more traditional processes because the accelerated high-resolution radiograph process necessitates fewer lower resolution radiographs to be captured, and therefore saves time and / or reduces wear and tear on a radiography machine, while still providing quality high-resolution 2D radiographs.SELECTED DRAWING: Figure 1

Description

[Technical field]

[0001] CROSS-REFERENCE TO RELATED APPLICATIONS This application claims priority to and the benefit of U.S. Provisional Patent Application No. 63 / 521,159, entitled “Accelerated Higher Resolution Industrial Radiography,” filed June 15, 2023, the entire contents of which are incorporated herein by reference.

[0002] Technical Field FIELD OF THE DISCLOSURE This disclosure relates generally to industrial radiography, and more particularly to accelerated high resolution industrial radiography. [Background technology]

[0003] background Industrial radiography systems are used to obtain two-dimensional (2D) radiographic images of parts used in industrial applications. Such industrial applications may include, for example, aerospace, automotive, electronic, medical, pharmaceutical, military, and / or defense applications. The 2D radiographic images may be reviewed to inspect the part(s) for cracks, scratches, and / or defects that may or may not be normally visible to the human eye.

[0004] By comparing such a system with the present disclosure described in the remainder of this application with reference to the drawings, the limitations and disadvantages of the conventional and traditional approaches will become apparent to one skilled in the art. Summary of the Invention

[0005] Quick Overview The present disclosure relates to accelerated high resolution industrial radiography substantially as illustrated and / or described in connection with at least one of the drawings and more fully described in the claims.

[0006] These and other advantages, aspects, and novel features of the present disclosure, as well as details of illustrated examples of the disclosure, will become more fully understood from the following description and drawings. [Brief description of the drawings]

[0007] [Figure 1] FIG. 1 illustrates an example of an industrial X-ray radiography machine according to aspects of the present disclosure.

[0008] [Diagram 2] FIG. 2 is a block diagram illustrating an example X-ray radiography system having the industrial X-ray radiographer of FIG. 1 in accordance with an aspect of the present disclosure.

[0009] [Figure 3a] 3 is a flowchart illustrating an example operation of an accelerated high resolution radiography process of the X-ray radiography system of FIG. 2 in accordance with an aspect of the present disclosure. [Figure 3b] 3 is a flowchart illustrating an example operation of an accelerated high resolution radiography process of the X-ray radiography system of FIG. 2 in accordance with an aspect of the present disclosure.

[0010] [Figure 4] FIG. 2 illustrates an exemplary detector pixel grid for the X-ray detector 108 of the industrial X-ray radiographer of FIG. 1, in accordance with an embodiment of the present disclosure.

[0011] [Figure 5a] FIG. 2 illustrates an exemplary radiographic pixel grid, in accordance with aspects of the present disclosure. [Figure 5b] FIG. 2 illustrates an exemplary radiographic pixel grid, in accordance with aspects of the present disclosure.

[0012] [Figure 6] FIG. 4 illustrates how the example pixel grid of FIG. 3 can be shifted by less than a sub-pixel to different detector positions, in accordance with an embodiment of the present disclosure.

[0013] [Figure 7] 2A-2C are diagrams illustrating different exemplary detector positions of the X-ray detector 108 of the industrial X-ray radiography machine of FIG. 1 in accordance with an embodiment of the present disclosure.

[0014] [Figure 8a] FIG. 5B illustrates an example of how different low-resolution radiograph pixels of different low-resolution 2D radiographs of FIG. 5A can be combined to set pixel values ​​of a first portion of high-resolution radiograph pixels of the high-resolution 2D radiograph of FIG. 5B, according to an embodiment of the present disclosure. [Figure 8b] FIG. 5B illustrates an example of how different low-resolution radiograph pixels of different low-resolution 2D radiographs of FIG. 5A can be combined to set pixel values ​​of a first portion of high-resolution radiograph pixels of the high-resolution 2D radiograph of FIG. 5B, according to an embodiment of the present disclosure. DETAILED DESCRIPTION OF THE PREFERRED EMBODIMENTS

[0015] The figures are not necessarily drawn to scale. Where appropriate, the same or similar reference numbers are used in the figures to refer to similar or identical components. For example, reference numbers utilizing letters (e.g., low-resolution 2D radiograph 500a, high-resolution 2D radiograph 500b) refer to instances of the same reference number without the letters (e.g., 2D radiograph 500).

[0016] Detailed Description Some examples of the present disclosure relate to industrial radiography systems that use an accelerated sub-pixel sampling process to generate high-resolution 2D radiographs with more detail than usual. In some examples, pixel (e.g., grayscale) values ​​of low-resolution radiograph pixels from one or more low-resolution 2D radiographs are used to set pixel values ​​for a first portion of high-resolution radiograph pixels in the high-resolution 2D radiograph. Pixel values ​​for the remaining portion of high-resolution pixels can then be set based on an analysis of pixel values ​​from the first portion of high-resolution radiograph pixels. This technique of using low-resolution 2D radiographs to directly set only a portion, rather than all, of high-resolution pixels means that fewer low-resolution 2D radiographs need to be captured compared to some other, more conventional techniques, thereby saving time and / or reducing wear and tear while at the same time providing high-quality high-resolution 2D radiographs. When multiple high-resolution 2D radiographs are generated and / or combined to form a three-dimensional (3D) radiography volume, model, and / or image, the time saved (and / or reduced wear and tear) using the accelerated sub-pixel sampling process becomes even more noticeable.

[0017] Some examples of the present disclosure relate to a non-transitory computer readable medium including machine readable instructions that, when executed by processing circuitry, cause processing circuitry to: capture a low 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 high resolution radiograph of the sample based on the low resolution radiograph, the high resolution radiograph including more pixels than the low resolution radiograph, the high resolution radiograph having high resolution pixels, the high resolution radiograph being generated by setting first high resolution pixel values ​​for a first portion of the high resolution pixels based on low resolution pixel values ​​of the low resolution radiograph and setting remaining high resolution pixel values ​​for a remaining portion of the high resolution pixels of the high resolution radiograph using an analysis of the first high resolution pixel values ​​for the first portion of the high resolution pixels.

[0018] In some examples, the low resolution radiograph includes a first low resolution radiograph of the sample while the radiation detector is at a first detector position and the sample is in a sample orientation relative to the radiation emitter or radiation detector, and the low resolution pixel values ​​include first low resolution pixel values, and the non-transitory computer readable medium further includes machine readable instructions that, when executed by the processing circuitry, cause the processing circuitry to capture a second low resolution radiograph of the sample while the radiation detector is at a second detector position and the sample is in the sample orientation, wherein the first high resolution pixel values ​​for a first portion of the high resolution pixels are set based on the first low resolution pixel values ​​of the first low resolution radiograph and the second low resolution pixel values ​​of the second low resolution radiograph.

[0019] In some examples, the radiation detector includes a detector surface including a plurality of detector pixels, each detector pixel 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, and the second detector position is offset from the first detector position by a first distance along the first detector axis or 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 circuitry, cause the processing circuitry to 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 circuitry, cause the processing circuitry to display a visual representation of the high resolution radiograph on a display screen.

[0020] 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 corrections (enhancements) to high resolution pixels of the high 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 high resolution radiography volume using the high resolution radiograph and the one or more additional high resolution radiographs.

[0021] Some examples of the present disclosure include 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 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; and an image acquisition system, the image acquisition system comprising processing circuitry and memory circuitry including machine-readable instructions that, when executed by the processing circuitry, cause a signal to be detected by the radiation detector. and generating a high resolution radiograph of the sample based on the low resolution radiograph, the high resolution radiograph including more pixels than the low resolution radiograph, the high resolution radiograph having high resolution pixels, the high resolution radiograph being generated by setting first high resolution pixel values ​​for a first portion of the high resolution pixels based on the low resolution pixel values ​​of the low resolution radiograph and setting remaining high resolution pixel values ​​for a remaining portion of the high resolution pixels of the high resolution radiograph using an analysis of the first high resolution pixel values ​​for the first portion of the high resolution pixels.

[0022] In some examples, the low resolution radiograph includes a first low resolution radiograph of the sample while the radiation detector is at a first detector position and the sample is in a sample orientation relative to the radiation emitter or radiation detector, and the low resolution pixel values ​​include first low resolution pixel values, and the memory circuitry further includes machine readable instructions that, when executed by the processing circuitry, cause the processing circuitry to capture a second low resolution radiograph of the sample while the radiation detector is at a second detector position and the sample is in the sample orientation, wherein the first high resolution pixel values ​​for the first portion of the high resolution pixels are set based on the first low resolution pixel values ​​of the first low resolution radiograph and the second low resolution pixel values ​​of the second low resolution radiograph.

[0023] In some examples, the radiation detector includes a detector surface including a plurality of detector pixels, each detector pixel 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, and the second detector position is offset from the first detector position by a first distance along the first detector axis or 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.

[0024] In some examples, the system further comprises a positioning system configured to move the radiation detector from the first detector position to the second detector position. In some examples, the image acquisition system further comprises a display screen configured to display a visual representation of the high resolution radiograph. In some examples, the memory circuitry further comprises machine readable instructions that, when executed by the processing circuitry, cause the processing circuitry to apply a correction to high resolution pixels of the high resolution radiograph. In some examples, the memory circuitry further comprises machine readable instructions that, when executed by the processing circuitry, cause the processing circuitry to construct a three dimensional high resolution radiography volume using the high resolution radiograph and the one or more additional high resolution radiographs.

[0025] Some examples of the present disclosure relate to a method of accelerated generation of high resolution radiographs, the method including capturing a low 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, via processing circuitry, a high resolution radiograph of the sample based on the low resolution radiograph, the high resolution radiograph including more pixels than the low resolution radiograph, the high resolution radiograph having high resolution pixels, the high resolution radiograph being generated by setting, via the processing circuitry, first high resolution pixel values ​​for a first portion of the high resolution pixels based on low resolution pixel values ​​of the low resolution radiograph, and setting, via the processing circuitry, remaining high resolution pixel values ​​for a remaining portion of the high resolution pixels of the high resolution radiograph using an analysis of the first high resolution pixel values ​​for the first portion of the high resolution pixels.

[0026] In some examples, the low resolution radiograph includes a first low resolution radiograph of the sample while the radiation detector is at a first detector position and the sample is in a sample orientation relative to the radiation emitter or radiation detector, and the low resolution pixel value includes a first low resolution pixel value, and the method further includes capturing a second low resolution radiograph of the sample using the radiation detector while the radiation detector is at a second detector position and the sample is in the sample orientation, and the first high resolution pixel value for the first portion of the high resolution pixel is set based on the first low resolution pixel value of the first low resolution radiograph and the second low resolution pixel value of the second low resolution radiograph.

[0027] In some examples, the radiation detector includes a detector surface including a plurality of detector pixels, each detector pixel 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, and the second detector position is offset from the first detector position by a first distance along the first detector axis or 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.

[0028] 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 a correction to high resolution pixels of the high resolution radiograph via the processing circuitry and displaying a visual representation of the high resolution radiograph on a display screen. In some examples, the method further includes constructing a three dimensional high resolution radiographic volume using the high resolution radiograph and the one or more additional high resolution radiographs via the processing circuitry.

[0029] FIG. 1 illustrates an exemplary industrial X-ray radiographer 100. In some examples, the X-ray radiographer 100 can be used for non-destructive testing (NDT), digital radiography (DR) scans, computerized tomography (CT) scans, and / or other applications performed on a sample 102. In some examples, the sample 102 can be an industrial component and / or assembly of components (e.g., engine castings, microchips, bolts, etc.). In some examples, the sample 102 can be relatively small such that finer, more detailed, and higher resolution radiography (e.g., radiographic imaging) processes can be utilized. Although primarily discussed with respect to X-rays for simplicity, in some examples, the industrial X-ray radiographer 100 discussed in this disclosure can also use radiation at other wavelengths (e.g., gamma rays, neutrons, etc.).

[0030] In the example of FIG. 1, the X-ray radiographer 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 impinges on (and / or is detected by) an X-ray detector 108. In some examples, the X-ray emitter 106 can include an X-ray tube configured to emit a cone or fan of X-ray radiation. In some examples, the X-ray emitter 106 can emit X-ray radiation in an energy range of 20 kiloelectron volts (keV) to 10 megaelectron volts (meV).

[0031] 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 combination with a computing system 202 (see, e.g., FIG. 2 ) in communication with the X-ray detector 108 and / or the X-ray radiographer 100.

[0032] 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 a 3D image. In some examples, 2D image slices of the 3D volume / image may also be formed. It should be noted that while the terms "image" and / or "radiograph" are used as shorthand in this disclosure, an "image" and / or "radiograph" may include representative data until that data is visually rendered by one or more appropriate components (e.g., a display screen, a graphics processing unit, the X-ray detector 108, etc.).

[0033] In some examples, the X-ray detector 108 can 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 can include a fluoroscopy detection system and / or a digital image sensor configured to receive images indirectly via scintillation. In some examples, the X-ray detector 108 can be implemented using a sensor panel (e.g., a charge coupled device (CCD) panel, a complementary metal-oxide-semiconductor (CMOS) panel, etc.) configured to directly receive X-rays and generate a digital image. In some examples, the X-ray detector 108 can include a scintillation layer / screen that absorbs X-rays and emits visible light photons that are then 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.

[0034] In some examples, the X-ray detector 108 (e.g., a solid-state detector panel) can include detector pixels 404 (see, e.g., FIG. 4). In some examples, the detector pixels 404 can correspond to portions of a scintillation screen. In some examples, the size of each detector pixel 404 can range from tens of micrometers to hundreds of micrometers. In some examples, the pixel size of the X-ray detector 108 can be in the range of 25 micrometers to 250 micrometers (e.g., 200 micrometers). In some examples, the detector pixels 404 can be arranged in a detector pixel grid 402 on the X-ray detector 108.

[0035] FIG. 4 illustrates an example of a detector pixel grid 402 comprised of a plurality of detector pixels 404. As illustrated, each detector pixel 404 has a pixel size determined by a pixel height (e.g., in the y-axis) and a pixel width (e.g., in the x-axis). In some examples, the x-axis may be approximately parallel (e.g., within 1-5 degrees) to one or more rails 154 of the detector positioner 150 (discussed below with respect to FIG. 1). In some examples, the y-axis may be approximately parallel to one or more posts 152 of the detector positioner 150 (discussed below with respect to FIG. 1). Although the detector pixels 404 are illustrated in the example of FIG. 4 as squares having equal pixel heights and pixel widths, in some examples, the detector pixels 404 may be rectangular with pixel heights that are not equal to the pixel widths. For convenience, the term "pixel length" may be used in the following disclosure to refer to either / both pixel heights and / or pixel widths.

[0036] In some examples, when a 2D radiograph 500a is generated, the 2D radiograph 500a is represented using an arrangement (e.g., a radiograph pixel grid 502) of radiograph pixels 504 (see, e.g., FIG. 5a). In some examples, each 2D radiograph 500a captured using the X-ray detector 108 may have the same number (and / or the same arrangement) of radiograph pixels 504 as the X-ray detector 108 has detector pixels 404. In some examples, each radiograph pixel 504 may have an associated pixel (e.g., grayscale) value that is set based on radiation detected by the X-ray detector 108 proximate to the corresponding detector pixel 404. The computing system 202 and / or user interface (UI) 204 (see, e.g., FIG. 2 ) can then output a visual representation (e.g., an image) of the 2D radiograph 500 a 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, with each display screen pixel having a display screen pixel value that is the same as (and / or correlates with, is based on, etc.) the pixel value of the corresponding radiograph pixel 504.

[0037] FIG 5a illustrates a simple example of a 2D radiograph 500a. In the example of FIG 5a, the 2D radiograph 500a is represented by a plurality 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 is the same shade of gray, indicating a common pixel (e.g., grayscale) value for those radiograph pixels 504a. In contrast, each radiograph pixel 504a in a given column (e.g., along the y-axis) is a different shade of gray from all other radiograph pixels 504a in that column, indicating a different pixel (e.g., grayscale) value for each radiograph pixel 504a in that column.

[0038] In some examples, the size of each detector pixel 404 of the X-ray detector 108 may be a limiting factor in the resolution, i.e., detail, of the 2D radiograph 500a captured by the X-ray detector 108 (and / or associated computing system 202). This may be problematic when the sample 102 includes features that are finer (e.g., smaller, denser, etc.) than the pixel size of the detector pixels 404 of the X-ray detector 108.

[0039] For example, a computer microchip may have very fine features that are smaller than the size of a detector pixel 404. Because each detector pixel 404 (and / or corresponding radiograph pixel 504a) can only have one pixel (e.g., grayscale) value, granular differences that occur (e.g., in color and / or grayscale) at scales smaller than the size of the detector pixel 404 may be lost. In such instances, it may be useful to use sub-pixel (e.g., less / smaller than the detector pixel 404) sampling to construct a high-resolution 2D radiograph 500b (see, e.g., FIG. 5b) having high-resolution radiograph pixels 504b capable of depicting more detail than is possible in a low-resolution 2D radiograph 500a captured using the x-ray detector 108. As used in this disclosure, "sub-pixel sampling" refers to the process of constructing a high-resolution 2D radiograph 500b using multiple low-resolution 2D radiographs 500a captured at different detector locations of the X-ray detector 108, where each detector location is offset from at least one other detector location (and / or all other detector locations) by a sub-pixel (e.g., less than the pixel length of the detector pixel 404).

[0040] Figure 5b shows an example of a high resolution 2D radiograph 500b. Like the low resolution 2D radiograph 500a of Figure 5a, the high resolution 2D radiograph 500b of Figure 5b is represented by a plurality of high resolution radiograph pixels 504b arranged in a radiograph pixel grid 502b. However, the high resolution 2D radiograph 500b of Figure 5b has a higher pixel density than the low resolution 2D radiograph 500a of Figure 5a (and / or the detector pixel grid 402 of Figure 4). That is, the high resolution 2D radiograph 500b of Figure 5b is shown as having more (and smaller) high resolution radiograph pixels 504b than the low resolution 2D radiograph 500a of Figure 5a (and / or the detector pixel grid 402 of Figure 4).

[0041] In particular, the high resolution 2D radiograph 500b of Figure 5b is shown as having four times as many high resolution radiograph pixels 504b as the low resolution 2D radiograph 500a has low resolution radiograph pixels 504a (and / or the detector pixel grid 402 has detector pixels 404). In some examples, the number of high resolution radiograph pixels 504b may be some other multiple (e.g., 2 times, 6 times, 8 times, 10 times, etc.) of the number of low resolution radiograph pixels 504a (and / or detector pixels 404). Nevertheless, both 2D radiographs 500 (and the detector pixel grid 402 of Figure 4) are shown as occupying (and / or representing) the same total area.

[0042] In some instances, the higher pixel density of the high resolution 2D radiograph 500b may allow for a more detailed depiction of the sample 102 than the low resolution 2D radiograph 500a. This is shown in Figures 5a and 5b, where both 2D radiographs 500 show a gradual progression from very bright to very dark, but the high resolution 2D radiograph 500b shows a finer, more gradual progression than the low resolution 2D radiograph 500a.

[0043] In the example of Figure 1, the X-ray machine 100 includes a positioning system 199 comprising a detector positioner 150, a sample positioner 110, and an emitter-detector positioner 160. 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 (and / or attached to) the rails 154 by one or more intermediate supports.

[0044] In some examples, the detector positioner 150 can be configured to move the X-ray detector 108 toward and / or away from either support 152 along rails 154. In some examples, the rails 154 can be configured to move along and / or parallel to (e.g., upward and / or downward) the support 152, thereby also moving the X-ray detector 108 along and / or parallel to the support 152. The detector positioner 150 is shown simply in the example of FIG. 1, but in some examples can be more complex, similar to the x translation stage 18, y translation stage 20, detector mounting frame 26, and / or x / y stage linear encoders 22 / 24 shown and described in U.S. Patent No. 9,459,217, entitled "High-Resolution Computed Tomography," dated September 30, 2015, 35 U.S.C. 371, the entire contents of which are incorporated herein by reference.

[0045] In some examples, the sample 102 can be moved by a sample positioner 110. In the example of FIG. 1, the sample positioner 110 holds the sample 102 in the path of the X-ray radiation 104 between the X-ray emitter 106 and the detector 108. In some examples, the sample positioner 110 can be configured to move the sample 102 toward and / or away from the X-ray emitter 106 and / or the X-ray detector 108, thereby changing the geometric magnification (defined as the distance between the X-ray emitter 106 and the X-ray detector 108 divided by the distance between the X-ray emitter 106 and the sample 102). In some examples, the sample positioner 110 can be configured to move and / or rotate the sample 102 such that a desired portion and / or orientation of the sample 102 is located in the path of the X-ray radiation 104. In some examples, the sample positioner 110 can position the sample 102 at various angles / orientations relative to the X-ray emitter 106 and / or the X-ray detector 108 to obtain 2D radiographs 500a at various orientations. These 2D radiographs 500a can then be used to generate one or more three-dimensional (3D) images of the sample 102.

[0046] 1, the sample positioner 110 includes a rotatable fixture 112 on which the sample 102 is positioned. As shown, the rotatable fixture 112 is a circular plate. As shown, the rotatable fixture 112 is mounted to a motorized spindle 116, through which the rotatable fixture 112 can rotate about an axis defined by the spindle 116. In some examples, one or more alternative and / or additional rotation mechanisms can be provided.

[0047] 1, rotatable fixture 112 is supported by support structure 118. In some examples, support structure 118 can be configured to translate rotatable fixture 112 (and / or sample 102) toward and / or away from X-ray emitter 106 and / or X-ray detector 108. In some examples, support structure 118 can include one or more actuators configured to provide the translation(s).

[0048] Although one exemplary sample positioner 110 is shown in the example of FIG. 1, in some examples, a different sample positioner 110 can be used. For example, a robotic object positioner can be used to translate and / or rotate the sample 102. Similarly, while the rotatable fixture 112 is shown in the example of FIG. 1 as a circular plate, in some examples, the rotatable fixture 112 can instead include a different fixture, such as, for example, a brake, a clamp, a gripper, and / or other holding mechanism. In some examples, rather than (or in addition to) the sample 102 being rotated by the rotatable fixture 112, the X-ray emitter 106 and the X-ray detector 108 can instead be rotated around the sample 102 (which can be useful, for example, when the sample 102 is awkward).

[0049] In the example of Figure 1, the X-ray machine 100 further includes an emitter-detector positioner 160. In the example of Figure 1, the emitter-detector positioner 160 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. In the example of Figure 1, the emitter-detector positioner 160 is shown elevated above and connected to the X-ray emitter 106 and the X-ray detector 108, for example, as may occur when implemented using a gantry system.

[0050] In some examples, the emitter-detector positioner 160 may alternatively be implemented differently, 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 means. In some examples, the emitter-detector positioner 160 may be configured to rotate about a different axis (e.g., a horizontal axis, a diagonal axis, etc.) and the X-ray emitter 106 and / or the X-ray detector 108 may be repositioned accordingly.

[0051] In some examples, one or more portions of the sample positioner 110 (e.g., support structure 118) can be modified and / or omitted to facilitate use (e.g., line of sight) of the X-ray emitter 106 and the X-ray detector 108 as they are moved around the sample 102 by the emitter-detector positioner 160. In some examples, the emitter-detector positioner 160 can be configured to maintain the same geometric magnification of the X-ray machine 100 as the X-ray emitter 106 and the X-ray detector 108 are moved around the sample 102. Although most of this disclosure discusses rotating the sample 102 during the accelerated high resolution radiography process 300, in some examples the X-ray emitter 106 and the X-ray detector 108 can instead rotate around the sample 102 as described above.

[0052] Figure 2 illustrates an example of an X-ray radiography system 200 that includes an X-ray radiography machine 100, such as the X-ray radiography machine 100 illustrated in Figure 1. 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. Although in the example of Figure 2, only one X-ray radiography machine 100, computing system 202, UI 204, and remote computing system 299 are shown, in some examples, the X-ray radiography system 200 can include multiple X-ray radiography machines 100, computing systems 202, UIs 204, and / or remote computing systems 299.

[0053] 2, the X-ray radiography machine 100 includes 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 160) enclosed within a housing 199. As shown, the X-ray radiography machine 100 is connected to and / or in communication with a computing system(s) 202 and a UI(s) 204. In some examples, the X-ray radiography system 100 may also be in electrical communication with a remote computing system(s) 299. In some examples, the communication and / or connection may be electrical, electromagnetic, wired, and / or wireless.

[0054] 2, 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 can include one or more touch screens, mice, keyboards, buttons, switches, slides, knobs, microphones, dials, and / or other electromechanical input devices. In some examples, the one or more output devices 208 can 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 the X-ray radiographer(s) 100, the computing system(s) 202, and / or the remote computing system(s) 299 via the UI(s) 204.

[0055] 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 together with the UI(s) 204 can comprise the image acquisition system of the X-ray radiography system 200. In some examples, the remote computing system(s) 299 can be similar or identical to the computing system 202.

[0056] 2, computing system 202 is in communication (e.g., electrically) with X-ray radiography machine(s) 100, UI(s) 204, and remote computing system(s) 299. In some examples, the communication may be direct communication (e.g., over wired and / or wireless medium) or indirect communication, such as, for example, over one or more wired and / or wireless networks (e.g., local area networks and / or wide area networks). As shown, computing system 202 includes processing circuitry 210, memory circuitry 212, and communication circuitry 214 interconnected with each other via a common electrical bus.

[0057] In some examples, the processing circuitry 210 can include one or more processors. In some examples, the communications circuitry 214 can include one or more wireless adapters, wireless cards, cable adapters, wired adapters, radio frequency (RF) devices, wireless communication devices, Bluetooth devices, IEEE 802.11 compliant devices, WiFi devices, cellular devices, GPS devices, Ethernet ports, network ports, Lightning cable ports, cable ports, etc. In some examples, the communications circuitry 214 can be configured to facilitate communications over one or more wired media and / or protocols (e.g., Ethernet cable(s), Universal Serial Bus cable(s), etc.) and / or wireless media and / or protocols (e.g., Near Field Communication (NFC), Very High Frequency Radio (commonly known as Bluetooth), IEEE 802.11x, Zigbee, HART, LTE, Z-Wave, WirelessHD, WiGig, etc.).

[0058] 2, memory circuitry 212 includes and / or stores accelerated high resolution radiography process 300. In some examples, accelerated high resolution radiography process 300 may be implemented by machine readable (and / or processor executable) instructions stored in memory circuitry 212 and / or executed by processing circuitry 210. In some examples, accelerated high resolution radiography process 300 may be performed as part of a larger scanning and / or imaging process of X-ray radiography system 200. Although some of the following disclosure describes accelerated high resolution radiography process 300 performing certain operations, this should be understood as shorthand for one or more components of X-ray radiography system 200 (e.g., processing circuitry 210, communications circuitry 214, UI 204, radiographer 100, etc.) performing an operation(s) as part of accelerated high resolution radiography process 300.

[0059] In some examples, the accelerated high resolution radiograph process 300 can use sub-pixel sampling along with pixel analysis to generate one or more high resolution 2D radiographs 500b faster than conventional sub-pixel sampling. Whereas in some conventional sub-pixel sampling examples, multiple low resolution 2D radiographs 500a are captured and the low resolution radiograph pixels 504a of the low resolution 2D radiographs are used to set pixel values ​​for all of the high resolution radiograph pixels 504b, in the accelerated high resolution radiograph process 300, the low resolution radiograph pixels 504a are only used to set pixel values ​​for a first portion of the high resolution radiograph pixels 504b, but not all of them. The pixel values ​​of the remaining portion of the high resolution radiograph pixels 504b are set using analysis of the pixel values ​​of the first portion of the high resolution radiograph pixels 504b. Because only a portion, rather than all, of the pixel values ​​of the high resolution pixels are set using the low resolution 2D radiographs, fewer low resolution 2D radiographs 500a need to be captured, thereby saving time and / or reducing wear and tear on the radiographer 100 while providing a high quality high resolution 2D radiograph.

[0060] Figure 3a is a flow chart illustrating an example operation of an accelerated high resolution radiography process 300. In the example of Figure 3a, the accelerated high resolution radiography process 300 begins at block 302. At block 302, the accelerated high resolution radiography process 300 identifies one or more parameter values ​​that may be used during the accelerated high resolution radiography process 300.

[0061] In some examples, the parameter values ​​may include values ​​for the type / size / geometry of the sample 102, a starting position / orientation / magnification of the sample 102, a target total rotation of the sample 102 (e.g., 1 degree to 360 degrees inclusive), a target rotation increment of the sample 102 (e.g., 1 degree, 5 degrees, etc.), a geometric magnification, a target high resolution, a resolution of the X-ray detector 108, 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 related information. In some examples, the accelerated high resolution radiography process 300 may prompt a user for one or more of the parameter values, such as via the UI 204.

[0062] In some examples, the accelerated high resolution radiography process 300 can automatically identify one or more of the parameter values ​​(e.g., if not provided via the UI 204). For example, if a target total rotation of the sample 102 is left unset, the accelerated high resolution radiography process 300 can default to 360 degrees. In some examples, the accelerated high resolution radiography process 300 can automatically identify one or more of the parameter values ​​based on one or more other parameter values. For example, the accelerated high 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 high resolution, such as through a data structure (e.g., look-up table, database) stored in the memory circuit 212 and / or dynamic algorithmic calculations.

[0063] 3a, after block 302, the accelerated high resolution radiography process 300 proceeds to block 304, where the accelerated high resolution radiography process 300 positions (e.g., via positioning system 199) the X-ray detector 108, the X-ray emitter 106, and / or the sample 102 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 may be determined based on one or more parameter values ​​input and / or determined in block 302. In some examples, the starting view positions the sample 102 in a particular orientation relative to the X-ray detector 108 (and / or the X-ray emitter 106).

[0064] After block 302, the accelerated high resolution radiography process 300 proceeds to block 306 where the accelerated high 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 in block 302. In some examples, the accelerated high resolution radiography process 300 may use one or more sensors of the radiographer 100 (e.g., position sensor(s), angle sensor(s), etc.) to determine the position of the X-ray detector 108 and / or when the X-ray detector 108 is properly positioned.

[0065] After block 306, the accelerated high resolution radiography process 300 proceeds to block 308 where the accelerated high resolution radiography process 300 captures a low 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 a first detector position and the sample 102 is in a starting view. In some examples, the sample 102 and / or the X-ray detector 108 are held stationary (e.g., via the positioning system 199) when capturing the low resolution 2D radiograph 500a. In some examples, the low resolution 2D radiograph 500a can be stored in the memory circuit 212.

[0066] 3a, after block 308, the accelerated high resolution radiography process 300 proceeds to block 310 where the accelerated high 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 ​​entered and / or determined in block 302 and / or the number of times the x-ray detector 108 has previously been moved while the sample 102 is in the same view (and / or the number of times blocks 306-310 have been executed).

[0067] In some examples, the accelerated high resolution radiography process 300 may use only one detector position while the sample 102 is in a given view. In some examples, the accelerated high resolution radiography process 300 may use two or more detector positions while the sample 102 is in a given view. In some examples where two or more detector positions are used, each detector position used by the accelerated high resolution radiography process 300 while the sample 102 is in a given view may be offset by less than a pixel length of a detector pixel 404 (e.g., less than a pixel width in the x-axis and / or a pixel height in the y-axis) from each other (or at least one other) detector position used while the sample 102 is in a given view.

[0068] FIG. 6 shows an example of how two detector positions can be offset from each other by less than a detector pixel length. In the example of FIG. 6, two different detector pixel grids 402 of detector pixels 404 are shown, showing two different positions of the X-ray detector 108. The first detector pixel grid 402a of detector pixels 404a is depicted using a solid line, while the second detector pixel grid 402b of detector pixels 404b is depicted using a dashed line. As shown, the two different detector pixel grids 402 are offset from each other by less than a pixel length. In particular, the position of the detector pixel grid 402b is offset from the position of the detector pixel grid 402a by half a detector pixel 404 in the positive x-direction and half a detector pixel in the negative y-direction (so that the offset in the diagonal direction is smaller than that of the detector pixel 404). Such an offset of less than the pixel length of the detector pixel 404 may be referred to as a sub-pixel offset. Although the detector pixel grids 402 are shown as being diagonally offset from one another for reasons of clarity and illustration, in some examples the detector pixel grids 402 may be offset only in the x-axis or only in the y-axis.

[0069] 7 shows an example of four different detector positions offset from each other by sub-pixels, the four positions being I, II, III, and IV. In the example of FIG. 7, the larger dotted rectangle represents the perimeter (and / or maximum range of motion) of the X-ray detector 108 across all the different detector positions I, II, III, and IV. The X-ray detector 108 is shown as smaller solid grey rectangles positioned within the dotted rectangle at the different detector positions I, II, III, and IV. As shown, each detector position is offset from each other detector position by less than a detector pixel 404.

[0070] In the example of Fig. 7, the first detector position (I) and the second detector position (II) of the X-ray detector 108 correspond to the positions of the solid detector pixel grid 402a and the dotted detector pixel grid 402b of Fig. 6. For positions within the dotted perimeter, the X-ray detector 108 is at the top left at the first detector position (I) and at the bottom right at the second detector position (II). The depicted third detector position (III) and fourth detector position (IV) are approximate mirror image positions of the first detector position (I) and the second detector position (II), respectively. For positions within the dotted perimeter, the X-ray detector 108 is at the top right at the third detector position (III) and at the bottom left at the fourth detector position (IV).

[0071] In the example of FIG. 3a, the accelerated high resolution radiography process 300 returns to block 306 and moves the X-ray detector 108 to the next detector position if the accelerated high resolution radiography process 300 determines that the X-ray detector 108 should be moved to a different detector position in block 310. For example, the first detector position may be detector position I shown in FIG. 7 and the next detector position may be detector position II shown in FIG. 7 offset by a sub-pixel from detector position I. Then, in block 308, the accelerated high resolution radiography process 300 captures another low resolution 2D radiograph 500a while the X-ray detector 108 is in the new detector position, similar to that described above. After block 308, the accelerated high resolution radiography process 300 again determines whether the X-ray detector 108 should be moved to a different detector position in block 310, as described above. Blocks 306-310 continue to execute until, in block 310, the accelerated high resolution radiography process 300 determines whether the x-ray detector 108 should be moved to a different detector position.

[0072] In some examples, the number of detector positions used by the accelerated high resolution radiography process 300 while the sample 102 is in a given view may be less than the number of high resolution radiography pixels 504b in the high resolution 2D radiograph 500b divided by the number of low resolution radiography pixels 504a in the low resolution 2D radiograph 500a. Thus, for example, if there are four times as many high resolution radiography pixels 504b as there are low resolution radiography pixels 504a (e.g., as shown in Figures 5a and 5b), the number of detector positions used by the accelerated high resolution radiography process 300 while 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 four positions (I, II, III, IV) shown in Figure 7.

[0073] If the accelerated high resolution radiography process 300 determines in block 310 that the x-ray detector 108 should not be moved to a new detector position, the accelerated high resolution radiography process 300 proceeds to block 312 where the accelerated high resolution radiography process 300 determines whether another view (e.g., orientation, magnification, or position) of the sample 102 is required (e.g., based on the parameter(s) identified in block 302). For example, if a high resolution three-dimensional (3D) radiographic volume, model, and / or image is to be constructed (e.g., using multiple high resolution 2D radiographs 500b), the accelerated high resolution radiography process 300 may determine that another orientation of the sample 102 is required until the sample 102 has been rotated 360 degrees. In contrast, if only a single high resolution 2D radiograph 500b is desired, the accelerated high resolution radiography process 300 may determine that another orientation of the sample 102 is not required. In another example, the accelerated high resolution radiography process 300 may determine that a different orientation of the sample is required if multiple high resolution 2D radiographs 500b are desired even if a 3D radiography volume is not constructed. In another example, the accelerated high resolution radiography process 300 may determine that the parameters require a different magnification or position of the sample 102 (e.g., relative to the x-ray detector 108 or x-ray emitter 106).

[0074] 3a, if the accelerated high resolution radiography process 300 determines that another view of the sample 102 is required, the accelerated high resolution radiography process 300 proceeds to block 314 where the accelerated high resolution radiography process 300 moves the sample 102 and / or the x-ray emitter 106 and x-ray detector 108 (e.g., via the positioning system 199) to position the sample 102 for the next view. In some examples, the next view of the sample 102 may be determined based on the current view of the sample 102 and / or one or more of the parameters identified in block 302. For example, the parameter(s) may specify a particular sequence of orientations of the sample 102 or incremental degrees of rotation that change the orientation of the sample 102 a particular number of times or until a final target orientation or degree of rotation is reached. In some examples, the accelerated high resolution radiography process 300 may use one or more sensors (e.g., position sensor(s), angle sensor(s), etc.) of the radiographer 100 to determine the view of the sample 102 (e.g., relative to the x-ray emitter 106 and / or the x-ray detector 108) and / or to determine when the next view of the sample 102 has been achieved.

[0075] After block 314, the accelerated high resolution radiography process 300 returns to block 306 where the accelerated high 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).

[0076] 3a, 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, in some examples this configuration may be reversed. In such a reversal, blocks 306 and 314 may effectively switch positions, and blocks 310 and 312 may effectively switch positions. However, such a reversal may make shift correction more difficult, as described below.

[0077] 3a, blocks 306-314 continue to iterate until the accelerated high resolution radiography process 300 determines that no low resolution 2D radiographs 500a need to be captured in additional views of the sample 102. Once this determination is made, the accelerated high resolution radiography process 300 proceeds to block 316 where the high resolution radiography process 300 performs a shift correction on the captured low resolution 2D radiograph 500a.

[0078] Shift correction refers to correction for unintended and / or undesired shifts in the focal point of radiation on the X-ray detector 108 that may occur over time due to thermal effects, etc. In some examples, this shift in focal point may result in a shift in the perspective of the low-resolution 2D radiograph 500a. In some examples, the degree of shift that occurs over the time it takes to perform a 360-degree scan may be measured based on a comparison of two low-resolution 2D radiographs 500a taken at the beginning and end of a 360-degree scan, with the X-ray detector 108 in the same position and the sample 102 in the same orientation (e.g., at 0 degrees rotation and 360 degrees rotation of the sample 102) for both low-resolution 2D radiographs 500a. In some examples, a corrective action may be determined based on the shift and applied to one or more low-resolution 2D radiographs 500a captured during the 360-degree scan to compensate for the shift. This shift correction may improve the quality and / or consistency of the low-resolution 2D radiographs 500a. Because shift correction requires a full 360 degree scan (and / or rotation of sample 102), block 316 can be skipped if such a full 360 degree scan (and / or rotation of sample 102) is not performed.

[0079] A conventional 360 degree sub-pixel sampling scan may not be able to utilize the shift correction because in a conventional 360 degree sub-pixel sampling scan (e.g., with 3D reconstruction), the X-ray detector 108 is moved 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 rotation of the sample 102) is completed. Furthermore, the shift in focus may be different during different scans (and / or 360 degree rotations of the sample 102). Thus, even if the shift is measured at the end of a first full scan when the X-ray detector 108 is in a first detector position (e.g., detector position I) and at the end of a second full scan when the X-ray detector 108 is in a second detector position (e.g., detector position II), the measured shift for the two scans may be significantly different. Thus, the determined corrections may be significantly different. If different corrections are applied to each set of low-resolution 2D radiographs 500a and then the two sets of low-resolution 2D radiographs 500a are interlaced to generate the high-resolution 2D radiographs 500b, lower image quality, loss of detail, lower sharpness, blurring, distortion, artifacts, and / or other adverse effects may result.

[0080] In contrast, in the exemplary accelerated high resolution radiography process 300 shown in Figure 3a, only one 360 ​​degree scan (and / or rotation of the sample 102) needs to be performed. All of the different detector positions of the x-ray detector 108 can be achieved during one 360 ​​degree scan (and / or rotation of the sample 102).

[0081] 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 can be measured by comparing the low-resolution 2D radiographs 500a acquired at 0 and 360 degrees for detector positions I and / or II. Also, since the time difference between the capture of the low-resolution radiographs 500a at detector positions I and II is minimized, the difference in the measured shift and / or determined correction should be minimal. Indeed, in some examples, only one shift may be measured to save time. Thereby, the shift correction may be applied in the accelerated high-resolution radiography process 300, resulting in improved quality and / or consistency of the low-resolution 2D radiographs 500a.

[0082] 3a, after shift correction of the low resolution 2D radiograph 500a, the accelerated high resolution radiograph process 300 generates one or more high resolution 2D radiographs 500b and / or sets pixel values ​​of the high resolution 2D radiograph(s) 500b at block 350 during the accelerated high resolution pixel setting process 350. In some examples, the pixel value of the high resolution radiograph pixel 504b is set using the pixel value of the low resolution radiograph pixel 504a of the low resolution 2D radiograph(s) 500a captured at block 308.

[0083] 3b is a flow chart illustrating an example operation of the accelerated high resolution pixel setting process 350. As shown, the accelerated high resolution pixel setting process 350 begins at block 352, where the accelerated high resolution pixel setting process 350 identifies a particular view of the sample 102 from which to generate the high resolution 2D radiograph 500b. In some examples, this particular view may be the lowest rotation degree (e.g., 0 degrees, 1 degree, etc.) of the sample 102 at which the low resolution 2D radiograph 500a was initially captured. After selecting a particular orientation at block 352, the accelerated high resolution pixel setting process 350 generates an "empty" high resolution 2D radiograph 500b (e.g., having no pixel values ​​set) for that particular orientation at block 354.

[0084] In block 356, the accelerated high resolution pixel setting process 350 sets pixel values ​​for a first portion of the high resolution radiograph pixels 504b of the high resolution 2D radiograph 500b. In some examples, the first portion of the high resolution radiograph pixels 504b may include fewer high resolution radiograph pixels 504b than the total number of high resolution radiograph pixels 504b in the high resolution 2D radiograph 500b. In some examples, the number of high resolution radiograph pixels 504b in the first portion is equal to the total number of high resolution radiograph pixels 504b in the high resolution 2D radiograph 500b divided by the total number of low resolution radiograph pixels 504a in the low resolution 2D radiograph 500a multiplied by the number of low resolution 2D radiographs 500a captured in block 308 for a particular view.

[0085] In some examples, pixel values ​​for a first portion of high resolution radiograph pixels 504b are set based on the low resolution 2D radiograph(s) 500a captured in block 308 for a particular view of the sample 102. In particular, pixel values ​​for a first portion of high resolution radiograph pixels 504b are set based on pixel values ​​of low resolution radiograph pixels 504a of the low resolution 2D radiograph(s) 500a captured in block 308 for a particular view of the sample 102.

[0086] In some examples, each low resolution radiograph pixel 504a of each low resolution 2D radiograph(s) 500a captured in block 208 for a particular view is used to set a pixel value of one high resolution radiograph pixel 504b that is within the same area as the low resolution radiograph pixel 504a. For example, in Figures 5a and 5b, the low resolution radiograph pixel 504a in the upper left corner of the low resolution 2D radiograph 500a covers the same area as four high resolution radiograph pixels 504b in the upper left corner of the high resolution 2D radiograph 500b. Thus, in some examples, the low resolution radiograph pixel 504a in the upper left corner of the low resolution 2D radiograph 500a is used to set a pixel value of one of the four high resolution radiograph pixels 504b in the upper left corner of the high resolution 2D radiograph 500b.

[0087] In some examples, the detector position of the X-ray detector 108 when the low resolution 2D radiograph 500a is captured can determine which of the high resolution radiograph pixels 504b in the covered area are set. For example, the low resolution radiograph pixel 504a in the upper left corner of the low resolution 2D radiograph 500a captured when the X-ray detector 108 is in the upper left detector position I can be used to set the high resolution radiograph pixel 504b in the upper left corner in the high resolution 2D radiograph 500b. As another example, the low resolution radiograph pixel 504a in the upper left corner of the low resolution 2D radiograph 500a captured when the X-ray detector 108 is in the lower right detector position II can be used to set the high resolution radiograph pixel 504b that is diagonally adjacent to the high resolution radiograph pixel 504b in the high resolution 2D radiograph 500b.

[0088] This positional relationship between detector position and pixel position is shown, for example, in Figure 8a. In the example of Figure 8a, the grey low resolution radiograph pixel 504a at the top left of the dashed rectangle represents the low resolution radiograph pixel 504a at the top left corner of the low resolution 2D radiograph 500a captured when the X-ray detector 108 is in the top left detector position I. The black low resolution radiograph pixel 504a at the bottom right of the dashed rectangle represents the low resolution radiograph pixel 504a at the top left corner of the low resolution 2D radiograph 500a captured when the X-ray detector 108 is in the bottom right detector position II.

[0089] In the example of Figure 8a, the top left high resolution radiograph pixel 504b is the same gray color as the top left low resolution radiograph pixel 504a, indicating that the pixel (e.g., grayscale) value of the top left high resolution radiograph pixel 504b was set according to (and / or the same as) the pixel value of the top left low resolution radiograph pixel 504a. Similarly, the bottom right high resolution radiograph pixel 504b is the same black color as the bottom right low resolution radiograph pixel 504a, indicating that the pixel (e.g., grayscale) value of the bottom right high resolution radiograph pixel 504b was set according to (and / or the same as) the pixel value of the bottom right low resolution radiograph pixel 504a.

[0090] In some conventional sub-pixel sampling examples, the top right and bottom left high resolution radiograph pixels 504b are similarly set using the low resolution radiograph pixels 504a from the low resolution 2D radiograph 500a captured when the X-ray detector 108 is in the top right detector position III and the bottom left detector position IV. However, in the example of FIG. 8a, the top right and bottom left high resolution radiograph pixels 504b are shown in white to indicate that they are "empty" and have no pixel values ​​set. Conventional sub-pixel sampling could set pixel values ​​for all high resolution radiograph pixels 504b based on the low resolution radiograph pixels 504a, but this would require the capture of more low resolution 2D radiographs 500a. In contrast, the high resolution radiograph process 300 (and / or the accelerated high resolution pixel setting process 350) sets pixel values ​​for only a first portion of the high resolution radiograph pixels 504b. This technique of setting pixel values ​​for only some, rather than all, of the high resolution radiograph pixels 504b based on the low resolution radiograph pixels 504a means that fewer low resolution 2D radiographs 500a need to be captured, thereby saving considerable time and requiring less movement of the X-ray detector 108 (which can save wear and tear).

[0091] Because fewer low resolution 2D radiographs 500a are captured than are needed to set pixel values ​​for each high resolution radiograph pixel 504b, after the pixel values ​​of a first portion of the high resolution radiograph pixels 504b have been set in block 356, a portion of the high resolution radiograph pixels 504b remain unset (and / or "empty"). This situation is depicted, for example, in Figure 8b, where a first portion (e.g., half) of the high resolution radiograph pixels 504b are colored gray or black to indicate that their pixel values ​​have been set, while the remaining portion (e.g., half) of the high resolution radiograph pixels 504b are colored white to represent the absence of pixel values. In the example of Figure 3b, the pixel values ​​of the remaining portion of the high resolution radiograph pixels 504b are set by the accelerated high resolution pixel setting process 350 in block 358.

[0092] In some examples, the accelerated high resolution pixel setting process 350 sets pixel values ​​for the remaining portion of the high resolution radiograph pixel 504b based on an analysis of pixel values ​​of the first portion of the high resolution radiograph pixel 504b. In some examples, the analysis may include and / or use some (e.g., bicubic, linear, bilinear, nearest neighbor, etc.) interpolation of nearby, adjacent, and / or surrounding first portions of the high resolution radiograph pixels 504b. Adjacent in this context may refer to adjacent high resolution radiograph pixels 504b horizontally along the x-axis, vertically along the y-axis, and / or diagonally along a diagonal axis that bisects the x-axis and y-axis.

[0093] 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 (e.g., stored in the memory circuitry 212) of previously captured low resolution 2D radiographs 500a and / or high resolution 2D radiographs 500b.

[0094] Research has shown that the quality and / or amount of detail in the high resolution 2D radiograph 500b can still be very high and / or only slightly reduced by using some analysis of the pixel values ​​of the first portion of the high resolution radiograph pixels 504b to populate the remaining high resolution radiograph pixels 504b. Also, the generation of the high resolution 2D radiograph 500b is significantly faster because fewer low resolution 2D radiographs 500a need to be captured. Additionally, capturing fewer low resolution 2D radiographs 500a requires less movement of the X-ray detector 108 (e.g., via the positioning system 199), which can prevent wear and tear.

[0095] In the example of Figure 3b, the accelerated high resolution pixel setting process 350 determines in block 360 whether there is another view of the sample 102 for which a high resolution 2D radiograph 500b is to be generated. If there is, the accelerated high resolution pixel setting process 350 iterates for the next view in block 352 and then loops through blocks 354-358 again for that view of the sample 102. If not, the accelerated high resolution pixel setting process 350 ends and the accelerated high resolution radiograph process 300 proceeds to block 318.

[0096] In the example of FIG. 3a, the accelerated high resolution radiograph process 300 corrects one or more of the high resolution 2D radiographs 500b generated during the accelerated high resolution pixel setting process 350 at block 318. In some examples, the correction at block 318 may include deconvolution. In some examples, the correction may include and / or use one or more artificial intelligence mechanisms similar to those described above. Although shown as being performed at the end of the loop of blocks 306-314, in some examples, blocks 316, 350, and / or 318 may be performed after each loop of blocks 306-310.

[0097] After block 318, the accelerated high resolution radiograph process 300 proceeds to block 320 where the accelerated high resolution radiograph process 300 assembles the high resolution 2D radiographs 500b into one or more high resolution 3D volumes (if so desired and / or possible). In some examples, the accelerated high resolution radiograph process 300 may further obtain one or more specific slices of the high resolution 2D radiographs 500b from the high 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 previously generated and / or obtained high resolution 2D radiographs 500b.

[0098] 3a, after block 320, the accelerated high resolution radiography process 300 proceeds to block 322, where one or more (e.g., visual) representations of the high resolution 3D volume and / or the high resolution 2D radiograph 500b 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 high resolution radiography process 300 ends.

[0099] The X-ray radiography system 200 described in this disclosure enables the generation of a high resolution 2D radiograph 500b using an accelerated high resolution radiograph process 300. In particular, the accelerated high resolution radiograph process 300 uses pixel (e.g., grayscale) values ​​of one or more low resolution 2D radiographs 500a to set pixel values ​​for a first portion of high resolution radiograph pixels 504b of the high resolution 2D radiograph 500b. The remaining portion of the high resolution radiograph pixels 504b are set based on an analysis of the first portion. The accelerated high resolution radiograph process 300 is faster than more conventional processes because the accelerated high resolution radiograph process 300 requires fewer low resolution radiographs to be captured, thus saving time and / or reducing wear and tear on the radiographer 100, while at the same time providing a high quality high resolution 2D radiograph 500b.

[0100] The method and / or system can be implemented in hardware, software, and / or a combination of hardware and software. The method and / or system can be implemented centrally in at least one computing system, or in a distributed fashion where different elements are distributed across several interconnected and / or remote computing systems. Any kind of computing system or other device adapted to perform the methods described in this disclosure is suitable. A typical combination of hardware and software can include a general-purpose computing system, with a program or other code that, when loaded and executed, controls the computing system to perform the methods described in this disclosure. Another typical embodiment can include an application-specific integrated circuit or chip. Some embodiments can include a non-transitory machine-readable (e.g., computer-readable) medium (e.g., flash drive, optical disk, magnetic storage disk, etc.), which stores one or more instructions (e.g., lines of code) executable by a machine, thereby causing the machine to perform a process as described in this disclosure.

[0101] Although the method and / or system have been described with reference to certain specific embodiments, those skilled in the art will recognize that various modifications can be made and equivalents can be substituted without departing from the scope of the method and / or system. In addition, many modifications can be made to adapt a particular situation or material to the teachings of the disclosure without departing from its scope. Therefore, the method and / or system is not limited to the particular embodiments disclosed, but it is contemplated that the method and / or system will include all embodiments falling within the scope of the appended claims.

[0102] As used in this disclosure, "and / or" means any one or more of the items in the list linked by "and / or." As an example, "x and / or y" means any element of 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" means any element of 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."

[0103] As used in this disclosure, the term "for example" begins a list of one or more non-limiting examples, instances, or illustrations.

[0104] As used in this disclosure, the terms "coupled," "coupled to," and / or "coupled with" mean a structural and / or electrical connection, whether attached, attached, connected, joined, fastened, linked, and / or otherwise secured. As used in this disclosure, the term "attach" means attached, attached, connected, joined, fastened, linked, and / or otherwise secured. As used in this disclosure, the term "connect" means attached, attached, connected, joined, fastened, linked, and / or otherwise secured.

[0105] As used in this disclosure, the terms "circuitry" and "circuitry" refer to physical electronic components (i.e., hardware) and any software and / or firmware ("code") that may comprise, be executed by, or otherwise be associated with the hardware. As used in this disclosure, a particular processor and memory, for example, may include a first "circuitry" when executing a first one or more lines of code, and may include a second "circuitry" when executing a second one or more lines of code. As used in this disclosure, whenever circuitry includes the hardware and / or code (if either is necessary) necessary to perform a function, the circuitry is "operable" and / or "configured" to perform that function, regardless of whether performance of that function is disabled or enabled (e.g., by a user-configurable setting, factory trim, etc.).

[0106] As used in this disclosure, control circuitry can include digital and / or analog circuitry, discrete and / or integrated circuitry, microprocessors, DSPs, etc., software, hardware and / or firmware that constitutes part or all of the controller and / or is located on one or more boards used to control the welding process and / or devices such as the power supply and wire feeder.

[0107] As used in this disclosure, the term "processor" refers to processing devices, apparatus, programs, circuits, components, systems, and subsystems, whether implemented in hardware, tangibly embodied software, or both, and whether programmable or not. As used in this disclosure, the term "processor" includes, but is not limited to, one or more computing devices, hardwired circuits, signal modifying devices and systems, system control devices and machines, central processing units, programmable devices and systems, field programmable gate arrays, application specific integrated circuits, systems on chips, systems with discrete elements and / or circuits, state machines, virtual machines, data processors, processing facilities, and any combination of the above. A processor can be, for example, any type of general purpose microprocessor or general purpose microcontroller, digital signal processing (DSP) processor, application specific integrated circuit (ASIC), graphics processing unit (GPU), reduced instruction set computer (RISC) processor with advanced RISC machine (ARM) core, etc. The processor may be coupled to and / or integrated into a memory device.

[0108] As used in this disclosure, the terms "memory" and / or "memory device" refer to computer hardware or circuitry that stores information for use by a processor and / or other digital device. The memory and / or memory device can 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 disc 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 medium, etc. 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, stacked memory, non-volatile RAM (NVRAM), static RAM (SRAM), cache, buffer, semiconductor memory, magnetic memory, optical memory, flash memory, flash card, compact flash card, memory card, secure digital memory card, micro card, mini card, expansion card, smart card, memory stick, multimedia card, picture card, flash storage, subscriber identity module (SIM) card, hard drive (HDD), solid state drive (SSD), etc. Memory may be configured to store code, instructions, applications, software, firmware, and / or data and may be external, internal, or both to the processor.

Claims

1. A non-transitory computer readable medium containing machine readable instructions that, when executed by processing circuitry, perform: capturing a low 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; generating a high resolution radiograph of the sample based on the low resolution radiograph, the high resolution radiograph including more pixels than the low resolution radiograph, the high resolution radiograph having high resolution pixels, the high resolution radiograph comprising: determining first high resolution pixel values ​​for a first portion of the high resolution pixels based on low resolution pixel values ​​of the low resolution radiograph; using the analysis of the first high resolution pixel value for the first portion of the high resolution pixels to establish a remaining high resolution pixel value for a remaining portion of the high resolution pixels of the high resolution radiograph; generating a high resolution radiograph, a non-transitory computer-readable medium that causes the processing circuitry to perform

2. The low resolution radiograph comprises a first low resolution radiograph of the sample while the radiation detector is at a first detector position and the sample is at a sample orientation relative to the radiation emitter or the radiation detector, the low resolution pixel values ​​comprise first low resolution pixel values, and the non-transitory computer readable medium, when executed by the processing circuitry, performs a program for: capturing a second low resolution radiograph of the sample while the radiation detector is in a second detector position and the sample is in the sample orientation; the first high resolution pixel value for the first portion of the high resolution pixel is set based on the first low resolution pixel value of the first low resolution radiograph and a second low resolution pixel value of the second low resolution radiograph. capturing a second low resolution radiograph; 10. The non-transitory computer readable medium of claim 1, further comprising machine readable instructions that cause the processing circuitry to:

3. 3. The non-transitory computer-readable medium of claim 2, wherein the radiation detector includes a detector surface including a plurality of detector pixels, each detector pixel 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, and the second detector position is offset from the first detector position by a first distance along the first detector axis or 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. 4. The non-transitory computer readable medium of claim 3, further comprising machine readable instructions that, when executed by the processing circuitry, cause the processing circuitry to: move the radiation detector from the first detector position to the second detector position using a positioning system.

5. 10. 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 high resolution radiograph on a display screen.

6. 10. 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 a correction to the high resolution pixels of the high resolution radiograph.

7. 10. 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 construct a three-dimensional high resolution radiography volume using the high resolution radiograph and one or more additional high resolution radiographs.

8. 1. 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 within the radiation path of the radiation; an image acquisition system; the image acquisition system comprising: A processing circuit unit; memory circuitry containing machine-readable instructions; the machine-readable instructions, when executed by the processing circuitry, capturing a low resolution radiograph of the sample using the radiation detected by the radiation detector; and generating a high resolution radiograph of the sample based on the low resolution radiograph, the high resolution radiograph including more pixels than the low resolution radiograph, the high resolution radiograph having high resolution pixels, the high resolution radiograph comprising: determining first high resolution pixel values ​​for a first portion of the high resolution pixels based on low resolution pixel values ​​of the low resolution radiograph; using the analysis of the first high resolution pixel value for the first portion of the high resolution pixels to establish a remaining high resolution pixel value for a remaining portion of the high resolution pixels of the high resolution radiograph; generating a high resolution radiograph, causing the processing circuit unit to perform system.

9. the low resolution radiograph comprises a first low resolution radiograph of the sample while 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 low resolution pixel values ​​comprise first low resolution pixel values, and the memory circuitry, when executed by the processing circuitry, capturing a second low resolution radiograph of the sample while the radiation detector is in a second detector position and the sample is in the sample orientation; the first high resolution pixel value for the first portion of the high resolution pixel is set based on the first low resolution pixel value of the first low resolution radiograph and a second low resolution pixel value of the second low resolution radiograph. capturing a second low resolution radiograph; 10. The system of claim 8, further comprising machine-readable instructions that cause the processing circuitry to:

10. 10. The system of claim 9, wherein the radiation detector includes a detector surface including a plurality of detector pixels, each detector pixel 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, and the second detector position is offset from the first detector position by a first distance along the first detector axis or 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. 10. The system of claim 8, wherein the image acquisition system further comprises a display screen configured to display a visual representation of the high resolution radiograph.

13. 9. The system of claim 8, wherein the memory circuitry further comprises machine readable instructions that, when executed by the processing circuitry, cause the processing circuitry to apply a correction to the high resolution pixels of the high resolution radiograph.

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

15. 1. A method for accelerated production of high resolution radiographs, comprising: capturing a low 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; generating, by processing circuitry, a high resolution radiograph of the sample based on the low resolution radiograph, the high resolution radiograph including more pixels than the low resolution radiograph, the high resolution radiograph having high resolution pixels, the high resolution radiograph having: determining, by the processing circuitry, first high resolution pixel values ​​for a first portion of the high resolution pixels based on low resolution pixel values ​​of the low resolution radiograph; establishing, by the processing circuitry, residual high resolution pixel values ​​for a remaining portion of the high resolution pixels of the high resolution radiograph using the analysis of the first high resolution pixel value for the first portion of the high resolution pixels; generating a high resolution radiograph, A method comprising:

16. The low resolution radiograph comprises a first low resolution radiograph of the sample while the radiation detector is at a first detector position and the sample is at a sample orientation relative to the radiation emitter or the radiation detector, the low resolution pixel values ​​comprise first low resolution pixel values, and the method further comprises: using the radiation detector to capture a second low resolution radiograph of the sample while the radiation detector is in a second detector position and the sample is in the sample orientation; the first high resolution pixel value for the first portion of the high resolution pixel is set based on the first low resolution pixel value of the first low resolution radiograph and a second low resolution pixel value of the second low resolution radiograph. capturing a second low resolution radiograph; The method of claim 15 further comprising:

17. 17. The method of claim 16, wherein the radiation detector includes a detector surface including a plurality of detector pixels, each detector pixel 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, and the second detector position is offset from the first detector position by a first distance along the first detector axis or 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. 20. 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. applying a correction by the processing circuitry to the high resolution pixels of the high resolution radiograph; displaying a visual representation of said high resolution radiograph on a display screen; The method of claim 15 further comprising:

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

Images