A dual resolution x-ray detector
By designing imaging surfaces and phosphor layer materials of different sizes in X-ray detectors, and combining TFT-PD and CMOS panels, the problems of resolution mismatch and multiple imaging in existing technologies have been solved, achieving high-efficiency, low-radiation, and high-quality image acquisition.
Patent Information
- Authority / Receiving Office
- CN · China
- Patent Type
- Utility models(China)
- Current Assignee / Owner
- JIKEMEIZHI (SUZHOU) TECHNOLOGY CO LTD
- Filing Date
- 2025-01-15
- Publication Date
- 2026-06-02
AI Technical Summary
Existing X-ray detectors have problems such as resolution mismatch in dental CT and panoramic radiography, increased radiation risk to patients due to multiple imaging sessions, and poor image quality. In particular, TFT detectors have high dark field noise at low doses, while CMOS detectors are expensive.
Design a dual-resolution X-ray detector that uses imaging surfaces and fluorescent layer materials of different sizes to obtain high-resolution and high-energy absorption images in a single exposure. Combine a TFT-PD and a CMOS panel, use optical adhesive for bonding and PET aluminum film for protection, and a control module to manage signal processing.
It enables the acquisition of high-quality CBCT and panoramic images in a single exposure on the same detector, reducing patient radiation dose, improving image signal-to-noise ratio and diagnostic efficiency, and reducing costs.
Smart Images
Figure CN224307344U_ABST
Abstract
Description
Technical Field
[0001] This application relates to the field of X-ray detector imaging, and more specifically, to a dual-resolution X-ray detector. Background Technology
[0002] X-ray flat panel detectors play a crucial role in X-ray imaging systems. Dental CT and panoramic radiography are currently important tools for clinical dental diagnosis, each with different requirements for spatial and density resolution. This necessitates the use of detectors with varying resolutions to image the human body. In recent years, the common practice is for CBCT and panoramic radiography to share a single detector imaging plane. CBCT uses part or all of the imaging plane's field of view, typically operating in 1x1 non-binning mode. However, CT imaging generally suffers from high noise and insufficient signal capture in 1x1 non-binning mode; therefore, CBCT often uses 2x2 or 3x3 binning modes. Panoramic radiography uses a very small portion of the imaging plane, narrow horizontally (typically 5-10 mm) and vertically (typically 150-230 mm). Panoramic radiography requires higher spatial resolution and only uses the detector's 1x1 non-binning mode.
[0003] CBCT and panoramic radiography share the same imaging plane, which can accomplish both functions and is somewhat economical. However, from an imaging perspective, there are many problems, and multiple shots are required.
[0004] As shown in the figure below, when using binning mode to capture CBCT, for example, by superimposing the signals acquired by four 100um pixels and then averaging them, the number of signals is significantly less than that captured by a single 200um pixel. Whether at low or high doses, the signal-to-noise ratio is at a disadvantage.
[0005] In simple terms, the fill factor of a typical 100µm pixel (i.e., the PD area in the image below) is around 55%, and the fill factor of a 200µm pixel is around 75%. This means that the signal receiving area of a 2x2 binning mode pixel (four 100µm pixels) is 22000µm. 2 A 200µm pixel has a signal receiving surface of 30000µm. 2 The latter has a 36.4% larger signal receiving area compared to the former.
[0006] Secondly, to reduce costs, the industry tends to use TFT / PD panels for CBCT and panoramic radiography, while using CMOS detectors to a lesser extent. In CBCT mode, due to the considerable dose level of a single frame of headshot, the signal-to-noise ratio of TFT detectors is almost the same as that of CMOS detectors. However, in panoramic radiography under low-dose X-ray imaging, TFT detectors have high dark-field noise, resulting in significantly inferior image quality compared to CMOS detectors.
[0007] Some high-end models will equip a single system with a TFT / PD detector for dental CBCT imaging and a CMOS line scan detector for panoramic imaging. However, the imaging process is complex and costly.
[0008] Note: Binning mode is an imaging method that combines adjacent pixels into one pixel. For example, 2x2 binning mode superimposes the signals collected by four pixels in a 2x2 array together as a single pixel signal for output.
[0009] In summary, the shortcomings of existing technologies are summarized as follows:
[0010] 1. Existing technology proposes a dual-spectrum, dual-resolution X-ray detector. This system has two layers of different fluorescent materials and imaging surfaces with different resolutions. The upper and lower images can output high-resolution images and high-energy absorption images, respectively. However, the imaging areas of the first and second layers are the same, making it unsuitable for panoramic imaging, and the cost is relatively high.
[0011] 2. Another method that can obtain both CBCT and panoramic images in a single scan is based on obtaining panoramic images from CBCT: first, three-dimensional data is generated based on oral CBCT, then curved tomographic images are extracted from the three-dimensional data through interpolation, and finally, oral panoramic images are obtained using the curved tomographic images; however, the oral panoramic images obtained in this way are significantly different from those obtained by traditional scanning methods, and extracting curved tomographic images after three-dimensional reconstruction will introduce secondary errors, resulting in a significant reduction in the quality and resolution of the obtained panoramic images. Utility Model Content
[0012] To address the aforementioned issues, this application provides a dual-resolution X-ray detector, which aims to enable the acquisition of images with two resolutions through a single exposure on the same detector, with superior image quality.
[0013] The first aspect of this utility model provides a dual-resolution X-ray detector, characterized in that the detector's structure, from top to bottom, includes: an encapsulation material, a fluorescent layer material, a first imaging surface, a second imaging surface, and a control module;
[0014] The pixel size of the first imaging surface is larger than the pixel size of the second imaging surface;
[0015] The first imaging surface and the second imaging surface are closely joined to form a flat plate located on the same horizontal plane;
[0016] The feature is that it further includes an image processing module, which is electrically connected to the control module.
[0017] In one alternative embodiment, the first imaging surface and the second imaging surface are used to receive visible photons generated by X-ray excitation of the fluorescent layer material.
[0018] In one alternative implementation, the first imaging surface and the second imaging surface are joined using optical adhesive.
[0019] In one optional implementation, the pixel size ratio of the first imaging surface to the second imaging surface is N:1.
[0020] In one optional implementation, both the first imaging surface and the second imaging surface can be selected from TFT-PD panels and CMOS panels.
[0021] The TFT-PD panel also includes an IGZO TFT-PD panel, an a-Si TFT-PD panel, and an LTPS TFT-PD panel.
[0022] In one optional implementation, the first imaging surface further includes a first readout chip and a first scanning chip; the second imaging surface further includes a second readout chip and a second scanning chip;
[0023] When both the first imaging surface and the second imaging surface are CMOS panels, then the first readout chip, the first scanning chip, the second readout chip, and the second scanning chip are not required.
[0024] In one alternative embodiment, the encapsulation material is a PET aluminum film, used to protect the fluorescent layer material from moisture deliquescence and oxidation, thereby reducing light loss.
[0025] In one optional implementation, the control module further includes a control circuit module, an analog-to-digital conversion module, and a signal processing module;
[0026] The control circuit module is used to manage the overall circuit, switch control modes, and transmit signals.
[0027] The analog-to-digital converter module is used to convert analog signals into digital signals;
[0028] The signal processing module is used to process digital signals, making them easy for the image processing module to recognize.
[0029] In one alternative implementation, the image processing module processes the digital signal output by the control module into an image output.
[0030] A second aspect of this utility model provides an imaging method for a dual-resolution X-ray detector, comprising:
[0031] When the X-ray source is turned on, the X-rays pass through the encapsulation material and irradiate the fluorescent layer material, generating visible photons;
[0032] The first and second imaging surfaces receive visible photons and convert them into electrical signals for output.
[0033] The control module receives electrical signals and converts them into digital signals for output.
[0034] The image processing module receives digital signals and converts them into image output.
[0035] The embodiments disclosed herein include the following beneficial effects:
[0036] In terms of imaging efficiency: By stitching together imaging planes of different resolutions, two images of different resolutions can be captured in a single shot, reducing the number of shots and the shooting time, thereby reducing the patient's radiation dose and improving diagnostic efficiency. Traditional multiple-shot methods increase the risk of radiation exposure for patients; this design effectively avoids this problem.
[0037] In terms of image quality: Compared with traditional binning mode CBCT, the large pixel size imaging surface1 acquires more signals and has a higher signal-to-noise ratio, which improves the image quality of oral CBCT, makes it easier to distinguish between bone and soft tissue, and provides more accurate imaging information for clinical diagnosis.
[0038] In terms of technical implementation: The unique imaging surface stitching design enables multi-resolution imaging and multiple mode applications on a single detector. Unlike the shared imaging surface or dual-layer imaging surface design of existing technologies, it effectively solves problems such as panoramic image capture, cost, and image quality, and has high innovation and practicality. Attached Figure Description
[0039] To more clearly illustrate the technical solutions of the embodiments of this application, the drawings used in the description of the embodiments of this application will be briefly introduced below. Obviously, the drawings described below are only some embodiments of this application. For those skilled in the art, other drawings can be obtained based on these drawings without creative effort.
[0040] Figure 1 This is a schematic diagram of the structure of a dual-resolution X-ray detector according to an embodiment of this application;
[0041] Figure 2This is a schematic diagram of the structure of the first imaging surface and the second imaging surface proposed in an embodiment of this application;
[0042] Figure 3 This is an example image of a dual-resolution X-ray detector imaging method according to an embodiment of this application;
[0043] Figure 4 This is an example flowchart of an imaging method using a dual-resolution X-ray detector proposed in one embodiment of this application. Figure 1 ;
[0044] Figure 5 This is an example flowchart of an imaging method using a dual-resolution X-ray detector proposed in one embodiment of this application. Figure 2 ;
[0045] Reference numerals: 1-Encapsulation material, 2-Fluorescent layer material, 3-First imaging surface, 4-Second imaging surface, 5-Control module, 6-Image processing module, 7-First readout chip, 8-First scanning chip, 9-Second readout chip, 10-Second scanning chip. Detailed Implementation
[0046] The technical solutions of the embodiments of this application will be clearly and completely described below with reference to the accompanying drawings. Obviously, the described embodiments are only some embodiments of this application, not all embodiments. Based on the embodiments of this application, all other embodiments obtained by those skilled in the art without creative effort are within the scope of protection of this application.
[0047] Please refer to Figure 1 , Figure 1 This is a schematic diagram of the structure of a dual-resolution X-ray detector proposed in Embodiment 1 of this application. Figure 1 As shown, the first aspect of this utility model provides a dual-resolution X-ray detector, the structure of which, from top to bottom, includes: an encapsulation material 1, a fluorescent layer material 2, a first imaging surface 3, a second imaging surface 4, and a control module 5;
[0048] The pixel size of the first imaging surface 3 is larger than the pixel size of the second imaging surface 4;
[0049] The first imaging surface 3 and the second imaging surface 4 are closely joined to form a flat plate located on the same horizontal plane;
[0050] The feature is that it further includes an image processing module 6, which is electrically connected to the control module 5.
[0051] In this embodiment, the detector structure is layered, consisting of, from top to bottom, encapsulation material 1, fluorescent material 2, first imaging surface 3, second imaging surface 4, and control module 5. The image processing module receives and processes signals from the imaging surface. This structural design allows the detector to acquire two different resolution projection images in a single image under X-ray irradiation through the coordinated operation of its various parts, meeting different clinical diagnostic needs, such as oral CBCT images and panoramic images.
[0052] Furthermore, the first imaging surface 3 and the second imaging surface 4 are used to receive visible photons generated by the X-ray excitation of the fluorescent layer material 2.
[0053] In this embodiment, when X-rays penetrate the encapsulation material and irradiate the fluorescent layer material 2 of the detector, the atoms or molecules inside the fluorescent layer material 2 undergo energy level transitions under the excitation of X-rays, thereby releasing visible photons.
[0054] Furthermore, the first imaging surface 3 and the second imaging surface 4 are joined together using optical adhesive.
[0055] In this embodiment, optical adhesive is used to bond the splicing joints, forming a flat plate on the same horizontal plane. The splicing joint can have a gap or no gap. When there is no gap, the two imaging surfaces can be seamlessly connected, ensuring that visible photons generated by X-ray excitation of the phosphor layer material will not suffer signal loss or interference during transmission due to gaps at the splicing joint. This maximizes the uniform and efficient reception of photons by both imaging surfaces. When there is a gap at the splicing joint, by rationally designing the size of the gap and the properties of the optical adhesive, the optical characteristics between the two imaging surfaces can be adjusted to a certain extent to adapt to different imaging scenarios and requirements.
[0056] Furthermore, the pixel size ratio of the first imaging surface 3 to the second imaging surface 4 is N:1.
[0057] In this embodiment, the pixel size ratio is N:1, where N is an integer ≥2 (generally not exceeding 4 for dental applications, but can be adjusted according to application requirements). The first imaging plane has large pixels, enabling the acquisition of more signals, resulting in a high signal-to-noise ratio and high projection image density resolution, which helps distinguish between bone and soft tissue, making it suitable for generating CBCT images from CT reconstruction. The second imaging plane has small pixels, resulting in a large projection image spatial resolution, and less noise generated by the CMOS panel, facilitating the diagnosis of soft tissues and enabling the generation of panoramic images.
[0058] Furthermore, both the first imaging surface 3 and the second imaging surface 4 can be selected from TFT-PD panels and CMOS panels;
[0059] The TFT-PD panel also includes an IGZO TFT-PD panel, an a-Si TFT-PD panel, and an LTPS TFT-PD panel.
[0060] In this embodiment, the IGZO TFT_PD panel uses indium gallium zinc oxide (IGZO) as the semiconductor material, which has a higher electron mobility compared to traditional amorphous silicon (a-Si) materials. This allows electrons to move and transmit more quickly in the pixel circuit during the process of X-ray excitation of the phosphor layer material to generate visible photons, which are then received by the panel and converted into electrical signals. This effectively improves the detector's response speed and signal processing efficiency.
[0061] Si TFT-PD panels are a traditional type of TFT panel. Although they have relatively low electron mobility, they offer advantages such as mature manufacturing processes and lower costs. In applications where cost control is stringent and imaging speed requirements are not extremely high, a-Si TFT-PD panels can effectively reduce detector production costs while maintaining a certain level of imaging quality.
[0062] LTPS TFT-PD panels, characterized by their low-temperature polycrystalline silicon (LTPS) technology, feature a high pixel aperture ratio and low power consumption. A higher pixel aperture ratio means that each pixel can more effectively receive visible photons generated by the phosphor layer, thereby improving detector sensitivity and signal-to-noise ratio.
[0063] Further, please refer to Figure 2 , Figure 2 This is a schematic diagram of the structure of the first imaging plane and the second imaging plane according to an embodiment of this application, as shown below. Figure 2 As shown, the first imaging surface 3 further includes a first readout chip 7 and a first scanning chip 8; the second imaging surface 4 further includes a second readout chip 9 and a second scanning chip 10;
[0064] When both the first imaging surface 3 and the second imaging surface 4 are CMOS panels, the first readout chip 7, the first scanning chip 8, the second readout chip 9, and the second scanning chip 10 are not required.
[0065] In this embodiment, the scanning chip is used to determine the position and status information of each pixel, ensuring that no pixel signal is missed or incorrectly acquired; the readout chip is a high-efficiency data transmission channel, which quickly and accurately reads and preliminarily processes the pixel signals acquired by the scanning chip, and appropriately amplifies and conditions these analog signals to meet the requirements of subsequent transmission and processing.
[0066] When both the first imaging surface 3 and the second imaging surface 4 are made of CMOS panels, the CMOS panels themselves have unique electrical characteristics and signal processing capabilities, so that no additional readout chip and scanning chip are needed to assist in the operation.
[0067] Furthermore, the encapsulation material 1 is a PET aluminum film, used to protect the fluorescent layer material 2 from moisture deliquescence and oxidation, thereby reducing light loss.
[0068] In this embodiment, the encapsulation material is a PET aluminum film with high reflectivity. On the one hand, the PET aluminum film can efficiently reflect any light that may leak back into the detector, avoiding the unnecessary loss of light, thereby maximizing the full utilization of the light generated by the fluorescent layer material 2 by the imaging surface. On the other hand, the PET aluminum film acts as a physical barrier, protecting the fluorescent material from the effects of moisture and oxidation, thus extending the lifespan of the detector.
[0069] Furthermore, the control module 5 also includes a control circuit module, an analog-to-digital conversion module, and a signal processing module;
[0070] The control circuit module is used to manage the overall circuit, switch control modes, and transmit signals.
[0071] The analog-to-digital converter module is used to convert analog signals into digital signals;
[0072] The signal processing module is used to process digital signals, making them easy for the image processing module 6 to recognize.
[0073] In this embodiment, the control circuit module monitors key parameters such as current and voltage in the circuit in real time. During operation, when it is necessary to switch between different imaging modes, the control circuit module can respond to the operation command quickly and accurately. By adjusting the circuit connection and signal path, it can achieve rapid switching from high-resolution imaging mode to high-energy absorption imaging mode.
[0074] The analog-to-digital converter module samples and quantizes these analog signals at a sampling frequency and precision, converting them into digital signals.
[0075] The signal processing module performs operations such as filtering, noise reduction, and enhancement on digital signals.
[0076] Furthermore, the image processing module 6 processes and converts the digital signal output by the control module 5 into an image output.
[0077] In this embodiment, the image processing module 6 receives the processed digital signal from the control module 5 and uses an image reconstruction algorithm. Based on the detector's imaging principle and geometry, and considering the different resolution characteristics of the first imaging surface 3 and the second imaging surface 4, it performs reasonable fusion and interpolation processing on signals from different sources. Next, a color correction algorithm is used, employing a pre-set standard color model and correction parameters, to finely adjust the image's color and grayscale, making the image's tone more natural and realistic, facilitating observation and judgment by doctors. Then, based on the image content and application scenario, it intelligently enhances the contrast between different tissues.
[0078] Please refer to Figure 3 , Figure 3 This is a flowchart of an imaging method using a dual-resolution X-ray detector as proposed in an embodiment. Figure 3 As shown, a second aspect of this utility model provides an imaging method for a dual-resolution X-ray detector, comprising:
[0079] When the X-ray source is turned on, the X-rays pass through the encapsulation material 1 and irradiate the fluorescent layer material 2, generating visible photons;
[0080] The first imaging surface 3 and the second imaging surface 4 receive visible photons and convert them into electrical signals for output.
[0081] Control module 5 receives electrical signals and converts them into digital signals for output;
[0082] The image processing module 6 receives digital signals and converts them into image output.
[0083] In this embodiment, the X-ray source is turned on, and the X-rays pass through the encapsulation material to irradiate the fluorescent layer material, causing it to generate visible photons. The first imaging surface and the second imaging surface receive the photons and convert them into electrical signals. If the imaging surface contains a readout chip and a scanning chip, corresponding signal reading and scanning are performed. The electrical signals are transmitted to the control module. The control circuit module manages the circuit, switches modes, and transmits signals. The analog-to-digital conversion module converts the analog signals into digital signals. The signal processing module processes the digital signals and transmits them to the image processing module. The image processing module converts the digital signals into image output. If a high-resolution image is required, the signal generation is mainly provided by the second imaging surface. If a high-energy absorption image is required, the signal generation is mainly provided by the first imaging surface.
[0084] Please refer to Figure 3 , Figure 3 This is an example diagram of a dual-resolution X-ray detector imaging method according to an embodiment of this application; the detector structure shown is used for capturing oral CT images and panoramic images, with the first imaging surface using a TFT-PD panel and the second imaging surface using a CMOS panel.
[0085] Example 1, please refer to Figure 4, Figure 4 This is an example flowchart of an imaging method using a dual-resolution X-ray detector proposed in one embodiment of this application. Figure 1 ,like Figure 4 As shown, after a single X-ray exposure, the fluorescent material is excited to produce visible photons. The first imaging plane has a larger pixel size, resulting in more signals acquired by each pixel, a higher signal-to-noise ratio, and a higher density resolution in the resulting projected image. This facilitates the differentiation between bone and soft tissue and can be used for CT reconstruction, outputting CBCT images. The second imaging plane has a smaller pixel size, resulting in a higher spatial resolution in the projected image. Furthermore, the CMOS panel generates less noise, which is beneficial for soft tissue diagnosis and can be used to generate panoramic images. In a single imaging session, both oral CBCT images and panoramic images can be obtained simultaneously, with superior image quality.
[0086] Example 2, please refer to Figure 5 , Figure 5 This is an example flowchart of an imaging method using a dual-resolution X-ray detector proposed in one embodiment of this application. Figure 2 ,like Figure 5 As shown, after a single X-ray exposure, the fluorescent material is excited to generate visible photons. The first and second imaging surfaces receive these photons and convert them into digital signals. These digital signals are then fused to form a single image. This fused image is then input into an image processing module for processing. The resulting oral CBCT image can simultaneously diagnose both bone and soft tissue. Simultaneously, the digital signal converted by the second imaging surface is also separately input into the image processing module, outputting a panoramic oral image. This approach generates both CBCT images capable of simultaneously diagnosing bone and soft tissue and a panoramic image.
[0087] Although preferred embodiments of the present application have been described, those skilled in the art, upon learning the basic inventive concept, can make other changes and modifications to these embodiments. Therefore, the appended claims are intended to be interpreted as including the preferred embodiments as well as all changes and modifications falling within the scope of the embodiments of the present application.
[0088] The various embodiments in this specification are described in a progressive manner, with each embodiment focusing on the differences from other embodiments. The same or similar parts between the various embodiments can be referred to each other.
[0089] Although preferred embodiments of the present application have been described, those skilled in the art, upon learning the basic inventive concept, can make other changes and modifications to these embodiments. Therefore, the appended claims are intended to be interpreted as including the preferred embodiments as well as all changes and modifications falling within the scope of the embodiments of the present application.
[0090] Finally, it should be noted that in this document, relational terms such as "first" and "second" are used only to distinguish one entity or operation from another, and do not necessarily require or imply any such actual relationship or order between these entities or operations. Furthermore, the terms "comprising," "including," or any other variations thereof are intended to cover non-exclusive inclusion, such that a process, method, article, or terminal device that comprises a list of elements includes not only those elements but also other elements not expressly listed, or elements inherent to such a process, method, article, or terminal device. Without further limitations, an element defined by the phrase "comprising one..." does not exclude the presence of other identical elements in the process, method, article, or terminal device that includes said element.
[0091] The above provides a detailed description of a dual-resolution X-ray detector provided in this application. Specific examples have been used to illustrate the principles and implementation methods of this application. The descriptions of the above embodiments are only for the purpose of helping to understand the method and core ideas of this application. At the same time, for those skilled in the art, there will be changes in the specific implementation methods and application scope based on the ideas of this application. Therefore, the content of this specification should not be construed as a limitation of this application.
Claims
1. A dual-resolution X-ray detector, characterized in that, The detector's structure, from top to bottom, includes: encapsulation material (1), fluorescent layer material (2), first imaging surface (3), second imaging surface (4), and control module (5); The pixel size of the first imaging surface (3) is larger than the pixel size of the second imaging surface (4); The first imaging surface (3) and the second imaging surface (4) are closely joined to form a flat plate located on the same horizontal plane; The feature is that it further includes an image processing module (6), which is electrically connected to the control module (5).
2. The dual-resolution X-ray detector according to claim 1, characterized in that, The first imaging surface (3) and the second imaging surface (4) are used to receive visible photons generated by X-ray excitation of the fluorescent layer material (2).
3. A dual-resolution X-ray detector according to claim 2, characterized in that, The first imaging surface (3) and the second imaging surface (4) are joined by optical adhesive.
4. A dual-resolution X-ray detector according to claim 3, characterized in that, The pixel size ratio of the first imaging surface (3) to the second imaging surface (4) is N:
1.
5. A dual-resolution X-ray detector according to claim 4, characterized in that, Both the first imaging surface (3) and the second imaging surface (4) can be selected from TFT-PD panels and CMOS panels; The TFT-PD panel also includes an IGZO TFT-PD panel, an a-Si TFT-PD panel, and an LTPS TFT-PD panel.
6. A dual-resolution X-ray detector according to claim 5, characterized in that, The first imaging surface (3) further includes a first readout chip (7) and a first scanning chip (8); the second imaging surface (4) further includes a second readout chip (9) and a second scanning chip (10). When both the first imaging surface (3) and the second imaging surface (4) are CMOS panels, the first readout chip (7), the first scanning chip (8), the second readout chip (9) and the second scanning chip (10) are not required.
7. A dual-resolution X-ray detector according to claim 1, characterized in that, The encapsulation material (1) is a PET aluminum film used to protect the fluorescent layer material (2) from moisture deliquescence and oxidation, thereby reducing light loss.
8. A dual-resolution X-ray detector according to claim 1, characterized in that, The control module (5) also includes a control circuit module, an analog-to-digital conversion module, and a signal processing module; The control circuit module is used to manage the overall circuit, switch control modes, and transmit signals. The analog-to-digital converter module is used to convert analog signals into digital signals; The signal processing module is used to process digital signals, which are easily recognized by the image processing module (6).
9. A dual-resolution X-ray detector according to claim 1, characterized in that, The image processing module (6) processes and converts the digital signal output by the control module (5) into an image output.