JP2011250981A - Multifocal lens simulator - Google Patents

Abstract

PROBLEM TO BE SOLVED: To provide a multifocal lens simulator enabling a subject to actually feel and experience the effects of a multifocal intraocular lens, the difference between a diffractive type and a refractive type, or demerits without undergoing multifocal intraocular lens implant surgery (before undergoing the implant surgery) and moreover to actually feel the difference in visible ways according to pupil diameters.SOLUTION: The multifocal lens simulator includes a test lens support means disposed in front of an afocal optical system to store a multifocal test lens having a plurality of refractive powers which are a predetermined basic refractive power and an additional refractive power with a differential refractive power added to the basic refractive power. An observer can observe an object from the rear of the afocal optical system through the multifocal test lens and the afocal optical system. The test lens support means is disposed in a position to have a pupil conjugate relation to a position where the observer's eye is supposed to be placed. Further, an optical path branching means for observing the pupil diameter of the observer from an optical path different from an optical path of the multifocal test lens is disposed in an optical path of the afocal optical system.

Description

  The present invention relates to a multifocal lens simulation apparatus.

  For the purpose of treating cataracts, surgery that removes a cloudy lens and inserts an intraocular lens (IOL) has become widespread. On the other hand, a multifocal intraocular lens is used not only for the purpose of treating cataracts but also to compensate for the adjustment that is losing in presbyopia. A multifocal intraocular lens has a plurality of refractive powers of a predetermined basic refractive power and an additional refractive power obtained by adding a differential refractive power to the basic refractive power, and the surface of the lens is configured with different radii of curvature for each area. There are known a refracting type and a diffractive type having a diffractive structure, both of which divide a condensing point into a plurality (for far vision and near vision) in the optical axis direction. With such a configuration, there is an advantage that it is possible to secure visual acuity at a condensing point for either far vision or near vision, and to live a life without depending on glasses.

Japanese Patent No. 3814017 Special table 2007-527263

  However, since one of the two condensing points is in a blurred state, it becomes a factor that degrades visibility such as contrast. For example, the diffractive type has glare in which highlights are glaring, while the refractive type has a drawback that a halo that appears as a ring around the light tends to appear. These are side effects caused by the multifocality of the intraocular lens, and are phenomena that are not recognized by normal eyes, and can be realized only after the operation of the multifocal intraocular lens (that is, it cannot be realized before surgery).

  Patent Document 1 is an apparatus in which an intraocular lens is arranged in an optical path of an imaging optical system, and an image corresponding to a retinal image is captured and presented by a CCD or the like. Since it is presented via an image sensor or display device, it cannot reflect what processing is performed in actual human vision.

  Patent Document 2 is an apparatus for synthesizing images with different diopters by inserting an addition lens in one of optical paths branched in the middle for the purpose of fitting a multifocal contact lens. Although it is a device that can actually be seen by humans, it cannot realize the difference in the functions of various multifocal intraocular lenses. This is because the optical method of multifocalization by combining images and the actual multifocal intraocular lens is different. For example, the difference in appearance due to the pupil diameter pointed out in the refraction type is expressed. Can not do it.

  Based on this awareness of the problem, the applicant has already relayed the optical action of the multifocal lens to the vicinity of the observer's crystalline lens, so that the same appearance as that of the subject wearing the multifocal lens can be obtained. A device and a method for experiencing it have been proposed (Japanese Patent Application No. 2009-232502). In this proposal, an afocal optical system capable of observing a distant object as well as disposing a lens support means at a position having a pupil conjugate relationship with a position where the observer's eyes are assumed to be disposed.

  By the way, recent multifocal intraocular lenses, regardless of whether they are refractive or diffractive, basically have a lens structure in which the energy distribution of the amount of light for far vision and near vision is changed according to the pupil diameter. ing. However, the energy distribution for far vision and near vision differs depending on the design concept, and how the multifocal intraocular lens actually acts is greatly influenced by the pupil diameter. That is, the appearance of the multifocal intraocular lens varies depending on the pupil diameter. Since the pupil diameter changes depending on the brightness and mental state, it is preferable that the multifocal intraocular lens simulator device also has a function of monitoring or controlling the pupil diameter during observation.

  Based on the awareness of the above problems, the present invention realizes and experiences the effects, the difference between the diffractive type and the refractive type, or the disadvantages, even if the multifocal intraocular lens insertion operation is not performed (before the insertion operation). Another object of the present invention is to obtain a multifocal lens simulation apparatus that can realize the difference in appearance depending on the pupil diameter.

  The present invention is based on the above-mentioned Japanese Patent Application No. 2009-232502 (a multifocal test lens is provided in front of an afocal optical system capable of observing a distant object that emits a light beam incident as substantially parallel light as approximately parallel light. In addition to the afocal optical system, you can feel the wearing feeling of the multifocal test lens by observing the object through the multifocal test lens and the afocal optical system from the back of the afocal optical system. It was made based on the point of view that if an optical path branching means such as a pupil diameter observation beam splitter is provided in the optical path of the optical system, pupil diameter information can be added to evaluate (actually) a multifocal intraocular lens. It is.

  That is, the multifocal lens simulation apparatus according to the present invention has an afocal optical system that emits a light beam incident as substantially parallel light as substantially parallel light, and has a predetermined reference refractive power and the basic power in front of the afocal optical system. A test lens support means for accommodating a multifocal test lens having a plurality of additional refractive powers obtained by adding a differential refractive power to a refractive power is disposed, and an observer from the rear passes through the afocal optical system to provide a multifocal target. An object lens support means is disposed at a position that is capable of observing an object through the analyzing lens and has a pupil conjugate relationship with a position where the observer's eyes are assumed to be disposed. In the optical path of the optical system, optical path branching means for observing the pupil diameter of the observer from an optical path different from the optical path of the multifocal lens is characterized.

  An optical system for observing the pupil image of the observer can be provided on the optical path branched from the optical path of the multifocal lens by the optical path branching means. However, it is more preferable to arrange an image sensor and an imaging lens for capturing a pupil image.

  In addition, it is preferable that an index indicating the pupil diameter is arranged in the optical path branching unit so that the pupil diameter can be directly grasped.

  Furthermore, it is preferable to arrange a light amount control means in the optical path from the multifocal lens to the optical path branching means. In order to guide the pupil diameter in the expansion direction, it is only necessary to reduce the amount of light by the light amount control means, and to obtain the opposite effect, an aperture device is provided in the optical path without actually reducing the pupil diameter. Thus, the diameter of the light beam incident on the pupil may be limited.

  The light quantity control means can be constituted by, for example, a neutral density filter device or a diaphragm device.

  The neutral density filter device is preferably a variable neutral density filter device that changes the light transmittance stepwise or steplessly, and the aperture device is preferably a variable aperture device that can change the aperture diameter.

  The afocal optical system is a Kepler type that creates a real image of an observation object in the afocal optical system. That is, the afocal optical system includes a Kepler type and a Galileo type, but it is necessary to adopt a Kepler type configuration in which the pupil conjugate point is a real image. This makes it possible to place the multifocal test lens at the entrance pupil position, and the optical action of the multifocal test lens is relayed to the exit pupil position. An observer can experience the same appearance as a subject wearing a multifocal lens by placing his eyes so that the crystalline lens is positioned at the exit pupil position as in a general telescope.

  In the afocal optical system, it is preferable to arrange an index indicating a conjugate position at infinity in the vicinity of the real image forming position. That is, the subject wearing the multifocal test lens does not have the eye adjustment function, but the observer has the eye adjustment function, so the multifocal test lens (multifocal intraocular lens or a test piece having an equivalent function). ) And the effect of adjusting force are mixed. Therefore, it is desirable that an index is arranged in the vicinity of the real image position formed inside the Kepler type afocal optical system, and the observer gazes at this index so as to induce the eye's adjustment power to be as small as possible.

  It is preferable that the afocal optical system has substantially the same magnification as the entire optical system. That is, in order for the observer to experience the same appearance as that of the subject, it is necessary to be able to observe the object to be observed (the scenery or object in the outside world) at the same magnification as in the naked eye state. Therefore, it is desirable that the afocal optical system as a whole has an angular magnification of approximately equal magnification. Even if it is not the same magnification, you can experience the optical action of the multifocal test lens if the pupil conjugation condition is satisfied, but the perspective of the object to be observed differs from the state of the naked eye, so the impression may be different is there.

  Specifically, the afocal optical system can be configured by arranging two afocal optical systems having substantially the same magnification so as to face each other. In order to erect an inverted image in a Kepler type optical system, an erecting optical system (image reversal optical system) typically represented by a Porro prism or the like is required. However, this prism simultaneously limits the incident angle of the optical system. In general Kepler-type binoculars, the incident angle is limited to about ± 10 ° even if the magnification is low. In the Kepler type optical system that is approximately the same magnification, the exit angle is about the same, so the apparent field of view is narrowed. Therefore, by replacing this erecting optical system with a relay optical system, it is possible to obtain a wide actual field of view (apparent field of view) as well as approximately equal magnification. More specifically, by disposing two afocal optical systems having the same magnification facing each other, both opposing objective lenses function as a relay optical system, thereby forming a substantially equal magnification Kepler optical system.

  Each of the two afocal optical systems can use binoculars. Since the binoculars are provided with a pair of afocal optical systems, the test lens support means is provided with a pair corresponding to the pair of afocal optical systems.

  The multifocal test lens supported by the test lens support means may be a multifocal intraocular lens that is actually inserted into the eye, that is, a multifocal intraocular lens that can be implanted and inserted into the naked eye instead of the crystalline lens. it can. Alternatively, a test piece that is optically equivalent to the multifocal intraocular lens can be used as the multifocal test lens. Specifically, in the case of the refractive type, the optically equivalent test piece is a portion where the refractive power is substantially zero, and a differential refractive power corresponding to the difference between the basic refractive power and the additional refractive power (for example, 4D In the case of the diffractive type, the 0th-order light as the basic refractive power does not have a refractive power, and the primary light can have a differential refractive power.

  When a multifocal intraocular lens that is actually inserted into the eye is used as the multifocal test lens, the test lens support means includes a liquid holding unit that holds a liquid, and the liquid holding unit includes the liquid holding unit. It is preferable to hold a multifocal intraocular lens that is actually inserted into the eye and a canceling lens having a refractive power that cancels the basic refractive power of the multifocal intraocular lens.

  The multifocal intraocular lens placed in front of the afocal optical system is preferably held in water in the liquid holding unit because its basic function is to replace the crystalline lens of the eye. On the other hand, since the multifocal intraocular lens has a power of about 20D as a basic refractive power in water, observation of a distant landscape is possible when the multifocal intraocular lens is held as it is in a parallel light beam near the entrance pupil of the afocal optical system. In other words, it becomes a state resembling extreme myopia. Therefore, it is held together with a canceling lens having a negative refractive power that cancels the basic refractive power of this multifocal intraocular lens, and only the difference between the multifocal refractive powers is extracted and relayed to the observer's crystalline lens. It is desirable. In the case of a test piece having an equivalent function, the canceling lens can be omitted by setting the basic refractive power to zero.

  The multifocal lens simulation device according to the present invention further includes an infrared illumination light source that emits infrared illumination light toward the observer's pupil, thereby observing the pupil diameter without affecting the function of the simulator. Can do.

  According to the present invention, the effect, the difference between the diffractive type and the refractive type, or the demerits can be realized and experienced without undergoing the insertion operation of the multifocal intraocular lens (before the insertion operation). Since the diameter can be observed, it is possible to easily confirm to which area of the multifocal intraocular lens the user is experiencing. Further, the observation pupil diameter can be controlled by the light amount control means without using a mydriatic drug or the like whose action continues after observation.

It is an optical block diagram which shows 1st embodiment of the multifocal lens simulation apparatus by this invention. It is sectional drawing which shows one Embodiment of the multifocal lens holder of the multifocal lens simulation apparatus of FIG. It is a front view which shows an example of the pupil diameter observation monitor of the multifocal lens simulation apparatus of FIG. It is an optical path diagram which shows 2nd embodiment of the multifocal lens simulation apparatus by this invention. It is an optical path diagram which shows 3rd embodiment of the multifocal lens simulation apparatus by this invention. It is an optical path diagram which shows 4th embodiment of the multifocal lens simulation apparatus by this invention. It is a lens figure which shows the specific example of the imaging lens used for the multifocal lens simulation apparatus by this invention. It is a schematic diagram which shows the structure of a refraction type test piece. (A) is a front view of an example of a refraction type multifocal intraocular lens, (B) is a graph which shows the example of energy distribution to the far and near of the light which permeate | transmits the same lens and injects into a pupil. (Source: "Multifocal intraocular lens", author: Hiroko Bissen, publisher: Elsevier Japan, Inc.). (A) is a front view of an example of a diffractive multifocal intraocular lens, (B) is a cross-sectional view of a diffractive structure portion, and (C) is a far and near distance of light that passes through the lens and enters the pupil. It is a graph which shows the example of energy allocation to (same as above).

  FIG. 9A is a front view of an example of a refractive multifocal intraocular lens, which is a far single focal region C at the center, a far single focal region P at the outermost periphery, and a near single focal point formed between the two. It consists of region Q. FIG. 4B shows an example of energy distribution to the far and near light beams that are transmitted through the lens and incident on the pupil. Until the diameter (pupil diameter) reaches a certain value, the central far distant single focal point is shown. When far-field energy that focuses far away (infinitely) by the region C is incident, and when the pupil diameter reaches the near-single focal region Q, the energy that focuses in the near-field (finite distance) increases, and far away (infinite The energy that focuses on the far side decreases, and when the pupil diameter reaches the far single focal region P, the energy that focuses on the far side (infinite) increases and the energy that focuses on the near side (finite distance) decreases. To do. This design gives only the energy of light focused far away while the pupil diameter is very small, and as the pupil diameter increases, the proportion of light focused far is reduced and the light focused near This is based on the idea of increasing the ratio of the energy of the light and further increasing the ratio of the energy of the light that is focused far away when the pupil diameter further increases.

  FIG. 10A is a front view of an example of a diffractive multifocal intraocular lens, which is composed of a far single focal region P at the outermost periphery and a near-far transition region D by a diffractive structure formed at the center. . FIG. 5B shows a cross section of the near-far transition region D of the same lens diffractive structure. The step from the central portion C to the peripheral portion is gradually lowered to give an apodization action. FIG. 6C shows an example of energy distribution to the far and near light beams that are transmitted through the lens and incident on the pupil. As the diameter (pupil diameter) increases, the focus increases to the far (infinity). While the energy connecting the points increases smoothly, the energy that focuses on the near (finite distance) decreases smoothly. This design is based on the idea that while the pupil diameter is small, the proportion of light energy focused in the near area is increased, and as the pupil diameter increases, the proportion of light energy focused in the distance is increased. Yes.

  As is clear from the above two examples, the far and near energy distribution of the multifocal intraocular lens differs depending on the lens, and a correct evaluation cannot be made unless the pupil diameter is taken into consideration.

“Embodiment 1”
1 to 3 show a first embodiment of a multifocal lens simulation apparatus according to the present invention. This multifocal lens simulation apparatus includes an afocal optical system 10 having an angular magnification of approximately equal magnification, and an intraocular lens support means (test lens support means) 20 disposed at an entrance pupil position of the afocal optical system 10. Have. The afocal optical system 10 is an optical system that emits a substantially parallel light beam when a parallel light beam from an object at infinity is incident.

  The afocal optical system 10 includes, in order from the object side, a positive power objective lens group 11, an erecting prism 12, an erecting prism 13, and a positive power eyepiece group 14. An imaging plane 15 is formed between the erecting prisms 13. The objective lens group 11 and the erecting prism 12, and the erecting prism 13 and the eyepiece lens group 14 are symmetric with respect to the imaging plane 15, and a real image of the observation object by the objective lens group 11 is formed on the imaging plane 15 ( Kepler type), the image of the imaging plane 15 is observed through the eyepiece group 14 by the observer's eye 16 placed at the exit pupil position of the afocal optical system 10. The erecting prism 12 and the erecting prism 13 are erecting optical systems that erect an image, and each has two reflecting surfaces in total. Specifically, for example, a Porro prism can be used. The image plane 15 is equipped with an index composed of a cross line drawn on a transparent plate, for example. The eyepiece group 14 is movable in the optical axis direction in order to adjust the diopter of the observer.

  In the erecting prism 13, an optical path branching means is constituted by a light beam splitting surface (film) 13 </ b> S that forms 45 ° with the optical axis. This light beam splitting surface 13S branches the light beam from the eye 16 out of the light beam of the afocal optical system 10, and an imaging lens 17 and an imaging device 18 including an imaging element 18S are arranged on the branched optical path. ing. That is, the light beam splitting surface 13 </ b> S, the imaging lens 17, and the imaging device 18 constitute an optical system that observes the pupil diameter of the eye 16. FIG. 3 is a schematic diagram of the observed image, and an index 19 for displaying the pupil diameter is provided.

  As shown in an enlarged view in FIG. 2, the intraocular lens support means 20 forms a liquid holding space 23 between the transmission parallel plane plates 21 and 22 on the incident side and the emission side. A multifocal intraocular lens (multifocal lens) 24 and an offset lens 25 are held in the held liquid (water). The transmission parallel flat plates 21 and 22 are fixed to a casing 26, and a multifocal intraocular lens 24 and a canceling lens 25 are held by a lens holder 27 that can be attached to and detached from the casing 26. In the use state, the space in the casing 26 including the space between the multifocal intraocular lens 24 and the canceling lens 25 is filled with liquid (water) as the liquid holding space 23. The intraocular lens support means 20 is arranged so that the multifocal intraocular lens 24 is positioned at the entrance pupil position of the afocal optical system 10. Regardless of whether the multifocal intraocular lens 24 is a refractive type or a diffractive type, the basic refractive power in water (the crystalline lens) (for example, 20D) and the additional refractive power obtained by adding a differential refractive power to the basic refractive power. An example of energy distribution has been described with reference to FIGS. 9 and 10. The cancellation lens 25 has a negative refractive power that cancels the basic refractive power of the multifocal intraocular lens 24, and extracts only the difference (4D) in the refractive power that has been multifocalized.

  Between the afocal optical system 10 and the intraocular lens support means 20, a light amount control means 40 is disposed. The light quantity control means 40 includes a variable aperture device 41 and a rotary variable neutral density filter device 42. The variable aperture device 41 changes the amount of light incident on the afocal optical system 10 by changing the mechanical aperture diameter. The rotary variable neutral density filter device 42 is a filter that can rotate around a rotation shaft 42S, and changes the light transmittance (concentration) in the circumferential direction steplessly or stepwise. Similarly, the amount of light incident on the afocal optical system 10 can be changed by rotating the rotation shaft 42S as a center and changing the portion located on the optical axis.

  According to the above multifocal lens simulation apparatus, the observer can observe the object to be observed from behind the afocal optical system 10 through the multifocal intraocular lens 24 of the intraocular lens support means 20 and the afocal optical system 10. . That is, the exit pupil position of the afocal optical system 10 is open so that the observer's eyes can be placed. In addition, since the intraocular lens support means 20 (multifocal intraocular lens 24) is disposed at a position having a pupil conjugate relationship with the position where the observer's eyes are assumed to be disposed, the afocal optical system 10 The optical action of the multifocal intraocular lens 24 of the intraocular lens support means 20 placed in front can be relayed to the observer's eye 16 (near the crystalline lens) placed behind the afocal optical system 10, and multifocal A visual appearance equivalent to that of a subject actually wearing the intraocular lens 20 can be experienced. The angular magnification of the afocal optical system 10 is equal, and an observation object (an outside scene or an object) can be observed at the same magnification as in the naked eye state. The entrance pupil diameter of the afocal optical system 10 is preferably larger than the diameter of the multifocal intraocular lens 24.

  The index placed (drawn) in the vicinity of the image plane 15 is guided by the observer so that the eye's adjustment force does not work as much as possible, thereby facilitating the realization of the differential refractive power. .

  On the other hand, the pupil diameter of the eye 16 of the observer who is observing the multifocal intraocular lens 24 using the above multifocal lens simulation apparatus is the same as that of the imaging lens 17 branched from the afocal optical system 10 by the light beam splitting surface 13S. The image can be observed by the imaging device 18 (pupil diameter observation optical system) and can be directly grasped by the index 19. Therefore, the multifocal intraocular lens 24 can be evaluated in consideration of both the pupil diameter and the energy distribution of the multifocal intraocular lens 24 illustrated in FIGS. 9 and 10. Further, the pupil diameter itself of the observer's eye 16 can be increased by increasing the amount of light incident on the eye 16 using one or both of the variable aperture device 41 and the rotary variable attenuation filter device 42 of the light amount control means 40. Since it can be enlarged by reducing and reducing, it is possible to experience the appearance of the multifocal intraocular lens 24 while changing the pupil diameter.

“Embodiment 2”
FIG. 4 shows a second embodiment of the multifocal lens simulation apparatus according to the present invention. This multifocal lens simulation apparatus includes an afocal optical system 30 having an angular magnification of approximately equal magnification, and an intraocular lens support means 20 disposed at the entrance pupil position of the afocal optical system 30. The observer's eye 16 is placed at the exit pupil position of the afocal optical system 30. The intraocular lens support means 20 is the same as that in the first embodiment.

  The afocal optical system 30 has two symmetrically arranged Kepler afocal optical systems 31 and 32. The Kepler afocal optical system 31 on the intraocular lens support means 20 side is in order from the object side in order. It has a lens group 31a and a positive lens group 31c, and an imaging plane (primary imaging plane) 31p is located between the positive lens groups 31a and 31c. The Kepler afocal optical system 32 on the eye 16 side has a positive lens group 32a and a positive lens group 32c in this order from the Kepler afocal optical system 31 side, and an image forming surface between the positive lens groups 32a and 32c. (Secondary imaging plane) 32p is located. The positive lens group 31a and the positive lens group 32c, and the positive lens group 31c and the positive lens group 32a are the same optical system arranged symmetrically. In the afocal optical system 30 described above, the positive lens group 31c and the positive lens group 32a facing each other of the Keplerian afocal optical systems 31 and 32 function as a relay optical system to constitute a substantially equal-magnification afocal optical system.

  A beam splitter 32BS is disposed in the afocal optical system 32, and an image pickup apparatus including the image pickup lens 17 and the image pickup element 18S similar to those in the embodiment of FIG. 1 on a branch optical path branched by the beam splitter 32BS. 18 is arranged. That is, the pupil diameter of the eye 16 can be observed by the pupil diameter observation optical system configured by the beam splitter 32BS, the imaging lens 17, and the imaging device 18.

  A light amount control means 40 is arranged between the positive lens group 31 c of the afocal optical system 31 and the positive lens group 32 a of the afocal optical system 32. The light quantity control means 40 of this embodiment comprises a variable stop device 41 and an insertion / removal type neutral density filter device 43 that replaces the rotary variable neutral density filter device 42 of FIG.

  Also in the second embodiment described above, the observer can observe the object to be observed from behind the afocal optical system 30 through the multifocal intraocular lens 24 of the intraocular lens support means 20 and the afocal optical system 30. . That is, the exit pupil position of the afocal optical system 30 is opened so that the observer's eyes can be placed. In addition, since the intraocular lens support means 20 (multifocal intraocular lens 24) is disposed at a position that has a pupil conjugate relationship with the position where the observer's eyes are assumed to be disposed, the afocal optical system 30 An observer who puts the optical action of the multifocal intraocular lens 24 of the intraocular lens support means 20 placed in front of the afocal optical system 30 through the primary imaging surface 31c and the secondary imaging surface 32c. Can be relayed to the eye 16 (near the crystalline lens), and a visual appearance equivalent to that of a subject actually wearing the multifocal intraocular lens 20 can be experienced. The angular magnification of the afocal optical system 30 is equal, and an observation object (an outside scene or an object) can be observed at the same magnification as that of the naked eye. The entrance pupil diameter of the afocal optical system 30 is preferably larger than the diameter of the multifocal intraocular lens 24.

  Similarly to the first embodiment, the pupil diameter of the eye 16 of the observer who is observing the multifocal intraocular lens 24 using the multifocal lens simulation apparatus is equal to the beam splitter 32BS, the imaging lens 17, and the imaging apparatus. 18 and can be directly grasped by the indicator 19. Therefore, the multifocal intraocular lens 24 can be evaluated in consideration of both the pupil diameter and the energy distribution of the multifocal intraocular lens 24 illustrated in FIGS. 9 and 10. In addition, the pupil diameter of the observer's eye 16 is increased by increasing the amount of light incident on the eye 16 using one or both of the variable aperture device 41 and the insertion / removal type neutral density filter device 43 of the light amount control means 40. Since it can be enlarged by reducing and reducing, it is possible to experience the appearance of the multifocal intraocular lens 24 while changing the pupil diameter.

Next, Numerical Example 1 that embodies the first embodiment will be described.
“Numerical Example 1”
5 and Table 1 show Numerical Example 1, FIG. 5 is a lens configuration diagram, and Table 1 is lens data. In Table 1, NO is the surface number counted from the object side, R is the radius of curvature, d is the lens thickness or lens spacing, N (d) is the d-line refractive index, and ν (d) is the d-line Abbe number. . The unit of R and d is mm. Surface numbers 1 to 8 are intraocular lens support means 20 (surface numbers 5 and 6 are multifocal intraocular lenses 24), and surface numbers 9 to 22 are afocal optical systems 10. The beam splitting surface (film) 13S is provided in the erecting prism 13. FIG. 7 is a lens diagram of an example of the imaging lens 17, and Table 2 shows lens data of the imaging lens 17. The lens data of the imaging lens 17 are assigned surface numbers 1 to 7 in order from the erecting prism 13 side.
"Table 1"
NO R d N (d) ν (d)
1 ∞ 2.000 1.51633 64.1
2 ∞ 1.000 1.33304 (Wed) 55.8
3 -13.650 0.500 1.49176 57.4 Canceling negative lens
4 17.900 0.200 1.33304 (Wed) 55.8
5 17.900 1.000 1.49176 57.4 Intraocular lens (20D)
6 -13.9 1.000 1.33304 (Wed) 55.8
7 ∞ 2.000 1.51633 64.1
8 ∞ 30.000
9 61.392 1.920 1.69680 55.5
10 -205.560 0.600
11 37.320 3.120 1.74400 44.9
12 -37.320 1.200 1.84666 23.8
13 480.000 2.400
14 ∞ 36.000 1.51633 64.1 Upright prism
15 ∞ 7.3
16 ∞ 36.000 1.51633 64.1 Upright prism
17 ∞ 2.400
18 -480.000 1.200 1.84666 23.8
19 37.320 3.120 1.74400 44.9
20 -37.320 0.600
21 205.560 1.920 1.6968 55.5
22 -61.392 34.000
Angular magnification = 0.99
An imaging plane 15 (index) is located between the plane numbers 15 and 16. The d value 34 of the surface number 22 is the distance (eye relief) from the 22nd surface to the eye point (position where the peripheral light beam intersects the optical axis). In an ideal observation state, the exit pupil of the afocal optical system 10 The position matches this eye point.

"Table 2"
No. R d N (d) ν (d) N (850nm)
1 -4.743 2.700 1.84666 23.8 1.82037
2 -5.997 0.900
3 32.385 1.200 1.61800 63.4 1.60987
4 -7.140 0.500 1.80518 25.4 1.78162
5 -30.622 0.150
6 136.146 1.000 1.75500 52.3 1.74299
7 -31.019 20.185
In Table 2, the reason why the refractive index of 850 nm is written together is that, in order to illuminate the eyeball without affecting the function of the simulator, the infrared illumination light source LED (60, FIG. This is because it is preferable to arrange 1).

Next, Numerical Example 2 that embodies the second embodiment will be described.
"Numerical example 2"
6 and Table 3 show Numerical Example 2, FIG. 6 is a lens configuration diagram, and Table 3 is lens data. In this embodiment, the Kepler afocal optical systems 31 and 32 are binocular optical systems (binocular erecting telescopes), and the Kepler afocal optical system 31 on the intraocular lens support means 20 side is the object side. The positive lens group (a positive eyepiece group in the state of binoculars) 31a, an erecting optical system 31b having a total of four reflecting surfaces, and a positive lens group (the same objective lens group) 31c are arranged in order from An imaging plane (primary imaging plane) 31p is located between the group 31a and the erecting optical system 31b. The Kepler afocal optical system 32 on the eye 16 side is an erect surface having a total of four reflecting surfaces, a positive lens group (a positive objective lens group in the state of binoculars) 32a in order from the Kepler afocal optical system 31 side. The optical system 32b includes a positive lens group (same positive eyepiece group) 32c, and an imaging plane (secondary imaging plane) 32p is positioned between the erecting optical system 32b and the positive lens group 32c. The positive lens group 31a and the positive lens group 32c, the erecting optical system 31b and the erecting optical system 32b, and the positive lens group 31c and the positive lens group 32a are the same optical system arranged symmetrically. For the diopter adjustment of the observer, the diopter adjustment function and focusing function of binoculars can be used as they are.

  In addition, since the afocal optical system 30 utilizing the binoculars includes a pair of afocal optical systems (a pair of the optical systems in FIG. 6), the intraocular lens support means 20 forms the pair of afocal optics. By providing a pair corresponding to the system, a simulation apparatus that can be observed with binocular vision can be obtained. Of course, even if the afocal optical system 10 or the afocal optical system 30 is designed exclusively without using the binoculars, the optical system and the intraocular lens support means 20 shown in FIGS. It is preferable to provide a pair for visual observation, but it is also possible to provide the optical system of FIGS. 1, 4 and 5 independently and use it as a simulation apparatus for each eye.

In Table 3, surface numbers 1 to 8 are intraocular lens support means 20 (surface numbers 5 and 6 are multifocal intraocular lenses 24), and surface numbers 9 to 24 are from Kepler afocal optical system 31 and surface number 25. Reference numeral 40 denotes a Keplerian afocal optical system 32. The Kepler afocal optical systems 31 and 32 are the same optical system each having an angular magnification of 8 times. The incident angle of the intraocular lens support means 20 is ± 20 °. The beam splitter 32BS is provided in the erecting prism 32. The imaging lens 17 is the same as that shown in FIG.
"Table 3"
NO R d N (d) ν (d)
1 ∞ 2.000 1.51633 64.1
2 ∞ 1.000 1.33304 (Wed) 55.8
3 -13.650 0.500 1.49176 57.4 Canceling negative lens
4 17.900 0.200 1.33304 (Wed) 55.8
5 17.900 1.000 1.49176 57.4 Intraocular lens (20D)
6 -13.900 1.000 1.33304 (Wed) 55.8
7 ∞ 2.000 1.51633 64.1
8 ∞ 18.000
9 -336.400 6.496 1.62041 60.3
10 -22.388 0.232
11 26.448 11.600 1.62041 60.3
12 -21.460 2.320 1.80518 25.5
13 -188.500 20.834
14 ∞ 52.850 1.51680 64.2
15 ∞ 0.928
16 ∞ 36.285 1.56883 56.0
17 ∞ 32.434
18 -93.448 2.32 1.51742 52.2
19 485.008 35.102
20 ∞ 5.800 1.51680 64.2
21 -87.904 0.348
22 734.524 2.900 1.69895 30.0
23 111.558 8.120 1.51680 64.2
24 -111.558 16.240
25 111.558 8.120 1.51680 64.2
26 -111.558 2.900 1.69895 30.0
27 -734.524 0.348
28 87.904 5.800 1.51680 64.2
29 ∞ 35.102
30 -485.008 2.320 1.51742 52.2
31 93.448 32.434
32 ∞ 36.285 1.56883 56.0
33 ∞ 0.928
34 ∞ 52.850 1.51680 64.2
35 ∞ 20.834
36 188.500 2.320 1.80518 25.5
37 21.460 11.600 1.62041 60.3
38 -26.448 0.232
39 22.388 6.496 1.62041 60.3
40 336.400 20.000
Angular magnification = 0.99
The index is located behind 8.120 (image plane 32p) of the surface number 35. The d value 20.000 of the surface number 40 is the distance (eye relief) from the 40th surface to the eye point (position where the peripheral light beam intersects the optical axis). In an ideal observation state, the exit pupil of the afocal optical system 30 The position matches this eye point.

In the above embodiment, the multifocal intraocular lens 24 is used as the multifocal test lens. However, a test piece optically equivalent to the multifocal intraocular lens 24 can be used as the multifocal test lens. . FIG. 8 is a schematic diagram showing a configuration of a refractive test piece 50 assuming a refractive bifocal intraocular lens. The test piece 50 is formed so that the basic refractive power, which is a distant power, is 0D, and the canceling negative lens can be omitted. The front surface of the test piece 50 is a six-zone structure portion 51, and a light beam passing through a parallel plane portion (concave portion) in the figure has a far focus, and a light beam passing through a convex spherical portion has a near focus. Table 4 shows the parameters of the test piece 50. In Table 4, r is the radius of curvature (mm) of the convex spherical portion, n1 is the refractive index, f is the focal length (mm) of the convex spherical portion, D is the near power (difference refractive power), and sagu is the central annular zone. The step amount (mm) is shown. The center thickness a is 2 mm, for example, and the outer diameter b is 6 mm, for example.
“Table 4”
r 41
n1 1.5
f 250
D 4.00
Sagu 0.11

10 30 Afocal optical system 11 Objective lens group 12 13 Erecting prism 13S Beam splitting surface 32BS Beam splitter 14 Eyepiece lens group 15 Imaging surface 16 Eye 17 Imaging lens 18S Imaging element 18 Imaging device 20 Intraocular lens support means (test) Lens support means)
21 22 Transmission parallel plane plate 23 Liquid holding space 24 Multifocal intraocular lens (multifocal test lens)
25 Offset lens 31 32 Kepler afocal optical system (binoculars)
31a 31c 32a 32c Positive lens group 31b 32b Erecting optical system 31p 32p Imaging surface 40 Light quantity control means 41 Variable aperture device 42 Rotating variable attenuation filter device 43 Insertion / removal attenuation filter device 50 Refractive test piece (multifocal) Test lens)
60 Infrared illumination light source

Claims (17)

An afocal optical system that emits a light beam incident as substantially parallel light as approximately parallel light, and an additional refractive power obtained by adding a difference refractive power to a predetermined reference refractive power and the basic refractive power in front of the afocal optical system A test lens support means for storing a multifocal test lens having a plurality of refractive powers, and an observer can observe an object through the multifocal test lens from the rear through the afocal optical system. The test lens support means is arranged at a position that is in a pupil conjugate relationship with the position where the observer's eyes are supposed to be arranged,
Furthermore, a multifocal lens simulation characterized in that optical path branching means for observing the pupil diameter of the observer from an optical path different from the optical path of the multifocal lens is disposed in the optical path of the afocal optical system. apparatus. 2. The multifocal lens simulation apparatus according to claim 1, wherein an imaging element and an imaging lens for imaging a pupil image of an observer are arranged in an optical path branched from the optical path of the multifocal test lens by the optical path branching unit. Multifocal intraocular lens simulation device. 3. The multifocal lens simulation apparatus according to claim 1, wherein an index indicating a pupil diameter is arranged in the optical path branching unit. The multifocal lens simulation apparatus according to any one of claims 1 to 3, wherein a light amount control means is arranged in an optical path from the multifocal test lens to the optical path branching means. The multifocal lens simulation apparatus according to claim 4, wherein
The light quantity control means is a multifocal lens simulator device which is a neutral density filter device. 6. The multifocal lens simulation device according to claim 5, wherein the neutral density filter device is a variable neutral density filter device that changes the light transmittance stepwise or steplessly. 5. The multifocal lens simulation apparatus according to claim 4, wherein the light amount control means is a diaphragm device that limits a diameter of a light beam reaching the observer. 8. The multifocal lens simulation device according to claim 7, wherein the aperture device is a variable aperture device capable of changing an aperture diameter. 9. The multifocal lens simulation apparatus according to claim 1, wherein the afocal optical system is a Keplerian type that creates a real image of an observation object in the afocal optical system. The multifocal lens simulation apparatus according to claim 9, wherein an index indicating a conjugate position with infinity is arranged in the vicinity of a real image formed in the afocal optical system. 11. The multifocal lens simulation apparatus according to claim 1, wherein the afocal optical system has substantially the same magnification as the entire optical system. 12. The multifocal lens simulation apparatus according to claim 11, wherein the afocal optical system is configured by arranging two afocal optical systems having substantially the same magnification so as to face each other. The multifocal lens simulation apparatus according to any one of claims 1 to 12, wherein the two afocal optical systems are arranged as a pair with a binocular arrangement. 14. The multifocal lens simulation apparatus according to claim 1, wherein the multifocal test lens supported by the test lens support means can be transplanted and inserted into the naked eye in place of the crystalline lens. Multifocal lens simulation device that is an inner lens. The multifocal lens simulation apparatus according to any one of claims 1 to 14, wherein the multifocal test lens supported by the test lens support means has either the basic refractive power or the additional refractive power. A multifocal lens simulation device that is a refractive test piece that is almost zero, or a diffractive test piece. 16. The multifocal lens simulation apparatus according to claim 15, wherein the lens support unit includes a liquid holding unit that holds a liquid, and the liquid holding unit includes the multifocal intraocular lens and the multifocal lens therein. A multifocal lens simulation apparatus that holds a canceling lens having a refractive power that cancels the basic refractive power of an intraocular lens. The multifocal lens simulation apparatus according to any one of claims 1 to 16, further comprising an infrared illumination light source that emits infrared illumination light toward a pupil of an observer.

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