WO2012086797A1 - Intraocular lens-inserting instrument - Google Patents

Intraocular lens-inserting instrument Download PDF

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Publication number
WO2012086797A1
WO2012086797A1 PCT/JP2011/079902 JP2011079902W WO2012086797A1 WO 2012086797 A1 WO2012086797 A1 WO 2012086797A1 JP 2011079902 W JP2011079902 W JP 2011079902W WO 2012086797 A1 WO2012086797 A1 WO 2012086797A1
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WO
WIPO (PCT)
Prior art keywords
portion
intraocular lens
insertion
side
distal end
Prior art date
Application number
PCT/JP2011/079902
Other languages
French (fr)
Japanese (ja)
Inventor
雄二 名倉
Original Assignee
興和株式会社
Priority date (The priority date is an assumption and is not a legal conclusion. Google has not performed a legal analysis and makes no representation as to the accuracy of the date listed.)
Filing date
Publication date
Priority to JP2010286408 priority Critical
Priority to JP2010-286408 priority
Application filed by 興和株式会社 filed Critical 興和株式会社
Publication of WO2012086797A1 publication Critical patent/WO2012086797A1/en

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    • AHUMAN NECESSITIES
    • A61MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61FFILTERS 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
    • A61F2/00Filters 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
    • A61F2/02Prostheses implantable into the body
    • A61F2/14Eye parts, e.g. lenses, corneal implants; Implanting instruments specially adapted therefor; Artificial eyes
    • A61F2/16Intraocular lenses
    • A61F2/1662Instruments for inserting intraocular lenses into the eye
    • AHUMAN NECESSITIES
    • A61MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61FFILTERS 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
    • A61F2/00Filters 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
    • A61F2/02Prostheses implantable into the body
    • A61F2/14Eye parts, e.g. lenses, corneal implants; Implanting instruments specially adapted therefor; Artificial eyes
    • A61F2/16Intraocular lenses
    • A61F2/1662Instruments for inserting intraocular lenses into the eye
    • A61F2/167Instruments for inserting intraocular lenses into the eye with pushable plungers

Abstract

Provided is a technology that is not only capable of reducing the size of incisions necessary for inserting intraocular lenses but also is capable of making insertion and withdrawal of the insertion tube of the intraocular lens-inserting instrument smoother or more stable. A slit (10m) extending rearward in the axial direction from the tip opening (10j) is provided on the nozzle part (15) of the main nozzle body and an insertion-inhibiting part (10q), which controls the extent to which the nozzle part (15) is inserted into the eye, is provided at the portion (10p) corresponding to the maximum length of insertion into the eye (3) from the tip of the nozzle part (15) (also called the insertion limit below). The base end (10n) of the slit (10m) is disposed behind the shoulder (10l) of the insertion-inhibiting part (10q) in the axial direction.

Description

Intraocular lens insertion device

The present invention relates to an intraocular lens insertion device for inserting an intraocular lens into a patient's eyeball.

Conventionally, in surgery such as cataracts, an incision is made in the eye tissue such as the cornea (capsular membrane) and anterior lens capsule in the eyeball, and the lens in the capsule is removed and removed through this incision, An intraocular lens that replaces the crystalline lens is inserted into the eye through the incision and placed in the sac.

Particularly in recent years, when an intraocular lens is inserted into an eyeball through an incision, an insertion instrument as shown below is often used. That is, the distal end opening of the insertion tube portion provided at the distal end portion of the instrument body is inserted into the eyeball through the incision, and the distal end opening of the insertion tube portion is deformed in the instrument body. The intraocular lens is inserted into the eyeball by pushing it out from the part with a rod-shaped plunger. By using such an insertion device, the intraocular lens can be easily inserted into the eyeball using the incision formed for the removal of the crystalline lens. Astigmatism and infection can be suppressed.

As an intraocular lens insertion instrument, the distal end opening end surface of the distal end portion of the insertion tube portion is an inclined surface inclined with respect to a plane orthogonal to the central axis of the insertion tube portion, and the insertion tube portion of the distal end opening end surface is used. A tilt angle with respect to a plane perpendicular to the central axis of the tip is formed larger on the base end side than on the tip end side, and the peripheral edge portion of the tip opening end face has a sharp edge shape with a tapered outer peripheral surface. (For example, see Patent Document 1). Thereby, the protrusion of the intraocular lens can be suppressed and stable extrusion to the distal end edge portion of the insertion tube portion can be performed, and the insertion tube portion can be smoothly inserted into the incision.

By the way, in the above-mentioned intraocular lens insertion work, in order to reduce the burden on the patient at the time of surgery, it is required to further reduce the size of the incision, and the distal end of the insertion tube portion in the insertion instrument There is a need to make it smaller. In response to this requirement, proposals have been made to provide a slit in the insertion tube. According to this, when the intraocular lens is inserted into the incision, the outer diameter of the insertion tube portion is temporarily reduced by the slit, and when the intraocular lens passes through the insertion tube portion, The burden on the intraocular lens can be reduced by increasing the diameter of the insertion tube portion by the restoring force of the lens. (For example, see Patent Documents 2 to 6.)

However, when the insertion tube portion is provided with a slit, the insertion tube portion is broken by the restoring force of the intraocular lens when the intraocular lens passes through the insertion tube portion after the insertion tube portion is inserted into the incision. In some cases, unexpected deformation occurred. As a result, it may be difficult to smoothly remove the insertion tube from the incision. In addition, even when the insertion tube portion is inserted into the incision, the proximal end portion of the slit is deformed, and there is a possibility that the eyeball is damaged when the deformed proximal end portion passes through the incision.

In order to prevent the above-mentioned inconvenience, it is conceivable to increase the length of the slit in order to prevent the base end of the slit from passing through the incision. As a result, the length of the portion itself is increased, and as a result, there is a disadvantage that the insertion tube portion is inserted into the eyeball more than necessary.

JP 2009-160153 A JP 2009-240728 A International Publication No. WO2005 / 070341 Pamphlet Japanese Unexamined Patent Publication No. 63-197453 Japanese Patent No. 3861138 European Patent Application No. 0519282

The present invention has been devised in view of the above-mentioned problems of the prior art, and its purpose is to make it possible to further reduce the size of the incision necessary for the insertion work of the intraocular lens. Another object of the present invention is to provide a technique capable of smoothing or stabilizing the insertion operation and the extraction operation of the insertion tube portion of the intraocular lens insertion device.

In the present invention, the insertion tube portion of the instrument body is provided with a slit extending rearward in the axial direction from the distal end opening, and the insertion amount of the insertion tube portion into the eye is restricted to a predetermined distance from the distal end of the insertion tube portion. A step-shaped insertion restricting portion is provided, and the rear end of the slit is arranged on the rear side in the axial direction from the step-shaped portion of the insertion restricting portion.

More specifically, an instrument body having a cylindrical shape (a cylindrical shape or a substantially cylindrical shape that is substantially a cylindrical shape) that accommodates an intraocular lens;
A pushing member that moves the intraocular lens forward in the axial direction by being inserted into the instrument body from the rear in the axial direction,
The instrument body has an insertion tube portion provided at the distal end portion and reduced in outer diameter and inner diameter, and a distal end opening portion opened at the distal end of the insertion tube portion,
An insertion device for an intraocular lens that is inserted into the eye by being released from the distal end opening after being deformed small by passing the insertion tube through the intraocular lens by the push member,
The instrument body is
A slit provided in the insertion tube portion so as to extend axially rearward from the tip opening,
A step-shaped insertion restricting portion that is provided at a predetermined distance from the distal end of the insertion tubular portion and restricts the amount of insertion of the insertion tubular portion into the eye; and
The rear end of the slit is disposed on the rear side in the axial direction from the stepped portion of the insertion restricting portion.

According to this, first, since the slit is formed in the distal end side of the insertion restricting portion, that is, in the entire region of the insertion tube portion inserted into the eyeball, the diameter of the insertion tube portion can be changed with a high degree of freedom. . Accordingly, the insertion tube portion can be inserted into the eyeball from a smaller incision. Further, when the intraocular lens passes through the insertion tube portion, the diameter of the insertion tube portion is appropriately enlarged due to the restoring force of the intraocular lens, so that the intraocular lens is inadvertently ejected from the distal end opening portion by the restoring force. Can also be suppressed. Furthermore, since the length of the slit is long, it is possible to suppress local action of the restoring force of the intraocular lens when the intraocular lens is inserted, and it is possible to suppress damage to the slit itself.

Also, according to this, since the proximal end portion, which is the rear end of the slit, is arranged behind the stepped portion of the insertion restricting portion, it does not enter the eyeball from the incision. Therefore, even if the rear end of the slit is deformed, it is possible to prevent the eyeball from being damaged or the insertion tube portion from being inserted and pulled out. In the above description, the predetermined distance indicates the length to be inserted into the eyeball from the incision at the time of inserting the intraocular lens, or the upper limit value thereof.

Further, in the present invention, the tip opening is provided so as to form an inclined surface inclined with respect to a surface orthogonal to the central axis of the insertion tube portion,
The inclined surface may be inclined so that the front side in the optical axis direction of the intraocular lens at the distal end opening is closer to the front side of the insertion tube portion than the rear side in the optical axis direction. In the present invention, the slit may be formed on the opposite side of the most distal end portion of the distal end opening as viewed from the distal end side of the insertion tube portion.

Here, normally, when the intraocular lens is moved by the pushing member and passed through the insertion tube portion, it is folded and deformed so as to be convex forward in the optical axis direction. In the present invention, since the slit is formed on the opposite side of the most distal end portion of the distal end opening as viewed from the distal end side of the insertion tube portion, it becomes difficult for the central portion of the intraocular lens to contact the slit. Therefore, it can suppress that the center part of an intraocular lens is damaged by a slit, or that an intraocular lens protrudes from a slit.

In the present invention, the instrument body is
When the intraocular lens is moved by the push-out member and passed through the insertion tube portion, the intraocular lens is viewed from the distal end side of the insertion tube portion toward the most distal portion of the distal end opening. You may make it further have a deformation | transformation auxiliary means to fold and deform | transform so that it may become convex.

That is, in the method in which the intraocular lens is simply moved by the pushing member and passed through the insertion tube portion, the intraocular lens may be folded and deformed so as to be convex rearward in the optical axis direction depending on the situation. In that case, it is difficult to normally push out the intraocular lens from the distal end opening, and the intraocular lens may be damaged by the slit. On the other hand, in the present invention, when the deformation assisting means is seen from the distal end side of the insertion tube portion, the intraocular lens is convex toward the most distal portion side of the distal end opening, that is, the front side of the optical axis. Collapse and deform.

Accordingly, the intraocular lens can be more reliably folded and deformed so as to be convex toward the front of the optical axis, and the center of the intraocular lens can be more reliably damaged by the slit, or the intraocular lens can be removed from the slit. It can suppress that it protrudes.

Further, in the present invention, the instrument main body has a reduced diameter portion that is provided behind the insertion tube portion and decreases in a substantially taper shape as the inner diameter of the instrument main body goes to the distal end side.
The deformation assisting means may have a multi-step taper structure in which the taper has a steeper inclination angle on the front end side than on the rear side in the reduced diameter portion.

Here, as a result of intensive research by the inventor, when the insertion tube portion is passed through the intraocular lens, the inner diameter of the instrument main body is reduced in a taper shape toward the distal end side, and the taper is further reduced. When the inclination angle is steeper on the tip side than on the rear side in the reduced diameter portion, the intraocular lens can be folded and deformed so as to be convex toward the optical axis front side. It became clear. Therefore, in the present invention, the instrument body has a reduced diameter portion that is provided behind the insertion tube portion and decreases in a substantially taper shape as the inner diameter of the instrument body goes to the distal end side. The taper has a multi-taper structure in which the inclination angle of the taper is steeper on the tip side than on the rear side in the reduced diameter portion.

As a result, the intraocular lens can be more reliably folded and deformed so as to be convex toward the front side of the optical axis, and the center of the intraocular lens can be more reliably damaged by the slit, or from the slit to the intraocular lens. Can be prevented from protruding.

Further, in the present invention, the instrument main body has a reduced diameter portion that is provided behind the insertion tube portion and decreases in a substantially taper shape as the inner diameter of the instrument main body goes to the distal end side.
The deformation assisting means may be a peripheral support guide that is provided on the inner wall of the instrument body at the reduced diameter portion and supports the peripheral portion of the intraocular lens from the front side in the optical axis direction of the intraocular lens. .

Again, as a result of the inventor's earnest research, when the insertion tube portion is passed through the intraocular lens, the inner diameter of the instrument main body is reduced to a taper shape as it goes to the distal end side. By supporting the peripheral part of the intraocular lens from the front side in the optical axis direction (the most advanced part side of the tip opening), the intraocular lens is more reliably folded so as to be convex toward the front side in the optical axis direction. It became clear that it could be deformed. Therefore, in the present invention, the instrument main body has a reduced diameter portion that is provided behind the insertion tube portion and decreases in a substantially taper shape as the inner diameter of the instrument main body goes to the distal end side. The peripheral portion support guide is provided on the inner wall of the instrument main body at the diameter portion and supports the peripheral portion of the intraocular lens from the front side in the optical axis direction of the intraocular lens.

This also makes it possible to fold and deform the intraocular lens so that it protrudes forward in the optical axis direction, and more reliably, the center of the intraocular lens is damaged by the slit, or from the slit to the eye. It can suppress that an inner lens protrudes.

In the present invention, the insertion restricting portion is provided on the rear side of the insertion cylindrical portion and on the distal end side of the reduced diameter portion, and has a cylindrical large diameter having an outer diameter larger than that of the insertion cylindrical portion. Department,
A rear end of the slit is disposed on a side surface of the large diameter portion, and a small diameter portion that is a surface extending from the side surface of the insertion tube portion is formed around the rear end of the slit in the large diameter portion. You may make it do.

According to this, in the insertion restricting portion, a step portion whose outer diameter increases over substantially the entire circumference of the insertion tube portion is formed, and it is more reliably suppressed that the instrument body is excessively inserted into the eyeball. Is possible. Further, the rear end of the slit is disposed on the side surface of the large diameter portion, and the side surface of the insertion tube portion is extended around the rear end of the slit on the side surface of the large diameter portion (that is, the same diameter as the insertion tube portion). ) Since the small-diameter portion is formed, the degree of freedom of deformation at the rear end of the slit can be ensured.

As a result, the insertion tube portion can be smoothly deformed with a higher degree of freedom, so the length or diameter of the necessary incision can be reduced, and the insertion tube portion can be inserted and withdrawn more smoothly. It becomes possible to do.

Further, the present invention may be a preset insertion system for an intraocular lens that is distributed in a state where the intraocular lens is accommodated in advance in any of the intraocular lens insertion devices described above.

In addition, about the means to solve the subject of the above-mentioned this invention, it can use combining as much as possible.

According to the present invention, the size of the incision required for the insertion operation of the intraocular lens can be further reduced, and the insertion operation and the extraction operation of the insertion device for the intraocular lens can be more smoothly or stabilized. Can do.

It is a figure which shows schematic structure of the insertion instrument of the intraocular lens in the Example of this invention. It is a figure which shows schematic structure of the intraocular lens in the Example of this invention. It is a figure which shows schematic structure of the nozzle main body in the Example of this invention. It is a figure which shows schematic structure of the positioning member in the Example of this invention. It is a figure which shows schematic structure of the plunger in the Example of this invention. It is the figure which looked at the conventional nozzle part vicinity from the up-down direction lower side. It is a figure for demonstrating the effect | action of the slit of a nozzle part. It is the figure which looked at the nozzle part vicinity in Example 1 of this invention from the up-down direction lower side. It is sectional drawing seen from the back direction in three places near the nozzle part in Example 1 of this invention. It is the figure which looked at the nozzle part vicinity in Example 2 of this invention from the up-down direction lower side. It is the figure which looked at the nozzle part vicinity in Example 3 of this invention from the up-down direction lower side, and the figure which shows the effect | action of a slit. It is the 2nd aspect of the figure which looked at the nozzle part vicinity in Example 3 of this invention from the up-down direction lower side.

Hereinafter, embodiments of the present invention will be described with reference to the drawings.

<Example 1>
FIG. 1 shows a schematic configuration of an intraocular lens insertion device 1 (hereinafter also simply referred to as an insertion device 1) in the present embodiment. 1A is a plan view, and FIG. 1B is a side view. The insertion instrument 1 includes a nozzle body 10 as an instrument body formed in a cylindrical shape having a substantially rectangular cross section. One side of the nozzle body 10 has a large opening (hereinafter, the side with the large opening is referred to as a rear end portion 10b), and a nozzle portion 15 as an insertion tube portion with a narrow diameter is provided at the other end portion. In addition, a tip portion 10 a that opens obliquely is provided at the end of the nozzle portion 15. The insertion instrument 1 includes a plunger 30 as an extrusion member that is inserted into the nozzle body 10 and can reciprocate. In the following, the direction from the front end portion 10a to the rear end portion 10b of the nozzle body 10 is the front-rear direction, and in FIG. And

In the vicinity of the rear end portion 10b of the nozzle body 10, there is integrally provided a holding portion 11 that protrudes in a plate shape and hooks a finger when the user pushes the plunger 30 toward the front end side of the nozzle body 10. A stage portion 12 for setting the intraocular lens 2 is provided on the rear end side of the nozzle portion 15 in the nozzle body 10. The stage portion 12 is configured such that the upper side of the nozzle body 10 (the front side perpendicular to the paper surface in FIG. 1A) is opened by opening the stage lid portion 13. In addition, a positioning member 50 is attached to the stage portion 12 from the lower side of the nozzle body 10 (the back side perpendicular to the paper surface in FIG. 1A). By this positioning member 50, the intraocular lens 2 is stably held in the stage portion 12 before use (during transportation).

That is, in the insertion instrument 1, the intraocular lens 2 is set on the stage unit 12 in a state where the stage lid unit 13 is opened and the positioning member 50 is attached to the stage unit 12 at the time of manufacture. Then, after the stage lid 13 is closed, it is shipped and sold, and the user removes the positioning member 50 while the stage lid 13 is closed. Then, a viscoelastic substance is injected from an injection port (not shown) provided in the stage lid 13, and then the plunger 30 is pushed into the distal end side of the nozzle body 10, thereby pressing the intraocular lens 2 with the plunger 30, The intraocular lens 2 is pushed out from the part 10a. In addition, the material of the nozzle body 10, the plunger 30, and the positioning member 50 in the insertion instrument 1 is formed of a resin such as polypropylene. Polypropylene is a material with a proven track record in medical equipment and high reliability such as chemical resistance.

FIG. 2 is a diagram showing a schematic configuration of the intraocular lens 2. FIG. 2A is a plan view, more specifically, a view seen from the front side of the optical axis. FIG. 2B is a side view, more specifically, a view seen from a direction perpendicular to the optical axis. The intraocular lens 2 is formed of a lens body 2a having a predetermined refractive power, and two beard-shaped support portions 2b, 2b that are provided on the lens body 2a and hold the lens body 2a in the eyeball. ing. The lens body 2a is made of a flexible resin material.

FIG. 3 shows a plan view of the nozzle body 10. As described above, in the nozzle body 10, the intraocular lens 2 is set on the stage unit 12. In this state, the intraocular lens 2 is pushed out from the distal end portion 10a by being pressed by the plunger 30. The nozzle body 10 is provided with a through-hole 10c whose cross-sectional shape changes according to a change in the outer shape of the nozzle body 10. When the intraocular lens 2 is pushed out, the intraocular lens 2 is deformed in accordance with a change in the cross-sectional shape of the through hole 10c in the nozzle body 10 and easily enters an incision formed in the patient's eyeball. It will be extruded after being transformed into.

A stage groove 12 a having a width slightly larger than the diameter of the lens body 2 a of the intraocular lens 2 is formed in the stage portion 12. The dimension in the front-rear direction of the stage groove 12 a is set to be larger than the maximum width dimension including the support portions 2 b and 2 b extending on both sides of the intraocular lens 2. A set surface 12b is formed by the bottom surface of the stage groove 12a. The vertical position of the set surface 12b (position perpendicular to the paper surface of FIG. 3) is above the height position of the bottom surface of the through hole 10c on the rear side of the stage portion 12 in the nozzle body 10 (perpendicular to the paper surface of FIG. 3). The set surface 12b and the bottom surface of the through hole 10c are connected by a bottom slope 10d.

The stage portion 12 and the stage lid portion 13 are integrally formed. The stage lid portion 13 has the same longitudinal dimension as the stage portion 12. The stage lid portion 13 is connected by a thin plate-like connecting portion 14 formed by extending the side surface of the stage portion 12 to the stage lid portion 13 side. The connecting portion 14 is formed to be bendable at the center portion, and the stage lid portion 13 can be closed by overlapping the stage portion 12 from above by bending the connecting portion 14.

In the stage lid 13, ribs 13 a and 13 b are provided on the surface facing the set surface 12 b when the lid is closed in order to reinforce the stage lid 13 and stabilize the position of the intraocular lens 2. A guide protrusion 13 c is provided as a guide for the plunger 30.

A positioning member 50 is detachably provided below the set surface 12b of the stage portion 12. FIG. 4 shows a schematic configuration of the positioning member 50. 4A shows a plan view, and FIG. 4B shows a side view. In FIG. 4, the left-right direction corresponds to the front-rear direction of the present embodiment, the up-down direction in FIG. 4A corresponds to the left-right direction of the present embodiment, and the up-down direction in FIG. The positioning member 50 is configured as a separate body from the nozzle body 10, and has a structure in which a pair of side wall portions 51 and 51 are connected by a connecting portion 52. At the lower ends of the respective side wall portions 51, holding portions 53, 53 extending outward and extending are formed.

Further, a pair of first mounting portions 54 and 54 are formed on the upper end portions of the respective side wall portions 51 and 51 so that the shape seen from above is an arc shape and protrudes upward. Further, first positioning portions 55, 55 are formed to protrude from the outer peripheral side of the upper end surface of the first placement portion 54. The distance between the inner diameters of the first positioning portion 55 is set to be slightly larger than the diameter dimension of the lens body 2 a of the intraocular lens 2.

Further, a pair of second placement portions 56 and 56 are formed at both ends of the connecting portion 52 in the front-rear direction, and the shape seen from above is a rectangular shape and protrudes upward. The height of the upper surface of the second placement portion 56 is equal to the height of the upper end surface of the first placement portion 54. Furthermore, second positioning portions 57 and 57 are formed on the outer surface of the second placement portions 56 and 56, and the second positioning portions 57 and 57 project further upward over the entire left and right direction of the second placement portions 56 and 56. ing. The separation between the insides of the second positioning portions 57 is set to be slightly larger than the diameter of the lens body 2a of the intraocular lens 2. In addition, as shown in FIG. 4B, locking claws 58 and 58 that slightly protrude in the front-rear direction are formed at the upper end portion of the second placement portion 56 over the entire left-right direction.

In this embodiment, the positioning member 50 is assembled from below the set surface 12b of the nozzle body 10. The set surface 12b of the nozzle body 10 is formed with four set surface through holes 12c penetrating the set surface 12b in the thickness direction. The outer shape of the set surface through-hole 12c is a substantially similar shape that is slightly larger than the shape of the first placement portion 54 and the second placement portion 56 of the positioning member 50 as viewed from above. When the positioning member 50 is attached to the nozzle body 10, the first placement portions 54 and 54 and the second placement portions 56 and 56 are inserted into the set surface through hole 12c from the lower side of the set surface 12b. , Protruding above the set surface 12b.

At that time, the locking claws 58, 58 provided on the second placement portions 56, 56 project to the set surface 12b through the set surface through hole 12c and are locked to the upper surface of the set surface 12b. Thus, the positioning member 50 is assembled from the lower side of the nozzle body 10, and the first placement portions 54 and 54 and the second placement portions 56 and 56 are fixed in a state of protruding from the set surface 12b. When the intraocular lens 2 is set on the setting surface 12b, the bottom surface of the outer peripheral portion of the lens body 2a is placed on the upper surfaces of the first placement portions 54 and 54 and the second placement portions 56 and 56. The Further, the position of the lens body 2a is restricted in the front-rear and left-right directions by the first positioning portions 55, 55 and the second positioning portions 57, 57.

FIG. 5 shows a schematic configuration of the plunger 30. FIG. 5A is a plan view, and FIG. 5B is a side view. The plunger 30 has a length in the front-rear direction that is slightly larger than the nozzle body 10. And it forms from the action part 31 of the front end side based on a column shape, and the insertion part 32 of the rear end side based on a rectangular rod shape. And the action part 31 is comprised including the cylindrical part 31a formed in the column shape, and the thin plate-shaped flat part 31b extended in the left-right direction of the cylindrical part 31a.

A notch 31 c is formed at the tip of the action part 31. As can be seen from FIG. 5A, the cutout portion 31 c is formed in a groove shape that opens upward in the action portion 31 and penetrates in the left-right direction. Further, as can be seen from FIG. 5B, the end surface on the front end side of the cutout portion 31 c is formed as an inclined surface that goes upward as it goes to the front end side of the action portion 31.

On the other hand, the insertion portion 32 has a substantially H-shaped cross section as a whole, and the horizontal and vertical dimensions thereof are set slightly smaller than the through hole 10c of the nozzle body 10. In addition, a disc-shaped pressing plate portion 33 is formed at the rear end of the insertion portion 32 so as to spread in the vertical and horizontal directions.

A claw portion 32 a that protrudes toward the upper side of the insertion portion 32 and can be moved up and down by the elasticity of the material of the plunger 30 is formed at the tip side of the insertion portion 32 in the front-rear direction center. When the plunger 30 is inserted into the nozzle body 10, the locking hole 10e provided in the thickness direction on the upper surface of the nozzle body 10 and the claw portion 32a engage with each other, whereby the nozzle in the initial state is engaged. A relative position between the main body 10 and the plunger 30 is determined. The claw portion 32a and the locking hole 10e are formed at the positions where the tip of the action portion 31 is located behind the lens body 2a of the intraocular lens 2 set on the stage portion 12 in the engaged state. It is set so that the notch 31c can support the support part 2b behind 2a from below.

Before the insertion instrument 1 configured as described above is used, the plunger 30 is inserted into the nozzle body 10 and disposed at the initial position. Further, as described above, the positioning member 50 is attached to the stage unit 12 from below the set surface 12b. Thereby, the 1st mounting part 54 and the 2nd mounting part 56 of the positioning member 50 are hold | maintained in the state protruded to the set surface 12b.

Further, the lens body 2a of the intraocular lens 2 is placed and positioned on the upper end surfaces of the first placement part 54 and the second placement part 56 with the support parts 2b and 2b facing the front-rear direction of the nozzle body 10. The In this state, since the outer peripheral portion of the lens body 2a is in contact with the first placement portion 54 and the second placement portion 56, the central portion of the intraocular lens 2 is supported in an unloaded state. In this state, the support portion 2 b of the intraocular lens 2 is supported by the bottom surface of the notch portion 31 c of the plunger 30.

In this state, the second mounting portion 56 constitutes a stopper that prevents the plunger 30 from moving forward. The plunger 30 cannot advance unless the positioning member 50 is removed from the nozzle body 10. It is in a state.

When the intraocular lens 2 is inserted into the patient's eyeball using the insertion instrument 1, first, the positioning member 50 is removed from the nozzle body 10. As a result, the first placement portion 54 and the second placement portion 56 that have supported the lens body 2a of the intraocular lens 2 are retracted from the set surface 12b, and the intraocular lens 2 is placed on the set surface 12b. The Since the set surface 12b is a flat surface, the intraocular lens 2 can be stably placed, and the width dimension of the stage groove 12a is slightly smaller than the diameter dimension of the lens body 2a of the intraocular lens 2. Since the degree is large, rotation of the intraocular lens 2 in the circumferential direction on the set surface 12b is also suppressed.

Subsequently, the nozzle portion 15 is inserted from the distal end portion 10a side of the nozzle body 10 into the incision provided in the eye tissue. In this state, the pressing plate portion 33 of the plunger 30 is pushed into the tip end side of the nozzle body 10. Thereby, the front-end | tip of the action part 31 of the plunger 30 contact | abuts to the lens body 2a outer periphery of the intraocular lens 2 set to the setting surface 12a, and the intraocular lens 2 is guided toward the front-end | tip part 10a by the plunger 30.

Next, the configuration in the vicinity of the nozzle portion 15 of the conventional nozzle body 10 will be described in detail with reference to FIG. FIG. 6B shows a view of the vicinity of the nozzle portion 15 in the conventional nozzle body 10 as seen from the lower side in the vertical direction. FIG. 6A is a view of the nozzle portion 15 as viewed from the tip side. The outer shape of the nozzle body 10 as a whole has a shape that gradually tapers from the stage portion 12 side toward the nozzle portion 15 side. In the through hole 10c, a taper portion 10f is formed as a reduced diameter portion whose cross-sectional area is gradually reduced. The taper portion 10f is configured such that the cross-sectional area is reduced by reducing the width dimension of the bottom surface and the top surface toward the nozzle portion 15 side. Here, the bottom surface of the rear end portion of the taper portion 10f is formed with an inclined surface 10g inclined so as to rise upward toward the tip end side, and a step is provided by the inclined surface 10g.

Near the taper portion 10f on the bottom surface of the through-hole 10c, a pair of introduction protrusions 10h extending in the front-rear direction of the nozzle body 10 is formed with the center of the bottom surface in the left-right direction. The introduction protrusion 10h is provided in the longitudinal direction of the axially inclined surface 10g, and is formed in a linear shape that protrudes slightly upward from the bottom surface on the rear end side of the taper portion 10f and extends in parallel with each other. ing. Here, the front end portion of the introduction protrusion 10h formed on the inclined surface 10g gradually becomes higher as the inclined surface 10g goes to the tip side so that the front end portion of the introduction surface 10g has the same height at the front end portion of the inclined surface 10g. Is formed. The separation distance between the introduction protrusions 10 h is slightly larger than the width of the action portion 31 of the plunger 30.

The nozzle portion 15 is formed on the tip end side of the taper portion 10f in the through hole 10c. In the nozzle portion 15, the through hole 10c is formed to extend straight with a substantially constant cross-sectional area. ing. The through hole 10c is opened at the tip 10a, and a tip opening 10j is formed. The tip opening portion 10j is formed by cutting the nozzle portion 15 in the nozzle body 10 obliquely so as to go to the rear side as it goes downward (front side in FIG. 6). That is, the upper end portion 100 at the upper end of the distal end portion 10a extends forward from the lower end portion 101 at the lower end.

Further, the nozzle portion 15 is formed with a slit 10m extending rearward from the tip lower end portion 101 of the tip opening 10j. The slit 10m in the present embodiment is formed to extend rearward from the tip opening 10j with substantially the same width.

FIG. 7 shows the operation of the slit 10m. First, in the state before the intraocular lens insertion operation, as shown in FIG. 7A, no load is applied to the nozzle portion 15, and the nozzle portion 15 extends straight as described above. It has a cylindrical shape. Next, FIG. 7 (b) shows a state in which the nozzle portion 15 is inserted into the incision 3 a formed in the eyeball 3. Here, the diameter of the incision 3 a is set slightly smaller than the diameter of the nozzle portion 15. In this state, when the nozzle portion 15 is inserted into the incision 3a, a load in the direction of reducing the incision 3a acts on the nozzle portion 15 by the eyeball 3. Accordingly, the nozzle portion 15 is deformed so that the width of the slit 10m particularly on the front end side becomes narrow. Due to such an action, the nozzle portion 15 can be inserted into the smaller incision 3a.

Next, FIG. 7C shows a state when the intraocular lens 2 is inserted into the eyeball 3 through the nozzle portion 15. As shown in FIG. 7C, when the intraocular lens 2 passes through the nozzle unit 15, the nozzle unit 15 is restored by the restoring force of the intraocular lens 2 that is slightly deformed by the taper unit 10f of the through hole 10c. The shape returns to the direction before deformation against the load from the incision 3a.

Thus, by forming the slit 10 m in the nozzle portion 15, it is possible to insert the intraocular lens 2 using a smaller incision, and when the intraocular lens 2 passes through the nozzle portion 15. Since the nozzle portion 15 is deformed in the expanding direction, the intraocular lens 2 can be prevented from jumping out from the distal end opening portion 10j by its own restoring force, and the intraocular lens 2 can be inserted more smoothly.

However, when the slit 10m as described above is formed in the nozzle portion 15, the slit 10m itself is broken by the restoring force of the deformed intraocular lens 2 during the insertion operation, causing unexpected deformation in the nozzle portion 15. After the insertion of the intraocular lens 2, it may be difficult to smoothly pull out the nozzle portion 15 from the eyeball 3. Further, when the nozzle portion 15 is inserted into the incision 3a, as can be seen from FIG. 7B, the base end portion 10n as the rear end of the slit 10m is deformed, and the nozzle portion 15 is inserted into the slit 10m. When the proximal end portion 10n is inserted into the eyeball 3, the deformed proximal end portion 10n may damage the eyeball. Further, when the length of the slit 10m is increased in order to suppress such inconvenience, the length of the nozzle portion 15 is inevitably increased, and as a result, the nozzle portion 15 on the eyeball 3 exceeds the required amount. There was an inconvenience of inserting.

On the other hand, FIG. 8 shows a view of the vicinity of the nozzle portion 15 according to the present embodiment. As can be seen from FIG. 8, in this embodiment, the slit 10 m is rearward of a portion corresponding to the maximum length to be inserted into the eyeball 3 from the tip of the nozzle portion 15 (hereinafter also referred to as an insertion limit point) 10 p. The insertion prohibiting portion 10q is formed by increasing the outer shape of the portion on the rear side of the insertion limit point 10p in the nozzle portion 15.

According to this, it is possible to more surely suppress the excessive insertion of the nozzle portion 15 into the eyeball 3 first. Even if the proximal end portion 10n of the slit 10m is deformed due to the deformation of the nozzle portion 15 when the nozzle portion 15 is inserted into the incision 3a or when the intraocular lens 2 passes, the deformation of the nozzle portion 15 is caused by this deformation. It is possible to suppress inconveniences in extracting from the incision 3a or damaging the eyeball 3. The insertion prohibiting portion 10q corresponds to an insertion restricting portion and a large diameter portion in the present embodiment.

In addition, the insertion prohibition part 10q in a present Example has the taper-shaped step part 10l in the front end side. Thereby, when inserting the nozzle part 15 in the incision 3a, it can suppress that the insertion prohibition part 10q strongly interferes with the eyeball 3, and the eyeball 3 is damaged. It is desirable that the diameter of the insertion prohibition portion 10q is larger than the length (or diameter) of the incision 3a. Thereby, it can suppress more reliably inserting the nozzle part 15 in the eyeball 3 more reliably. Further, it is desirable that the taper angle of the step portion 101 is a steep angle of 45 degrees or more, for example. Thereby, it can suppress more reliably that the nozzle part 15 will be inserted excessively in the incisional wound 3a.

Further, as shown in FIG. 8, the through hole 10c in the present embodiment has a first taper in which the width dimension of the bottom surface and the top surface is gradually reduced from the stage portion 12 side to the nozzle portion 15 side. And a second taper portion 10s in which the width dimension of the bottom surface and the top surface is steeperly smaller than that of the first taper portion 10r as it goes from the stage portion 12 side to the nozzle portion 15 side. It has been. In this way, the taper part is divided into two stages, and the lens body 2a of the intraocular lens 2 is passed by passing the intraocular lens 2 first through the gentle taper part and then through the steep taper part. It can be deformed gently at the beginning and abruptly thereafter. Thus, the intraocular lens 2 can be more reliably folded and deformed in the direction shown in FIG. 8A, that is, in the direction in which the intraocular lens body 2a is convex on the side opposite to the slit 10m. Further, the support portion 2b on the front side of the intraocular lens 2 is reliably bent backward by the action of the second tapered portion 10s. Therefore, since the deformation of the intraocular lens 2 is performed more reliably in both the lens body 2a and the support portion 2b, the operation when releasing the intraocular lens 2 from the nozzle portion 15 is stable, and the intraocular lens 2 can be easily inserted into the eyeball 3. The lens 2 can be inserted.

Then, when the intraocular lens 2 is deformed, the outer periphery thereof can be disposed on the slit 10m side, and the intraocular lens 2 is damaged by the slit 10m, or the intraocular lens 2 protrudes from the slit 10m. Inconvenience such as can be suppressed. The first taper portion 10r and the second taper portion 10s correspond to a multi-step taper structure and deformation assisting means in this embodiment.

FIG. 9 shows a cross-sectional view of the syringe 10 in the present embodiment. 9A shows the AA cross section in FIG. 8, FIG. 9B shows the BB cross section in FIG. 8, and FIG. 9C shows the CC cross section in FIG. Each sectional view also shows the shape of the lens body 2a of the intraocular lens 2 when passing through the section. As can be seen from FIG. 9 (a), in this embodiment, at least the guides 10t, 10t that contact the left and right outer peripheral portions of the lens body 2a from above in the through hole 10c corresponding to the first taper portion 10r. Is formed.

At least when the intraocular lens 2 passes through the first taper portion 10r, the guides 10t and 10t guide the left and right outer peripheral portions of the lens body 2a so as not to be displaced upward, so that the intraocular lens 2 is 9 can be prevented from being deformed so as to protrude downward in FIG. That is, the lens body 2a can be more reliably deformed so as to be convex upward in FIG. 9, as shown in FIGS. 9B and 9C. The guides 10t and 10t correspond to a peripheral portion support guide and deformation assisting means in this embodiment.

In this embodiment, when the diameter of the through hole 10c is reduced, a two-step taper structure of the first taper portion 10r and the second taper portion 10s is adopted. Is not limited to two stages. Three or more taper portions may be used, or a taper angle may be changed smoothly in a curved shape.

In addition, the insertion prohibiting portion 10q in the present embodiment has a cylindrical shape larger in diameter than the nozzle portion 15, but the shape of the insertion prohibiting portion 10q is not limited thereto. Other shapes may be used as long as the nozzle portion 15 can be prevented from being inserted into the incision 3a beyond the insertion limit point. For example, it is good also as a stopper shape which a part of outer periphery of the nozzle part 15 protruded to the outer peripheral side. Further, the shape of the stepped portion 101 is not necessarily a tapered shape, and may be a curved surface having a circular longitudinal cross section, or another curved surface shape may be adopted. A step portion having a rectangular longitudinal section may be adopted.

<Example 2>
Next, a second embodiment of the present invention will be described. In this embodiment, the base end portion of the slit of the nozzle portion is located on the side surface of the insertion prohibition portion having a diameter larger than that of the nozzle portion, but an area having the same thickness as the nozzle portion is formed around the base end portion of the slit. The provided example will be described.

FIG. 10 shows a view of the vicinity of the nozzle portion 15 according to this embodiment as viewed from the lower side in the vertical direction. The slit 20m in the present embodiment is narrower than the slit 10m in the first embodiment. Further, a nozzle extension portion 20t as a small diameter portion having the same diameter as the nozzle portion 15 is formed around the base end portion 20n of the slit 20m in the insertion prohibition portion 10q. Other configurations are substantially the same as those of the first embodiment.

According to this configuration, the degree of freedom of deformation at the base end portion 20n of the slit 20m can be maintained relatively high. Therefore, the nozzle part 15 can be smoothly deformed with a higher degree of freedom. Further, since the insertion prohibiting portion 10q is provided around the nozzle extension portion 20t as in the first embodiment, the nozzle portion 15 can be prevented from being inserted too deeply into the eyeball. Although the slit 20m in the present embodiment is narrower than the slit 10m in the first embodiment, the width of the slit itself may be equal to or greater than that of the first embodiment.

<Example 3>
Next, a third embodiment of the present invention will be described. In this embodiment, an example will be described in which the slit shape of the nozzle portion is a V-shape that becomes wider toward the tip side.

FIG. 11 shows a view of the vicinity of the nozzle portion 15 according to the present embodiment as seen from the lower side in the vertical direction. The slit 30m in the present embodiment has the narrowest width at the base end 30n, and has a V-shape that increases in width toward the distal end opening 10j. A nozzle extension portion 30t having the same diameter as the nozzle portion 15 is formed around the base end portion 30n of the slit 30m in the insertion prohibition portion 10q.

According to this configuration, the degree of freedom of deformation at the base end portion 30n of the slit 30m becomes relatively high, and the deformable amount of the nozzle portion 15 increases as it goes to the tip end side of the nozzle portion 15. Then, as shown in FIG. 11 (b), when the nozzle portion 15 is inserted into the incision 3a of the eyeball 3, the distal end side of the nozzle portion 15 can be made thinner by deformation, and the shorter or smaller diameter can be obtained. It is possible to perform an intraocular lens insertion operation with the incision 3a. Further, when the nozzle portion 15 is gradually pushed into the incision 3a when the intraocular lens is inserted, the nozzle portion 15 is also gradually deformed and thinned, so that it can easily cope with the short or small-diameter incision 3a. .

FIG. 12 shows a second mode in the present embodiment. In the embodiment shown in FIG. 12, the slit 40m is formed in a V shape continuously from the portion of the tip opening 40j having the substantially maximum width. Even with such a configuration, the distal end side of the nozzle portion 15 can be made thinner by deformation, and the intraocular lens can be inserted with a shorter or smaller diameter incision 3a. 12, the length L1 from the tip of the nozzle 15 to the insertion limit point 10p is 4 to 7 mm, the length L2 of the nozzle extension 40t is 0.5 to 2 mm, the diameter D1 of the nozzle 15 is 2 to 3 mm, The diameter D2 of the insertion prohibition portion 10q is 2.5 to 3.5 mm (= D1 + 0.5 to 1 mm).

In addition, about the shape of the slit in a present Example, it can change suitably and is not limited to the shape mentioned above. Moreover, the above is an example about the value of L1, L2, D1, and D2, and you may employ | adopt another dimension.

Each embodiment has described a so-called preset system in which an intraocular lens is loaded in advance on an intraocular lens insertion device, but the present invention is not limited to this, and the intraocular lens insertion device and intraocular lens are not limited thereto. The present invention can also be applied to a so-called separate inserter for storing lenses separately and loading the intraocular lens immediately before the insertion into the eyeball. Similarly, in each embodiment, the intraocular lens to be inserted has been described as an example using a so-called three-piece type in which the lens body (optical part) and the support part are made of different materials, but the lens body (optical part) The present invention can also be applied to an insertion instrument for inserting a so-called one-piece intraocular lens in which the support part is integrally molded.

DESCRIPTION OF SYMBOLS 1 ... Insertion instrument 2 ... Intraocular lens 10 ... Instrument main body 10a ... Tip part 10c ... Through-hole 10j ... Tip opening part 10l ... Step part 10m, 20m, 30m, 40 m: slits 10 n, 20 n, 30 n, 40 n: base end portion 10 p: insertion limit point 10 r: first taper portion 10 s: second taper portion 10 t: guide 15 ... Nozzle portions 20t, 30t, 40t ... Nozzle extension 30 ... Plunger 50 ... Positioning member 100 ... Top end upper portion 101 ... Tip bottom side portion

Claims (8)

  1. An instrument body having a cylindrical shape or a substantially cylindrical shape for accommodating an intraocular lens;
    An extrusion member that moves the intraocular lens forward in the axial direction by being inserted into the instrument body from the rear in the axial direction, and
    The instrument body has an insertion tube portion provided at the distal end portion and reduced in outer diameter and inner diameter, and a distal end opening portion opened at the distal end of the insertion tube portion,
    An insertion device for an intraocular lens that is inserted into the eye by being discharged from the distal end opening after being deformed by passing the insertion tube through the intraocular lens by the pushing member,
    The instrument body is
    A slit provided in the insertion tube portion so as to extend axially rearward from the tip opening,
    A step-shaped insertion restricting portion that is provided at a predetermined distance from the distal end of the insertion tubular portion and restricts the amount of insertion of the insertion tubular portion into the eye; and
    An insertion device for an intraocular lens, wherein a rear end of the slit is arranged on the rear side in the axial direction from a stepped portion of the insertion restricting portion.
  2. The tip opening is provided so as to form an inclined surface that is inclined with respect to a surface orthogonal to the central axis of the insertion tube portion;
    The inclined surface is inclined so that the front side of the intraocular lens in the optical axis direction of the intraocular lens at the distal end opening portion is more forward than the rear side in the optical axis direction. An insertion device for an intraocular lens according to 1.
  3. 3. The intraocular lens insertion device according to claim 2, wherein the slit is formed on the opposite side of the most distal end portion of the distal end opening as viewed from the distal end side of the insertion tube portion.
  4. The instrument body is
    When the intraocular lens is moved by the push-out member and passed through the insertion tube portion, the intraocular lens is viewed from the distal end side of the insertion tube portion toward the most distal portion of the distal end opening. The intraocular lens insertion device according to claim 3, further comprising a deformation assisting unit that is folded and deformed so as to be convex.
  5. The instrument main body has a reduced diameter portion that is provided behind the insertion tube portion and decreases in a substantially tapered shape as the inner diameter of the instrument main body goes to the tip side.
    The intraocular structure according to claim 4, wherein the deformation assisting means has a multi-stage taper structure in which the taper has a steeper inclination angle at the front end side than at the rear side in the reduced diameter portion. Lens insertion instrument.
  6. The instrument main body has a reduced diameter portion that is provided behind the insertion tube portion and decreases in a substantially tapered shape as the inner diameter of the instrument main body goes to the tip side.
    The deformation assisting means is a peripheral portion support guide provided on the inner wall of the instrument main body at the reduced diameter portion and supporting the peripheral portion of the intraocular lens from the front side in the optical axis direction of the intraocular lens. The intraocular lens insertion device according to claim 4.
  7. The insertion restricting portion is a cylindrical large-diameter portion provided on the rear side of the insertion cylindrical portion and on the distal end side of the reduced diameter portion and having an outer diameter larger than the insertion cylindrical portion,
    A rear end of the slit is disposed on a side surface of the large diameter portion, and a small diameter portion that is a surface extending from the side surface of the insertion tube portion is formed around the rear end of the slit in the large diameter portion. The intraocular lens insertion device according to any one of claims 1 to 6, wherein the intraocular lens insertion device is provided.
  8. A preset insertion system for an intraocular lens, in which the intraocular lens is housed in the intraocular lens insertion device according to any one of claims 1 to 7.
PCT/JP2011/079902 2010-12-22 2011-12-22 Intraocular lens-inserting instrument WO2012086797A1 (en)

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WO2014084355A1 (en) * 2012-11-29 2014-06-05 興和株式会社 Intraocular lens insertion device
FR3011174A1 (en) * 2012-09-07 2015-04-03 Sarl M D J Device for injecting an intraocular cataract treatment lens and corresponding cataract treatment assembly
WO2015076308A1 (en) * 2013-11-19 2015-05-28 興和株式会社 Intraocular lens insertion instrument
WO2018003853A1 (en) * 2016-06-28 2018-01-04 Hoya株式会社 Intraocular lens insertion tool
EP3222247A4 (en) * 2014-11-19 2018-07-11 Kowa Company Ltd. Intraocular lens insertion tool
US10172706B2 (en) 2015-10-31 2019-01-08 Novartis Ag Intraocular lens inserter
US10188506B2 (en) 2012-06-04 2019-01-29 Alcon Pharmaceuticals, Ltd. Intraocular lens inserter

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JP3861138B2 (en) * 2001-09-04 2006-12-20 キヤノンスター株式会社 Intraocular lens insertion device
JP2008544816A (en) * 2005-07-01 2008-12-11 アドバンスト メディカル オプティクス, インコーポレーテッド Intraocular lens insertion device having a soft tip with low irritation
JP2009240728A (en) * 2008-03-31 2009-10-22 Nidek Co Ltd Intraocular lens inserter

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JP2002514466A (en) * 1998-05-11 2002-05-21 ジェイ・スチュアート・カミング Intraocular lens insertion tool
JP2002542884A (en) * 1999-04-30 2002-12-17 アラーガン・セイルズ・インコーポレイテッド Intraocular lens insertion device and methods of use thereof
JP3861138B2 (en) * 2001-09-04 2006-12-20 キヤノンスター株式会社 Intraocular lens insertion device
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JP2009240728A (en) * 2008-03-31 2009-10-22 Nidek Co Ltd Intraocular lens inserter

Cited By (15)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US10188506B2 (en) 2012-06-04 2019-01-29 Alcon Pharmaceuticals, Ltd. Intraocular lens inserter
US10485657B2 (en) 2012-06-04 2019-11-26 Alcon Pharmaceuticals, Ltd. Intraocular lens inserter
FR3011174A1 (en) * 2012-09-07 2015-04-03 Sarl M D J Device for injecting an intraocular cataract treatment lens and corresponding cataract treatment assembly
CN104812337B (en) * 2012-11-29 2018-03-16 兴和株式会社 Intraocular lens insertion apparatus
CN104812337A (en) * 2012-11-29 2015-07-29 兴和株式会社 Intraocular lens insertion device
US9855138B2 (en) 2012-11-29 2018-01-02 Kowa Company, Ltd. Intraocular lens insertion device
WO2014084355A1 (en) * 2012-11-29 2014-06-05 興和株式会社 Intraocular lens insertion device
JPWO2014084355A1 (en) * 2012-11-29 2017-01-05 興和株式会社 Intraocular lens insertion device
JPWO2015076308A1 (en) * 2013-11-19 2017-03-16 興和株式会社 Intraocular lens insertion device
WO2015076308A1 (en) * 2013-11-19 2015-05-28 興和株式会社 Intraocular lens insertion instrument
US10195019B2 (en) 2013-11-19 2019-02-05 Kowa Company, Ltd. Intraocular lens insertion apparatus
US10507099B2 (en) 2014-11-19 2019-12-17 Kowa Company, Ltd. Intraocular lens insertion apparatus
EP3222247A4 (en) * 2014-11-19 2018-07-11 Kowa Company Ltd. Intraocular lens insertion tool
US10172706B2 (en) 2015-10-31 2019-01-08 Novartis Ag Intraocular lens inserter
WO2018003853A1 (en) * 2016-06-28 2018-01-04 Hoya株式会社 Intraocular lens insertion tool

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JPWO2012086797A1 (en) 2014-06-05

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