CN110850580B

CN110850580B - Endoscope optical system

Info

Publication number: CN110850580B
Application number: CN201911201371.5A
Authority: CN
Inventors: 郭毅军; 刘剑; 刘中航
Original assignee: Chongqing Xishan Science and Technology Co Ltd
Current assignee: Chongqing Xishan Science and Technology Co Ltd
Priority date: 2019-11-29
Filing date: 2019-11-29
Publication date: 2021-07-06
Anticipated expiration: 2039-11-29
Also published as: CN110850580A

Abstract

The application provides an endoscope optical system, including objective optical assembly, rod mirror optical assembly and eyepiece optical assembly, objective optical assembly is including the first group mirror, second group mirror and the third group mirror that arrange in proper order, and the third group mirror includes first achromat, second achromat, third achromat and fourth achromat, and eyepiece optical assembly includes meniscus lens and three cemented lens. Because the second achromatic lens and the third achromatic lens have the effect of eliminating chromatic aberration, the first achromatic lens and the second achromatic lens (which are ultra-low dispersion lenses) are arranged at the two ends of the second achromatic lens and the third achromatic lens, and the effect of eliminating chromatic aberration is greatly improved; in addition, the triple cemented lens is a cemented lens comprising three single lenses, and the cemented lens can reduce chromatic aberration of a light beam. The endoscope optical system can eliminate distortion and chromatic aberration and obtain ultrahigh-definition imaging.

Description

Endoscope optical system

Technical Field

The invention relates to the field of optical imaging, in particular to an endoscope optical system.

Background

The endoscope is a detection instrument integrating optical, electronic, software and other technologies, enters through a natural pore passage or a minimally invasive opening of a human body and reaches a lesion position to be checked so as to perform real-time dynamic imaging monitoring on the lesion condition, and the clear and accurate imaging effect is of great importance.

With the continuous development of modern medicine, higher and higher requirements are clinically put forward on imaging effects, however, the optical system of the existing endoscope has larger imaging chromatic aberration, so that the optical image source has larger aberration, the resolution of final imaging is lower, and higher requirements are difficult to meet.

Disclosure of Invention

Provided is an endoscope optical system which can eliminate chromatic aberration and has high resolution.

The present application provides an endoscope optical system comprising:

the objective optical assembly comprises a first group of lenses, a second group of lenses and a third group of lenses which are sequentially arranged, wherein the first group of lenses is used for collecting images of a large field of view, the second group of lenses is used for turning a light path, the third group of lenses comprises a first achromatic lens, a second achromatic lens, a third achromatic lens and a fourth achromatic lens which are sequentially arranged on an emergent light path of the second group of lenses, and the first achromatic lens and the fourth achromatic lens are ultra-low dispersion lenses;

the rod lens optical assembly is positioned on an emergent light path of the third group of lenses and used for transmitting real images;

and an eyepiece optical assembly including a meniscus lens and a cemented triplet, the cemented triplet being a cemented doublet including three singlet lenses, the meniscus lens being located on a light path exiting the rod lens optical assembly, the cemented triplet being located on the light path exiting the meniscus lens.

According to a specific embodiment of the present application, the second achromatic lens includes a first lens and a second lens cemented in sequence, the second lens being an ultra-low dispersion lens.

According to a specific embodiment of the present application, the third achromatic lens includes a third lens, a fourth lens and a fifth lens which are sequentially cemented, and the third lens, the fourth lens and the fifth lens are respectively a positive lens, a negative lens and a positive lens.

According to a specific embodiment of the application, the entrance pupil diameter of the objective optical assembly is not less than 0.5mm and not more than 0.8mm, the focal length f is 2-3 mm, and the resolution limit is not less than 250 lp/mm.

According to a specific embodiment of the application, the first set of mirrors comprises an aspherical mirror and a negative lens, the negative lens being located between the aspherical mirror and the second set of mirrors, the aspherical mirror and the negative lens being adapted for converging.

According to a specific embodiment of the present application, the aspheric lens has a convex incident surface and a flat exit surface, and the negative lens has a convex incident surface and a concave exit surface.

According to a specific embodiment of the present application, the second set of lenses further comprises a first protective lens positioned at a front end of the aspherical lens.

According to a specific embodiment of this application, second group mirror is including prism, plano-concave lens and the biconvex lens who arranges in proper order, the prism is close to first group mirror, the biconvex lens is kept away from first group mirror.

According to an embodiment of the present application, the periphery of the incident surface of the meniscus is a plane, the middle of the incident surface is a concave surface, and the exit surface is a convex surface.

According to a specific embodiment of the present application, the cemented triplet includes a second biconvex lens, a first crescent lens, and a second crescent lens, the front end of the first crescent lens cemented at the rear end of the second biconvex lens, the front end of the second crescent lens cemented at the rear end of the first crescent lens; the incident surface of the second biconvex lens is a convex surface, and the emergent surface of the second biconvex lens is a convex surface; the incident surface of the first crescent lens is a concave surface, and the emergent surface of the first crescent lens is a convex surface; the incident surface of the second February lens is a concave surface, and the emergent surface of the second February lens is a convex surface.

According to a specific embodiment of the present application, the refractive index of the meniscus and the second biconvex lens is larger than 1.7.

According to the endoscope optical system of the above embodiment, since the third group lens includes the first achromatic lens, the second achromatic lens, the third achromatic lens and the fourth achromatic lens, the second achromatic lens and the third achromatic lens have the effect of eliminating chromatic aberration themselves, and the first achromatic lens and the second achromatic lens (which are ultra-low dispersion lenses) are further provided at both ends of the second achromatic lens and the third achromatic lens, the effect of eliminating chromatic aberration is greatly improved; in addition, the triple cemented lens is a cemented lens comprising three single lenses, and the cemented lens can reduce chromatic aberration of light beams. The endoscope optical system can eliminate distortion and chromatic aberration, thereby improving the quality of an optical image source and realizing ultrahigh-definition imaging.

Drawings

FIG. 1 is a block diagram showing the configuration of an endoscopic imaging system according to an embodiment;

FIG. 2 is a schematic diagram of the configuration of an optical system of the endoscope in one embodiment;

FIG. 3 is a schematic diagram of an embodiment of an objective optic assembly;

FIG. 4 is a schematic diagram of the first and second sets of mirrors in one embodiment;

FIG. 5 is a schematic diagram of a third set of mirrors in an embodiment;

FIG. 6 is a schematic diagram of an embodiment of an eyepiece optical assembly;

fig. 7 is a schematic structural view of an endoscope optical system in one embodiment.

Detailed Description

The present invention will be described in further detail with reference to the following detailed description and accompanying drawings. Wherein like elements in different embodiments are numbered with like associated elements. In the following description, numerous details are set forth in order to provide a better understanding of the present application. However, those skilled in the art will readily recognize that some of the features may be omitted or replaced with other elements, materials, methods in different instances. In some instances, certain operations related to the present application have not been shown or described in detail in order to avoid obscuring the core of the present application from excessive description, and it is not necessary for those skilled in the art to describe these operations in detail, so that they may be fully understood from the description in the specification and the general knowledge in the art.

Furthermore, the features, operations, or characteristics described in the specification may be combined in any suitable manner to form various embodiments. Also, the various steps or actions in the method descriptions may be transposed or transposed in order, as will be apparent to one of ordinary skill in the art. Thus, the various sequences in the specification and drawings are for the purpose of describing certain embodiments only and are not intended to imply a required sequence unless otherwise indicated where such sequence must be followed.

The numbering of the components as such, e.g., "first", "second", etc., is used herein only to distinguish the objects as described, and does not have any sequential or technical meaning. The term "connected" and "coupled" when used in this application, unless otherwise indicated, includes both direct and indirect connections (couplings). As used herein, "front end" and "back end" are the front end that is closer to the patient and the back end that is further from the patient relative to the patient, which are also the front and back ends of the imaging optical path.

In the embodiment of the invention, the endoscope optical system is provided, because the third group of lenses comprises the first achromatic lens, the second achromatic lens, the third achromatic lens and the fourth achromatic lens, the second achromatic lens and the third achromatic lens have the function of eliminating chromatic aberration, and the first achromatic lens and the second achromatic lens (which are ultra-low dispersion lenses) are arranged at two ends of the second achromatic lens and the third achromatic lens, the effect of eliminating chromatic aberration is greatly improved; in addition, the triple cemented lens is a cemented lens comprising three single lenses, and the cemented lens can reduce chromatic aberration of light beams. The endoscope optical system can eliminate distortion and chromatic aberration, thereby improving the quality of an optical image source and realizing ultrahigh-definition imaging.

As shown in fig. 1, an embodiment provides an endoscopic camera system that mainly includes an endoscope 100, a light source 200, a camera 300, and a host 400. The endoscope 100 is connected with the light source 200 through an optical fiber, the light source 200 illuminates human tissues through the optical fiber, the endoscope 100 is used for acquiring light reflected by the human tissues and transmitting light signals to the camera head 300, one end of the camera head 300 is connected with the endoscope 100, the other end of the camera head 300 is connected with the host 400, the camera head 300 is used for converting the light signals transmitted by the endoscope 100 into electric signals and transmitting the electric signals to the host 400, and the host 400 is used for processing the electric signals and outputting images.

Here, the light source 200 is white light, and the light source 200 is guided to the tip end by an optical fiber and emitted as illumination light.

The camera 300 has a light sensor and a processor therein, the light sensor acquires light emitted from the endoscope 100 and converts light signals into electrical signals, and the processor performs preprocessing such as amplification and filtering on the electrical signals and then sends the electrical signals to the host.

In one embodiment, an endoscope optical system is provided, and the endoscope optical system is the optical system of the endoscope 100 in the above-described embodiment.

As shown in fig. 2, the endoscope optical system includes an objective optical assembly 10, a rod lens optical assembly 20, and an eyepiece optical assembly 30. The objective optical assembly 10 is used for collecting information of a measured object and forming a real image, the rod lens optical assembly 20 is used for transmitting the real image, and the eyepiece optical assembly 30 is used for presenting the real image of the measured object. The endoscope optical system of the present embodiment is an ultra-high-definition distortion-free abdominal cavity endoscope optical system.

The rod lens optical assembly 20 is disposed behind the objective optical assembly 10 along the optical path, and is used for transmitting the real image formed by the objective optical assembly 10 to the eyepiece optical assembly 30. In a particular embodiment, the rod lens optical assembly 20 may include multiple sets of cemented lenses of the same size and parameters to deliver a real image formed by the objective optical assembly 10 to the eyepiece optical assembly 30 on a 1:1 scale; alternatively, the rod lens optical assembly 20 may be composed of tens of thousands of extremely fine glass fibers, and transmits the image formed by the objective lens optical assembly 10 to the eyepiece lens optical assembly 30 according to the principle of total reflection of light; in another embodiment, the rod optic assembly 20 may also be a micro-integrated circuit sensor for converting image information formed by the objective optic assembly 10 into an electrical signal and then transmitting the electrical signal to the eyepiece optic assembly 30.

As shown in fig. 3, the objective optical assembly 10 of the present embodiment includes a first group of mirrors 11, a second group of mirrors 12, and a third group of mirrors 13, where the first group of mirrors 11 is located at the frontmost end and is close to the target to be measured, the second group of mirrors 12 and the third group of mirrors 13 are located at the rear end of the first group of mirrors 11 in sequence, and the first group of mirrors 11, the second group of mirrors 12, and the third group of mirrors 13 are aligned on the axis of the optical path.

As shown in fig. 4, the first group of mirrors 11 is used for collecting an image of a field of view, the first group of mirrors 11 includes an aspherical mirror 111 and a negative lens 112, and the aspherical mirror 111 and the negative lens 112 are fixed together by a mounting seat. The front light incident surface of the aspherical mirror 111 is a convex surface, and the rear end of the aspherical mirror 111 is a plane, which is a light emergent surface. The negative lens 112 may be a spherical mirror or an aspherical mirror, and the front light incident surface thereof is a convex surface; the rear light exit surface of the negative lens 112 may be convex or concave, for example: when the objective optical assembly 10 is an objective lens of an endoscope optical system, the light exit surface of the negative lens 112 is concave to collect light with a large field of view. In a specific embodiment, the shapes of the light exit surface of the aspherical mirror 111 and the light entrance surface of the negative lens 112 may be different, and it is only necessary that the aspherical mirror 111 and the negative lens 112 are coaxially disposed.

In order to better protect the front end of the objective optical assembly 10, the first lens group 11 further includes a first protective lens 113, the first protective lens 113 is a sapphire glass sheet, and has the advantages of high hardness, scratch resistance, fracture resistance and the like, and the first protective lens 113 is installed at the front end of the aspheric lens 111, is located at the foremost end of the whole objective optical assembly 10, and plays a role in protection.

In this embodiment, the aspheric mirror 111 and the negative lens 112 of the first group of mirrors 11 are made of high refractive index materials, for example, the refractive indexes of the aspheric mirror 111 and the negative lens 112 are greater than 1.75, the aspheric mirror 111 and the negative lens 112 with large refractive indexes are used for collecting images with large field of view, and meanwhile, the incident surface of the aspheric mirror 111 is an aspheric surface with an incident surface close to an elliptical surface or a paraboloid, so that parallel light rays are incident on the lenses, and no matter whether paraxial light rays or paraxial light rays can converge to a point, so as to obtain clearer imaging, so that distortion of the first group of mirrors 11 can be reduced, and distortion-free imaging can be realized. In other embodiments, the first group of mirrors 11 may also be formed by at least three lenses, and the light incident surface of one lens close to the object space is a convex aspheric mirror to eliminate the distortion of the system.

The second group of mirrors 12 is at least used for converging the light beams emitted by the first group of mirrors 11, and the second group of mirrors 12 at least comprises a plano-convex lens which is used for converging the light beams. In this embodiment, the second set of mirrors 12 further includes at least one lens for changing the viewing angle, and when the viewing angles of the objective optical assembly 10 are different, the shape and number of the lenses are changed accordingly.

As shown in fig. 4, in the present embodiment, the second group mirror 12 includes a prism 121, a plano-concave lens 122, and a lenticular lens 123, which are sequentially disposed along the optical path, the prism 121 is close to the first group mirror 11, the lenticular lens 123 is far from the first group mirror 11, and the prism 121 is also a cylindrical mirror. In the present embodiment, the directions of the optical axes of the prism 121, the plano-concave lens 122 and the lenticular lens 123 are the same, and the central field of view is defined as the viewing angle of the objective optical assembly 10 is 0 °, and at this time, the light beams are transmitted along the optical axes of the prism 121, the plano-concave lens 122 and the lenticular lens 123 in sequence, corresponding to the scene in which the detected object is located right in front of the objective optical assembly 10.

In the present embodiment, the third group of mirrors 13 is used to eliminate chromatic aberration of the optical system, the third group of mirrors 13 includes a first achromatic lens 131, a second achromatic lens 132, a third achromatic lens 133 and a fourth achromatic lens 134, the first achromatic lens 131, the second achromatic lens 132, the third achromatic lens 133 and the fourth achromatic lens 134 are aligned in sequence on the light path exiting from the second group of mirrors 12, the first achromatic lens 131 is close to the second group of mirrors 12, the fourth achromatic lens 134 is far from the second group of mirrors 12, and the first achromatic lens 131 and the fourth achromatic lens 134 are located at two ends of the second achromatic lens 132 and the third achromatic lens 133.

The second achromatic lens 132 and the third achromatic lens 133 are formed by bonding lenses of at least two different materials, wherein both the most front mirror surface of the second achromatic lens 132 and the most rear mirror surface of the third achromatic lens 133 are convex surfaces. As shown in fig. 5, in a preferred embodiment, for better chromatic aberration elimination, the second achromatic lens 131 is a double cemented lens, the second achromatic lens 132 includes a first lens 132a and a second lens 132b, an incident surface of the second lens 132a is a convex surface, an exit surface is a concave surface, both incident and exit surfaces of the second lens 132b are convex surfaces, and an exit surface of the first lens 132a is cemented with the incident surface of the second lens 132 b.

The first lens 132a and the second lens 132b are made of 2 different materials, and the 2 materials for forming the double cemented mirror generally include at least one of flint glass and crown glass, which can compensate for the color difference due to refraction of white light to eliminate chromatic aberration.

In the present embodiment, the first achromatic lens 131 and the fourth achromatic lens 134 are provided at both ends of the second achromatic lens 132 and the third achromatic lens 133, respectively. In order to reduce chromatic aberration of image formation, the first achromatic lens 131 and the fourth achromatic lens 134 are ultra-low dispersion lenses, and special glass having a characteristic of low wavelength of dispersed light is used. The most preferable material of the first achromatic lens 131 and the fourth achromatic lens 134 is fluorite. However, the natural fluorite mineral is rare and difficult to process, and artificial fluorite imitating the optical characteristics of fluorite can be used instead. The first achromatic lens 131 and the fourth achromatic lens 134 can solve the problem of chromatic dispersion generated by large-field large-aperture imaging, and ultrahigh-resolution imaging is obtained.

In this embodiment, in order to further reduce the imaging chromatic aberration, the second lens 132b also adopts an ultra-low dispersion lens, so that a double ultra-low dispersion lens combination is formed in the objective lens to better solve the imaging chromatic dispersion problem.

In the present embodiment, the third achromatic lens 133 includes a third lens 133a, a fourth lens 133b, and a fifth lens 133c, which are a positive lens, a negative lens, and a positive lens, respectively. The incident surface and the exit surface of the third lens 133a are convex surfaces, the incident surface and the exit surface of the fourth lens 133b are concave surfaces, and the incident surface and the exit surface of the fifth lens 133c are convex surfaces. Among them, the third lens 133a, the fourth lens 133b, and the fifth lens 133c may be glued together.

In this embodiment, the third group of mirrors 13 is a combination of four achromatic lenses including the first achromatic lens 131, the second achromatic lens 132, the third achromatic lens 133 and the fourth achromatic lens 134, and the third group of mirrors 13 is a combination of lenses having achromatic function, so that the third group of mirrors 13 has better achromatic effect and obtains super-high resolution imaging.

In the objective optical assembly 10 of the present embodiment, the focal length F of the objective lens is 2-3 mm, a large aperture design is adopted, the diameter of the entrance pupil is 0.5mm or more and D is less than or equal to 0.8mm, F/#isless than or equal to 4, the actual resolution limit of the optical system is greater than or equal to 250lp/mm, and higher resolution imaging can be obtained by adopting the above optical parameters. The specific principle is as follows:

the diffraction limit (diffraction limit) means that an ideal object point is imaged by an optical system, and due to the diffraction limit, the ideal image point cannot be obtained, but a fraunhofer diffraction image is obtained. The aperture of the optical system is usually circular, and the images of the Freund and Fischer diffraction are called Airy spots. Therefore, each object point is like a diffuse spot, two diffuse spots are not well distinguished after being close to each other, the resolution ratio of the system is limited, and the larger the spot is, the lower the resolution ratio is. The diffraction limit limits the resolution of the system.

Diffractive emitterThe formula for the limit is:

where D is the minimum resolving size, D is the entrance pupil diameter, F is the focal length, λ is the wavelength, and F/# is the optical system F number.

From the above formula, when the F/# is smaller, the smaller the theoretical resolvable size of the optical system is, the stronger the resolving power is, and the easier the high resolution design is to be realized; conversely, when the F/# is larger, the larger the theoretically resolvable size of the optical system, the weaker the resolving power, and the more difficult it is to realize a high resolution design. In the design, the diameter D of the entrance pupil of the optical system is more than or equal to 0.5mm, and F/#isless than or equal to 4, so that compared with a high-definition laparoscope, the diameter of the entrance pupil is increased, and the F/#issmaller, so that the theoretical resolution capability of the system is stronger, and the resolution is higher.

The entrance pupil diameter is the effective aperture for limiting the incident beam, and is determined by the entire objective optical assembly, which is the image of the aperture stop on the front optical system. The larger the entrance pupil diameter is, the larger the light flux amount is, the higher the limit resolution is, and based on the miniaturization of the endoscope, the entrance pupil diameter cannot be too large, in this embodiment, the entrance pupil diameter is not less than 0.5mm and not more than D and not more than 0.8mm, that is, the resolution can be increased without affecting the miniaturization of the endoscope.

However, in the design of an optical system, the actual resolution of the system can only approach the diffraction limit to the maximum extent due to the existence of aberration. It will be understood that the higher the diffraction limit of the system, the higher the actual resolution of the system. The resolution of an optical system, lp/mm, is typically characterized by the number of black and white line pairs that can be clearly resolved by one millimeter. The higher the line logarithm is, the higher the detail resolution energy rate of the system is, and the higher the resolution is; conversely, the lower the line logarithm, the weaker the detail resolution of the system, and the lower the resolution. In the design, the diffraction limit of the optical system is more than or equal to 270 lp/mm. Due to the optimized control of the system aberration, the practical resolution limit of the optical system is more than or equal to 250lp/mm under the condition of not considering the processing error.

As shown in fig. 6, the eyepiece optical assembly 30 of the present embodiment includes a meniscus lens 31 and a cemented triplet 32, and the cemented triplet 32 is located on the optical path from the meniscus lens 31 and aligned on the optical axis of the imaging optical path.

In this embodiment, the meniscus lens 31 has a concave incident surface and a convex exit surface. Preferably, the peripheral edge of the incident surface of the meniscus lens 31 is a flat surface, and the center of the incident surface is a concave surface. The circumferential edge is a circumferential edge, and is similar to a circular ring. The meniscus lens 31 has a thin central part and a thick peripheral part, and can diffuse light beams.

In the present embodiment, the triple cemented lens 32 is formed by combining single lenses made of three different materials, and the curvature radii of the single lenses are different. It should be understood that different materials and curvatures cooperate to compensate for the color difference caused by white light refraction to eliminate chromatic aberration.

In this embodiment, the cemented triplet 32 includes a second biconvex lens 321, a first crescent lens 322, and a second crescent lens 323, wherein the front end of the first crescent lens 322 is cemented to the rear end of the second biconvex lens 321, and the front end of the second crescent lens 323 is cemented to the rear end of the first crescent lens 322; the incident surface of the second biconvex lens 321 is a convex surface, and the exit surface is a convex surface; the incident surface of the first crescent lens 322 is a concave surface, and the emergent surface is a convex surface; the incident surface of the second February lens 323 is a concave surface, and the emergent surface is a convex surface. It should be noted that, three lenses have one more lens capable of compensating each other than the combination of two lenses, and it can be seen that the effect of eliminating chromatic aberration of the tri-cemented lens 32 is better.

In this embodiment, the meniscus lens 31 and the second biconvex lens 321 are high refractive index lenses, and in this embodiment, preferably, the refractive indexes of the meniscus lens 31 and the second biconvex lens 321 are greater than 1.7, and the refractive indexes of the meniscus lens 31 and the second biconvex lens 321 are different, and the chromatic dispersion of the meniscus lens 31 and the second biconvex lens 321 with high refractive index can compensate each other, so as to reduce chromatic aberration.

In this embodiment, the meniscus lens 31 is used to diverge the light beam, and the second biconvex lens 323 is used to focus the light beam, so as to diverge and converge the light beam in sequence, thereby effectively eliminating distortion.

In the present embodiment, the sizes of the meniscus lens 31, the second biconvex lens 321, the first meniscus lens 322 and the second biconvex lens 323 satisfy a predetermined relationship, and the meniscus lens 31 and the second biconvex lens 321 have a predetermined distance therebetween, so that the focal length f of the entire eyepiece optical assembly 30 is 15 to 20 mm. The eyepiece optical assembly 30 of the present embodiment is used to enlarge an image to infinity, and the eyepiece optical assembly 30 can effectively reduce an imaging chromatic aberration.

As shown in fig. 7, in an embodiment, the endoscope optical system further includes a second protective lens 40, the second protective lens 40 is located on the light path of the light emitted from the cemented triplet 32, and the second protective lens 40 is a sapphire glass sheet, like the first protective lens 113, and has the advantages of high hardness, scratch resistance, fracture resistance, and the like. The first protective lens 113 and the second protective lens 40 are respectively located at the front end and the rear end of the whole endoscope optical system, so that the endoscope optical system can be well protected, and the lenses between the first protective lens 113 and the second protective lens 40 can be prevented from being scratched and broken.

While the principles herein have been illustrated in various embodiments, many modifications of structure, arrangement, proportions, elements, materials, and components particularly adapted to specific environments and operative requirements may be employed without departing from the principles and scope of the present disclosure. The above modifications and other changes or modifications are intended to be included within the scope of this document.

The foregoing detailed description has been described with reference to various embodiments. However, one skilled in the art will recognize that various modifications and changes may be made without departing from the scope of the present disclosure. Accordingly, the disclosure is to be considered in an illustrative and not a restrictive sense, and all such modifications are intended to be included within the scope thereof. Also, advantages, other advantages, and solutions to problems have been described above with regard to various embodiments. However, the benefits, advantages, solutions to problems, and any element(s) that may cause any element(s) to occur or become more pronounced are not to be construed as a critical, required, or essential feature or element of any or all the claims. As used herein, the terms "comprises," "comprising," or any other variation thereof, are intended to cover a non-exclusive inclusion, such that a process, method, article, or apparatus that comprises a list of elements does not include only those elements but may include other elements not expressly listed or inherent to such process, method, system, article, or apparatus. Furthermore, the term "coupled," and any other variation thereof, as used herein, refers to a physical connection, an electrical connection, a magnetic connection, an optical connection, a communicative connection, a functional connection, and/or any other connection.

Those skilled in the art will recognize that many changes may be made to the details of the above-described embodiments without departing from the underlying principles of the invention. Therefore, the scope of the present invention should be determined by the claims of the present invention.

Claims

1. An endoscope optical system, comprising:

the objective optical assembly consists of a first group of lenses, a second group of lenses and a third group of lenses which are sequentially arranged, wherein the first group of lenses is used for collecting images with a large field of view, the second group of lenses is used for turning a light path, the third group of lenses consists of a first achromatic lens, a second achromatic lens, a third achromatic lens and a fourth achromatic lens which are sequentially arranged on an emergent light path of the second group of lenses, and the first achromatic lens and the fourth achromatic lens are ultra-low dispersion lenses;

and eyepiece optical assembly comprises meniscus lens and three cemented lens, three cemented lens are the cemented lens who contains three single lens, meniscus lens is that the incident surface is the concave surface, the exit surface is the single lens of convex surface, meniscus lens is located the light path of rod mirror optical assembly outgoing, three cemented lens are located the light path of meniscus lens outgoing.

2. The endoscope optical system of claim 1 wherein said second achromatic lens is comprised of a first lens and a second lens cemented together in sequence, said second lens being an ultra-low dispersion lens.

3. The endoscope optical system according to claim 2, wherein the third achromatic lens is composed of a third lens, a fourth lens and a fifth lens which are sequentially cemented, the third lens, the fourth lens and the fifth lens being a positive lens, a negative lens and a positive lens, respectively.

4. An endoscope optical system according to claim 1, characterized in that said objective optical assembly has an entrance pupil diameter of 0.5mm or less, D or less, 0.8mm or less, a focal length f or 2 to 3mm or less, and a resolution limit of 250lp/mm or more.

5. The endoscopic optical system of claim 1 wherein the first set of mirrors consists of an aspherical mirror and a negative lens, the negative lens being located between the aspherical mirror and the second set of mirrors, the aspherical mirror and the negative lens being for convergence.

6. The endoscope optical system of claim 5 wherein the aspheric lens has a convex entrance surface and a flat exit surface, and wherein the negative lens has a convex entrance surface and a concave exit surface.

7. The endoscope optical system according to claim 1, wherein the second group of lenses is composed of a prism, a plano-concave lens and a lenticular lens arranged in this order, the prism being close to the first group of lenses, and the lenticular lens being far from the first group of lenses.

8. An endoscope optical system according to any one of claims 1 to 7, wherein a peripheral edge of an incident surface of the meniscus lens is a flat surface, a central portion of the incident surface is a concave surface, and the exit surface is a convex surface.

9. An endoscope optical system according to any of claims 1 to 7 wherein said triplex cemented lens comprises a second biconvex lens, a first crescent lens having a front end cemented at a rear end of said second biconvex lens, and a second crescent lens having a front end cemented at a rear end of said first crescent lens; the incident surface of the second biconvex lens is a convex surface, and the emergent surface of the second biconvex lens is a convex surface; the incident surface of the first crescent lens is a concave surface, and the emergent surface of the first crescent lens is a convex surface; the incident surface of the second February lens is a concave surface, and the emergent surface of the second February lens is a convex surface.

10. The endoscopic optical system of claim 9 wherein the refractive index of the meniscus and the second biconvex lens is greater than 1.7.