CN114947922B - Method and medium for constructing image data of CT device in double-source wide-body mode - Google Patents

Method and medium for constructing image data of CT device in double-source wide-body mode Download PDF

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CN114947922B
CN114947922B CN202210644443.9A CN202210644443A CN114947922B CN 114947922 B CN114947922 B CN 114947922B CN 202210644443 A CN202210644443 A CN 202210644443A CN 114947922 B CN114947922 B CN 114947922B
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ray source
coordinate representation
axis
ray
angle
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CN114947922A (en
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李涛涛
廉世俊
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Siemens Shanghai Medical Equipment Ltd
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Siemens Shanghai Medical Equipment Ltd
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    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B6/00—Apparatus or devices for radiation diagnosis; Apparatus or devices for radiation diagnosis combined with radiation therapy equipment
    • A61B6/02—Arrangements for diagnosis sequentially in different planes; Stereoscopic radiation diagnosis
    • A61B6/03—Computed tomography [CT]
    • A61B6/032—Transmission computed tomography [CT]
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B6/00—Apparatus or devices for radiation diagnosis; Apparatus or devices for radiation diagnosis combined with radiation therapy equipment
    • A61B6/02—Arrangements for diagnosis sequentially in different planes; Stereoscopic radiation diagnosis
    • A61B6/03—Computed tomography [CT]
    • A61B6/032—Transmission computed tomography [CT]
    • A61B6/035—Mechanical aspects of CT
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B6/00—Apparatus or devices for radiation diagnosis; Apparatus or devices for radiation diagnosis combined with radiation therapy equipment
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    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B6/00—Apparatus or devices for radiation diagnosis; Apparatus or devices for radiation diagnosis combined with radiation therapy equipment
    • A61B6/40—Arrangements for generating radiation specially adapted for radiation diagnosis
    • A61B6/4007—Arrangements for generating radiation specially adapted for radiation diagnosis characterised by using a plurality of source units
    • A61B6/4014—Arrangements for generating radiation specially adapted for radiation diagnosis characterised by using a plurality of source units arranged in multiple source-detector units
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B6/00—Apparatus or devices for radiation diagnosis; Apparatus or devices for radiation diagnosis combined with radiation therapy equipment
    • A61B6/42—Arrangements for detecting radiation specially adapted for radiation diagnosis
    • A61B6/4266—Arrangements for detecting radiation specially adapted for radiation diagnosis characterised by using a plurality of detector units
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B6/00—Apparatus or devices for radiation diagnosis; Apparatus or devices for radiation diagnosis combined with radiation therapy equipment
    • A61B6/44—Constructional features of apparatus for radiation diagnosis
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B6/00—Apparatus or devices for radiation diagnosis; Apparatus or devices for radiation diagnosis combined with radiation therapy equipment
    • A61B6/44—Constructional features of apparatus for radiation diagnosis
    • A61B6/4429—Constructional features of apparatus for radiation diagnosis related to the mounting of source units and detector units
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B6/00—Apparatus or devices for radiation diagnosis; Apparatus or devices for radiation diagnosis combined with radiation therapy equipment
    • A61B6/54—Control of apparatus or devices for radiation diagnosis
    • G—PHYSICS
    • G06—COMPUTING; CALCULATING OR COUNTING
    • G06T—IMAGE DATA PROCESSING OR GENERATION, IN GENERAL
    • G06T11/00—2D [Two Dimensional] image generation
    • G06T11/003—Reconstruction from projections, e.g. tomography
    • G—PHYSICS
    • G06—COMPUTING; CALCULATING OR COUNTING
    • G06T—IMAGE DATA PROCESSING OR GENERATION, IN GENERAL
    • G06T2210/00—Indexing scheme for image generation or computer graphics
    • G06T2210/41—Medical

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Abstract

The present disclosure relates to a method and medium for constructing image data of a CT apparatus in a dual source wide volume mode. The method comprises the following steps: establishing a rectangular coordinate system; acquiring a distance from a first x-ray source to a rotation center point; acquiring a first angle; acquiring a first coordinate representation of a first x-ray source using a first angle and distance; acquiring a second angle and a third angle; acquiring a second coordinate representation of a point at a predetermined distance from the first x-ray source using the first coordinate representation, the second angle, and the third angle; acquiring a third coordinate representation at a predetermined distance from the second x-ray source using the second coordinate representation, the predetermined angle between the first subsystem and the second subsystem, and the predetermined distance in the axial direction; and constructing image data of the detection site using the second coordinate representation and the third coordinate representation.

Description

Method and medium for constructing image data of CT device in double-source wide-body mode
Technical Field
The present disclosure relates to the medical field, and more particularly, to a method and a storage medium for reconstructing data of a CT apparatus in a dual-source wide-volume mode.
Background
Among high-end CT apparatuses, there are two apparatus designs, i.e., a dual-source CT apparatus with high time resolution and a single-source wide-body CT apparatus with large z-coverage (e.g., 12cm to 16 cm). For both devices, there are various strengths and weaknesses in clinical applications.
For example, dual source CT devices may obtain CT images with high temporal resolution, but may result in step artifacts in the CT images due to limited z-coverage in, for example, cardiac scanning.
The single source wide body CT apparatus has a wide z coverage, but the following problems also exist: the time resolution is not high, and the best single-source wide body CT device at present can only provide 125ms of time resolution, which is still too long for arrhythmia patients; for a single-source wide-body CT device, cone beam artifacts in CT images are very serious due to the large z coverage; the image quality obtained by spiral scanning in the all-z coverage mode is poor, and in order to ensure the image quality, the single-source wide CT device can only perform spiral scanning in the z coverage range of 6 cm-8 cm, and the all-z coverage mode is only used for special axial scanning.
To overcome the limitation of z-coverage in dual source CT devices, the size of the detector in dual source CT devices may be increased, however, as the detector size increases, cone beam artifacts become very severe and the cost increases dramatically.
In order to overcome the limitation of the time resolution in the single-source wide-body CT apparatus, the rotation speed of the single-source wide-body CT apparatus may be increased. However, a small increase in rotational speed will cause a large increase in centrifugal force, which requires a very high strength of the rotating parts, which would otherwise present a potential safety risk for x-ray tubes and the like of single source wide body CT devices as well as for patients.
Disclosure of Invention
In view of the state of the art and the shortcomings, it is an object of the present disclosure to provide a CT apparatus capable of providing not only a dual source mode, but also a dual source wide body mode, in which a high time resolution can be achieved, in which a large z coverage can be achieved, while cone beam artifacts can be reduced, improving the quality of CT images and making the mode switching operation convenient and simple. In addition, with respect to the CT apparatus, the current method of constructing CT image data is not applicable when it is in the dual-source wide-volume mode, and thus, another object of the present disclosure is to provide a method of constructing image data applicable to the CT apparatus in the dual-source wide-volume mode.
According to an embodiment of the present disclosure, there is provided a method of constructing image data of a CT apparatus in a dual source wide volume mode, the CT apparatus including: a cylindrical housing rotatable about an axis thereof; a first subsystem disposed within the housing, comprising a first x-ray source and a first detector, wherein the first x-ray source and the first detector are disposed radially opposite on an inner wall of the housing; a second subsystem disposed within the housing and including a second x-ray source and a second detector, wherein the second x-ray source and the second detector are disposed radially opposite to each other in a sliding manner on an inner wall side of the housing, and a line direction of the first x-ray source and the first detector forms a predetermined angle with a line direction of the second x-ray source and the second detector; and an actuator provided in the housing and configured to be capable of moving the second subsystem relative to the first subsystem in an axial direction of the housing, wherein the first subsystem and the second subsystem are identical in structure, and when the CT apparatus detects a detection site moving in the axial direction with the second subsystem being shifted by a predetermined distance in the axial direction relative to the first subsystem, the CT apparatus is in a dual-source wide body mode in which the method includes:
Determining a predetermined point on an axis as a rotation center point, taking a straight line passing through the rotation center point and perpendicular to the axis direction of the shell as a first axis, taking a straight line passing through the rotation center point and perpendicular to the first axis and the axis direction as a second axis, and taking the axis as a third axis to establish a rectangular coordinate system;
acquiring a distance from the first x-ray source to a center point of rotation in a plane formed by the first axis and the second axis;
acquiring a first angle sandwiched between a first axis and a line connecting the first x-ray source and a center point of rotation in a plane;
acquiring a first coordinate representation of the first x-ray source in a rectangular coordinate system relative to the detection site using the first angle and the distance;
acquiring a second angle between a first x-ray source and a rotation center point line in a plane and a predetermined x-ray emitted from the first x-ray source in the plane, the predetermined x-ray being an x-ray passing through the detection site;
Acquiring a third angle, the third angle being a maximum x-ray beam angle of an x-ray beam emitted from the first x-ray source that is received by the first detector in a direction of a third axis;
acquiring a second coordinate representation in a rectangular coordinate system of a point in a plane at a predetermined length from the first x-ray source on a predetermined x-ray emitted from the first x-ray source, using the first coordinate representation, the second angle, and the third angle;
Acquiring a third coordinate representation in a rectangular coordinate system of a point on an x-ray emitted from the second x-ray source at a predetermined length in a plane from the second x-ray source with the second coordinate representation, the predetermined angle, and the predetermined distance; and
Image data of the detection site is constructed using the second coordinate representation and the third coordinate representation.
In this way, image data suitable for the CT apparatus in the dual-source wide-volume mode can be constructed.
In the method of constructing image data of a CT apparatus in a dual source wide volume mode according to the present disclosure, further comprising: spatially transforming the second coordinate representation using the first relationship; and spatially transforming the third coordinate representation using a second relationship.
The coordinate representation in the rectangular coordinate system can be transformed into a space which is easy to carry out subsequent data processing by utilizing the first relation and the second relation, and the data processing efficiency is submitted.
In a method of constructing image data of a CT apparatus in a dual-source wide-volume mode in accordance with the present disclosure, the first coordinate representation includes a coordinate representation of the first x-ray source relative to the detection site on a first axisCoordinate representation on the second axis/>And a coordinate representation/>, on a third axisWherein using the first angle and the distance, obtaining a first coordinate representation of the first x-ray source relative to the detection site in the rectangular coordinate system comprises:
Wherein R F represents a distance from the first x-ray source to the rotation center point in the plane, α represents the first angle between a line connecting the first x-ray source and the rotation center point in the plane and the first axis, and z rot represents a distance by which the detection portion moves in the axis direction for one rotation of the CT apparatus.
The above gives a specific form of the first coordinate representation.
In a method of constructing image data of a CT apparatus in a dual-source wide-volume mode according to the present disclosure, the second coordinate representation includes a coordinate representation of a point on the predetermined x-ray in the plane at a predetermined length from the first x-ray source on a first axis relative to the detection siteCoordinate representation on the second axis/>And a coordinate representation/>, on a third axisWherein using the first coordinate representation, the second angle, and the third angle, obtaining a second coordinate representation of a point in the rectangular coordinate system relative to the detection site at a predetermined length in the plane from the first x-ray source on a predetermined x-ray emitted from the first x-ray source includes:
Where β is the second angle, θ cone is the third angle, l represents a predetermined length from the first x-ray source over a predetermined x-ray emitted from the first x-ray source in the plane, and q is a scaling factor in the range of-1 to 1.
The above way gives a specific form of the second coordinate representation
In a method of constructing image data of a CT apparatus in a dual source wide volume mode according to the present disclosure, the third coordinate representation includes a coordinate representation on the first axis of a point on a predetermined x-ray emitted from the second x-ray source at the predetermined length in the plane from the second x-ray source relative to the detection siteCoordinate representation on the second axis/>And a coordinate representation/>, on a third axisWherein using the second coordinate representation, the predetermined angle, and the predetermined distance, obtaining a third coordinate representation of a point in the rectangular coordinate system in the plane at the predetermined length from the second x-ray source on x-rays emitted from the second x-ray source relative to the detection site comprises:
wherein, D shift is the predetermined distance for the predetermined angle.
The above way gives a specific form of the third coordinate representation
In a method of constructing image data of a CT apparatus in a dual source wide volume mode according to the present disclosure, the first relationship includes: θ=α+β, p=r F sin β, spatially transforming the second coordinate representation using the first relationship comprises: substituting the first relation into a coordinate representationCoordinate representation/>And coordinate representation/>To obtain:
by transforming the coordinate representation in the rectangular coordinate system to the coordinate representation in the p- θ space, the subsequent data processing efficiency can be improved.
In the method of constructing image data of a CT apparatus in a dual source wide volume mode according to the present disclosure, the second relationship includes: Spatially transforming the third coordinate representation with the second relationship comprises substituting the second relationship into the coordinate representation/> Coordinate representation/>And coordinate representation/>To obtain:
by transforming the coordinate representation in the rectangular coordinate system to the coordinate representation in the p- θ space, the subsequent data processing efficiency can be improved.
According to another embodiment of the present disclosure, there is provided a computer-readable storage medium having stored thereon a program which, when executed, causes a processor to perform a method of constructing image data of a CT apparatus in a dual source wide mode according to the present disclosure.
Drawings
The accompanying drawings, which are included to provide a further understanding of the disclosure, illustrate and explain the present disclosure, and together with the description serve to explain the present disclosure. In the drawings:
fig. 1 shows a block diagram of a CT apparatus according to an embodiment of the present disclosure.
Fig. 2 illustrates a specific structure of a CT apparatus according to an embodiment of the present disclosure.
Fig. 3 illustrates another specific structure of a CT apparatus according to an embodiment of the present disclosure.
Fig. 4 shows a graph of the distance between the first and second probes as the actuator is driven.
Fig. 5 is a diagram illustrating an x-ray beam configuration of a CT apparatus operating in a dual source mode according to an embodiment of the present disclosure.
Fig. 6 shows an x-ray beam configuration diagram of a CT apparatus operating in a dual source wide volume mode according to an embodiment of the present disclosure.
Fig. 7 illustrates a method of constructing image data of a CT apparatus in a dual source wide volume mode according to an embodiment of the present disclosure.
Fig. 8 shows a diagram of an x-ray beam of the first x-ray source in the xy plane of a rectangular coordinate system.
Fig. 9 shows a graphical representation of the x-ray beam of the first x-ray source in the yz-plane of the rectangular coordinate system.
Wherein, the reference numerals are as follows:
100: a CT device;
101: a housing;
103: a first subsystem;
105: a second subsystem;
107: an actuator;
1031: a first x-ray source;
1032: a first beam limiter;
1033: a first detector;
1051: a second x-ray source;
1052: a second beam limiter;
1053: a second detector;
107: an actuator;
109: a support part;
111: a connection part;
1111: a linear track;
1113: a linear bushing;
1091: a first support part
1092: A second supporting part
1071: A first actuator;
1072: a second actuator;
S1-S9: and (3) step (c).
Detailed Description
The following description of the technical solutions in the embodiments of the present disclosure will be made clearly and completely with reference to the accompanying drawings in the embodiments of the present disclosure, and it is apparent that the described embodiments are only some embodiments of the present disclosure, not all embodiments. All other embodiments, which can be made by one of ordinary skill in the art without inventive effort, based on the embodiments in this disclosure, shall fall within the scope of the present disclosure.
The present disclosure provides a CT apparatus. Fig. 1 illustrates a block diagram of a CT apparatus according to an embodiment of the present disclosure, fig. 2 illustrates one specific structure of the CT apparatus according to an embodiment of the present disclosure, and fig. 3 illustrates another specific structure of the CT apparatus according to an embodiment of the present disclosure. For simplicity, only the components related to the inventive point are schematically shown in fig. 2 and 3, and the illustration of the components unrelated to the inventive point is omitted.
A CT apparatus according to an embodiment of the present disclosure will be described below with reference to fig. 1 to 3.
As shown in fig. 1, a CT apparatus 100 according to an embodiment of the present disclosure includes a housing 101, a first subsystem 103, a second subsystem 105, and an actuator 107.
Specifically, as shown in fig. 2 and 3, the housing 101 is a cylindrical structure that is rotatable about its axis. The housing 101 is typically made of an aluminum casting, but the present disclosure is not limited thereto and any material having sufficient strength may be used to form the housing 101.
The first subsystem 103 is disposed within the housing 101 and includes a first x-ray source 1031 and a first detector 1033, the first x-ray source 1031 and the first detector 1033 being disposed on an inner wall of the housing 101 in diametrically opposed relation. Specifically, the line between the first x-ray source 1031 and the first detector 1033 intersects the axis of the cylindrical housing 101, i.e., the first x-ray source 1031 and the first detector 1033 are disposed on an inner diameter of the cylindrical housing 101. The first x-ray source 1031 and the first detector 1033 may be fixed to an inner wall of the housing 101.
The first x-ray source 1031 may be, for example, an x-ray tube, and the first detector 1033 detects x-rays emitted from the first x-ray source 1031 and sends the detected data to a processor for subsequent processing.
As shown in fig. 2 and 3, the first subsystem 103 may optionally further include a first beam limiter 1032 disposed between the first x-ray source 1031 and the first detector 1033 proximate to the first x-ray source 1031 side. The first beam limiter 1032 limits x-rays emitted from the first x-ray source 1031 before the x-rays are detected by the first detector 1033, thereby further improving CT image quality. The first beam limiter 1032 may be an x-ray tube beam limiter.
The second subsystem 105 is disposed within the housing 101 and includes a second x-ray source 1051 and a second detector 1053, the second x-ray source 1051 and the second detector 1053 being disposed diametrically opposite on an inner wall of the housing 101. In particular, the line between the second x-ray source 1051 and the second detector 1053 intersects the axis of the cylindrical housing 101, i.e., the second x-ray source 1051 and the second detector 1053 are disposed on the other inner diameter of the cylindrical housing 101. In the embodiment of the present disclosure, the inner diameters of the first x-ray source 1031 and the first detector 1033 are preferably perpendicular to the inner diameters of the second x-ray source 1051 and the second detector 1053, but the present disclosure is not limited thereto, and the inner diameters of the first x-ray source 1031 and the first detector 1033 and the inner diameters of the second x-ray source 1051 and the second detector 1053 may be at other angles, for example, in the range of 85 degrees to 95 degrees.
The second x-ray source 1051 may be, for example, an x-ray tube, and the second detector 1053 detects x-rays emitted from the second x-ray source 1051 and sends the detected data to a processor for subsequent processing.
As shown in fig. 2 and 3, the second subsystem 105 may optionally further include a second beam limiter 1052 disposed between the second x-ray source 1051 and the second detector 1053 proximate to the second x-ray source 1051. The second beam limiter 1052 limits x-rays emitted from the second x-ray source 1051 before they are detected by the second detector 1053, thereby further improving CT image quality. The second beam limiter 1052 may be an x-ray tube beam limiter.
An actuator 107 is disposed within the housing 101 and is configured to be able to move the second subsystem 105 relative to the first subsystem 103 in an axial direction of the housing 101. The actuator 107 may be a linear actuator.
As shown in fig. 2 and 3, the CT apparatus 100 may further include a support portion 109 and a connection portion 111.
The support 109 is disposed between the inner walls of the housing 101 along the direction of the line connecting the second x-ray source 1051 and the second detector 1053 (i.e., the other inner diameter direction of the housing 101). A second x-ray source 1051 and a second beam limiter 1052 are disposed at one end of the support 109 and proximate to an inner wall of the housing 101. The second probe 1053 is provided at the other end of the support portion 109 and is close to the inner wall of the housing 101.
The connection portion 111 connects the support portion 109 to the inner wall of the housing 101. The support portion 109 slides along the axial direction of the housing 101 via the connection portion 111. The actuator 107 is connected to the support 109 and configured to drive the support 109 to slide along the axial direction of the housing 101.
One particular mounting arrangement for the support, connection, actuator is shown in figure 2.
Specifically, as shown in fig. 2, the support portion 109 is a plate-like structure with a hole in the center, the connection portions 111 connect the support portion 109 to the inner wall of the housing at four corners of the plate-like structure, and the actuator 107 is connected to the support portion 109 on the second probe 1053 side.
The connection 111 may include a linear track 1111 and a linear bushing 1113. The linear rail 1111 is fixed to an inner wall of the housing along an axial direction of the housing 101, the linear bushing 1113 is fixed to a corner edge of the support portion 109 along the axial direction of the housing 101, and the linear bushing 1113 is sleeved on the linear rail 1111, so that the support portion 109 can move along the axial direction of the housing 101 under the driving of the actuator 107, and the relative movement of the second subsystem 105 and the first subsystem 103 in the axial direction of the housing 101 is realized.
The mounting arrangement of the support portion, the connection portion, and the actuator is not limited to the above-described form. Another form of mounting arrangement for the support, connection, actuator is shown in fig. 3.
Specifically, as shown in fig. 3, the support 109 includes a first support 1091 and a second support 1092 which are diametrically opposed and are provided separately, that is, there is no portion of the support 109 in the central portion of the housing 101. The first support portion 1091 and the second support portion 1092 are both disposed near the inner wall of the housing 101.
The actuator 107 includes a first actuator 1071 and a second actuator 1072.
The first support 1091 and the second support 1092 are each plate-like structures. The first support 1091 has two linear bushes 1113 at both corner edges of its plate-like structure near the inner wall of the housing 101, respectively, the two linear bushes 1113 are respectively fitted over two linear rails 1111 fixed to the inner wall of the housing 101 in the axial direction of the housing 101, and the first actuator 1071 is provided on the first support 1091 near the center portion side of the housing 101, and is capable of driving the first support 1091 to slide in the axial direction of the housing 101. The second support 1091 has two linear bushes 1113 at both corner edges of its plate-like structure near the inner wall of the housing 101, respectively, the two linear bushes 1113 are respectively fitted over two linear rails 1111 fixed to the inner wall of the housing 101 in the axial direction of the housing 101, and the second actuator 1072 is provided on the second support 1092 near the center portion side of the housing 101, and is capable of driving the second support 1092 to slide in the axial direction of the housing 101.
The second x-ray source 1051 and the second beam limiter 1052 are disposed on the first support 1091 and the second detector 1053 is disposed on the second support 1092. The first and second actuators 1071, 1072 are synchronously controlled to maintain the second x-ray source 1051, the second beam limiter 1052, and the second detector 1053 of the moved second subsystem 105 in alignment.
The widths of the first probe 1033 and the second probe 1053 in the axial direction of the housing 101 are preferably the same, and may be, for example, 6cm to 8cm each. However, the disclosure is not limited thereto, and the widths of the first probe 1033 and the second probe 1053 in the axial direction of the housing 101 may be different and may be selected as needed.
In the above embodiment, an example in which the connection portion is constituted by the linear rail and the linear bushing was described, but the present disclosure is not limited thereto, and the connection portion may be constituted by the linear rail and, for example, a double V-shaped bearing. With this structure, the second subsystem can perform accurate linear movement in the axial direction of the housing, while such a structure can withstand loads in various directions.
In the above embodiments, the movement of the second subsystem with respect to the first subsystem in the axial direction of the housing was described using the linear actuator, but the present disclosure is not limited thereto, and the second subsystem may be moved in the axial direction of the housing with respect to the first subsystem by a screw, a hydraulic drive, or the like.
In the above embodiments, although not specifically described, it should be noted that the circular opening in the center portion of the cylindrical housing in fig. 2 and 3 represents an opening through which an inspection object is fed into or removed from the CT apparatus at the time of CT inspection, and a circular plate having the circular opening may be used to support other components of the CT apparatus. In addition, the first subsystem may be connected to the inner wall of the housing by means of support ribs not shown in the figures. Since the inventive point of the present disclosure is not the circular plate and the supporting rib, the circular plate and the supporting rib are not described in detail.
In order to better understand the present disclosure, an operation mode switching of the CT apparatus according to an embodiment of the present disclosure is described in detail below. Fig. 4 shows a graph of the distance between the first and second probes as the actuator is driven. Fig. 5 is an x-ray beam configuration diagram illustrating a CT apparatus according to an embodiment of the present disclosure operating in a dual source mode, and fig. 6 is an x-ray beam configuration diagram illustrating a CT apparatus according to an embodiment of the present disclosure operating in a dual source wide body mode.
Hereinafter, for convenience of description, the axial direction of the housing 101 is described as a z-direction, widths of the first and second detectors in the z-direction in the CT apparatus are described as z-coverage and assuming that they are equal, and a plane in the radial direction of the housing 101 is described as a phi plane, wherein the z-direction is perpendicular to the phi plane.
In the CT apparatus according to the embodiment of the present disclosure, the distance between the first subsystem 103 and the second subsystem 105 in the z-direction may be changed by moving the second subsystem 105 by an actuator.
Fig. 4 shows that as the actuator is driven, the distance between the first detector 1033 in the first subsystem 103 and the second detector 1053 in the second subsystem 105 changes in the z-direction. Fig. 4 (a) shows that the distance in the z-direction between the first probe 1033 and the second probe 1053 is smaller than the z-coverage, and the first probe 1033 and the second probe 1053 overlap in part in the z-direction coverage; fig. 4 (B) shows that the distance between the first detector 1033 and the second detector 1053 in the z-direction is greater than the z-coverage, the first detector 1033 and the second detector 1053 being spaced apart in the z-direction; fig. 4 (C) shows that the distance between the first detector 1033 and the second detector 1053 in the z direction is equal to the z coverage, and the first detector 1033 and the second detector 1053 are just connected in the z direction, when the CT apparatus is said to be in the dual-source wide-volume mode; fig. 4 (D) shows that the distance between the first detector 1033 and the second detector 1053 in the z direction is 0, and the CT apparatus is said to be in the dual source mode.
The CT apparatus can be switched between the dual source mode and the dual source wide body mode by driving the actuator as needed.
For example, in clinical scans, if a patient is severely arrhythmic, a CT device with high temporal resolution is required to image the patient's heart with high quality. At this time, the CT apparatus may be switched to the dual source mode shown in (D) of fig. 4.
As shown in fig. 5, in the dual source mode, the first detector 1033 of the first subsystem and the second detector 1053 of the second subsystem of the CT apparatus are co-located in the z-direction, and the x-ray beam a from the first x-ray source 1031 and the x-ray beam B from the second x-ray source 1051 are on the same phi-plane, thereby imaging the same slice region of the heart.
Because the first subsystem and the second subsystem are vertically arranged on the same phi plane, compared with a single-source CT device which needs to scan 180 degrees to finish scanning of one slice part, the CT device according to the embodiment of the disclosure can finish scanning of one slice part only by scanning 90 degrees in a double-source mode, so that the time resolution is 2 times that of the single-source CT device. In the dual source mode, a high quality CT image can be obtained with high temporal resolution.
For example, in clinical scanning, if the scanning performed is an enhanced scanning, the scanning should be performed in the presence of a contrast agent, and in order to avoid artifacts in the CT image due to simultaneous movement of the contrast agent and the scanning bed, it is desirable to not move the scanning bed as much as possible, in which case the CT apparatus according to the present disclosure may be switched to the dual source wide body mode shown in fig. 4 (C).
As shown in fig. 6, in the dual-source wide-volume mode, the first detector 1033 of the first subsystem and the second detector 1053 of the second subsystem of the CT apparatus are connected right back and forth in the z direction, and the x-ray beam a emitted by the first x-ray source 1031 and the x-ray beam B emitted by the second x-ray source 1051 are continuously irradiated right to the examination object in the z direction, so that the examination object can be scanned and imaged in a wide imaging area.
In the dual source wide body mode, since the first subsystem and the second subsystem are vertically disposed on different phi planes, the first and second x-ray sources 1031 and 1051 are respectively used to emit scanning x-rays to the first and second detectors 1033 and 1053 having a narrow z-coverage (e.g., 6cm to 8 cm) with respect to the single source wide body CT apparatus (the z-coverage is 12cm to 16 cm), thereby realizing scanning in the z-direction with a wide z-coverage and reducing cone beam artifacts caused by the wide z-coverage, so that a high quality CT image can be obtained with a wide z-coverage.
The CT apparatus according to embodiments of the present disclosure may provide at least two modes of operation, a dual source mode and a dual source wide body mode, which may provide a higher temporal resolution than a single source wide body CT apparatus, and a wider z-coverage than any existing dual source CT apparatus.
In addition, when the CT apparatus according to the present disclosure operates in the dual source wide body mode, the two subsystems operate with different scan parameters, and since the cone angle of the two subsystems is half that of the single source wide body CT apparatus having the same z-coverage, cone beam artifacts are reduced, and spiral scanning can be performed in the all z-coverage mode.
Although the mode in which the first detector 1033 and the second detector 1053 are just connected in the z-direction in fig. 4 (C) is referred to as the CT apparatus being in the dual-source wide mode, in a broad sense, the CT apparatus may be referred to as the dual-source wide mode as long as the first detector 1033 and the second detector 1053 are offset by a certain distance in the z-direction, for example, all of (a) - (C) of fig. 4 may be referred to as the CT apparatus being in the dual-source wide mode.
The present disclosure also provides a method of constructing image data of a CT apparatus in a dual source wide volume mode. Fig. 7 illustrates a method of constructing image data of a CT apparatus in a dual source wide volume mode according to an embodiment of the present disclosure. As shown in fig. 7, a method of constructing image data of a CT apparatus in a dual source wide volume mode includes:
s1: determining a predetermined point on an axis as a rotation center point, taking a straight line passing through the rotation center point and perpendicular to the axis direction of the shell as a first axis, taking a straight line passing through the rotation center point and perpendicular to the first axis and the axis direction as a second axis, and taking the axis as a third axis to establish a rectangular coordinate system;
S2: acquiring a distance from the first x-ray source to a center point of rotation in a plane formed by the first axis and the second axis;
S3: acquiring a first angle sandwiched between a first axis and a line connecting the first x-ray source and a center point of rotation in the plane;
s4: acquiring a first coordinate representation of the first x-ray source in a rectangular coordinate system with respect to the detection site moving in the axial direction using the first angle and the distance;
S5: acquiring a second angle between a line connecting the first x-ray source and the rotation center point in the plane and a predetermined x-ray emitted from the first x-ray source in the plane, the predetermined x-ray being an x-ray passing through the detection site;
s6: acquiring a third angle, the third angle being a maximum x-ray beam angle of an x-ray beam emitted from the first x-ray source that is received by the first detector in a direction of a third axis;
S7: acquiring a second coordinate representation in a rectangular coordinate system of a point in the plane at a predetermined length from the first x-ray source on a predetermined x-ray emitted from the first x-ray source, using the first coordinate representation, the second angle, and the third angle;
S8: acquiring a third coordinate representation in a rectangular coordinate system of a point in the plane at the predetermined length from the second x-ray source on x-rays emitted from the second x-ray source, using the second coordinate representation, the predetermined angle, and the predetermined distance; and
S9: image data of the detection site is constructed using the second coordinate representation and the third coordinate representation.
Fig. 8 shows a diagram of an x-ray beam of the first x-ray source in the xy plane of a rectangular coordinate system. Fig. 9 shows a graphical representation of the x-ray beam of the first x-ray source in the yz-plane of the rectangular coordinate system. A method of constructing image data of a CT apparatus in a dual source wide body mode according to an embodiment of the present disclosure will be described in detail with reference to fig. 7 to 9. In the following description, it is assumed that the first subsystem and the second subsystem of the CT apparatus are identical in structure for simplicity.
Here, the axis direction of the housing of the CT apparatus is the traveling direction in which the detection object is fed into or removed from the CT apparatus, and if the patient lies on the detection bed of the CT apparatus, the right hand direction of the patient is the direction of the first axis, the direction in which the face of the patient faces is the direction of the second axis, and the direction from the head to the foot of the patient is the direction of the third axis. When the dual-source wide body mode is operated, the first subsystem and the second subsystem rotate around the detection part of the patient by taking the third axis as a rotation axis, and the rotation center point is any point on the third axis, for example, an intersection point of a plane of the first subsystem and the third axis. Hereinafter, for convenience of description, the first axis is also referred to as an x-axis, the second axis is referred to as a y-axis, the third axis is referred to as a z-axis, and the intersection of the x-axis, the y-axis, and the z-axis is referred to as a rotation center point O.
Since the first and second subsystems of the CT apparatus have the same structure, only the positions are shifted in the xy plane and the z axis direction, only the relationship between the first x-ray source of the first subsystem and the x-axis and the y-axis is shown in the xy plane shown in fig. 8, and only the relationship between the first x-ray source of the first subsystem and the y-axis and the z-axis is shown in the yz plane shown in fig. 9, and the relationship between the second x-ray source of the second subsystem and the x-axis, the y-axis and the z-axis is similar.
In fig. 8, the x-axis and the y-axis intersect at a rotation center point O, the first x-ray source is represented by a point F in the xy-plane, R F represents the distance from the first x-ray source to the rotation center point O in the xy-plane, the angle α represents the angle between the line between the first x-ray source and the rotation center point O in the xy-plane and the x-axis, the x-ray L' represented by an arrow-headed ray in the figure is a predetermined x-ray L emitted from the first x-ray source through the detection site in the xy-plane, and it is to be noted here that the expression "predetermined x-ray L emitted from the first x-ray source through the detection site in the xy-plane" represents the projection of the predetermined x-ray L emitted from the first x-ray source through the detection site on the xy-plane. The projected x-rays L' are at an angle β to a line from the first x-ray source and the center of rotation O.
The distance R F of the first x-ray source from the center of rotation O in the xy plane and the angle alpha of the line between the first x-ray source and the center of rotation O to the x-axis are obtained.
Using the distance R F and the angle a, a first coordinate representation of the first x-ray source in an xyz rectangular coordinate system with respect to the detection site moving in the z direction can be obtained.
In the CT apparatus, the first x-ray source of the first subsystem rotates around the detection site moving in the z direction only with the z axis as the rotation axis, and the first x-ray source does not move in the z direction, but from the view point of the detection site, the position of the first x-ray source in the z direction changes with the movement of the detection site in the z direction. The expression "first x-ray source in xyz rectangular coordinate system with respect to the detection site moving in the z direction" mentioned above means coordinates of the first x-ray source in xyz rectangular coordinate system from the view angle of the detection site moving in the z direction. Like expressions herein mean like meanings.
As shown in FIG. 8, the first coordinate representation may include a coordinate representation of the first x-ray source relative to the detection site in the x-axisCoordinate representation on y-axis/>And coordinate representation/>, on the z-axisI.e.
Wherein z rot represents the distance the detection portion moves in the z direction for one rotation of the CT apparatus.
An angle β between a line of the first x-ray source and the rotation center point O in the xy plane and a predetermined x-ray L emitted from the first x-ray source through the detection site in the xy plane, that is, an angle β between a line of the first x-ray source and the rotation center point O and the projection x-ray L' in the xy plane is obtained, and a maximum x-ray beam angle θ cone of an x-ray beam emitted from the first x-ray source and received by the first detector in the z direction is obtained.
A second coordinate representation of the predetermined x-ray L in a rectangular coordinate system relative to the detection site at a point P A in the xy plane at a predetermined length L from the first x-ray source is obtained using the first coordinate representation, the angle β, and the maximum x-ray beam angle θ cone.
The second coordinate representation includes a coordinate representation of a point P A on the predetermined x-ray L in the xy-plane a predetermined length L from the first x-ray source relative to the detection portion in the x-axisCoordinate representation on y-axis/>And coordinate representation/>, on the z-axisI.e.
Wherein q is a proportionality coefficient in the range of-1 to 1.
In the present disclosure, the x-ray beams of the first x-ray source and the second x-ray source are fan-shaped in the xy-plane, have a certain width in the z-direction and are cone-shaped, so that there are a plurality of x-rays in the x-ray cone-shaped in the z-direction which are received by different positions of the first detector in the z-direction at points in the xy-plane which are a predetermined length l from the first x-ray source.
As shown in fig. 9, in the yz plane, a predetermined x-ray L emitted from a first x-ray source (point F) at a point P A in the xy plane, which is a predetermined length L from the first x-ray source, is indicated by a dotted line, P 1 is a position on the first detector at which the predetermined x-ray L is received, Z 1 is a distance from the y-axis at a position P 1, P 2 is a detection position at the most edge of the first detector, Z 2 is a distance from the y-axis at a position P 2, and q is a ratio between Z 1 and Z 2, which is generally in the range of-1 to 1.
Using a second coordinate representation, a predetermined angle being formed between the first subsystem and the second subsystemAnd the first subsystem and the second subsystem are offset a predetermined distance d shift in the z-direction, acquiring a third coordinate representation in a rectangular coordinate system of a point on an x-ray emitted from the second x-ray source that is within the xy-plane a predetermined length l from the second x-ray source relative to the detection site.
The third coordinate representation includes a coordinate representation in the x-axis of a point on a predetermined x-ray emitted from the second x-ray source that is a predetermined length l from the second x-ray source in the xy-plane with respect to the detection siteCoordinate representation on the y-axisAnd coordinate representation/>, on the z-axisI.e.
Image data of the examination region can be constructed using the second coordinate representation for the first subsystem and the third coordinate representation for the second subsystem.
Preferably, the second coordinate representation and the third coordinate representation may also be spatially transformed according to the first relationship and the second relationship, respectively, to make the subsequent data processing more efficient.
As shown in fig. 8, for the first subsystem, the first relationship includes: θ=α+β, p=r F sin β, and substituting the first relation into the second coordinate representation results in:
for the second subsystem, the second relationship includes: p=r F sin β is obtained by substituting the second relation into the third coordinate representation:
That is, the coordinate representation in the rectangular coordinate system is converted into the coordinate representation in the p- θ space using the first relationship and the second relationship. In the prior art, since various mature methods and algorithms for processing data exist in the p-theta space, the efficiency of subsequent data processing can be improved through the above spatial transformation.
In this way, image data suitable for a CT apparatus in a dual-source wide-volume mode is constructed.
According to an embodiment of the present disclosure, there is provided a computer-readable storage medium having stored thereon a program which, when executed, causes a processor to perform the above-described method of constructing an image of a CT apparatus in a dual-source wide-volume mode.
In the foregoing embodiments of the disclosure, the descriptions of the embodiments are emphasized, and in part, reference is made to the related descriptions of other embodiments.
The foregoing is merely a preferred embodiment of the present disclosure, 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 disclosure, which are intended to be comprehended within the scope of the present disclosure.

Claims (8)

1. A method of constructing image data of a CT apparatus, the CT apparatus (100) comprising: a cylindrical housing (101) rotatable about an axis thereof; a first subsystem (103) disposed within the housing (101) comprising a first x-ray source (1031) and a first detector (1033), wherein the first x-ray source (1031) and the first detector (1033) are disposed radially opposite on an inner wall of the housing (101); a second subsystem (105) disposed within the housing (101) and including a second x-ray source (1051) and a second detector (1053), wherein the second x-ray source (1051) and the second detector (1053) are slidably disposed radially opposite to each other on an inner wall side of the housing (101), and a line direction of the first x-ray source (1031) and the first detector (1033) forms a predetermined angle with a line direction of the second x-ray source (1051) and the second detector (1053); and an actuator (107) disposed within the housing (101) and configured to be able to move the second subsystem (105) relative to the first subsystem (103) in an axial direction of the housing (101), wherein, in a case where the second subsystem (105) is offset a predetermined distance in the axial direction relative to the first subsystem (103), the method comprises:
determining a predetermined point on the axis as a rotation center point, taking a straight line passing through the rotation center point and perpendicular to the axis direction of the shell as a first shaft, taking a straight line passing through the rotation center point and perpendicular to the first shaft and the axis direction as a second shaft, and taking the axis as a third shaft to establish a rectangular coordinate system;
acquiring a distance from the first x-ray source to the rotation center point in a plane formed by the first axis and the second axis, and acquiring a first angle sandwiched between a line connecting the first x-ray source and the rotation center point in the plane and the first axis;
acquiring a first coordinate representation of the first x-ray source in the rectangular coordinate system relative to the detection site using the first angle and the distance;
Acquiring a second angle sandwiched between a line connecting the first x-ray source and the rotation center point in the plane and a predetermined x-ray emitted from the first x-ray source in the plane, wherein the predetermined x-ray is an x-ray passing through the detection site, and acquiring a third angle, which is a maximum x-ray beam angle of an x-ray beam emitted from the first x-ray source and received by the first detector in a direction of the third axis;
Acquiring a second coordinate representation of a point in the rectangular coordinate system relative to the detection site at a predetermined length in the plane from the first x-ray source on a predetermined x-ray emitted from the first x-ray source using the first coordinate representation, the second angle, and the third angle;
acquiring a third coordinate representation in the rectangular coordinate system of a point in the plane at the predetermined length from the second x-ray source on x-rays emitted from the second x-ray source, using the second coordinate representation, the predetermined angle, and the predetermined distance; and
And constructing image data of the detection part by using the second coordinate representation and the third coordinate representation.
2. The method according to claim 1, wherein the method further comprises:
spatially transforming the second coordinate representation using the first relationship; and
And performing spatial transformation on the third coordinate representation by using the second relation.
3. The method of claim 2, wherein the step of determining the position of the substrate comprises,
The first coordinate representation includes a coordinate representation of the first x-ray source relative to the detection site on a first axisCoordinate representation on the second axis/>And a coordinate representation/>, on a third axis
Wherein, using the first angle and the distance, obtaining a first coordinate representation of the first x-ray source relative to the detection site in the rectangular coordinate system comprises calculating a first coordinate representation according to the following formula:
Wherein R F represents a distance from the first x-ray source to the rotation center point in the plane, α represents the first angle between a line connecting the first x-ray source and the rotation center point in the plane and the first axis, and z rot represents a distance by which the detection portion moves in the axis direction for one rotation of the CT apparatus.
4. The method of claim 3, wherein the step of,
The second coordinate representation includes a coordinate representation of a point on the predetermined x-ray in the plane at a predetermined length from the first x-ray source relative to the detection site on a first axisCoordinate representation on the second axisAnd a coordinate representation/>, on a third axis
Wherein using the first coordinate representation, the second angle, and the third angle, obtaining a second coordinate representation of a point in the rectangular coordinate system relative to the detection site at a predetermined length in the plane from the first x-ray source on a predetermined x-ray emitted from the first x-ray source includes calculating a second coordinate representation as follows:
Wherein beta is the second angle, Is the third angle, l represents a predetermined length from the first x-ray source over a predetermined x-ray emitted from the first x-ray source in the plane, q is a scaling factor in the range of-1 to 1.
5. The method of claim 4, wherein the step of determining the position of the first electrode is performed,
The third coordinate representation includes a coordinate representation of a point on the first axis relative to the detection site at the predetermined length from the second x-ray source in the plane on a predetermined x-ray emitted from the second x-ray sourceCoordinate representation on the second axis/>And a coordinate representation/>, on a third axis
Wherein using the second coordinate representation, the predetermined angle, and the predetermined distance, obtaining a third coordinate representation of a point in the rectangular coordinate system at the predetermined length from the second x-ray source in the plane on x-rays emitted from the second x-ray source relative to the detection site comprises calculating the third coordinate representation according to the following formula:
wherein, D shift is the predetermined distance for the predetermined angle.
6. The method of claim 5, wherein the step of determining the position of the probe is performed,
The first relationship includes: θ=α+β, p=r F sin β,
Spatially transforming the second coordinate representation using the first relationship comprises: substituting the first relation into a coordinate representationCoordinate representation/>And coordinate representation/>To obtain:
7. The method of claim 5, wherein the step of determining the position of the probe is performed,
The second relationship includes:p＝RFsinβ，
spatially transforming the third coordinate representation with the second relationship includes substituting the second relationship into the coordinate representation Coordinate representation/>And coordinate representation/>To obtain:
8. a computer readable storage medium having stored thereon a program which, when executed, causes a processor to perform the method of any of claims 1 to 7.
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