JP2012068551A - Intraocular lens simulation device and simulation method - Google Patents

Abstract

PROBLEM TO BE SOLVED: To provide an intraocular lens simulation device and a method which enable a patient to perceive and experience effects and the like of a multifocal intraocular lens without undergoing surgery for insertion of a multifocal intraocular lens.SOLUTION: The intraocular lens simulation device has a main afocal optical system, test lens support means housing a prescribed test intraocular lens, and a front optical system having a function of reducing the diameter of an incident on-axis luminous flux and then emitting the luminous flux toward the test intraocular lens. An observer can observe an observation object from behind the main afocal optical system through the front optical system, the test intraocular lens, and the main afocal optical system. The test lens support means is disposed in a position having a conjugate relation with the eyes of the observer. A resultant angular magnification of an entire system including the front optical system and the main afocal optical system is approximately one, and the simulation device satisfies a relation 0.77<φ2/φ1<0.89, where φ1 is the diameter of the on-axis luminous flux incident on the front optical system, and φ2 is the diameter of the on-axis luminous flux incident on the test intraocular lens.

Description

  The present invention relates to an intraocular lens simulation apparatus and a simulation method.

  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 at least one of the two condensing points appears to be blurred, the blur becomes noise and deteriorates 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.

  The present invention relates to an intraocular lens simulation apparatus capable of realizing and experiencing the effect, the difference between the diffraction type and the refractive type, or the disadvantages, even without undergoing the insertion operation of the multifocal intraocular lens (before the insertion operation). The purpose is to obtain a simulation method. Furthermore, the present invention provides a high-accuracy intraocular lens that takes into account the influence of the cornea because the light beam incident on the intraocular lens in the eye that has actually undergone the insertion surgery is affected by the positive refractive power of the cornea. An object is to obtain a simulation apparatus and a simulation method.

  In the present invention, a multifocal sample lens (multifocal intraocular lens) is disposed in front of an afocal optical system that emits a light beam incident as parallel light and emits substantially parallel light, and can observe a distant object. From the back of the system, an object to be observed is observed through a multifocal sample lens and an afocal optical system, and an optical system that simulates the positive refractive power of the human cornea is added in front of the afocal optical system. This is based on the viewpoint that the user can feel the wearing feeling of the multifocal sample lens.

That is, the intraocular lens simulation apparatus according to the present invention has a main afocal optical system that emits a light beam incident as parallel light as substantially parallel light; a test lens support unit that houses a predetermined intraocular lens; A front optical system, and the front optical system has a function of reducing the diameter of an axial light beam incident on the front optical system and emitting the light toward the intraocular lens to be examined; The system is arranged in front of the main afocal optical system, and an observer can observe the object to be observed from the rear of the main afocal optical system through the intraocular lens to be examined and the main afocal optical system. The test lens support means is arranged at a position which is in a pupil conjugate relationship with the position where the observer's eyes are supposed to be placed; the test lens support means supports the intraocular lens to be examined Thus, the combined angle magnification of the entire system including the main afocal optical system from the front optical system is approximately equal, and the on-axis light beam diameter of the light beam incident on the front optical system is φ1, When the axial beam diameter of the incident beam is φ2,
0.77 <φ2 / φ1 <0.89
It is characterized by satisfying.

  The intraocular lens simulation device according to the present invention relays the optical action of a multifocal intraocular lens (multifocal intraocular lens or a test piece having an equivalent function) to the vicinity of the observer's crystalline lens. This is a visual experience similar to that of a subject wearing a lens. In order to realize this, a main afocal optical system capable of observing a distant object as well as disposing a test lens support means at a position having a pupil conjugate relationship with a position where an observer's eye is supposed to be disposed. Used. If the lower limit of the above conditional expression is not reached, the focal point, which is the effect of the differential refractive power (difference between the basic refractive power and the additional refractive power), which is the optical action of the multifocal intraocular lens (multifocal intraocular lens), is obtained. The difference in object distance between the far object and the near object that fits is less than the effect of the intraocular lens in the eye that has actually undergone the insertion surgery, making it difficult to feel the actual feeling of two focal points (or multiple focal points). If the upper limit of the conditional expression is exceeded, the difference in the object distance between the far object and the near object in focus, which is the effect of the differential refractive power of the multifocal intraocular lens, in the eye actually undergoing the insertion surgery For example, the object distance of an in-focus object is too close to the effect of an intraocular lens, and it is difficult to experience the usability in a state where an insertion operation is actually performed.

  In the intraocular lens simulation apparatus of the present invention, the front optical system is an enlarged afocal optical system having an angular magnification of about 1.2 times, and the main afocal optical system has an angular magnification of about 1 / 1.2 times. It is preferable that

  In another aspect, a negative power is given to the front optical system, and a positive power rear is provided between the intraocular lens to be examined supported by the lens support means and the main afocal optical system. An optical system is disposed, and the test lens support means holds the test intraocular lens in water, and with the test intraocular lens held in water, the combined angular magnification from the front optical system to the rear optical system is approximately It is preferable to set the same magnification.

  The main afocal optical system is a Kepler type that creates a real image of an observation object in the main afocal optical system. That is, the main 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. As a result, the intraocular lens to be examined can be arranged at the entrance pupil position, and the optical action of the intraocular lens to be examined is relayed to the exit pupil position. The observer can experience the same appearance as the subject wearing the intraocular lens to be examined by placing his eyes so that the crystalline lens is at the exit pupil position as in a general telescope.

  In the main afocal optical system, it is preferable to place an index indicating the spatial position near the real image in the vicinity of the real image formation position. That is, the subject wearing the intraocular lens to be examined does not have an eye adjustment function, but the observer has an eye adjustment function, so the optical action of the multifocal test intraocular lens and the action by the adjustment force are mixed. It is in a state. Therefore, it is desirable to guide an eye so that the eye's accommodation power does not work as much as possible by arranging an index in the vicinity of the real image position formed inside the Kepler type main afocal optical system and observing the index by an observer.

  Specifically, the main 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.

  The main afocal optical system can be arranged binocularly with one pair as one set.

  The multifocal sample lens supported by the lens support means can 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. . Alternatively, a test piece that is optically equivalent to the multifocal intraocular lens can be used as the multifocal intraocular lens. Specifically, in the case of a refractive type multifocal intraocular lens, the optically equivalent test piece includes a transmission portion having no refractive power and the basic refractive power (multifocal actually inserted into the eye). A test piece having a refractive power difference (for example, 4D) with respect to the basic refractive power of the intraocular lens (for example, 20 diopters, hereinafter referred to as D)). It is possible to provide a test piece in which the primary light has a differential refractive power.

  According to an aspect of the simulation method of the multifocal intraocular lens, the present invention provides a step of preparing a main afocal optical system that emits a light beam incident as parallel light as substantially parallel light; A step of arranging an intraocular lens to be examined and a front optical system that emits an incident on-axis light beam with a reduced diameter on the axial axis; synthesis of the entire system including the main afocal optical system from the front optical system The angular magnification is approximately equal; and the observer's eyes are placed behind the main afocal optical system, and the object to be observed is observed through the front optical system, the intraocular lens to be examined, and the main afocal optical system. And a step of performing.

  According to the present invention, it is possible to accurately reproduce a state in which the influence of the positive refractive power of the cornea of the eye after the operation is taken into consideration even without undergoing the insertion operation of the multifocal intraocular lens (before the insertion operation). Therefore, you can accurately experience and experience the effects of intraocular lenses, the difference between diffractive and refractive types, or demerits.

1 is an optical path diagram showing a first embodiment of an intraocular lens simulation apparatus according to the present invention. It is sectional drawing which shows one Embodiment of the vicinity of the intraocular lens optical system of the intraocular lens simulation apparatus of FIG. It is sectional drawing which shows one Embodiment of the test lens holder of the intraocular lens simulation apparatus of FIG. 1, FIG. It is an optical path diagram which shows 2nd embodiment of the intraocular lens simulation apparatus by this invention. FIG. 5 is an enlarged cross-sectional view of the vicinity of an intraocular lens optical system of the intraocular lens simulation apparatus of FIG. 4. It is sectional drawing which shows one Embodiment of the to-be-tested lens holder of the intraocular lens simulation apparatus of FIG. 4, FIG. It is a schematic diagram which shows the structure of a refraction type test piece. It is an external appearance perspective view of one Embodiment which made the intraocular lens simulation apparatus by this invention the binocular type.

“Embodiment 1”
1 to 3 show a first embodiment of an intraocular lens simulation apparatus according to the present invention. This intraocular lens simulation apparatus has a main afocal optical system 10 and an intraocular lens optical system 200 disposed at the entrance pupil position of the main afocal optical system 10. The main afocal optical system 10 is an optical system that emits a substantially parallel light beam when a light beam (parallel light beam) from an object at infinity is incident.

  The main afocal optical system 10 is a so-called Keplerian optical system having a positive power objective lens group 11, a prism 12, a prism 13, and a positive power eyepiece group 14 in order from the object side. A real image of the observed object is formed on the imaging plane 15, and 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 main afocal optical system 10. The The prism 12 and the prism 13 are erecting optical systems for erecting an image, and each of the two surfaces has a total of four reflecting surfaces. 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.

  The intraocular lens optical system 200 includes an intraocular lens support means 20 and a front optical system 40 positioned in front of the intraocular lens support means 20 as shown in an enlarged view in FIGS. Yes. The intraocular lens support means 20 is a liquid holding space 23 between the transmission side parallel plane plates 21 and 22 on the incident side and the emission side, and in the liquid (water) held in the liquid holding space 23, A focal intraocular lens (intraocular lens to be examined) 24 and a canceling lens 25 are held. The transmission parallel flat plates 21 and 22 are fixed to a casing 26, and a lens holder 27 that can be attached to and detached from the casing 26 holds an intraocular lens (multifocal sample lens) 24 and an offset lens 25. . The liquid holding space 23 of the intraocular lens optical system 200 is disposed at the entrance pupil position of the main afocal optical system 10. Regardless of whether the multifocal intraocular lens 24 is a refractive type or a diffractive type, the basic refractive power (for example, 20D) in water (body fluid) and the additional refractive power obtained by adding a differential refractive power to the basic refractive power. Force (eg 24D). 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. The incident angle of the intraocular lens optical system 200 in FIG. 2 is ± 10 °. FIG. 3 shows an embodiment in which the intraocular lens optical system 200 having the intraocular lens support means 20 and the front optical system 40 is made into a holder.

  Further, in the case of using a test piece having a basic refractive power of zero and giving only a differential refractive power instead of the multifocal intraocular lens, the canceling lens 25 can be omitted. Further, in the first embodiment, since the light beam entering / exiting the liquid holding space 23 is afocal, the difference refractive power of the test piece is relayed to the observer when held in water. The design which relays predetermined difference refractive power to an observer, when hold | maintaining in air may be sufficient. In the case of an in-air test piece, liquid (water) may be drained from the liquid holding space 23 to be hollow.

  The front optical system 40 includes a Galileo afocal system including a positive lens 41 and a negative lens 42, and simulates the influence of the positive refractive power of the cornea of the eye. In other words, when an intraocular lens is inserted instead of actually extracting the crystalline lens, the light beam incident on the intraocular lens becomes a condensed light beam due to the influence of the cornea, so that the light beam diameter incident on the cornea is incident on the intraocular lens. The luminous flux diameter is different. On the other hand, a light beam diameter before and after the multifocal intraocular lens 24 (test lens) in the intraocular lens optical system 200 is disposed in the intraocular lens optical system 200. Thus, the multifocal intraocular lens 24 can be evaluated by making it equal to the light beam diameter before and after the intraocular lens in a state where the intraocular lens is actually inserted into the eye.

  The angular magnification of the front optical system 40 is determined so that the angular magnification in the entire system is substantially equal in consideration of the combined angular magnification with the main afocal optical system 10. Specifically, when the angular magnification of the front optical system 40 is about 1.2 times, the angular magnification of the main afocal optical system 10 is set to about 0.83 times (= 1 / 1.2). The angular magnification of the entire system can be made approximately equal. In this embodiment, the intraocular lens support means 20 including the multifocal intraocular lens 24 and the cancellation lens 25 has only the remaining differential refractive power. In this way, by setting the power of the front optical system 40, the main afocal optical system 10, and the canceling lens 25, the pupil magnification in the vicinity of the multifocal intraocular lens 24 and the observer's crystalline lens is made approximately equal, so that The action of the differential refractive power in the optical action of the intraocular lens 24 can be relayed with high accuracy to the vicinity of the observer's crystalline lens.

  More specifically, in order to more accurately relay the optical action of the multifocal intraocular lens 24 to the vicinity of the crystalline lens of the observer of the simulation apparatus, the pupil diameter at the intraocular lens position in the simulation apparatus is determined. It is desirable that the (axial beam diameter) and the pupil diameter (axial beam diameter) at the observer's crystalline lens position are approximately equal. This is because the pupil diameter (axial beam diameter) of the intraocular lens in the simulation apparatus is approximately equal to the pupil diameter (axial beam diameter) that passes through the intraocular lens inserted into the eye by surgery. It means to do. The refractive power (optical action) of the multifocal intraocular lens 24 is relayed to the observer's eye in proportion to the square of the pupil diameter in the simulation apparatus. If the difference between the diameter and the pupil diameter in the state of being actually inserted into the eye is large, the simulation accuracy is significantly reduced. Here, depending on the numerical value of LeGrand's model eye, the pupil diameter of the lens is reduced to about 0.89 times on the entrance surface of the lens and about 0.77 times on the exit surface relative to the entrance pupil diameter (axial beam diameter) to the cornea. It is known that this reduction relationship is related to the relationship between the axial beam diameter of the multifocal intraocular lens 24 and the exit-side axial beam diameter of the main afocal optical system 10, that is, the incident beam diameter to the observer's cornea. In addition, the optical action of the multifocal intraocular lens can be relayed with high accuracy. That is, it is desirable that the pupil magnification (= exit pupil / incident pupil) of the main afocal optical system 10 takes this reduction relationship into consideration. In other words, the reduction magnification of the pupil diameter at the lens position is 0.89 to 0.77 in the LeGrand model eye, so when the average magnification is about 0.83 times, the pupil magnification of the main afocal optical system is 1 / 0.83 = 1.2 times (in this case, angular magnification) Therefore, the relationship between the axial light beam diameter of the multifocal intraocular lens 24 and the light beam diameter incident on the cornea of the observer is close to the state in which the intraocular lens is inserted by actual surgery. It can be set to the state. However, since only the main afocal optical system 10 has an angular magnification of 0.83, the perspective of the object to be observed (outside landscape or object) is not correctly reflected. Therefore, by adding a front optical system 40 (Galileo afocal system) having an angular magnification of about 1.2 times in front of the intraocular lens support means 20, a multi-focal intraocular lens 24 is allowed to pass a light beam of 0.83 times, The angle magnification in the entire system of this simulation apparatus is the same magnification (main afocal optical system 0.83 times × front optical system 1.2 times = 1.0 times), and the perspective of the object to be observed is appropriately maintained.

  According to the intraocular lens simulation apparatus described above, the observer can positively correlate the cornea by the light beam that has passed through the front optical system 40, the multifocal intraocular lens 24, and the main afocal optical system 10 in this order. The object to be observed can be observed in a state where the influence of refractive power is also simulated. That is, the intraocular lens optical system 200 (multifocal intraocular lens 24) is arranged at a position that has a pupil conjugate relationship with the exit pupil position of the main afocal optical system 10 where the observer's eyes are assumed to be arranged. In addition, since the intraocular lens optical system 200 includes a front optical system 40 that simulates the influence of the cornea in front of the intraocular lens optical system 200, the intraocular lens optical system 200 placed in front of the main afocal optical system 10 The optical action of the multifocal intraocular lens 24 can be relayed to the observer's eye 16 (near the lens) placed behind the main afocal optical system 10 in consideration of the effect of the cornea. A visual appearance equivalent to that of the subject actually wearing the intraocular lens 24 can be experienced. The combined angle magnification from the front optical system 40 to the main afocal optical system 10 is equal, and an object to be observed (an outside scene or object) can be observed at a magnification similar to that of the naked eye. The entrance pupil diameter (mechanical open diameter) of the main afocal optical system 10 is preferably larger than the diameter of the multifocal intraocular lens 24.

  An index placed (drawn) in the vicinity of the imaging plane 15 is guided by an observer to fix the eye's accommodation power to a predetermined value as much as possible by observing the index, and the difference power can be realized. Make it easier.

Next, a specific numerical example 1 will be described.
“Numerical Example 1”
Table 1 shows lens data of Numerical Example 1. 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 6 are the front optical system 40 (the plane parallel plate 21 is also an element of the front optical system 40), surface numbers 7 and 8 are the canceling lens 25, surface numbers 9 and 10 are the multifocal intraocular lens 24, and the surface Reference numerals 13 to 26 denote the main afocal optical system 10.
"Table 1"
NO R d N (d) ν (d)
1 33.000 3.200 1.77250 49.6
2 -54.300 2.930
3 -36.400 1.500 1.80 100 35.0
4 36.400 1.000
5 ∞ 2.000 1.51633 64.1
6 ∞ 1.000 1.33304 (Wednesday) 55.8
7 -13.650 0.500 1.49176 57.4 Refracting power canceling lens
8 17.900 0.200 1.33304 (Wed) 55.8
9 17.900 1.000 1.49176 57.4 Intraocular lens (20D)
10 -13.900 1.000 1.33304 (Wed) 55.8
11 ∞ 2.000 1.51633 64.1
12 ∞ 20.500
13 51.160 1.600 1.69680 55.5
14 -171.300 0.500
15 31.100 2.600 1.74400 44.9
16 -31.100 1.000 1.84666 23.8
17 400.000 2.000
18 ∞ 30.000 1.51633 64.1 Prism 12
19 ∞ 6.690
20 ∞ 36.000 1.51633 64.1 Prism 13
21 ∞ 2.400
22 -480.000 1.200 1.84666 23.8
23 37.320 3.120 1.74400 44.9
24 -37.320 0.600
25 205.560 1.920 1.69680 55.5
26 -61.392 34.000
Total system angle magnification = 0.98
On-axis beam diameter φ1 to the front optical system = 7.08
On-axis incident beam diameter φ2 = 5.98 to the intraocular lens to be examined
φ2 / φ1 = 0.84
An index is arranged on the imaging plane 15 between the plane numbers 19 and 20. The d value 34 of the surface number 26 is the distance (eye relief) from the 26th surface to the eye point (position where the peripheral light beam intersects the optical axis). In an ideal observation state, the exit value of the main afocal optical system 10 The pupil position matches this eye point.

“Embodiment 2”
4 to 6 show a second embodiment of the intraocular lens simulation apparatus according to the present invention. This intraocular lens simulation apparatus has a main afocal optical system 30 with an angular magnification of approximately equal magnification, and an intraocular lens optical system 200N disposed at the entrance pupil position of the main afocal optical system 30. The intraocular lens optical system 200N includes an intraocular lens support unit 20N and a front optical system 40N positioned in front of the intraocular lens support unit 20N. An observer's eye 16 is placed at the exit pupil position of the main afocal optical system 30.

  The intraocular lens support means 20N is obtained by replacing the parallel plane plates 21 and 22 before and after the intraocular lens support means 20 of Embodiment 1 with a negative lens 21N and a positive lens 22P, and a multifocal intraocular lens 24 and an offset lens. 25 is the same as in the first embodiment. When the liquid holding space is filled with water, the negative lens 21N and the positive lens 22P also serve as a cover glass for holding the liquid.

  The front optical system 40N includes a positive lens 41, a negative lens 42, and a negative lens 21N of the intraocular lens support means 20N. The front optical system 40N, the intraocular lens 24 to be examined of the intraocular lens support means 20N, The combined angular magnification of the canceling lens 25 and the positive lens 22P (rear optical system) is set to approximately equal magnification. Thus, by making the combined angle magnification from the front optical system 40N to the rear optical system 22P substantially equal, the perspective of the object to be observed can be appropriately maintained. FIG. 6 shows an embodiment in which an intraocular lens optical system 200N having an intraocular lens support means 20N and a front optical system 40N is made into a holder.

  The main afocal optical system 30 has two symmetrically arranged Kepler afocal optical systems 31 and 32, and the Kepler afocal optical system 31 on the intraocular lens support means 20N side is in order from the object side. The positive lens group 31a includes an erecting optical system 31b having a total of four reflecting surfaces, and a positive lens group 31c. An imaging surface (primary imaging surface) 31p is formed between the positive lens group 31a and the erecting optical system 31b. Is located. The Kepler afocal optical system 32 on the eye 16 side includes, in order from the Kepler afocal optical system 31 side, a positive lens group 32a, an erecting optical system 32b having a total of four reflecting surfaces, and a positive lens group 32c. An imaging plane (secondary imaging plane) 32p is located 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.

  Since the combined angular magnification and pupil magnification of the Kepler afocal system 31 on the intraocular lens support means 20N side and the Kepler afocal optical system 32 on the eye 16 side are both approximately equal, the main afocal optical system 30 is The optical function of the intraocular lens support means 20N including the multifocal intraocular lens 24 placed at the entrance pupil position is merely a function of simply relaying to the exit pupil position. That is, unlike the first embodiment, the main afocal optical system 30 does not cancel the angular magnification of the front optical system 40N that simulates the cornea. Therefore, in the second embodiment, the relationship between the axial light beam diameter of the multifocal intraocular lens 24 and the incident light beam diameter to the observer's cornea, which the main afocal optical system 10 of the first embodiment is responsible for, is actually measured. The intraocular lens optical system 200N has an optical function for setting a state close to the state in which the intraocular lens is inserted by surgery. That is, by the front optical system 40N (including the negative lens 21N) of the intraocular lens optical system 200N, the emitted light beam from the multifocal intraocular lens 24 is set as a divergent light having a predetermined divergence at a predetermined distance. It is arranged so as to be incident on a certain positive lens 22P (rear optical system), and the ratio of the axial beam diameter emitted from the positive lens 22P to the axial beam diameter emitted from the multifocal intraocular lens 24 is 1 / 0.89 = 1.12 times. I am doing so. The positive power of the positive lens 22P is set so that the light beam emitted from the positive lens 22P is made into a substantially parallel light beam and enters the main afocal optical system 30. The negative lens 21N functions so that the light beam incident on the multifocal intraocular lens 24 becomes a predetermined divergent light. In this embodiment, for example, when a parallel light beam is incident on the front optical system 40, the positive lens 41 and the negative lens 42 function as a Galileo afocal system. Accordingly, the light beam incident on the negative lens 21N also becomes a parallel light beam, and the axial light beam emitted from the positive lens 22P (rear optical system) is also converted into a parallel light beam. Therefore, as the intraocular lens support means 20N, an inverse Galilean afocal optical system is used. Is configured. In addition, the angular magnification of the intraocular lens optical system 200N is configured to be kept approximately equal. As described above, by placing the front optical system 40N, the cancellation lens 25, the multifocal intraocular lens 24, and the positive lens (rear optical system) 22P inside the intraocular lens optical system 200N, the intraocular lens pupil diameter can be reduced. It is possible to simulate the influence of the observer's cornea by setting the observer's lens pupil diameter to approximately the same magnification. In this case, the ratio of the axial beam diameter incident on the negative lens 21N and the axial beam diameter emitted from the positive lens 22P is 1 / 0.83 = 1.2 times that of the multifocal intraocular lens 24. It gets bigger. In this example, the pupil magnification of the front optical system 40N is 0.78 times (angular magnification is 1.29 times). Further, in this embodiment, the power of the positive lens 22P is set to substantially match the power of the cornea to be used as a pseudo cornea, and the intraocular lens 24 is held at a position where the axial beam diameter is reduced to about 0.83 times. . Thus, the relationship between the incident and output angles of the axial rays of the positive lens 22P functioning as a pseudo cornea and the multifocal intraocular lens 24 is set to a state close to the state in which the intraocular lens is inserted by the operation. Since the intraocular lens support means 20N (Galileo afocal system) is configured so that the angular magnification is substantially equal, the angle of the entire optical system can be set even if it is attached to the entrance pupil position of the main afocal optical system 30. The magnification is maintained at approximately the same magnification.

  In the second embodiment, for example, two commercially available Kepler binoculars can be used as they are, and the objective optical systems can be arranged to face each other. In that case, the diopter adjustment of the observer can use the diopter adjustment function and the focusing function provided in the binoculars as they are. Each binocular has a pair of left and right erecting optical systems 31b and a pair of left and right erecting optical systems 32b. For example, erecting optics using a plurality of reflecting surfaces such as Porro prisms are used. Since the system (image reversal optical system) limits the incident angle of the optical system, all the erecting optical systems 31b and the erecting optical systems 32b are used when configuring an optical system dedicated to the intraocular lens simulation apparatus. Is preferably omitted. In the afocal optical system in which the erecting optical system 31b and the erecting optical system 32b are omitted, the positive lens group 31c and the positive lens group 32a facing each other of the Kepler afocal optical systems 31 and 32 are a relay optical system and an image correcting system. It functions as a vertical optical system.

  Further, when binoculars are used, the main afocal optical system 30 includes a pair of afocal optical systems (a pair of the optical systems in FIG. 4), so the intraocular lens support means 20N forms a pair. By providing a pair corresponding to the afocal optical system, a simulation apparatus that can be observed with binocular eyes can be obtained. Of course, even if the main afocal optical system 10 or the main afocal optical system 30 is designed exclusively without using the binoculars, the optical system and the intraocular lens support means 20 (20N) shown in FIGS. It is preferable to provide a pair for left and right eyesight, but it is also possible to provide the optical system of FIGS. 1 and 4 independently and use it as a simulation apparatus for each eye.

Next, a specific numerical example 2 will be described.
"Numerical example 2"
Table 2 shows lens data of Numerical Example 2. Surface numbers 1 to 6 are the front optical system 40, surface numbers 7 and 8 are the cancellation lens 25, 9 and 10 are the multifocal intraocular lens 24, surface numbers 11 and 12 are the positive lens (rear optical system) 22P, and surface number 13 Reference numerals 28 to 28 denote a Keplerian afocal optical system 31, and surface numbers 29 to 44 denote a Kepler 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. Further, when a test piece having a basic refractive power of zero and only a differential refractive power is used instead of the multifocal intraocular lens, the canceling lens 25 can be omitted. The incident angle of the intraocular lens support means 20N is ± 20 °.
"Table 2"
NO R d N (d) ν (d)
1 32.000 3.500 1.77250 49.6
2 -73.650 4.800
3 -36.400 1.500 1.80 100 35.0
4 36.400 1.000
5 -10.500 1.000 1.49176 57.4
6 21.500 0.930 1.33304 (Wed) 55.8
7 -13.650 0.500 1.49176 57.4 Refracting power canceling lens
8 17.900 0.200 1.33304 (Wed) 55.8
9 17.900 1.000 1.49176 57.4 Intraocular lens (20D)
10 -13.900 1.500 1.33304 (Wed) 55.8
11 ∞ 2.000 1.49176 57.4
12 -11.700 17.000
13 -336.400 6.496 1.62041 60.3
14 -22.388 0.232
15 26.448 11.600 1.62041 60.3
16 -21.460 2.320 1.80518 25.5
17 -188.500 20.834
18 ∞ 52.850 1.51680 64.2
19 ∞ 0.928
20 ∞ 36.285 1.56883 56.0
21 ∞ 32.434
22 -93.448 2.320 1.51742 52.2
23 485.008 35.102
24 ∞ 5.800 1.51680 64.2
25 -87.904 0.348
26 734.524 2.900 1.69895 30.0
27 111.558 8.120 1.51680 64.2
28 -111.558 16.240
29 111.558 8.120 1.51680 64.2
30 -111.558 2.900 1.69895 30.0
31 -734.524 0.348
32 87.904 5.800 1.51680 64.2
33 ∞ 35.102
34 -485.008 2.320 1.51742 52.2
35 93.448 32.434
36 ∞ 36.285 1.56883 56.0
37 ∞ 0.928
38 ∞ 52.850 1.51680 64.2
39 ∞ 20.834
40 188.500 2.320 1.80518 25.5
41 21.460 11.600 1.62041 60.3
42 -26.448 0.232
43 22.388 6.496 1.62041 60.3
44 336.400 20.000
Total system angle magnification = 1.00
On-axis beam diameter φ1 to the front optical system = 6.28
On-axis incident beam diameter φ2 = 5.48 to the intraocular lens to be examined
φ2 / φ1 = 0.87
An index is located on the imaging plane 32p at the rear 8.12 of the surface number 39. The d value 20 of the surface number 44 is the distance (eye relief) from the 44th surface to the eye point (position where the peripheral light beam intersects the optical axis), and is emitted from the main afocal optical system 30 in an ideal observation state. The pupil position matches this eye point.

In the above embodiment, the multifocal intraocular lens 24 is used as the intraocular lens to be examined. However, a test piece that is optically equivalent to the multifocal intraocular lens 24 can be used as the intraocular lens to be examined. FIG. 7 is a schematic diagram showing the 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 3 shows the parameters of the test piece 50. In Table 3, r is the radius of curvature of the convex spherical portion (mm), n1 is the refractive index, f is the focal length of the convex spherical portion in water (mm), D is the near power in water (differential refractive power), sagu indicates the amount of step (mm) in the central ring zone. The center thickness a is 2 mm, for example, and the outer diameter b is 6 mm, for example.
"Table 3"
r 41
n1 1.5
f 250
D 4.00
Sagu 0.11

  FIG. 8 shows an appearance of an embodiment in which the intraocular lens simulation apparatus according to the present invention is a binocular type. The optical barrel 10B or 30B incorporating the afocal optical system 10 shown in FIG. 1 or the afocal optical system 30 shown in FIG. 4 is provided with a pair of left and right, and the pair of optical barrels 10B or 30B is provided. The intraocular lens optical system 200 shown in FIG. 2 is provided at the tip. According to this binocular intraocular lens simulation apparatus, the simulation effect can be experienced with binocular.

10 30 Main afocal optical system 11 Objective lens group 12 13 Prism 14 Eyepiece lens group 15 Imaging surface 16 Eye 200 200N Intraocular lens optical system 20 20N Intraocular lens support means (test lens support means)
21 22 Transmission plane parallel plate 21N Negative lens 22P Positive lens (rear optical system)
23 Liquid holding space 24 Multifocal intraocular lens (multifocal subject intraocular 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 40N Front optical system 41 Positive lens 42 Negative lens 50 Refractive test piece (multifocal intraocular lens)

Claims (11)

Having a main afocal optical system that emits a light beam incident as parallel light as substantially parallel light;
A test lens support means for storing a predetermined test intraocular lens and a front optical system, and the front optical system is directed toward the test intraocular lens by reducing the diameter of the axial light beam incident on the front optical system. Having the action of injecting,
The test lens support means and the front optical system are arranged in front of the main afocal optical system, and an observer passes through the test intraocular lens and the main afocal optical system from the rear of the main afocal optical system. Being able to observe the object,
The test lens support means is disposed at a position that is in a pupil conjugate relationship with the position where the observer's eyes are assumed to be disposed;
The combined angular magnification of the entire system including the main afocal optical system is approximately equal to the front optical system with the intraocular lens to be tested supported by the test lens support means, and is incident on the front optical system. When the axial light beam diameter of the light beam to be incident is φ1, and the axial light beam diameter of the light beam incident on the intraocular lens to be examined is φ2,
0.77 <φ2 / φ1 <0.89
Be satisfied,
An intraocular lens simulation apparatus characterized by the above.   2. The intraocular lens simulation apparatus according to claim 1, wherein the front optical system is an enlargement afocal optical system having an angular magnification of about 1.2 times, and the main afocal optical system has an angular magnification of about 1/1. Intraocular lens simulation device that is double.   The intraocular lens simulation device according to claim 1, wherein the front optical system has a negative power, and the test intraocular lens supported by the test lens support means and the main afocal optical system, A positive power rear optical system is disposed, and the test lens support means holds the test intraocular lens in water and holds the test intraocular lens in water, from the front optical system to the rear optical system. An intraocular lens simulation apparatus in which the combined angle magnification is set to approximately equal magnification.   4. The intraocular lens simulation apparatus according to claim 1, wherein the main afocal optical system is a Kepler type that creates a real image of an observation object in the main afocal optical system. .   5. The intraocular lens simulation apparatus according to claim 4, wherein an index indicating a spatial position in the vicinity of the real image is arranged in the vicinity of the real image formed in the main afocal optical system.   4. The intraocular lens simulation apparatus according to claim 1, wherein the main afocal optical system is configured by arranging two afocal optical systems having substantially the same magnification so as to face each other.   The intraocular lens simulation apparatus according to any one of claims 1 to 6, wherein the main afocal optical system is a binocular arrangement with a pair as a pair.   8. The intraocular lens simulation apparatus according to claim 1, wherein the test intraocular lens supported by the test lens support means is a multifocal intraocular that can be implanted and inserted into the naked eye instead of the crystalline lens. An intraocular lens simulation device that is a lens.   8. The intraocular lens simulation apparatus according to claim 1, wherein the intraocular lens to be examined supported by the test lens support means is an addition of a basic refractive power or a basic refractive power plus a differential refractive power. An intraocular lens simulation apparatus, which is a refractive test piece or a diffractive test piece in which either one of the refractive powers is almost zero. 7. The multifocal lens simulation apparatus according to claim 6, wherein a variable stop is disposed in the main afocal optical system. Preparing a main afocal optical system for emitting a light beam incident as parallel light as substantially parallel light;
Disposing a predetermined intraocular lens in front of the main afocal optical system, and a front optical system that emits an incident axial light beam with a reduced diameter on the axial axis;
The combined angle magnification of the entire system including the main afocal optical system from the front optical system is approximately equal; and the observer's eyes are arranged behind the main afocal optical system, and the front optical system Observing the object through the intraocular lens to be examined and the main afocal optical system;
An intraocular lens simulation method comprising: