CN220735412U - X-ray three-dimensional image diagnosis system - Google Patents
X-ray three-dimensional image diagnosis system Download PDFInfo
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- CN220735412U CN220735412U CN202321747791.5U CN202321747791U CN220735412U CN 220735412 U CN220735412 U CN 220735412U CN 202321747791 U CN202321747791 U CN 202321747791U CN 220735412 U CN220735412 U CN 220735412U
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Abstract
The utility model provides an X-ray three-dimensional image diagnosis system. An X-ray three-dimensional image diagnosis system of an embodiment includes: the X-ray three-dimensional image diagnosis system comprises an X-ray shooting stand and a bed, wherein a projection feature is arranged in the bed, and the X-ray three-dimensional image diagnosis system detects the projection feature from X-ray projection data formed during three-dimensional scanning shooting to complete calculation of calibration data of the space position of an X-ray passage required during three-dimensional image reconstruction. According to the utility model, maintenance operation of periodically updating calibration data through the phantom can be omitted, and the image quality of the three-dimensional reconstructed image can be improved.
Description
Technical Field
The present utility model relates to an X-ray three-dimensional image diagnosis system.
Background
An X-ray three-dimensional image diagnostic system is a diagnostic system that photographs a subject mounted on a bed by an X-ray photographing stand. The X-ray three-dimensional image diagnosis system includes an X-ray generating section capable of generating X-rays that penetrate through a subject, and the X-rays that are incident on the subject by the X-ray generating section are received by an X-ray detecting section after penetrating through the subject. The X-ray detector converts X-rays transmitted through a human body into an electrical signal to generate an image of a subject.
In the reconstruction of the three-dimensional image, the positional relationship between the subject space and the projection image is required, and thus the X-ray path needs to be calibrated. In the prior art, the process of calibrating the X-ray path requires the placement of a phantom embedded with metal particles on the bedding. The position of the particles in the phantom is defined in global coordinates by design or actual measurement as required, and the X-rays emitted by the X-ray focus are projected through the phantom onto the surface of the X-ray detector, whereby the positional correspondence between a specific point on the phantom and the projected surface of the X-ray detector can be calculated. This correspondence is referred to as calibration data (Wobble table).
The X-ray generating unit and the X-ray detecting unit generate movement and deformation (vibration) due to gravity, driving force, and inertial force. Therefore, the calibration data needs to be updated in real time according to the state of the X-ray three-dimensional image diagnosis system, but the time and the labor are wasted, and more importantly, even if the operation of updating the calibration data can be performed before the three-dimensional scanning photographing is performed each time, the vibration phase generated in the scanning operation cannot be completely matched with the phase in the calibration process, so that the position of an X-ray passage calculated by the calibration data cannot be completely consistent with the position in the three-dimensional scanning photographing, and the image reconstruction is inevitably prevented from generating artifacts.
Disclosure of Invention
The utility model aims to provide an X-ray three-dimensional image diagnosis system capable of improving the image quality of a three-dimensional reconstructed image.
In order to achieve the above object, an X-ray three-dimensional image diagnosis system of an embodiment of the present utility model includes: the X-ray three-dimensional image diagnosis system comprises an X-ray shooting stand and a bed, wherein a projection feature is arranged in the bed, and the X-ray three-dimensional image diagnosis system detects the projection feature from X-ray projection data formed during three-dimensional scanning shooting to complete calculation of calibration data of the space position of an X-ray passage required during three-dimensional image reconstruction.
According to the utility model, the projection feature is arranged in the bed, the projection feature is detected in the X-ray projection data formed during three-dimensional scanning photography, so that the calculation of the calibration data of the space position of the X-ray passage required for reconstructing the three-dimensional image is completed, the maintenance operation of periodically updating the calibration data through a phantom can be omitted, and the calibration data can be dynamically carried out in real time, so that the artifact caused by the difference of the X-ray projection states during the three-dimensional scanning and the X-ray calibration can be eliminated, and the image quality of the three-dimensional reconstructed image can be improved.
Drawings
FIG. 1 is a schematic diagram showing the structure of an X-ray three-dimensional image diagnosis system according to the present utility model;
FIG. 2 is a schematic diagram illustrating a prior art method of calibrating an X-ray path for an X-ray three-dimensional image diagnostic system;
fig. 3 is a schematic view showing a structure in which a projection feature is embedded in a top plate of a bed according to the first embodiment;
FIG. 4 is a schematic diagram showing a search area of the projected feature at section D-D in FIG. 3;
fig. 5 is a schematic view showing a change in CT value after overlapping a negative film of a projection feature with an actual projection image at different positions, fig. 5 (a) shows a change in CT value after overlapping a negative film of a projection feature with an actual projection image region where no projection feature is provided, fig. 5 (b) shows a change in CT value after overlapping a negative film of a projection feature with an actual projection image region where a projection feature is provided, and fig. 5 (c) shows a change in CT value after overlapping a negative film of a projection feature with an actual projection image region where a projection feature is provided.
Fig. 6 is a schematic diagram showing a configuration of an X-ray three-dimensional image diagnosis system according to a second embodiment;
fig. 7 is a schematic diagram showing a coordinate relationship of projection features of the X-ray three-dimensional image diagnostic system according to the second embodiment.
Detailed Description
Hereinafter, an embodiment of the X-ray three-dimensional image diagnostic system 1 according to the present utility model will be described with reference to the drawings. In the drawings, the same components are denoted by the same reference numerals.
In the drawings, the structure is appropriately enlarged, reduced, or omitted for convenience of explanation. In order to clearly illustrate the X-ray three-dimensional image diagnostic system 1 of the present utility model, components not directly related to the present utility model are omitted.
(first embodiment)
Fig. 1 is a schematic diagram showing the structure of an X-ray three-dimensional image diagnosis system 1 according to the present utility model.
As shown in fig. 1, in the present embodiment, an X-ray three-dimensional image diagnosis system 1 includes an X-ray imaging gantry 2, a bed 3 on which an object P to be X-ray imaged is placed, a control unit 4, and the like. The X-ray three-dimensional image diagnosis system 1 is a device that photographs a subject P placed on a bed 3 with an X-ray photographing stand 2.
In the present embodiment, the X-ray imaging gantry 2 (i.e., C-arm) includes an X-ray generating unit 5 and an X-ray detecting unit 6. The X-ray generating unit 5 generates X-rays for irradiating the subject P. The X-ray generating section 5 includes an X-ray tube (tube ball device) and an X-ray diaphragm. The X-ray tube generates X-rays. The X-ray diaphragm adjusts the size of the irradiation range of X-rays. The X-rays generated by the X-ray tube and having the irradiation range adjusted by the X-ray diaphragm are irradiated onto the detection site of the subject P placed on the bed 3. The X-ray detector 6 detects X-rays transmitted through the subject P. The X-ray detector 6 is, for example, a flat panel detector. The X-ray detector 6 receives and detects the X-rays penetrating the subject P, and converts the X-rays into an electrical signal corresponding to the X-ray dose to generate detection data.
The control unit 4 controls the X-ray generation unit 5 and the X-ray detection unit 6.
The method of calibrating an X-ray path by means of a phantom 7 according to the prior art will now be described with reference to fig. 2.
Fig. 2 is a schematic diagram showing a method of calibrating an X-ray path of an X-ray three-dimensional image diagnosis system according to the related art.
As shown in fig. 2, the body mold 7 is made of a propylene material, and metal particles are embedded in the body mold 7. In performing X-ray passage marking for an X-ray three-dimensional image diagnosis system, it is necessary to fix the body membrane 7 to a top plate (not shown in fig. 2) of a bedtable in a detachable manner. The position of the particles in the phantom 7 is defined in global coordinates by design or actual measurement as needed, and the X-rays emitted from the focal point of the X-ray generating unit 5 are projected onto the surface of the X-ray detecting unit 6 through the phantom 7, whereby the correspondence relationship between the position of a specific point on the phantom 7 and the projected surface of the X-ray detecting unit 6, that is, calibration data (wobbe table) can be calculated.
In particular, the relationship of the three-dimensional reconstruction region points (x, y, z) and the image pixels (c, l) of the two-dimensional projection image plane is generally given by the following transformation,
λ[cl1] T ＝M[xyz1] T (1)
in the above equation, the matrix M is the calibration data, the matrix expansion becomes the following form,
the X-ray paths detected by the X-ray detection unit 6 are represented as discrete data on the two-dimensional projection planes (c, l). For ease of computation, define m 34 Each X-ray path is expressed as a linear equation of the following formula.
c＝m 11 x+m 12 y+m 13 z+m 14 -m 31 (cx)-m 32 (cy)-m 33 (cz)
l＝m 21 x+m 22 y+m 23 z+m 24 -m 31 (lz)-m 32 (ly)-m 33 (lz) (3)
Eleven components in the matrix M define the position information of the X-ray path. The matrix M can be calculated from the coordinate values (x, y, z) of the metal particles in the phantom and the data set of the coordinates (c, l) of the projection points of the detected particles in the projection data.
In the prior art, since the phantom is required to be mounted on the bed when the calibration data is updated, and the phantom is required to be dismounted after the calibration data is updated, the labor and the effort are wasted. In addition, since the X-ray generating unit and the X-ray detecting unit move and deform (vibrate) due to the gravity, driving force and inertia force, even if the operation of updating the calibration data can be performed each time before the three-dimensional scanning is performed, it is impossible to completely match the vibration phase generated during the scanning operation with the phase at the time of calibration, and therefore it is impossible to ensure that the position of the X-ray path calculated by the calibration data is completely identical to the position at the time of the three-dimensional scanning, and thus, artifacts are inevitably generated at the time of image reconstruction.
Next, the structure of the bed 3 of the X-ray three-dimensional image diagnosis system 1 for improving the image quality of the three-dimensional reconstructed image in the first embodiment will be described with reference to fig. 3.
Fig. 3 is a schematic view showing a structure in which the projection feature 30 according to the first embodiment is embedded in the top plate 31 of the bed 3.
As shown in fig. 3, in the present embodiment, a projection feature 30 equivalent to a phantom or a pellet (pellet) is provided in a bed 3 of an X-ray three-dimensional image diagnosis system 1, and the X-ray three-dimensional image diagnosis system 1 detects the projection feature 30 from X-ray projection data formed at the time of three-dimensional scanning imaging to complete calculation of calibration data of a spatial position of an X-ray path required at the time of reconstructing a three-dimensional image.
Specifically, the projection feature 30 is embedded in the top plate 31 of the bed 3, and the projection feature 30 is a spherical bead composed of a high-density material. In this embodiment, the projection feature 30 may be constructed, for example, from an artificial bone material. In addition, the projection feature 30 may be made of a metal material such as iron or molybdenum. The projection features 30 form a circular or elliptical image in the projection data, whereby the center position of the projection features 30 can be easily detected from the projection data.
In order that the projection features 30 do not overlap in the projection image at the time of three-dimensional scanning, the respective projection features 30 need to be arranged at certain intervals, and the specific interval is not particularly limited as long as the respective projection features 30 do not overlap in the projection image of three-dimensional scanning. The following table shows one way of arranging six projection features in global coordinates. Six projection features 30 may be embedded on the top plate 31 of the bed 3, for example, with global coordinates as shown in the table below.
In the present embodiment, since the projection feature 30 is provided on the bed 3, the projection feature 30 is also reflected on the projection data obtained by three-dimensional scanning imaging of the subject, and the projection position of each projection feature 30 in the projection data is detected, so that the calibration data matrix M can be calculated by using the above formula (3), and then the matrix M and the projection data are used together for reconstructing the three-dimensional image. Since the calibration data is calculated from the projection data (including the projection information of the object and the projection feature embedded in the table top) obtained in each actual three-dimensional scanning photography, the operation of updating the calibration data by the phantom is not required, and therefore time and effort are saved. In addition, since the calibration can be dynamically performed in real time, the artifacts caused by the difference between the state of the actual scanning and the state of the updated X-ray calibration data can be eliminated, and the image quality of the three-dimensional reconstructed image can be improved.
In addition, when the density of the material constituting the projection feature 30 is too high, it causes an artifact in reconstructing a three-dimensional image, and therefore, in order to detect the projection feature 30 from the projection data of the imaging subject P, it is preferable that the density of the material constituting the projection feature 30 is smaller than the average value of the human bone densities.
In addition, the larger the diameter of the projection feature 30 is, the higher the calculation accuracy of the projection position of the projection feature 30 is, which is more advantageous for preventing the occurrence of artifacts upon the reconstruction of the three-dimensional image. However, if the diameter of the projection feature 30 is too large, the adverse effect on the projected image is also large. Therefore, it is preferable that the diameter size of the spherical bead constituting the projection feature 30 is two to four times the pixel size of the X-ray detection section 6 of the X-ray three-dimensional image diagnostic system 1. Thus, the projected image of the projection feature 30 is about twice the diameter thereof, and the accuracy of calculating the center of the projected image of the projection feature 30 can be ensured.
Further, it is preferable that the position requirement of the distance (i.e., SID) between the focal point of the X-ray emitted from the tube ball of the X-ray generating section 5 and the image receiving surface of the X-ray detecting section 6 is: the X-rays are perpendicular to the surface of the X-ray detection section 6, and the focal point of the X-rays is aligned with the center of the X-ray detection section 6.
Hereinafter, a method of performing X-ray path data calibration without using a phantom by using the X-ray three-dimensional image diagnostic system 1 according to the above embodiment will be described with reference to fig. 4 and 5.
Fig. 4 is a schematic diagram showing the search area of the projection feature 30 at the section D-D in fig. 3.
Fig. 5 is a schematic view showing a change in CT value after overlapping the negative film of the projection feature 30 with the actual projection image at different positions, fig. 5 (a) shows a change in CT value after overlapping the negative film of the projection feature 30 with the region of the actual projection image where the projection feature 30 is not provided, that is, the negative film of the projection feature 30 overlaps with the non-overlapping region e1 in fig. 4, fig. 5 (b) shows a change in CT value after overlapping the negative film of the projection feature 30 with the region of the actual projection image where the projection feature 30 is provided, that is, the negative film of the projection feature 30 overlaps with the full overlapping region e2 in fig. 4, and fig. 5 (c) shows a change in CT value after overlapping the negative film of the projection feature 30 with the region of the actual projection image where the projection feature 30 is provided, that is, the negative film of the projection feature 30 overlaps with the partial overlapping region e3 in fig. 4. In fig. 5, the broken line is the CT value R before the overlap, and the solid line is the CT value R after the overlap.
In the first step, the X-ray three-dimensional image diagnostic system 1 is scanned once without the object P, whereby a partial projection image of only the projection feature 30, which is called a projection feature reference projection image, can be obtained.
In the second step, the value of the X-ray transmission amount passing through the center of the projection feature reference projection image is obtained, and the projection feature reference projection image is converted into a negative film, thereby obtaining a reference value 2t of the X-ray absorption amount of the projection feature, and the data is stored in the memory unit of the control unit 4 of the X-ray three-dimensional image diagnosis system 1.
And thirdly, acquiring a projection image of the object to be picked and the projection feature object, and selecting the area predicted to contain the projection feature object as a search area of the projection feature object.
Specifically, the actual projection image obtained by performing one main scan of the subject mounted on the bed 3 is an image of the subject P including the projection feature 30 (i.e., a projection image in which the subject and the projection feature overlap). The X-ray transmission amount is represented by a gray value on the image, and the X-ray transmission amount of the projection image of the projection feature 30 superimposed on the subject P is reduced, whereby the projection position of the projection feature 30 can be detected in the projection image. In addition, in order to reduce the time of image processing, the approximate range of the projection image including the projection feature 30 can be predicted from the known installation position of the projection feature 30. The area predicted to contain the projection of the projection feature 30 is selected as the search area for the projection feature 30.
Fourth, the projection positions (cp, lp) of the projection feature 30 are detected in the search area.
Specifically, first, a plurality of straight lines parallel to the c-axis and the l-axis, respectively, with a certain interval are defined in the search area of the two-dimensional projection plane formed by the X-ray detection section 6, and as shown in fig. 4, the X-ray transmission value 2T of the straight line parallel to the l-axis at the D-D section in the actual projection image is shown. Thereafter, the reference value 2t of the X-ray absorption amount of the projection feature obtained in the second step is overlapped along a straight line parallel to the l-axis at the D-D section, and the objective function Q is calculated according to the following expression (4).
Since the originally smooth tissue changes by the projection of the projection feature 30, when the "superimposition processing" is performed at the projection position of the actual projection feature, the CT value of the image (image of the projection feature 30) that is not subjected to the "superimposition processing" is inevitably larger than the change of the image (image from which the influence of the projection feature 30 is removed) after the "superimposition processing" due to the projection of the projection feature 30, and this is represented by the objective function Q.
The maximum value of the objective function Q of the X-ray absorption amount reference value overlapping position of the projection feature 30 is defined as c ', c ' (i) is obtained by calculating n straight lines parallel to the l axis, i is the number of the nth straight line parallel to the l axis, wherein the maximum value of c ' is cp.
c′[max 2T {Q}] (5)
The method of detecting the coordinates lp in the projection position of the projection feature 30 is the same as the method of detecting the coordinates cp in the projection position of the projection feature 30, and thus will not be described again.
Fifth, a matrix M (i.e., calibration data) is calculated using the detected projection positions (cp, lp) of the respective projection features 30 according to the above formula (3).
Specifically, as shown in the above formula (3), two equations can be established by the projection coordinates (cp, lp) of each projection feature 30, whereby at least twelve equations established from at least six projection features 30 are required in the present embodiment to be able to calculate eleven unknowns in the matrix M. That is, in the present embodiment, since it is necessary to reflect the projection points of at least six projection features 30 on the X-ray projection image at the time of three-dimensional scanning imaging, it is necessary to make the number of projection features 30 embedded in the bed 3 at least six.
The above-described calculation by the objective function Q is merely a specific example, and is not limited thereto. For example, the Machine Learning (ML) may be performed using the projection image of the projection feature as "teacher" data, the AI system may be identified using the teaching image of the ML, the coordinates of the projection feature in the projection image may be detected, and the calibration data may be calculated using the above formula (3).
According to the present embodiment, by providing the projection feature in the bed, and detecting the projection feature from the X-ray projection data formed during the three-dimensional scanning imaging, the calculation of the calibration data of the spatial position of the X-ray path required for reconstructing the three-dimensional image can be performed, and not only the maintenance operation of periodically updating the calibration data by the phantom can be omitted, but also the calibration data can be dynamically performed in real time, so that the artifact caused by the difference in the X-ray projection state between the three-dimensional scanning and the X-ray calibration can be eliminated, and the image quality of the three-dimensional reconstructed image can be improved.
(second embodiment)
Next, a configuration of an X-ray three-dimensional image diagnosis system 1 for improving the image quality of a three-dimensional reconstructed image in the second embodiment will be described with reference to fig. 6.
Fig. 6 is a schematic diagram showing the structure of an X-ray three-dimensional image diagnosis system 1 according to the second embodiment.
The same parts as those of the first embodiment in this embodiment will not be described again. Only the different parts will be described. Other undescribed portions are the same as or equivalent to the first embodiment.
As shown in fig. 6, in the present embodiment, as in the first embodiment, a projection feature 30 equivalent to a phantom or a pellet (pellet) is provided in the bed 3 of the X-ray three-dimensional image diagnosis system 1. The X-ray three-dimensional image diagnosis system 1 detects the projection feature 30 from the X-ray projection data formed during three-dimensional scanning imaging to complete calculation of calibration data of the spatial position of the X-ray path required for reconstructing the three-dimensional image.
In the present embodiment, unlike the first embodiment, the projection feature 30 is also provided on the X-ray generating section 5 of the X-ray three-dimensional image diagnostic system 1. Specifically, in the present embodiment, the number of projection features 30 is at least six (for example, six, eight, or ten), and half of the projection features 30 are provided on the X-ray generating section 5 of the X-ray three-dimensional image diagnosis system 1, and the remaining projection features 30 are provided in the bed 3.
In the present embodiment, since the projection feature 30 is provided on the bed 3 and the X-ray generating unit 5, the projection feature 30 is also reflected on the projection data obtained by three-dimensional scanning imaging of the subject, and the projection position of each projection feature 30 in the projection data is detected, so that the calibration data matrix M can be calculated by using the above formula (3), and then the matrix M and the projection data are used together for reconstructing the three-dimensional image. Since the calibration data is calculated from the projection data (including the projection information of the object, the bed and the projection feature in the X-ray generation unit) obtained in each actual three-dimensional scanning photography, the operation of updating the calibration data by the phantom is not required, and therefore time and effort are saved. In addition, since the calibration can be dynamically performed in real time, the artifacts caused by the difference between the state of the actual scanning and the state of the updated X-ray calibration data can be eliminated, and the image quality of the three-dimensional reconstructed image can be improved.
Next, a method of performing X-ray path data calibration without using a phantom by using the X-ray three-dimensional image diagnostic system 1 according to the above embodiment will be described with reference to fig. 7.
Fig. 7 is a schematic diagram showing a coordinate relationship of a projection feature 30 of the X-ray three-dimensional image diagnostic system 1 according to the second embodiment.
As shown in fig. 7, in the present embodiment, it is necessary to provide each of the six projection features a, b, c, P, P2, and P3 at a position that can be projected on the X-ray detection unit 6 of the X-ray three-dimensional image diagnosis system 1 at the time of three-dimensional scanning imaging.
In fig. 7, a coordinate system O ' -X ' y ' z. is a coordinate system established with the focal point S of the tube ball device of the X-ray generation unit as the origin. Since the projection features a, b, and c are provided on the balloon apparatus of the X-ray generating unit and are positioned so as to be able to be projected onto the X-ray detecting unit 6 during imaging, the coordinate values of the projection features a, b, and c in the coordinate system O '-X' y 'z' are known. For example, the point a coordinates are (x' a ，y′ a ，z′ a )。
In the imaging, the projection points of the projection features a, b, and c on the X-ray detection unit 6 are the points A, B, C, and the coordinate values of the three points of the point A, B, C in the projection coordinate systems 0f to clv can be detected by the same method as in the first embodiment.
In the coordinate system O '-X' y 'z', the plane equation at the X-ray detection section 6 is,
m′ 31 x′+m′ 32 y′+m′ 33 z′＝m′ 34 (6)
wherein m 'is' 31 、m′ 32 、m′ 33 、m′ 34 Is four unknowns.
In the coordinate system O '-X' y 'z', the X-rays passing through the projection feature a are represented as straight-line equations,
(x′-x′ a )/x′ a ＝(y′-y′ a )/y′ a ＝(z′-z′ a )/z′ a 。 (7)
the linear equations of the X-rays passing through the projection features b, c in the coordinate system O '-X' y 'z' are consistent with the above examples and are not described here again.
The coordinate values (including m ' in the coordinate system O ' -X ' y ' z. of the intersection of the three X-rays passing through the projection features a, b, and c and the X-ray detection unit 6 can be calculated by the above formulas (6) and (7) ' 31 、m′ 32 、m′ 33 、m′ 34 Four unknowns).
Next, m 'is calculated' 31 、m′ 32 、m′ 33 、m′ 34 The method of these four unknowns is illustrated.
As shown in fig. 7, the vector cross in any two straight directions in the plane constituted by the point A, B, C and the vector cross in the normal direction to the plane of the X-ray detecting section 6 are zero. For example, ABxCBx (m' 31 ，m′ 32 ，m′ 33 ) T ＝0。
Since the coordinates of the points A, B, C are known, an equation is established based on the distance between any two of the points A, B, C.
The plane equation of the X-ray detection unit 6 obtained by this calculation method has two solutions, and it is necessary to perform a process of removing the solution of the antisymmetric position of the focal point S of the tube ball device. Specifically, three projection features P1, P2, P3 in the coordinate system O-xyz are provided on the bed and are located at positions where they can be projected onto the X-ray detection section 6 at the time of photographing, and therefore their coordinate values in O-xyz are known.
In the imaging, the projection images Of the projection features P1, P2, P3 projected onto the X-ray detection unit 6 are points Pp1, pp2, pp3, the coordinate values Of the points Pp1, pp2, pp3 in the projection coordinate system Of-clv are known, and then the same calculation as in the above method is performed, except that O-xyz and O '-X' y 'z' are interchanged, whereby the position Of the X-ray path in the coordinate system Of O-xyz can be determined.
Since the positions of the projection points of the three projection features on the pipe ball device at the global coordinates O-xyz are known, the calculation of the calibration data (matrix M) can be performed using the above formula (3).
According to the present embodiment, since the projection feature is provided on the bed and the X-ray generating unit, the projection feature is detected from the X-ray projection data formed during the three-dimensional scanning imaging to complete the calculation of the calibration data of the spatial position of the X-ray path required for reconstructing the three-dimensional image, and the maintenance operation of periodically updating the calibration data by the phantom can be omitted, and since the calibration data can be dynamically performed in real time, the artifact caused by the difference in the X-ray projection state between the three-dimensional scanning and the X-ray calibration can be eliminated, and the image quality of the three-dimensional reconstructed image can be improved.
Any of the embodiments described above may be expressed as follows,
an X-ray three-dimensional image diagnostic system comprising:
the X-ray three-dimensional image diagnosis system comprises an X-ray shooting stand and a bed, wherein a projection feature is arranged in the bed, and the X-ray three-dimensional image diagnosis system detects the projection feature from X-ray projection data formed during three-dimensional scanning shooting to complete calculation of calibration data of the space position of an X-ray passage required during three-dimensional image reconstruction.
According to at least one embodiment, by providing the projection feature on the bed, and detecting the projection feature from the X-ray projection data formed during the three-dimensional scanning imaging to complete the calculation of the calibration data of the spatial position of the X-ray path required for reconstructing the three-dimensional image, it is possible to omit the maintenance work of periodically updating the calibration data by the phantom, and to perform the calibration data in real time on a dynamic basis, so that the artifact caused by the difference in the X-ray projection state between the three-dimensional scanning and the X-ray calibration can be eliminated, and the image quality of the three-dimensional reconstructed image can be improved.
While several embodiments of the present utility model have been described, these embodiments are presented by way of example only and are not intended to limit the scope of the utility model. These novel embodiments can be implemented in various other modes, and various omissions, substitutions, combinations, and modifications can be made without departing from the spirit of the utility model. These embodiments and modifications thereof are included in the scope and gist of the present utility model, and are included in the present utility model and their equivalents as set forth in the claims.
Claims (7)
1. An X-ray three-dimensional image diagnostic system, comprising:
the X-ray three-dimensional image diagnosis system comprises an X-ray shooting stand and a bed, wherein a projection feature is arranged in the bed, and the X-ray three-dimensional image diagnosis system detects the projection feature from X-ray projection data formed during three-dimensional scanning shooting to complete calculation of calibration data of the space position of an X-ray passage required during three-dimensional image reconstruction.
2. The X-ray three-dimensional image diagnostic system according to claim 1, wherein,
the projection features are embedded in the top panel of the bedding table, the projection features being spherical beads formed of a high density material.
3. The X-ray three-dimensional image diagnostic system according to claim 1, wherein,
it is necessary to reflect the projection points of at least six of the projection features on the X-ray projection image at the time of three-dimensional scanning photography.
4. The X-ray three-dimensional image diagnostic system according to claim 2, wherein,
the density of the material comprising the projection feature is less than the average of the human bone density.
5. The X-ray three-dimensional image diagnostic system according to claim 2, wherein,
the spherical beads have a diameter size twice to four times the pixel size of an X-ray detection section of the X-ray three-dimensional image diagnosis system.
6. The X-ray three-dimensional image diagnostic system according to claim 3, wherein,
half of the projection features are arranged on an X-ray generating part of the X-ray three-dimensional image diagnosis system, the rest of the projection features are arranged in the bed, and the projection features are all positioned at positions which can be projected on an X-ray detecting part of the X-ray three-dimensional image diagnosis system during three-dimensional scanning shooting.
7. The X-ray three-dimensional image diagnostic system according to claim 6, wherein,
the projection features are at least six.
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