WO2025110869A1 - Continuous multifocal intraocular lens and insertion method thereof - Google Patents

Abstract

The present invention relates to a continuous multifocal intraocular lens. The continuous multifocal intraocular lens comprises: an optical part including an optical lens; and an integral part coupled to the optical part and including a basic lens formed on a surface in contact with the optical part, wherein the optical part is formed to be detachable from the integral part in a state in which the integral part is inserted into the eyeball of a user, and the optical lens and the basic lens may have different parameters regarding optical properties.

Description

Continuous multifocal intraocular lens and method for inserting the same

The present invention relates to a continuous multifocal intraocular lens and a method for inserting the same.

Specifically, the present invention relates to a continuous multifocal intraocular lens, in which the boundary of the curved surface does not appear on the lens surface, which is designed to produce a magnifying effect in the intraocular lens.

In general, conventional existing technologies related to artificial lenses are diffractive multifocal IOLs that are made to produce a magnifying glass effect with multiple spiral edges, or refractive multifocal IOLs that have different partial refractive powers. The disadvantage of multifocal IOLs is that in the case of diffractive multifocal IOLs, light is reflected in the spiral edge portion, and in the case of refractive IOLs, the refractive area is partially divided, causing image distortion, light scattering, and glare.

On the other hand, middle-aged and elderly people often use presbyopia contact lenses. These presbyopia contact lenses do not have separate refractive areas that produce a magnifying effect. The problem is that the position is not fixed after being worn on the cornea, so the magnifying effect cannot be seen.

As such, existing single-focus artificial lenses and presbyopia contact lenses each have their own clear shortcomings.

The problem to be solved by the present invention is to provide a continuous multifocal intraocular lens and a method for inserting the same, which can overcome the disadvantages and side effects of existing presbyopic contact lenses by combining a monofocal intraocular lens and a presbyopic contact lens.

The purposes of the present invention are not limited to the purposes mentioned above, and other purposes and advantages of the present invention which are not mentioned can be understood by the following description, and will be more clearly understood by the embodiments of the present invention. In addition, it will be easily understood that the purposes and advantages of the present invention can be realized by the means and combinations thereof indicated in the claims.

A continuous multifocal artificial lens according to some embodiments of the present invention comprises an integral part including an optical part including an optical lens and a base lens formed on a surface that is coupled to the optical part and contacts the optical part, wherein the optical part is formed to be detachable from the integral part while the integral part is inserted into a user's eye, and parameters regarding optical properties of the optical lens and the base lens may be different from each other.

Additionally, the optical lens may include a continuous multifocal lens and may provide variable refractive power required for near, intermediate and far distance vision.

Additionally, the basic lens may include a single-focus lens.

Additionally, the single-focus lens may include a single-focus lens having a biconvex shape.

In addition, the optical portion further includes a connector, the integral portion includes a connector, the connector and the connector can be coupled to each other, and the connector and the connector can be at least two or more in the same number.

Additionally, the connector and the connecting body may have shapes corresponding to each other so that they can be combined with each other.

Additionally, the integral part may include a predetermined number of through holes.

Additionally, it may include a sealing button that can be inserted into the through hole.

Additionally, the material of the optical portion and the integral portion may include a biocompatible material.

Additionally, the biocompatible material may include at least one of silicone and hydrogel.

A continuous multifocal intraocular lens and a method for inserting the same according to some embodiments of the present invention have a novel effect of overcoming the disadvantages and side effects of existing monofocal intraocular lenses and existing presbyopic contact lenses by combining a monofocal intraocular lens and a presbyopic contact lens.

Specifically, the continuous multifocal intraocular lens and the insertion method thereof according to some embodiments of the present invention can prevent the defects of existing technologies, such as diffuse reflection of light, image distortion, light scattering, glare, non-fixation of lens position, stepped edges, and discontinuity of curved surfaces, by combining a monofocal intraocular lens and a presbyopic contact lens.

In addition to the above-described contents, the specific effects of the present invention are described together with the specific matters for carrying out the invention below.

FIGS. 1A to 1D illustrate a continuous multifocal intraocular lens according to some embodiments of the present invention.

FIG. 2 is a drawing for explaining an optical lens of an optical unit according to some embodiments of the present invention.

FIGS. 3A and 3B are drawings for explaining a connection method of a connector and a connecting body according to some embodiments of the present invention.

FIG. 4 is a drawing for explaining a sealing button and a through hole according to some embodiments of the present invention.

Figures 5a and 5b are drawings for explaining problems of an integrated artificial lens.

FIG. 6 is a flow chart illustrating a method for inserting an artificial lens into an eye according to some embodiments of the present invention.

FIG. 7 is a flow chart illustrating a retinal surgery method through a through-hole and a through-hole sealing method according to some embodiments of the present invention.

The terms or words used in this specification and the claims should not be interpreted as limited to their general or dictionary meanings. In accordance with the principle that the inventor can define the concept of a term or word in order to best explain his or her invention, they should be interpreted as meanings and concepts that are consistent with the technical idea of the present invention. In addition, the embodiments described in this specification and the configurations illustrated in the drawings are only one embodiment in which the present invention is realized, and do not represent the entire technical idea of the present invention, so it should be understood that there may be various equivalents, modifications, and applicable examples that can replace them at the time of this application.

The terms first, second, A, B, etc. used in this specification and claims may be used to describe various components, but the components should not be limited by the terms. The terms are used only for the purpose of distinguishing one component from another. For example, it could be called the first component without departing from the scope of the present invention. The term 'and/or' includes any combination of a plurality of related described items or any item among a plurality of related described items.

The terminology used in this specification and claims is only used to describe specific embodiments and is not intended to limit the present invention. The singular expression includes the plural expression unless the context clearly indicates otherwise. It should be understood that the terms "comprise" or "have" in this application do not exclude in advance the possibility of the presence or addition of features, numbers, steps, operations, components, parts or combinations thereof described in the specification.

Unless otherwise defined, all terms used herein, including technical or scientific terms, have the same meaning as commonly understood by one of ordinary skill in the art to which this invention belongs.

Terms defined in commonly used dictionaries should be interpreted as having a meaning consistent with the meaning they have in the context of the relevant technology, and shall not be interpreted in an ideal or overly formal sense unless explicitly defined in this application. In addition, each configuration, process, process, or method included in each embodiment of the present invention may be shared within a scope that is not technically contradictory to one another.

Hereinafter, with reference to FIGS. 1A to 7, a continuous multifocal intraocular lens and a method for inserting the same according to some embodiments of the present invention will be described.

FIGS. 1A to 1D illustrate a continuous multifocal intraocular lens according to some embodiments of the present invention.

The intraocular lens (hereinafter referred to as “IOL”) illustrated in FIGS. 1A to 1D is an intraocular lens (IOL) in which an optical section can be added to an integral part including a basic lens. At this time, the material of the intraocular lens (IOL) of the present invention may include a soft and flexible material among biocompatible materials, such as silicone and/or hydrogel, but the embodiments of the present invention are not limited thereto.

Referring to FIGS. 1A to 1D, an artificial lens (IOL) may include an optical part (hereinafter referred to as “OP”) and a whole portion (hereinafter referred to as “WP”). The IOL of the present invention may perform refractive power correction or individualization, etc., by additionally using an optical lens (OP_lens) of the optical part (OP), in addition to a basic lens (WP_lens) included in the whole portion (WP). That is, the IOL according to some embodiments of the present invention may correct the optical properties of the whole portion (WP) through the optical part (OP).

At this time, the optical lens (OP_lens) included in the optical unit (OP) and the basic lens (WP_lens) included in the integral unit (WP) may have different parameters regarding optical properties. For example, the optical lens (OP_lens) and the basic lens (WP_lens) may have different parameters regarding fixed focal length, refractive index, etc. For example, the optical lens (OP_lens) may include a contact lens for correcting presbyopia, such as a continuous multifocal lens, and the basic lens (WP_lens) may include a single focal lens. However, the embodiments of the present invention are not limited thereto.

The optical section (OP) can assist or correct the role of collecting light or concentrating light to change the direction of light propagation by the integral section (WP).

As some examples, the optical unit (OP) may include an optical lens (OP_lens).

The optical lens (OP_lens) may have various parameter values. The parameters of the optical lens (OP_lens) may include the type of the optical lens (OP_lens), the focal length, the refractive index, the traveling angle, the diameter, the thickness, etc., but the embodiments of the present invention are not limited thereto. The types of the optical lens (OP_lens) may include a biconvex lens, a single-sided convex lens, a bending concave lens, etc., but the embodiments of the present invention are not limited thereto.

At this time, the optical lens (OP_lens) may include a presbyopic contact lens. In other words, the optical properties of the optical lens (OP_lens) may be for correcting vision for presbyopia.

For example, the optical lens (OP_lens) may be in the form of a continuous multifocal lens, i.e., the optical lens (OP_lens) may provide variable refractive powers required for near, intermediate, and far vision.

Hereinafter, the optical lens (OP_lens) of the present invention will be described in more detail with reference to FIG. 2.

FIG. 2 is a drawing for explaining an optical lens of an optical unit according to some embodiments of the present invention.

Referring to FIG. 2, the optical lens (OP_lens) may include a form of a continuous multifocal lens used as a presbyopic contact lens.

For example, an optical lens (OP_lens) can provide variable refractive power required for near, intermediate, and far vision.

Taking Fig. 2 as an example, the optical lens (OP_lens) may include a first region (R1) that provides refractive power required for near vision, a second region (R2) that provides refractive power required for intermediate vision, and a third region (R3) that provides refractive power required for far vision. At this time, the refractive powers of the first region (R1) to the third region (R3) may be different from each other.

However, the embodiments of the present invention are not limited thereto, and it is obvious that the optical lens (OP_lens) can be designed to have various shapes and optical properties.

Referring again to FIGS. 1A to 1D, the integral part (WP) performs refractive power correction or improvement, etc., and is also connected to the optical part (OP) to support and sustain the optical part (OP).

Although the integral part (WP) is illustrated in FIGS. 1A to 1D as having a rectangular solid shape with rounded corners, the embodiment of the present invention is not limited thereto, and it is obvious that the shape of the integral part (WP) may have various shapes such as a cube with rounded corners, a cylinder, a cone, etc.

A component (WP) may include a base lens (WP_lens).

As some examples, the basic lens (WP_lens) can perform refractive power correction or improvement, etc. At this time, the basic lens (WP_lens) can have various parameter values. The parameters of the basic lens (WP_lens) can include the type of the basic lens (WP_lens), the focal length, the refractive index, the traveling angle, the diameter, the thickness, etc., but the embodiments of the present invention are not limited thereto. The types of the basic lens (WP_lens) can include a biconvex lens, a single convex lens, a bending concave lens, etc., but the embodiments of the present invention are not limited thereto.

At this time, the basic lens (WP_lens) may include a single-focus lens. In other words, the optical properties of the optical lens (OP_lens) may be designed according to the single-focus lens. At this time, the basic lens (WP_lens) may include various forms of single-focus lenses. For example, the basic lens (WP_lens) may include various forms of single-focus lenses such as a biconvex single-focus lens, a biconcave single-focus lens, a concave-convex single-focus lens, a plano-convex single-focus lens, and a plano-concave single-focus lens.

FIG. 1d illustrates a case in which the basic lens (WP_lens) is a biconvex single-focus lens as a main embodiment of the present invention, but the present invention is not limited thereto.

In this way, the intraocular lens (IOL) according to some embodiments of the present invention combines an integral part (WP) having the form of a monofocal IOL and an optical part (OP) having the form of a presbyopic contact lens, thereby having a new effect that can overcome the disadvantages and side effects of existing monofocal IOLs and existing presbyopic contact lenses.

That is, an intraocular lens (IOL) according to some embodiments of the present invention may not cause the defects of existing technologies, such as diffuse reflection of light, image distortion, light scattering, glare, non-fixation of lens position, and discontinuity of stepped edge curvature, by combining a single focus IOL and a presbyopic contact lens.

Additionally, the intraocular lens (IOL) according to some embodiments of the present invention may enable additional attachment and replacement of an optical portion (optical portion, OP) after the integral portion (WP) including the basic lens (WP_lens) is inserted into the eye. That is, the intraocular lens (IOL) of the present invention can have an optical portion (OP) additionally attached without removing the IOL itself after the integral portion (WP) including the basic lens (WP_lens) is inserted into the eye, thereby having the effect of easily performing refractive correction, etc.

In addition, unlike conventional integral IOLs, the IOL can be used to replace the optical part (OP) without removing the already inserted IOL when refractive correction is required after IOL insertion, making the surgical procedure simpler and safer.

Meanwhile, the optical part (OP) and the integral part (WP) can have corresponding shapes so that they can be combined with each other.

For example, the optical portion (OP) may be formed with a curvature corresponding to the curvature of the basic lens (WP_lens) of the integral portion (WP). In other words, the curvature of the optical portion (OP) may be identical to or very similar to the curvature of the basic lens (WP_lens) of the integral portion (WP).

As another example, the optical unit (OP) may include a connector (OP_access) for coupling with the integral unit (WP), and the integral unit (WP) may include a connector (WP_connect) for coupling with the optical unit (OP). In this case, the connector (OP_access) and the connector (WP_connect) may be coupled to each other.

The connector (OP_access) can be connected to the connector (WP_connect) of the integral part (WP). In other words, the connector (OP_access) of the optical part (OP) can be connected to the connector (WP_connect) of the integral part (WP) to form a union.

In Fig. 1b, the shape of the connector (OP_access) is depicted as a rod shape and the number of connectors (OP_access) is depicted as two, but this is only for convenience of explanation. In other words, the shape and number of connectors (OP_access) are not limited to those depicted in Fig. 1b and can be freely modified.

The connector (WP_connect) can be connected to the connector (OP_access) of the optical unit (OP). In other words, the connector (WP_connect) of the integral unit (WP) can be connected to the connector (OP_access) of the optical unit (OP) to form a union.

In Fig. 1b, the shape of the connector (WP_connect) is shown as an L-shape and the number of connectors (WP_connect) is shown as two, but this is only for convenience of explanation. In other words, the shape and number of connectors (WP_connect) are shown in Fig. 5b.

It can be freely transformed without being limited to the illustrated bar.

Hereinafter, a connection method of a connector (OP_access) and a connection body (WP_connect) according to some embodiments of the present invention will be described with reference to FIGS. 3a and 3b.

FIGS. 3A and 3B are drawings for explaining a connection method of a connector and a connecting body according to some embodiments of the present invention.

FIGS. 3A and 3B are drawings for explaining a connection method of a connector and a connecting body according to some embodiments of the present invention.

Referring to FIGS. 3a and 3b, an access and a connect can be connected to each other to form a union.

The connector (access) illustrated in FIGS. 3a and 3b may refer to a connector (OP_access) included in an artificial lens (IOL) illustrated in FIGS. 1a to 1d, and the connector (connect) illustrated in FIGS. 3a and 3b may refer to a connector (WP_connect) included in an artificial lens (IOL1) illustrated in FIGS. 1a to 1d.

Fig. 3a illustrates a connection method in which an access is formed in the shape of a hook or a hook and is wound around an access, and Fig. 3b illustrates a connection method in which an access is inserted into and fixed inside an access.

However, it is obvious that the connection method of the access and the connect is not limited to that shown in FIGS. 3a and 3b.

Referring again to FIGS. 1A to 1D , on the other hand, the integral part (WP) may include a predetermined number of through holes (WP_hole). The through holes (WP_hole) may serve as a space into which a surgical instrument for simple retinal surgery may be inserted. The through holes (WP_hole) may be utilized as a space into which a surgical instrument for simple retinal surgery may be inserted. Simple retinal surgery may include treatment for floaters, small-volume vitrectomy, treatment for micro-retinal tears, etc., but the embodiments of the present invention are not limited thereto. At this time, the diameter of the through holes (WP_hole) may be 2 mm or less, and the diameter of the surgical instrument inserted into the through holes (WP_hole) may be 1 mm or less, but the embodiments of the present invention are not limited thereto.

In FIGS. 1A to 1D, the shape of the through hole (WP_hole) is depicted as an arc and the number of through holes (WP_hole) is two, but this is only for convenience of explanation. In other words, the shape and number of through holes (WP_hole) are not limited to those depicted in FIGS. 1A to 1D and can be freely modified.

Although not shown in FIGS. 1A to 1D, the artificial lens (IOL) of the present invention may further include a sealing button inserted into the through hole (WP_hole).

Hereinafter, the through hole (WP_hole) and sealing button of the present invention will be described with reference to FIG. 4.

FIG. 4 is a drawing for explaining a sealing button and a through hole according to some embodiments of the present invention.

Referring to FIG. 4, a sealing button (hereinafter referred to as “SB”) can be connected to a through hole. In other words, the sealing button (SB) can be inserted into a through hole.

At this time, the through hole (hole) may mean a through hole (WP_hole) included in an artificial lens (IOL) as shown in FIGS. 1a to 1d.

In some examples, the sealing button (SB) may have a shape corresponding to the through hole. For example, if the through hole is in the shape of an arc, the sealing button (SB) may also have a shape corresponding to the arc, but the embodiments of the present invention are not limited thereto.

The present invention can prevent the vitreous body filling the retinal area behind the lens capsule from being detached through the through hole by means of a sealing button (SB) inserted into the through hole.

That is, the artificial lens (IOL) of the present invention includes a through hole to facilitate simple retinal surgery. However, if the through hole is open, there may be a problem in which the vitreous body at the back of the lens capsule leaks out through the through hole.

Accordingly, the artificial lens (IOL) of the present invention has the effect of achieving both the convenience of retinal surgery and the prevention of vitreous detachment by opening the penetration hole when retinal surgery is required and blocking the penetration hole with a sealing button (SB) in other cases.

Referring again to FIGS. 1A to 1D, the intraocular lens (IOL) of the present invention is implemented in a functional manner in which the optical portion (OP) and the integral portion (WP) can be assembled. In other words, the intraocular lens (IOL) of the present invention may be a functional continuous multifocal IOL implemented in a form in which the optical portion (OP) including a presbyopic contact lens and the integral portion (WP) including a single-focus lens can be assembled.

At this time, a user using the artificial lens (IOL) of the present invention can wear the IOL of the present invention through a first wearing method in which the optical part (OP) and the integral part (WP) are inserted into the user's eyeball in an assembled state, or a second wearing method in which only the integral part (WP) is inserted into the user's eyeball and then the optical part (OP) is coupled to the integral part (WP) while the integral part (WP) is mounted on the user's eyeball.

Hereinafter, the process and advantages of wearing the intraocular lens (IOL) of the present invention by a user through the second wearing method described above will be described.

Figures 5a and 5b are drawings for explaining problems of an integrated artificial lens.

Referring to FIGS. 5a and 5b, a conventional integral artificial lens (IOL) is an integral product composed of a central part including an optical lens and a peripheral part (haptic part) that supports the central part.

At this time, if there is a need to replace the artificial lens (IOL), a new artificial lens (IOL) must be inserted to resolve this. The need to replace the IOL occurs when a refractive error occurs after cataract surgery, when the function of the IOL needs to be supplemented from monofocal to multifocal or corrected from multifocal to monofocal, when the IOL is dislocated from the lens capsule (hereinafter referred to as "LC"), when the IOL becomes cloudy, when the IOL causes bullous keratopathy (corneal endothelial thinning or cystic macular edema), and when the IOL is lost due to trauma.

In general, the process of extracting the existing intraocular lens (IOL) before inserting a new intraocular lens (IOL) is required. However, this method is very difficult to use when the IOL and the lens capsule (LC) are absorbed, and is also impossible if a subsequent cataract surgery has been performed.

Specifically, first, if the lens capsule (LC) is not absorbed by the IOL within a few months (e.g., 3 months) after the IOL is inserted (see <A1> in Fig. 5a), in order to replace the IOL, the IOL inside the lens capsule (LC) must be cut into several pieces, extracted out of the eye, a new IOL must be inserted, and the IOL extraction site must be sutured. This is a complicated and time-consuming surgical procedure, and there is also a possibility that the corneal endothelial cells may be touched or the lens capsule (LC) may rupture.

Then, approximately 3 to 6 months after the intraocular lens (IOL) is inserted into the lens capsule (LC), epithelial cells (EC) proliferate in the empty space of the lens capsule (LC) and firmly adhere to the IOL (see <A2> in Figure 5a).

At this time, since the inserted artificial lens (IOL) is firmly fixed to the lens bag (LC), it is very difficult to extract and exchange the IOL adsorbed on the lens bag (LC). When extracting such an IOL, the surgical process is complicated and takes a long time, and the lens bag (LC) adsorbed on the IOL can be easily torn when trying to separate it, and if the lens bag (LC) is torn, not only can the vitreous humor filling the retinal area behind the lens bag (LC) leak out, but also it is impossible to insert a new IOL into the lens bag (LC) after extracting the IOL.

Therefore, in cases where it is not possible to insert an artificial lens (IOL) into the lens capsule for the reasons described above, this problem has been solved by using an anterior segment IOL implantation surgery, in which a new IOL is inserted in front of the iris, and a posterior segment IOL implantation surgery, in which the IOL is inserted behind the iris.

However, there is a high possibility that anterior chamber IOL implantation will cause side effects such as corneal endothelium damage, anterior chamber angle blockage, and glaucoma. In addition, posterior chamber IOL implantation is a method of connecting both ends of the peripheral part that supports the optical part of the IOL with sutures, and then suturing both ends of the peripheral part to the adjacent sclera. This makes the surgical process complicated, takes a long time, and has the disadvantage of causing visual discomfort because it is not fixed in the lens capsule (LC) like an IOL after surgery.

To address the above shortcomings, there is a surgical procedure that involves creating a support for an artificial lens (IOL) and melting the surrounding area with a thermocautery device to secure it to a plate-shaped flange. However, this is not a commonly performed surgical procedure.

If secondary cataract surgery is performed to remove the posterior capsule (LC_back) of the lens capsule (LC) adhered to the back of the artificial lens (IOL) after cataract surgery, exchange of the IOL becomes completely impossible.

Referring to Figure 5b, a secondary cataract is a symptom in which epithelial cells proliferate and clouding occurs in the posterior capsule (LC) behind the lens, that is, the posterior capsule (LC_back). To resolve this, the posterior capsule (LC_back) is burned and removed with a laser during secondary cataract surgery. At this time, if the artificial lens (IOL) needs to be replaced and the IOL is removed, the highly viscous vitreous body that fills the retina behind the lens capsule (LC) inevitably leaks.

Therefore, when performing secondary cataract surgery after inserting a conventional intraocular lens (IOL), exchange of the IOL is not possible.

In addition, there has been no simple solution to the small amount of floaters, fine vitreous admixtures, or fine retinal tears that occur within the existing retina. Since all of these symptoms can only be treated through the existing retinal surgery process, ophthalmologists who are not retina specialists were unable to treat them.

Therefore, there has been a significant need for artificial lens technology to address these problems and inconveniences.

Fig. 6 is a flow chart illustrating a method for inserting an artificial lens into an eye according to some embodiments of the present invention. Each step (S100 to S500) of Fig. 6 can be performed by a human and/or automated medical equipment, ocular surgical equipment, surgical gown, etc.

Referring to FIGS. 1A to 1D and FIG. 6, FIG. 6 is a flowchart illustrating a process of connecting an optical part (OP) after inserting an integral part (WP) of an artificial lens (IOL) illustrated in FIGS. 1A to 1D into an eyeball. In other words, FIG. 6 is a flowchart illustrating a second wearing method, that is, a method in which only the integral part (WP) is inserted into a user's eyeball and then the optical part (OP) is connected to the integral part (WP) while the integral part (WP) is mounted on the user's eyeball.

Referring to FIG. 6, first, an integral part (WP) of a continuous multifocal IOL can be inserted into a capsular bag (S100). At this time, the integral part (WP) can include a basic lens (WP_lens), a connector (WP_connect), a through hole (WP_hole), etc. At this time, as described above, the basic lens (WP_lens) can include a biconvex single-focus lens, but the embodiment of the present invention is not limited thereto.

Next, it is possible to determine whether vision correction is necessary (S200). For example, it is possible to determine whether presbyopia correction is necessary. At this time, it is possible to determine whether presbyopia correction is necessary by determining the degree of error in the refractive power of the artificial lens (IOL), or, if requested by the user, it is possible to determine that presbyopia correction is necessary.

If vision correction is required as a result of the judgment, a portion of the lens capsule near the connection (WP_connect) of the integral part (WP) can be resected (S300)

Next, the optical unit (OP) can be connected to the integral unit (WP) (S400).

As some examples, the connector (OP_access) of the optical part (OP) and the connector (WP_connect) of the integral part (WP) can be connected to each other. At this time, the parameter value of the optical lens (OP_lens) included in the optical part (OP) may be the same as or different from the parameter value of the basic lens (WP_lens) of the integral part (WP).

At this time, the optical part (OP) may include an optical lens (OP_lens). The optical lens (OP_lens) may include a presbyopic contact lens. In other words, the optical properties of the optical lens (OP_lens) may be for correcting vision of presbyopia. For example, the optical lens (OP_lens) may be in the form of a continuous multifocal lens. That is, the optical lens (OP_lens) may provide variable refractive power required for near, intermediate, and far vision.

FIG. 7 is a flow chart illustrating a retinal surgery method through a through-hole and a through-hole sealing method according to some embodiments of the present invention. Each step (S600 to S900) of FIG. 7 can be performed by a human and/or automated medical equipment, ocular surgical equipment, surgical robot, etc.

Referring to FIGS. 1A to 1D and FIG. 7, first, local anesthesia can be performed after the surgery (S600). In other words, local anesthesia can be performed after the surgeon's pupil is dilated.

Next, a surgical instrument can be inserted through the through hole (WP_hole) (S700). At this time, the diameter of the through hole (WP_hole) may be 2 mm or less, and the diameter of the surgical instrument may be 1 mm or less, but the embodiment of the present invention is not limited thereto.

Next, a surgical instrument can be inserted into the retina to perform surgery (S800). The surgery performed at this time may include treatment of vitrectomy, small-volume vitrectomy, treatment of microscopic retinal tears, etc., but the embodiments of the present invention are not limited thereto.

Next, the through hole (WP_hole) can be sealed with a sealing button (SB) (S900). At this time, the sealing button (SB) can have a shape corresponding to the through hole (WP_hole). For example, if the through hole (WP_hole) is in the shape of an arc, the sealing button (SB) can also have a shape corresponding to an arc, but the embodiment of the present invention is not limited thereto.

The present invention can prevent the vitreous body filling the retinal region behind the lens capsule from being detached through the through hole (WP_hole) by using a sealing button (SB) inserted into the through hole (WP_hole).

That is, the artificial lens (IOL) of the present invention includes a through hole (WP_hole) to facilitate the aforementioned simple retinal surgery. However, if the through hole (WP_hole) is open, a problem may occur in which the vitreous body at the back of the lens capsule leaks out through the through hole (WP_hole).

Accordingly, the artificial lens (IOL) of the present invention has the effect of achieving both convenience of retinal surgery and prevention of vitreous detachment by opening the through hole (WP_hole) when retinal surgery is required and blocking the through hole (WP_hole) with a sealing button (SB) in other cases.

The above description is merely an example of the technical idea of the present embodiment, and those skilled in the art will appreciate that various modifications and variations may be made without departing from the essential characteristics of the present embodiment. Accordingly, the present embodiments are not intended to limit the technical idea of the present embodiment, but rather to explain it, and the scope of the technical idea of the present embodiment is not limited by these embodiments. The protection scope of the present embodiment should be interpreted by the following claims, and all technical ideas within a scope equivalent thereto should be interpreted as being included in the scope of the rights of the present embodiment.

Claims (10)

An optical section comprising an optical lens; and Comprising an integral part that is coupled to the optical part and includes a basic lens formed on a surface that contacts the optical part, The above optical part is formed so as to be detachable from the integral part while the integral part is inserted into the user's eye, The above optical lens and the above basic lens have different parameters regarding optical properties. Continuous multifocal intraocular lens. In the first paragraph, The optical lens comprises a continuous multifocal lens and provides variable refractive power for near, intermediate and far vision. Continuous multifocal intraocular lens. In the first paragraph, The above basic lens includes a single-focus lens. Continuous multifocal intraocular lens. In the third paragraph, The above single-focus lens includes a single-focus lens of a biconvex shape. Continuous multifocal intraocular lens. In the first paragraph, The above optical part further includes a connector, The above integral part includes a connecting body, The above connector and the above connecting body can be connected to each other, The above connecting body and the above connecting body are at least two identical numbers. Continuous multifocal intraocular lens. In clause 5, The above connecting body and the connecting body have corresponding shapes so that they can be joined to each other. Continuous multifocal intraocular lens. In the first paragraph, The above integral part includes a predetermined number of through holes. Continuous multifocal intraocular lens. In Article 7, Further comprising a sealing button that can be inserted into the above through hole. Continuous multifocal intraocular lens. In the first paragraph, The material of the optical part and the integral part includes a biocompatible material. Continuous multifocal intraocular lens. In Article 9, The biocompatible material comprises at least one of silicon and hydrogel. Continuous multifocal intraocular lens.

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