Detector and radiation source integrated static CT imaging system and imaging method

Abstract

The invention relates to a static CT imaging system and imaging method integrating a detector and a radiation source, the static CT imaging system integrating the detector and the radiation source is provided with more than three integrated rings, all the integrated rings are stacked from front to back, and the central axes of all the integrated rings are overlapped; each integrated ring consists of a detection ring and a ray ring; the ray ring is formed by encircling a plurality of ray bulb tubes; the detection ring is formed by splicing a plurality of arc-shaped detectors, the number of the ray bulb tubes in each integrated ring is the same as that of the arc-shaped detectors, and each ray bulb tube is embedded in one arc-shaped detector; and in two adjacent integrated rings, all the ray bulb tubes of one integrated ring and all the ray bulb tubes of the other integrated ring are distributed in a staggered manner. According to the invention, a wider Z-axis coverage range can be realized, the influence of taper angle artifacts can be effectively reduced, the CT imaging precision and quality can be improved, the space occupation volume can be effectively reduced, and the imaging quality can be improved.

Description

Technical Field

[0001] The present invention relates to the technical field of static CT real-time imaging, and in particular to a static CT imaging system integrating a detector and a ray source and an imaging method thereof. Background Art

[0002] Computed tomography (CT) is an imaging technique that uses X-rays to collect multi-angle projections of an object and then uses reconstruction algorithms to generate cross-sectional images of the object's interior. The basic architecture of a CT imaging system typically consists of an X-ray source, a rotating mechanical structure, a detector array, and an image reconstruction module. During a CT scan, the X-ray source rotates around the object at multiple angles to collect images. The detectors receive the X-ray signals, which have been attenuated by the object, and convert them into electrical signals for input into a computer. The computer then divides the selected slice into uniform cubes (voxels). After calculating the scan information layer by layer, the X-ray attenuation coefficient or absorption coefficient of each voxel is calculated and arranged into a digital voxel matrix. The digital information in the voxel matrix is then converted into pixels of varying grayscale, and a reconstruction algorithm is used to generate a two-dimensional or three-dimensional cross-sectional image. Traditional CT imaging systems primarily utilize a single X-ray source and a single detector array, acquiring CT data through mechanical rotation. While this system architecture is relatively simple and cost-effective, it has certain limitations in practical applications, such as slow imaging speed and low temporal resolution. This makes it difficult to meet the requirements of real-time imaging, especially in dynamic and high-speed imaging.

[0003] Chinese patent application No. 201410425061.2 discloses a static real-time CT imaging system. This system primarily comprises an annular X-ray detector, an annular scanning X-ray source, and a scan timing controller. During scanning, the annular scanning X-ray source does not require significant rotation. This static real-time CT imaging system effectively reduces signal smearing and overlap crosstalk during high-speed rotation. Through electronic control, the X-ray irradiation position can be sequentially switched, thereby increasing the scanning speed by dozens of times and enabling the acquisition of dynamic three-dimensional images. Furthermore, the system uses an X-ray detector to acquire absorption and energy data, enabling real-time data reconstruction. To meet the practical application requirements of wide-field imaging, World Patent No. WO2018153382A1 discloses a static real-time CT imaging system and imaging method adapted to wide-field imaging requirements. This static real-time CT imaging system comprises an annular multi-focus X-ray source and an annular photon detector. The annular multi-focus X-ray source comprises multiple scanning X-ray sources evenly distributed along a circumference, while the annular photon counting detector comprises several photon counting detector units arranged in a ring. Each scanning X-ray source sequentially emits wide-beam X-rays, which penetrate the object being measured and are precisely projected onto corresponding photon-counting detector units. This static real-time CT imaging system utilizes a non-opposing geometric imaging mode. The detector units operate in an overlapping, collaborative manner, transmitting the collected exposure data to a data processing module, where real-time image reconstruction and intuitive visualization are performed. Leveraging the wide-beam X-rays emitted by the annular multi-focus X-ray source and the unique design of non-opposing geometric imaging between the source and detectors, the system effectively meets the requirements of large-field-of-view imaging. Furthermore, Chinese patent application No. 201910865387.X discloses a static real-time CT imaging system equipped with paired X-ray rings and an imaging method thereof. This static real-time CT imaging system features a X-ray ring on each side of the detector ring. By reconstructing the projection areas of the two X-ray rings separately, two independent FOV reconstruction regions are formed. However, a gap exists between these two FOV regions. While this gap can be filled with supplementary scans in the helical scanning mode, it cannot be completely filled in the single axial scanning mode. Therefore, this static real-time CT imaging system has certain limitations in application scenarios where the scanning coverage is to be expanded.

[0004] In the existing technology, due to the fixed nature of static CT, the optimal and most space-saving design is to evenly distribute detectors on a circular ring. However, this layout poses a challenge to the arrangement design of detectors and X-ray sources in static CT systems: in order to install a full circle of X-ray tubes, the installation space of the detectors will be significantly disturbed. In addition, when a full circle of detectors is synchronously set up opposite the X-ray tube, the installation space of other components will be squeezed, leading to difficulties in spatial layout. At the same time, the current static CT system has a small coverage area when scanning patients, which limits its application scenarios.

[0005] Therefore, in view of the shortcomings of the existing technology, it is necessary to provide a static CT imaging system and system that integrates a detector and a radiation source to solve the shortcomings of the existing technology. Summary of the Invention

[0006] The first objective of the present invention is to overcome the shortcomings of the prior art and provide a static CT imaging system with an integrated detector and radiation source. This static CT imaging system with an integrated detector and radiation source can achieve a wider Z-axis coverage range, effectively reduce the impact of cone-angle artifacts, improve CT imaging accuracy and quality, and effectively reduce the space occupied by the device while improving imaging quality.

[0007] The above-mentioned purpose of the present invention is achieved through the following technical measures:

[0008] Provided is a static CT imaging system integrating a detector and a ray source, which is provided with three or more integrated rings, all of which are stacked from front to back, and the central axes of all the integrated rings overlap.

[0009] Each integrated ring consists of a detection ring and a ray ring.

[0010] The radiation ring is formed by surrounding a plurality of radiation tubes.

[0011] The detection ring is formed by splicing together a plurality of arc-shaped detectors. In each integrated ring, the number of the ray tubes is the same as the number of the arc-shaped detectors, and each ray tube is embedded in an arc-shaped detector.

[0012] In two adjacent integral rings, all the radiation tubes of the integral ring and all the radiation tubes of the other integral ring are staggered in distribution.

[0013] The central axis of the integrated ring is defined as the Z axis of the static CT imaging system.

[0014] Three adjacent integral rings are defined as an integral ring group, and the ray rings in the same integral ring group are defined as a left ray ring, a middle ray ring and a right ray ring respectively.

[0015] In the same integrated ring group, any one ray tube in the left ray ring is located between two adjacent ray tubes in the middle ray ring, and any one ray tube in the middle ray ring is located between two adjacent ray tubes in the right ray ring.

[0016] Each detection ring is a closed circular ring structure formed by splicing an odd number of arc-shaped detectors, and the arc-shaped detectors are evenly distributed in the detection ring.

[0017] In each integrated ring, a straight line is drawn from the center of any ray tube, passing through the center of the integrated ring, and then extending to the other side of the integrated ring, where the straight line passes through an arc detector.

[0018] An opening is provided in the middle of each arc-shaped detector, and the ray tube is embedded in the corresponding opening.

[0019] In the same integrated ring group, the position of the radiation tube of the left radiation ring is exactly the same as the position of the radiation tube of the right radiation ring.

[0020] Preferably, the arc-shaped detector is a photon counting detector or an integrating detector.

[0021] Any straight line perpendicular to the Z axis and passing through the Z axis is defined as the X axis.

[0022] Each integral ring is provided with a beam limiting ring group for limiting the projection area of the ray source tube. The beam limiting ring group and the corresponding integral ring are in a concentric circle structure, and the beam limiting ring is located inside the corresponding integral ring.

[0023] Each beam limiting ring group is composed of a Z-direction beam limiting ring and an X-direction beam limiting ring. In each integrated ring, the Z-direction beam limiting ring and the X-direction beam limiting ring are both concentric circle structures with the corresponding integrated ring.

[0024] Preferably, the Z-direction beam limiting ring is an annular structure composed of a plurality of first beam limiters.

[0025] Preferably, the X-direction beam limiting ring is a ring structure composed of a plurality of second beam limiters.

[0026] The projection area formed after the X-rays generated by each ray tube pass through the corresponding Z-direction beam limiting ring and the corresponding X-direction beam limiting ring is a rectangular projection area.

[0027] The static CT imaging system with integrated detector and ray source of the present invention is further provided with a timing controller, and the timing controller is connected to the detection ring and the ray ring respectively.

[0028] Preferably, the timing controller is used to control the focus and exposure timing of the X-ray tube and the acquisition timing of the arc detector.

[0029] The scanning mode on the Z axis is a spiral scanning mode or a step scanning mode.

[0030] A second object of the present invention is to provide an imaging method that overcomes the shortcomings of the prior art. This imaging method can achieve a wider Z-axis coverage range, effectively reduce the impact of cone angle artifacts, improve CT imaging accuracy and quality, and effectively reduce the space occupied by the volume and improve imaging quality.

[0031] The above-mentioned purpose of the present invention is achieved through the following technical measures:

[0032] An imaging method is provided, which is performed using the static CT imaging system integrating the detector and the ray source.

[0033] Three adjacent integral rings are defined as an integral ring group, and the ray rings in the same integral ring group are defined as a left ray ring, a middle ray ring and a right ray ring respectively.

[0034] The scanning methods for the same integrated ring group include the following:

[0035] First, multiple exposure cycles are performed along the Z-axis direction to obtain projection images of all X-ray tubes; each exposure cycle is for exposing any X-ray tube in the left X-ray ring, then for exposing any X-ray tube in the middle X-ray ring, and finally for exposing any X-ray tube in the right X-ray ring;

[0036] Second, all the X-ray tubes in the left X-ray ring are exposed in turn, then all the X-ray tubes in the middle X-ray ring are exposed in turn, and finally all the X-ray tubes in the right X-ray ring are exposed in turn, to obtain projection images of all the X-ray tubes;

[0037] Third, all the ray tubes in the left ray ring are exposed in turn to obtain a left ray source projection image;

[0038] Fourth, all the ray tubes in the middle ray ring are exposed in turn to obtain a projection image of the middle and side ray sources;

[0039] Fifth, all the ray tubes in the right ray ring are exposed in turn to obtain a right ray source projection image.

[0040] Preferably, the above-mentioned ray ring is a multi-energy level switching ray ring.

[0041] The imaging method of the present invention uses a first energy level at the focus of all the ray tubes in the left ray ring along the Z-axis direction, a second energy level at the focus of multiple ray tubes in the middle ray ring, and a third energy level at the focus of multiple ray tubes in the right ray ring, and the first energy level, the second energy level, and the third energy level are all different, thereby obtaining energy spectrum images of three different energy levels in one scan.

[0042] The present invention provides a static CT imaging system and imaging method with an integrated detector and radiation source, wherein the static CT imaging system with an integrated detector and radiation source is provided with three or more integrated rings, all of which are stacked from front to back, and the central axes of all the integrated rings overlap; each integrated ring is composed of a detection ring and a radiation ring; the radiation ring is surrounded by a plurality of radiation tubes; the detection ring is composed of a plurality of arc detectors spliced together, the number of radiation tubes in each integrated ring is the same as the number of arc detectors, and each radiation tube is embedded in an arc detector; in two adjacent integrated rings, all the radiation tubes of an integrated ring are staggered with all the radiation tubes of the other integrated ring; the central axis of the integrated ring is defined as the Z axis of the static CT imaging system. The beneficial effects of the present invention are: 1. The integrated ring can further reduce the space occupied by the static CT system; 2. It provides a larger scanning coverage range on the Z axis. The staggering of three or more integrated rings can achieve a wider Z-direction coverage range, further reducing cone angle artifacts. 3. Three or more integrated devices are equipped with multiple X-ray tubes, which can achieve scanning through various scanning methods to meet different scanning needs. BRIEF DESCRIPTION OF THE DRAWINGS

[0043] The present invention is further described with reference to the accompanying drawings, but the contents in the accompanying drawings do not constitute any limitation to the present invention.

[0044] Figure 1 Schematic diagram of the structure of multiple integrated rings.

[0045] Figure 2 Schematic diagram of the structure of a single integrated ring.

[0046] Figure 3 For Figure 1 Schematic diagram of the X-axis and Z-axis.

[0047] Figure 4 Schematic diagram of the structure of the arc detector and the X-ray tube.

[0048] Figure 5 Schematic diagram of the arc detector structure.

[0049] Figure 6 Schematic diagram corresponding to three integrated ring components in this embodiment.

[0050] Figure 7 Schematic diagram of the structure of the integral ring and the limiting ring group.

[0051] Figure 8 It is a partial schematic diagram of the ray tube, the Z-direction beam limiting ring and the X-direction beam limiting ring in the Z-axis direction.

[0052] Figure 9 It is a partial schematic diagram of the X-axis direction of the ray tube and the Z-direction beam limiting ring and the X-direction beam limiting ring.

[0053] Figure 10 Schematic diagram of the projection cone angle formed by the left ray ring and the right ray ring in the Z-axis direction.

[0054] Figure 11 Schematic diagram of the projection cone angle formed by the middle ray ring in the Z-axis direction.

[0055] Figure 12 Schematic diagram of the detector module on the left and right ray rings.

[0056] Figure 13 Schematic diagram of the detector module in the middle ray ring.

[0057] Figure 14 Schematic diagram of the overall static CT imaging system of the present invention.

[0058] exist Figures 1 to 14 Including:

[0059] One-piece ring 100,

[0060] Detection ring 110, arc detector 111, opening 112, detector module 113, ray ring 120, ray tube 121,

[0061] Beam limiting ring group 200,

[0062] Z-direction beam limiting ring 210, first beam limiter 211,

[0063] X-axis beam limiting ring 220, second beam limiter 221,

[0064] Fixed frame 300 , scanning bed support 400 , scanning bed 500 . DETAILED DESCRIPTION

[0065] The technical solution of the present invention is further described with reference to the following examples.

[0066] Example 1

[0067] A static CT imaging system with integrated detector and radiation source, such as Figure 1, more than three integral rings 100 are provided, all the integral rings 100 are stacked from front to back, and the central axes of all the integral rings 100 overlap.

[0068] like Figure 2 Each integral ring 100 is composed of a detection ring 110 and a ray ring 120. Figure 4 As shown. The ray ring 120 is composed of a plurality of ray tubes 121. The detection ring 110 is composed of a plurality of arc detectors 111. The number of ray tubes 121 in each integrated ring 100 is the same as the number of arc detectors 111, and each ray tube 121 is embedded in one arc detector 111. Figure 5 An opening 112 is formed in the middle of each arc-shaped detector 111 , and the X-ray tube 121 is embedded in the corresponding opening 112 .

[0069] The detection ring 110 and the ray ring 120 of the present invention form an integrated structure, which can greatly reduce the volume occupied by the static CT system.

[0070] like Figure 3 In two adjacent integrated rings 100, all the X-ray tubes 121 of one integrated ring 100 are staggered with all the X-ray tubes 121 of the other integrated ring 100. The central axis of the integrated ring 100 is defined as the Z-axis of the static CT imaging system. Any straight line perpendicular to and passing through the Z-axis is defined as the X-axis.

[0071] It should be noted that unlike existing traditional static CT architectures, such as dual detector rings or a Z-direction structure where the radiation source ring is separated from the detector ring, the dual detector ring comprises a three-ring structure in the Z-direction: a radiation source ring, a detector ring, and a radiation source ring. While maintaining the same Z-direction width for all three rings, the present invention adds at least one integrated ring 100. By embedding the radiation tube 121 within an arc-shaped detector 111 to form an integrated integrated ring 100, the present invention reduces volume and facilitates the addition of the integrated ring 100. The addition of at least one integrated ring 100 also reduces the cone angle, achieving the same exposure range as other dual-ring structures, adding more radiation sources. This reduces cone angle artifacts by reducing the X-ray cone angle emitted by the radiation source.

[0072] The static CT imaging system of the present invention can be provided with 3, 4, 5, 10, etc. The specific number of rings 100 can be determined according to actual conditions. This embodiment takes three integral rings 100 as an example to illustrate the present invention.

[0073] Three adjacent integrated rings 100 are defined as an integrated ring group, and the radiation rings 120 in the same integrated ring group are defined as a left radiation ring 120, a middle radiation ring 120, and a right radiation ring 120. In the same integrated ring group, any radiation tube 121 in the left radiation ring 120 is located between two adjacent radiation tubes 121 in the middle radiation ring 120, and any radiation tube 121 in the middle radiation ring 120 is located between two adjacent radiation tubes 121 in the right radiation ring 120. Within the same integrated ring group, the positions of the radiation tubes 121 in the left radiation ring 120 are exactly the same as those in the right radiation ring 120. Each detection ring 110 is a closed circular structure composed of an odd number of arc detectors 111, and the arc detectors 111 are evenly distributed in the detection ring 110; in each integrated ring 100, a straight line is drawn through the center of any X-ray tube 121, the straight line passes through the center of the integrated ring 100, and the straight line continues to extend to the other side of the integrated ring 100, and the arc detector 111 is passed through on the other side of the integrated ring 100.

[0074] like Figure 6 , the left radiation ring 120 of this embodiment is defined as F1, the middle radiation ring 120 as F2, and the right radiation ring 120 as F3. The detection ring 110 corresponding to the left radiation ring 120F1 is defined as the left detection ring 110d1, the detection ring 110 corresponding to the middle radiation ring 120F2 is defined as the middle detection ring 110d2, and the detection ring 110 corresponding to the right radiation ring 120F3 is defined as the right detection ring 110d3. All radiation tubes 121 in the left radiation ring 120F1 are defined as F11 to F1n, all radiation tubes 121 in the middle radiation ring 120F2 are defined as F21 to F2n, and all radiation tubes 121 in the right radiation ring 120F3 are defined as F31 to F3n. The multiple openings 112 in the left detection ring 110d1 are defined as h11 to h1n in sequence, the multiple openings 112 in the middle detection ring 110d2 are defined as h21 to h2n in sequence, and the multiple openings 112 in the right detection ring 110d3 are defined as h31 to h3n in sequence.

[0075] Due to the staggered arrangement of adjacent radiation rings 120, the radiation tubes 121 of each integrated ring 100 will not be collinear on the same axis. For example, F21 will not be collinear with F11 and F31.

[0076] It should be noted that the purpose of configuring the detector ring 110 of the present invention with an odd number of arc detectors 111 is to ensure that the radiation source exposure of each radiation tube 121 in the circular ring structure is not collinear with another radiation source, thereby directly irradiating the corresponding arc detector 111. An odd number of radiation tubes 121 are arranged in each detector ring 110, and the radiation tubes 121 in adjacent radiation rings 120 are staggered. This minimizes the impact of the openings 112 of the arc detectors 111, thereby achieving the largest field of view (FOV).

[0077] like Figure 7 Each integrated ring 100 is equipped with a beam limiting ring assembly 200 for limiting the projection area of the radiation source tube. The beam limiting ring assembly 200 forms a concentric circle structure with the corresponding integrated ring 100 and is located inside the corresponding integrated ring 100. Each beam limiting ring assembly 200 consists of a Z-direction beam limiting ring 210 and an X-direction beam limiting ring 220. In each integrated ring 100, the Z-direction beam limiting ring 210 and the X-direction beam limiting ring 220 form a concentric circle structure with the corresponding integrated ring 100 and are both located inside the corresponding integrated ring 100.

[0078] It should be noted that the present invention does not limit the order of the Z-direction beam limiting ring 210, the X-direction beam limiting ring 220, and the integrated ring 100. For example, from the outside to the inside, the integrated ring 100, the Z-direction beam limiting ring 210, the X-direction beam limiting ring 220, or the integrated ring 100, the X-direction beam limiting ring 220, the Z-direction beam limiting ring 210 can also be arranged. This embodiment is described using the integrated ring 100, the Z-direction beam limiting ring 210, and the X-direction beam limiting ring 220 as an example.

[0079] Meanwhile, the projection cone angle of the ray tube 121 of the left ray ring 120F1 is defined as a1, the projection cone angle of the ray tube 121 of the middle ray ring 120F2 is defined as a2, and the projection cone angle of the ray tube 121 of the right ray ring 120F3 is defined as a3.

[0080] like Figure 8 and Figure 9 The Z-axis beam limiting ring 210 of the present invention is a ring structure composed of a plurality of first beam limiters 211, and the X-axis beam limiting ring 220 is a ring structure composed of a plurality of second beam limiters 221. Figure 9 For each radiation source in the X-ray tube 121, only a relatively small beam limiter is needed to achieve the beam limiting effect, equivalent to an inscribed polygon in a large circle. Each side of the polygon is very short and has a large arc, so it can be nearly a straight line. To facilitate drawing, the detector is also partially approximated as a straight line.

[0081] like Figures 10 and 11The projection area formed after the X-rays generated by each ray tube 121 pass through the corresponding Z-direction beam limiting ring 210 and the corresponding X-direction beam limiting ring 220 is a rectangular projection area.

[0082] In the present invention, for the left radiation ring 120, the area detected by any radiation tube 121 on the left radiation ring 120F1 is defined as the detector module 113. The area of the detector module 113, where the line from the radiation tube 121 passes through the center of the integral ring 100 and reaches directly opposite the integral ring 100, is the detector module 113. The detector module 113 comprises the rectangular area formed by two adjacent arc-shaped detectors 111. Because the three detector rings 110 of the present invention are tightly connected along the Z-axis, data from the light source of the middle radiation ring 120F2 can be collected simultaneously by all three detector rings 110 after exposure. The multiple arc-shaped detectors corresponding to the same radiation tube 121 constitute a single detector module 113.

[0083] The detector modules 113 corresponding to the radiation tubes 121 of the left radiation ring 120F1 and the radiation tubes 121 of the right radiation ring 120F3 when they are exposed are as shown in FIG. Figure 12 As shown, there is an opening 112 of the middle detection ring 110d2 between the two detector modules 113 on the same straight line. The dotted rectangular box in the figure is the detector module 113 area; when the ray tube 121 of the middle side ray ring 120F2 is exposed, the corresponding detector module 113 is as shown in FIG. Figure 13 As shown, there are two openings 112 on both sides of a detector module 113 , namely a left detection ring 110 d 1 and a right detection ring 110 d 3 . The dotted rectangular frame in the figure represents the detector module 113 area.

[0084] Taking this embodiment as an example, when there are three integral rings 100, the number of focal points of equivalent radiation in the static CT real-time imaging system of this embodiment is twice that of a single radiation ring 120 in the prior art. Furthermore, compared to the single radiation ring 120 and dual-detector rings of the prior art, the present invention significantly increases the coverage in the Z-axis direction, significantly improving imaging accuracy and quality without increasing the difficulty of radiation source manufacturing. By constructing three adjacent integral rings 100, the present invention enables the static CT real-time imaging system to cleverly avoid the impact of the opening 112, providing a solution for further reducing the geometric structure of static CT.

[0085] It should also be noted that the lengths of the first beam limiter 211 and the second beam limiter 221 of the present invention can be freely changed, thereby being able to freely change the exposure range of the radiation source of the X-ray tube 121, thereby affecting the size of its exposure cone angle. For example, by changing the length of the first beam limiter 211 to change the exposure range of the X-ray tube 121F11, the X-ray tube 121F21, and the X-ray tube 121F31 on the Z axis, thereby affecting the size of its Z-axis exposure cone angles a1, a2, and a3; at the same time, by changing the length of the second beam limiter 221 to change the exposure range of the X-ray tube 121F11, the X-ray tube 121F21, and the X-ray tube 121F31, thereby affecting the size of its Z-axis exposure cone angles a1, a2, and a3. By adding the first beam limiter 211 and the second beam limiter 221 between each X-ray tube 121 and the corresponding detector module 113 to limit its exposure range in the X and Z directions, the requirements can be met. Figure 10 and Figure 12 It is understood that by controlling the size of the beam limiter opening in the X and Z directions, different X-ray beam coverages can be achieved, thereby enabling adaptive adjustments based on clinical needs.

[0086] The static CT imaging system with integrated detectors and radiation sources of the present invention also includes a timing controller connected to the detector ring 110 and radiation ring 120. The timing controller is used to control the focus and exposure timing of the radiation tube 121 and the acquisition timing of the arc detector 111. The scanning mode on the Z axis is spiral scanning or step scanning.

[0087] like Figure 14 The static CT imaging system of the present invention is also equipped with a whole machine fixed frame 300, a scanning bed support 400 that can move up and down, a movable scanning bed 500, and the integrated ring 100 of embodiment 1. Figure 13 The intermediate beam ring is not shown. The static CT imaging system is also equipped with supporting control unit modules to enable its normal operation, such as a power control unit, a timing control unit, a radiation source control unit, a data acquisition unit, a main control unit, a human-computer interaction unit, an image reconstruction unit, and a data storage unit. The power control unit, the timing control unit, the radiation source control unit, the data acquisition unit, the main control unit, the human-computer interaction unit, the image reconstruction unit, and the data storage unit can be arranged inside the annular CT gantry.

[0088] The static CT imaging system integrating the detector and the radiation source has the following beneficial effects:

[0089] 1. The integrated ring 100 can further reduce the space occupied by static CT systems. 2. It provides a wider scanning coverage range on the Z axis. Interlacing three or more integrated rings 100 can achieve a wider Z-direction coverage range, further reducing cone-angle artifacts. 3. Three or more integrated rings 100 are equipped with multiple X-ray tubes 121, enabling scanning via a variety of scanning methods to accommodate different scanning requirements. 4. The beam limiting ring of the present invention can adjust the coverage range of the X-rays generated by the radiation source to accommodate different FOV range requirements.

[0090] Example 2

[0091] An imaging method, such as Figure 1 , and is performed using a static CT imaging system in which the detector and the ray source are integrated in Example 1.

[0092] Three adjacent integral rings 100 are defined as an integral ring group, and the ray rings 120 in the same integral ring group are defined as a left ray ring 120, a middle ray ring 120, and a right ray ring 120, respectively;

[0093] The scanning methods for the same integrated ring group include the following:

[0094] First, multiple exposure cycles are performed along the Z-axis direction to obtain projection images of all the X-ray tubes 121. Each exposure cycle is performed by exposing any X-ray tube 121 in the left X-ray ring 120, then exposing any X-ray tube 121 in the middle X-ray ring 120, and finally exposing any X-ray tube 121 in the right X-ray ring 120.

[0095] Second, all the X-ray tubes 121 in the left X-ray ring 120 are exposed in turn, then all the X-ray tubes 121 in the middle X-ray ring 120 are exposed in turn, and finally all the X-ray tubes 121 in the right X-ray ring 120 are exposed in turn, to obtain projection images of all the X-ray tubes 121;

[0096] Third, all the ray tubes 121 in the left ray ring 120 are exposed in turn to obtain a left ray source projection image;

[0097] Fourth, all the ray tubes 121 in the middle ray ring 120 are exposed in turn to obtain a middle-side ray source projection image;

[0098] Fifth, all the ray tubes 121 in the right ray ring 120 are exposed in turn to obtain a right ray source projection image.

[0099] In the imaging method of the present invention, in each of the aforementioned exposure scanning modes, the X-ray tubes 121 within a single X-ray ring 120 can emit X-rays simultaneously or in a time-sharing manner, individually or multiple times, or point by point or alternately, according to a pre-set exposure sequence. The exposure state of each X-ray tube 121 can be independently controlled by a timing controller. Similarly, the timing controller can coordinate the exposure states of multiple X-ray rings 120, allowing for flexible adjustment based on actual usage requirements.

[0100] Simultaneously, each X-ray tube 121 projects light through the object under test onto its corresponding detector module 113. Data acquisition by these detector modules 113 is also performed by the timing controller. The projection data collected by the curved detectors 111 at a specified timing is pre-processed by the data processing unit to distinguish projection data from different X-ray sources and at different timings. The data processing unit then transmits this pre-processed projection data to the reconstruction unit and data storage unit for CT reconstruction and data storage.

[0101] The ray ring 120 is a multi-energy-level switching ray ring 120. In addition, the ray tube 121 in each ray source ring can instantly switch to multiple energy levels, and the specific energy levels to be switched are determined by design requirements.

[0102] In the imaging method of the present invention, along the Z-axis direction, the foci of all the ray tubes 121 in the left ray ring 120 use the first energy level, the foci of multiple ray tubes 121 in the middle ray ring 120 use the second energy level, and the foci of multiple ray tubes 121 in the right ray ring 120 use the third energy level, and the first energy level, the second energy level and the third energy level are all different, so that energy spectrum images of three different energy levels are obtained in one scan.

[0103] The imaging method has the following beneficial effects: 1. The integrated ring 100 can further reduce the space occupied by the static CT system; 2. It provides a larger scanning coverage range on the Z axis. Three or more integrated rings 100 are staggered to achieve a wider Z-direction coverage range, further reducing cone angle artifacts. 3. More than three integrated rings are provided with multiple ray tubes 121, which can be scanned in a variety of scanning modes to meet different scanning requirements. 4. The beam limiting ring of the present invention can adjust the coverage range of the X-rays generated by the ray source to meet different FOV range requirements. 5. Along the Z axis, the multiple focal points in the left ray ring 120 use one energy level, the multiple focal points in the middle ray ring 120 use another energy level, and the multiple focal points in the right ray ring 120 use another energy level. One scan can achieve energy spectrum images of multiple energy levels.

[0104] Finally, it should be noted that the above embodiments are only used to illustrate the technical solutions of the present invention and are not intended to limit the scope of protection of the present invention. Although the present invention has been described in detail with reference to preferred embodiments, those skilled in the art should understand that the technical solutions of the present invention may be modified or replaced by equivalents without departing from the essence and scope of the technical solutions of the present invention.

Claims

1. A static CT imaging system with an integrated detector and radiation source, characterized by: There are three or more integrated rings, all of which are stacked from front to back, and the central axes of all the integrated rings overlap; Each integrated ring consists of a detection ring and a ray ring; The ray ring is composed of a plurality of ray tubes surrounding each other; The detection ring is formed by splicing together a plurality of arc-shaped detectors. The number of the X-ray tubes in each integrated ring is the same as the number of the arc-shaped detectors, and each X-ray tube is embedded in one arc-shaped detector. In two adjacent integrated rings, all the ray tubes of one ring are staggered with all the ray tubes of the other integrated ring; The central axis of the integrated ring is defined as the Z axis of the static CT imaging system.

2. The static CT imaging system with integrated detector and radiation source according to claim 1, characterized in that: Three adjacent integral rings are defined as an integral ring group, and the ray rings in the same integral ring group are defined as a left ray ring, a middle ray ring, and a right ray ring respectively; In the same integrated ring group, any one ray tube in the left ray ring is located between two adjacent ray tubes in the middle ray ring, and any one ray tube in the middle ray ring is located between two adjacent ray tubes in the right ray ring.

3. The static CT imaging system with integrated detector and radiation source according to claim 2, characterized in that: Each detection ring is a closed circular ring structure formed by splicing an odd number of arc-shaped detectors, and the arc-shaped detectors are evenly distributed in the detection ring; In each integrated ring, a straight line is drawn from the center of any ray tube, passing through the center of the integrated ring, and then extending to the other side of the integrated ring, where the straight line passes through an arc detector.

4. The static CT imaging system with integrated detector and radiation source according to claim 3, characterized in that: An opening is formed in the middle of each arc-shaped detector, and the ray tube is embedded in the corresponding opening; In the same integrated ring group, the position of the radiation tube of the left radiation ring is exactly the same as the position of the radiation tube of the right radiation ring.

5. The static CT imaging system with integrated detector and radiation source according to claim 4, characterized in that: The arc detector is a photon counting detector or an integrating detector.

6. The static CT imaging system with integrated detector and radiation source according to claim 4, characterized in that: Any straight line perpendicular to the Z axis and passing through the Z axis is defined as the X axis; Each integral ring is provided with a beam limiting ring group for limiting the projection area of the ray source tube, the beam limiting ring group and the corresponding integral ring are in a concentric circle structure, and the beam limiting ring is located inside the corresponding integral ring; Each beam limiting ring group consists of a Z-direction beam limiting ring and an X-direction beam limiting ring. In each integral ring, the Z-direction beam limiting ring and the X-direction beam limiting ring are both concentric with the corresponding integral ring. The Z-direction beam limiter ring is an annular structure composed of a plurality of first beam limiters; The X-axis beam limiting ring is a ring structure composed of multiple second beam limiters; The projection area formed after the X-rays generated by each ray tube pass through the corresponding Z-direction beam limiting ring and the corresponding X-direction beam limiting ring is a rectangular projection area.

7. The static CT imaging system with integrated detector and radiation source according to any one of claims 1 to 6, characterized in that: A timing controller is also provided, and the timing controller is connected to the detection ring and the ray ring respectively; The timing controller is used to control the focus and exposure timing of the X-ray tube and the acquisition timing of the arc detector; The scanning mode on the Z axis is a spiral scanning mode or a step scanning mode.

8. An imaging method, characterized in that: The method is performed using a static CT imaging system in which a detector and a radiation source are integrated as described in any one of claims 1 to 7.

9. The imaging method according to claim 8, wherein: Three adjacent integral rings are defined as an integral ring group, and the ray rings in the same integral ring group are defined as a left ray ring, a middle ray ring, and a right ray ring respectively; The scanning methods for the same integrated ring group include the following: First, multiple exposure cycles are performed along the Z-axis direction to obtain projection images of all X-ray tubes; each exposure cycle is for exposing any X-ray tube in the left X-ray ring, then for exposing any X-ray tube in the middle X-ray ring, and finally for exposing any X-ray tube in the right X-ray ring; Second, all the X-ray tubes in the left X-ray ring are exposed in turn, then all the X-ray tubes in the middle X-ray ring are exposed in turn, and finally all the X-ray tubes in the right X-ray ring are exposed in turn, to obtain projection images of all the X-ray tubes; Third, all the ray tubes in the left ray ring are exposed in turn to obtain a left ray source projection image; Fourth, all the ray tubes in the middle ray ring are exposed in turn to obtain a middle ray source projection image; Fifth, all the ray tubes in the right ray ring are exposed in turn to obtain a right ray source projection image.

10. The imaging method according to claim 9, wherein: The ray ring is a multi-energy-level switching ray ring; Along the Z-axis direction, the foci of all the ray tubes in the left ray ring use a first energy level, the foci of multiple ray tubes in the middle ray ring use a second energy level, and the foci of multiple ray tubes in the right ray ring use a third energy level, and the first energy level, the second energy level, and the third energy level are all different, so that energy spectrum images of three different energy levels are obtained in one scan.

Images