CN117958849A - Automatic geometric correction double-view image system and method - Google Patents
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Abstract
The invention relates to the technical field of double-view images, and provides an automatic geometric correction double-view image system, wherein a first image device and a second image device are provided with shooting view angles with different directions; the first and second sources are configured to emit X-rays at a preset frame rate, and the first and second detectors are configured to receive the X-rays passing through the patient screening site and output first and second image data; the workstation is configured to receive the first image data and the second image data output by the first detector and the second detector, perform geometric correction on each pixel point in the first image data and the second image data by using a polynomial fitting coefficient, and output first undistorted image data and second undistorted image data. And the distorted images of the image data obtained from two visual angles in the medical double-visual-angle image system are subjected to geometric correction simultaneously, so that undistorted image data is corrected, and the characteristics of the part of the patient are reflected more truly.
Description
Technical Field
The present invention relates to the field of dual-view images, and more particularly, to a dual-view image system and method with automatic geometric correction.
Background
The medical dual view imaging system is a specially designed image acquisition device for the medical field, which has two views or cameras for acquiring multi-angle medical images. Such systems acquire images from two different locations or orientations simultaneously to provide more comprehensive, accurate medical information. This helps the physician obtain more detailed visual data when making diagnoses and surgical plans. The dual-view imaging system can be used for depth perception, and the distance of the object in the image is calculated by analyzing the parallax of the object, so that three-dimensional imaging is realized.
The current acquisition method of the double-view images of the patients in the market utilizes a medical double-view image system of two sets of X-ray image equipment comprising two X-ray sources and two image receivers to acquire image data, and the two sets of image systems represent a 90-degree angle. When image data of a patient are acquired through the double-view image system, the workstation controls two sets of X-ray image equipment to acquire the image data of the patient according to a certain time sequence, normal position and side position image data of the patient are obtained, then the image of the patient is presented to a user through software processing, and meanwhile, the irradiation range of X-rays is controlled by the beam splitter.
However, in the prior art, both views of the medical dual-view imaging system irradiate the patient with an X-ray cone beam or a fan-shaped beam similar to the cone beam, so as to obtain image information of the patient part, and the beam is the cone beam or the fan-shaped beam similar to the cone beam, so that the image of the obtained image data is distorted.
Disclosure of Invention
In view of the above problems, the present invention aims to provide an automatic geometric correction dual-view image system and method, which can perform geometric correction on distorted images of image data obtained from two views in a medical dual-view image system at the same time, and correct the images into undistorted image data, so as to more truly reflect the characteristics of a patient part.
The above object of the present invention is achieved by the following technical solutions:
an automatically geometrically corrected dual view imaging system comprising: the system comprises a first image device, a second image device and a workstation;
The first image equipment and the second image equipment are provided with shooting visual angles with different directions, the first image equipment comprises a first ray source and a first detector, and the second image equipment comprises a second ray source and a second detector;
The first and second sources are configured to emit X-rays at a preset frame rate, the first and second detectors are configured to receive the X-rays passing through a patient screening site and output first and second image data;
The workstation is configured to receive the first image data and the second image data output by the first detector and the second detector, perform geometric correction on each pixel point in the first image data and the second image data by using a polynomial fitting coefficient, and output first undistorted image data and second undistorted image data.
Further, the automatic geometrically correct dual-view image system further comprises: a distance measuring instrument;
The distance-measuring instrument is configured to measure a distance OID A of the patient screening site to the first detector and a distance OID B of the patient screening site to the second detector, respectively, and to send the distance OID A and the distance OID B to the workstation, which in combination with the distance OID A and the distance OID B, and a distance SID A of the first radiation source to the first detector and a distance SID B of the second radiation source to the second detector, calculates the polynomial fit coefficients.
Further, in the workstation, the polynomial fit coefficients are calculated by combining the distance OID A and the distance OID B, and the distance SID A from the first radiation source to the first detector and the distance SID B from the second radiation source to the second detector, specifically:
The workstation respectively finds image center points of the first image data and the second image data, respectively establishes a coordinate system by taking the image center points as original points, marks original coordinates of all pixel points in the first image data as (u A,vA), and marks original coordinates of all pixel points in the second image data as (u B,vB);
p A、pB pixel points are selected as control points in the central areas of the first image data and the second image data, which are close to the central point of the image;
The ideal coordinates (x A,yA) and (x B,yB) of each control point in the first image data and the second image data are calculated according to the following formulas in combination with the values of the distance OID A and the distance OID B, and the distance SID A and the distance SID B, respectively:
substituting the original coordinates and ideal coordinates of p A control points and p B control points in the first image data and the second image data into the following polynomials respectively to calculate a first polynomial fitting coefficient corresponding to the first image data and a second polynomial fitting coefficient corresponding to the second image data:
Wherein a ij and b ij are the fitted polynomial fitting coefficients, p is the number of the control points, n is the polynomial fitting times, s and t are fitting times related values, i, j, k are variables for solving sum formula traversal, and n, s, t satisfy the following definitions:
n is the maximum positive integer calculated by the formula;
s＝0,1,2,…,n；
t＝0,1,2,…,n-s；
s+t≤n；
p is detected through experiments according to different image devices;
and fitting the first image data and the second image data through the formulas respectively to obtain the first polynomial fitting coefficient corresponding to the first image data and the second polynomial fitting coefficient corresponding to the second image data.
Further, in the workstation, further comprising: according to the calculated polynomial fitting coefficients including the first polynomial fitting coefficient and the second polynomial fitting coefficient, the geometric correction is performed on each pixel point in the first image data and the second image data by respectively adopting the following formulas:
Wherein a ij and b ij are the fitted polynomial fitting coefficients, (u, v) are the original coordinates of the control points, (x, y) are the ideal coordinates of the control points, n is the polynomial fitting times, p is the number of the control points, n is the polynomial fitting times, s and t are the fitting times related values, i, j are variables traversed by a sum formula.
Further, in the workstation, further comprising: and carrying out gray interpolation on the first image data and the second image data subjected to geometric correction so as to avoid discontinuous gray scales of the corrected first image data and the corrected second image data.
Further, the photographing angles of view of the first image device and the second image device are set vertically, the first image device photographs the first image data as an orthographic image of the patient screening site, and the second image device photographs the second image data as a lateral image of the patient screening site.
Further, the automatic geometrically correct dual-view image system further comprises: a first source rack, a second source rack, a first detector rack, and a second detector rack;
The first ray source rack, the second ray source rack, the first detector rack and the second detector rack are respectively loaded with the first ray source, the second ray source, the first detector and the second detector to do reciprocating motion in the vertical direction and are used for being suitable for different patients or different screening positions of the patients.
Further, the automatic geometrically correct dual-view image system further comprises: a first collimator and a second collimator;
The first collimator is arranged in front of the first ray source and is used for controlling the ray beam of the X-rays emitted by the first ray source;
the second collimator is arranged in front of the second ray source and is used for controlling the ray beam of the X-rays emitted by the second ray source.
Further, the automatic geometrically correct dual-view image system further comprises: a first radiation dose measuring unit and a second radiation dose measuring unit;
the first ray dose measuring unit is arranged in front of the first collimator and is used for measuring the ray dose of the first ray source;
the second ray dose measuring unit is arranged in front of the second collimator and is used for measuring the ray dose of the second ray source.
A dual view image method for performing automatic geometric correction of a dual view image system as described above, comprising the steps of:
s1: the first and second sources emit X-rays at a preset frame rate.
S2: the first detector and the second detector receive the X-rays passing through the patient screening site and output first image data and second image data.
S3: the workstation receives the first image data and the second image data output by the first detector and the second detector, performs geometric correction on each pixel point in the first image data and the second image data by adopting a polynomial fitting coefficient, and outputs first undistorted image data and second undistorted image data.
Compared with the prior art, the invention has the beneficial effects that:
By providing an automatically geometrically corrected dual view imaging system, comprising: the system comprises a first image device, a second image device and a workstation; the first image equipment and the second image equipment are provided with shooting visual angles with different directions, the first image equipment comprises a first ray source and a first detector, and the second image equipment comprises a second ray source and a second detector; the first and second sources are configured to emit X-rays at a preset frame rate, the first and second detectors are configured to receive the X-rays passing through a patient screening site and output first and second image data; the workstation is configured to receive the first image data and the second image data output by the first detector and the second detector, perform geometric correction on each pixel point in the first image data and the second image data by using a polynomial fitting coefficient, and output first undistorted image data and second undistorted image data. According to the technical scheme, the distorted images of the image data obtained from two visual angles in the medical double-visual-angle image system are subjected to geometric correction by using the calculated polynomial fitting coefficients, so that the undistorted image data is corrected, and the characteristics of the part of a patient can be reflected more truly.
Drawings
FIG. 1 is a schematic top view of a prior art medical dual view imaging system;
FIG. 2 is a schematic diagram of distortion generated in the prior art;
FIG. 3 is a block diagram of an auto-geometry-corrected dual-view imaging system according to the present invention;
FIG. 4 is a schematic block diagram of an auto-geometrically correct dual view imaging system according to the present invention;
FIG. 5 is a block diagram illustrating the geometry correction of the auto geometry correction dual view imaging system of the present invention;
FIG. 6 is a flowchart illustrating an exemplary method for automatically geometrically correcting a dual-view image according to the present invention.
Detailed Description
For the purpose of making the objects, technical solutions and advantages of the embodiments of the present application more apparent, the technical solutions of the embodiments of the present application will be clearly and completely described below with reference to the accompanying drawings in the embodiments of the present application, and it is apparent that the described embodiments are some embodiments of the present application, but not all embodiments of the present application. All other embodiments, which can be made by those skilled in the art based on the embodiments of the application without making any inventive effort, are intended to be within the scope of the application.
As used herein, the singular forms "a", "an", "the" and "the" are intended to include the plural forms as well, unless expressly stated otherwise, as understood by those skilled in the art. It will be further understood that the terms "comprises" and/or "comprising," when used in this specification, specify the presence of stated features, integers, steps, operations, elements, and/or components, but do not preclude the presence or addition of one or more other features, integers, steps, operations, elements, components, and/or groups thereof.
A schematic top view of a medical dual view imaging system currently on the market is shown in fig. 1, where the distance from the source to the detector is generally defined as SID, and the distance from the patient to the detector is defined as OID.
As shown in fig. 2, taking one view as an example, the other view principle is the same, because a cone beam is used, an object should be projected at B (X ', Y'), but projected at a (X, Y), and because the center point of an image and the cone X-ray beam coincide, no distortion is generated, and the farther from the center of the image, the greater the distortion.
Based on the problems existing in the current market, the invention provides an automatic geometric correction double-view image system, which can simultaneously perform geometric correction on distorted images of image data obtained from two views in a medical double-view image system, and correct the distorted images into undistorted image data, so that the characteristics of the part of a patient are reflected more truly. The following is described by way of specific examples:
First embodiment
As shown in fig. 3 and 4, the present embodiment provides an automatic geometry correction dual-view image system, which includes: the system comprises a first image device, a second image device and a workstation;
The first image equipment and the second image equipment are provided with shooting visual angles with different directions, the first image equipment comprises a first ray source and a first detector, and the second image equipment comprises a second ray source and a second detector; the first and second sources are configured to emit X-rays at a preset frame rate, the first and second detectors are configured to receive the X-rays passing through a patient screening site and output first and second image data; the workstation is configured to receive the first image data and the second image data output by the first detector and the second detector, perform geometric correction on each pixel point in the first image data and the second image data by using a polynomial fitting coefficient, and output first undistorted image data and second undistorted image data.
In this embodiment, the directions of the first image device and the second image device are not limited, and only the directions of the first image device and the second image device are required to be different. But the preferred scheme is: the photographing visual angles of the first image device and the second image device are vertically set, the first image device photographs the first image data serving as the positive image of the patient screening part, and the second image device photographs the second image data serving as the lateral image of the patient screening part. That is, the first radiation source in the first imaging device is an AP radiation source, the first detector is an AP detector, the second radiation source in the second imaging device is an LAT radiation source, and the second detector is an LAT detector. And finally, outputting an orthographic image and a lateral image of the screened part of the patient through the geometric correction of the workstation.
The automatic geometry correction dual-view image system of the present embodiment further includes: a distance measuring instrument;
The distance-measuring instrument is configured to measure a distance OID A of the patient screening site to the first detector and a distance OID B of the patient screening site to the second detector, respectively, and to send the distance OID A and the distance OID B to the workstation, which in combination with the distance OID A and the distance OID B, and a distance SID A of the first radiation source to the first detector and a distance SID B of the second radiation source to the second detector, calculates the polynomial fit coefficients.
Further, in the workstation, the polynomial fit coefficients are calculated by combining the distance OID A and the distance OID B, and the distance SID A from the first radiation source to the first detector and the distance SID B from the second radiation source to the second detector, specifically:
The workstation respectively finds image center points of the first image data and the second image data, respectively establishes coordinate systems by taking the image center points as original points (0, 0), marks original coordinates of all pixel points in the first image data as (u A,vA), and marks original coordinates of all pixel points in the second image data as (u B,vB);
Since the distortion of the central region of the image is less affected by the human body characteristics, p A、pB pixel points are selected as control points in the central regions of the first image data and the second image data, which are close to the central point of the image, the control points of the central region can be measured through experiments according to different image devices without considering the image of the human body thickness.
The ideal coordinates (x A,yA) and (x B,yB) of each control point in the first image data and the second image data are calculated according to the following formulas in combination with the values of the distance OID A and the distance OID B, and the distance SID A and the distance SID B, respectively:
substituting the original coordinates and ideal coordinates of p A control points and p B control points in the first image data and the second image data into the following polynomials respectively to calculate a first polynomial fitting coefficient corresponding to the first image data and a second polynomial fitting coefficient corresponding to the second image data:
Wherein a ij and b ij are the fitted polynomial fitting coefficients, p is the number of the control points, n is the polynomial fitting times, s and t are fitting times related values, i, j, k are variables for solving sum formula traversal, and n, s, t satisfy the following definitions:
n is the maximum positive integer calculated by the formula;
s＝0,1,2,…,n；
t＝0,1,2,…,n-s；
s+t≤n；
p is detected through experiments according to different image devices;
and fitting the first image data and the second image data through the formulas respectively to obtain the first polynomial fitting coefficient corresponding to the first image data and the second polynomial fitting coefficient corresponding to the second image data.
Further, according to the calculated polynomial fitting coefficients including the first polynomial fitting coefficient and the second polynomial fitting coefficient, the geometric correction is performed on each pixel point in the first image data and the second image data by using the following formulas:
Wherein a ij and b ij are the fitted polynomial fitting coefficients, (u, v) are the original coordinates of the control points, (x, y) are the ideal coordinates of the control points, n is the polynomial fitting times, p is the number of the control points, n is the polynomial fitting times, s and t are the fitting times related values, i, j are variables traversed by a sum formula.
For example, when n is taken to be 3, the transformation for performing geometric correction on each pixel point in the first image data or the second image data is as follows:
x＝a00+a01v+a02v2+a03v3+a10u+a11uv+a12uv2+a20u2+a21u2v+a30u3
y＝b00+b01v+b02v2+b03v3+b10u+b11uv+b12uv2+b20u2+b21u2v+b30u3
Further, since non-integer phenomenon may occur in the mapped coordinates, gray interpolation is performed on the first image data and the second image data after geometric correction, so as to avoid gray discontinuity of the corrected first image data and second image data.
Note that, the manner of gray interpolation is not limited in this embodiment, and for example, the following manner may be adopted:
bilinear interpolation: for a non-integer coordinate position, bilinear interpolation uses the gray values of the surrounding four pixels for weighted averaging.
Bicubic interpolation: more accurate than bilinear interpolation, interpolation is performed by using information of more neighboring pixels.
Triangular interpolation: a trigonometric function is used to approximate the gray value at the non-integer coordinate location.
Nearest neighbor interpolation: the gray value at the nearest integer coordinate position is selected as the interpolation result.
As shown in fig. 5, which is a schematic block diagram of distortion calibration of the first image data or the second image data, since the geometric calibration principles of the two different directions are the same, fig. 5 is only an example with a single view angle.
In addition, the automatic geometry correction dual-view image system of the present embodiment further includes: a first source rack, a second source rack, a first detector rack, and a second detector rack; the first ray source rack, the second ray source rack, the first detector rack and the second detector rack are respectively loaded with the first ray source, the second ray source, the first detector and the second detector to do reciprocating motion in the vertical direction and are used for being suitable for different patients or different screening positions of the patients.
Further, the automatic geometry correction dual-view image system of the present embodiment further includes: a first collimator and a second collimator; the first collimator is arranged in front of the first ray source and is used for controlling the ray beam of the X-rays emitted by the first ray source; the second collimator is arranged in front of the second ray source and is used for controlling the ray beam of the X-rays emitted by the second ray source.
Further, the automatic geometry correction dual-view image system of the present embodiment further includes: a first radiation dose measuring unit and a second radiation dose measuring unit; the first ray dose measuring unit is arranged in front of the first collimator and is used for measuring the ray dose of the first ray source; the second ray dose measuring unit is arranged in front of the second collimator and is used for measuring the ray dose of the second ray source.
Second embodiment
As shown in fig. 6, the present example provides a dual view image method of performing automatic geometric correction of a dual view image system as in the first embodiment, comprising the steps of:
s1: the first and second sources emit X-rays at a preset frame rate.
S2: the first detector and the second detector receive the X-rays passing through the patient screening site and output first image data and second image data.
S3: the workstation receives the first image data and the second image data output by the first detector and the second detector, performs geometric correction on each pixel point in the first image data and the second image data by adopting a polynomial fitting coefficient, and outputs first undistorted image data and second undistorted image data.
A computer readable storage medium storing computer code which, when executed, performs a method as described above. Those of ordinary skill in the art will appreciate that all or part of the steps in the various methods of the above embodiments may be implemented by a program to instruct related hardware, the program may be stored in a computer readable storage medium, and the storage medium may include: read Only Memory (ROM), random access Memory (RAM, random Access Memory), magnetic or optical disk, and the like.
The above description is only a preferred embodiment of the present invention, and the protection scope of the present invention is not limited to the above examples, and all technical solutions belonging to the concept of the present invention belong to the protection scope of the present invention. It should be noted that modifications and adaptations to the present invention may occur to one skilled in the art without departing from the principles of the present invention and are intended to be within the scope of the present invention.
The technical features of the above-described embodiments may be arbitrarily combined, and all possible combinations of the technical features in the above-described embodiments are not described for brevity of description, however, as long as there is no contradiction between the combinations of the technical features, they should be considered as the scope of the description.
It should be noted that the above embodiments can be freely combined as needed. The foregoing is merely a preferred embodiment of the present invention and it should be noted that modifications and adaptations to those skilled in the art may be made without departing from the principles of the present invention, which are intended to be comprehended within the scope of the present invention.
Claims (10)
1. An automatically geometrically corrected dual view imaging system, comprising: the system comprises a first image device, a second image device and a workstation;
The first image equipment and the second image equipment are provided with shooting visual angles with different directions, the first image equipment comprises a first ray source and a first detector, and the second image equipment comprises a second ray source and a second detector;
The first and second sources are configured to emit X-rays at a preset frame rate, the first and second detectors are configured to receive the X-rays passing through a patient screening site and output first and second image data;
The workstation is configured to receive the first image data and the second image data output by the first detector and the second detector, perform geometric correction on each pixel point in the first image data and the second image data by using a polynomial fitting coefficient, and output first undistorted image data and second undistorted image data.
2. The automatically geometrically correct dual view imaging system of claim 1, further comprising: a distance measuring instrument;
The distance-measuring instrument is configured to measure a distance OID A of the patient screening site to the first detector and a distance OID B of the patient screening site to the second detector, respectively, and to send the distance OID A and the distance OID B to the workstation, which in combination with the distance OID A and the distance OID B, and a distance SID A of the first radiation source to the first detector and a distance SID B of the second radiation source to the second detector, calculates the polynomial fit coefficients.
3. The automatic geometrically correct dual view imaging system of claim 2, wherein in said workstation, said polynomial fit coefficients are calculated in combination of said distance OID A and said distance OID B, and said distance SID A from said first source to said first detector and said distance SID B from said second source to said second detector, in particular:
The workstation respectively finds image center points of the first image data and the second image data, respectively establishes a coordinate system by taking the image center points as original points, marks original coordinates of all pixel points in the first image data as (u A,vA), and marks original coordinates of all pixel points in the second image data as (u B,vB);
p A、pB pixel points are selected as control points in the central areas of the first image data and the second image data, which are close to the central point of the image;
The ideal coordinates (x A,yA) and (x B,yB) of each control point in the first image data and the second image data are calculated according to the following formulas in combination with the values of the distance OID A and the distance OID B, and the distance SID A and the distance SID B, respectively:
substituting the original coordinates and ideal coordinates of p A control points and p B control points in the first image data and the second image data into the following polynomials respectively to calculate a first polynomial fitting coefficient corresponding to the first image data and a second polynomial fitting coefficient corresponding to the second image data:
Wherein a ij and b ij are the fitted polynomial fitting coefficients, p is the number of the control points, n is the polynomial fitting times, s and t are fitting times related values, i, j, k are variables for solving sum formula traversal, and n, s, t satisfy the following definitions:
n is the maximum positive integer calculated by the formula;
s＝0,1,2,…,n；
t＝0,1,2,…,n-s；
s+t≤n；
p is detected through experiments according to different image devices;
and fitting the first image data and the second image data through the formulas respectively to obtain the first polynomial fitting coefficient corresponding to the first image data and the second polynomial fitting coefficient corresponding to the second image data.
4. The automatically geometrically correct dual view imaging system of claim 3, further comprising, in the workstation: according to the calculated polynomial fitting coefficients including the first polynomial fitting coefficient and the second polynomial fitting coefficient, the geometric correction is performed on each pixel point in the first image data and the second image data by respectively adopting the following formulas:
Wherein a ij and b ij are the fitted polynomial fitting coefficients, (u, v) are the original coordinates of the control points, (x, y) are the ideal coordinates of the control points, n is the polynomial fitting times, p is the number of the control points, n is the polynomial fitting times, s and t are the fitting times related values, i, j are variables traversed by a sum formula.
5. The automatically geometrically correct dual view imaging system of claim 1, further comprising, in the workstation: and carrying out gray interpolation on the first image data and the second image data subjected to geometric correction so as to avoid discontinuous gray scales of the corrected first image data and the corrected second image data.
6. The automatically geometrically correct dual view imaging system of claim 1, further comprising:
The photographing visual angles of the first image device and the second image device are vertically set, the first image device photographs the first image data serving as the positive image of the patient screening part, and the second image device photographs the second image data serving as the lateral image of the patient screening part.
7. The automatically geometrically correct dual view imaging system of claim 1, further comprising: a first source rack, a second source rack, a first detector rack, and a second detector rack;
The first ray source rack, the second ray source rack, the first detector rack and the second detector rack are respectively loaded with the first ray source, the second ray source, the first detector and the second detector to do reciprocating motion in the vertical direction and are used for being suitable for different patients or different screening positions of the patients.
8. The automatically geometrically correct dual view imaging system of claim 1, further comprising: a first collimator and a second collimator;
The first collimator is arranged in front of the first ray source and is used for controlling the ray beam of the X-rays emitted by the first ray source;
the second collimator is arranged in front of the second ray source and is used for controlling the ray beam of the X-rays emitted by the second ray source.
9. The automatically geometrically correct dual view imaging system of claim 8, further comprising: a first radiation dose measuring unit and a second radiation dose measuring unit;
the first ray dose measuring unit is arranged in front of the first collimator and is used for measuring the ray dose of the first ray source;
the second ray dose measuring unit is arranged in front of the second collimator and is used for measuring the ray dose of the second ray source.
10. A dual view imaging method for performing automatic geometry correction of the automatic geometry correction dual view imaging system of any of claims 1-9, comprising the steps of:
s1: the first and second radiation sources emit X-rays at a preset frame rate;
s2: the first detector and the second detector receive the X-rays passing through the patient screening part and output first image data and second image data;
S3: the workstation receives the first image data and the second image data output by the first detector and the second detector, performs geometric correction on each pixel point in the first image data and the second image data by adopting a polynomial fitting coefficient, and outputs first undistorted image data and second undistorted image data.
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