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WO2016195095A1 - Outil d'insertion de lentille intraoculaire - Google Patents

Outil d'insertion de lentille intraoculaire Download PDF

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Publication number
WO2016195095A1
WO2016195095A1 PCT/JP2016/066659 JP2016066659W WO2016195095A1 WO 2016195095 A1 WO2016195095 A1 WO 2016195095A1 JP 2016066659 W JP2016066659 W JP 2016066659W WO 2016195095 A1 WO2016195095 A1 WO 2016195095A1
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WO
WIPO (PCT)
Prior art keywords
intraocular lens
plunger
pressing force
insertion device
shaft portion
Prior art date
Legal status (The legal status 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 status listed.)
Ceased
Application number
PCT/JP2016/066659
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English (en)
Japanese (ja)
Inventor
小林　研一
Current Assignee (The listed assignees may be inaccurate. Google has not performed a legal analysis and makes no representation or warranty as to the accuracy of the list.)
Kowa Co Ltd
Original Assignee
Kowa Co Ltd
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
Application filed by Kowa Co Ltd filed Critical Kowa Co Ltd
Priority to JP2017522295A priority Critical patent/JPWO2016195095A1/ja
Publication of WO2016195095A1 publication Critical patent/WO2016195095A1/fr
Anticipated expiration legal-status Critical
Ceased legal-status Critical Current

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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 or corneal implants; Artificial eyes
    • A61F2/16—Intraocular lenses
    • 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
    • A61F9/00—Methods or devices for treatment of the eyes; Devices for putting in contact-lenses; Devices to correct squinting; Apparatus to guide the blind; Protective devices for the eyes, carried on the body or in the hand
    • A61F9/007—Methods or devices for eye surgery

Definitions

  • the present invention relates to an intraocular lens insertion device.
  • Intraocular lenses that are inserted as a substitute for the crystalline lens in order to correct the refraction by replacing the human turbid crystalline lens in the treatment of cataract are in practical use.
  • intraocular lens insertion surgery in the treatment of cataracts, for example, a few millimeters of incision wound (incision) is provided at the edge of the cornea, cornea, etc., and the lens is crushed by ultrasonic phacoemulsification, etc. After removal, the intraocular lens is inserted and fixed by an intraocular lens insertion device.
  • techniques for assisting insertion of an intraocular lens into the eye using an intraocular lens insertion device have been proposed (for example, Patent Documents 1, 2, and 3).
  • the intraocular lens is formed using a soft material such as a soft acrylic material or a silicon-based material, it has a certain degree of adhesiveness. Further, when the intraocular lens is inserted into the eye, the movement path of the intraocular lens in the intraocular lens insertion device is filled with a viscoelastic substance such as hyaluronic acid. Furthermore, when the surgeon releases the intraocular lens from the distal end of the intraocular lens insertion device, the surgeon moves the intraocular lens to the distal end of the intraocular lens insertion device by using a plunger that is an extrusion member of the intraocular lens. In such a state, the movement is temporarily interrupted to check whether the intraocular lens has a normal posture and whether there is damage or the like.
  • a viscoelastic substance such as hyaluronic acid
  • the intraocular lens may remain in contact with the inner wall of the intraocular lens insertion device, and the intraocular lens may stick to the inner wall.
  • a viscoelastic substance used as a lubricant for movement of the intraocular lens in the intraocular lens insertion device may leak from the tip of the intraocular lens insertion device, which may hinder subsequent movement of the intraocular lens. There is.
  • the intraocular lens rotates in an unintended direction in the intraocular lens insertion device, deforms into an abnormally folded state, or positions the intraocular lens within the eye.
  • an abnormality such as that the support part of the battery does not tacken properly will occur.
  • the plunger is pushed and moved in order to release the intraocular lens from the intraocular lens insertion device, it is necessary to apply a pressing force larger than the normal pressing force to the plunger. There is.
  • the intraocular lens When such an urging force is applied to the plunger to move the intraocular lens, the intraocular lens is released vigorously from the tip of the intraocular lens insertion device, and part of the pushing plunger is also in the eye. There is a possibility of protruding from the tip of the inner lens insertion device. When the plunger protruding from the tip of the intraocular lens insertion device touches the eyeball tissue such as the cornea, the tissue may be damaged.
  • the technology of the present disclosure has been made in view of the above circumstances, and its purpose is to prevent a sudden and unintentional protrusion of the plunger from the intraocular lens insertion device into the eye.
  • An intraocular lens insertion device is provided.
  • An intraocular lens insertion device includes a device main body having a storage portion in which an intraocular lens is stored and an insertion tube portion for releasing the intraocular lens into a patient's eye, A plunger provided movably, and the intraocular lens is inserted into the insertion tube portion by moving the plunger toward the insertion tube portion and pressing the intraocular lens accommodated by the tip of the plunger.
  • the plunger has a restraining portion that suppresses the movement of the tip of the plunger when the pressing force of the plunger against the intraocular lens exceeds a predetermined threshold value.
  • the suppression unit is a cross-sectional area reduction unit that reduces the cross-sectional area of the plunger provided at a position not in contact with the intraocular lens, and the cross-sectional area reduction unit is configured such that the pressing force of the plunger against the intraocular lens is a predetermined threshold value. If it becomes above, it will change.
  • the cross-sectional area reduction part is a notch part extending in the vertical direction of the plunger provided on the side surface of the plunger. Further, the cutout portion may be provided on the side surface of the plunger and in a thin flat plate portion. Or a cross-sectional area reduction
  • decrease part is a hole which penetrates a plunger in the direction different from the direction of movement of a plunger.
  • the restraining unit has a first shaft portion and a second shaft portion that are connected to each other, and the pressing force applied to the second shaft portion is transmitted to the first shaft portion, whereby the plan is
  • the first shaft portion and the second shaft portion may be relatively moved. Accordingly, when the pressing force applied to the plunger when the plunger is pushed and moved becomes a predetermined magnitude or more, the first shaft portion and the second shaft portion move relative to each other. The pressing movement of the jar is interrupted.
  • the restraining portion includes a first region and a second region that can store a part of the second shaft portion, and a locking portion that locks a portion of the second shaft portion within the first region.
  • the first region and the second region are provided across the locking portion in the movement direction of the plunger, and the locking portion is not less than a predetermined threshold from a part of the second shaft portion.
  • the second shaft portion that is locked to the first region by the locking portion when the pressing force is equal to or greater than a predetermined magnitude is The movement of the plunger is released and the plunger moves by moving to the second region.
  • the intraocular lens may be accommodated in the insertion tube portion before the intraocular lens insertion device is distributed.
  • an intraocular lens insertion device capable of preventing a sudden and unintentional protrusion of the plunger from the intraocular lens insertion device into the eye.
  • FIG.1 (a) and FIG.1 (b) are figures which show schematic structure of the intraocular lens insertion instrument in one Embodiment.
  • FIG. 2A and FIG. 2B are diagrams illustrating a schematic configuration of an intraocular lens according to an embodiment. It is a figure which shows schematic structure of the nozzle main body in one Embodiment.
  • FIG. 4A and FIG. 4B are diagrams showing a schematic configuration of a positioning member in one embodiment.
  • Fig.5 (a) and FIG.5 (b) are figures which show schematic structure of the plunger in one Embodiment. It is a figure which shows typically the plunger in one Embodiment.
  • FIG. 7 (a) and FIG.7 (b) are figures which show schematic structure of the plunger in one Embodiment.
  • FIG. 8 is a diagram schematically illustrating a plunger according to an embodiment.
  • Fig.9 (a) and FIG.9 (b) are figures which show schematic structure of the plunger in one Embodiment.
  • FIG. 10 is a diagram schematically illustrating a plunger according to an embodiment.
  • Fig.11 (a) and FIG.11 (b) are figures which show schematic structure of the plunger in one Embodiment. It is a figure which shows typically the plunger in one Embodiment.
  • FIG. 13A and FIG. 13B are diagrams showing a schematic configuration of a plunger in one embodiment. It is a figure which shows typically the plunger in one Embodiment.
  • FIG. 15A and FIG. 15B are diagrams showing a schematic configuration of a plunger in one embodiment. It is a figure which shows typically the plunger in one Embodiment.
  • FIG. 1A and FIG. 1B show a schematic configuration of an intraocular lens insertion device 1 according to the first embodiment.
  • 1A is a plan view of the intraocular lens insertion instrument 1 when the stage lid 13 is opened
  • FIG. 1B is a side view of the intraocular lens insertion instrument 1 when the stage lid 13 is closed.
  • the intraocular lens insertion instrument 1 is roughly composed of an instrument body and an intraocular lens pushing member.
  • the instrument body has a nozzle body 10 and a stage portion 12 and a stage lid portion 13 which are storage portions for intraocular lenses.
  • the push member of the intraocular lens has a plunger 30.
  • the stage unit 12 is provided integrally with the nozzle body 10 or separately.
  • a plunger 30 is inserted into the nozzle body 10.
  • the intraocular lens 2 is set on the stage unit 12.
  • the stage unit 12 is formed integrally with the stage lid unit 13.
  • FIG. 1A and FIG. 1B show a state where the stage lid 13 is opened.
  • the nozzle main body 10 of the intraocular lens insertion device 1 is formed in a cylindrical shape having a substantially rectangular cross section, and one end of the nozzle body 10 is greatly open (hereinafter, the side having the large opening is referred to as the rear end 10b), and the other side.
  • the end portion of the head is provided with a tip portion 10a that is narrowed down. As shown in FIG.1 (b), the front-end
  • the plunger 30 is inserted into the nozzle body 10 and can reciprocate in the longitudinal direction of the nozzle body 10.
  • the direction from the rear end 10b of the nozzle body 10 to the front end 10a is the front direction
  • the opposite direction is the rear direction
  • the front side of the page in FIG. 1A is the upper direction
  • the reverse direction is the lower direction
  • the front side of the page is the left direction
  • the opposite direction is the right direction.
  • the upper side is the front side of the optical axis of the lens body 2a set on the stage part
  • the lower side is the rear side of the optical axis of the lens body 2a set on the stage part
  • the front side is the front side in the pressing direction by the plunger 30
  • the rear side corresponds to the rear side in the pressing direction by the plunger 30.
  • FIG. 2A and FIG. 2B are diagrams showing a schematic configuration of the intraocular lens 2.
  • 2A is a plan view and FIG. 2B is a side view.
  • the intraocular lens 2 is a so-called one-piece type. In the following description, the intraocular lens 2 is described as being a one-piece type, but instead of the one-piece type intraocular lens 2, a so-called three-piece type intraocular lens or a plate-type intraocular lens is used. Also good.
  • the intraocular lens 2 is formed of a lens body 2a having a predetermined refractive power and two flat plate-like support portions 2b connected to the lens body 2a for holding the lens body 2a in the eyeball. Yes.
  • FIG. 3 shows a plan view of only the nozzle body 10.
  • the intraocular lens 2 is set on the stage unit 12. In this state, the intraocular lens 2 is pressed by the plunger 30 and ejected from the distal end portion 10a.
  • the nozzle body 10 is provided with a through-hole 10c having a cross-sectional shape that becomes smaller toward the tip according to the shape that the outer shape of the nozzle body 10 becomes thinner toward the tip.
  • the cross-sectional shape of the through hole is an oval shape (egg shape) in the embodiment drawing, it may be a circular shape or an oval shape for the convenience of the lens used or specifications.
  • the through-hole corresponds to an example of an insertion path for inserting the intraocular lens into the eye.
  • the intraocular lens 2 when the intraocular lens 2 is inject
  • 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 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 is set higher than the height position of the bottom surface of the through hole 10c of the nozzle body 10, and the set surface 12b and the bottom surface of the through hole 10c are connected by a bottom slope 10d. .
  • 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. Further, a guide protrusion 13 c is provided as a guide on the upper side of the plunger 30.
  • the stage lid 13 is provided with an insertion hole 13d for supplying a viscoelastic substance to the intraocular lens 2 in a state where the stage lid 13 is closed.
  • the viscoelastic substance is an example of a lubricant used when the intraocular lens 2 is moved to the tip portion 10a of the nozzle body 10, and hyaluronic acid or the like is often used.
  • a positioning member 50 is detachably provided below the set surface 12b of the stage portion 12.
  • 4A and 4B show a schematic configuration of the positioning member 50.
  • FIG. FIG. 4A shows a plan view of the positioning member 50
  • FIG. 4B shows a left side view of the positioning member 50.
  • 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 are connected by a connecting portion 52.
  • a holding portion 53 is formed at the lower end of each side wall portion 51 so as to extend outward.
  • a pair of first mounting portions 54 are formed on the upper end portions of the respective side wall portions 51.
  • the pair of first mounting portions 54 are formed in an arc shape when viewed from above and project upward.
  • a first positioning portion 55 is formed on the outer peripheral side of the upper end surface of the first placement portion 54 so as to protrude. The distance between the inner diameters of the first positioning portions 55 is set to be slightly larger than the diameter dimension of the lens body 2 a of the intraocular lens 2.
  • a pair of second mounting portions 56 are formed at both ends in the front-rear direction of the connecting portion 52, and the shape viewed from above is a rectangular shape and protrudes upward.
  • the height of the upper surface of the second placement unit 56 is equal to the height of the upper surface of the first placement unit 54.
  • a second positioning portion 57 that further protrudes upward over the entire left and right direction of the second placement portion 56 is formed on the outer portion of the upper surface of the second placement portion 56.
  • the distance between the insides of the second positioning portions 57 is set slightly larger than the diameter of the lens body 2a of the intraocular lens 2.
  • a locking claw 58 that slightly protrudes in the front-rear direction is formed at the upper end portion of the second placement portion 56 over the entire left-right direction.
  • 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 a set surface through hole 12c that penetrates the set surface 12b in the thickness direction.
  • the outer shape of the set surface through-hole 12c is substantially similar to the shape of the first mounting portion 54 and the second mounting portion 56 of the positioning member 50 as viewed from above.
  • the first placement portion 54 and the second placement portion 56 are inserted into the set surface through hole 12c from the lower side of the set surface 12b, and the set surface 12b. Protrudes above.
  • the locking claw 58 provided in the second positioning portion 57 protrudes to the set surface 12b through the set surface through hole 12c and is locked to the upper surface of the set surface 12b.
  • the positioning member 50 is assembled from the lower side of the nozzle body 10, and the first placement portion 54 and the second placement portion 56 are fixed in a state of protruding from the set 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 portion 54 and the second placement portion 56.
  • the position of the lens body 2a is restricted with respect to the horizontal direction (the direction horizontal to the set surface 12b) by the first positioning portion 55 and the second positioning portion 57.
  • the plunger 30 has a slightly larger longitudinal length 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 made into the column shape, and the thin plate-shaped flat part 31b extended in the left-right direction of the cylindrical part 31a.
  • a first notch 31 c is formed at the tip of the action part 31.
  • the first 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.
  • the groove wall on the distal end side of the first cutout portion 31 c is formed with an inclined surface that goes upward as it goes to the distal end side of the action portion 31.
  • the insertion part 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 10 c of the nozzle body 10.
  • 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 upward from the insertion portion 32 and that can move up and down by the elasticity of the material of the plunger 30 is formed at a portion of the insertion portion 32 that is ahead of the center in the front-rear direction.
  • the locking hole 10e shown in FIG. 3 provided in the thickness direction on the upper surface of the nozzle body 10 and the claw portion 32a are engaged.
  • the relative position between the nozzle body 10 and the plunger 30 in the initial state is determined.
  • the claw portion 32a and the locking hole 10e are formed at the positions where the distal end of the action portion 31 is located on the rear side of the lens body 2a of the intraocular lens 2 set on the stage portion 12 in the engaged state.
  • the support portion 2b on the rear side of the main body 2a is set so that the first cutout portion 31c can be supported from below.
  • a second cutout portion 35 different from the first cutout portion 31c is provided in the cylindrical portion 31a of the action portion 31.
  • the 2nd notch part 35 is a groove
  • the cross-sectional area of the cylindrical portion 31a is smaller than the other portions.
  • the second cutout portion 35 is provided at a position where it does not come into contact with the support portion 2b of the intraocular lens 2.
  • the second cutout portion 35 corresponds to an example of a cross-sectional area decreasing portion in which the cross-sectional area of the plunger provided at a position not in contact with the intraocular lens is reduced.
  • the plunger 30 Prior to the accommodation of the intraocular lens 2 of the intraocular lens insertion device 1 configured as described above, 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 nozzle body 10 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
  • the lens body 2 a of the intraocular lens 2 is placed and positioned on the upper surfaces of the first placement part 54 and the second placement part 56 with the support part 2 b facing the front-rear direction of the nozzle body 10.
  • a part of the support portion 2b on the rear side of the intraocular lens 2 enters the first cutout portion 31c of the plunger 30 and is supported by the bottom surface thereof.
  • the tip of the plunger 30 is in contact with the optical part 2 a of the intraocular lens 2.
  • the needle of the syringe When inserting the intraocular lens 2 into the eyeball, first, the needle of the syringe is inserted from the distal end portion 10a of the nozzle body 10 or the insertion hole 13d, and the lubrication necessary for the intraocular lens 2 to move within the nozzle 10 is obtained. Inject hyaluronic acid, the agent. Once the required amount has been injected, the positioning member 50 is then removed from the nozzle body 10. Thereby, the 1st mounting part 54 and the 2nd mounting part 56 which were supporting the lens main body 2a of the intraocular lens 2 retreat from the set surface 12b, and the intraocular lens 2 can move on the set surface 12b. Placed. Then, the plunger 30 pushes the intraocular lens 2 to a predetermined position.
  • the tip 10a of the nozzle body 10 is inserted into the incision provided in the eye tissue, and the positional relationship between the tip 10a and the incision is determined.
  • the surgeon pushes the pressing plate portion 33 of the plunger 30 into the distal end side of the nozzle body 10 again.
  • the distal end of the action portion 31 of the plunger 30 comes into contact with the outer periphery of the lens body 2a of the intraocular lens 2 set on the set surface 12a, and the intraocular lens 2 is guided toward the distal end portion 10a by the plunger 30.
  • the surgeon interrupts the pressing movement of the plunger 30, and whether the intraocular lens 2 is normally tacked, that is, the optical part It is confirmed whether or not the support portion is in a state of being folded in between or whether the intraocular lens 2 is damaged or the like. Thereafter, the surgeon resumes the pressing movement of the plunger 30 and releases the intraocular lens 2 from the distal end portion 10a of the nozzle body 10 into the eye.
  • FIG. 6 shows an example of such a case.
  • the nozzle body 10 is indicated by a dotted line
  • the plunger 30 and the intraocular lens 2 are indicated by a solid line.
  • FIG. 6 shows a state in which the intraocular lens 2 is moved to the tapered portion of the through hole 10 c of the nozzle body 10 by the pressing movement of the plunger 30.
  • the intraocular lens 2 is firmly fixed in the through hole 10c, although the support portion 2b of the extraocular lens 2 is normally tacked to the optical portion 2a.
  • the intraocular lens 2 Since the intraocular lens 2 is fixed in the through hole 10c, when the surgeon presses and moves the plunger 30 in the forward direction of the nozzle body 10, the force acting on the intraocular lens 2 from the plunger 30 is normal operation. Compared to As a result, the external force that the cylindrical portion 31a of the plunger 30 receives from the intraocular lens 2 also increases. Then, in the present embodiment, since the second cutout portion 35 is provided in the cylindrical portion 31c, stress concentration occurs in the second cutout portion 35 with respect to the stress generated in the cylindrical portion 31a. That is, the 2nd notch part 35 becomes a starting point of the shape change and destruction of the cylindrical part 31a. FIG. 6 shows a case where the second notch 35 of the cylindrical portion 31a is broken.
  • FIGS. 9A and 9B show a case where fracture occurs in the reduced diameter portion 36 of the cylindrical portion 31a.
  • the reduced diameter portion 36 is preferably formed near the insertion portion 32 in consideration of preventing broken pieces of the cylindrical portion 31a from moving into the eye from the opening of the tip portion 10a of the nozzle body 10. .
  • the portion where the flat portion 31b is not provided is formed longer in the pressing direction than the tip portion 31a portion. Then, the shape is easily changed or broken at that portion. As a result, the cylindrical portion 31a can be broken as shown in FIG.
  • the plunger 30 shown to Fig.11 (a) and FIG.11 (b) the part which does not provide the flat part 31b can be considered as an example of a notch part.
  • an intraocular lens insertion device according to a fourth embodiment will be described.
  • the same components as those in the first embodiment are denoted by the same reference numerals, and detailed description thereof is omitted.
  • the intraocular lens insertion device 100 according to the third embodiment is different in that a hole 37 is provided instead of the second notch 35 in the cylindrical portion 31a of the plunger 30 in the first embodiment.
  • the hole 37 corresponds to an example of a suppression unit.
  • the hole 37 since the hole 37 penetrates the cylindrical part 31a in the vertical direction of the plunger 30, when a breakage occurs in the hole 37, as shown in FIG. 14, the tip part 31d of the cylindrical part 31a cut by the breakage is provided.
  • the rear side end portion 31f moves to the side opposite to the side where the hole 37 is provided with respect to the central axis AX. That is, the hole 37 has a shape change or breakage when a larger pressing force than usual is applied to the plunger 30 in the pressing movement of the plunger 30 in the same manner as the second notch 35 in the first embodiment. In addition to being a starting point, it also has a function of determining the folding direction of the cylindrical portion 31a.
  • an intraocular lens insertion device according to a fifth embodiment will be described.
  • the same components as those in the first embodiment are denoted by the same reference numerals, and detailed description thereof is omitted.
  • the intraocular lens insertion device 100 according to the fourth embodiment is different in that a plunger 40 is used instead of the plunger 30 in the first embodiment.
  • the locking portion 41a positions the pressing force transmission plate portion 43 between the rear end surface 41b and is pressed by the pressing force transmission plate portion 43. By this, it is formed to be able to bend on the front side end face 41c side.
  • the locking portion 41a is provided in a flange shape that goes around the side surface 41d.
  • the operator moves the plunger 40 relative to the plunger 40 in the moving direction when the plunger 40 is pressed and moved.
  • the peak of the pressing force to be applied is assumed to be about 5N. Therefore, when the peak of the pressing force applied to the plunger 40 in the moving direction of the plunger 40 is about 10 N or more, the magnitude of the pressing force applied by the locking portion 41a from the pressing force transmitting plate portion 43. Accordingly, the locking portion 41a may be configured to bend toward the front end face 41c.
  • the pressing force applied by the surgeon to the pressing plate portion 33 increases, the pressing force transmitted from the pressing force transmission plate portion 43 to the locking portion 41a also increases. And when the said pressing force becomes about 10 N or more, the latching
  • the locking portion 41a continues to bend as it continues to be pressed by the pressing force transmission plate portion 43.
  • the pressing force transmission plate portion 43 moves to a position sandwiched between the locking portions 41a.
  • the pressing force transmitting plate portion 43 moves between the locking portions 41a and moves into the region 41g of the space 41e as shown in FIG. 12 (c). .
  • the configuration of the intraocular lens insertion device is not limited to the above-described embodiment, and various configurations are possible within the scope that does not lose the technical idea of the present invention. Can be changed and combined.
  • the magnitude of the pressing force applied by the surgeon to the pressing plate portion 33 is about 5N when there is no malfunction in the intraocular lens, the pressing force becomes about 10N or more.
  • the plunger is broken or the engagement portion is disengaged from the pressing force transmission plate portion.
  • the magnitude of these pressing forces is only an example, and can be appropriately changed according to the intraocular lens insertion instrument to be used.
  • the case where the plunger is broken has been described. However, when the pressing force applied to the plunger when the plunger is pushed and moved exceeds a predetermined threshold value, the deformation is caused instead of the breakage.
  • the second cutout portion, the reduced diameter portion, and the hole may be respectively configured.
  • the cross-sectional area reducing portion in which the cross-sectional area of the plunger provided at a position not in contact with the intraocular lens is reduced is engaged with another member for performing plunger axial alignment or the like. It is not intended to be provided, but can be configured to be molded integrally with the plunger.
  • the hole is provided in the position remove
  • the locking portion 41a is provided in a flange shape that goes around the side surface 41d.
  • the locking portion 41a does not have to be provided so as to go around the side surface 41d, and a part of the side surface 41d. It is good also as a structure which provided multiple projection parts which protrude in the space 41e side.
  • what is necessary is just to form the cross section, when providing such a projection part as Fig.12 (a) shows.

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  • Prostheses (AREA)

Abstract

La présente invention concerne un outil d'insertion de lentille intraoculaire grâce auquel une saillie involontaire d'un piston depuis l'outil d'insertion de lentille intraoculaire dans un œil peut être évitée. L'outil d'insertion de lentille intraoculaire selon la présente invention est configuré sous la forme d'un outil d'insertion de lentille intraoculaire pourvu d'un corps principal d'outil ayant une partie de logement dans laquelle une lentille intraoculaire est logée et d'un cylindre d'insertion pour libérer la lentille intraoculaire dans l'œil d'un patient, et d'un piston disposé de façon à pouvoir e déplacer à travers l'intérieur du corps principal d'outil, le piston étant déplacé vers le cylindre d'insertion et la lentille intraoculaire logée étant poussée par l'extrémité distale du piston, grâce à quoi la lentille intraoculaire peut être libéréedu cylindre d'insertion, le piston comporant une partie de retenue pour limiter le déplacement du piston lorsque la force de pression du piston contre la lentille intraoculaire devient égale ou supérieure à une valeur de seuil prédéterminée.
PCT/JP2016/066659 2015-06-04 2016-06-03 Outil d'insertion de lentille intraoculaire Ceased WO2016195095A1 (fr)

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JP2017522295A JPWO2016195095A1 (ja) 2015-06-04 2016-06-03 眼内レンズ挿入器具

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JP2015114278 2015-06-04
JP2015-114278 2015-06-04

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Cited By (10)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US10195018B2 (en) 2013-03-21 2019-02-05 Shifamed Holdings, Llc Accommodating intraocular lens
US10350056B2 (en) 2016-12-23 2019-07-16 Shifamed Holdings, Llc Multi-piece accommodating intraocular lenses and methods for making and using same
US10350057B2 (en) 2013-02-14 2019-07-16 Shifamed Holdings, Llc Hydrophilic AIOL with bonding
US10548718B2 (en) 2013-03-21 2020-02-04 Shifamed Holdings, Llc Accommodating intraocular lens
US10736734B2 (en) 2014-08-26 2020-08-11 Shifamed Holdings, Llc Accommodating intraocular lens
US10987214B2 (en) 2017-05-30 2021-04-27 Shifamed Holdings, Llc Surface treatments for accommodating intraocular lenses and associated methods and devices
US11141263B2 (en) 2015-11-18 2021-10-12 Shifamed Holdings, Llc Multi-piece accommodating intraocular lens
US11266496B2 (en) 2017-06-07 2022-03-08 Shifamed Holdings, Llc Adjustable optical power intraocular lenses
US12167960B2 (en) 2016-12-23 2024-12-17 Shifamed Holdings, Llc Multi-piece accommodating intraocular lenses and methods for making and using same
US12376958B2 (en) 2015-11-18 2025-08-05 Shifamed Holdings, Llc Multi-piece accommodating intraocular lens

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US4765329A (en) * 1987-10-19 1988-08-23 Cumming, Redwitz & Wilson, Inc. Intraocular lens insertion instrument
JP2008194479A (ja) * 2007-02-15 2008-08-28 Alcon Manufacturing Ltd 眼内レンズ送出装置
JP2012508596A (ja) * 2008-11-12 2012-04-12 アルコン リサーチ， リミテッド 複数の部品から成るプランジャ先端を伴う眼内レンズ送達デバイス
JP2012125355A (ja) * 2010-12-14 2012-07-05 Kowa Co 眼内レンズの挿入器具
WO2014099487A1 (fr) * 2012-12-19 2014-06-26 Alcon Research, Ltd. Commande d'injecteurs de lentille intraoculaire automatisés

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* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US4765329A (en) * 1987-10-19 1988-08-23 Cumming, Redwitz & Wilson, Inc. Intraocular lens insertion instrument
JP2008194479A (ja) * 2007-02-15 2008-08-28 Alcon Manufacturing Ltd 眼内レンズ送出装置
JP2012508596A (ja) * 2008-11-12 2012-04-12 アルコン リサーチ， リミテッド 複数の部品から成るプランジャ先端を伴う眼内レンズ送達デバイス
JP2012125355A (ja) * 2010-12-14 2012-07-05 Kowa Co 眼内レンズの挿入器具
WO2014099487A1 (fr) * 2012-12-19 2014-06-26 Alcon Research, Ltd. Commande d'injecteurs de lentille intraoculaire automatisés

Cited By (17)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US10350057B2 (en) 2013-02-14 2019-07-16 Shifamed Holdings, Llc Hydrophilic AIOL with bonding
US10709549B2 (en) 2013-02-14 2020-07-14 Shifamed Holdings, Llc Hydrophilic AIOL with bonding
US11540916B2 (en) 2013-02-14 2023-01-03 Shifamed Holdings, Llc Accommodating intraocular lens
US10195018B2 (en) 2013-03-21 2019-02-05 Shifamed Holdings, Llc Accommodating intraocular lens
US10548718B2 (en) 2013-03-21 2020-02-04 Shifamed Holdings, Llc Accommodating intraocular lens
US12251303B2 (en) 2014-08-26 2025-03-18 Shifamed Holdings, Llc Accommodating intraocular lens
US10736734B2 (en) 2014-08-26 2020-08-11 Shifamed Holdings, Llc Accommodating intraocular lens
US11583390B2 (en) 2014-08-26 2023-02-21 Shifamed Holdings, Llc Accommodating intraocular lens
US11141263B2 (en) 2015-11-18 2021-10-12 Shifamed Holdings, Llc Multi-piece accommodating intraocular lens
US12376958B2 (en) 2015-11-18 2025-08-05 Shifamed Holdings, Llc Multi-piece accommodating intraocular lens
US12376957B2 (en) 2015-11-18 2025-08-05 Shifamed Holdings, Llc Multi-piece accommodating intraocular lens
US11065109B2 (en) 2016-12-23 2021-07-20 Shifamed Holdings, Llc Multi-piece accommodating intraocular lenses and methods for making and using same
US12167960B2 (en) 2016-12-23 2024-12-17 Shifamed Holdings, Llc Multi-piece accommodating intraocular lenses and methods for making and using same
US10350056B2 (en) 2016-12-23 2019-07-16 Shifamed Holdings, Llc Multi-piece accommodating intraocular lenses and methods for making and using same
US10987214B2 (en) 2017-05-30 2021-04-27 Shifamed Holdings, Llc Surface treatments for accommodating intraocular lenses and associated methods and devices
US11266496B2 (en) 2017-06-07 2022-03-08 Shifamed Holdings, Llc Adjustable optical power intraocular lenses
US12465483B2 (en) 2017-06-07 2025-11-11 Shifamed Holdings, Llc Adjustable optical power intraocular lenses

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