Dual energy spectral binning architecture for x-ray based ct detector

Abstract

This invention discloses a dual-spectrum hierarchical architecture and CT detector based on X-rays, relating to the field of medical CT equipment technology. It includes: a scintillator layer capable of receiving high-energy X-rays and low-energy X-rays respectively; and several sets of metal sheets positioned on one end face of the scintillator layer, wherein the metal sheets can block high-energy or low-energy X-rays irradiating a portion of the scintillator layer. This invention solves the technical problems of complex structure, low yield, and high cost of existing dual-spectrum CT detectors.

Description

Technical Field

[0001] This invention relates to the field of medical CT equipment technology, and more specifically, to a dual-spectrum hierarchical architecture based on X-rays and a CT detector. Background Technology

[0002] Currently, in mainstream modern medical CT systems, the detector module plays a crucial role as the device for acquiring CT image data. Specifically, X-rays are emitted from the X-ray tube, covering the entire area of ​​the body to be scanned. The detector module then collects the X-rays, converts them into electrical signals, and then converts them into digital information through a data acquisition and conversion unit. This digital information is then stored in the image processing system, which uses a series of correction and image reconstruction algorithms to generate an image that is displayed on the monitor.

[0003] Current medical CT detectors primarily use scintillators made of GOS or GAGG materials for energy integration and signal processing. These signals are single-spectrum data, which often cannot fully represent human tissue. Therefore, dual-spectrum CT can achieve a higher level of precision and clarity in representing human tissue compared to single-spectrum CT, and a dual-spectrum CT detector is a core and essential condition for realizing dual-spectrum CT.

[0004] In existing technologies, dual-spectrum CT detectors generally have a sandwich structure, that is, two layers of scintillators and two layers of PD stacked on top of each other. This structure is more complex, has a low manufacturing yield, and is expensive, making it difficult to meet the economical demand of modern medical fields for detectors with high cost performance and high yield. Summary of the Invention

[0005] To address these issues, this invention provides an X-ray-based dual-spectrum hierarchical architecture and CT detector, thereby solving the technical problems of complex structure, low yield, and high cost of existing dual-spectrum CT detectors.

[0006] To achieve the above objectives, the present invention provides the following technical solution: An X-ray-based dual-spectrum hierarchical architecture, comprising: The scintillator layer is capable of receiving high-energy X-rays and low-energy X-rays separately. Several sets of metal sheets are positioned on one end face of the scintillator layer, and the several sets of metal sheets can block high-energy X-rays or low-energy X-rays that irradiate a part of the scintillator layer.

[0007] Based on the above technical solution, the present invention is further described as follows: As a further aspect of the present invention, Several groups of the aforementioned metal sheets are interspersed or pasted onto one end face of the scintillator layer.

[0008] As a further aspect of the present invention, Several sets of metal sheet layers are positioned at the back-emitting layer position of the pixels of the scintillator layer.

[0009] As a further aspect of the present invention, The thickness of the metal sheet 2 is set to 0.8 mm.

[0010] As a further aspect of the present invention, The scintillator layer is configured as a single-layer structure.

[0011] A CT detector comprising the aforementioned X-ray-based dual-spectrum hierarchical architecture.

[0012] As a further aspect of the present invention, it also includes: The photodiode layer is fixedly disposed between the end face of the scintillator layer and the end face of the metal sheet layer opposite to the scintillator layer.

[0013] As a further aspect of the present invention, it also includes: The substrate structure is fixedly connected to one end face of the photodiode layer opposite to the scintillator layer.

[0014] As a further aspect of the present invention, The substrate structure includes a mounting base and a substrate layer; The photodiode layer is disposed on one end face away from the scintillator layer at the substrate layer position of the substrate structure, and the substrate layer is positioned on the mounting base of the substrate structure.

[0015] As a further aspect of the present invention, The single-layer scintillator layer is configured as a four-sided splicable structure.

[0016] The present invention has the following beneficial effects: 1. This architecture and device, by using a single scintillator layer in conjunction with a metal sheet layer to block low-energy rays, abandons the traditional stacked structure and can effectively achieve energy spectrum classification using a single set of scintillator layers without the need for complex stacked design. While ensuring the accuracy of dual-energy CT imaging, it effectively simplifies the overall structure of the detector, significantly improves the yield, reduces production costs, and enhances the functionality and practicality.

[0017] 2. The four-sided modular design of the detector effectively enhances the expandability of the equipment, enabling it to flexibly adapt to the usage needs of different CT equipment and further improve the overall functionality and practicality. Attached Figure Description

[0018] To more clearly illustrate the embodiments of the present invention or the technical solutions in the prior art, the accompanying drawings used in the description of the embodiments or the prior art will be briefly introduced below. The structures, proportions, sizes, etc., drawn in this specification are only used to complement the content disclosed in the specification, so that those skilled in the art can understand and read them. Any modifications to the structure, changes in the proportional relationships, or adjustments to the size, without affecting the effects and objectives that the present invention can produce, should still fall within the scope of the technical content disclosed in the present invention.

[0019] Figure 1 This is a schematic diagram of an isometric structure of an X-ray-based dual-energy spectral hierarchical architecture provided in an embodiment of the present invention.

[0020] Figure 2 This is a schematic diagram of the isometric structure of an X-ray-based CT detector provided in an embodiment of the present invention.

[0021] The attached diagram lists the components represented by each number as follows: Scintillator layer 1; Metal sheet layer 2; Photodiode layer 3; Substrate structure 4: mounting base 41, substrate layer 42. Detailed Implementation

[0022] The following specific embodiments illustrate the implementation of the present invention. Those skilled in the art can easily understand other advantages and effects of the present invention from the content disclosed in this specification. Obviously, the described embodiments are only some, not all, of the embodiments of the present invention. Based on the embodiments of the present invention, all other embodiments obtained by those skilled in the art without creative effort are within the scope of protection of the present invention.

[0023] The terms "upper," "lower," "left," "right," and "middle" used in this specification are merely for clarity of description and are not intended to limit the scope of the invention. Any changes or adjustments to their relative relationships, without substantially altering the technical content, should also be considered within the scope of the invention.

[0024] like Figures 1 to 2 As shown, this embodiment of the invention provides an X-ray-based dual-spectrum hierarchical architecture and a CT detector including the aforementioned dual-spectrum hierarchical architecture. The dual-spectrum hierarchical architecture includes a scintillator layer 1 and a metal sheet layer 2, which achieves spectral hierarchical classification through a single scintillator layer 1 combined with the metal sheet layer 2. This simplifies the overall detector configuration structure, significantly improves yield, and enhances scalability through a four-sided splicable design, effectively improving overall functional adaptability and practicality. Specific settings are as follows: Please refer to Figure 1The scintillator layer 1 is a single-layer structure, and several groups of metal sheet layers 2 are provided. These groups of metal sheet layers 2 are intermittently embedded or pasted into the back-emitting layer of the pixels of the scintillator layer 1. The metal sheet layers 2 can block low-energy X-rays irradiating the corresponding area, while only high-energy X-rays can penetrate the metal sheet layers 2 to reach the scintillator layer 1. The areas of the scintillator layer 1 that are not blocked by the metal sheet layers 2 can simultaneously receive both high-energy and low-energy X-rays. The detector collects signals from the blocked and unblocked areas respectively, and after processing, two sets of spectral data with different energies can be obtained. This achieves energy spectrum classification without the need for a stacked configuration of dual scintillator layers 1, effectively simplifying the detector configuration structure and improving the overall yield. The number of metal sheet layers 2 can be adjusted according to the design requirements to adapt to different detection scenarios, thereby simplifying the structure while ensuring the accuracy of dual-energy spectrum detection.

[0025] As a preferred embodiment, the thickness of the metal sheet 2 can be adjusted according to the actual radiation shielding requirements, specifically set to 0.8 mm thickness, to ensure the accuracy of energy spectrum classification.

[0026] Please refer to Figure 2 The CT detector further includes a photodiode layer 3 and a substrate structure 4. The scintillator layer 1, with one end facing away from the metal sheet layer 2, is fixedly connected to the photodiode layer 3. The photodiode layer 3, with one end facing away from the scintillator layer 1, is positioned on the substrate layer 42 of the substrate structure 4. The substrate layer 42 is mounted on the mounting base 41 of the substrate structure 4. The scintillator layer 1 receives X-rays and converts them into visible light, while the photodiode layer 3 converts the visible light into photocurrent, achieving signal conversion and providing data support for subsequent image generation. The single-layer scintillator layer 1 features a four-sided splicable design, making it easier to assemble detector arrays of different sizes according to requirements, adapting to different specifications of CT equipment, and improving the expandability and practicality of the equipment.

[0027] This invention, through an innovative design combining a single-layer scintillator layer 1 with a metal sheet layer 2, abandons the traditional stacked structure and solves the problems of complex structure, low yield, and high cost of existing dual-energy CT detectors. The flexible adjustment design of the metal sheet layer 2 can adapt to different detection scenarios and ensure the accuracy of energy spectrum classification. The four-sided splicing structure design enhances the expandability of the equipment and adapts to CT equipment of different specifications. The collaborative work of each module forms a simple, stable, and cost-controllable medical dual-energy CT detector system, breaking through the limitations of existing technologies and possessing extremely high practical value and market prospects.

[0028] Although the present invention has been described in detail above with general descriptions and specific embodiments, modifications or improvements can be made to it, which will be obvious to those skilled in the art. Therefore, all such modifications or improvements made without departing from the spirit of the present invention fall within the scope of protection claimed by the present invention.

Claims

1. A dual-energy spectral hierarchical architecture based on X-rays, characterized in that, include: The scintillator layer is capable of receiving high-energy X-rays and low-energy X-rays separately. Several sets of metal sheets are positioned on one end face of the scintillator layer, and the several sets of metal sheets can block high-energy X-rays or low-energy X-rays that irradiate a part of the scintillator layer.

2. The X-ray-based dual-spectrum hierarchical architecture according to claim 1, characterized in that, Several groups of the aforementioned metal sheets are interspersed or pasted onto one end face of the scintillator layer.

3. The X-ray-based dual-spectrum hierarchical architecture according to claim 1 or 2, characterized in that, Several sets of metal sheet layers are positioned at the back-emitting layer position of the pixels of the scintillator layer.

4. The X-ray-based dual-spectrum hierarchical architecture according to claim 1, characterized in that, The thickness of the metal sheet 2 is set to 0.8 mm.

5. The X-ray-based dual-spectrum hierarchical architecture according to claim 1, characterized in that, The scintillator layer is configured as a single-layer structure.

6. A CT detector, characterized in that, Including the X-ray-based dual-energy spectral hierarchical architecture as described in any one of claims 1-5.

7. The CT detector according to claim 6, characterized in that, Also includes: The photodiode layer is fixedly disposed between the end face of the scintillator layer and the end face of the metal sheet layer opposite to the scintillator layer.

8. The CT detector according to claim 7, characterized in that, Also includes: The substrate structure is fixedly connected to one end face of the photodiode layer opposite to the scintillator layer.

9. The CT detector according to claim 8, characterized in that, The substrate structure includes a mounting base and a substrate layer; The photodiode layer is disposed on one end face away from the scintillator layer at the substrate layer position of the substrate structure, and the substrate layer is positioned on the mounting base of the substrate structure.

10. The CT detector according to claim 6, characterized in that, The single-layer scintillator layer is configured as a four-sided splicable structure.

Images