CN118202233A - High resolution continuous rotation industrial radiographic imaging process - Google Patents

Abstract

Examples of industrial radiography systems are described herein that control or recommend certain parameter values of a high resolution, continuously rotating radiographic imaging process. By controlling or recommending specific parameter values, it may be possible to alleviate certain synchronization problems that occur during high resolution, continuously rotating radiographic imaging procedures. With the synchronization problem alleviated, the user is able to perform high-resolution, continuously rotating radiographic imaging procedures at high speed without loss of detail and/or blurring sometimes caused by the synchronization problem.

Description

High resolution continuous rotation industrial radiographic imaging process

Cross Reference to Related Applications

The present application claims priority from U.S. provisional application No. 63/244,329, entitled "HIGH RESOLUTION CONTINUOUS ROTATION INDUSTRIAL RADIOGRAPHY IMAGING PROCESSES [ high resolution continuous rotation industrial radiographic imaging procedure ]", filed 9/15 of 2021, the entire contents of which are incorporated herein by reference.

Technical Field

The present disclosure relates generally to industrial radiographic imaging procedures, and more particularly, to high resolution, continuously rotating industrial radiographic imaging procedures.

Background

Industrial radiographic imaging 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, electronic, medical, pharmaceutical, military, and/or defense applications. The 2D radiographic image may be inspected to inspect the part(s) for cracks, flaws and/or defects that may or may not be generally visible to the human eye.

Limitations and disadvantages of conventional and traditional approaches will become apparent to one of skill in the art, through comparison of such systems with the present disclosure as set forth in the remainder of the present application with reference to the drawings.

Disclosure of Invention

The present disclosure relates to a high resolution, continuously rotating industrial radiographic imaging process substantially as shown in and/or described in connection with at least one of the figures, and as set forth more completely in the claims.

These and other advantages, aspects and novel features of the present disclosure, as well as details of illustrated examples thereof, will be more fully understood from the following description and drawings.

Drawings

Fig. 1 illustrates an example of an industrial X-ray radiation camera in accordance with aspects of the present disclosure.

Fig. 2 is a block diagram illustrating an example X-ray radiography system having the industrial X-ray camera of fig. 1 in accordance with aspects of the present disclosure.

Fig. 3 is a flowchart illustrating an example operation of a high resolution imaging process of the X-ray radiography system of fig. 2 in accordance with aspects of the present disclosure.

Fig. 4 illustrates how different images captured at different (e.g., subpixel shifted) X-ray detector positions may be combined together to produce a single higher resolution image in accordance with aspects of the present disclosure.

Fig. 5 a-5 b illustrate concepts of angular variation introduced due to lack of synchronization between the start of rotation of an object and the start of image capture of the object, in accordance with aspects of the present disclosure.

Fig. 6 illustrates an example of a display screen showing various parameters of the high resolution imaging process of fig. 3, in accordance with aspects of the present disclosure.

The figures are not necessarily drawn to scale. Wherever appropriate, the same or like reference numbers will be used throughout the drawings to refer to the same or like elements. For example, instances of the same reference number (e.g., grid 402) without a letter are denoted with the reference number (e.g., grid 402a, grid 402 b) of the letter.

Detailed Description

Some examples of the present disclosure relate to industrial radiography systems that control or recommend certain parameter values of high resolution, continuously rotating radiographic imaging processes. By controlling or recommending specific parameter values, it is possible to alleviate certain synchronization problems that occur during high resolution, continuously rotating radiographic imaging procedures. With the synchronization problem alleviated, the user may be able to perform high-resolution, continuously rotating radiographic imaging procedures at high speed without loss of detail and/or increased ambiguity, which is frequent due to the synchronization problem.

Some examples of the present disclosure relate to a non-transitory computer-readable medium comprising machine-readable instructions that, when executed by a processor, cause the processor to: receiving, via an input device of a user interface, a selection of a continuous high resolution image acquisition process that acquires radiographic images of the object at a plurality of different detector positions of the radiation detector while the object is rotating; in response to the selection, identifying a maximum starting angle change comprising a maximum allowable difference between an orientation of the object when a first initial image is acquired during the high resolution image acquisition process and an orientation of the object when a second initial image is acquired, the first initial image being acquired during the high resolution image acquisition process when the radiation detector is in a first detector position, and the second initial image being acquired during the high resolution image acquisition process when the radiation detector is in a second detector position; setting or recommending a first parameter value of a first parameter as a first value or a second parameter value of a second parameter as a second value based on the maximum starting angle change; and performing a high resolution image acquisition process based on the first parameter value and the second parameter value to generate an image of the object.

In some examples, the first parameter includes a number of image projections and the second parameter includes a number of image frames averaged together to produce one image projection. In some examples, the non-transitory computer-readable medium further includes machine-readable instructions for a high resolution image acquisition process, which when executed by processing circuitry, cause the processing circuitry to: generating a first set of radiographic images based on radiation detected by the radiation detector while the radiation detector is in the first detector position, when the rotatable clamp rotates the object through the first revolution; generating a second set of radiographic images based on radiation detected by the radiation detector while the radiation detector is in the second detector position, when the rotatable clamp rotates the object through the second revolution; and generating a third set of higher resolution radiographic images based on the radiographic images of the first set of radiographic images and the corresponding radiographic images of the second set of radiographic images, the higher resolution radiographic images having a higher resolution than the radiographic images of the first set of radiographic images and the corresponding radiographic images of the second set of radiographic images, wherein a size of the first set of radiographic images, the second set of radiographic images, or the third set of radiographic images is dependent on a first parameter value of the first parameter or a second parameter value of the second parameter.

In some examples, the non-transitory computer-readable medium further includes machine-readable instructions for a high resolution image acquisition process, which when executed by processing circuitry, cause the processing circuitry to: a third set of higher resolution radiographic images are combined into an image of the object that includes data representing a two-dimensional (2D) image, data representing a three-dimensional (3D) volume, or data representing a 2D slice of the 3D volume. In some examples, the first set of radiographic images and the second set of radiographic images are equal in size to the first parameter value times the second parameter value, and the third set of radiographic images are equal in size to the first parameter value. In some examples, setting or recommending a first parameter value of a first parameter to a first value or a second parameter value of a second parameter to a second value based on a maximum starting angle change includes: determining one or more first values of the first parameter or a second value of the second parameter, which may result in a starting angular change exceeding a maximum starting angular change, the starting angular change comprising a difference between an orientation of the object when a first initial image of the first set of radiographic images is acquired by the radiation detector during a first rotation of the object and an orientation of the object when a second initial image of the second set of radiographic images is acquired by the radiation detector during a second rotation of the object, and disabling or disabling the input or selection of the one or more first values of the first parameter or the second value of the second parameter, or not recommending the input or selection of the one or more first values of the first parameter or the second value of the second parameter.

In some examples, setting or recommending a first parameter value of the first parameter to a first value or a second value of the second parameter to a second value based on the maximum starting angle change further comprises automatically setting the first parameter value or the second parameter value such that the starting angle change will not exceed the maximum starting angle change. In some examples, the first detector position is offset from the second detector position by less than a pixel size of the radiation detector. 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: the image is displayed on a display screen. In some examples, the maximum starting angular change is identified based on a geometric magnification of the industrial radiographic imaging system, which includes a first distance from the radiation emitter to the radiation detector divided by a second distance from the radiation emitter to the object, or an image quality required for a particular application of the industrial radiographic imaging system.

Some examples of the present disclosure relate to an industrial radiographic imaging system comprising: a radiation emitter configured to emit radiation; a radiation detector configured to detect radiation emitted by the radiation emitter; a rotatable clamp configured to hold and rotate an object, the rotatable clamp positioned between the radiation emitter and the radiation detector; a detector positioner configured to move the radiation detector to a plurality of different detector positions; and an image acquisition system configured to generate an image of the object based on radiation detected by the radiation detector after passing through the object, the image acquisition system comprising: a user interface comprising an input device, processing circuitry, and memory circuitry, the memory circuitry comprising machine-readable instructions that, when executed by the processing circuitry, cause the processing circuitry to: a selection of a successive high resolution image acquisition process is received via the input device, the successive high resolution image acquisition process acquiring images at a plurality of different detector positions while rotating the object, in response to the selection, a maximum starting angle change is identified, the maximum starting angle change comprising a maximum allowable difference between an orientation of the object when a first initial image is acquired during the high resolution image acquisition process and an orientation of the object when a second initial image is acquired, the first initial image being acquired during the high resolution image acquisition process when the radiation detector is at the first detector position and the second initial image being acquired during the high resolution image acquisition process when the radiation detector is at the second detector position, a first parameter value of the first parameter is set or recommended to be a first value, or a second parameter value of the second parameter is set or recommended to be a second value, and the high resolution image acquisition process is performed based on the first value and the second value to generate an image of the object.

In some examples, the first parameter includes a number of image projections and the second parameter includes a number of image frames averaged together to produce one image projection. In some examples, the memory circuitry further includes machine-readable instructions for the high-resolution image acquisition process, which when executed by the processing circuitry, cause the processing circuitry to: a first set of radiographic images is generated based on radiation detected by the radiation detector when the rotatable clamp rotates the object a first turn while the radiation detector is in the first detector position, a second set of radiographic images is generated based on radiation detected by the radiation detector when the rotatable clamp rotates the object a second turn while the radiation detector is in the second detector position, and a third set of higher resolution radiographic images is generated based on the radiographic images of the first set of radiographic images and corresponding radiographic images of the second set of radiographic images, the higher resolution radiographic images having a higher resolution than the radiographic images of the first set of radiographic images and corresponding radiographic images of the second set of radiographic images, wherein a size of the first set of radiographic images, the second set of radiographic images, or the third set of radiographic images is based on the first value of the first parameter or the second value of the second parameter.

In some examples, the memory circuitry includes machine-readable instructions for a high-resolution image acquisition process that, when executed by the processing circuitry, further cause the processing circuitry to: a third set of higher resolution radiographic images are combined into an image of the object that includes data representing a two-dimensional (2D) image, data representing a three-dimensional (3D) volume, or data representing a 2D slice of the 3D volume. In some examples, the first set of radiographic images and the second set of radiographic images are equal in size to the first parameter value times the second parameter value, and the third set of radiographic images are equal in size to the first parameter value. In some examples, setting or recommending a first parameter value of a first parameter to a first value or a second parameter value of a second parameter to a second value based on a maximum starting angle change includes: determining one or more first values of a first parameter or a second value of a second parameter that may result in a starting angular change that exceeds a maximum starting angular change, the starting angular change including a difference between an orientation of the object when a first initial image of the first set of radiographic images is acquired by the radiation detector during a first revolution of the object and an orientation of the object when a second initial image of the second set of radiographic images is acquired by the radiation detector during a second revolution of the object, and disabling or preventing the input or selection of the one or more first values of the first parameter or the second value of the second parameter, or not recommending the input or selection of the one or more first values of the first parameter or the second value of the second parameter.

In some examples, setting or recommending a first parameter value of the first parameter to a first value or a second parameter value of the second parameter to a second value based on the maximum starting angle change further comprises automatically setting the first parameter value or the second parameter value such that the starting angle change will not exceed the maximum starting angle change. In some examples, the first detector position is offset from the second detector position by less than a pixel size of the radiation detector. In some examples, the memory circuitry further includes machine-readable instructions that, when executed by the processor: an image of the object is displayed on a display screen of the user interface. In some examples, the maximum starting angular change is identified based on a geometric magnification of the industrial radiographic imaging system, which includes a first distance from the radiation emitter to the radiation detector divided by a second distance from the radiation emitter to the object, or an image quality required for a particular application of the industrial radiographic imaging system.

Fig. 1 illustrates an example industrial X-ray radiation camera 100. In some examples, the X-ray radiation camera 100 may be used to perform non-destructive testing (NDT), digital Radiography (DR) scanning, computed Tomography (CT), and/or other applications on the object 102. In some examples, the object 102 may be an industrial component and/or an assembly of components (e.g., an engine casting, microchip, bolt, etc.). In some examples, the object 102 may be relatively small, such that finer, more detailed, higher resolution radiographic imaging procedures may be useful. Although discussed primarily in terms of X-rays for simplicity, in some examples, the industrial X-ray radiography 100 discussed herein may use other wavelengths of radiation (e.g., gamma rays, neutrons, etc.).

In the example of fig. 1, an X-ray radiation camera 100 directs X-ray radiation 104 from an X-ray emitter 106 through an object 102 to an X-ray detector 108. In some examples, the X-ray emitter 106 may include an X-ray tube configured to emit cone-shaped 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 kilo-electron volts (keV) to 10 meV.

In some examples, a two-dimensional (2D) digital image (e.g., a radiographic image, an X-ray image, etc.) may be generated based on X-ray radiation 104 incident on an X-ray detector 108. In some examples, the 2D image may be generated by the X-ray detector 108 itself. In some examples, the 2D image may be generated by the X-ray detector 108 in combination with a computing system in communication with the X-ray detector 108.

In some examples, the X-ray detector 108 (e.g., in free-running mode) may continue to capture/acquire 2D images at a given frame rate as long as the X-ray detector 108 is powered on. However, in some examples, the 2D image may be completely generated by the X-ray detector 108 (and/or associated computing system (s)) only when the scanning/imaging process has been selected and/or is running. Also, in some examples, the 2D image may only be saved in permanent (i.e., non-volatile) memory when the scanning/imaging process has been selected and/or is running.

In some examples, 2D images generated by the X-ray detector 108 (and/or associated computing system (s)) may be combined to form a three-dimensional (3D) volume and/or image. In some examples, 2D image slices of the 3D volume/image may also be formed. Although the term "image" is used herein as shorthand, it should be understood that the "image" 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, an X-ray detector 108, etc.).

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 images 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.) 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 that are in turn detected by a solid state detector panel (e.g., CMOS X-ray panel and/or CCD X-ray panel) coupled to the scintillation screen.

In some examples, the X-ray detector 108 (e.g., a solid state detector panel) may include pixels 404 (e.g., see fig. 4). In some examples, the pixels 404 may correspond to portions of a flicker screen. In some examples, the size of each 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 micrometers to 250 micrometers (e.g., 200 micrometers).

In some examples, the 2D image captured by the X-ray detector 108 (and/or an associated computing system) may contain features that are finer (e.g., smaller, denser, etc.) than the pixel size of the X-ray detector 108. For example, a computer microchip may have very fine features that are smaller than pixels 404. In such examples, it may be useful to use sub-pixel sampling to achieve a higher, more detailed resolution than otherwise would be possible.

For example, multiple 2D images of the object 102 may be captured when the object 102 is in the same orientation and the X-ray detector 108 is in two (or more) different positions. In some examples, different positions of the X-ray detector 108 may be staggered from one another by less than the size of the pixel 404 (i.e., sub-pixel). The plurality of subpixel shifted 2D images may then be combined (e.g., via an interleaving technique) to form a single higher resolution 2D image of the object 102 in that orientation. Thus, when the term "high resolution imaging process" is used herein, it may refer to an imaging process (e.g., radiography, computed tomography, etc.), wherein sub-pixel sampling is used to ensure that the resolution (and/or pixel density) of the final image is greater than the resolution (and/or pixel density) of the X-ray detector 108 (and/or a portion of the X-ray detector 108 and/or a virtual detector) used to capture the image. While sub-pixel sampling may be performed instead of translating the object 102 instead of the X-ray detector 108, the moving object 102 may also change the imaging geometry, which may negatively affect the resulting combination of images.

Fig. 4 illustrates the concept of using different images from different (e.g., subpixel shifted) positions of the X-ray detector 108 to form a single higher resolution image. As shown, the figure depicts two different grids 402 of pixels 404, indicating two different positions of the X-ray detector 108 that are offset from each other by less than the size of the pixels 404. The first grid 402a of pixels 404a is depicted using a solid line, while the second grid 402b of pixels 404b is depicted using a dashed line. As shown, the position of grid 402b is offset from the position of grid 402a by half a pixel 404 in the positive x-direction and by half a pixel in the negative y-direction (resulting in a smaller offset in the diagonal direction than pixel 404).

In the example of fig. 4, the smaller square formed by overlapping pixels 404 indicates how pixels 404 of two grids 402 may be combined to increase resolution beyond that of pixels 404 (e.g., to sub-pixel resolution). Further description of this concept can be found in ≡371, U.S. Pat. No. 9,459,217, entitled "High-Resolution Computed Tomography [ High resolution computed tomography ]", 9 months and 30 days of date 2015, the entire contents of which are incorporated herein by reference. Although two grids 402 are shown representing two positions for simplicity and clarity, in some examples, the X-ray detector 108 may be moved to four, six, eight, and/or more positions during sub-pixel sampling.

In the example of fig. 1, the X-ray machine 100 includes a detector positioner 150 configured to move the X-ray detector 108 to a different detector position (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 a rail 154. In some examples, the X-ray detector 108 may be held on (and/or attached to) the rail 154 by one or more intermediate supports.

In some examples, the detector positioner 150 may be configured to move the X-ray detector 108 along the rail 154 toward and/or away from either column 152. In some examples, the rails 154 may be configured to move along and/or parallel to the column 152 (e.g., up and/or down), thereby also moving the X-ray detector 108 along and/or parallel to the column 152. Although shown briefly in the example of fig. 1, in some examples, the detector positioner 150 may be more complex, similar to the x-translation stage 18, the y-translation stage 20, the detector mounting frame 26, and/or the x/y stage linear encoder 22/24 shown and described in the following patents: U.S. Pat. No. 9,459,217, entitled "High-Resolution Computed Tomography (High-resolution computed tomography)" for 30 months, 9, 2015, incorporated herein by reference in its entirety.

Because the X-ray detector 108 may be moved by the detector positioner 150, in some examples, the object 102 may be moved by the object positioner 110. In the example of fig. 1, an object locator 110 holds the object 102 in the path of the X-ray radiation 104, between the X-ray emitter 106 and the detector 108. In some examples, the object locator 110 may be configured to move the object 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 object 102). In some examples, the object locator 110 may be configured to move and/or rotate the object 102 such that a desired portion and/or orientation of the object 102 is located in the path of the X-ray radiation 104. In some examples, the object locator 110 may position the object 102 at different angles/orientations relative to the X-ray emitter 106 and/or the X-ray detector 108 to obtain 2D images at different orientations, which may then be used to generate one or more three-dimensional (3D) images of the object 102.

In the example of fig. 1, the object locator 110 includes a rotatable clamp 112 on which the object 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 may rotate about an axis defined by the spindle 116. In some examples, one or more alternative and/or additional rotation mechanisms may be provided.

In the example of fig. 1, the rotatable clamp 112 is supported by a support structure 118. In some examples, the support structure 118 may be configured to translate the rotatable clamp 112 (and/or the object 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 may include one or more actuators configured to apply translation(s).

Although one example object locator 110 is shown in the example of fig. 1, in some examples, a different object locator 110 may be used. For example, a robotic character positioner may be used to translate and/or rotate the object 102. Similarly, while shown as a circular plate in the example of fig. 1, in some examples rotatable clamp 112 may alternatively include a different clamp, e.g., a clip, clasp, gripper, and/or other retaining mechanism. In some examples, the X-ray emitter 106 and the X-ray detector 108 may instead rotate around the object 102 instead of (or in addition to) rotating the object 102 via the rotatable clamp 112 (e.g., which may be helpful if the object 102 is cumbersome).

In the example of fig. 1, the X-ray machine 100 further includes a rotatable platform 160 configured to move the X-ray emitter 106 and the X-ray detector 108 around the object 102. In the example of fig. 1, rotatable platform 160 is shown raised above and connected to X-ray emitter 106 and X-ray detector 108, as may occur, for example, when implemented using a gantry system.

In some examples, rotatable platform 160 may also be implemented in different ways, such as via a platform built-in on the floor of X-ray machine 100, one or more robotic movers, a conveyor, and/or one or more other suitable devices. In some examples, the rotatable platform 160 may be configured to rotate about a different (e.g., horizontal, diagonal, etc.) axis, with the X-ray emitter 106 and/or the X-ray detector 108 repositioned accordingly.

In some examples, one or more portions of the object locator 118 (e.g., the support structure 118) may be changed and/or omitted to facilitate use of the X-ray emitter 106 and the X-ray detector 108 (e.g., to leave their view unobstructed) while moving about the object 102 via the rotatable platform 160. In some examples, the rotatable platform 160 may 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 object 102.

Fig. 2 shows an example of an X-ray radiography system 200 including an X-ray radiography camera 100, such as the X-ray radiography camera 100 shown in fig. 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 only one X-ray camera 100, computing system 202, UI 204, and remote computing system 299 are shown in the example of fig. 2, in some examples, X-ray radiography system 200 may include several X-ray cameras 100, computing systems 202, UIs 204, and/or remote computing systems 299.

In the example of fig. 2, X-ray radiation camera 100 has an emitter 106, a detector 108, a detector positioner 150, and an object positioner 110 enclosed within a housing 199. As shown, the X-ray radiation camera 100 is connected to and/or in communication with computing system(s) 202 and UI(s) 204. In some examples, the X-ray radiography system 100 may also be in electrical communication with remote computing system(s) 299. In some examples, the communication and/or connection may be electrical, electromagnetic, wired, and/or wireless.

In the example of fig. 2, 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 displays, speakers, lights, haptic devices, and/or other devices. In some examples, a user may provide input to and/or receive output from X-ray camera(s) 100, computing system(s) 202, and/or remote computing system(s) 299 via UI(s) 204.

In some examples, UI(s) 204 may be part of computing system 202. In some examples, computing system 202 may implement one or more controllers of X-ray radiation camera(s) 100. In some examples, the computing system 202 may, along with the UI(s) 204, constitute an image acquisition system of the X-ray radiography system 200. In some examples, remote computing system(s) 299 may be similar to or the same as computing system 202.

In the example of fig. 2, computing system 202 is in communication with X-ray camera(s) 100, UI(s) 204, and remote computing system(s) 299 (e.g., electrically). In some examples, the communication may be direct communication (e.g., through a wired and/or wireless medium) or indirect communication, e.g., through one or more wired and/or wireless networks (e.g., a local area network and/or a wide area network). As shown, computing system 202 includes processing circuitry 210, memory circuitry 212, and communication circuitry 214 interconnected with one another via a common electrical bus.

In some examples, processing circuitry 210 may include one or more processors. In some examples, the communication circuitry 214 may include one or more wireless adapters, wireless cards, cable adapters, wire 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 conductor cable ports, and the like. In some examples, the communication circuitry 214 may be configured to facilitate communications via 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 Communications (NFC), ultra-high frequency radio waves (commonly referred to as bluetooth), IEEE 802.11x, zigbee, HART, LTE, Z-Wave, wireless HD, wiGig, etc.).

In the example of fig. 2, the memory circuitry 212 includes and/or stores a high resolution imaging process 300. In some examples, the high resolution imaging process 300 may be implemented via machine readable (and/or processor executable) instructions stored in the memory circuitry 212 and/or executed by the processing circuitry 210. In some examples, the high resolution imaging process 300 may be performed as part of a larger scanning and/or imaging process of the X-ray radiography system 200.

In some examples, the high resolution imaging process 300 may be performed in response to user selection of a high resolution (e.g., sub-pixel) imaging/scanning process that generates and/or stores images as the object 102 is continuously rotated (e.g., via the object locator 110). In some examples, the high resolution imaging process 300 may address synchronization issues that may occur during such high resolution, continuously rotating imaging processes. This may be distinguished from more traditional high resolution (e.g., sub-pixel) imaging processes that generate and/or store images in a stepwise manner after the object 102 has been rotated (e.g., while the object 102 is stationary), in which synchronization may not be an issue.

In particular, the high resolution imaging process 300 may provide a solution to mitigate the problem of the start of image capture/generation being synchronized with the start of rotation of the object 102. In some examples, it may be difficult to synchronize the start of image capture/generation with the start of rotation of the object 102, at least because the X-ray detector 108 may be capturing images at all times. Due to synchronization problems, the initial image captured/generated during the scan may be captured/generated at some non-zero degree of rotation (considered by the scan process).

Further, because the rotation of the object 102 is continuous, such a change in rotation angle may occur in a chain reaction across all images of a set of images captured/generated while the X-ray detector 108 is in a given position. Furthermore, the same synchronization problem and/or angular change may occur each time the X-ray detector 108 is shifted to a different position (since shifting to a different position then starting to rotate and capture an image again takes some time). Thus, the orientation angle of the object 102 may be different in the first/initial image (and corresponding subsequent images) of the different sets of images (captured/generated at different locations of the X-ray detector 108). When these images are combined into (what should be) a higher resolution image, such angular changes in the angular alignment image of the object 102 in what should be an object may lead to reduced image quality, loss of detail, reduced sharpness, blurring, and/or other negative consequences.

While much of the present disclosure discusses rotating the object 102 during the high resolution imaging process 300, in some examples, the X-ray emitter 106 and the X-ray detector 108 may alternatively be rotated about the object 102, as discussed above. However, even in such examples, the angle variation still presents a problem.

Fig. 5a to 5b show examples of such angle variations. These figures show a top view of the rectangular object 102 when capturing/generating a first/initial image for two different sets of images (e.g., taken at different locations of the X-ray detector 108). Fig. 5a illustrates an angular orientation of the object 102 (e.g., relative to the X-ray emitter 106 and/or the X-detector 108) when the X-ray detector 108 is in the first position. Fig. 5b shows the position of the object 102 when the X-ray detector 108 is in the second (e.g. slightly displaced) position. The dashed crosshairs indicate the center of the object 102 and angles of 0 degrees, 90 degrees, 180 degrees and 270 degrees. A dark black line extending from the center of the object 102 is used as a visual aid to make the rotation angle clearer.

In the example of fig. 5a, at the time of initial image capture, the object 102 has been rotated beyond the 0 degree dashed line. In the example of fig. 5b, the object has also been rotated beyond the 0 degree dashed line at the time of initial image capture. However, the rotation angle of the object 102 is different in fig. 5a and 5 b. Instead, the object 102 has been rotated through a greater angle of rotation in fig. 5a than in fig. 5 b. Thus, the corresponding image will show the object 102 at two different angles, and the high resolution image formed by the combination of the two images (and all subsequent images) may be negatively affected, as discussed above.

In the corresponding images of any two sets of images, the angular difference between the object 102 may potentially be as large as (but not greater than) the maximum angle to which the object 102 was rotated at/before the first/initial image in the set of images was captured. This potential initial angular change is directly related to the rotational speed of the object 102. The faster the object rotates, the greater the potential change in starting angle and vice versa.

Interestingly, the frame rate does not have any impact on the potential starting angle change. It appears that the potential onset angle change should be inversely proportional to the frame rate. After all, the faster the image is captured, the shorter the time the object 102 rotates beyond the starting angle before the image is captured. Thus, one might consider that a larger frame rate should be associated with a lower potential starting angle change. However, at high resolution (e.g., sub-pixels), continuously rotating scans, the rotation speed is also directly related to the frame rate. Since the potential starting angle change is directly related to the rotation speed (rotation speed is directly related to frame rate) and the potential starting angle change is also inversely proportional to the frame rate, the frame rate term counteracts and does not have any effect.

The parameters affecting the potential starting angle change are the number of image projections captured at a particular location of the X-ray detector 108 and the number of image frames averaged together to produce a single image projection.

As used herein, "image projection" refers to a single image of the object 102 (at a given orientation of the object 102) that is projected onto the X-ray detector 108 (as the radiation 104 passes from the X-ray emitter 106 through the object 102 and is projected onto/onto the X-ray detector 108) and then stored in the memory circuitry 212. However, to increase the signal-to-noise ratio in a single image projection, sometimes several image frames (e.g., captured as the object 102 rotates to its image projection orientation) are averaged together to produce a single image projection. Thus, during a continuous rotation high resolution (e.g., sub-pixel) scan, the total number of images captured during a single (partial or complete) rotation of the object 102 (at one location of the X-ray detector 108) is equal to the number of image projections to be captured multiplied by the number of images averaged together to produce a single image projection. These parameters will be referred to hereinafter as image projection and frame averaging parameters.

Using the image projections and the frame average parameter values, the rotational speed (and potentially the starting angular change) of the object 102 can be calculated. Specifically, the rotation speed may be calculated as the rotation degree (e.g., 270, 360, etc.) divided by the total number of images to be captured (i.e., the number of image projections x the number of frames averaged) multiplied by the frame rate (i.e., rotation speed = degrees per image frame x image frames per second = degrees per second). The potential starting angular change may then be calculated as the rotational speed multiplied by the time one image frame was captured (i.e., rotational speed x (1/frame rate)). However, since the frame rate is also a part of the rotational speed, the frame rate is not in the potential starting angle change equation. By reduction, the potential starting angle change is equal to the rotation degree divided by the total number of images to be captured (i.e., the potential starting angle change = rotation degree/(number of image projections x number of frames averaged)).

Furthermore, it has been found that the negative effects of potential starting angle variations can be mitigated if the potential starting angle variations remain below a certain maximum starting angle variation. While it is most safe to keep the potential starting angle change to a minimum, the potential starting angle change is directly related to the rotational speed; thus, keeping the potential starting angle change as low as possible also means keeping the rotational speed as slow as possible. In addition, one of the main advantages of high-resolution continuous rotation scanning compared to high-resolution step-and-rotate scanning is that the scanning speed is increased. Accordingly, the high resolution imaging process 300 disclosed herein and discussed below controls (and/or strongly suggests) the values of the parameters for image projection and frame averaging to ensure that adequate speed and image quality are obtained.

Some of the following disclosure discusses certain actions performed by the high resolution imaging process 300. In some examples, this is used as shorthand for one or more components of the X-ray radiography system 200 (e.g., processing circuitry 210, communication circuitry 214, UI 204, radiography camera 100, etc.) to perform actions(s) as part of the high resolution imaging process 300.

Fig. 3 is a flowchart illustrating an example operation of a high resolution imaging process 300. In the example of fig. 3, the high resolution imaging process 300 begins at block 302. At block 302, the high resolution imaging process 300 receives an input (e.g., input device(s) 206 from the UI 204) representing a selection of a continuous rotation high resolution (e.g., sub-pixel) scan. Although shown as part of the high resolution imaging process 300 in the example of fig. 3 for purposes of completeness, in some examples, block 302 may be part of a more general scanning process that performs the high resolution imaging process 300 in response to selection of block 302. In the example of fig. 3, the high resolution imaging process 300 proceeds to block 304 after block 302.

At block 304, the high resolution imaging process 300 identifies one or more parameter values that will affect the potential starting angle change and/or the maximum starting angle change. While other parameter values (e.g., ramp time to rotational speed, number of different positions of X-ray detector 108, distance (e.g., sub-pixels) between different positions of X-ray detector 108, etc.) may also be identified at block 304 (and/or other blocks), the present disclosure focuses on parameter values that will affect potential starting angle changes and/or maximum starting angle changes. In some examples, parameter values that will affect the potential starting angle change and/or the maximum starting angle change may include values of image projection, average frame number, degree of rotation (e.g., between 1 and 360, including 1 and 360), geometric magnification, and level of detail (and/or image quality) required for a particular scanning application. In some examples, high resolution imaging process 300 may prompt a user for one or more parameter values, e.g., via one or more fields of a Graphical User Interface (GUI) 604 (see, e.g., fig. 6).

In some examples, the high resolution imaging process 300 may automatically identify one or more parameter values. For example, the high resolution imaging process 300 may automatically identify a geometric magnification of the X-ray radiation camera 100 (e.g., based on analysis of test images captured via the X-ray radiation camera 100, analysis of radiation detected by the X-ray detector 108, one or more position/distance/proximity sensors of an industrial radiation camera, etc.).

In some examples, high resolution imaging process 300 may identify one or more parameter values based on one or more other parameter values. For example, the high resolution imaging process 300 may identify an ideal (and/or default) geometric magnification value based on a desired level of detail (and/or image quality), such as by a data structure (e.g., a look-up table, database) and/or dynamic algorithm calculations stored in the memory circuitry 212. In the example of fig. 3, the high resolution imaging process 300 proceeds to block 306 after block 308.

At block 308, the high resolution imaging process 300 determines whether sufficient parameter values are identified at block 304 to identify a maximum starting angular change. In some examples, the high resolution imaging process 300 may require at least identifying a level of detail (and/or image quality) and a geometric magnification in order to determine a maximum starting angle change. However, as discussed above, geometric magnification may be determined based on the identified level of detail (and/or image quality). Thus, in some examples, if at least a level of detail (and/or image quality) value is identified at block 304, the high resolution imaging process 300 may determine that sufficient parameter values are identified.

In the example of fig. 3, if sufficient parameter values are not identified at block 304, the high resolution imaging process 300 returns to block 304. However, if sufficient parameter values are identified at block 304 to enable a maximum starting angle change to be determined, the high resolution imaging process 300 proceeds to block 308.

At block 308, the high resolution imaging process 300 identifies a maximum starting angle change based on the necessary level of detail (and/or image quality) and geometric magnification. As used herein, a maximum starting angle change refers to a maximum threshold potential starting angle change that will still allow the captured image to have the necessary level of detail (and/or image quality).

In some examples, the memory circuitry 212 may store a look-up table, database table, and/or other data structure that maps values of geometric magnification and/or detail levels (and/or image quality) to values of maximum starting angle change (e.g., experimentally determining various levels of detail and/or geometric magnification). In such an example, at block 308, the high resolution imaging process 300 may determine a value of the maximum starting angle change based on the data structure map and the identified values of geometric magnification and detail level (and/or image quality).

In some examples, the maximum starting angle change may be determined via one or more specialized algorithms. In such an example, at block 308, the high resolution imaging process 300 may dynamically determine and/or calculate a value of the maximum starting angle change based on one or more specialized algorithms and the identified values of geometric magnification and/or detail level (and/or image quality). In the example of fig. 3, the high resolution imaging process 300 proceeds to block 310 after block 308.

At block 310, the high resolution imaging process 300 determines whether sufficient parameter values are identified at block 304 to identify potential starting angle changes. In some examples, the high resolution imaging process 300 may require at least identifying parameter values for image projection, average frame number, and rotation number parameters in order to identify potential starting angle changes. In the example of fig. 3, if there are not enough parameter values to identify a potential starting angle change, the high resolution imaging process 300 proceeds to block 312.

At block 312, the high resolution imaging process 300 may control or recommend parameter values for parameters (e.g., image projection, average frame number, and degree of rotation) required to identify potential starting angle changes. In some examples, the operation at block 312 may depend on the number of parameter values that have been set (or unset) (and/or which parameter values have been set (or unset)). If only one desired parameter remains unset, in some examples, the high resolution imaging process 300 may control or recommend a parameter having a parameter value that will result in the potential starting angle change being equal to, or below and within the threshold of the maximum starting angle change.

In some examples, the high resolution imaging process 300 may control or recommend parameters having parameter values that will result in as large a potential starting angle change as possible without exceeding a maximum starting angle change. In some examples, the high resolution imaging process 300 may prohibit or not recommend parameter values (e.g., in order to maintain sufficient rotation/scan speed) that would result in a potential starting angle change that is greater than a threshold amount below a maximum starting angle change. In some examples, the high resolution imaging process 300 may determine parameter values based on the identified other parameter values and potential starting angle change equations (discussed above) or data structures (e.g., look-up tables, databases) stored in the memory circuitry 212.

In some examples, if parameter values are not set for the image projection parameters and/or the frame average parameters, the high resolution imaging process 300 may first identify an optimal number of image projections. For example, nyquist theory, the level of detail (and/or image quality) identified, geometric magnification, the number and/or size of pixels 404 on X-ray detector 108, and/or other relevant information may be used to identify the optimal number of image projections. The number of image projections may then be controlled or recommended to be equal to the optimal number of image projections (and/or within its threshold). The parameter values of the frame average parameters may then be controlled or recommended, as discussed above (where only one desired parameter remains unset).

In some examples, if one of the desired parameters that remain unset (or the only desired parameter that is unset) is a rotation number parameter, the high resolution imaging process 300 may default or recommend a parameter value of 360 ° (or some other default parameter value stored in the memory circuitry 212).

In the example of fig. 3, the high resolution imaging process 300 returns to block 310 after block 312. As shown, if sufficient parameter values have been identified to identify a potential starting angular change, the high resolution imaging process 300 proceeds to block 314 after block 312.

At block 314, the high resolution imaging process 300 determines potential starting angle changes (discussed above) based on the identified/desired parameter values and the potential starting angle change equation. In some examples, the high resolution imaging process 300 may use data structures (e.g., look-up tables, databases) stored in the memory circuitry 212 (e.g., data structures implementing potential starting angle change equations) instead of the potential starting angle change equations themselves. Once the potential starting angle change is determined, the high resolution imaging process 300 checks whether the potential starting angle change is equal to or below the maximum starting angle change and within a threshold range of the maximum starting angle change.

The threshold range requirement (in combination with the maximum value) effectively sets the minimum start angle variation and the maximum start angle variation (to ensure adequate rotation/scan speed). In some examples, the threshold range may be omitted. In the example of fig. 3, if the potential starting angle change is not equal to the maximum starting angle change, or is not below the maximum starting angle change and is not within the threshold range of the maximum starting angle change, the high resolution imaging process 300 proceeds to block 316 after block 314. In some examples, the high resolution imaging process 300 may also output an alert (similar to the recommendation discussed below) informing the user that the potential starting angle change is not equal to the maximum starting angle change, or is not below the maximum starting angle change and is not within a threshold range of the maximum starting angle change.

At block 316, the high resolution imaging process 300 controls or recommends one or more parameter values for geometric magnification, image projection, and/or frame averaging parameters to ensure that the potential starting angle change is equal to or below the maximum starting angle change and within a threshold range of the maximum starting angle change. In some examples, the high resolution imaging process 300 may control or recommend only one of the parameter values (e.g., the most recently set parameter value, the parameter value in memory or identified by the user as the most malleable, etc.). In some examples, the high resolution imaging process 300 may only control or recommend different parameter values for the geometric magnification parameter if the maximum starting angle change is below a threshold (e.g., a threshold stored in the memory circuitry 212 and/or set via the UI 204) and/or the identified geometric magnification is greater than a threshold amount of default/ideal geometric magnification (discussed above) at a particular level of detail (and/or image quality).

In some examples, the high resolution imaging process 300 may make recommendations by outputting a message via the output device(s) 208 of the UI 204. In some examples, the high resolution imaging process 300 may output recommendations in the form of audio, text, image(s), video(s), and/or other suitable formats. In some examples, the recommendation may inform the user of the parameter, the current parameter value, and/or the problem (e.g., the currently identified parameter value is too high/low and/or results in a rotational speed, a scan time, a maximum starting angle change, and/or a potential starting angle change is too high/low). In some examples, the recommendation may inform the user of a recommended value and/or a direction of modification (e.g., a higher/lower value) that will solve the problem. In some examples, the recommendation may inform the user of one or more values to avoid.

In some examples, the high resolution imaging process 300 may directly control parameter values, for example, by setting the parameter values. In some examples, the high resolution imaging process 300 may indirectly control parameter values, for example, by disabling the input of undesirable parameter values. In some examples, the high resolution imaging process 300 may output a notification to inform the user of the time, manner, and/or cause of controlling the parameter values, similar to that discussed above with respect to recommendations.

In the example of fig. 3, the high resolution imaging process 300 returns to block 308 after controlling or recommending parameter value(s) at block 316. As shown, if the potential starting angle change is equal to the maximum starting angle change, or is below the maximum starting angle change and within a threshold range of the maximum starting angle change, the high resolution imaging process 300 proceeds to block 318 after block 314. In some examples, if the user chooses to start the scanning/imaging process (e.g., via UI 204), the high resolution imaging process 300 proceeds to block 318 only after block 314.

At block 318, the high resolution imaging process 300 controls the X-ray emitter 106, the X-ray detector 108, the detector positioner 150, the object positioner 110, and/or the rotatable platform 160 based on the above-described parameter values to acquire and/or generate a number of different sets (e.g., 2 sets, 3 sets, 4 sets, 5 sets, 6 sets, 7 sets, 8 sets, etc.) of radiographic images. In some examples, each set of radiographic images may be captured and/or generated while the X-ray detector 108 is in a slightly different (e.g., sub-pixel shifted) position and/or while the object 102 is rotating (e.g., via the object locator 110). In some examples, the size of each set of radiographic images (and/or the number of images) may be equal to the number of image projections times the number of frames averaged. In some examples, one or more radiographic images may be output to a user via the output device(s) 208 of the UI 204 and/or stored in the memory circuitry 212.

In the example of fig. 3, the high resolution imaging process 300 proceeds to block 320 after block 318. At block 320, the high resolution imaging process 300 combines corresponding image projections (at the same orientation angle of the object 102) of different sets of radiographic images together to produce a set of higher resolution radiographic images, as described above. In some examples, each higher resolution radiographic image of the set of higher resolution radiographic images will have a higher resolution than each corresponding (and/or any other) radiographic image(s) of the set of radiographic images. In some examples, the size of the set of higher resolution radiographic images is equal to the identified parameter values corresponding to the image projection parameters. In some examples, one or more higher resolution images may be output to a user via output device(s) 208 of UI 204 and/or stored in memory circuitry 212.

In the example of fig. 3, the high resolution imaging process 300 proceeds to block 322 after block 320. At block 322, the high resolution imaging process 300 combines the higher resolution radiographic images into one or more 3D volumes and/or 3D images. In some examples, the 3D volume may be an image and/or model of the object 102. In some examples, the high resolution imaging process 300 may additionally (e.g., based on some user selected or stored parameters) capture one or more specific 2D image slices of the 3D volume. In some examples, the 2D image slice(s) may be different from any 2D image previously generated and/or acquired. In some examples, one or more of the 3D images and/or 2D images may be output to a user via the output device(s) 208 of the UI 204 and/or stored in the memory circuitry 212.

Fig. 6 is an example of a display screen 602 of the output device(s) 208 of the UI 204 of the GUI 204, which may, for example, allow a user to set one or more parameters during the high resolution imaging process 300. As shown, GUI 204 depicts several different parameters on the left side and corresponding parameter values for each parameter in the right row. Specifically, GUI 204 shows that for the scan type parameter, a high resolution sub-pixel (i.e., subPiX) parameter value has been set. In addition, for rotation type parameters, continuous (rather than stepwise) rotation parameter values have been selected. The scan type parameter values and the rotation type parameter values together may indicate a selection of the high resolution imaging process 300. Although shown as two separate parameters and/or parameter values in the example of fig. 3, in some examples there may be only one (or more than two) parameter and/or parameter values to indicate the selection of the high resolution imaging process 300.

In the example of fig. 6, high parameter values have been set for detail need parameters, and 4-fold parameter values have been set for geometric magnification parameters. From this information, a parameter value of 40 ° has been identified (e.g., by the high resolution imaging process 300) for the maximum starting angle change parameter. However, GUI 204 also shows a parameter value of 90 ° for the potential starting angle change parameter that is higher than the parameter value of 40 ° for the maximum starting angle change parameter.

Because the potential starting angle change parameter value exceeds the maximum starting angle change parameter value, the high resolution imaging process 300 has output an alert 606. As shown, GUI 604 has also grayed out start scan button 610, which indicates that button 610 cannot currently be activated to initiate a scan. In some examples, button 610 may remain inactive until the potential starting angle change parameter value is equal to the maximum starting angle change parameter value, or is below the maximum starting angle change parameter value and within a threshold of the maximum starting angle change parameter value.

In the example of fig. 6, the high resolution imaging process 300 also outputs several recommendations 608 on how to solve the problem. In particular, recommendation 608 is directed to modification of parameter values that may reduce the potential starting angle change parameter value or increase the maximum starting angle change parameter value, thereby solving the problem.

For example, recommendation 608a proposes to reduce the geometric magnification to 2 times. In some examples, this reduced geometric magnification may still meet the high parameter values of the detail need parameters, while also allowing a sufficiently high maximum starting angle change (and/or faster scan) to address this issue.

As another example, recommendation 608b proposes to increase the image projection parameter value from 100 to 225. As another example, recommendation 608c proposes to increase the frame average parameter value from 4 to 9. In some examples, such an increase in image projection parameter values or frame average parameter values will result in the potential starting angle change parameter value being equal to the maximum starting angle change parameter value, thereby solving the problem. Although short text interpretations are depicted for alert 606 and recommendation 608, in some examples, these interpretations may be more extensive and/or detailed, and/or include links to more extensive and/or detailed interpretations.

By controlling or recommending certain parameter values of the high resolution imaging process 300, problems due to lack of synchronization may be alleviated. After these problems are alleviated, the user may be able to perform high resolution scanning of the object 102 at an increased speed (e.g., due to continuous rotation) without loss of detail and/or blurring typically caused by synchronization problems.

The present methods and/or systems may be implemented in hardware, software, or a combination of hardware and software. The method and/or system may be implemented in a centralized fashion in at least one computing system, or in a distributed fashion where different elements are spread across several interconnected computing systems and/or remote computing systems. Any kind of computing system or other apparatus adapted for carrying out the methods described herein is suited. A typical combination of hardware and software could be a general purpose computing system with a program or other code that, when being loaded and executed, controls the computing system such that it carries out the methods described herein. Another exemplary embodiment may include an application specific integrated circuit or chip. Some implementations may include a non-transitory machine-readable (e.g., computer-readable medium (e.g., flash drive, optical disk, magnetic storage disk, etc.) having one or more instructions (lines of code) stored thereon that are executable by a machine to cause the machine to perform a process as described herein.

While the present method and/or system has been described with reference to certain embodiments, it will be understood 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 disclosure without departing from the scope thereof. Therefore, it is intended that the present method and/or system not be limited to the particular embodiments disclosed, but that the present method and/or system will include all embodiments falling within the scope of the appended claims.

As used herein, "and/or" refers to any one or more of the items in the manifest that are connected by "and/or". By way of example, "x and/or y" refers to any element in the triplet set { (x), (y), (x, y) }. In other words, "x and/or y" refers to "one or both of x and y". As another example, "x, y, and/or z" refers to any element in a seven-element set { (x), (y), (z), (x, y), (x, z), (y, z), (x, y, z) }. In other words, "x, y, and/or z" refers to "one or more of x, y, and z".

As used herein, the terms "such as (e.g.") "and" for example "lead to a list of one or more non-limiting examples, instances, or illustrations.

As used herein, the terms "coupled," "coupled to," and "coupled with … …" refer to a structural and/or electrical connection, whether attached, affixed, connected, joined, fastened, connected, and/or otherwise secured, respectively. As used herein, the term "attached" refers to attaching, coupling, connecting, engaging, fastening, tying, and/or otherwise securing. As used herein, the term "connected" refers to attaching, coupling, engaging, fastening, tying, and/or otherwise securing.

As used herein, the terms "circuitry" and "circuitry" refer to physical electronic components (i.e., hardware) as well as any software and/or firmware ("code") that may configure, be executed by, and/or otherwise be associated with 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 a second "circuit" when executing a second one or more lines of code. As used herein, circuitry is "operable" and/or "configured" to perform a function when the circuitry includes the hardware and/or code necessary to perform the function (if necessary), regardless of whether execution of the function is disabled or enabled (e.g., by user-configurable settings, factory adjustments, etc.).

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

As used herein, the term "processor" refers to processing means, devices, programs, circuits, components, systems, and subsystems, whether implemented in hardware, software in tangible form, or both, and whether or not they are programmable. As used herein, the term "processor" includes, but is not limited to, one or more computing devices, hardwired circuitry, signal modifying 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 chip, systems including discrete components and/or circuits, state machines, virtual machines, data processors, processing facilities, and any combination of the above. The processor may be, for example, any type of general purpose microprocessor or 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, or the like. The processor may be coupled to and/or integrated with the memory device.

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 means 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 disc read-only memory (CDROM), electro-optic memory, magneto-optic memory, programmable read-only memory (PROM), erasable programmable read-only memory (EPROM), electrically erasable programmable read-only memory (EEPROM), computer-readable media, and the like. 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 card, compact flash card, memory card, secure digital memory 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.

Claims (20)

1. A non-transitory computer-readable medium comprising machine-readable instructions that, when executed by a processor, cause the processor to:

Receiving, via an input device of a user interface, a selection of a continuous high resolution image acquisition process that acquires radiographic images of an object at a plurality of different detector positions of a radiation detector while the object is rotating;

In response to the selection, a maximum starting angle change is identified,

The maximum starting angle change comprises a maximum allowable difference between an orientation of the object when a first initial image is acquired and an orientation of the object when a second initial image is acquired during the high resolution image acquisition process,

The first initial image is acquired during the high resolution image acquisition process when the radiation detector is in a first detector position, and the second initial image is acquired during the high resolution image acquisition process when the radiation detector is in a second detector position;

setting or recommending a first parameter value of a first parameter as a first value or a second parameter value of a second parameter as a second value based on the maximum starting angle change; and

The high resolution image acquisition process is performed based on the first parameter value and the second parameter value to generate an image of the object.

2. The non-transitory computer readable medium of claim 1, wherein the first parameter comprises a number of image projections and the second parameter comprises a number of image frames averaged together to produce one image projection.

3. The non-transitory computer-readable medium of claim 2, further comprising: machine readable instructions for the high resolution image acquisition process, which when executed by the processing circuitry cause the processing circuitry to:

generating a first set of radiographic images based on radiation detected by the radiation detector while the radiation detector is in the first detector position, when the rotatable clamp rotates the object through a first revolution;

generating a second set of radiographic images based on radiation detected by the radiation detector when the rotatable clamp rotates the object through a second revolution while the radiation detector is in the second detector position; and

Generating a third set of higher resolution radiographic images based on the radiographic images of the first set of radiographic images and the corresponding radiographic images of the second set of radiographic images, the higher resolution radiographic images having a higher resolution than the radiographic images of the first set of radiographic images and the corresponding radiographic images of the second set of radiographic images,

Wherein the size of the first, second or third set of radiographic images depends on a first parameter value of the first parameter or a second parameter value of the second parameter.

4. The non-transitory computer-readable medium of claim 3, further comprising: machine readable instructions for the high resolution image acquisition process, which when executed by the processing circuitry cause the processing circuitry to: combining the third set of higher resolution radiographic images into an image of the object, the image of the object comprising data representing a two-dimensional (2D) image, data representing a three-dimensional (3D) volume, or data representing a 2D slice of the 3D volume.

5. A non-transitory computer readable medium as set forth in claim 3, wherein the first set of radiographic images and the second set of radiographic images are equal in size to the first parameter value multiplied by the second parameter value, and the third set of radiographic images are equal in size to the first parameter value.

6. The non-transitory computer-readable medium of claim 3, wherein setting or recommending a first parameter value of the first parameter as the first value or a second parameter value of the second parameter as the second value based on the maximum starting angle change comprises:

determining one or more first values of the first parameter or second values of the second parameter, which values are capable of causing a start angle change exceeding the maximum start angle change,

The initial angular change includes a difference between an orientation of the object when the first initial image of the first set of radiographic images is acquired by the radiation detector during a first revolution of the object and an orientation of the object when the second initial image of the second set of radiographic images is acquired by the radiation detector during a second revolution of the object, and

The input or selection of one or more first values of the first parameter or of a second value of the second parameter is prohibited or not recommended.

7. The non-transitory computer-readable medium of claim 6, wherein setting or recommending a first parameter value of the first parameter as the first value or a second value of the second parameter as the second value based on the maximum starting angle change further comprises automatically setting the first parameter value or the second parameter value such that the starting angle change will not exceed the maximum starting angle change.

8. The non-transitory computer readable medium of claim 3, wherein the first detector position is staggered from the second detector position by less than a pixel size of the radiation detector.

9. 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: and displaying the image on a display screen.

10. The non-transitory computer readable medium of claim 1, wherein the maximum starting angular change is identified based on a geometric magnification of the industrial radiographic imaging system or an image quality required for a particular application of the industrial radiographic imaging system, the geometric magnification comprising a first distance from the radiation emitter to the radiation detector divided by a second distance from the radiation emitter to the object.

11. An industrial radiographic imaging system, comprising:

A radiation emitter configured to emit radiation;

A radiation detector configured to detect radiation emitted by the radiation emitter;

A rotatable clamp configured to hold and rotate an object, the rotatable clamp positioned between the radiation emitter and radiation detector;

A detector positioner configured to move the radiation detector to a plurality of different detector positions; and

An image acquisition system configured to generate an image of the object based on radiation detected by the radiation detector after passing through the object, the image acquisition system comprising:

A user interface, the user interface comprising an input device,

Processing circuitry, and

Memory circuitry comprising machine-readable instructions that, when executed by the processing circuitry, cause the processing circuitry to:

receiving, via the input device, a selection of a continuous high resolution image acquisition process that acquires images at the plurality of different detector positions while the object is rotating,

In response to the selection, a maximum starting angle change is identified,

The maximum starting angle change comprises a maximum allowable difference between an orientation of the object when a first initial image is acquired and an orientation of the object when a second initial image is acquired during the high resolution image acquisition process,

The first initial image is acquired during the high resolution image acquisition process when the radiation detector is in a first detector position, and the second initial image is acquired during the high resolution image acquisition process when the radiation detector is in a second detector position,

Setting or recommending a first parameter value of a first parameter to a first value or a second parameter value of a second parameter to a second value based on the maximum starting angle change, and

The high resolution image acquisition process is performed based on the first value and the second value to generate an image of the object.

12. The system of claim 11, wherein the first parameter comprises a number of image projections and the second parameter comprises a number of image frames averaged together to produce one image projection.

13. The system of claim 12, wherein the memory circuitry further comprises machine-readable instructions for the high-resolution image acquisition process, which when executed by the processing circuitry, cause the processing circuitry to:

generating a first set of radiographic images based on radiation detected by the radiation detector when the rotatable clamp rotates the object through a first revolution while the radiation detector is in the first detector position,

Generating a second set of radiographic images based on radiation detected by the radiation detector while the radiation detector is in the second detector position, when the rotatable clamp rotates the object through a second revolution, and

Generating a third set of higher resolution radiographic images based on the radiographic images of the first set of radiographic images and the corresponding radiographic images of the second set of radiographic images, the higher resolution radiographic images having a higher resolution than the radiographic images of the first set of radiographic images and the corresponding radiographic images of the second set of radiographic images,

Wherein the size of the first, second or third set of radiographic images is based on a first value of the first parameter or a second value of the second parameter.

14. The system of claim 13, wherein the memory circuitry comprises machine-readable instructions for the high-resolution image acquisition process, which when executed by the processing circuitry further cause the processing circuitry to: combining the third set of higher resolution radiographic images into an image of the object, the image of the object comprising data representing a two-dimensional (2D) image, data representing a three-dimensional (3D) volume, or data representing a 2D slice of the 3D volume.

15. The system of claim 13, wherein the first and second sets of radiographic images are equal in size to the first parameter value multiplied by the second parameter value, and the third set of radiographic images are equal in size to the first parameter value.

16. The system of claim 13, wherein setting or recommending a first parameter value of the first parameter as the first value or a second parameter value of the second parameter as the second value based on the maximum starting angle change comprises:

determining one or more first values of the first parameter or second values of the second parameter, which values are capable of causing a start angle change exceeding the maximum start angle change,

The initial angular change includes a difference between an orientation of the object when the first initial image of the first set of radiographic images is acquired by the radiation detector during a first revolution of the object and an orientation of the object when the second initial image of the second set of radiographic images is acquired by the radiation detector during a second revolution of the object, and

The input or selection of one or more first values of the first parameter or of a second value of the second parameter is prohibited or not recommended.

17. The system of claim 16, wherein setting or recommending a first parameter value of the first parameter as the first value or a second parameter value of the second parameter as the second value based on the maximum starting angle change further comprises automatically setting the first parameter value or the second parameter value such that the starting angle change will not exceed the maximum starting angle change.

18. The system of claim 13, wherein the first detector position is staggered from the second detector position by less than a pixel size of the radiation detector.

19. The system of claim 11, wherein the memory circuitry further comprises machine-readable instructions that, when executed by the processor: an image of the object is displayed on a display screen of the user interface.

20. The system of claim 11, wherein the maximum starting angular change is identified based on a geometric magnification of the industrial radiographic imaging system or a required image quality for a particular application of the industrial radiographic imaging system, the geometric magnification comprising a first distance from the radiation emitter to the radiation detector divided by a second distance from the radiation emitter to the object.