CN113940692B - Multi-view-field X-ray imaging splicing method - Google Patents
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- CN113940692B CN113940692B CN202111217884.2A CN202111217884A CN113940692B CN 113940692 B CN113940692 B CN 113940692B CN 202111217884 A CN202111217884 A CN 202111217884A CN 113940692 B CN113940692 B CN 113940692B
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- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
- A61B6/00—Apparatus for radiation diagnosis, e.g. combined with radiation therapy equipment
- A61B6/52—Devices using data or image processing specially adapted for radiation diagnosis
- A61B6/5211—Devices using data or image processing specially adapted for radiation diagnosis involving processing of medical diagnostic data
- A61B6/5229—Devices using data or image processing specially adapted for radiation diagnosis involving processing of medical diagnostic data combining image data of a patient, e.g. combining a functional image with an anatomical image
- A61B6/5235—Devices using data or image processing specially adapted for radiation diagnosis involving processing of medical diagnostic data combining image data of a patient, e.g. combining a functional image with an anatomical image combining images from the same or different ionising radiation imaging techniques, e.g. PET and CT
- A61B6/5241—Devices using data or image processing specially adapted for radiation diagnosis involving processing of medical diagnostic data combining image data of a patient, e.g. combining a functional image with an anatomical image combining images from the same or different ionising radiation imaging techniques, e.g. PET and CT combining overlapping images of the same imaging modality, e.g. by stitching
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- G—PHYSICS
- G06—COMPUTING; CALCULATING OR COUNTING
- G06T—IMAGE DATA PROCESSING OR GENERATION, IN GENERAL
- G06T3/00—Geometric image transformation in the plane of the image
- G06T3/40—Scaling the whole image or part thereof
- G06T3/4038—Scaling the whole image or part thereof for image mosaicing, i.e. plane images composed of plane sub-images
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- G06—COMPUTING; CALCULATING OR COUNTING
- G06T—IMAGE DATA PROCESSING OR GENERATION, IN GENERAL
- G06T2200/00—Indexing scheme for image data processing or generation, in general
- G06T2200/32—Indexing scheme for image data processing or generation, in general involving image mosaicing
Abstract
The invention relates to a multi-view-field X-ray imaging splicing method, which performs multi-view-field X-ray scanning on an imaging object during focusing. The depth information of the object is obtained at the overlapping part of the multi-view projection, so that the defect that the single-view projection does not have the depth information of the object is overcome. The projection data are weighted and fused, wherein the projection values of pixels in each view field are given weight through calculation, and the approximate parallel light projection data of the overlapped position points are obtained through weighting. The pixel normalization is to average the parts of all the overlapping points obtained in the previous step belonging to the same pixel, assign the parts to the corresponding pixels and output the parts to obtain a complete image. The invention can obviously improve the splicing quality of the scanned images, can splice the images while scanning the X-rays, can select the number of used fields according to the requirements of splicing accuracy of imaging objects, has high detection speed, small radiation to patients and good imaging effect. Can meet the requirements of low dosage and high precision of X-ray imaging.
Description
Technical Field
The invention belongs to the X-ray imaging technology, and relates to a multi-view-field X-ray imaging splicing method, in particular to a multi-view-field X-ray imaging splicing method which is characterized in that under fan-beam X-ray scanning, a plurality of scanning images are deformed, so that an imaging object with a large difference between an output image and an actual object is subjected to scanning multi-view-field image acquisition, overlapping positions are positioned, projection data are subjected to weighted fusion and pixel normalization, so that depth information of the object can be obtained, projection data of each overlapping depth point are approximately perpendicular to the projection data obtained by the object, and the splicing speed is improved while scanning is carried out, so that the radiation dose of a patient is reduced, the deformation of the X-ray scanning images is improved, and the imaging quality is improved, and the method belongs to the field of X-ray radiation detection and imaging.
Background
With the development of X-ray detectors and digital image processing techniques, X-ray imaging techniques have become an integral part of the medical field. In current medical diagnostics, it is often necessary to acquire a complete image of a portion or bone of a patient, assisting the physician in selecting an optimal treatment regimen for the patient.
X-ray imaging is often limited by the size of the detector, except for the limitations on the performance of the hardware itself, such as the detector. Because the size of the detector is limited, the whole image of the large affected part or bones such as the spine of the patient cannot be directly obtained by scanning the bones with the same length, and the whole image of the required part can be obtained only by splicing a plurality of images after scanning the region of interest for a plurality of times. Therefore, it is important to stitch the images of the multiple scans into an overall image. In addition, in the image stitching process, the image obtained by fan-beam X-ray irradiation has the deformation problems of enlargement, reduction, partial overlapping and the like compared with the image obtained by parallel light. The accuracy of image stitching directly influences the judgment of a doctor on the patient's condition.
Image stitching methods of X-rays have been explored, but due to the principle of digital radiography (Direct Radiography, abbreviated as DR) imaging, depth information of a detected part is lacking in single-view X-ray projection images. In order to obtain structural information of objects at different depth layers, an electronic computer tomography (Computed Tomography, CT) technique is typically used. While CT imaging techniques can achieve high accuracy, they have a greater radiation dose and a longer time. But it is rarely reported that the depth information of an object is obtained by DR imaging of multiple fields of view to stitch multiple scanned images. The quality of image stitching directly affects the diagnosis of doctors, is an important factor limiting the application of X-ray imaging, and the improvement and optimization of the X-ray imaging stitching method is a great trend of developing X-ray imaging technology.
Disclosure of Invention
Technical problem to be solved
In order to avoid the defects of the prior art, the invention provides a multi-view X-ray imaging splicing method, the obtained method has good X-ray scanning image splicing capability and reduces radiation dose, and meanwhile, compared with an X-ray spliced image without the method, the method has higher quality and faster splicing speed, and solves the technical problems in the prior art.
Technical proposal
A multi-view-field X-ray imaging splicing method is characterized by comprising the following steps:
1. the detector is arranged in parallel with the object placing table and the X-ray machine in the vertical direction, and a stationary object to be detected is placed on the object placing table; the distance from the detector to the object placing table is 4 times of the distance from the X-ray machine to the object placing table; the detector and the X-ray machine synchronously move at a uniform speed through synchronous belt transmission;
2. the step of each movement of the detector and the optics is determined by the following formula:
3. the detector and the X-ray machine move in an arch shape along the axis of the object in parallel to the object placing table until the scanning of the interested part of the object to be detected is completed;
1. establishing a rectangular coordinate system by taking the center of a first pixel of a first scanning detector as an origin, taking the horizontal direction of the pixel as an X axis and taking the vertical direction as a Y axis;
2. determining a straight line by scanning each pixel center of the detector and two points of the X-ray machine each time, wherein the position of each pixel center of each detector and the optical machine connecting line can be expressed by the following formula in a rectangular coordinate system:
where h represents the perpendicular distance of the light engine to the detector, x i X represents the abscissa, x, of the position of the ith scan ray apparatus ij An abscissa indicating the center position of the jth pixel of the ith scan, and d indicating the step of the optical machine movement;
3. acquiring all straight line intersection points in the area between the detector and the optical machine, and determining all intersection point coordinates to acquire depth information of an object overlapping area;
D＝|x ij -x mn |
wherein represents the projection value of the intersection point position, P ij ，P mn Representing the projection value of the jth pixel of the ith scan and the projection value of the nth pixel of the mth scan, x respectively mn An abscissa indicating a center position of an nth pixel of the mth scan;
step 4, pixel normalization:
1. determining the abscissa positions of all the intersection points, wherein the intersection points of the abscissa in the intervals of the pixel positions are defined as belonging to the same pixel;
2. the final projection value of each pixel is determined, and the projection value calculation formula is as follows:
wherein n is j Representing the number of intersection points belonging to the j-th pixel in total, P t Representing the projection value of the t-th intersection belonging to the j-th pixel. 3) And outputting by using the projection value to obtain a complete spliced image.
The maximum energy of the X-ray machine is above 80kV, and the type of emitted X-rays is a fan-shaped narrow beam.
The detector is a photon technology linear array detector, and the energy resolution of the detector is below 20%.
The detector is calibrated by energy and threshold before use.
The detector material is telluriumZinc cadmium, requiring a material resistivity of 10 9 The working leakage current is less than 10nA, no macroscopic defect exists in the crystal, no grain boundary exists, and tellurium inclusions are uniformly distributed.
The electrode material of the detector is gold or indium or silver or aluminum.
Advantageous effects
The invention provides a multi-view-field X-ray imaging splicing method, which comprises the steps of collecting multi-view-field X-ray scanning image projections, positioning overlapped positions, weighting and fusing projection data and normalizing pixels, and the aim of splicing a plurality of X-ray scanning images into a complete image is fulfilled by combining the four parts. The X-ray scanning system comprises a detector, a X-ray machine, a multi-field X-ray scanning image projection acquisition device, a multi-field X-ray scanning image projection image acquisition device. By setting different X-ray machine moving steps, the number of the fields used in the splicing can be determined, the smaller the steps are, the more fields are spliced, the more obvious the influence on 'triangular light' imaging is counteracted, and the better the splicing result of the obtained images is. Wherein the overlapping position is positioned to overcome the disadvantage of monoscopic projection without depth information of the object by obtaining depth information of the object at the overlapping portion of the multi-field projection. The projection data are weighted and fused, wherein the projection values of all pixels in each view field are given weight through calculation, the projection data of the depth information of the overlapped position are obtained through weighting, and the approximate 'parallel light' projection data of the overlapped position point is obtained. The pixel normalization is to average the parts of all the overlapping points obtained in the previous step belonging to the same pixel, assign the parts to the corresponding pixels, ensure the unchanged resolution of the detector and output and obtain a complete image. The multi-view-field X-ray imaging stitching method provided by the invention can obviously improve the stitching quality of scanned images, stitch the images while scanning the X-rays, select the number of the used view fields according to the requirements of stitching precision of imaging objects, and has the advantages of high detection speed, small radiation to patients and good imaging effect. Can meet the requirements of low dosage and high precision of X-ray imaging.
The beneficial effects of the invention are as follows:
the acquisition system of the multi-view X-ray scanning image projection can solve the problem that the single-view X-ray projection image lacks the depth information of the detected part, and obtain the depth information of each part of an object;
secondly, the invention can select different numbers of field acquisition according to actual selection, and can select different numbers of field acquisition according to different precision requirements, so that a patient receives X-ray radiation with minimum dose.
Thirdly, the invention greatly weakens the deformation of the fan beam X-ray to the object by the overlapping position determination and the weighted fusion of the projection data by the specific weight, approximates to the parallel light projection, obtains a high-precision scanning image and is beneficial to the doctor to better judge the illness state of the patient;
fourth, the X-ray image scanning and stitching of the invention can be performed simultaneously, the stitching time is greatly shortened, and the imaging speed is high, so that the patient can be scanned by rays for a shorter time and is subjected to less radiation.
Fifth, the scanning and splicing mode of the invention is not limited by hardware conditions, the equipment is simple and easy to operate, and the method can realize automatic splicing of images by integrating the method into a program.
Drawings
FIG. 1 is a schematic diagram of a dual field of view image scan;
FIG. 2 is a schematic view of a three field image scan;
FIG. 3 is a schematic diagram of a synchronous motion mode of the detector and the optical machine;
FIG. 4 is a flow chart of a multi-field X-ray imaging stitching method;
FIG. 5 is an image of a sphere that has not been stitched by this method;
FIG. 6 is a sphere image of a dual field X-ray imaging stitch completed;
main component symbol description: 1-detector, 2-object to be measured, 3-X ray machine.
Detailed Description
The invention will now be further described with reference to examples, figures:
the technical scheme of the invention is as follows:
the design of the acquisition system of the multi-view X-ray scanning image projection comprises the following steps:
the detector, the object placing table and the X-ray machine are arranged in parallel in the vertical direction;
the distance from the detector to the object placing table is about 4 times of the distance from the X-ray machine to the object placing table;
the detector and the X-ray machine synchronously move at a uniform speed through synchronous belt transmission;
placing a stationary object to be tested on the object placing table;
the steps of each movement of the detector and the optical machine are changed along with the number of required splices, and the steps are determined by the following formula:
the detector and the X-machine move in an arch shape along the axis of the object in parallel to the object placing table until the scanning of the interested part of the object to be detected is completed.
Positioning the overlapped position, comprising the following steps:
establishing a rectangular coordinate system by taking the center of a first pixel of a first scanning detector as an origin, taking the horizontal direction of the pixel as an X axis and taking the vertical direction as a Y axis;
in the process of multi-field scanning, a straight line is determined by using the center of each pixel of each scanning detector and two points of an X-ray machine, and the center position of each pixel of each detector and the connecting line of the X-ray machine can be expressed by the following formula in a rectangular coordinate system:
where h represents the perpendicular distance of the light engine to the detector, x i X represents the abscissa, x, of the position of the ith scan ray apparatus ij An abscissa indicating the center position of the jth pixel of the ith scan, and d indicating the step of the optical machine movement;
acquiring all straight line intersection points in the area between the detector and the optical machine, and determining all intersection point coordinates to acquire depth information of an object overlapping area;
the projection data weighted fusion comprises the following steps:
and forming a triangle by connecting each intersection point with the corresponding two pixel center positions, and determining the projection value of the intersection point position by using the projection values of two pixels below the triangle, wherein the projection value calculation formula is as follows:
D＝|x ij -x mn |
wherein represents the projection value of the intersection point position, P ij ，P mn Representing the projection value of the jth pixel of the ith scan and the projection value of the nth pixel of the mth scan, x respectively mn The abscissa representing the center position of the nth pixel of the mth scan.
The pixel normalization comprises the following steps:
determining the abscissa positions of all the intersection points, wherein the intersection points of the abscissa in the intervals of the pixel positions are defined as belonging to the same pixel;
and finally determining the final projection value of each pixel, wherein the projection value calculation formula is as follows:
wherein n is j Representing the number of intersection points belonging to the j-th pixel in total, P t Representing a projection value of a t-th intersection belonging to a j-th pixel; and outputting by using the projection value to obtain a complete spliced image.
The detector for X-ray imaging is characterized in that:
the detector material is tellurium zinc cadmium, and the resistivity of the material is required to be 10 9 The working leakage current is less than 10nA, no macroscopic defect, no grain boundary and even tellurium inclusion distribution exist in the crystal;
the electrode material of the detector is gold or indium or silver or aluminum;
the detector is of a photon technology linear array detector, the energy resolution of the detector is below 20%, and the energy and threshold calibration is carried out before the detector is used.
The maximum energy of the X-ray machine is above 80kV, and the type of emitted X-rays is a fan-shaped narrow beam.
Embodiments of the present invention are described in detail below, examples of which are illustrated in the accompanying drawings, wherein the same or similar symbols indicate the same or similar components or components having the same or similar functions throughout. The embodiments described below by referring to the drawings are illustrative and intended to explain the present invention and should not be construed as limiting the invention.
In the description of the present invention, it should be understood that the terms "intermediate," "inner," "horizontal," "vertical," and the like indicate orientations or positional relationships, which are merely used for convenience in describing the present invention and simplifying the description, and do not indicate or imply that the devices or elements being referred to must have a specific orientation, be configured and operated in a specific orientation, and thus should not be construed as limiting the invention.
In the description of the present invention, the terms "first," "second," "third," and the like are used for descriptive purposes only and are not to be construed as indicating or implying relative importance or the number of technical features being referred to. Thus, a feature defining "a first", "a second", "a third", etc. may explicitly or implicitly include one or more such feature.
The invention relates to a multi-view-field X-ray imaging splicing method, wherein the specific view field number of scanned multi-view fields is determined according to the precision required by different positions during actual X-ray imaging, and the design thought of the invention is as follows:
according to different requirements of the nuclear medicine field on affected parts of patients, the number of multiple fields of view required to be scanned is determined by combining the requirements of high precision and low dosage. And calculating the step of synchronous movement of the detector and the X-ray machine according to the determined number of the multiple fields of view to be scanned.
The detector and the X-ray machine are driven by the synchronous belt to move in an arch shape along the axis of the object in parallel according to the determined steps until the scanning of the interested part of the object to be detected is completed.
And establishing a rectangular coordinate system by taking the center of a first pixel of the first scanning detector as an origin, taking the horizontal direction of the pixel as an X axis and taking the vertical direction as a Y axis, determining a straight line by using two points of each pixel center of the scanning detector and an X ray machine each time in the multi-view field scanning process, obtaining all straight line intersection points of the area between the detector and the ray machine, and determining all intersection point coordinates to obtain the depth information of the object overlapping area.
And forming a triangle by connecting each intersection point with the corresponding two pixel center positions, and determining the projection value of the intersection point position by using the projection values of the two pixels below the triangle.
And determining the abscissa positions of all the intersection points, wherein the intersection points of the abscissa in the intervals of the pixel positions are defined as belonging to the same pixel, finally determining the final projection value of each pixel, and outputting the final projection value to obtain a complete spliced image.
The invention is based on the following further description by means of the figures and examples:
example 1: double-view-field X-ray imaging splicing method
The detector material is tellurium zinc cadmium, and the resistivity of the material is required to be 10 9 The working leakage current is less than 10nA, no macroscopic defect exists in the crystal, no grain boundary exists, and tellurium inclusions are uniformly distributed. The detector is a 64-pixel linear array detector adopting photon technology, the energy resolution of the detector is 10%, the pixel size is 0.9mm multiplied by 1.8mm, the pixel spacing is 0.1mm, the electrode material of the detector is gold, and the energy and threshold value calibration is carried out before the detector is used. The maximum energy of the X-ray machine is 80kV, and the type of emitted X-rays is a fan-shaped narrow beam. The distance from the detector to the object placing plate is 200cm, and the distance from the X-ray machine to the object placing plate is 50cm. The object to be measured is a vertebral body model.
The whole method flow chart is shown in fig. 4. According to the set three-field image scanning, a three-field image scanning schematic diagram is shown in fig. 2, and the synchronous movement step of the detector and the optical machine is determined to be 32mm. The object placing table is provided with a hollow circular sphere, the detector and the X-ray machine are driven by the synchronous belt to move in an arch shape along the axis of the sphere according to determined steps, the movement mode is shown in figure 3, and the scanning of the whole sphere is completed. And establishing a rectangular coordinate system by taking the center of a first pixel of the first scanning detector as an origin, taking the horizontal direction of the pixel as an X axis and taking the vertical direction as a Y axis, determining a straight line by using two points of each pixel center of the scanning detector and an X ray machine each time in the multi-view field scanning process, obtaining all straight line intersection points of the area between the detector and the ray machine, and determining all intersection point coordinates to obtain the depth information of the object overlapping area. And forming a triangle by connecting each intersection point with the corresponding two pixel center positions, and determining the projection value of the intersection point position by using the projection values of the two pixels below the triangle. And determining the abscissa positions of all the intersection points, wherein the intersection points of the abscissa in the intervals of the pixel positions are defined as belonging to the same pixel, finally determining the final projection value of each pixel, and outputting the final projection value to obtain a complete spliced image.
The whole method can output the spliced complete sphere image in number while scanning is completed, the sphere image spliced by the method is shown in figure 5, and the sphere image spliced by the method is shown in figure 6.
Claims (6)
1. A multi-view-field X-ray imaging splicing method is characterized by comprising the following steps:
step 1, acquisition of multi-field X-ray scanning image projection:
1. the detector is arranged in parallel with the object placing table and the X-ray machine in the vertical direction, and a stationary object to be detected is placed on the object placing table; the distance from the detector to the object placing table is 4 times of the distance from the X-ray machine to the object placing table; the detector and the X-ray machine synchronously move at a uniform speed through synchronous belt transmission;
2. the step of each movement of the detector and the optics is determined by the following formula:
3. the detector and the X-ray machine move in an arch shape along the axis of the object in parallel to the object placing table until the scanning of the interested part of the object to be detected is completed;
step 2, positioning the overlapped positions:
1. establishing a rectangular coordinate system by taking the center of a first pixel of a first scanning detector as an origin, taking the horizontal direction of the pixel as an X axis and taking the vertical direction as a Y axis;
2. determining a straight line by scanning each pixel center of the detector and two points of the X-ray machine each time, wherein the position of each pixel center of each detector and the optical machine connecting line can be expressed by the following formula in a rectangular coordinate system:
where h represents the perpendicular distance of the light engine to the detector, x i X represents the abscissa, x, of the position of the ith scan ray apparatus ij An abscissa indicating the center position of the jth pixel of the ith scan, and d indicating the step of the optical machine movement;
3. acquiring all straight line intersection points in the area between the detector and the optical machine, and determining all intersection point coordinates to acquire depth information of an object overlapping area;
step 3, projection data weighted fusion: each intersection point and the connecting line of the central positions of the two corresponding pixels form a triangle, the projection values of the positions of the intersection points are determined by the projection values of the two pixels below the triangle, and the calculation formula of the projection values is as follows:
D＝|x ij -x mn |
wherein represents the projection value of the intersection point position, P ij ，P mn Representing the projection value of the jth pixel of the ith scan and the projection value of the nth pixel of the mth scan respectively,x mn an abscissa indicating a center position of an nth pixel of the mth scan;
step 4, pixel normalization:
1. determining the abscissa positions of all the intersection points, wherein the intersection points of the abscissa in the intervals of the pixel positions are defined as belonging to the same pixel;
2. the final projection value of each pixel is determined, and the projection value calculation formula is as follows:
wherein n is j Representing the number of intersection points belonging to the j-th pixel in total, P t Representing a projection value of a t-th intersection belonging to a j-th pixel; 3. and outputting by using the projection value to obtain a complete spliced image.
2. The multi-field X-ray imaging stitching method of claim 1, wherein: the maximum energy of the X-ray machine is above 80kV, and the type of emitted X-rays is a fan-shaped narrow beam.
3. The multi-field X-ray imaging stitching method of claim 1, wherein: the detector is a photon technology linear array detector, and the energy resolution of the detector is below 20%.
4. The multi-field X-ray imaging stitching method of claim 1, wherein: the detector is calibrated by energy and threshold before use.
5. The multi-field X-ray imaging stitching method of claim 1, wherein: the detector material is tellurium zinc cadmium, and the resistivity of the material is required to be 10 9 The working leakage current is less than 10nA, no macroscopic defect exists in the crystal, no grain boundary exists, and tellurium inclusions are uniformly distributed.
6. The multi-field X-ray imaging stitching method of claim 1, wherein: the electrode material of the detector is gold or indium or silver or aluminum.
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| EP1495720A1 (en) * | 2003-07-07 | 2005-01-12 | GE Medical Systems Global Technology Company LLC | X-ray computerised tomography (CT) imaging method and system |
| CN102860838A (en) * | 2012-09-13 | 2013-01-09 | 清华大学 | Equipment and method for dental X-ray tomography |
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| CN107714072A (en) * | 2017-11-20 | 2018-02-23 | 中国科学院高能物理研究所 | Compensation method, computer tomographic scanning imaging method and the system of missing data |
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