Illumination uniformizing device for endoscope and endoscope

Abstract

The application discloses an illumination homogenizing device of an endoscope and the endoscope, and relates to the technical field of endoscope illumination. The illumination homogenizing device of the endoscope comprises a light guide rod with no optical power, a first lens with positive optical power and a second lens with positive optical power which are sequentially arranged from a light source side to a receiving side. The core thickness of the light guide rod is d1, the diameter of the light guide rod is D1, and the following relationship is satisfied: 1.2 < |d1 / D1| < 1.6. The focal length of the first lens is f2, the focal length of the second lens is f3, and the following relationship is satisfied: 1.2 < |f2 / f3| < 1.6. The illumination homogenizing device of the endoscope can solve the problems of poor uniformity, prominent dark corner phenomenon and image quality decline existing in the current endoscope illumination system.

Description

Technical Field

[0001] This application relates to the field of endoscopic illumination technology, and more specifically, to an illumination homogenizing device for an endoscope and an endoscope. Background Technology

[0002] In modern medical systems, endoscopes are crucial diagnostic and therapeutic devices, widely used in various surgical procedures and examinations. For endoscopes, the performance of the illumination system plays a decisive role in providing doctors with clear and accurate images.

[0003] Traditional endoscopic illumination systems typically rely on an illumination component at the tip to illuminate the objective lens's field of view. However, limited by existing illumination lens designs, this system suffers from a series of significant problems:

[0004] First, poor illumination uniformity: The existing illumination lens selection is unreasonable, resulting in significant differences in illuminance values ​​between the central and peripheral areas during endoscopic imaging, especially under large field-of-view conditions, where the illuminance in the peripheral areas is severely insufficient.

[0005] Second, vignetting is a prominent issue: when the endoscopic objective lens has a large field of view, vignetting is very likely to appear in the edge areas of the image. This problem not only seriously reduces image quality but may also prevent medical staff from accurately identifying the lesion site, thus adversely affecting the treatment outcome.

[0006] Third, image quality deteriorates: the dark corners of the image become blurry, greatly increasing the difficulty of operation for medical staff, especially in complex surgical environments, which seriously affects the accuracy and efficiency of the surgery. Utility Model Content

[0007] The purpose of this application is to provide an illumination homogenizing device for an endoscope and an endoscope that can solve the problems of poor uniformity, prominent vignetting, and degraded image quality in existing endoscope illumination systems.

[0008] The embodiments of this application are implemented as follows:

[0009] A first aspect of this application provides an illumination homogenizing device for an endoscope, comprising a light guide rod with no optical power, a first lens with positive optical power, and a second lens with positive optical power, arranged sequentially from the light source side to the receiving side; wherein the core thickness of the light guide rod is d1, the diameter of the light guide rod is D1, and they satisfy the following relationship: 1.2 < |d1 / D1| < 1.6; the focal length of the first lens is f2, and the focal length of the second lens is f3, and they satisfy the following relationship: 1.2 < |f2 / f3| < 1.6. This illumination homogenizing device for an endoscope can solve the problems of poor uniformity, prominent vignetting, and degraded image quality in existing endoscope illumination systems.

[0010] In one possible implementation, the radius of curvature of the optical surface of the first lens near the light guide is R3, and the radius of curvature of the optical surface of the first lens away from the light guide is R4, and the following relationship is satisfied: R3=R4, and the diameter of the first lens is D2, and the following relationship is satisfied: |R3 / D2|≥0.55.

[0011] In one possible implementation, the radius of curvature of the optical surface of the second lens near the light guide rod is R5, and the radius of curvature of the optical surface of the second lens away from the light guide rod is R6, satisfying the following relationship: R5 ≠ R6, the diameter of the second lens is D3, and the following relationships are satisfied: |R5 / D3|≥0.55 and |R6 / D3|≥0.55.

[0012] As one possible implementation, the core thickness d1 of the light guide rod satisfies the following relationship: 1.2 < d1 < 2.9, and the refractive index of the light guide rod is 1.4 to 1.6 and the Abbe number is 60 to 80.

[0013] As one possible implementation, the first lens is a biconvex lens with a refractive index of 1.8 to 2.0 and an Abbe number of 30 to 50, and the focal length f2 of the first lens satisfies the following relationship: 0.7 < f2 < 1.4.

[0014] As one possible implementation, the second lens is a biconvex lens with a refractive index of 1.8 to 2.0 and an Abbe number of 30 to 50, and the focal length f3 of the second lens satisfies the following relationship: 0.4 < f3 < 1.0.

[0015] As one possible implementation, the beam angle of the device is greater than or equal to 140°, and the beam field of view of the device is greater than or equal to 170°.

[0016] In one possible implementation, the light guide rod, the first lens, and the second lens are coaxially arranged and adjacent optical surfaces abut against each other.

[0017] As one possible implementation, it also includes a lens barrel and a light source, wherein the light source, the light guide rod, the first lens and the second lens are all disposed inside the lens barrel.

[0018] A second aspect of this application provides an endoscope including the aforementioned illumination homogenizing device for the endoscope. This illumination homogenizing device for the endoscope can solve the problems of poor uniformity, prominent vignetting, and degraded image quality in existing endoscope illumination systems.

[0019] The beneficial effects of the embodiments of this application include:

[0020] The illumination homogenizing device for this endoscope includes a light guide rod with no optical power, a first lens with positive optical power, and a second lens with positive optical power, arranged sequentially from the light source side to the receiving side. The core thickness of the light guide rod is d1, and its diameter is D1, satisfying the following relationship: 1.2 < |d1 / D1| < 1.6. The focal length of the first lens is f2, and the focal length of the second lens is f3, satisfying the following relationship: 1.2 < |f2 / f3| < 1.6. The illumination homogenizing device for the endoscope provided in this application, through the initial transmission and distribution of light by the light guide rod, and the further convergence and adjustment of light by two lenses with specific focal length ratios (i.e., the first lens and the second lens), enables a more uniform distribution of light projected onto the endoscope objective lens field of view. This effectively reduces the difference in illuminance values ​​between the central and peripheral regions, overcoming the problem of uneven illumination in existing lighting systems. Furthermore, a well-designed lens focal length ratio and light guide parameters ensure that light can cover the entire field of view relatively evenly even at a wide field of view, reducing vignetting caused by insufficient light at the edges. This helps improve the overall image quality, allowing medical staff to clearly observe the entire field of view and accurately determine the location of lesions. Based on this, the improved illumination uniformity and reduced vignetting significantly enhance the image quality captured by the endoscope. Images no longer have blurry vignetting areas; details are clearer, and contrast is more balanced. This greatly reduces the difficulty of operation for medical staff, especially in complex surgical environments, enabling more accurate diagnosis and treatment, and improving surgical success rates and treatment outcomes. Attached Figure Description

[0021] To more clearly illustrate the technical solutions of the embodiments of this application, the accompanying drawings used in the embodiments will be briefly introduced below. It should be understood that the following drawings only show some embodiments of this application and should not be regarded as a limitation of the scope. For those skilled in the art, other related drawings can be obtained based on these drawings without creative effort.

[0022] Figure 1 A schematic diagram of the illumination homogenizing device for an endoscope provided in the first embodiment of this application;

[0023] Figure 2 A light distribution curve diagram of the illumination homogenizing device for an endoscope provided in the first embodiment of this application;

[0024] Figure 3 Illuminance diagram at 50mm for the illumination homogenizing device of the endoscope provided in the first embodiment of this application;

[0025] Figure 4A schematic diagram of the illumination homogenizing device for an endoscope provided in the second embodiment of this application;

[0026] Figure 5 A light distribution curve diagram of the illumination homogenizing device for an endoscope provided in the second embodiment of this application;

[0027] Figure 6 Illuminance diagram at 50mm for the illumination homogenizing device of the endoscope provided in the second embodiment of this application;

[0028] Figure 7 A schematic diagram of the illumination homogenizing device for an endoscope provided in the third embodiment of this application;

[0029] Figure 8 A light distribution curve diagram of the illumination homogenizing device for an endoscope provided in the third embodiment of this application;

[0030] Figure 9 Illuminance diagram at 50mm for the illumination homogenizing device of the endoscope provided in the third embodiment of this application.

[0031] Icons: 100 - Illumination and homogenization device for endoscope; 10 - Light guide rod; 20 - First lens; 30 - Second lens. Detailed Implementation

[0032] To make the objectives, technical solutions, and advantages of the embodiments of this application clearer, 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. The components of the embodiments of this application described and shown in the accompanying drawings can generally be arranged and designed in various different configurations. It should be noted that similar reference numerals and letters in the following drawings denote similar items; therefore, once an item is defined in one drawing, it does not need to be further defined and explained in subsequent drawings.

[0033] In the description of this application, it should be noted that the terms "center," "upper," "lower," "left," "right," "vertical," "horizontal," "inner," and "outer," etc., indicate the orientation or positional relationship based on the orientation or positional relationship shown in the accompanying drawings, or the orientation or positional relationship commonly used when the product is in use. These terms are used only for the convenience of describing this application and for simplifying the description, and do not indicate or imply that the device or element referred to must have a specific orientation, or be constructed and operated in a specific orientation. Therefore, they should not be construed as limitations on this application. Furthermore, the terms "horizontal," "vertical," etc., do not indicate that the component must be absolutely horizontal or suspended, but can be slightly tilted. The terms "first," "second," and "third," etc., are used only to distinguish descriptions and should not be construed as indicating or implying relative importance.

[0034] In the description of this application, it should also be noted that, unless otherwise expressly specified and limited, the terms "set up," "install," "connect," and "link" should be interpreted broadly. For example, they can refer to a fixed connection, a detachable connection, or an integral connection; they can refer to a mechanical connection or an electrical connection; they can refer to a direct connection or an indirect connection through an intermediate medium; and they can refer to a connection within two components. Those skilled in the art can understand the specific meaning of the above terms in this application based on the specific circumstances.

[0035] Please refer to the reference. Figures 1 to 9 This application provides an illumination homogenizing device 100 for an endoscope, comprising a light guide rod 10 with no optical power, a first lens 20 with positive optical power, and a second lens 30 with positive optical power, arranged sequentially from the light source side to the receiving side. The core thickness of the light guide rod 10 is d1, and its diameter is D1, satisfying the following relationship: 1.2 < |d1 / D1| < 1.6. The focal length of the first lens 20 is f2, and the focal length of the second lens 30 is f3, satisfying the following relationship: 1.2 < |f2 / f3| < 1.6. This illumination homogenizing device 100 for an endoscope can solve the problems of poor uniformity, prominent vignetting, and degraded image quality in existing endoscope illumination systems.

[0036] It should be noted that, as Figure 1 , Figure 4 and Figure 7 As shown, the illumination homogenizing device 100 of the endoscope includes a light guide rod 10, a first lens 20, and a second lens 30 arranged sequentially from the light source side to the receiving side. The light guide rod 10 has no optical power and its function is to conduct light emitted from the light source. By limiting the ratio of the core thickness d1 to the diameter D1 of the light guide rod 10 to 1.2 < |d1 / D1| < 1.6, scattering and light energy loss are reduced during beam transmission within the light guide rod 10, optimizing the initial beam distribution and providing a uniform incident light field for subsequent lenses. This ratio range helps optimize the light propagation path within the light guide rod 10, reducing light scattering and loss, and ensuring relatively uniform light output from the light guide rod 10. For example, the ratio of the core thickness d1 to the diameter D1 of the light guide rod can be specifically designed as 1.3, 1.4, or 1.5, etc.

[0037] The first lens 20 and the second lens 30 have positive optical power, which helps to converge light. By limiting the ratio of the focal length f2 of the first lens 20 to the focal length f3 of the second lens 30 to 1.2 < |f2 / f3| < 1.6, the refraction and convergence angles of the light can be precisely controlled. This allows the light from the light guide rod 10 to be more evenly distributed in the objective lens field of view after passing through the first lens 20 and the second lens 30, avoiding a sudden drop in edge illumination. The above ratio range allows the lenses to reasonably adjust the light, avoiding excessive convergence or divergence, thereby improving illumination uniformity and reducing vignetting. For example, the ratio of the focal length f2 of the first lens 20 to the focal length f3 of the second lens 30 can be 1.3, 1.4, or 1.5, etc., without specific limitations.

[0038] The illumination homogenizing device 100 for endoscopes provided in this application, through the initial transmission and distribution of light by the light guide rod 10, and the further convergence and adjustment of light by two positive power lenses (i.e., the first lens 20 and the second lens 30) with a specific focal length ratio, enables the light finally projected onto the field of view of the endoscope objective lens to be distributed more evenly, effectively reducing the difference in illuminance values ​​between the central and edge areas, and overcoming the problem of uneven illumination existing in the existing illumination system.

[0039] Furthermore, the well-designed lens focal length ratio and the parameters of the light guide rod 10 ensure that light can cover the entire field of view relatively evenly even at a large field of view, reducing vignetting in edge areas due to insufficient light. This helps improve the overall image quality, allowing medical personnel to clearly observe the entire field of view and accurately determine the location of lesions.

[0040] Building upon this, the image quality captured by the endoscope is significantly improved due to the enhanced uniformity of illumination and the reduction of vignetting. Images no longer exhibit blurry, vignetted areas; details are clearer, and contrast is more balanced. This greatly reduces the operational difficulty for medical staff, especially in complex surgical environments, enabling more accurate diagnosis and treatment, and improving surgical success rates and treatment outcomes.

[0041] As one possible implementation, the radius of curvature of the optical surface of the first lens 20 near the light guide rod 10 is R3, and the radius of curvature of the optical surface of the first lens 20 away from the light guide rod 10 is R4, and the following relationship is satisfied: R3=R4.

[0042] It should be noted that, as Figure 1 , Figure 4 and Figure 7As shown, the first lens 20 has two optical surfaces: one near the light guide rod 10, with a radius of curvature defined as R3; and the other away from the light guide rod 10, with a radius of curvature defined as R4. The fact that R3 and R4 are equal means that these two optical surfaces of the first lens 20 have the same degree of curvature, and in terms of shape, the first lens 20 is symmetrical about its central plane. This symmetrical lens structure provides specific light refraction and convergence characteristics in an optical system.

[0043] When light rays exit the light guide rod 10 and strike the first lens 20, the refraction paths of the light rays within the first lens 20 are relatively symmetrical because the radii of curvature of the two optical surfaces of the first lens 20 are equal. This helps to make the light rays converge or diverge more regularly, avoiding uneven refraction caused by the different radii of curvature of the two optical surfaces of the first lens 20, thereby improving the utilization efficiency of the light rays and allowing the light rays after passing through the first lens 20 to be more evenly distributed in the subsequent optical path.

[0044] Furthermore, the symmetrical lens structure helps reduce light scattering and distortion during propagation. In the illumination homogenizing device 100 of this endoscope, this characteristic allows light to be directed towards the second lens 30 at a more uniform angle and intensity after passing through the first lens 20, thereby improving the uniformity of the entire illumination system. This helps solve the problem of poor illumination uniformity in existing endoscope illumination systems, providing more uniform illumination for the endoscope, enabling doctors to observe the details of internal tissues more clearly, and reducing misdiagnosis or missed diagnosis caused by uneven illumination.

[0045] Furthermore, two optical surfaces with the same radius of curvature can reduce aberrations and distortions to some extent. Aberrations and distortions lead to a decrease in image quality, while this structure of the first lens 20 helps maintain the propagation characteristics of light, making imaging clearer and more accurate, reducing image distortion and blurring, improving the quality of images acquired by the endoscope, and providing a more reliable basis for medical diagnosis.

[0046] From a design and manufacturing perspective, using two optical surfaces with the same radius of curvature simplifies the design and manufacturing process of the first lens 20. Compared to asymmetrical lens structures, the symmetrical structure of the first lens 20 makes optical design calculations and optimization easier, facilitates processing and quality control during manufacturing, reduces production costs and manufacturing difficulty, and helps improve product consistency and stability.

[0047] As one possible implementation, the diameter of the first lens 20 is D2, and it satisfies the following relationship: |R3 / D2|≥0.55. Since the radii of curvature of the two optical surfaces of the first lens 20 are equal, i.e., R3=R4, it can also be said that the diameter D2 of the first lens 20 satisfies the following relationship: |R4 / D2|≥0.55. For example, the ratio of the radius of curvature R3 to the diameter D2 of the first lens 20 can be 0.6, 0.7, or 0.8, etc.

[0048] It should be noted that, as Figure 1 , Figure 4 and Figure 7 As shown, by limiting the ratio of the radius of curvature R3 to the diameter D2 of the first lens 20 to |R3 / D2|≥0.55, the light emitted from the light guide rod 10 can be converged more effectively. This ratio range helps reduce light reflection and scattering losses on the surface of the first lens 20, allowing more light to pass through the first lens 20 along the designed path, thereby improving light utilization efficiency and providing a more sufficient amount of light for subsequent illumination.

[0049] Furthermore, it helps to make the propagation of light within the first lens 20 more regular, thereby improving the uniformity of light distribution across the entire field of view. This aforementioned range allows light to cover all areas of the objective lens's field of view more evenly, reducing illuminance differences between the central and peripheral areas, avoiding localized over-brightness or under-brightness, and solving the problem of uneven illumination in existing endoscopic illumination systems.

[0050] Furthermore, it helps optimize the optical structure of the first lens 20, making the refraction of light through it more ideal, thereby reducing aberrations. This results in a clearer and more accurate final image, improving the quality of endoscopic images and enabling medical personnel to observe lesions more accurately and make more precise diagnoses.

[0051] In one possible implementation, the radius of curvature of the optical surface of the second lens 30 near the light guide rod 10 is R5, and the radius of curvature of the optical surface of the second lens 30 away from the light guide rod 10 is R6, and the following relationship is satisfied: R5≠R6. The diameter of the second lens 30 is D3, and the following relationship is satisfied: |R5 / D3|≥0.55 and |R6 / D3|≥0.55.

[0052] It should be noted that, as Figure 1 , Figure 4 and Figure 7As shown, the second lens 30 has two optical surfaces: one near the light guide rod 10, with a radius of curvature defined as R5; and the other away from the light guide rod 10, with a radius of curvature defined as R6. The unequal values ​​of R5 and R6 indicate that the curvature of these two optical surfaces of the second lens 30 differs, meaning that the second lens 30 is not a symmetrical lens structure. This asymmetrical design allows for different refraction and control of light according to specific needs for light propagation and uniform illumination, achieving better lighting effects. For example, the optical surface of the second lens 30 near the light guide rod 10 can initially refract and adjust the light based on its angle and distribution, while the optical surface away from the light guide rod 10 can further optimize the direction and angle of light propagation, enabling the light to more uniformly cover the objective lens field of view of the endoscope, effectively improving the uniformity of illumination and reducing vignetting.

[0053] By limiting the ratio of the radii of curvature R5 and R6 of the two optical surfaces of the second lens 30 to |R5 / D3|≥0.55 and |R6 / D3|≥0.55, a suitable curvature-to-diameter ratio is ensured for each optical surface of the second lens 30. This helps enhance the second lens 30's ability to converge or diverge light, allowing light to propagate and distribute according to design requirements. With a large field of view, more light can reach the edge areas, increasing edge illumination and solving the problem of insufficient edge illumination in existing lighting systems. After the second lens 30 optimizes the light, the uniformity of illumination is significantly improved, vignetting is reduced, and the image quality acquired by the endoscope is enhanced. The images are clearer, brighter, and richer in detail, helping medical personnel to more accurately observe lesions, reducing operational difficulty, and improving the accuracy of diagnosis and treatment.

[0054] In one possible implementation, the core thickness d1 of the light guide rod 10 satisfies the following relationship: 1.2 < d1 < 2.9, the refractive index of the light guide rod 10 is 1.4 to 1.6, and the Abbe number is 60 to 80. The first lens 20 is a biconvex lens, with a refractive index of 1.8 to 2.0 and an Abbe number of 30 to 50, and the focal length f2 of the first lens 20 satisfies the following relationship: 0.7 < f2 < 1.4. The second lens 30 is a biconvex lens, with a refractive index of 1.8 to 2.0 and an Abbe number of 30 to 50, and the focal length f3 of the second lens 30 satisfies the following relationship: 0.4 < f3 < 1.0.

[0055] For example, in the first, second and third embodiments provided in this application, the specific values ​​of the core thickness d1, refractive index and Abbe number of the light guide rod 10, the refractive index and Abbe number of the first lens 20 and the refractive index and Abbe number of the second lens 30 are shown in the table below.

[0056] type surface radius of curvature thickness Refractive index Nd Abbe number Vd focal length Standard surface 1 Infinity 1.96 1.49 70.44 ∞ Standard surface 2 Infinity 0.00 Standard surface 3 1.990 0.80 1.88 40.79 1.24 Standard surface 4 -1.990 0.00 Standard surface 5 0.770 1.09 1.88 40.79 0.82 Standard surface 6 -4.200 50.00

[0057] type surface radius of curvature thickness Refractive index Nd Abbe number Vd focal length Standard surface 1 Infinity 2.69 1.49 70.44 ∞ Standard surface 2 Infinity 0.00 Standard surface 3 2.670 1.01 1.88 40.79 0.82 Standard surface 4 -2.670 0.00 Standard surface 5 0.880 1.05 1.88 40.79 0.58 Standard surface 6 -3.300 50.00

[0058] type surface radius of curvature thickness Refractive index Nd Abbe number Vd focal length Standard surface 1 Infinity 1.40 1.49 70.44 ∞ Standard surface 2 Infinity 0.00 Standard surface 3 1.42 0.57 1.88 40.79 0.82 Standard surface 4 -1.42 0.00 Standard surface 5 0.55 0.78 1.88 40.79 0.58 Standard surface 6 -3.00 50.00

[0059] As one possible implementation, the beam angle of the device is greater than or equal to 140°, and the beam field of view of the device is greater than or equal to 170°.

[0060] It should be noted that the beam angle refers to the conical angle formed by the light emitted from the light source in space. In this device, the beam angle is greater than or equal to 140°, meaning that the light emitted from the device can propagate over a relatively large angular range, forming a relatively wide beam. The beam field of view, on the other hand, refers to the angular range from which the observer can see the light emitted from the light source. In this device, the beam field of view is greater than or equal to 170°, meaning that the light emitted from the device can cover a very wide angular range in space, almost approaching a hemisphere.

[0061] In this way, the larger beam angle and field of view allow the device to illuminate a large area. In practical applications, such as endoscopy, this provides doctors with a wider field of view, enabling them to observe internal organs and tissues more comprehensively, reducing blind spots and helping to detect potential lesions or abnormalities.

[0062] Furthermore, the wide beam distribution contributes to a more uniform illumination effect. The light can be distributed more evenly within the target area, avoiding areas of excessive brightness or darkness, thus improving the quality and consistency of the illumination. This is crucial for accurately observing the details and features of objects, providing doctors with clearer and more accurate images, and aiding in accurate diagnoses.

[0063] Because a beam of light can cover a wide angular range and illuminate objects from different directions, it can effectively reduce the formation of shadows. During observation, shadows can obscure important details and affect a doctor's judgment of a condition. By reducing shadows, the outline and surface features of objects can be displayed more clearly, improving the accuracy of observation.

[0064] The wide beam field of view ensures that doctors receive sufficient light during endoscopic examinations, even from different viewing angles, guaranteeing a clear field of vision. This increases operational flexibility, allowing doctors to more freely adjust the position and angle of the endoscope for better observation of different areas, thus improving the efficiency and effectiveness of the examination.

[0065] As one possible implementation method, such as Figure 1 , Figure 4 and Figure 7 As shown, the light guide rod 10, the first lens 20 and the second lens 30 are coaxially arranged and their adjacent optical surfaces abut against each other.

[0066] It should be noted that, as Figure 1 , Figure 4 and Figure 7 As shown, the light guide rod 10, the first lens 20, and the second lens 30 are coaxially arranged. In this device, light propagates along this common axis, ensuring that the light stays on a specific path from the light guide rod 10 to the first lens 20 and then to the second lens 30, without any light deflection or scattering, thereby improving the efficiency and stability of light propagation. The adjacent optical surfaces of the light guide rod 10, the first lens 20, and the second lens 30 abut against each other, which can reduce the reflection and refraction loss of light at the interface, allowing light to be transmitted more smoothly between different optical elements, further improving the utilization rate of light.

[0067] As one possible implementation, the illumination homogenizing device 100 of the endoscope also includes a tube and a light source (not shown in the figure), and the light source, light guide rod 10, first lens 20 and second lens 30 are all disposed inside the tube.

[0068] It should be noted that the illumination homogenizing device 100 of this endoscope also includes a tube and a light source. The tube is the outer shell of the entire device, serving to protect and support the internal components. The light source is the component that generates light, providing the initial light energy for the entire illumination system. The light emitted by the light source is transmitted through a light guide rod 10, which efficiently guides the light to the area requiring illumination. The first lens 20 and the second lens 30 further process the light, such as converging and refracting, to achieve a uniform illumination effect. By placing the light source, light guide rod 10, first lens 20, and second lens 30 all inside the tube, these components can be integrated into a compact and stable structure, facilitating installation and use.

[0069] This application also provides an endoscope, including the aforementioned endoscope illumination homogenizing device 100. Since the structure and beneficial effects of the endoscope illumination homogenizing device 100 have been described in detail in the foregoing embodiments, they will not be repeated here.

[0070] The above description is merely an optional embodiment of this application and is not intended to limit this application. Various modifications and variations can be made to this application by those skilled in the art. Any modifications, equivalent substitutions, improvements, etc., made within the spirit and principles of this application should be included within the protection scope of this application.

[0071] It should also be noted that the various specific technical features described in the above embodiments can be combined in any suitable manner without contradiction. In order to avoid unnecessary repetition, this application will not describe the various possible combinations separately.

Claims

1. An illumination homogenizing device for an endoscope, characterized in that, The light guide includes a light guide rod with no optical power, a first lens with positive optical power, and a second lens with positive optical power, arranged sequentially from the light source side to the receiving side. The core thickness of the light guide rod is d1, the diameter of the light guide rod is D1, and they satisfy the following relationship: 1.2 < |d1 / D1| < 1.

6. The focal length of the first lens is f2, and the focal length of the second lens is f3, and they satisfy the following relationship: 1.2 < |f2 / f3| < 1.

6.

2. The illumination homogenizing device for an endoscope according to claim 1, characterized in that, The radius of curvature of the optical surface of the first lens near the light guide is R3, and the radius of curvature of the optical surface of the first lens away from the light guide is R4, and they satisfy the following relationship: R3=R4. The diameter of the first lens is D2, and it satisfies the following relationship: |R3 / D2|≥0.

55.

3. The illumination homogenizing device for an endoscope according to claim 1, characterized in that, The radius of curvature of the optical surface of the second lens near the light guide rod is R5, and the radius of curvature of the optical surface of the second lens away from the light guide rod is R6, satisfying the following relationship: R5 ≠ R6, the diameter of the second lens is D3, and the following relationships are satisfied: |R5 / D3|≥0.55 and |R6 / D3|≥0.

55.

4. The illumination homogenizing device for an endoscope according to claim 1, characterized in that, The core thickness d1 of the light guide rod satisfies the following relationship: 1.2 < d1 < 2.9, and the refractive index of the light guide rod is 1.4 to 1.6 and the Abbe number is 60 to 80.

5. The illumination homogenizing device for an endoscope according to claim 1, characterized in that, The first lens is a biconvex lens with a refractive index of 1.8 to 2.0 and an Abbe number of 30 to 50. The focal length f2 of the first lens satisfies the following relationship: 0.7 < f2 < 1.

4.

6. The illumination homogenizing device for an endoscope according to claim 1, characterized in that, The second lens is a biconvex lens with a refractive index of 1.8 to 2.0 and an Abbe number of 30 to 50. The focal length f3 of the second lens satisfies the following relationship: 0.4 < f3 < 1.

0.

7. The illumination homogenizing device for an endoscope according to claim 1, characterized in that, The beam angle of the device is greater than or equal to 140°, and the beam field of view of the device is greater than or equal to 170°.

8. The illumination homogenizing device for an endoscope according to claim 1, characterized in that, The light guide rod, the first lens, and the second lens are coaxially arranged and adjacent optical surfaces abut against each other.

9. The illumination homogenizing device for an endoscope according to claim 1, characterized in that, It also includes a lens barrel and a light source, and the light source, the light guide rod, the first lens and the second lens are all disposed inside the lens barrel.

10. An endoscope, characterized in that, The illumination homogenizing device for an endoscope as described in any one of claims 1 to 9.

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