KR101718074B1 - Intraocular lens supporter - Google Patents

Abstract

The present invention discloses an intraocular lens support capable of effectively transmitting the motion of the epilator to improve the performance of the intraocular lens.
The present invention relates to an intraocular lens support (10) having a ring shape inserted into a capsule color and accommodating an intraocular lens (30) therein, wherein an outer peripheral surface (11) of the intraocular lens support (10) And is protruded toward one side with respect to an equatorial line which is an end protruding from the equatorial line and protrudes convexly toward the other side on the basis of the equatorial line with at least part of the arc form, And an outer rear surface portion 11b having an arcuate shape and a portion of the outer front surface portion 11a and the outer rear surface portion 11b is provided with a composite motion transmitting surface 20 is provided to improve the motion transmission capability of the intraocular lens support.

Description

[0001] INTRAOCULAR LENS SUPPORTER [0002]

BACKGROUND OF THE INVENTION 1. Field of the Invention The present invention relates to an intraocular lens support, and more particularly, to an intraocular lens support which improves a cross-sectional structure of an intraocular lens support to improve shrinkage and swelling of an intraocular lens.

In the case of ophthalmologic diseases such as cataracts, it is a treatment method for removing the contents of a lens inside a capsular sac, and an artificial intraocular lens ) Are now widely practiced.

When an intraocular lens is inserted, the intraocular lens can replace the natural lens to provide the patient with a haze-free field of view. However, despite the advantages of intraocular lenses, there is a problem that the capsular sac with the intraocular lens inserted after the insertion of the intraocular lens contracts after surgery.

Therefore, recently, a method of inserting an encapsulant ring into an equatorial region of a capsular sac and fixing an intraocular lens to the encapsulant ring has been gradually used before insertion of an intraocular lens.

The encapsulant ring is an open or closed annular shape, and a method of partially alleviating the shrinkage of the capsular sac and fixing the lens lens is increasingly being used.

In order to use the capsule ring tension ring more efficiently, studies on the structure for facilitating the insertion of the encapsulant ring and the structure for preventing posterior capsule opacity are underway.

However, the problem with conventional intraocular lens implantation is that the capsular sac of the anterior capsule and the posterior capsule attach to each other, which causes the relaxation and contraction of the Zonule of Zinn to be transmitted, The function will be lost. That is, the patient's eyes after surgery do not secure the field of view by actively performing three-dimensional motion according to the object to be viewed, but have a problem that passive vision is secured according to the frequency determined in the intraocular lens. These problems will be described with reference to the drawings shown in Figs. 1A to 4.

FIG. 1 is a cross-sectional view of a human eye, and FIG. 2 is a cross-sectional view illustrating the structure of a natural lens. The cornea 1 protects the eyeball with the transparent vein tissue at the outermost side of the eye. The cornea is also responsible for the refraction of the light along with the lens, Adjusts the amount of light that enters the eyes and serves as the diaphragm of the camera. The pupil (3) is a hole in the center of the iris (2). The pupil (3) is reduced in size under a bright light and enlarged in a dark place to control the amount of light entering the retina (4).

The lens 5 is a colorless transparent structure having no convex lens shape on both sides and is located behind the iris 2. The shape of the lens 5 changes depending on the contraction and relaxation of the corpuscular muscle 6 and the strap 7 connected thereto.

As the age of the lens increases, the hardness of the lens 5 increases year by year and the shape of the lens 5 does not change even if the ciliary body 6 contracts. In the cataract, It is a disease that becomes turbid according to entering.

The lens body 5 is filled in a capsular sac 8 and the capsular sac 8 is composed of an anterior capsule 8a and a posterior capsule 8b, The front face 5a and the rear face 5b of the lens body 5 are connected to each other at the equator E and the front face 5a and the rear face 5b are connected to each other at a distance the central portion a of the front surface 5a is smaller in curvature than the central portion a of the rear surface 5b and the equatorial portion b of the front surface 5a is smaller than the central portion a of the rear surface 5b. Has a larger curvature than the equatorial portion (b) of the rear surface (5).

The strap 7 is connected along the edge of the encapsulant 8. The strap 7 is a kind of fiber structure that connects the cervical roots 6 and the capsule shell 8 and has a first platelets 8 connected to the vicinity of the equator where the front and back caps 8a, And a second platoon 7b connected to the vicinity of the periphery of the equatorial portion.

Figs. 3 and 4 are explanatory views explaining the action of the phantom, the lens, and the capsule color when looking at the distance and the nearness, respectively. In this specification, the Y-axis direction is the axial direction of the lens, and the X-axis direction is the equatorial direction of the lens. The axial direction of the crystalline body 5 is a direction in which light enters the lens body 5 through the pupil and the equatorial direction is a direction connecting the front and rear caps of the lens in a direction perpendicular to the axial direction.

The first platoon 7a connected to the center of the equatorial portion of the encapsulant 8 is strained and the second platoon 8 connected to the periphery of the equatorial portion of the encapsulant 8 7b are loosened. As a result, the capsule color 8 is stretched in the X direction of the lens body 5, and the lens body 5 located inside is also stretched in the same direction.

The first platoon 7a connected to the center of the equatorial portion of the encapsulant 8 is loosened and the second platoon 7b connected to the periphery of the equatorial portion of the encapsulant 8, Is tightened. This causes the capsule lens 8 to be convex in the Y-axis direction of the dl lens 5, so that the lens 5 located therein also extends in the same direction. As described above, the capsule lens 8 having the natural lens therein is actively connected to the lens 7 to change the shape of the natural lens. However, when the intraocular lens and the encapsulant tension ring of the conventional structure are used , The capsule color 8 is contracted and its function is substantially lost.

It is necessary to improve the conventional method of artificially extinguishing the amygdala 6, which is connected to the phantom 7 and is involved in the shape change of the phantom 5, as a built-in muscle that does not become tired until the moment of death.

In addition, when an intraocular lens is used, it is necessary to improve the structure of the intraocular lens support in order to enhance the ability of the intraocular lens to transmit the force generated by the motion of the supporting member 7 to the intraocular lens Do.

Korean Patent No. 10-0843454 (Intraocular lens support, 2008.06.26.)

It is an object of the present invention to provide an intraocular lens support having improved motion transmission capability for transmitting a force applied by a snare to an intraocular lens.

It is another object of the present invention to provide an intraocular lens support capable of enhancing the function of an intraocular lens by allowing motion of the epicenter to be efficiently transmitted to the intraocular lens.

In order to achieve the above-mentioned object, an intraocular lens support has a ring shape inserted into a capsule color and accommodates an intraocular lens therein, wherein an outer circumferential surface of the intraocular lens support protrudes convexly And at least a part of which is convexly protruded toward one side with respect to an equatorial line on the other side of the equatorial line and protruding convexly toward the other side with reference to the equatorial line, And a rear part of the outer front part is provided with a complex motion transmitting surface which is recessed toward the center part so that the motion transmitting ability can be improved.

More preferably, the complex motion transmitting surface forms a straight section at the time of front projection.

More preferably, the composite motion transmitting surface forms a arc-shaped cross section at the time of front projection.

Still more preferably, in a state in which the intraocular lens support is mounted on the capsule color, the complex motion transmitting surface is located in the vicinity of the second platoon constituting the epilator.

In addition, more preferably, the complex motion transfer surface formed on the outer front portion is located in a section of 0.9 mm to 1.5 mm length in the equator.

Further, more preferably, the complex motion transfer surface formed on the outer rear portion is located in a section of 1.2 to 1.9 mm in length in the equator.

More preferably, the inner circumferential surface of the intra-ocular lens support has a sectional shape depressed toward the equatorial portion, and the inner circumferential surface extends from the equatorial portion toward the distal end of the outer front portion so that at least a part of the inner circumferential surface forms an arc An inner front portion; And an inner rear surface portion extending from the equatorial portion toward an end of the outer rear surface portion so as to form an arcuate shape at least in a section thereof.

More preferably, the arcs of the outer front portion, the outer rear portion, the inner front portion, and the inner rear portion form a section of the ellipse, wherein the short axis of each ellipse constituting each arc has an outer front portion, And the inner front surface portion is formed shorter than the inner rear surface portion.

More preferably, the short axis of each ellipse constituting each arc has the longest inner rear face portion and the shortest outer front face portion.

In addition, more preferably, a part of the outer rear portion further includes a complex motion transmitting surface that is recessed toward the center portion so that the motion transmitting ability can be improved.

As described above, the intraocular lens support according to the present invention has the effect of improving the ability of the intraocular lens by smoothly transmitting complex motion caused by the force generated from the soma muscle and transmitted through the epicardium and the capsule color to the intraocular lens.

In addition, the intraocular lens support according to the present invention can be applied to intraocular lens insertion surgery for treating cataract, presbyopia, and high myopia, and at the same time, a substitute effect of LASIK or ICL (Implantable Contact Lens) surgery is expected.

In addition, the intra-ocular lens support according to the present invention has a complex motion transferring surface that is recessed in the outer circumferential surface of the intra-ocular lens support, thereby enabling a compound motion such as twisting including motion in X, Y, And the function of the intraocular lens can be improved.

1 is a cross-sectional view showing a human eyeball,
2 is a cross-sectional view illustrating the structure of a natural lens,
FIG. 3 is a state diagram showing the interaction and the motion state of the lens when viewed from a distance,
Fig. 4 is a state diagram showing the interaction and the state of motion of the lens when observing near,
FIG. 5 is a perspective view illustrating an intraocular lens assembly equipped with an intraocular lens support, which is a preferred embodiment of the present invention. FIG.
Figure 6 is a plan view of the intraocular lens assembly shown in Figure 5;
FIG. 7 is a cross-sectional view of the intra-ocular lens support shown in FIG. 5,
FIG. 8 is a cross-sectional view of the intra-ocular lens support shown in FIG. 5,
FIG. 9 is a view showing the interaction and movement state of the lens, the lens, and the intraocular lens assembly when looking at a distance from a state where the intraocular lens assembly is mounted, which is a preferred embodiment of the present invention.
FIG. 10 is a state diagram showing the interaction and movement of the lens, the lens, and the intraocular lens assembly when the eye lens is viewed in a state where the intra-ocular lens assembly is mounted, which is a preferred embodiment of the present invention.
11 is a cross-sectional view of an intraocular lens support, which is another embodiment of the present invention.

Hereinafter, an intraocular lens support, which is a preferred embodiment of the present invention, will be described in more detail with reference to the accompanying drawings. The same reference numerals are given to the same parts as those in the conventional structure, and a detailed description thereof will be given with reference to Figs. 1 to 4. Fig.

Here, the shape, size, ratio, angle, number and the like shown in the accompanying drawings are schematic and may be modified somewhat. 2) Since the drawing is shown by the line of sight of the observer, the direction or position to explain the drawing can be variously changed according to the position of the observer. 3) The same reference numerals can be used for the same parts even if the drawing numbers are different. 4) If 'include', 'have', 'have', etc. are used, other parts can be added unless '~ only' is used. 5) Numerals can also be interpreted as described in the singular. 6) Even if the shape, size comparison, positional relationship, etc. are not described as 'weak or substantial', it is interpreted to include the normal error range. 7) 'after', 'before', 'after', 'after', and 'after' are not used to limit the temporal position. 8) The terms 'first, second, third', etc. are used selectively, interchangeably or repeatedly for convenience of division, and are not construed in a limiting sense. 9) If the positional relationship of the two parts is described as 'on top of', 'on top', 'on bottom', 'on side', 'on side' and so on, This can also be located. 10) When parts are electrically connected to '~ or', parts are interpreted to include not only singles but also combinations, but parts are interpreted solely if they are electrically connected to '~ or'.

FIG. 5 is a perspective view showing an intraocular lens assembly equipped with an intraocular lens support, which is a preferred embodiment of the present invention, FIG. 6 is a plan view showing the intraocular lens assembly shown in FIG. 5, FIG. 8 is a cross-sectional view illustrating a state in which an intra-ocular lens support shown in FIG. 5 is assembled, and FIG. 9 is a cross-sectional view illustrating an intraocular lens assembly, which is a preferred embodiment of the present invention. FIG. 10 is a view illustrating a state in which an eyeball lens assembly, which is a preferred embodiment of the present invention, is mounted, FIG. 11 is a cross-sectional view showing an intraocular lens support, which is another embodiment of the present invention, and FIG. 11 is a cross- .

5 to 8, an intraocular lens assembly equipped with an intraocular lens support 10, which is a preferred embodiment of the present invention, includes an intraocular lens 30, an eyeball 30 surrounding the intraocular lens 30, An inner lens support 10 and a connecting means 50 for fixing the intraocular lens 30 to the intraocular lens support 10. The connecting means 50 consists of a structure which receives the intraocular lens 30 therein and is inserted and fixed inside the intraocular lens support 10.

The intraocular lens support 10 is formed into a ring shape to be inserted into the capsule color. It is preferable that it is formed into a closed ring shape, but it may be formed into a ring shape with one side opened.

The inner lens support 10 may have a material different from that of the outer circumference 11 and the inner circumference 12 so that the shape deforming ability of the lens support 10 due to the motion of the lens can be increased.

It is preferable that the entire length of the outer circumferential surface 11 is formed to be longer than the entire length of the inner circumferential surface 12 and the thickness of the equatorial portion E is formed to be the thickest and the thickness becomes gradually thinner toward both ends.

The diameter of the intraocular lens support 10 is approximately equal to the inner diameter of the capsule color 8. The diameter of the capsule color 8 varies depending on the person. Usually the diameter is 9mm to 13mm. The equatorial diameter of the intraocular lens support 10 is preferably equal to the inner diameter of the equatorial portion of the patient lens.

The material of the intraocular lens support 10 may be selected from the group consisting of silicone, silicone elastomer, silicone polymer, polydimethyl siloxane, polypropylene, polyimide, poly Polybutester, PMMA (polymethyl methacrylate), PMMA (Microplex PMMA), CQ-UV PMMA, Acrylic, Rigid acrylic, Flexible acrylic, Acrylate plastic ), Hydrophobic acrylic, hydrophilic acrylic, hydrophilic acrylic polymer, UV absorbing acrylate, methacrylate copolymer, butyl acrylate ( Butyl acrylate, polysiloxane elastomer, UV absorbing polysiloxane, collagen copolymer, gold d), Hydrogel, HEMA (2-hydroxyethyl methacrylate), MMA (methyl methacrylate), CAB (cellulose acetate butylate), 2-HAMA (2-hydroxy ethyl methacrylate), NVP (polyvinyl pyrrolidone), MA (methacrylic acid), GMA (glycerol methacrylate), DMS (dimethyl siloxane), PHEMA (polyhydroxyethyl methacrylate), PEGMMA (polyethylenehlycol methacrylate), poly HEMA hydrogel, PVA / MA, HEMA / PVA / MMA, HEMA / MMA, HEMA / NVP, HEMA / PVP / Any one or more of HEMA / NVP / MA, HEMA / NVP / MMA, HEMA / Acryl, and HEMA / PC may be used.

7, the outer circumferential surface 11 is a surface tangent to at least one point on the inner surface of the encapsulant 8, and the outer circumferential surface 11 has a convexly protruding end, And an outer rear portion 11b protruding in a convex direction toward the other side and having at least a part of an arc shape. The front surface portion 11a has a curvature larger than that of the outer rear surface portion 11b in the cross section cut at the front projection in the lens axial direction (Y direction). This is because the cross section of the outer peripheral surface 11 cut in the front projection is formed to be the same as that of the equatorial section of the natural lens. As described above, the front surface of the central portion of the lens has a smaller curvature than the rear surface, And the curvature changes.

More preferably, the outer peripheral surface 11 is formed in the same shape as the cross-sectional shape of the lens of the procedure patient. The cross-sectional shape of the lens of the patient before surgery can be photographed by ultrasound imaging, CT and MRI, and the cross-sectional shape of the outer surface 11 is a cross-sectional shape in which the pupil becomes larger and smaller, And may have a shape conforming to the shape. Therefore, the outer circumferential surface 11 coincides with the inner surface and the shape of the equatorial portion of the capsule light 8.

7, the outer circumferential surface 11 in the section cut at the front projection has a length of 3/4 of the length between the front side second platoon 7b and the rear side second platoon 7b on the outer surface of the capsule color 8, To 3 times as long as the length of the guide rail. When the distance between the second platoon 7b and the second platoon 7b is less than 3/4 of the distance between the second platoon 7b and the second platoon 7b, The optic part of the intraocular lens 30 is covered. When constructed at such a magnification, the outer circumferential surface 11 has a total length of 2 mm to 8 mm.

An extension length d1 from the equator E to the end point of the outer front portion 11a and an extension length d1 from the equatorial portion E to the end point of the outer rear portion 11b in the section cut at the front projection as shown in Fig. (d2) may generally be from 1 mm to 4.2 mm. If it is more than 4.2 mm, there is a problem that insertion is difficult during surgery and the optic part becomes too small. In case of less than 1 mm, the intra-ocular lens support is provided inside the point where the second platoon 7b of the eardrum is connected to the capsule color 8, 30, and the movement and deformation of the intraocular lens 30 may not be sufficiently performed.

The extension length d1 and the extension length d2 in the equator E may be the same or different. Preferably, the extension length d2 is longer than the extension length d1.

The outer circumferential surface 11 has a shape in which a cross section of the outer circumferential surface 11 is convexly protruded in a radial direction. The surface roughness of the lens support 10 in the eyeball may be made higher than that of the other surface so that the capsule lens 8 can be stably mounted on the capsule lens 8, or a separate mounting material may be used. Tissue glue or glue is used as the mounting material.

The inner circumferential surface 12 has a sectional shape depressed toward the equatorial portion. The inner circumferential surface 12 has an inner front surface portion 12a extending from the equatorial portion E toward an end of the outer front surface portion 11a so as to form at least part of an arc shape and an inner front surface portion 12b extending from the equatorial portion E to the outer rear surface portion 11b And an inner rear surface portion 12b extending toward the end so as to form at least part of the arc shape. The inner circumferential surface 12 is a surface to which the connecting means 50 is coupled.

The total extension length d4 of the inner peripheral surface 12 is formed to be smaller than or equal to the total extension length d3 of the outer peripheral surface. The extension length d4 is formed to be smaller than or equal to the extension length d3 in order to amplify or maintain the force applied to the outer peripheral surface 11 from the edge to the inner peripheral surface 12. [

When the extension length d4 is made smaller than the extension length d3, more movement and deformation are induced as the outer peripheral surface 11 moves. F2 = k * F1, k? 1 ', which is transmitted to the inner circumferential surface 12, when the force F1 is applied to the outer peripheral surface 11 from the edge. Where k is a constant determined by the length ratio of the extension length d3 to the extension length d4. The ratio of the lengths of d3 and d4 may vary depending on the patient's abilities, and the length of d4 is preferably 0.4 to 1 times the length of d3.

The arcs of the outer front portion 11a, the outer rear portion 11b and the inner front portion 12a and the inner rear portion 12b to be described later may be formed as a part of the ellipse.

In this case, when the respective ellipses are positioned on the same central axis, when the magnification is adjusted so that the vertexes in the long direction are located at the same position, the short axis of each ellipse constituting each arc is shorter than the outer front portion 11 Ib, The inner front portion 12a is formed to be shorter than the inner rear portion 12b. Of the short axes of the respective ovals constituting each arc, the short axis of the ellipse constituting the inner rear face portion 12b is the longest, and the short axis constituting the outer front portion 11a is formed to be the shortest.

As shown in FIGS. 7 and 8, a complex motion transfer surface 20 is provided on the outer peripheral surface 11 of the intra-ocular lens support 10. The complex motion transmitting surface 20 is formed in a part of the outer front portion 11a and the outer rear portion 11b so as to transmit the motion of the epilator (in particular, the motion of the second platoon) It forms a depression toward the center so that the ability can be improved. It is preferable that the composite motion transmitting surface 20 forms a cross section of arc shape in front projection. The intraocular lens support 10, which is another embodiment of the present invention, may be configured to have a straight cross section in the front projection as shown in FIG. In addition, it is preferable that the complex motion transmitting surface 20 forming the arc shape or the rectilinear cross-sectional shape is located in the vicinity of the second platoon 7b which forms the epicenter. However, the position of the complex motion transmitting surface 20 is not limited to the vicinity of the second platoon 7b but may be formed at any position between the first platoon 7a and the second platoon 7b. In this state, It is preferable that the second platoon 7b is partially overlapped with the second platoon 7b. The intra-ocular lens support 10 in which the complex motion transfer surface 20 is formed may be formed in such a structure that the cross section of the complex motion transfer surface 20 is gradually reduced toward the end as the depression is formed.

It is preferable that the complex motion transmitting surface 20 formed on the outer front portion 11a is located at a position of 0.9 mm to 1.5 mm from the equatorial point E. [ That is, the distance from the equator E to the starting point 21 of the complex motion transmitting surface 20 is 0.9 mm and the distance from the equator E to the end point 22 of the complex motion transmitting surface 20 is 1.5 mm .

It is preferable that the complex motion transmitting surface 20 formed on the outer rear surface portion 11b is located at a position 1.2 mm to 1.9 mm from the equatorial point E. That is, the distance from the equator E to the starting point 23 of the complex motion transfer surface 20 is 1.2 mm and the distance from the equator E to the end point 24 of the complex motion transfer surface 20 is 1.9 mm .

The composite motion transmitting surface 20 is configured to have a shape that is partially recessed from the outer circumferential surface having a generally convex shape so that no force is applied to only one of the X axis and Y axis and the X axis, So that the motion of the epilating complex acting in the triaxial direction can be efficiently transmitted to the connecting means 50 and the intraocular lens 30. [ The intraocular lens 30 can move or change the volume more precisely through the complex motion transfer surface 20. That is, a force for transmitting a complex movement such as a subtle movement or twist due to the movement of the epilator is effectively transmitted to the connecting means 50 and the intraocular lens 30 through the complex motion transmitting surface 20. Further, the complex motion transmitting surface 20 can be deformed more smoothly by the motion of the epicenter, due to the structural feature that the formed point of the complex motion transmitting surface 20 is formed to have a thickness greater than the peripheral portion, And also transmits force or deformation to the connecting means 50 and the intraocular lens 30 more easily.

5, 6 and 8, the intraocular lens 30 is fixed to the intra-ocular lens support 10 through the connecting means 50. As shown in Figs. The haptic portion of the intraocular lens 30 is fixed to the groove formed on the inner circumferential surface of the connecting means 50 while keeping the inner circumferential surface 12 of the intraocular lens support 10 and the connecting means 50 in contact with each other. The intraocular lens 30 is located in the ring-shaped interior of the connecting means 50 and the connecting means 50 is located in the ring-shaped interior of the intraocular lens support 10.

The intraocular lens 30 is composed of an optic part positioned at the rear of the pupil and a haptic part protruding radially from the optic part and fixed to the inner circumferential surface of the connecting means 50. [ The intraocular lens 30 can be manufactured in various shapes and is not limited to a specific shape. The haptic part has a plurality of branch shapes radially protruding from the circumference of the optic part. Preferably three at intervals of 120 [deg.]. In addition, the tips of the haptic units may be additionally configured to be connected to each other in a ring shape. When a ring-shaped support rod connecting the ends of the haptic portion is formed, the force transmitting the motion of the skin can be more effectively transmitted to the intraocular lens through the support and the haptic portion.

The process of operating the intraocular lens support, which is a preferred embodiment of the present invention, is as follows.

9, the first platoon 7a of the capsule color 8 becomes taut and the second platoon 7b becomes loose when looking at the distance. As a result, the equatorial portion of the capsule color 8 is subjected to a force that stretches in the X direction, and the elastic intraocular lens 30 located in the interior of the capsule color 8 also extends in the same direction, Lt; / RTI > At this time, the force exerted by the strap 7 does not merely act in one direction of the X-axis, but substantially forms a combined movement of vectors in the directions of the triaxial directions of X, Y and Z, To the connecting means 50 and the intraocular lens 30 more efficiently through the eye. At this time, the role of the complex motion transmitting surface 20 is as described above.

10, the first platoon 7a of the capsule color 8 is loosened and the second platoon 7b is strained. As a result, the equatorial portion of the capsule color 8 is subjected to a force stretching in the Y direction, and the elastic intraocular lens 30 located inside the capsule color 8 is stretched in the same direction and becomes thick, Lt; / RTI > At this time, the force exerted by the shin (7) does not merely act in one direction of the Y axis, but actually forms a combined movement of the vectors of the three directions of X, Y and Z, Is transmitted to the connecting means (50) and the intraocular lens (30) more efficiently through the complex motion transmitting surface (20).

In the case of forming the complex motion transfer surface 20 in the intra-ocular lens support 10 according to the present invention, the fine motion of the fingertips or the complex motion simultaneously acting in the three axial directions can be more effectively performed by the connecting means 50 and the eyeball The lens 30 can be adjusted in its thickness and position as in the case of an intraocular lens 30. In other words, as the thickness of the natural lens is closely controlled by the action of the capsule connected to the epiglottis, the intraocular lens using the intraocular lens support according to the present invention can also be changed in thickness, As shown in Fig.

It will be understood by those skilled in the art that various changes in form and details may be made therein without departing from the spirit and scope of the invention as defined in the appended claims and their equivalents. Of course, such modifications are within the scope of the claims.

10: intraocular lens support 11: outer peripheral surface
11a: outer front portion 11b: outer rear portion
12: inner circumferential surface 12a: inner front surface portion
12b: Inner rear portion 20: Complex motion transfer surface
30: intraocular lens 50: connecting means

Claims (10)

An intraocular lens support (10) having a ring shape inserted into a capsule color and accommodating an intraocular lens (30) therein,
The outer peripheral surface 11 of the intra-ocular lens support 10 has an outer front surface portion 11a protruding convexly toward one side with reference to the equator E as a convexly protruding end, And an outer rear part (11b) protruding toward the other side with reference to the equator (E) and having at least part of an arc shape,
The inner circumferential surface 12 of the in-ocular lens support 10 has a sectional shape depressed toward the equator E and has an inner front surface 11a extending toward the distal end of the outer front surface 11a so as to form at least part of an arc And an inner rear surface portion 12b extending at an end portion of the outer rear surface portion 11b toward an end of the outer rear surface portion 11b,
A part of the outer front portion 11a is provided with a complex motion transfer surface 20 which is recessed toward a central portion passing from the outer circumferential surface to the inner circumferential surface so as to improve the motion transmission capability,
Wherein the complex motion transmitting surface (20) forms a rectilinear section in the front projection or a arc section in the direction of the inner circumferential surface. delete delete 2. The intraocular lens support (10) according to claim 1, characterized in that, in a state where the intraocular lens support (10) is mounted on the capsule color, the complex motion transfer surface (20) . 5. The intraocular lens support according to claim 4, wherein the complex motion transfer surface (20) formed on the outer front portion (11a) is located in a section of 0.9 mm to 1.5 mm length in the equator. The intraocular lens support according to claim 4, wherein the complex motion transfer surface (20) formed on the outer rear portion (11b) is located in a section of 1.2 mm to 1.9 mm length in the equator. delete The method according to claim 1,
The arcs of the outer front part 11a, the outer rear part 11b, the inner front part 12a and the inner rear part 12b form a part of an ellipse,
The short axis of each ellipse constituting each arc is formed such that the outer front portion 11a is shorter than the outer rear portion 11b and the inner front portion 12a is formed shorter than the inner rear portion 12b. The intraocular lens support according to claim 8, wherein the short axis of each ellipse forming each arc has the longest inner rear face part (12b) and the shortest outer front face part (11a). The intraocular lens support according to claim 1, further comprising a complex motion transfer surface (20) recessed toward a central portion of the outer rear surface portion (11b) to improve motion transfer capability.

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