KR20100004777A - Intraocular lens and correction method of postoperative refractive error of intraocular lens - Google Patents

Intraocular lens and correction method of postoperative refractive error of intraocular lens Download PDF

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Publication number
KR20100004777A
KR20100004777A KR1020080065126A KR20080065126A KR20100004777A KR 20100004777 A KR20100004777 A KR 20100004777A KR 1020080065126 A KR1020080065126 A KR 1020080065126A KR 20080065126 A KR20080065126 A KR 20080065126A KR 20100004777 A KR20100004777 A KR 20100004777A
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South Korea
Prior art keywords
lens
lens unit
groove
intraocular lens
holder
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KR1020080065126A
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Korean (ko)
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김현호
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김현호
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Priority to KR1020080065126A priority Critical patent/KR20100004777A/en
Priority to PCT/KR2009/003636 priority patent/WO2010002215A2/en
Publication of KR20100004777A publication Critical patent/KR20100004777A/en

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    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61F—FILTERS IMPLANTABLE INTO BLOOD VESSELS; PROSTHESES; DEVICES PROVIDING PATENCY TO, OR PREVENTING COLLAPSING OF, TUBULAR STRUCTURES OF THE BODY, e.g. STENTS; ORTHOPAEDIC, NURSING OR CONTRACEPTIVE DEVICES; FOMENTATION; TREATMENT OR PROTECTION OF EYES OR EARS; BANDAGES, DRESSINGS OR ABSORBENT PADS; FIRST-AID KITS
    • A61F2/00—Filters implantable into blood vessels; Prostheses, i.e. artificial substitutes or replacements for parts of the body; Appliances for connecting them with the body; Devices providing patency to, or preventing collapsing of, tubular structures of the body, e.g. stents
    • A61F2/02—Prostheses implantable into the body
    • A61F2/14—Eye parts, e.g. lenses, corneal implants; Implanting instruments specially adapted therefor; Artificial eyes
    • A61F2/16—Intraocular lenses
    • A61F2/1613—Intraocular lenses having special lens configurations, e.g. multipart lenses; having particular optical properties, e.g. pseudo-accommodative lenses, lenses having aberration corrections, diffractive lenses, lenses for variably absorbing electromagnetic radiation, lenses having variable focus
    • A61F2/1624—Intraocular lenses having special lens configurations, e.g. multipart lenses; having particular optical properties, e.g. pseudo-accommodative lenses, lenses having aberration corrections, diffractive lenses, lenses for variably absorbing electromagnetic radiation, lenses having variable focus having adjustable focus; power activated variable focus means, e.g. mechanically or electrically by the ciliary muscle or from the outside
    • A61F2/1629—Intraocular lenses having special lens configurations, e.g. multipart lenses; having particular optical properties, e.g. pseudo-accommodative lenses, lenses having aberration corrections, diffractive lenses, lenses for variably absorbing electromagnetic radiation, lenses having variable focus having adjustable focus; power activated variable focus means, e.g. mechanically or electrically by the ciliary muscle or from the outside for changing longitudinal position, i.e. along the visual axis when implanted
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61F—FILTERS IMPLANTABLE INTO BLOOD VESSELS; PROSTHESES; DEVICES PROVIDING PATENCY TO, OR PREVENTING COLLAPSING OF, TUBULAR STRUCTURES OF THE BODY, e.g. STENTS; ORTHOPAEDIC, NURSING OR CONTRACEPTIVE DEVICES; FOMENTATION; TREATMENT OR PROTECTION OF EYES OR EARS; BANDAGES, DRESSINGS OR ABSORBENT PADS; FIRST-AID KITS
    • A61F2/00—Filters implantable into blood vessels; Prostheses, i.e. artificial substitutes or replacements for parts of the body; Appliances for connecting them with the body; Devices providing patency to, or preventing collapsing of, tubular structures of the body, e.g. stents
    • A61F2/02—Prostheses implantable into the body
    • A61F2/14—Eye parts, e.g. lenses, corneal implants; Implanting instruments specially adapted therefor; Artificial eyes
    • A61F2/15—Implant having one or more holes, e.g. for nutrient transport, for facilitating handling
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61F—FILTERS IMPLANTABLE INTO BLOOD VESSELS; PROSTHESES; DEVICES PROVIDING PATENCY TO, OR PREVENTING COLLAPSING OF, TUBULAR STRUCTURES OF THE BODY, e.g. STENTS; ORTHOPAEDIC, NURSING OR CONTRACEPTIVE DEVICES; FOMENTATION; TREATMENT OR PROTECTION OF EYES OR EARS; BANDAGES, DRESSINGS OR ABSORBENT PADS; FIRST-AID KITS
    • A61F2/00—Filters implantable into blood vessels; Prostheses, i.e. artificial substitutes or replacements for parts of the body; Appliances for connecting them with the body; Devices providing patency to, or preventing collapsing of, tubular structures of the body, e.g. stents
    • A61F2/02—Prostheses implantable into the body
    • A61F2/14—Eye parts, e.g. lenses, corneal implants; Implanting instruments specially adapted therefor; Artificial eyes
    • A61F2/16—Intraocular lenses
    • A61F2/1613—Intraocular lenses having special lens configurations, e.g. multipart lenses; having particular optical properties, e.g. pseudo-accommodative lenses, lenses having aberration corrections, diffractive lenses, lenses for variably absorbing electromagnetic radiation, lenses having variable focus
    • A61F2/1616—Pseudo-accommodative, e.g. multifocal or enabling monovision
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61F—FILTERS IMPLANTABLE INTO BLOOD VESSELS; PROSTHESES; DEVICES PROVIDING PATENCY TO, OR PREVENTING COLLAPSING OF, TUBULAR STRUCTURES OF THE BODY, e.g. STENTS; ORTHOPAEDIC, NURSING OR CONTRACEPTIVE DEVICES; FOMENTATION; TREATMENT OR PROTECTION OF EYES OR EARS; BANDAGES, DRESSINGS OR ABSORBENT PADS; FIRST-AID KITS
    • A61F2/00—Filters implantable into blood vessels; Prostheses, i.e. artificial substitutes or replacements for parts of the body; Appliances for connecting them with the body; Devices providing patency to, or preventing collapsing of, tubular structures of the body, e.g. stents
    • A61F2/02—Prostheses implantable into the body
    • A61F2/14—Eye parts, e.g. lenses, corneal implants; Implanting instruments specially adapted therefor; Artificial eyes
    • A61F2/16—Intraocular lenses
    • A61F2002/1681—Intraocular lenses having supporting structure for lens, e.g. haptics
    • A61F2002/169—Surrounding optic
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61F—FILTERS IMPLANTABLE INTO BLOOD VESSELS; PROSTHESES; DEVICES PROVIDING PATENCY TO, OR PREVENTING COLLAPSING OF, TUBULAR STRUCTURES OF THE BODY, e.g. STENTS; ORTHOPAEDIC, NURSING OR CONTRACEPTIVE DEVICES; FOMENTATION; TREATMENT OR PROTECTION OF EYES OR EARS; BANDAGES, DRESSINGS OR ABSORBENT PADS; FIRST-AID KITS
    • A61F2250/00—Special features of prostheses classified in groups A61F2/00 - A61F2/26 or A61F2/82 or A61F9/00 or A61F11/00 or subgroups thereof
    • A61F2250/0004—Special features of prostheses classified in groups A61F2/00 - A61F2/26 or A61F2/82 or A61F9/00 or A61F11/00 or subgroups thereof adjustable
    • A61F2250/0008—Special features of prostheses classified in groups A61F2/00 - A61F2/26 or A61F2/82 or A61F9/00 or A61F11/00 or subgroups thereof adjustable for adjusting a position by translation along an axis or two perpendicular axes

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  • Health & Medical Sciences (AREA)
  • Ophthalmology & Optometry (AREA)
  • Cardiology (AREA)
  • Oral & Maxillofacial Surgery (AREA)
  • Transplantation (AREA)
  • Engineering & Computer Science (AREA)
  • Biomedical Technology (AREA)
  • Heart & Thoracic Surgery (AREA)
  • Vascular Medicine (AREA)
  • Life Sciences & Earth Sciences (AREA)
  • Animal Behavior & Ethology (AREA)
  • General Health & Medical Sciences (AREA)
  • Public Health (AREA)
  • Veterinary Medicine (AREA)
  • Prostheses (AREA)

Abstract

PURPOSE: An artificial intraocular lens and a method for correcting refraction error are provided, which can simply and safely correct the refraction error generated after intraocular lens implantation. CONSTITUTION: An artificial intraocular lens comprises a lens unit(110) which makes an image of phase of the external object on th retina and forms the crystalline lens main body; a holder(120) accepting the lens unit of the ring shape; and a fixing member(130) connected to the constant area on the outer circumference of the holder. The lens unit has a convex lens shape on the front and back. The fixing member is refracted to the back side and is formed to be curved.

Description

Intraocular Lens and Correction method of Postoperative Refractive Error of Intraocular Lens}

The present invention relates to an intraocular lens that is implanted into the eye during cataract surgery, which is a kind of ocular disease. It is about.

In general, the human eye is very similar to the structure and function of the camera, and the back of the eye has a lens made of a convex lens-like transparent tissue, which functions as a camera lens, which causes aging, external damage, diabetes, various Cataracts are a condition that causes cloudiness due to side effects of drugs, irradiation, and exposure to harmful electromagnetic waves, causing vision loss.

The treatment of cataracts is treated by drug treatment and by surgery. Although there are various drug treatment methods on the market, it is not possible to expect the effect of replacing the surgical treatment with drug treatment. Eventually, cataract treatment is ultimately dependent on surgical treatment, and the development direction is mainly along the surgical side.

The cataract surgery can be divided into two stages: first, removing the cloudy lens and implanting an intraocular lens that replaces the function of the lens to focus on the retina. In the cataract surgery method, a turbid lens is removed by a method such as ultrasonic emulsification, and then a surgical procedure is performed in which a predetermined type of intraocular lens is inserted into an anterior chamber or a posterior chamber of the eye.

In most cases, the intraocular lens is inserted into the inside of a part called CAPSULAR BAG (or lens capsule) in the back chamber or between the capsuleer bag and the iris.

In detail, the intraocular lens may be classified into an anterior insertion lens and a rear insertion lens according to the insertion position, and may be divided into a hard and a soft intraocular lens according to whether or not it can be folded in half when inserted. Polymethyl methacrylate (PMMA) material is used, and the soft artificial lens is usually made of silicon or acrylic material.

Most of the currently used intraocular lens is a posterior insertion lens, and the intraocular lens of the soft material that can be folded to less than 3mm is mostly used so that only 3mm of the lens can be inserted into the eye during surgery.

Next, an example of a cataract surgery procedure for inserting a conventional soft intraocular lens as shown in FIG. 1 will be described.

1 is a plan view showing an example of a conventional intraocular lens.

Referring to FIG. 1, the intraocular lens 10 refracts incident light to form an image of an alien object in the retina, and forms an optical lens 20 that forms a lens body, and a circumferential image of the lens 20. Consists of a pair of haptic (30) connected in the form of an arm (arm) in a symmetrical position on a predetermined portion.

Typically, the diameter of the lens unit 20 of the intraocular lens 10 is about 6 mm and has a convex lens shape in front and rear, and the fixing member 30 is generally refracted to the rear side as a 'C' or 'J' shape. It is curved and curved, and the total diameter of the intraocular lens including the lens part and the fixing member is about 12.0 mm to 13 mm.

In order to insert the intraocular lens 10 into the capsuleer bag in the eye, a 3 mm wide incision is made in the cornea or sclera.

Subsequently, the surgical instrument is inserted through the above-described 3 mm incision and an additional side-port incision wound of less than 1 mm to perform ultrasonic emulsification to cleanly remove the cloudy lens material and to remove the lens material. The intraocular lens is inserted into the space within the capsuleer bag.

At this time, the intraocular lens is inserted into the folded state to be inserted into the incision window of about 3mm, and after the intraocular lens is inserted into the eye, the folded intraocular lens is opened again, and the intraocular lens is fixed by the fixing member in the eye.

However, the conventional intraocular lens has the following problems.

To see objects clearly after cataract surgery, it is important to obtain an emmetropia state in which the cornea and lens are properly refracted by the cornea and lens to focus precisely on the surface of the retina. It is important to determine the correct intraocular lens power (Refractive power).

To this end, corneal curvature and the axial length of the eye, which influences the distance between the lens and the retina, are measured before surgery by ultrasound (A-scan mode) or laser (partial coherence interferometry). By substituting these values into a formula for calculating the intraocular lens frequency, the intraocular lens frequency is determined.

However, these formulas are basically only to predict the required refractive power according to the optical position of the intraocular lens post-operatively before surgery, and the corneal curvature and eye length measured before surgery are known to determine the intraocular lens power. Depending on the measurement error of or the operator factor (surgeon factor), there is a fundamental limit that does not completely exclude the occurrence of postoperative refractive error (primary or myopia).

In general, the measurement error ± 0.3 mm of the ocular axial length (or the distance between the intraocular lens and the retina) with respect to an average sized eye of 24 mm is associated with a refractive error of about ± 1.0 D. Corneal curvature measurement error ± 1.0D is known to be associated with refractive error of ± 1.0D as it is, the operator factor is impossible to predict accurately before surgery.

That is, due to these fundamental limitations, such refractive errors (primary or myopia) occur in many cases after cataract surgery using conventional intraocular lenses, and when refractive errors occur after surgery, the refractive index and focus of the intraocular lens Because of the fixed distance, in order to remove the refractive error (primary or myopia) that occurred after intraocular lens implantation, the intraocular lens must be removed and a new intraocular lens with the corrected refractive error corrected.

Moreover, the above-described surgery to remove the intraocular lens and reinsert the new intraocular lens is technically difficult to remove and reinsert the intraocular lens and various surgical complications such as intraocular structure damage, bleeding, and postoperative inflammation. In addition, due to the high economic potential due to additional surgery, it is difficult to be realistically performed, and the patient often suffers from poor visual acuity or wearing glasses due to refractive errors.

In addition, in the case of expensive multifocal intraocular lens developed for the purpose of simultaneously correcting cataract and presbyopia, the initial refractive state after implantation of the intraocular lens becomes non-timed (refractive error: raw or myopia). The expected effect of presbyopia correction is remarkably inferior. The fundamental problem-solving method is to remove the intraocular lens already inserted in the eye and reinsert the new intraocular lens that corrects the refractive error. Even if the patient does not obtain the presbyopia correction effect as expected before surgery, even though the patient has undergone an expensive presbyopia correction multifocal intraocular lens, in many cases, it is necessary to take the inconvenience of wearing the cap.

In recent years, the accuracy of corneal curvature and ocular axial length measurement has been improved, and the predictive value of various calculation formulas has been improved to reduce the degree of refractive error due to inadequate intraocular lens power after surgery, and more than 90% when using the latest test equipment and calculation formulas. It has been reported that postoperative refractive index values stay within the refractive error range within ± 1.0 D (Diopter). However, these reports expect only the best results, and the incidence of refraction errors that occur is generally higher than that, and myopic refraction errors of -1.0 D (Diopter) alone may cause Snellen at long-distance visual acuity compared with on-time visual acuity. A 2-3 line difference in the visual acuity table (a patient who can see 1.0 on-time sees only 0.6-0.7 uncorrected vision with a -1.0D myopia and requires glasses correction to see 1.0),

Particularly in cases of primitive refractive errors other than myopia after surgery (e.g. +1.0 hyperopia), the patient may not be able to see both near and far objects without dioptric correction glasses (reduced both near and far vision) There is a risk that the patient will experience serious problems in their daily lives.

Therefore, in many cases, surgery is focused on reducing the incidence of primitive refractive error rather than postoperative myopia, with the target refractive index about -0.5D near to myopia rather than on-time, resulting in refractive error. It is not uncommon for myopic refractive errors of more than -1.5D after tilting toward myopia.

As a result, at present, there is no way to completely prevent the refractive error (primary or myopia) after intraocular lens implantation. Therefore, a method for simple and safe correction of the refractive error occurred after surgery or the development of a suitable intraocular lens is urgently needed. It is a state.

Accordingly, an object of the present invention is to provide a method for easily and safely correcting a refractive error (primary or myopia) occurring after intraocular lens implantation or suitable intraocular lens.

The present invention also provides an intraocular lens for removing an intraocular lens that has already been inserted into the eye and reinserting a new intraocular lens that corrects the refractive error when refractive errors occur after intraocular lens implantation. An object of the present invention is to provide a method for correcting refractive error of an intraocular lens.

In order to achieve the object as described above, the present invention is a lens unit (optic); And an optical holder for accommodating the lens unit, wherein the lens unit provides an intraocular lens that is capable of vertical movement in the holder of the lens unit.

The present invention also provides an artificial insemination body, characterized in that the holder includes a main body portion constituting the main body and a lens unit support portion extending from the main body portion, and a screw portion having a screw groove is formed on an inner surface of the main body portion. do.

In addition, the present invention provides an artificial insemination body characterized in that the outer peripheral surface of the lens portion is coupled to the screw groove of the screw portion is fixed.

In addition, the present invention provides an intraocular lens, wherein the lens unit is capable of spiral rotation along the screw groove, and the lens unit is moved vertically to the front or the rear by the spiral rotation of the lens unit.

In addition, the screw groove is a screw groove spiral is formed so that the lens portion can be moved vertically to the front when the lens portion rotates in the clockwise direction, and the lens portion can be moved vertically to the rear side when the lens portion is rotated counterclockwise. In another aspect, the present invention provides an intraocular lens, wherein the screw groove moves vertically toward the rear of the lens when the lens is rotated clockwise, and vertically on the front when the lens is rotated counterclockwise. It provides an intraocular lens characterized in that the spiral of the screw groove is formed so as to move in the direction.

In addition, the present invention has a measurement error ± 0.3mm of the eyeball axial length (or the distance between the intraocular lens and the retina) on the basis of the average size of the eyeball axial length (24mm) as described above is about ± 1.0D Inversely using the fact associated with refractive error, the intraocular lens is characterized in that for correcting the refractive error of ± 1.0D (Diopter) with respect to the movement of the lens unit in the front or rear vertical direction of ± 0.3mm by the rotation of the lens unit. to provide.

In addition, the present invention, when the lens unit is rotated along the screw groove when forming a spiral of the screw groove to be moved by 0.3mm each to the front or rear when rotating the lens 360 °, ± 90 °, 180 of the lens unit It provides an intraocular lens characterized in that for correcting the refractive error of ± 0.25D, 0.50D, 0.75D respectively by rotation of °, 270 °.

In addition, the present invention is a lens unit; And a holder for accommodating the lens unit, wherein the lens unit includes a first groove in a predetermined front area of the lens unit, and the holder includes a second groove in a predetermined front area of the holder. It supports the entire lens, and provides a refractive error correction method of the intraocular lens, characterized in that for rotating the lens unit through the first groove.

In addition, the present invention supports the entire artificial insemination through the second groove, and rotating the lens unit through the first groove is hook-shaped mechanism (Hook) in each of the first groove and the second groove It provides a refractive error correction method of the intraocular lens, characterized in that performed.

In addition, the holder includes a main body portion constituting the main body and a lens portion support portion extending from the main body portion, the inner surface of the main body portion is formed with a screw portion having a screw groove, the outer peripheral surface of the lens portion is the screw portion It provides a refractive error correction method of the intraocular lens, characterized in that coupled to the screw groove is fixed.

In addition, the present invention provides a method for correcting the refractive error of the intraocular lens, characterized in that to correct the hyperopia when the lens unit moves to the front, and to correct myopia when the lens unit moves to the rear.

In addition, the present invention is to make a small incision in the cornea, the hook-shaped device inserted into the eye through the small incision through the hook to the second groove of the intraocular lens already inserted into the eye to support the entire intraocular lens, Another hook-shaped mechanism is hooked to the first groove to rotate the lens unit, thereby providing a refractive error correction method of the intraocular lens, characterized in that for performing refractive error correction by moving the front and rear of the lens unit.

Therefore, the present invention has the effect of providing a method capable of safely correcting the refractive error after intraocular lens implantation or a suitable method of correcting the intraocular lens and the intraocular lens by a simple procedure.

In addition, when the refractive error occurs after intraocular lens implantation, there is an effect of eliminating the operation of removing the intraocular lens already inserted into the eye, and reinserting a new intraocular lens having corrected the refractive error.

Details of the above objects and technical configurations and the effects thereof according to the present invention will be more clearly understood by the following detailed description with reference to the drawings showing preferred embodiments of the present invention. In addition, in the drawings, the length, thickness, etc. of layers and regions may be exaggerated for convenience. Like numbers refer to like elements throughout.

FIG. 2A is a plan view illustrating an intraocular lens according to the present invention, and FIG. 2B is a cross-sectional view taken along the line II ′ of FIG. 2A.

Referring to FIG. 2A, the intraocular lens 100 according to the present invention refracts incident light to form an image of an external object on the retina, forming a lens body, an optical unit 110, and a lens unit 110. It consists of a ring-shaped holder (optic holder) 120 for receiving the haptic 130 connected to a predetermined area on the outer peripheral surface of the holder (120).

First, the lens unit 110 has a convex lens shape at the front and rear, and the fixing member 30 is curved to be curved to the rear side in the form of a 'C' or 'J' shape, and is curved. The total diameter of the lens ("X" region in FIG. 2A) can be formed from 12.0 mm to 13 mm to suit the eye of the public.

In this case, the shape of the lens portion, the shape and type of the fixing member, the total length of the artificial lens is general, and the shape of the lens portion, the shape and type of the fixing member, the total length of the artificial lens is not limited in the present invention.

However, the lens unit 110 according to the present invention includes a first groove 111 in a predetermined region of the front of the lens unit as compared to the general lens unit, which will be described later.

Next, a ring holder 120 according to the present invention accommodates the lens unit 110.

Referring to FIG. 2B, the holder 120 includes a main body 120a constituting the main body of the holder and a lens support 120b extending from the main body, and an inner surface of the main body 120a. The threaded portion 123 having a screw groove 123a is formed therein.

The lens unit 110 is accommodated in a ring-shaped holder 120, and the outer circumferential surface of the lens unit 110 is coupled to and fixed to the screw groove 123a of the screw unit 123.

In this case, the screw unit 123 is formed such that the lens unit 110 is capable of spiral rotation along the screw groove 123a, and the lens unit moves vertically to the front or the rear by the spiral rotation of the lens unit. This is possible.

That is, when the screw portion rotates the lens portion clockwise, the lens portion moves vertically to the front side (A direction of FIG. 2B), and when the lens portion rotates counterclockwise, the lens portion moves vertically to the rear surface (FIG. 2B). The spiral of the screw groove can be formed so as to, in the contrary, when the screw portion rotates the lens portion clockwise, the lens portion is moved in the vertical direction to the rear (B direction in Fig. 2b), the lens portion When rotating counterclockwise, a spiral of the screw groove may be formed so that the lens portion can move vertically to the front side (A direction in FIG. 2B).

At this time, the screw groove 123a and the lens support portion 120b of the screw portion 123 move the lens portion vertically toward the front or the rear, or in the process of folding the artificial lens to be inserted into the eye, the lens portion is separated from the holder. The lens unit 110 is supported so as not to be.

Subsequently, the lens unit 110 according to the present invention includes a first groove 111 in a predetermined region of the front surface of the lens unit, and the holder 120 according to the present invention also has a second region in a predetermined region of the front surface of the holder. The groove 122 is provided.

The first groove 111 and the second groove 122 are for rotating the lens unit in the clockwise or counterclockwise direction as described above, and hook-shaped mechanisms are formed in the first groove and the second groove, respectively. The lens unit is rotated by walking on the groove.

For example, a hook-shaped device may be hooked to the second groove 122 to support the entire intraocular lens, and a hook-shaped device may be hooked to the first groove 111 to rotate the lens unit in a desired direction.

At this time, as will be described later, since the procedure to rotate the lens unit is performed in the state inserted into the eye of the patient, in order to facilitate the technique of rotating the lens unit by hooking the mechanism of the hook-shaped groove, as shown in Figure 2a Likewise, the first groove 111 and the second groove 122 are preferably positioned in a pair of grooves symmetrically at intervals of 180 degrees to the top, bottom or left and right, respectively.

In addition, the second groove 122 is preferably formed in the main body portion 120a in consideration of the thin thickness of the lens support 120b, and the first groove 111 is for ease of rotation. In addition, it is preferable to form near the outer periphery rather than near the center of the lens portion so that the optical characteristics of the central portion of the lens important to the quality of vision due to the presence of the first groove 111 is not affected. In forming the first groove 111 near the outer circumferential portion, the lens unit 110 should be formed in an area which does not overlap with the lens unit support 120b in order to enable rotation.

Subsequently, referring to FIG. 2B, the thickness (“b” region of FIG. 2B) of the threaded portion 123 is preferably 0.6 mm or more.

This, the lens unit according to the present invention may be located at the middle point of the first thickness of the screw portion, the lens unit 110 is rotated along the screw groove 123a, the rear vertical direction (B direction of Figure 2b) or the front When moving in the vertical direction (A direction in FIG. 2B), the distance between the intraocular lens and the retina or the axial length of the eye, which determines the position of the focal point of the intraocular lens, can be corrected. As described above, the refractive error of ± 1.0D (Diopter) can be corrected by shifting ± 0.3mm of the axial length of the eye (or the length between the intraocular lens and the retina) with respect to the average eyeball of 24mm in axial length. to be.

That is, if the lens part is moved 0.3mm to the front or the rear, respectively, it is possible to correct the refractive error of ± 1.0D, a total of 2D (Diopter), which is the range of refractive error with the highest frequency of occurrence after intraocular lens implantation. In order to secure the thickness of the threaded portion is preferably at least 0.6mm.

In addition, when the lens unit 110 rotates spirally along the screw groove 123a, when the lens unit rotates 360 °, a spiral of the screw groove may be formed to move by 0.3 mm to the front or the rear, respectively. Accordingly, when the lens unit rotates by ± 90 °, 180 °, and 270 °, minute refractive errors may be corrected by ± 0.25D, 0.50D, and 0.75D, respectively.

In this case, when the lens unit is moved to the front has a primitive correction effect, when moving to the rear has a myopia correction effect.

In addition, the thickness of the lens support 120b ("a" region of Figure 2b) and the material, while the lens can be passed through the incision through a 3mm wide incision during the operation, the lens will leave the lens support and escape The thickness of the holder 120 corresponding to the sum of the thickness of the lens part support part 120b and the thickness of the screw part 123 is preferably formed by a minimum thickness and a material capable of firmly supporting the lens part. (B of "c" region) is the thickness of the thickness of the threaded portion 123 of 0.6 mm and the thickness of the front and rear lens portion support (two times the "a" region of Figure 2b).

In addition, the width of the holder main body portion 120a ("g" region in FIG. 2B) is the minimum width of the screw portion 123 and the shape of the holder 120 that can firmly support the lens portion and smoothly drive the screw portion. Preferably, the width of the lens unit support part 120b ("h" region of FIG. 2B) is preferably formed to the minimum width that enables firm support of the lens unit and smooth screw driving.

In addition, the diameter of the lens unit 200 that causes actual refraction ("e" region of FIG. 2B) is preferably 5 mm or more so as not to interfere with the object even when the pupil becomes large when the eye sees the object in a dark place (dark adaptation). . In the present invention, rather than causing refraction through the entire lens portion, refraction is caused through the lens portion of the region ("f" region of Figure 2b) except for the region where the lens portion and the support portion overlap, and the lens portion support portion is also minimal Since the width (“h” region of FIG. 2B) must be ensured, the diameter of the lens portion causing actual refraction is reduced by twice the width of the lens portion support portion (h of FIG. 2B), so that the diameter of the lens portion overlaps with the support portion. It is desirable to ensure at least 5 mm or more including the area ("h" area of FIG. 2B) to be.

In addition, the diameter of the holder 120 corresponding to the sum of the diameter of the lens portion and the width of the main body portion 120a (“d” region of FIG. 2B) is folded into the eye through the cornea or scleral incision of 3 mm or less due to the folding of the intraocular lens. In order not to interfere with the insertion process, it is desirable to secure 6 mm, which is the same as the conventional diameter of the conventional intraocular lens.

Subsequently, referring to FIG. 2A, the holder 120 according to the present invention may include a notch 121 in a predetermined region, which, as described above, in the case of a soft intraocular lens, is folded into the eye. It is inserted, so that the process of folding the intraocular lens by the holder 120 relatively thicker than other components of the intraocular lens is not disturbed.

At this time, the notch 121 is preferably positioned symmetrically at intervals of 180 degrees to the left, right or up and down, as shown in Figure 2a to facilitate folding of the intraocular lens, which is the holder 120 It is preferable to form according to the shape and position of the pair of fixing members 130 symmetrically connected to each other on the outer peripheral surface of the.

That is, when the artificial lens is folded in half, since the folding direction will be changed according to the shape and position of the fixing member, it is preferable to form it accordingly. In FIG. 2A of the present invention, the holder 120 of the lens Notches 121 were formed at 3 o'clock and 9 o'clock, respectively, so that they could be folded in half.

In addition, the lens unit may be a polymethyl methacrylate (PMMA) material in the case of a hard artificial lens, a silicone material or an acrylic material may be used in the case of a soft artificial lens, preferably a silicone material or an acrylic material. .

In addition, the holder may use a silicone or acrylic material having transparency, but in the case of the holder, the thickness of the body part is thick and the support part is thin, and the space between the support part and the lens part is overlapped. Since aberration problems may occur, it may be desirable to use an opaque material in the holder, and the pigment may be mixed with a silicone material or an acrylic material to be opaque.

3 is a perspective view showing a holder of an intraocular lens according to the present invention.

As described above, the holder 120 according to the present invention is composed of a main body portion 120a constituting the main body of the holder and a lens portion support portion 120b extending from the main body portion, and the main body portion 120a of the main body portion 120a. On the inner side, a threaded portion 123 having a threaded groove 123a is formed.

In addition, the second groove 122 may be provided in a predetermined region of the holder 120 and the notch 121 may be provided in the predetermined region.

Hereinafter, since the description of the configuration of the holder is as described above, a detailed description thereof will be omitted.

4A and 4B are schematic diagrams showing the movement of the lens unit of the intraocular lens according to the present invention.

First, FIG. 4A is a schematic diagram showing that the lens portion of the intraocular lens has moved to the rear side. In FIG. 2A, the lens portion is located at the midpoint of the thread thickness. Referring to FIG. 4A, it is understood that the lens portion is located at the rear of the thread thickness. Can be.

4B is a schematic diagram showing that the lens portion of the intraocular lens has moved to the front surface. In FIG. 2A, the lens portion is located at the midpoint of the thickness of the screw portion. Referring to FIG. 4B, the lens portion is located at the front of the thickness of the screw portion. Can be.

That is, when the intraocular lens of the present invention is inserted into the eye during cataract surgery, as shown in FIG. 2A, the lens unit of the first intraocular lens is placed at the midpoint of the thickness of the screw.

However, refractive errors (myopia or hyperopia) may occur after intraocular lens implantation, depending on the preoperatively measured corneal curvature and eye length measurement errors, surgeon factors, and errors in the intraocular lens calculation itself. In this case, it is possible to correct the refractive error by obtaining a visual state in which the focal point of the intraocular lens is precisely formed on the retinal surface by moving the intraocular lens lens to the rear surface (myopia correction) or the front surface (primary correction), respectively.

That is, in the conventional case, when the refractive error occurs after the operation as described above, to remove the refractive error, the second operation is performed to remove the intraocular lens and reinsert the new intraocular lens that corrects the refractive error. In most cases, due to the technical difficulties and possible surgical complications of the procedure, the patient was unable to perform the procedure realistically, and the patient was forced to suffer from visual acuity or wearing glasses due to refractive errors, but using the intraocular lens according to the present invention. In this case, as shown in Figures 4a and 4b, it is possible to easily and safely correct the refractive error occurred after cataract surgery by moving the intraocular lens lens to the rear or front.

As described above, the lens unit of the intraocular lens is moved through the first groove 111 provided on the lens unit 200 and the second groove 122 provided in the holder 120, for example. Correction of refractive error caused after surgery by hooking the second grooves 122 in the hook-shaped device to support the entire intraocular lens, and hooking the other hook-shaped devices in the first groove 111 to rotate the lens unit in a desired direction. Since this is possible, the procedure of removing the intraocular lens already inserted into the guide and reinserting the new intraocular lens having corrected the refractive error is not necessary.

 In addition, the procedure for rotating the lens unit is to create a side-port incision wound of less than 1mm in the cornea, the insertion of the hook-type instrument in the eye through the small incision through the intraocular lens Since the lens unit is rotated, the refractive error can be corrected more easily and safely than the procedure of removing the existing intraocular lens and reinserting the new intraocular lens.

Although the present invention has been shown and described with reference to the preferred embodiments as described above, it is not limited to the above embodiments and those skilled in the art without departing from the spirit of the present invention. Various changes and modifications will be possible.

1 is a plan view showing an example of a conventional intraocular lens;

Figure 2a is a plan view showing an intraocular lens according to the present invention,

FIG. 2B is a cross-sectional view taken along line II ′ of FIG. 2A;

3 is a perspective view showing a holder of an intraocular lens according to the present invention;

Figure 4a is a schematic diagram showing that the lens portion of the intraocular lens moved to the rear,

4B is a schematic diagram showing that the lens portion of the intraocular lens was moved to the front side.

<Explanation of symbols for the main parts of the drawings>

100: artificial lens 110: lens

111: first groove 120: holder

120a: main body portion 120b: lens portion support portion

121: notch 122: second groove

123: screw part 123a: screw groove

130: fixing member

Claims (26)

Lens (optic); And An optical holder for accommodating the lens unit, The lens unit is characterized in that the vertical movement in the holder is possible. The method of claim 1, The holder is an artificial lens, characterized in that the ring (ring) shape. The method of claim 1, The holder includes a main body constituting the main body and a lens unit support extending from the main body, An artificial insemination body, characterized in that the screw portion having a screw groove is formed on the inner surface of the body portion. The method of claim 3, wherein An outer lens of the lens unit is fixed to the screw groove, characterized in that the screw groove is fixed. The method of claim 4, wherein The lens unit is capable of spiral rotation along the screw groove, The intraocular lens of claim 1, wherein the lens unit moves in a vertical direction toward the front or the rear by the spiral rotation of the lens unit. The method of claim 5, wherein The screw groove is formed such that the lens portion moves vertically toward the front when the lens portion is rotated clockwise, and the lens portion moves vertically toward the back when the lens portion is rotated counterclockwise, or the screw groove is clocked through the lens portion. And the lens unit moves vertically toward the rear when rotating in the direction, and the lens unit moves vertically to the front when rotating the lens counterclockwise. The method of claim 5, wherein And the lens unit supporter supports the lens unit such that the lens unit is not detached from the holder when the lens unit is moved vertically to the front or the rear or when the lens is folded for the guide insertion. The method of claim 1, The lens unit of claim 1, wherein the lens unit includes a first groove in a predetermined front surface of the lens unit. The method of claim 8, The first lens is an artificial insemination lens characterized in that the pair is located symmetrically up, down or left and right of the front of the lens unit. The method of claim 1, The holder is an artificial lens, characterized in that provided with a second groove in a predetermined front area of the holder. The method of claim 10, The second lens is an artificial insemination lens characterized in that the pair is located symmetrically up, down or left and right of the front surface of the holder body. The method of claim 3, wherein The screw lens is characterized in that the thickness of 0.6mm or more. The method of claim 5, wherein Correct the refractive error of ± 1.0D (Diopter) with respect to ± 0.3mm front or rear vertical movement of the lens part by the helical rotation of the lens part, correct the hyperopia by moving the + direction (front), An intraocular lens myopic corrected by direction (rear) movement. The method of claim 5, wherein When the lens unit is spirally rotated along the screw groove, when the lens unit is rotated 360 °, when the screw groove spiral is formed to move 0.3 mm to the front or the rear, respectively, Correct the refractive errors of ± 0.25D, 0.50D, 0.75D for the ± 90 °, 180 °, and 270 ° rotations of the lens unit, correct the hyperopia by the + direction (front) movement, and the − direction ( Back) artificial intraocular lens, characterized in that to correct myopia by movement. The method of claim 1, An intraocular lens having a notch portion that is symmetrical in an up, down, left, or right direction at a predetermined front surface of the holder. The method of claim 1, The holder is an artificial lens, characterized in that using a silicone material or an acrylic material having transparency or opacity. The method of claim 1, An intraocular lens is characterized in that it further comprises a fixing member connected to a predetermined region on the outer peripheral surface of the holder. A lens unit; And A holder for accommodating the lens unit, The lens unit has a first groove in a predetermined front area of the lens unit, the holder has a second groove in a predetermined front area of the holder, Supporting the entire intraocular lens through the second groove, the refractive error correction method of the intraocular lens, characterized in that for rotating the lens unit through the first groove. The method of claim 18, Supporting the entire intraocular lens through the second groove, and rotating the lens unit through the first groove is characterized in that the hook-shaped mechanism is performed to the first groove and the second groove, respectively. Refractive error correction method of the intraocular lens. The method of claim 18, The holder includes a main body constituting the main body and a lens unit support extending from the main body, On the inner surface of the main body portion is formed a screw portion having a screw groove, And an outer circumferential surface of the lens unit is fixed to the screw groove of the screw unit to fix the refractive error of the intraocular lens. The method of claim 20, The lens unit is capable of rotating the spiral along the screw groove, Refractive error correction method of the intraocular lens, characterized in that for moving the lens portion in the vertical direction to the front or rear by the rotation of the lens. The method of claim 21, When the lens unit is rotated along the screw groove, the lens unit moves vertically to the front when the lens unit rotates clockwise, and when the lens unit rotates vertically to the rear side when the lens unit rotates counterclockwise, or when the lens unit rotates clockwise. The lens unit is moved in the vertical direction to the rear, and the lens unit to move in the vertical direction in the counterclockwise rotation of the lens, the refractive error correction method of the intraocular lens. The method of claim 21, Correcting hyperopia when the lens unit moves to the front, and correcting myopia when the lens unit moves to the rear. The method of claim 21, Correct the refractive error of ± 1.0D (Diopter) with respect to ± 0.3mm front or rear vertical movement of the lens unit by the spiral rotation of the lens unit, correct the hyperopia by the + direction (front) movement, and the-direction (Rear) Correction of the refractive error of the intraocular lens characterized in that the correction of myopia by movement. The method of claim 21, When the lens unit is spirally rotated along the screw groove, when the screw groove spiral is formed so that the lens unit is moved by 0.3 mm to the front or the rear when the lens unit is rotated 360 °, Correct the refractive errors of ± 0.25D, 0.50D, 0.75D for the ± 90 °, 180 °, and 270 ° rotations of the lens unit, correct the hyperopia by the + direction (front) movement, and the − direction ( Refraction error correction method of the intraocular lens, characterized in that for correcting myopia by moving. The method of claim 19, The process of supporting the entire intraocular lens through the second groove, and rotating the lens unit through the first groove, first make a small incision in the cornea and insert a hook-shaped instrument into the eye through the small incision. Then, the second lens groove of the intraocular lens, which is already inserted into the eyeball, supports the entire intraocular lens, and another lens-shaped instrument is inserted into the eyeball, and then the lens part of the intraocular lens is rotated by hooking the first groove. Refractive error correction method characterized in that the artificial lens.
KR1020080065126A 2008-07-04 2008-07-04 Intraocular lens and correction method of postoperative refractive error of intraocular lens KR20100004777A (en)

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