Front-end assembly, endoscope, and image acquisition and analysis method

Abstract

A front-end assembly, an endoscope (10), and an image acquisition and analysis method, relating to the technical field of medical instruments. The front-end assembly comprises a front-end housing (100); a camera module (200), provided on the front-end housing (100) and used for acquiring images; an illumination light source (300), provided on the front-end housing (100) and used for illumination; and a marking light source (400), provided on the front-end housing (100) and used for forming a marking light spot (420) in an image acquisition area of the camera module (200). An image acquired by the camera module (200) has an indication mark (210) and a range mark (510); and in an image acquired by the camera module (200) in a clear imaging area, the marking light spot (420) is located in the area between the range mark (510) and the indication mark (210). The front-end assembly can provide effective guidance for doctors, and assists the doctors in adjusting the position of the front-end housing (100), such that the front-end housing (100) is at an appropriate distance from a target, so as to enable the target to be located within the clear imaging area, thus acquiring clear images of the target.

Description

A front-end component, endoscope, image acquisition and analysis method Technical Field

[0001] This invention relates to the field of medical device technology, and in particular to a front-end component, an endoscope, and an image acquisition and analysis method. Background Technology

[0002] A lesion is an abnormal growth formed in the body's tissues, which may include tumors, polyps, kidney stones, etc. These lesions vary in size and shape, affecting doctors' diagnostic and treatment decisions. Endoscopy is a commonly used technique that allows direct observation of the lesion and provides important information for subsequent treatment. Accurately assessing the size of the lesion helps in developing an appropriate treatment plan, such as choosing a suitable removal or excision method.

[0003] In endoscopic surgery, surgeons adjust the position of the endoscope to obtain images of lesions and then use these images to determine the location of the lesions. However, the complexity of the internal environment often limits image clarity, and the surgeon's experience directly impacts image quality. Because different surgeons have varying levels of experience, the clarity of the images obtained when adjusting the endoscope will differ. This experience-dependent adjustment method can easily lead to decreased image quality, thus affecting the accurate assessment of lesions. Such inaccurate judgments may result in inappropriate treatment plans, negatively impacting the patient's recovery. Summary of the Invention

[0004] To address the aforementioned issues, this application provides a front-end component, an endoscope, and an image acquisition and analysis method.

[0005] In a first aspect, this application provides a front-end component for use in an endoscope, comprising:

[0006] Front housing;

[0007] A camera module is disposed on the front housing and is used to acquire images. The camera module has preset near and far boundaries to define the clear imaging area of ​​the camera module.

[0008] A lighting source, disposed in the front end housing, is used for illumination; and

[0009] A marker light source is disposed on the front housing and is used to form a marker light spot within the image acquisition area of ​​the camera module;

[0010] The image captured by the camera module has an indicator mark and a range mark. The indicator mark is used to indicate the optical axis of the camera module, and the range mark is set at intervals with the indicator mark. The optical axis of the marker light source intersects with the optical axis of the camera module to form a first intersection point, which is located at the near or far boundary.

[0011] When the first intersection point is located at the near-field boundary, in the image acquired at the far-field boundary, the optical axis of the marked light source intersects with the range mark;

[0012] When the first intersection point is located at the distant boundary, in the image captured at the near boundary, the optical axis of the marked light source intersects with the range mark.

[0013] This application also provides an endoscope using the aforementioned front-end components, and a method for acquiring and analyzing images using the aforementioned endoscope.

[0014] The present invention has the following beneficial effects:

[0015] By setting indicator and range markers, doctors can be effectively guided to adjust the position of the front shell to ensure it is at an appropriate distance from the target, thereby ensuring the target is within the clear imaging area and obtaining a clear image. This not only reduces operational difficulty but also ensures that different doctors can obtain consistent image clarity under similar conditions, eliminating image quality fluctuations caused by differences in experience. This structural optimization effectively addresses the impact of the complexity of the internal environment on image clarity and the problem of inaccurate assessments caused by differences in doctors' operational experience, thus reducing the risk of inappropriate treatment plans. Attached Figure Description

[0016] Figure 1 is a structural schematic diagram of an embodiment of this application;

[0017] Figure 2 is a schematic diagram of the front-end component structure;

[0018] Figure 3 is a schematic diagram of the imaging of the camera module when the target is between the near-field boundary and the camera module;

[0019] Figure 4 is a schematic diagram of the image captured by the camera module in the case shown in Figure 3;

[0020] Figure 5 is a schematic diagram of the imaging of the camera module when the target is at the far horizon away from the camera module side;

[0021] Figure 6 is a schematic diagram of the image captured by the camera module in the case shown in Figure 5;

[0022] Figure 7 is a schematic diagram of the imaging module when the target is within the clear imaging area;

[0023] Figure 8 is a schematic diagram of the image captured by the camera module in the case shown in Figure 7;

[0024] Figure 9 is a schematic diagram of the imaging of the camera module when the optical axis of the range light source intersects with the optical axis of the camera module;

[0025] Figure 10 shows images captured by the endoscope;

[0026] Figure 11 is a schematic diagram of the endoscope.

[0027] The diagram is marked as follows:

[0028] 10. Endoscope; 20. Target; 100. Front housing; 200. Camera module; 210. Indicator mark; 220. Near field boundary; 230. Far field boundary; 240. Clear imaging area; 300. Illumination source; 400. Marker light source; 410. First intersection point; 420. Marker spot; 430. Second intersection point; 500. Range light source; 510. Range marker; L1. Optical axis of camera module; L2. Optical axis of marker light source; L3. Optical axis of range light source. Detailed Implementation

[0029] In this application, "proximal" and "distal" refer to the end of the endoscope and its components relative to the user's position in the usage environment, with the end closer to the user being designated as "proximal" and the end farther from the user being designated as "distal".

[0030] A camera has a specific depth of field, which refers to the range of distances from which the camera can capture a clear image. This range is defined by the near-field boundary and the far-field boundary. The near-field boundary is the closest point from which the camera can capture a clear image, while the far-field boundary is the farthest point from which the camera can capture a clear image. The area between the near-field boundary and the far-field boundary is the camera's sharp imaging area. In practical applications, the existence of depth of field allows the camera to provide a relatively clear image within a certain distance, but if the target object is outside this range, the image sharpness will decrease.

[0031] In modern medicine, endoscopic technology is widely used in various minimally invasive surgeries and diagnostic procedures. Many endoscopic devices are equipped with cameras so that doctors can observe the target in real time. However, due to economic and operational limitations, many endoscopic cameras still employ a design that does not autofocus. This means that the operator needs to manually adjust the distance between the camera and the target area to ensure that the observation area is within the camera's clear imaging range. This manual adjustment increases the complexity of the operation, especially in dynamic surgical environments, and can affect the doctor's judgment and surgical efficiency.

[0032] Furthermore, doctors have varying levels of experience, resulting in differences in image clarity when adjusting the endoscope. This experience-based adjustment method can lead to a decrease in image quality, thereby affecting the accurate assessment of the target. Therefore, finding effective solutions to improve endoscopic image clarity is particularly important.

[0033] To address this issue, this application provides a front-end component, an endoscope, and an image acquisition and analysis method.

[0034] The first aspect of this embodiment describes a front-end component in detail.

[0035] Embodiments of this application provide a front-end component applied to an endoscope 10. Exemplarily, referring to Figures 1 and 11, the endoscope 10 includes an insertion portion, and the front-end component is located within the insertion portion. Specifically, the front-end component is located at the distal end of the insertion portion. In some embodiments, the front-end component may be part of the insertion portion; exemplaryly, the front-end component and a portion of the insertion portion are integrally formed. In some embodiments, the front-end component is detachably mounted to the insertion portion; exemplaryly, the front-end component is connected to the insertion portion via a snap-fit ​​structure and / or bolts.

[0036] Referring to Figures 1 and 2, the front-end assembly includes a front-end housing 100, a camera module 200, an illumination source 300, and a marker light source 400. Exemplarily, the front-end housing 100 is a basic structural component. The front-end housing 100 can serve as the mounting base for the camera module 200, the illumination source 300, and the marker light source 400.

[0037] In some designs, the illumination source 300 is located on the front housing 100. The illumination source 300 illuminates the internal space, thereby making the images captured by the camera module 200 clearer. It is understood that in this embodiment, the light emitted by the illumination source 300 is non-parallel light. For example, the illumination source 300 is a point source, meaning that light radiates outwards from the illumination source 300.

[0038] In some embodiments, referring to Figures 2-3, the camera module 200 has a preset near-field boundary 220 and a far-field boundary 230 to define the clear imaging area 240 of the camera module 200.

[0039] The camera module 200 comprises an optical lens and a photosensitive element, enabling it to focus light onto the photosensitive element. The focal length of the lens determines the setting of the near-field boundary 220 and the far-field boundary 230. Properly setting these boundaries helps optimize the focusing effect of light, thereby enhancing image sharpness. By setting the near-field boundary 220, the camera module 200 can avoid image defocusing or distortion caused by objects being too close; setting the far-field boundary 230 prevents image blurring caused by objects being too far away.

[0040] In some embodiments, referring to Figures 2-3, the image captured by the camera module 200 has an indicator mark 210, which is used to indicate the optical axis of the camera module 200. The optical axis of the camera module 200 represents the direction of light rays emanating from the optical center (typically the geometric center) of the lens of the camera module 200. For example, the center position in the image captured by the camera module 200 is the position of the optical axis, which is perpendicular to the image plane and passes through the center point of the image.

[0041] In some implementations, a marker light source 400 is used to form a marker spot 420 within the image acquisition area of ​​the camera module 200. For example, the marker light source 400 can be a laser or focused light. This design allows the marker spot 420 to have high brightness and clarity in the image, facilitating rapid location of the target object 20 by the physician during observation.

[0042] Understandably, the brightness of the marking light source 400 is higher than that of the illumination light source 300, ensuring that the marking spot 420 is clearly distinguishable in an environment illuminated by the illumination light source 300. For example, the color of the marking light source 400 differs from that of the illumination light source 300; this color contrast helps surgeons more easily identify and locate the marking spot 420. This design enhances the visibility of the marking spot 420, enabling surgeons to quickly determine the location of the target 20 in complex surgical environments.

[0043] In some embodiments, referring to Figures 3 and 4, the optical axis of the marker light source 400 intersects with the optical axis of the camera module 200 to form a first intersection point 410, which is located at the near-field boundary 220 or the far-field boundary 230. It can be understood that the first intersection point 410 is a virtual point located in the area in front of the lens of the camera module 200, as shown in Figures 3, 5, and 7, where L1 is the optical axis of the camera module 200 and L2 is the optical axis of the marker light source 400.

[0044] In some embodiments, the image captured by the camera module 200 includes a range marker 510, which is spaced apart from the indicator marker 210. When the first intersection point 410 is located at the near-field boundary 220, the optical axis of the marker light source 400 intersects with the range marker 510 in the image captured at the far-field boundary 230. When the first intersection point 410 is located at the far-field boundary 230, the optical axis of the marker light source 400 intersects with the range marker 510 in the image captured at the near-field boundary 220. For example, the intersection of the optical axis of the marker light source 400 and the range marker 510 forms a second intersection point 430. That is, one of the first intersection point 410 and the second intersection point 430 is located at the near-field boundary 220, while the other is located at the far-field boundary 230.

[0045] Since the optical axis of the marker light source 400 intersects the optical axis of the camera module 200 at the first intersection point 410, and the optical axis of the marker light source 400 intersects the range mark 510 at the second intersection point 430, the optical axis of the marker light source 400 between the first intersection point 410 and the second intersection point 430 is located between the near-field boundary 220 and the far-field boundary 230. This means that when the camera module 200 captures an image located between the near-field boundary 220 and the far-field boundary 230, it is possible to obtain an image in which the marker spot 420 is located between the indicator mark 210 and the range mark 510 (see Figures 7 and 8).

[0046] When the camera module 200 acquires an image of the target, if the marker spot 420 is located between the range marker 510 and the indicator marker 210, it indicates that the target is located between the near-field boundary 220 and the far-field boundary 230. In other words, the target is within the clear imaging area 240 of the camera module 200, and the acquired target image will be clear. Therefore, the operator can determine the position between the target and the camera module 200 by observing the relationship between the marker spot 420 and the range marker 510 and indicator marker 210 in the image of the camera module 200. By ensuring that the marker spot 420 is located within the area between the range marker 510 and the indicator marker 210, a clear target image can be obtained.

[0047] It should be noted that in the image captured by the camera module 200, the marker spot 420, the indicator mark 210 and the range mark 510 may be located on the same straight line (see Figure 5) or they may not be located on the same straight line.

[0048] If the marker spot 420 is located on the same straight line, it facilitates the determination of its positional relationship with the indicator mark 210 and the range mark 510, thus providing the doctor with a more intuitive reference. If they are not on the same straight line, the marker spot 420 will still be located in the area between the indicator mark 210 and the range mark 510. This ensures that the doctor can effectively identify the relative position between the target and the camera module 200 when observing the image, regardless of whether the spot is on the same straight line as other marks. Therefore, the relative position of the marker spot 420 can provide the doctor with important positioning information, helping them to make more accurate judgments. This flexibility is of great significance in practical applications, helping to optimize the operation of the endoscope 10 and improve imaging results.

[0049] In an optional embodiment, referring to Figures 2 and 4, an indicator mark 210 is disposed on the lens of the camera module 200, with the optical axis of the camera module 200 passing through the center point of the indicator mark 210. The indicator mark 210 is used to block light of at least a portion of its wavelength. Exemplarily, the indicator mark 210 is etched, pasted, or printed at the center of the lens of the camera module 200. This ensures that the optical axis of the camera module 200 passes through the center of the mark. The color and transparency of the indicator mark 210 can also be adjusted to create a clear visual contrast in the acquired image, thereby enhancing its visibility.

[0050] When the camera module 200 acquires images, since the indicator mark 210 is located at the center of the lens, the acquired image will contain the corresponding indicator mark 210. By blocking some wavelengths of light, the indicator mark 210 appears more prominent in the image, helping doctors to more accurately determine the mark's location. For example, if a cross mark is printed at the center of the lens, a cross-shaped indicator mark 210 will appear in the image acquired by the camera module 200 (see Figure 10). Since the indicator mark 210 is located at the center of the lens, it will also be centered in the acquired image, which helps doctors quickly locate and determine the target's position when observing the image.

[0051] In an optional embodiment, a range marker 510 is disposed on the lens of the camera module 200 (not shown). In the image captured by the camera module 200 in the clear imaging area 240, the marker spot 420 is located in the area between the range marker 510 and the indicator marker 210. Exemplarily, the range marker 510 may be designed as a straight line, curve, cross, or other geometric shape. These markers may be applied to the surface of the lens of the camera module 200 by etching, printing, or pasting to enhance their visibility in the image.

[0052] The color and transparency of the range mark 510 can be adjusted as needed to ensure a clear visual contrast in the acquired image. For example, a cross-shaped range mark 510 can be printed on the lens of the camera module 200, with a certain distance between it and the indicator mark 210. In this way, the indicator mark 210 and the range mark 510 will be clearly displayed in the image acquired by the camera module 200, and because the indicator mark 210 and the range mark 510 differ in size and color, doctors can easily distinguish between the two marks.

[0053] In some designs, the range marker 510 has a first axis parallel to the optical axis of the camera module 200. This first axis intersects the optical axis of the marker light source 400, forming a second intersection point 430. One of the second intersection point 430 and the first intersection point 410 is located at the near-field boundary 220, and the other is located at the far-field boundary 230. This design provides the doctor with a clear reference frame, aiding in determining the distance between the target and the camera module 200.

[0054] In an optional embodiment, referring to Figures 2 and 3, the front-end assembly further includes a range light source 500 disposed on the front-end housing 100. The range light source 500 is used to form a range mark 510 within the image acquisition area of ​​the camera module 200. Specifically, the range mark 510 is generated by the illumination of the range light source 500, providing a clear visual guide to help doctors quickly identify the target location when observing the image. In the figures, L3 is the optical axis of the range light source 500.

[0055] In the image acquired by the camera module 200 in the clear imaging area 240, the marker spot 420 is located in the region between the range marker 510 and the indicator marker 210. This design ensures that the surgeon can visually determine the relative position of the object to the camera module 200 through the marker spot 420 in the image. This setup not only improves image readability but also enhances the accuracy and efficiency of the surgeon's operations in a dynamic surgical environment.

[0056] For example, a range light source 500 is configured on the front housing 100 to illuminate and generate range markings 510. This range light source 500 can be of different light source types, such as LED lights, lasers, or other suitable lighting devices, the selection of which depends on the actual application environment and requirements.

[0057] The illumination angle and intensity of the range light source 500 can be adjusted to provide optimal marking results in different surgical environments. By adjusting the brightness of the range light source 500, the surgeon can achieve consistent visibility in bright or dim environments. For example, in a darker internal environment, the range light source 500 can enhance the salience of the range mark 510, thereby ensuring that the surgeon can clearly identify the range mark 510 in the image.

[0058] The range marker 510 can be designed in various shapes and colors according to the characteristics of the range light source 500 to create a clear visual contrast in the image. For example, the range marker 510 can be designed as a dot, a cross, or other geometric shape, or even a dynamically changing light spot to attract the doctor's attention. Different colors and patterns will help doctors quickly identify the markers in complex surgical scenarios and avoid visual interference.

[0059] Referring to Figures 3 and 4, when the target is located between the camera module 200 and the near-field boundary 220, the marker spot 420 in the image captured by the camera module 200 is located outside the area marked by the range marker 510 and the indicator marker 210. In this case, the image captured by the camera module 200 is unclear, which may make it difficult for doctors to accurately determine the location of the target.

[0060] Referring to Figures 5 and 6, the target is located on the side of the distant boundary 230 away from the camera module 200. In the image captured by the camera module 200, the marker spot 420 is also located in the area outside the range marker 510 and the indicator marker 210.

[0061] Referring to Figures 7 and 8, when the target is located within the clear imaging area 240 of the camera module 200, the marker spot 420 in the image acquired by the camera module 200 is located in the area between the range marker 510 and the indicator marker 210. At this time, the image acquired by the camera module 200 is clear, and the doctor can clearly identify the location of the target and make an accurate judgment based on the relative position of the marker, thereby optimizing the observation and treatment effect of the target.

[0062] In an optional embodiment, referring to FIG9, the optical axis of the range light source 500 intersects the optical axis of the camera module 200, and the intersection point is located outside the clear imaging area 240. This means that the illumination direction of the range light source 500 forms a certain angle with the shooting direction of the camera module 200. When the camera module 200 is close to the near-field boundary 220, the distance between the indicator mark 210 and the range mark 510 in the acquired image is relatively large. However, when it is close to the far-field boundary 230, the distance between the two in the acquired image is relatively small.

[0063] Specifically, near the near-field boundary 220, the target image captured by the camera module 200 is typically larger, while near the far-field boundary 230, the target image is relatively smaller. Therefore, in larger target images, the greater distance between the indicator mark 210 and the range mark 510 facilitates clearer identification of the marks by the doctor, avoiding visual confusion. Conversely, in images of smaller targets, the closer distance between the indicator mark 210 and the range mark 510 prevents the range mark 510 from being outside the target area when the two marks are far apart.

[0064] The core of this structural design lies in ensuring that the indicator marker 210 and the range marker 510 are always within the target area, enabling the surgeon to accurately determine the actual distance between the target and the camera module 200, thereby acquiring clearer images. By ensuring that the relative positional relationship between the indicator marker 210 and the range marker 510 is maintained under different distance conditions, the surgeon can make rapid adjustments in a dynamic surgical environment, improving the accuracy of observation and judgment.

[0065] In an optional embodiment, referring to Figures 5 and 6, the optical axis of the range light source 500 is parallel to the optical axis of the camera module 200. This design allows the range light source 500 to form a clear and consistent range mark 510 within the image acquisition area of ​​the camera module 200. This structure ensures that the spacing between the range mark 510 and the indicator mark 210 remains consistent at different shooting distances, thereby facilitating doctors to quickly determine the relationship between the target's location and the camera module 200.

[0066] With this configuration, doctors can more intuitively understand the actual location of the target when observing the images. Since the parallel optical axis of the range light source 500 does not interfere with the imaging of the camera module 200, doctors can clearly see the boundaries of the imaging area, which is crucial for optimizing adjustments and operations during the surgical procedure.

[0067] In an optional embodiment, referring to Figures 7 and 8, the light emitted by the range light source 500 is parallel light. This configuration allows the range light source 500 to form range markers 510 of consistent size and brightness within the image acquisition area of ​​the camera module 200, facilitating accurate judgment by the doctor during observation.

[0068] In an optional embodiment, referring to Figures 1 and 2, the range light source 500 is located on one side of the camera module 200, and the marker light source 400 is located on the other side of the camera module 200. Since the optical axis of the range light source 500 needs to intersect with the optical axis of the marker light source 400, this arrangement can increase the included angle between the two within the limited space of the front housing 100. This configuration helps to effectively generate the indicator marks 210 and range marks 510 with the required spacing.

[0069] Furthermore, separating the range light source 500 and the marker light source 400 not only avoids heat dissipation problems caused by concentrated heat, but also allows the front housing 100 to maintain a smaller size. While ensuring functionality, the optimized size of the device makes the endoscope 10 more flexible and easier to use in confined operating environments.

[0070] In an optional embodiment, the light emitted by the marker light source 400 is parallel light. In this way, the marker light source 400 can form marker spots 420 of uniform size and brightness within the image acquisition area, which helps doctors quickly identify and locate the markers.

[0071] In an optional embodiment, referring to Figures 1 and 2, the light source 400 and the illumination source 300 are located on the same side of the camera module 200. This design not only ensures better illumination conditions for the clear imaging area 240, but also improves the efficiency of doctors' operations in complex environments and ensures the quality of the captured images.

[0072] Specifically, since the optical axis of the marker light source 400 intersects with the optical axis of the camera module 200, the illumination light source 300 is positioned on the same side of the camera module 200, particularly on the side of the marker light source 400 away from the camera module 200. This configuration allows the optical axis of the marker light source 400 to oriented away from the illumination light source 300, avoiding a situation where the optical axes of the illumination light source 300 and the marker light source 400 coincide within the clear imaging area 240. If they coincide, the illumination light source 300 would be too bright, affecting the visibility of the marker spot 420. This makes it easier for doctors to identify the marker spot 420.

[0073] In one optional embodiment, the optical axis of the illumination source 300 intersects the optical axis of the camera module 200, and the intersection point is located outside the clear imaging area 240. This design can avoid interference from the illumination source 300 on the imaging of the camera module 200, thereby improving the clarity and quality of the image.

[0074] In another alternative embodiment, the optical axis of the illumination source 300 is parallel to the optical axis of the camera module 200, and the optical axis of the illumination source 300 intersects the optical axis of the marker source 400, with the intersection located outside the clear imaging area 240. This configuration also helps to maintain image sharpness and avoids brightness concentration on the area illuminated by the marker source 400, thereby improving the visibility of the marker spot 420.

[0075] Specifically, the illumination source 300 is a point source, with the highest brightness at its center. If the center of the point source coincides with the area illuminated by the marking source 400, it may be difficult for doctors to distinguish the marking spot 420 when observing the image. Therefore, by designing the intersection of the illumination source 300 and the marking source 400 to be located outside the clear imaging area 240, this overlap can be avoided to some extent, thereby improving the recognizability of the marking spot 420.

[0076] The second aspect of this embodiment describes an endoscope in detail.

[0077] Referring to Figure 11, an embodiment of this application provides an endoscope 10, including a front-end component as described in the above embodiment. This endoscope 10 thus possesses the beneficial effects of the aforementioned front-end component, which will not be elaborated further here. The endoscope 10 referred to in this application embodiment can be a bronchoscope, pyeloscope, esophagoscope, gastroscope, colonoscope, otoscope, rhinoscope, oral endoscope, laryngoscope, colposcope, laparoscope, arthroscope, etc. This application embodiment does not specifically limit the type of endoscope 10.

[0078] The third aspect of this embodiment provides a detailed description of an image acquisition method.

[0079] This application provides an image acquisition method applied to an endoscope described in the above embodiments, comprising the following steps:

[0080] S001. The camera module 200 acquires images of the area where the target is located.

[0081] S002. Adjust the position of the front housing 100 so that the indicator mark 210 in the image captured by the camera module 200 is centered on the target.

[0082] S003. Adjust the distance between the front housing 100 and the target so that the marker spot 420 in the image captured by the camera module 200 is in the area between the indicator mark 210 and the range mark 510, thereby obtaining a clear image of the target.

[0083] The fourth aspect of this embodiment provides a detailed description of an image analysis method.

[0084] The embodiments of this application provide an image analysis method, including an image acquisition method described in the above embodiments, which determines the size of the target based on the relative size of the target and the marker spot 420 in a clear image.

[0085] For example, the marker spot 420 is generated by parallel light illumination, and the size of the marker spot 420 is fixed after it illuminates the target location. The area of ​​the target area can be calculated by comparing the area of ​​the marker spot 420 with the area of ​​the target area in the image acquired by the camera module 200.

[0086] For example, this method can determine the size of the stone, helping doctors assess its volume for effective removal and preventing situations where misjudgment prevents stone removal through the ureter. This not only improves surgical efficiency and effectiveness but also reduces patient discomfort and surgical risks. Through this design, the endoscope provides more precise information during target analysis and processing, ensuring a higher success rate and greater safety for the procedure.

[0087] It is understood that in this embodiment, target 20 can be a lesion, foreign body, etc., and the specific type is not limited. This method is applicable to various scenarios of foreign body detection in medical or tubular objects.

Claims

1. A front-end component for use in an endoscope (10), characterized in that, include: Front housing (100); A camera module (200) is disposed on the front housing (100) for capturing images. The camera module (200) has a preset near-field boundary (220) and far-field boundary (230) to define the clear imaging area (240) of the camera module (200). An illumination source (300) is disposed in the front end housing (100) for illumination; as well as A marker light source (400) is disposed in the front housing (100) and is used to form a marker light spot (420) in the image acquisition area of ​​the camera module (200). The image captured by the camera module (200) has an indicator mark (210) and a range mark (510). The indicator mark (210) is used to indicate the optical axis of the camera module (200), and the range mark (510) is spaced apart from the indicator mark (210). The optical axis of the marker light source (400) intersects with the optical axis of the camera module (200) to form a first intersection point (410), which is located at the near-field boundary (220) or the far-field boundary (230). When the first intersection point (410) is located at the near boundary (220), in the image acquired at the far boundary (230), the optical axis of the marker light source (400) intersects with the range marker (510); When the first intersection point (410) is located at the far horizon (230), in the image acquired at the near horizon (220), the optical axis of the marker light source (400) intersects with the range marker (510).

2. A front-end component according to claim 1, characterized in that, The indicator mark (210) is disposed on the lens of the camera module (200), the optical axis of the camera module (200) passes through the center point of the indicator mark (210), and the indicator mark (210) is used to block light of at least a portion of the wavelength band; And / or, the range marker (510) is disposed on the lens of the camera module (200), and the marker spot (420) is located in the area between the range marker (510) and the indicator marker (210) in the image captured by the camera module (200) in the clear imaging area (240).

3. A front-end component according to claim 1, characterized in that, It also includes a range light source (500) disposed on the front housing (100), the range light source (500) being used to form the range mark (510) within the image acquisition area of ​​the camera module (200); In the image captured by the camera module (200) in the clear imaging area (240), the marker spot (420) is located in the area between the range marker (510) and the indicator marker (210).

4. A front-end component according to claim 3, characterized in that, The optical axis of the range light source (500) intersects with the optical axis of the camera module (200), and the intersection point is located outside the clear imaging area (240); Alternatively, the optical axis of the range light source (500) is parallel to the optical axis of the camera module (200).

5. A front-end component according to claim 4, characterized in that, The light emitted by the range light source (500) is parallel light; And / or, the range light source (500) is located on one side of the camera module (200), and the marker light source (400) is located on the other side of the camera module (200).

6. A front-end component according to claim 1, characterized in that, The light emitted by the marker light source (400) is parallel light; And / or, the marker light source (400) and the illumination light source (300) are located on the same side of the camera module (200).

7. A front-end component according to claim 1, characterized in that, The optical axis of the illumination source (300) intersects with the optical axis of the camera module (200), and the intersection point is located outside the clear imaging area (240); Alternatively, the optical axis of the illumination source (300) is parallel to the optical axis of the camera module (200), and the optical axis of the illumination source (300) intersects with the optical axis of the marker light source (400), with the intersection located outside the clear imaging area (240).

8. An endoscope, characterized in that, Includes a front-end component as described in any one of claims 1-7.

9. An image acquisition method, characterized in that, The method of applying the endoscope according to claim 8 includes the following steps: Images of the area where the target (20) is located are acquired by the camera module (200); Adjust the position of the front housing (100) so that the indicator mark (210) in the image captured by the camera module (200) is at the center of the target (20); Adjust the distance between the front housing (100) and the target (20) so that the marker spot (420) in the image acquired by the camera module (200) is located in the area between the indicator mark (210) and the range mark (510), thereby obtaining a clear image of the target (20).

10. An image analysis method, characterized in that, The image acquisition method of claim 9 determines the size of the target (20) based on the relative size of the target (20) and the marker spot (420) in the clear image.

Images