JP2014036769A - Intraocular lens member and intraocular lens - Google Patents

Abstract

PROBLEM TO BE SOLVED: To provide an intraocular lens member and an intraocular lens that allow the eye to exhibit the accommodation ability based on a change in shape of the lens capsule due to tension and relaxation of the ciliary muscle and a change in tensile force acting on the lens capsule, and that allow achievement of normal vision and aberration correction.SOLUTION: An intraocular lens member is accommodated in the lens capsule and freely deformed according to deformation of the lens capsule. The intraocular lens member has a hallow part. When an outermost surface in the intraocular lens member is taken as an outer plane and a plane to form the hollow part in the intraocular lens member is taken as an inner plane, a curvature radius of the outer plane is different from that of the inner plane in at least one of an anterior capsule portion and a posterior capsule portion at the center of the intraocular lens member in a plane view.

Description

  The present invention relates to an intraocular lens member and an intraocular lens. More specifically, the present invention relates to an intraocular lens member and an intraocular lens corresponding to a change in the shape of the lens capsule or a change in tension acting on the lens capsule due to tension and relaxation of the ciliary muscle.

  Naturally, the human eye has a so-called “adjustment power” that is the ability to change the object distance imaged on the retina. The “adjustment power” is expressed as follows. If the farthest object point that can be imaged on the retina is the far point and the closest object point is the near point, the difference between the "reciprocal of the distance to the far point" and the "reciprocal of the distance to the near point" It becomes adjustment power. Here, the unit of distance is meters (m), and the unit of accommodation force is diopter (hereinafter referred to as D). In other words, the larger the numerical value, the wider the distance from the far point to the near point, and the wider the range of the object distance that can be imaged on the retina.

  In general, young people have an adjustment power of about 10D. However, the adjusting power tends to gradually decrease with aging, and in general, the adjusting power significantly decreases after the age of 50 years. This is called presbyopia.

On the other hand, when the cataract surgery removes the lens cortex and lens nucleus (hereinafter referred to as the lens parenchyma) in the lens capsule and replaces it with an artificial intraocular lens, most of the lens is lost. Loss of adjustability.
Currently, there are single-focus intraocular lenses and multi-focus intraocular lenses that are generally used. However, since the focal distance of the single focus intraocular lens is fixed, the object distance imaged on the retina is fixed, and an object at an arbitrary distance cannot be imaged on the retina. The multifocal intraocular lens is set so that an object at an object distance of 2 to 3 points forms an image on the retina. It cannot be changed to a position. In addition, since a single object point forms a plurality of images with different blurs on the retina in a superimposed manner, the lens wearer may complain that it is difficult to see.

  Lens refilling is a method for reconstructing the lens. Lens refilling is a lens reconstruction that replaces the lens parenchyma in the lens capsule with a flexible artifact while retaining most of the natural lens capsule. There are various methods for lens refilling, but most of them aim to restore the adjustment force by deforming the substituted artificial lens due to the change in the shape of the lens capsule or the change in the tension acting on the lens capsule. Yes.

As a technique for carrying out lens refilling, various methods are known as follows.
・ Direct injection method that directly injects artifacts into the lens capsule (Patent Document 1)
A balloon system in which a thin film-like balloon is inserted into the lens capsule and an injection substance is injected into the balloon (Patent Document 2, Non-Patent Document 1)
In the lens capsule, a bag is placed on the side of the lens facing the retina, and a filling member is filled in the bag, while a substance that defines the volume of the lens is inserted on the side facing the cornea Deformed balloon system (Patent Document 3)
A method of inserting an artificial intraocular lens (IOL) into a lens capsule containing a gel substance (Patent Documents 4 to 5)
A so-called lid lens system in which an artificial intraocular lens replaces the hole so that the gel-like substance does not leak from the hole formed in the anterior capsule portion of the lens capsule during surgery (Patent Document 6, Non-Patent Document) Reference 2)
-An expansible gel method in which an expansive gel is inserted into the lens capsule and the expansive gel is swollen by aqueous humor (Patent Document 7)

JP-T-2002-506690 JP-A-4-2224746 Special table 2003-521335 gazette Special table 2007-535381 gazette Special table 2003-532491 gazette JP 2005-73890 A JP 2005-160565 A

Nishi O, Nishi K, Mano C, Ichihara M, Honda T, Controlling the capsule shape in lens refilling. , Arch Ophthalmol. 1997; 115 (4): 507-510. Research on lens regeneration and restoration of restoration by artificial substance injection, Nishi Koshi, Osaka City Medical Society Journal 2010; 59 (1/2): 1-10 Latest technology and development of medical gel, Ryo Yoshida, CMC Publishing, page 2.3, section 2.3

However, in the direct injection method, the balloon method, and the deformed balloon method as in Patent Documents 1 to 3 and Non-Patent Document 1, the injection amount of the injection substance is related to both the normalization and the aberration correction.
Here, “straightening” means a state in which an appropriate refractive power is secured so that an object at a set object distance forms an image on the retina.
“Aberration correction” refers to a state in which aberrations (mainly spherical aberration) due to an artificial object inserted in the lens capsule are corrected.

  Even if the normalization is appropriate, if the aberration correction is not appropriate, the object to which the line of sight is directed is visually recognized in a blurred or distorted state. As for the injection amount of the artifact, there is an optimal injection amount for correcting the aberration, while there is an optimal injection amount for correcting the aberration. That is, there is a possibility that normalization and aberration correction cannot be achieved at the same time.

  Further, it is known that the injection amount of the artificial object affects the adjustment force obtained after the operation (see Results and Confusions on p.507 of Non-Patent Document 1). Therefore, the injection amount of the artifact is substantially related to three items, that is, normalization, aberration correction, and maximization of adjustment power. Therefore, when the injection amount is determined so as to optimize one of the items, the other two items tend not to be arbitrarily controlled.

  The method of inserting an IOL into a capsular bag containing a gel-like substance as in Patent Documents 4 to 6 and Non-Patent Document 2 enables control of two elements of the injection amount and the lens shape. Of the maximization of adjustment power, it has the possibility of controlling two at the same time. When tension and relaxation of the ciliary muscle occur and deformation occurs in the capsular bag, References 4 and 6 indicate that the IOL moves back and forth, and Reference 5 and Non-Patent Document 2 indicate that the adjustment occurs due to the deformation of the IOL. However, with a force that causes deformation of the capsular bag, there is a low possibility that a back-and-forth movement or shape change that can generate a practical adjustment force will occur.

  The swellable gel used in the expansive gel method as in Patent Document 7 is lower than the refractive index of the original human crystalline lens. For example, in Non-Patent Document 3, the refractive index of such an expansible material is close to the value (1.33) of water, which is the main component. Since the difference in refractive index between the inflatable material and the aqueous humor is small, even if the lens changes in shape, the resulting adjustment force is small. Moreover, since the refractive index of the expansible material is small, there is also a problem that it is difficult to ensure the refractive power necessary for making it normal.

  Therefore, the present invention makes it possible to exert the accommodation power of the eye based on the change in the shape of the lens capsule due to the tension and relaxation of the ciliary muscles or the change in the tension acting on the lens capsule, while performing the normalization and aberration correction. It is a main object to provide an intraocular lens member and an intraocular lens that can be achieved.

  The present inventor has studied a method for solving the above-described problem. In the study, it was assumed that eye accommodation was secured. That is, in the intraocular lens, at least the member that contacts the lens capsule is used in the lens capsule and can be deformed as the lens capsule deforms.

  However, with only the above setting, as described in the problem of the present invention, there remains a problem of the injection amount related to the normalization and the aberration correction. Also, it is not easy to prepare a material capable of realizing a refractive power as high as required by the lens wearer for the refractive index of the injected material.

  Therefore, the present inventor has obtained the following knowledge. First, the intraocular lens member that finally becomes a part of the intraocular lens has a hollow structure having a hollow portion. When finally becoming an intraocular lens, this hollow portion is filled with a filling member having fluidity. Then, when the outermost surface of the intraocular lens member is the outer surface and the surface of the intraocular lens member that forms the hollow portion is the inner surface, the shape of the outer surface is the filling amount of the filling member (in the above-mentioned problem “ The inventors have come up with an intraocular lens member and an intraocular lens that make it possible to reduce the ratio depending on the injection amount “) as much as possible. That is, the present inventor has obtained the knowledge that the outer surface and the inner surface are designed based on different ideas in advance at the stage of the intraocular lens member.

  Normalization and aberration correction are achieved in the design of the refractive index and internal shape of the material used for the filling member. On the other hand, the present inventor has conceived the idea of designing the outer surface shape so that the force from the capsular bag is efficiently brought into the shape change of the inner surface shape.

  The aspect which materialized the above thought is the following aspects.

The first aspect of the present invention is:
A member for an intraocular lens that is housed in a capsular bag and can be deformed along with the deformation of the capsular bag,
The intraocular lens member has a hollow portion,
When the outermost surface of the intraocular lens member is an outer surface, and the surface forming the hollow portion in the intraocular lens member is an inner surface,
In the central portion of the intraocular lens member in plan view, the curvature radius of the outer surface and the curvature radius of the inner surface are different from each other in at least one of the anterior capsule side portion and the posterior capsule side portion. It is a member for intraocular lenses.

According to a second aspect of the present invention, in the invention according to the first aspect,
The curvature radius of the outer surface and the curvature radius of the inner surface are different from each other at least in a portion on the anterior capsule side in the central portion.

According to a third aspect of the present invention, in the invention according to the second aspect,
A curvature radius of the outer surface is larger than a curvature radius of the inner surface.

According to a fourth aspect of the present invention, in the invention according to any one of the first to third aspects,
The outer surface is shaped like a lens capsule.

According to a fifth aspect of the present invention, in the invention according to any one of the first to fourth aspects,
The elastic coefficient of the intraocular lens member is 2.0 KPa or more and 40.0 KPa or less.

According to a sixth aspect of the present invention, in the invention according to any one of the first to fifth aspects,
The intraocular lens member has a refractive index of 1.33 to 1.36.

According to a seventh aspect of the present invention, in the invention according to any one of the first to sixth aspects,
The thickness of the portion on the anterior capsule side of the intraocular lens member is 0.25 mm or more and 1.00 mm or less.

  According to an eighth aspect of the present invention, the hollow portion of the intraocular lens member according to any one of the first to seventh aspects is filled with a filling member having fluidity, so that the inner surface has an optical function. In addition, the intraocular lens is characterized by exhibiting an eye accommodation function as a whole.

According to a ninth aspect of the present invention, in the invention described in the eighth aspect,
The outer surface has a shape following the crystalline lens capsule, and the shape of the inner surface and the refractive index of the filling member can be set independently of the shape of the outer surface.

According to a tenth aspect of the present invention, in the invention according to the ninth aspect,
The refractive index of the intraocular lens member and the refractive index of the filling member are different from each other.

According to an eleventh aspect of the present invention, in the invention according to the tenth aspect,
When the elastic coefficient of the intraocular lens member is Ec and the elastic coefficient of the filling member is En, 0 <En / Ec <1.0 is satisfied.

  According to the present invention, it is possible to exert eye accommodation based on changes in the shape of the lens capsule due to tension and relaxation of the ciliary muscles or changes in the tension acting on the lens capsule, while achieving orthorhombicization and aberration correction. It is possible to provide an intraocular lens member and an intraocular lens that can achieve the above.

It is a cross-sectional schematic diagram (the 1) for demonstrating the usage method (mechanism) of the intraocular lens in this embodiment. (A) is a figure which shows a mode that the member for intraocular lenses was inserted in the crystalline lens capsule. (B) is a figure which shows a mode that a filling member is inject | poured into the hollow part of the member for intraocular lenses. (C) is a figure which shows the state (non-adjustment state) by which the intraocular lens is arrange | positioned in a crystalline lens capsule. It is a cross-sectional schematic diagram (2) for demonstrating the usage method (mechanism) of the intraocular lens in this embodiment. (A) is a figure which shows the state (non-adjustment state) by which the intraocular lens is arrange | positioned in a crystalline lens capsule. (B) is a figure which shows a mode that the adjustment | control power of eyes is working so that a lens wearer can be seen near. (C) is a figure which shows a mode that the adjustment | control power of eyes is working so that a lens wearer can see from a distance.

Hereinafter, embodiments of the present invention will be described in detail with reference to the drawings.
In the present embodiment, description will be given in the following order.
1. 1. Outline of intraocular lens member and intraocular lens 2. Intraocular lens member Intraocular lens 4. Intraocular lens member and method of using intraocular lens (mechanism)
5. Effects of the embodiment 6. Modifications etc.

<1. Overview of intraocular lens member 2 and intraocular lens 1>
First, the outline | summary of the member 2 for intraocular lenses and the intraocular lens 1 in this embodiment is described. In the description, FIG. 1 is used. FIG. 1 is a schematic cross-sectional view (No. 1) for explaining a method (mechanism) of using an intraocular lens 1 in the present embodiment. Fig.1 (a) is a figure which shows a mode that the member 2 for intraocular lenses was inserted in the lens capsule. FIG. 1B is a diagram illustrating a state where the filling member 4 is injected into the hollow portion 3 of the intraocular lens member 2. FIG.1 (c) is a figure which shows the state by which the intraocular lens 1 is arrange | positioned in the crystalline lens capsule.

  It is assumed that the intraocular lens 1 in this embodiment is attached after the lens is extracted by a cataract operation or the like of the eyeball. The intraocular lens 1 is formed by filling a hollow member 3 formed in the intraocular lens member 2 with a filling member 4 having fluidity.

  Hereinafter, the outermost surface of the intraocular lens member 2 is referred to as an “outer surface”, and the surface of the intraocular lens member 2 that forms the hollow portion 3 is referred to as an “inner surface”. Also, the front capsule side portion of the intraocular lens member 2 is the top side portion, and the rear capsule side portion of the intraocular lens member 2 is the top side portion.

  In the intraocular lens 1 of the present embodiment, the hollow member 3 formed in the intraocular lens member 2 is filled with a filling member 4 having fluidity. Certainly, the optical function is ensured also by the refractive index of the filling member 4, but the inner surface (that is, the interface between the intraocular lens member 2 and the filling member 4) exhibits the optical function. At the same time, the function of adjusting the eyes is exhibited as a whole.

  Hereinafter, the inside of the lens capsule is also simply referred to as “inside”. On the other hand, the outside of the lens capsule is also simply referred to as “outside”. Further, the direction of the outermost surface side of the human eye (that is, the side where the target object that the eye should see) exists is referred to as “front”. On the other hand, the direction toward the back of the human eye (that is, the fundus) is referred to as “rear”.

  Further, hereinafter, in addition to the normalization and aberration correction, the optical parameters necessary for the lens wearer are collectively referred to as “optical function”.

<2. Intraocular lens member 2>
The intraocular lens member 2 in this embodiment has the hollow part 3 as mentioned above, and is stored in a crystalline lens capsule. The intraocular lens member 2 can be deformable with the deformation of the lens capsule. The “hollow part 3” may be formed in a state where the intraocular lens member 2 is not in communication with the outside world (that is, in a completely hollow state), or a part thereof is in communication with the outside world. It may be formed as.
After all, when the lens capsule is deformed after the filling member 4 is filled in the hollow portion 3, the curvature of the inner surface of the hollow portion 3 varies according to the deformation of the lens capsule, so that the lens wearer can obtain a desired one. It is sufficient that the space capable of providing an optical function is formed as the hollow portion 3.

  The external shape (that is, the external shape) of the intraocular lens member 2 may be any shape as long as it can be accommodated in the crystalline lens capsule. However, as will be described later, the outer surface shape is preferably a shape that follows the shape of the lens capsule. Therefore, the outer surface shape of the intraocular lens member 2 is preferably a spherical shape or an ellipsoid. However, it may not be a perfect sphere or a perfect ellipsoid as in the case where the outer surface of the intraocular lens member 2 is partially uneven. Such exceptional cases are collectively referred to as “spherical or ellipsoid” in this specification.

In order to realize the above contents, the intraocular lens member 2 in the present embodiment has the following shape. That is, in the central portion when the intraocular lens member 2 is viewed in plan, at least one of the front capsule side portion (top and bottom side) and the back capsule side portion (top and bottom side), the curvature radius of the outer surface And the radius of curvature of the inner surface are different from each other.
As will be described later, the hollow portion 3 is filled with a filling member 4 that bears one end of the optical function. The boundary between the intraocular lens member 2 and the hollow portion 3 (that is, the inner surface of the intraocular lens member 2) is also responsible for one end of the optical function. Therefore, it is preferable that the inner surface of the intraocular lens member 2 in the central portion is also spherical or elliptical. However, the inner surface of the intraocular lens member 2 may have other shapes. For example, the edge surface (the line connecting the front surface and the rear surface) of the hollow portion 3 may be a straight line in a cross-sectional view.
That is, it is preferable that the intraocular lens member 2 and the hollow portion 3 have a spherical shape or a partial shape of an ellipsoid at least in the central portion when the intraocular lens member 2 is viewed in plan.

  The “central portion” refers to a portion in the vicinity of the approximate geometric center when the intraocular lens member 2 is viewed in plan. From another viewpoint, the “central portion” is the vicinity of the portion that passes through the optical axis when the intraocular lens member 2 is inserted into the crystalline lens capsule and the hollow portion 3 is filled with the filling member 4. Refers to the part. When the intraocular lens member 2 and the intraocular lens 1 are viewed in plan, a portion that may affect the normalization and aberration correction for the lens wearer is included in the central portion. . As a specific example, the “central portion” is the case after the intraocular lens member 2 is accommodated in the lens capsule (that is, the intraocular lens member 2 swells and comes into contact with the lens capsule). Assuming (after), it is a region having a radius of 2.5 mm from the portion passing through the optical axis.

  The above points are very different from the simple balloon system mentioned in the prior art. By differentiating the curvature radius of the outer surface and the curvature radius of the inner surface at the central portion, normalization and aberration correction are achieved in the design of the refractive index and the inner surface shape of the material used for the filling member. On the other hand, the outer surface shape can realize a shape that allows the force from the lens capsule to efficiently change the shape of the inner surface shape. The refractive power of the filling member 4 is determined by the shape of the boundary surface between the filling member 4 and the intraocular lens member 2 and the refractive index of the filling member 4 itself. Therefore, as described above, by making the curvature radius of the outer surface different from the curvature radius of the inner surface, the desired refractive power is exerted on the intraocular lens 1 (particularly, the filling member 4).

  Specifically, <4. The method of using the intraocular lens member 2 and the intraocular lens 1 (mechanism)> will be described, but when scratched, the interface between the intraocular lens member 2 and the filling member 4 (ie, the inner surface); The difference in the radius of curvature of the outer surface of the intraocular lens member 2 is utilized. Moreover, on the other hand, the intraocular lens member 2 can be freely deformed as the lens capsule is deformed. For this reason, the adjustment power that the lens wearer has can be recovered or changed to a normal state. This means that the outer surface and inner surface of the intraocular lens member 2 can be changed according to the deformation of the lens capsule. And the curvature radius of the outer surface and the curvature radius of the inner surface are designed differently in advance. As a result, the difference between the curvature radius of the outer surface and the curvature radius of the inner surface can be made variable by the eye's accommodation force. That is, the deformation mode of the outer surface and the deformation mode of the inner surface of the intraocular lens member 2 can be made inconsistent. As a result, the difference between the curvature radius of the outer surface and the curvature radius of the inner surface can be optimally varied while reducing the dependency on the filling amount of the filling member 4.

  In addition, the outer surface shape and inner surface shape of the intraocular lens member 2 and the setting of the curvature radius of the outer surface and the curvature radius of the inner surface of the intraocular lens member 2 in the central portion satisfy the above conditions, and the lens wearer It can be determined as appropriate depending on the shape of the capsule and the prescription of the lens wearer.

  For example, assuming the optimum far point for the lens wearer, the deformation of the lens capsule when the lens wearer looks at the far point is simulated. A simulation is also performed as to how the intraocular lens member 2 is deformed by the deformation of the lens capsule. If possible, the case where the hollow member 3 of the intraocular lens member 2 is filled with the filling member 4 is also simulated. And this simulation is performed also about the optimal near point for a lens wearer. In these simulations, an ideal inner surface shape that can achieve normalization and aberration correction when the optimum far point and near point are viewed is obtained. In addition, when the intraocular lens member 2 is actually used as the intraocular lens 1 and the lens wearer views the far point, the intraocular lens member 2 can be reproduced so that an ideal inner surface shape can be reproduced. Design the inner surface shape.

  Of course, the shape of the intraocular lens member 2 at the time of shipment may be different from the shape after the intraocular lens 1 is inserted into the lens capsule. In that case, the intraocular lens 2 is calculated by back-calculating from the ideal inner shape after being inserted into the lens capsule to become the intraocular lens 1, and taking into account the expansion of the intraocular lens member 2 due to the absorption of aqueous humor. The shape of the lens member 2 at the time of shipment is designed.

  In addition, although the shape at the time of shipment of the member 2 for intraocular lenses is different from the shape after it inserts in a crystalline lens capsule and becomes the intraocular lens 1, although it mentions later, the member 2 for intraocular lenses is a chamber. It is mentioned that it is a member swollen with water. At that time, if the curvature radius of the outer surface and the curvature radius of the inner surface are different from each other in the shape of the intraocular lens member 2 at the time of shipment, the curvature radii of the two naturally differ after swelling. In this specification, “the curvature radius of the outer surface and the curvature radius of the inner surface are different from each other” is, of course, a condition for the case where the intraocular lens member 2 is housed in the lens capsule. However, the above condition may be a condition for the case before the intraocular lens member 2 is housed in the crystalline lens capsule (when the intraocular lens member 2 is shipped).

  In addition, as a material for the intraocular lens member 2, when the intraocular lens 1 is finally formed, a material having an appropriate elasticity so as to follow the deformation of the capsular bag so as to exhibit an eye adjustment function. It is necessary to use it. This elasticity may be provided in the intraocular lens member 2 before insertion into the lens capsule, or may be provided using a body substance such as aqueous humor after insertion into the lens capsule. In other words, “can be deformable with the deformation of the lens capsule” means not only that it can be deformed before insertion into the lens capsule, but also after being inserted into the lens capsule, even if it is not deformable before insertion into the lens capsule. This includes the case where elasticity is provided by swelling or the like and the lens capsule becomes deformable as the lens capsule deforms.

In addition, the portion where the curvature radius of the outer surface and the curvature radius of the inner surface are different was defined as “at least one of the front capsule side portion and the rear capsule side portion”, but more preferably, at least the front capsule side portion in the central portion. , The curvature radius of the outer surface and the curvature radius of the inner surface are made different from each other. By doing so, it is possible to more effectively achieve normal vision and aberration correction by making the curvature radii different on the side closer to the object to which the line of sight is directed (that is, the front side).
In addition, it is more preferable that the radius of curvature of the outer surface and the radius of curvature of the inner surface are made different from each other also in the portion on the posterior capsule side. By doing so, it is possible to achieve more effective normalization and aberration correction on the side farther from the object to which the line of sight is directed (backward) in addition to the front.

  Of course, even in cases other than those described above, by appropriately selecting the shape and refractive index of the intraocular lens member 2, and further the refractive index of the filling member 4, etc., the normalization and aberration correction can be achieved effectively. It is possible.

  It is also preferable to make the curvature radius of the outer surface larger than the curvature radius of the inner surface in the central portion. Assuming a case where the filling member 4 filled in the hollow portion 3 is made of a material having a high refractive index, and the intraocular lens member 2 existing so as to cover it is made of a material having a lower refractive index than the filling member 4. If the curvature radius of the outer surface is made larger than the curvature radius of the inner surface, it is possible to effectively achieve normalization and aberration correction.

  Of course, even when the relationship between the curvature radius of the outer surface and the curvature radius of the inner surface and the refractive index relationship between the intraocular lens member 2 and the filling member 4 are reversed, the intraocular lens member 2 By appropriately selecting the shape, the refractive index, and the refractive index of the filling member 4, etc., it is also possible to achieve normalization and aberration correction while obtaining adjustment power. For example, the refractive power of the filling member 4 takes a positive value, but not only the refractive index of the filling member 4 is larger than the refractive index of the intraocular lens member 2, but also the reverse case. Therefore, the filling member 4 can take various shapes such as a convex lens, a concave lens, and a meniscus lens.

  In the central portion, it is preferable that the outer surface of the intraocular lens member 2 has a shape following the crystalline lens capsule. By doing so, when the intraocular lens 1 is obtained, the intraocular lens member 2 can easily follow the deformation of the crystalline lens capsule. In this case, the possibility that the lens capsule and the intraocular lens member 2 are separated (sliding between the two) is extremely reduced. As a result, the deformation of the lens capsule accompanying the exertion of the adjusting force when viewing the far point and the near point is successfully transmitted to the intraocular lens member 2, and a sufficient adjusting force can be obtained. Become.

  Moreover, it is preferable that the inner surface of the intraocular lens member 2 has an independent shape with respect to the outer surface of the intraocular lens member 2 (that is, a portion in contact with the lens capsule). The “independent shape” refers to a shape that is not generally similar to the outer surface shape of the intraocular lens member 2. Certainly, the inner surface shape and the outer surface shape may be similar to each other. However, the inner surface shape is appropriately determined according to the lens wearer's sac shape, the lens wearer's prescription, and the like. In addition, it is effective to make the outer surface shape and the inner surface shape greatly different in terms of normalization and aberration correction. Therefore, preferably, the inner surface of the intraocular lens member 2 has a shape independent of the outer surface.

  Moreover, it is preferable that some physical property parameters in the intraocular lens member 2 are in the following numerical ranges. Specific grounds for the numerical range will be described later in Examples, but their physical property parameters are listed below.

  The elastic coefficient of the intraocular lens member 2 is preferably 2.0 KPa or more and 40.0 KPa or less.

  In the capsular bag, the practically effective adjustment force is exerted while performing the same movement as the normal adjustment when the elastic coefficient of the intraocular lens member 2 is approximately 2.0 Kpa or more. On the other hand, the tension of the chin band necessary to obtain the adjustment force is about 90 mN in a simulation with a general eye of 45 years old, and a force that greatly exceeds this value may not be exhibited in the actual eye There is sex. Therefore, the elastic coefficient of the intraocular lens member 2 is preferably suppressed to a certain level. Considering the above, it is desirable that the elastic coefficient of the intraocular lens member 2 is approximately 2.0 Kpa or more and 40.0 Kpa or less.

  The intraocular lens member 2 preferably has a refractive index of 1.33 to 1.36. More specifically, it is preferable that the refractive index in e-line (mercury spectrum line of 546 nm wavelength) is 1.33 or more and 1.36 or less.

  When the refractive index of the intraocular lens member 2 is in the above range, the refractive index of the intraocular lens member 2 is substantially the same as the refractive index of the aqueous humor. As a result, the refractive power at the interface between the intraocular lens member 2 and the aqueous humor becomes substantially zero.

  Note that “substantially the same” regarding the refractive index and refractive power in this specification includes the case where the refractive index and refractive power are completely the same. On the other hand, when the lens wearer wears an intraocular lens, it indicates that a difference in refractive index and refractive power that does not hinder adjustment power, normalization, and aberration correction is allowed. The same applies to “substantially zero”.

  Since the intraocular lens member 2 is accommodated in the crystalline lens capsule, it is desirable that the shape of the outer surface of the intraocular lens member 2 is substantially matched with the original lens capsule shape of the lens wearer. “Substantially coincidence” also indicates that, when a lens wearer wears an intraocular lens, a difference in shape that does not hinder adjustment power, normalization, and aberration correction is allowed.

  Here, when the outer surface shape of the intraocular lens member 2 is substantially matched with the shape of the crystalline lens capsule, the intraocular lens member 2 and the aqueous humor have different refractive indexes. Refractive power is generated at the interface between 2 and aqueous humor. At this time, the shape of the boundary surface is determined only by substantially matching the shape of the lens capsule. For this reason, the refractive power generated at the boundary surface does not necessarily become a refractive power suitable for achieving normalization and aberration correction.

  On the other hand, when it is determined to have a refractive power suitable for normalizing the outer surface shape of the intraocular lens member 2, the separation between the inner surface shape of the lens capsule and the outer surface shape of the intraocular lens member 2 increases. There is a possibility that the change in the shape of the lens capsule accompanying the adjustment is not successfully transmitted to the intraocular lens 1. If this happens, there is a possibility that sufficient adjusting power cannot be obtained.

  Therefore, it is preferable that the refractive index of the intraocular lens member 2 and the refractive index of the aqueous humor are substantially the same. That is, even when the outer shapes of the lens capsule and the intraocular lens member 2 are substantially matched, the refractive power at the boundary surface between the intraocular lens member 2 and the aqueous humor is the outer surface shape of the intraocular lens member 2. Always make it almost zero without depending. By doing so, it is possible to set the refractive index of the intraocular lens member 2 within the above refractive index range after the outer surface shape of the intraocular lens member 2 is made to follow the inner surface shape of the crystalline lens capsule. In this way, it is possible to prevent a deviation in refractive power from the normal viewing state.

<3. Intraocular lens 1>
The intraocular lens 1 of this embodiment is formed by filling the hollow portion 3 of the intraocular lens member 2 with a filling member 4 having fluidity. The interface (ie, “inner surface”) between the intraocular lens member 2 and the filling member 4 exhibits an optical function. Of course, other entities (for example, the refractive index of the material of the filling member 4) may exhibit the optical function. At the same time, the intraocular lens 1 of the present embodiment exhibits an eye adjustment function as a whole.

  The filling member 4 of this embodiment has fluidity, and the filling member 4 is injected into the hollow portion 3 of the intraocular lens member 2 using a syringe or the like. By doing so, the filling member 4 can be injected into the hollow portion 3 after the intraocular lens member 2 is inserted into the crystalline lens capsule. Then, compared with the case where the filling member 4 is injected into the hollow portion 3 of the intraocular lens member 2 outside the eye and then inserted into the eye, the cross-sectional area at the time of insertion can be reduced. As a result, a necessary corneal incision and anterior lens capsule incision can be reduced. It is said that when the corneal incision or anterior lens capsule incision becomes large, the increase in induced astigmatism and the period of wound healing are prolonged, and this embodiment also has an advantage against this.

  On the other hand, even when the filling member 4 is injected into the hollow portion 3 of the intraocular lens member 2 outside the eye and then inserted into the eye, the filling member 4 portion has fluidity, so that the intraocular lens The whole 1 is easily deformed. Then, there is a possibility that the incision width can be reduced. Furthermore, when the filling member 4 is made a fluid object, an effect of increasing the refractive index change of the intraocular lens 1 accompanying the adjustment can be expected.

  In the case of the intraocular lens 1 of the present embodiment, as described above, the refractive power of the filling member 4 is such that the shape of the boundary surface between the filling member 4 and the intraocular lens member 2 and the filling member 4 itself. Determined by refractive index. However, these parameters can be set independently of the shape of the capsular bag. When the outer surface of the intraocular lens member 2 has a shape following the crystalline lens capsule, this means that “the shape of the boundary surface (that is, the inner surface) between the filling member 4 and the intraocular lens member 2” and “the filling member 4”. It means that the “refractive index of itself” can be set independently of the outer surface shape of the intraocular lens member 2. By doing so, not only the acquisition of the adjustment force but also the normalization and the aberration correction can be achieved more reliably regardless of the shape of the lens capsule of the lens wearer.

  It is preferable that the refractive index of the intraocular lens member 2 and the refractive index of the filling member 4 are different from each other.

  By adopting the above-described configuration, it is possible to cause the boundary surface between the intraocular lens member 2 and the filling member 4 to bear the refractive power that should be borne by the filling member 4 in order to achieve normal vision and aberration correction. It becomes. That is, it is possible to share the roles of adjusting the adjustment force to the intraocular lens member 2 (particularly the outer surface) and the optical function (normalization and aberration correction) to the filling member 4. As described above, the refractive power of the filling member 4 is determined by the shape of the boundary surface (shape of the inner surface) between the filling member 4 and the intraocular lens member 2 and the refractive index of the filling member 4 itself. With the configuration of the present embodiment, the above parameters can be set independently of the shape of the lens capsule (in this embodiment, the outer surface shape of the intraocular lens member 2). Therefore, normalization and aberration correction can be achieved regardless of the outer surface shape of the intraocular lens member 2.

  When the elastic coefficient of the intraocular lens member 2 is Ec and the elastic coefficient of the filling member 4 is En, it is preferable that 0 <En / Ec <1.0 is satisfied.

  As will be described in Examples (Tables 7 and 8), which will be described later, basically, the smaller the elastic coefficient of the filling member 4, the greater the adjustment force. That is, it is easier to obtain a large adjustment force when the elastic modulus of the filling member 4 is not too large. On the other hand, setting the elastic coefficient of the filling member 4 in consideration of the relationship with the elastic coefficient of the intraocular lens member 2 is preferable from the viewpoint of obtaining a large adjustment force. Assuming that the elastic coefficient of the filling member 4 is En and the elastic coefficient of the intraocular lens member 2 is Ec, in order to obtain a practically sufficient adjustment force, the equation 0 <En / Ec <1.0 is satisfied. Is preferred.

  The thickness of the portion of the intraocular lens member 2 on the anterior capsule side is preferably 0.25 mm or more and 1.00 mm or less.

  As will be described in Examples (Tables 9 and 10) to be described later, it is true that the filling member 4 in the capsular bag of the intraocular lens 1 is more likely to be affected by deformation and has a large adjustment force. Become. However, if the position of the filling member 4 is too close to the anterior capsule, the adjustment force is reduced due to the influence of CCC. CCC is a small opening (CCC: Continuous Curvular Capsular Hexis or Continuous Circular Capsule Hexis) that is formed in the anterior capsule during lens extraction surgery. The CCC is formed by incising the lens capsule in a circular shape with a dedicated instrument (chistotom, anterior capsule insulator, femtosecond laser). In normal cataract surgery, CCC is formed by incising the central part of the anterior capsule.

  In addition, as an example of the size of the CCC, an opening of the central portion of the anterior capsule with a diameter of 4.0 mm can be given. However, the diameter of the CCC is determined in consideration of the size of the intraocular lens 1 to be inserted into the lens capsule and the tip diameter of the ultrasonic emulsification and suction device that crushes and sucks the lens cortex and lens substance. Therefore, the diameter is not limited to 4.0 mm, and a larger or smaller diameter may be used. Further, the position of the CCC is not limited to the central portion, and may be formed in a portion other than the central portion.

  In addition, when the intraocular lens member 2 is relatively soft, the intraocular lens member 2 is easily affected by CCC. Therefore, the thickness of the intraocular lens member 2 on the anterior capsule side is preferably thick to some extent. On the other hand, if the intraocular lens member 2 is rigid, it is not affected by CCC, so the anterior capsule cortex thickness is preferably thin. Considering the above, it is desirable that the film thickness on the anterior capsule side of the intraocular lens member 2 is in the range of 0.25 mm or more and 1.00 mm or less.

  Furthermore, it is preferable that the intraocular lens member 2 has a configuration in which the filling member 4 can be injected after the intraocular lens member 2 is accommodated in the lens capsule. With this configuration, the work can be divided into insertion of the intraocular lens member 2 and injection of the filling member 4. As a result, compared with the case where the filling member 4 is injected into the hollow portion 3 minutes of the intraocular lens member 2 outside the eye and then inserted into the eye, the cross-sectional area during insertion can be reduced, Necessary corneal incision and anterior lens capsule incision can be reduced. An increase in corneal incision and anterior lens capsule incision is said to increase the induced astigmatism and prolong the period of wound healing, but this also has advantages.

Specifically, as described in the definition of “hollow part 3”, the intraocular lens member 2 is formed with a communication path for communicating the hollow part 3 with the outside world. Is mentioned. After the intraocular lens member 2 is housed in the lens capsule, the filling member 4 is injected through the communication path.
Moreover, as another structure, although a communicating path is not formed, you may elaborate the idea which becomes easy to inject | pour the filling member 4 with a syringe. For example, a method may be adopted in which a portion indicating the needle of the syringe is determined in advance with respect to the outer surface of the intraocular lens member 2, and the portion is formed thin in advance.

<4. Method of using intraocular lens member 2 and intraocular lens 1 (mechanism)>
Hereinafter, the usage method of the intraocular lens 1 in this embodiment is demonstrated centering on the mechanism. In the description, FIG. 1 is used.

  First, when inserting the intraocular lens 1 into the eye, a wound (circular opening, hereinafter also referred to as “opening”) is formed on the surface of the eye prior to the insertion, and the lens (the lens cortex, the lens substance) is formed through this opening. ).

  A known method may be used for extracting the cataractous lens from the lens capsule. For example, a small opening (CCC) of about 4 mm is formed in the anterior capsule of the lens capsule, and ultrasonic emulsification (PEA) is used.

  On the other hand, an intraocular lens member 2 is prepared in advance. And the filling member 4 is also prepared separately. The intraocular lens member 2 is a substance that has the property of being swellable by the body fluid of the lens wearer, and the shape after swelling is designed to be a shape that follows the sac shape. Furthermore, the curvature radius of the outer surface of the central part (anterior capsule side and posterior capsule side) of the intraocular lens member 2 is set to be larger than the curvature radius of the inner surface. And the curvature radius is set so that it may have the same relationship even after swelling.

  And this intraocular lens member 2 is arrange | positioned in an injector. The injector may be a known surgical instrument used to insert the intraocular lens 1 into the eye. In the present embodiment, the injector is used to insert the intraocular lens member 2 into the eye. And the front-end | tip part of the injector with which the member 2 for intraocular lenses was mounted | worn faces the opening of an eyeball, and the member 2 for intraocular lenses is pushed out from an injector in the state. By doing so, as shown in FIG. 1A, the intraocular lens member 2 is inserted into the eye (in the lens capsule) through the opening. Of course, an opening having a size larger than that described above may be formed, and the intraocular lens member 2 may be inserted into the lens capsule using a lever or the like. However, considering the increase in induced astigmatism and the period of wound healing, the above method using an injector is preferable.

  Thereafter, as shown in FIG. 1B, the filling member 4 is injected into the hollow portion 3 of the intraocular lens member 2. A known syringe may be used for this injection. With this configuration, the work can be divided into insertion of the intraocular lens member 2 and injection of the filling member 4. As a result, a necessary corneal incision and anterior lens capsule incision can be reduced. At that time, the filling member 4 is injected to such an extent that the hollow portion 3 is filled even after the intraocular lens member 2 swells.

  After insertion, body fluid (aqueous humor) enters the lens capsule. Then, as shown in FIG. 1C, the intraocular lens member 2 starts to swell. As a result of this swelling, first, the lens capsule comes into contact with the intraocular lens member 2. That is, the body fluid of the lens wearer is used as part of the configuration of the intraocular lens 1, and the intraocular lens member 2 is swollen with the body fluid. By doing so, the foreign body reaction in the body can be suppressed extremely effectively, and the burden on the body of the lens wearer can be reduced. At that time, the hollow portion 3 is set to be filled with the filling member 4 even after the intraocular lens member 2 is swollen.

  When the lens capsule comes into contact with the intraocular lens member 2, the intraocular lens member 2 may be treated so that no slip occurs between them. By doing so, the intraocular lens member 2 can faithfully follow the deformation of the capsular bag and can acquire a large adjustment force.

Hereinafter, the state in which the eye accommodation is exerted will be described with reference to FIG. FIG. 2 is a schematic cross-sectional view (No. 2) for explaining a method (mechanism) for using the intraocular lens 1 in the present embodiment. Fig.2 (a) is a figure which shows the state by which the intraocular lens 1 is arrange | positioned in the lens capsule. FIG. 2B is a diagram showing a state in which the eye adjustment force is working so that the lens wearer can view near. FIG.2 (c) is a figure which shows a mode that the adjustment | control power of eyes is working so that a lens wearer can view far.
As shown in FIGS. 2B to 2C, the intraocular lens member 2 can be deformed when the lens wearer tries to exert an eye adjustment force so that the user can see far or near. Therefore, it becomes possible to acquire adjustment power. More specifically, when the ciliary muscle contracts, the chin ligament relaxes, and the lens capsule deforms into a spherical shape as shown in FIGS. 2 (a) to 2 (b), the intraocular lens member 2 becomes It transforms into a shape suitable for seeing near points. On the other hand, when the ciliary muscle relaxes, the chin ligament contracts, and the lens capsule deforms flatly as shown in FIGS. Deforms to a shape suitable for In this embodiment, since the radius of curvature of the central portion of the intraocular lens member 2 is different between the inner surface and the outer surface, the intraocular lens 1 can exhibit a predetermined optical function even in both of these modifications. It becomes possible.

  Note that the opening formed in the lens capsule and the communication path communicating the hollow portion 3 of the intraocular lens member 2 and the outside may be closed by a known method after the operation. The intraocular lens member 2 may be used as a lid for the opening of the crystalline lens capsule. With this configuration, it is possible to efficiently close the opening of the lens capsule.

<5. Advantages of the embodiment>
According to the present embodiment, the effects described above are produced. The following summarizes the contents briefly.

  In the present embodiment, the intraocular lens member 2 that finally becomes a part of the intraocular lens 1 has a hollow structure having a hollow portion 3. When finally becoming the intraocular lens 1, the hollow member 3 is filled with a filling member 4 having fluidity. When the outermost surface of the intraocular lens member 2 is the outer surface and the surface of the intraocular lens member 2 that forms the hollow portion 3 is the inner surface, the ratio of the outer surface shape depending on the filling amount of the filling member 4 is It becomes possible to reduce as much as possible.

  The outer surface of the intraocular lens member 2 is designed to be able to exert an adjusting force with the deformation of the lens capsule. On the other hand, a filling member 4 is prepared which realizes normalization and aberration correction to some extent. The inner surface of the intraocular lens member 2 is designed so that the normalization and aberration correction, which are insufficient with the filling member 4, can be exerted by the deformation of the inner surface of the intraocular lens member 2.

  As described above, it is possible to achieve eyesight and aberration correction based on the ability to exert eye accommodation based on changes in the shape of the lens capsule or tension on the lens capsule caused by tension and relaxation of the ciliary muscle. It is possible to provide the intraocular lens member 2 and the intraocular lens 1 that can be used.

<6. Modified example>
In addition to the above-described embodiment, the intraocular lens member 2 preferably has the following configuration.
That is, the average value of the height of the hollow portion 3 when the central portion of the intraocular lens member 2 is viewed in plan view in the vertical direction is h, and the center of the central portion of the intraocular lens member 2 (light When the width (horizontal distance) from the axis) is _RL , when the intraocular lens member 2 is viewed in plan, the height of the hollow portion is 0.45 _RL away from the center of the center portion in the vertical direction ( It is preferably 0.56 h or more and 0.94 h or less in a direction parallel to the optical axis). Incidentally, R _L is, if the intraocular lens member 2 is spherical or ellipsoidal body, do not may be used R _L as the minimum value when viewed in plan, may be used R _L having a maximum value Or _RL which becomes an average value may be used. Moreover, h may not be an average value but a height along the optical axis of the hollow portion. 1 and 2 are schematic views, and the idea of the present invention is described even if the hollow portion described in FIGS. 1 and 2 is not included in the size defined above. There is no change.

  By having the above configuration, the hollow portion 3 occupies most of the volume in the central portion of the intraocular lens member 2, while the intraocular lens portion 2 other than the central portion (particularly the equator portion) It becomes possible to make the lens member 2 thick. Compared to the central portion of the intraocular lens member 2, the equator portion of the intraocular lens member 2 can be made thicker. Thus, by making the thickness of the central portion and the thickness of the equator portion unbalanced, the dependence on the injection amount of the filling member 4 is reduced, and the outer surface and the inner surface of the intraocular lens member 2 are reduced. It becomes possible to deform independently. That is, the deformation mode of the outer surface and the deformation mode of the inner surface of the intraocular lens member 2 can be made inconsistent. Such deformation enhances the effect realized in the above embodiment.

  Incidentally, the reason why the average value h of the height of the hollow portion 3 is used in the central portion is as follows. That is, when the height of the hollow part 3 is large at a small part in the central part (that is, when the thickness of the intraocular lens member 2 is small at a small part at the central part), or vice versa. In addition, when the hollow portion 3 is secured with a predetermined size as the entire central portion, the above-described effects are exhibited. In order to include the above contents in the present invention, the expression “average value h” is used.

  In addition, if it is said conditions, it will become possible to change the outer surface and inner surface of the member 2 for intraocular lenses more independently. If the above conditions are satisfied, when the hollow member 3 is filled with the filling member 4, the outer surface shape can be designed so that the force from the lens capsule can be efficiently changed to the shape change of the inner surface shape. It becomes. The normalization and aberration correction are achieved by designing the refractive index and inner surface shape of the material used for the filling member. Further, unlike the simple balloon-type intraocular lens 1, it is more certain that the dependency on the injection amount of the filling member 4 is reduced and the outer surface and the inner surface of the intraocular lens member 2 are independently deformed. Become.

By the way, the reason why “the place is 0.45 _RL away from the optical axis” is as follows. The standard value of the diameter (ie, the width of the equator) in the human lens capsule is 8.9 mm. On the other hand, the width of the CCC formed during surgery is usually 4 mm. And it assumes that the intraocular lens 1 in this embodiment is arrange | positioned directly under CCC. From the above, in order to give a desired refractive power to the lens wearer, at least 0.45 (= 4 mm / 8.9 mm) R _L from the optical axis with the optical axis as the center, the above-mentioned The inventor considered that it is preferable to set the height of the hollow portion.

  In the hollow portion 3, the front surface on the anterior capsule side and the rear surface on the posterior capsule side within the range satisfying the above conditions are also optically effective apertures. The effective optical aperture can also be defined as “the larger of the ranges in which the light rays contributing to imaging pass through the front surface or the rear surface of the hollow portion 3”.

  Next, an Example is shown and this invention is demonstrated concretely. Of course, the present invention is not limited to the following examples.

  In the present embodiment, the effectiveness of the intraocular lens 1 according to the present embodiment was examined using a numerical simulation using ABAQUS which is a finite element method simulation software.

First, in order to verify the effectiveness of the present example, it was verified how much adjustment power a general human eye has. At this time, 45-year-old data described in the following references were used as physical data of human eyes (Tables 1 to 4).
Reference: Burd, H .; J. et al. Judge, S .; J. et al. Cross, J .; A. , Numeric modeling of the accommodating len. , Vision Research 2002; 42 (18): 2235-2251.

  The refractive index of the lens cortex and the lens lens was 1.42, which is the same as the value shown in the same document. In addition, although the data of 11 years old, 29 years old, and 45 years old are described in the reference document, the “intraocular lens 1 having an adjustment power” which is the object of the present embodiment is in the 40s in which the adjustment power decreases. Since it is aimed at the later people and elderly people who are more likely to develop cataracts, we decided to use data at the age of 45 years close to that age.

  Tables 1 to 4 show eye data in an adjusted state. From this state, a simulation of pulling 0.3 mm in the direction perpendicular to the optical axis of the joint portion of three films imitating a chin band was performed. In the present embodiment, this case is set to a state where the adjusting force is not working (non-adjusted state) as shown in FIG. Conversely, in the state of FIG. 2B (ie, near vision looking at the near point) and in the state of FIG. 2C (ie far vision looking at the far point), the adjusting force is applied. The state (adjusted state).

  First, in a general human eye, a change in refractive power (adjustment power) caused by a change from an adjusted state to an unadjusted state was calculated. As described above, “adjusting power = refractive power in non-adjusted state (far vision) −refractive power in adjusted state (near vision)”. As a result, with respect to the initial refractive power (refractive power for near vision) of 27.8D, the adjustment force was -2.910D, and the tension required at that time was 90.284 mN.

  A simulation was performed on the intraocular lens 1 of the present example by the same method as described above, and the adjustment force was calculated.

  The radius of curvature of the intraocular lens member 2 is 6.0625 mm for the outer surface on the anterior capsule side and the inner surface on the anterior capsule side as shown in the table in the portion passing through the optical axis, whereas the outer surface on the posterior capsule side is -8.1 mm, the inner surface on the posterior capsule side was as shown in the table. In addition, in the intraocular lens member 2 in a present Example, it assumed that the shape before insertion to a crystalline lens capsule and the shape after insertion are the same.

Moreover, the average value of the height of the hollow part 3 when the central part when the intraocular lens member 2 was viewed in a cross-sectional view in the vertical direction was 3.8253 mm. In addition, the average value of the height of the hollow portion 3 when the central portion when the intraocular lens member 2 is viewed in plan is viewed in cross section in the vertical direction, and the center of the central portion of the intraocular lens member 2 (light Assuming that the width (horizontal distance) from (axis) is _RL , when the intraocular lens member 2 is viewed in plan, the height of the hollow portion is 0.45 _RL away from the optical axis in the vertical direction (optical axis). In a direction parallel to the horizontal axis) is 0.56 h or more and 0.94 h or less.

  Table 5 below assumes a case where the crystalline lens capsule and the intraocular lens member 2 are bonded. Conversely, Table 6 below assumes a state in which the crystalline lens capsule and the intraocular lens member 2 are not bonded. That is, it is assumed that there is no friction between the lens capsule and the intraocular lens member 2 and the intraocular lens member 2 slides relative to the lens capsule. Further, the arrow “←” in the following tables indicates that it is the same as the numerical value in the direction indicated by the arrow. For example, in Table 5, the refractive power (refractive power) D of Examples 2 to 6 is the same as the refractive power of Example 1.

  The thickness of the intraocular lens member 2 was based on the thickness of the portion passing through the optical axis. The thickness of the filling member 4 was also made the same.

  Here, Examples 1 to 6 are the results when the elastic coefficients of the intraocular lens member 2 are different. When the numerical value of the adjustment force is positive, the refraction change is opposite to that of normal adjustment. That is, when the lens capsule is pulled by the chin band, the refractive power is usually reduced, and the intraocular lens 1 becomes far vision and the value becomes negative.

  On the other hand, when the value is positive, the refractive power increases, indicating that the intraocular lens 1 is near vision. However, in the human eye, the normal adjustment movement is from the state of FIG. 2B (ie, near vision looking at the near point) to the state of FIG. 2C (ie far distance looking at the far point). It is a movement to shift to sight). This is because the state of FIG. 2 (b) is a state where the chin band is relaxed, and the chin band is contracted from there to shift to the state of FIG. 2 (c).

  In order to exhibit a practically effective adjustment force with the same movement as normal adjustment, it is preferable that the elastic coefficient of the intraocular lens member 2 is approximately 2.0 Kpa or more. In addition, the adjustment force increased as the elastic coefficient of the intraocular lens member 2 was further increased. Specifically, in Example 5 of Table 5, when the elastic coefficient of the intraocular lens member 2 was 16.0 Kpa, a very large adjustment force of about −14D was obtained.

  As shown in Table 5, when the crystalline lens capsule and the intraocular lens member 2 were not adhered, the adjusting force was slightly reduced. However, when the elastic coefficient of the intraocular lens member 2 is approximately 8.0 Kpa or more, an adjustment force equivalent to that when the crystalline lens capsule and the intraocular lens member 2 are bonded is generated. Furthermore, if the elastic coefficient of the intraocular lens member 2 is increased, a practically sufficient adjustment force can be obtained.

  In the case of Table 5, as compared with the case where the lens capsule and the intraocular lens member 2 are adhered as shown in Table 6, the resulting adjustment force is certainly smaller. However, when it is necessary to remove the intraocular lens 1 for some reason after the operation, there is an advantage that it is easier to remove the lens capsule and the intraocular lens member 2 without bonding them. Is also expected.

  Next, the result at the time of changing the elastic modulus of the filling member 4 is shown (Table 7, Table 8). Table 7 below assumes a case where the crystalline lens capsule and the intraocular lens member 2 are bonded. Conversely, Table 8 below assumes a state where the lens capsule and the intraocular lens member 2 are not bonded.

  From the viewpoint of obtaining accommodation force with reference to Tables 7 and 8, assuming that the elastic coefficient of the intraocular lens member 2 is Ec and the elastic coefficient of the filling member 4 is En, 0 <En / Ec < It is desirable to satisfy 1.0.

  On the other hand, the tension of the chin band necessary to obtain the adjustment force is about 90 mN in a 45-year-old general eye simulation. However, a force that greatly exceeds this value may not be exerted by the actual eye. Therefore, it is not always preferable to increase the elastic coefficient of the intraocular lens member 2 to a dark cloud. From the viewpoint of obtaining adjustment force with reference to Tables 5 to 8, the elastic coefficient of the intraocular lens member 2 is desirably 2.0 KPa or more and 40.0 KPa or less.

  Next, the results when the thickness of the intraocular lens member 2 on the anterior capsule side of the intraocular lens member 2 is changed are shown (Tables 9 and 10). In Tables 9 and 10, the elastic coefficient of the intraocular lens member 2 is different.

  From the viewpoint of obtaining adjustment force with reference to Tables 9 and 10, the anterior capsule side film thickness of the intraocular lens member 2 is preferably in the range of 0.25 mm to 1.00 mm, It is more desirable to be in the range of 0.29 mm or more and 0.89 mm or less.

  Although the optical surface of the filling member 4 in this embodiment is formed as a rotationally symmetric surface with respect to the optical axis, it can also be a surface that corrects astigmatism by making it a toric surface. In addition, the refractive power can be corrected after the operation by increasing or decreasing the injection amount (filling amount) of the filling member 4 after the operation or by reinjecting the filling member 4 having a different refractive index.

DESCRIPTION OF SYMBOLS 1 Intraocular lens 2 Intraocular lens member 3 Hollow part 4 Filling member

Claims (11)

A member for an intraocular lens that is housed in a capsular bag and can be deformed along with the deformation of the capsular bag,
The intraocular lens member has a hollow portion,
When the outermost surface of the intraocular lens member is an outer surface, and the surface forming the hollow portion in the intraocular lens member is an inner surface,
In the central portion of the intraocular lens member in plan view, the curvature radius of the outer surface and the curvature radius of the inner surface are different from each other in at least one of the anterior capsule side portion and the posterior capsule side portion. An intraocular lens member.   2. The intraocular lens member according to claim 1, wherein the curvature radius of the outer surface and the curvature radius of the inner surface are different from each other at least in a portion of the central portion on the anterior capsule side.   The intraocular lens member according to claim 2, wherein a curvature radius of the outer surface is larger than a curvature radius of the inner surface.   The intraocular lens member according to any one of claims 1 to 3, wherein the outer surface has a shape imitating a lens capsule.   5. The intraocular lens member according to claim 1, wherein an elastic coefficient of the intraocular lens member is 2.0 KPa or more and 40.0 KPa or less.   6. The intraocular lens member according to claim 1, wherein the intraocular lens member has a refractive index of 1.33 or more and 1.36 or less.   The intraocular lens member according to any one of claims 1 to 6, wherein a thickness of a portion on the anterior capsule side of the intraocular lens member is 0.25 mm or more and 1.00 mm or less.   The hollow portion of the intraocular lens member according to any one of claims 1 to 7 is filled with a fluid-filling member so that the inner surface exhibits an optical function and the eye adjustment function as a whole. Intraocular lens characterized by exhibiting   9. The eye according to claim 8, wherein the outer surface has a shape following the lens capsule, and the shape of the inner surface and the refractive index of the filling member can be set independently of the shape of the outer surface. Inner lens.   The intraocular lens according to claim 9, wherein a refractive index of the intraocular lens member and a refractive index of the filling member are different from each other.   The intraocular lens according to claim 10, wherein 0 <En / Ec <1.0 is satisfied, where Ec is an elastic coefficient of the intraocular lens member and En is an elastic coefficient of the filling member.

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