DE102014222069B4 - Insertion device and device for inserting an intraocular lens into an eye - Google Patents

Insertion device and device for inserting an intraocular lens into an eye

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Publication number
DE102014222069B4
DE102014222069B4 DE102014222069.6A DE102014222069A DE102014222069B4 DE 102014222069 B4 DE102014222069 B4 DE 102014222069B4 DE 102014222069 A DE102014222069 A DE 102014222069A DE 102014222069 B4 DE102014222069 B4 DE 102014222069B4
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Germany
Prior art keywords
insert device
device
insert
eye
according
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DE102014222069.6A
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German (de)
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DE102014222069A1 (en
Inventor
Joachim Storsberg
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Fraunhofer Gesellschaft zur Forderung der Angewandten Forschung eV
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Fraunhofer Gesellschaft zur Forderung der Angewandten Forschung eV
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Publication of DE102014222069A1 publication Critical patent/DE102014222069A1/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
    • A61LMETHODS OR APPARATUS FOR STERILISING MATERIALS OR OBJECTS IN GENERAL; DISINFECTION, STERILISATION, OR DEODORISATION OF AIR; CHEMICAL ASPECTS OF BANDAGES, DRESSINGS, ABSORBENT PADS, OR SURGICAL ARTICLES; MATERIALS FOR BANDAGES, DRESSINGS, ABSORBENT PADS, OR SURGICAL ARTICLES
    • A61L31/00Materials for other surgical articles, e.g. stents, stent-grafts, shunts, surgical drapes, guide wires, materials for adhesion prevention, occluding devices, surgical gloves, tissue fixation devices
    • A61L31/04Macromolecular materials
    • A61L31/041Mixtures of macromolecular compounds
    • AHUMAN NECESSITIES
    • A61MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61LMETHODS OR APPARATUS FOR STERILISING MATERIALS OR OBJECTS IN GENERAL; DISINFECTION, STERILISATION, OR DEODORISATION OF AIR; CHEMICAL ASPECTS OF BANDAGES, DRESSINGS, ABSORBENT PADS, OR SURGICAL ARTICLES; MATERIALS FOR BANDAGES, DRESSINGS, ABSORBENT PADS, OR SURGICAL ARTICLES
    • A61L2430/00Materials or treatment for tissue regeneration
    • A61L2430/16Materials or treatment for tissue regeneration for reconstruction of eye parts, e.g. intraocular lens, cornea

Abstract

An inserter (10) of an apparatus for inserting an intraocular lens through an incision in an eye, comprising a polymer blend containing or consisting of at least one thermoplastic polymer and at least one amphiphilic block copolymer selected from the group consisting of amphiphilic block copolymers having a hydrocarbon block of the formula CH3CH2 (CH2CH2) a, where "a" is 10, 11, 12, 13, 14, 15, 16, 17, 18, 19, 20, 21, 22, 23, 24 or 25 and a hydrophilic B block.

Description

  • The present invention relates to an inserting device which is part of a device for inserting an intraocular lens through an incision in an eye. In addition, the invention relates to a device for inserting an intraocular lens through an incision in an eye comprising an inserting device as described above.
  • An intraocular lens (IOL) is implanted in the eye, for example, as a replacement for a natural crystalline lens after surgery on a cataract has taken place, or it is used to alter the optical properties of an eye (to perform visual correction) the natural lens remains in the eye. The intraocular lenses often have optics, and preferably have at least one flexible fixation member or feel that extends from the optic and is fixed in the eye to secure the lens in place. The optics usually consist of an optically transparent lens. Planting such an intraocular lens in the eye requires making an incision into the eye. It is advantageous to keep the size of the incision as small as possible in order to reduce trauma and accelerate healing.
  • There are known intraocular lenses that are foldable (deformable) so that the intraocular lens can be inserted through a smaller incision into the eye. Numerous instruments have been proposed for inserting such foldable lenses into the eye.
  • Many of the known IOL deployment systems feed and / or fold the lens at the distal end, that is, at the end closest to the eye or the end inserted into the eye. Such "distal loading" systems often disadvantageously include a bulky loading component at or near the distal end of the system, thereby rendering the distal end relatively large. This relatively large distal end makes the use of the intraocular lens through a small incision even more difficult, if not impossible. Systems that fold and deploy the IOL near the distal end provide certain advantages over the "distal loading" systems, such as reduced stress on the IOL and / or the deployment device.
  • However, whether distal loading systems or proximal feeding systems are used, in both cases there is a factor limiting the size of the insert tube and this is the insert tube itself. The material making up the insert tube, for example, polypropylene and like polymer materials, may not be compatible or otherwise suitable for passing the optics, which may be made of, for example, silicone polymer materials, through the relatively small voids. For example, the insert tube may be made of materials, particularly polymeric materials, that have insufficient lubricity to transfer a folded IOL through the tube.
  • Due to the lack of lubricity, the cavity of the injector tube must be made relatively larger to accommodate the folded intraocular lens. This is disadvantageous since, as mentioned above, it is advantageous to make the smallest possible incision for the use of the IOL.
  • In addition, if you wanted to use a very small diameter tube to insert the IOL, a considerable force would be needed to force the IOL through the small cavity, increasing the potential for damage to the IOL, and in extreme cases even that Eye in which the IOL is to be used. One way could be to insert a lubricant, such as a conventional viscous-elastic agent, into the cavity of the tube to facilitate passage of the IOL through the deployment device. Such a lubricant, in turn, requires considerable space, and thereby at least partially overrides the purpose of using such means. In addition, such lubricants often end up in the eye, causing the risk of trauma and / or irritation and / or injury to the eye.
  • The US 4,681,102 A. describes, for example, that the lumen of an IOL deployment device is treated with a lubricant, for example, a substance known by the trade name "Healon", and this is an aqueous solution containing sodium hyaluronate. In this way, the lubricant is inserted into the hollow channel or the lumen of the insert device.
  • Such lubricants are essentially free-flowing materials. Such lubricants themselves occupy valuable space, at least partially counteracting the purpose of using such means. In addition, such lubricants often end up in the eye, resulting in the risk of trauma and / or irritation and / or injury to the eye.
  • In addition, it is known to make insert devices to the effect that monomeric lubricants z. B. glycerol monostearate with the plastic material from which the insert device exists to blind. The disadvantage here, however, is that such monomeric lubricants can dissolve in the intended use of the insert device, for example, when inserted into the eye of the plastic and thus remain in the eye. This is as undesirable as it is disadvantageous.
  • It would be advantageous to have a simple and uncomplicated IOL deployment device and methods that allow the passage of a folded IOL through the device in a controlled manner without requiring significant force.
  • Thus, it is an object of the present invention to provide an inserting device for an intraocular lens, which is as slippery as possible for intraocular lenses. It is also an object of the present invention to provide a device for inserting intraocular lenses.
  • This object is achieved with respect to an inserting device having the features of patent claim 1 with respect to an apparatus for inserting an intraocular lens having the features of patent claim 10. The respective dependent claims represent advantageous developments.
  • Thus, according to the invention there is provided an inserting device of an apparatus for inserting an intraocular lens through an incision in an eye comprising a polymer mixture containing or consisting of at least one thermoplastic polymer and at least one amphiphilic block copolymer selected from the group consisting of amphiphilic block copolymers having a hydrocarbon block Formula CH 3 CH 2 (CH 2 CH 2 ) a wherein "a" is 10, 11, 12, 13, 14, 15, 16, 17, 18, 19, 20, 21, 22, 23, 24 or 25 and provided with a hydrophilic B block.
  • Surprisingly, it has been found that a deployment device according to the present invention containing a polymer mixture as defined above has extremely low friction with respect to intraocular lenses, so that an almost powerless insertion of the intraocular lens into the eye via the deployment device is possible.
  • Due to the fact that the lubricant used in the invention is a polymer, as well as the disadvantages can be avoided that the lubricant dissolves from the insert when used properly from the insert and thus remains in the eye.
  • In addition, the lubricant causes a hard separation effect on the surface of the insert device, so that adhesion of the contact lens to the insert device is omitted.
  • Preferred amphiphilic block copolymers are, for example, from EP 2 316 498 A1 known. With regard to the basic structure and preferred embodiments of the amphiphilic block copolymers, reference is made to the complete disclosure content of this patent application. The subject matter of this patent application with respect to the amphiphilic block copolymers is also the subject of the present patent application.
  • A preferred embodiment provides that at least one thermoplastic polymer is selected from the group consisting of polyolefins, PVC, polyurethanes (PUR), styrene-butadiene copolymer (SBC), thermoplastic elastomer, styrene-ethylene-butylene-styrene copolymers (SEBS ) as well as mixtures or combinations thereof.
  • In particular, the polyolefins are selected from the group consisting of polyethylene, polypropylene and blends thereof.
  • A further advantage is that the B block is a hydrophilic oligomer, in particular a homo or co-oligomer containing or consisting of 2 to 10 monomer units derived from monomers selected from the group consisting of ethylene oxide, propylene oxide, ethylene glycol, propylene glycol, Epichlorohydrin, acrylic acid, methacrylic acid, ethyleneimine, caprolactone, vinyl alcohol and vinyl acetate.
  • The amphiphilic block copolymer can constitute from 1.5 to 25% by weight, preferably from 2 to 20% by weight, particularly preferably from 3 to 15% by weight, of the polymer mixture.
  • The insert device of the present invention is characterized in particular by a reduced surface friction, so that an extremely slippery surface of the insert device results. The surface friction is preferably less than 0.4, more preferably less than 0.2, particularly preferably less than 0.1.
  • The surface friction is determined in the following way: To determine the surface friction, a rheometer AR-G2 from TA Instruments was used. The rheometer was used in plate-plate mode. Friction force was measured between two rotors mounted on the rotors (point medical, NuSil MED-4750, 2 x 20 mm) and a stator mounted polycarbonate plate (Macrolon, 3 x 3 cm) with or without EO treatment using a water film or of a movie Cromafluid (eye fill HD, aq. Hydroxypropyl methylcellulose). The distance between the polymers was systematically reduced. The rotational force and the normal force needed to make the rotor rotate with respect to the stator were determined at a speed of 2 rad / s. For comparison purposes, the ratio of the torque (in μNm) to the normal force (in N), the so-called normalized torque, was used. To illustrate the measurement method are exemplary results obtained in the 1 and 2 shown.
  • It can be seen that the frictional force of silicone on an EO treated polycarbonate surface is dramatically reduced compared to untreated material.
  • A further advantageous embodiment of the insert device provides that the polymer mixture has a gradient with respect to the B block, wherein the concentration of the B block on the surface of the insert device formed from the polymer mixture is more than 2 to 60 times as high as the concentration of B. -Blocks in the center of the insert device.
  • Another advantage of the present invention is that the wear resistance of the inserter is increased. Thus, the wear resistance is increased compared to coated surfaces, and in particular from 1: 5 to 100: 1.
  • The insert device according to the present invention comprises in particular
    an insert tube having an inner wall defining a cavity through which an intraocular lens passes, and having an outlet through which the intraocular lens is transferred from the cavity to an eye,
    a feed chamber having a first member and a second member pivotally connected together.
  • With regard to the particularly preferred geometric embodiments of the insert device is on the DE 697 29 450 T2 directed.
  • In addition, the present invention relates to a device for inserting an intraocular lens through an incision into an eye, comprising an insert device according to one of the preceding claims,
    a handpiece having a through bore extending from a proximal end to a distal end of the handpiece and including a receiving aperture for receiving an inserter
    and a push rod which can be inserted into the bore of the handpiece via the proximal end.
  • The present invention will be explained in more detail with reference to the following embodiments, without limiting the invention to the parameters shown.
  • Brief description of the drawings
  • 1 is a front perspective view of a device according to the invention with the loading chamber in the open position;
  • 2 is a schematic partial view of a small portion of the device according to 1 ;
  • 2a is a partial schematic representation of a small part of a modified embodiment of the device according to 1 , with coating material;
  • 3 is a perspective side view of the device according to 1 , wherein the feed chamber is shown in the closed position;
  • 4 is a front perspective view of the device according to 3 into which a handpiece is inserted;
  • 5 is a partial section according to the line 5-5 according to 4 ;
  • 6 is a schematic representation of the device according to 4 with the handpiece shown partially inserted to insert an IOL into an eye.
  • This shows 7 a gap-dependent rotational force in polycarbonate surfaces with respect to silicone with different fluids at a rotational speed of 2 rad / s.
  • In 8th is the gap-dependent normalized torque at a rotation of 2 rad / s shown.
  • Detailed description of the drawings
  • The 1 illustrates an insert device 10 for an intraocular lens, with a loading chamber 12 and an insert tube fourteen , The IOL deployment device 10 exists z. Polypropylene, to which is physically added a proportion, for example from 1.5% to about 25% by weight of the insert, of a lubricity enhancing component which is an amphiphilic block copolymer as defined above.
  • The amphiphilic block copolymer is physically mixed with the other material making up the insert 10 exists, preferably before the inserter is made. In a particularly useful embodiment, the amphiphilic block copolymer is mixed with the other material, for example, the polymeric material, such as polypropylene, while the material is in the molten or liquid state. The amphiphilic block copolymer can be blended in this process so that it is substantially uniformly distributed throughout the material. The material is then placed in a mold or similar device suitable for use 10 to create. After the use 10 is prepared, the amphiphilic block copolymer remains substantially uniformly distributed throughout the insert.
  • After the insert device 10 is prepared, it is subjected to conditions that cause the concentration of the amphiphilic block copolymer on the inner wall or in the vicinity thereof to be greater than the concentration of the amphiphilic block copolymer inside the insert device. According to a particularly advantageous embodiment, the insert device is subjected to an elevated temperature for a time sufficient to cause the amphiphilic block copolymer to migrate to the surface, for example, to the inner surface of the insert device. A common name for this phenomenon is "blooming." Preferably, the inserter is exposed to the elevated temperatures of at least 35 ° C but conveniently in the range of about 40 ° C or about 45 ° C to about 100 ° C or about 120 ° C for a period between 6 hours to about 150 hours, and preferably a period between 8 hours and about 120 hours.
  • It is believed, without limiting the invention to any particular working theory, that this "blooming" causes a portion of the amphiphilic block copolymer present in the insert 10 is present, comes to lie on the inner surface of the insert device or in the vicinity thereof. It is also believed that the amphiphilic block copolymer is physically attached to or close to the inner surface of the insert body rather than being chemically covalently bonded to the inserter, which has been treated to provide improved lubricity. The insert device 10 can be exposed to an effective plasma. For example, the insert device 10 be placed in a chamber containing a plasma. The plasma may originate from a variety of materials, preferably gases, especially in gases such as oxygen, helium, nitrogen, argon, and mixtures thereof. More useful is the use of an oxygen-containing plasma.
  • According to an embodiment of the present invention, a radio frequency inductively coupled plasma is generated in a plasma chamber by contacting the chamber with a gas, for example oxygen, preferably at a pressure below about 1.33 Pa (0.01 Torr) or below atmospheric pressure more, and more conveniently still at a pressure ranging between about 1.33 Pa to about 39.9 Pa or about 66.65 Pa or about 133.3 Pa (0.01 Torr to about 0.3 Torr or about 0.5 torr or about 1.0 torr).
  • The preferred output power is in a range between 10 watts and about 600 watts.
  • The insert device 10 is preferably exposed to the plasma for a period of time in the range between 15 seconds and about 120 minutes, and conveniently in a range between 30 seconds and about 100 minutes. However, the particular gas, residence time, performance and / or other parameters may be changed depending on the equipment and the particular deployment equipment and deployment components, and optimization based on the present disclosure is easily possible using routine experimentation ,
  • Although the present invention is not limited to any particular mechanism, and without limiting the present invention to any particular working theory, it is believed that the present methodology is a modification or modification, for example, a physical and / or chemical modification or modification of the exposed one Causes areas of the insert device, which in turn leads to an improved sliding property.
  • It has been found that the "blooming" step and the plasma step in combination are very beneficial in improving the lubricity of the inserter. In other words, an inserter that has only been subjected to the "bloom" step, or that has only been exposed to the plasma step, has less favorable results than it has an inserter that performs both the "bloom" step was also exposed to the plasma step.
  • In any event, the amphiphilic block copolymer is present in an amount which, in combination with the plasma step, enhances the passage of the IOL through the insert 10 into the eye. The lubricity enhancing component does not need to be in the inserter 10 to be present in the form of discrete particles. It exists, however, essentially none covalent chemical bond between the lubricity enhancing component and the other material from which the inserter 10 consists.
  • The amphiphilic block copolymer is present in an amount effective to enhance the lubricity of the inner wall of the hollow tube which forms the cavity through which the IOL to be inserted into the eye enters. Such amphiphilic block copolymers are preferably effective to maintain improved lubricity over relatively long periods of time, such as at least over a month or at least over three months, and more preferably over six months so that the IOL insert device has a relatively long life and after its packaging and storage can be stored for relatively long periods of time and maintains lubricity.
  • The 1 and 3 to 6 illustrate the use of the IOL deployment device 10 containing an effective amount of the amphiphilic block copolymer 19 ( 2 ) or 20 ( 2A ) concentrated on or near the inner surfaces thereof.
  • The body of the IOL deployment device 10 is integral, for example, by casting, made primarily of polycarbonate. The loading chamber 12 has a first link 16 and a second link 18 which are connected to each other and a joint line 21 pivotally connected to each other. This joint line 21 lies parallel to the longitudinal axis 30 the deployment device 10 ,
  • The insert tube fourteen has a proximal end portion 22 , a distal end portion 24 and an open distal end 26 on. A reinforcing sleeve 28 surrounds the proximal end portion 22 of the insert tube fourteen , The reinforcement sleeve is optional.
  • The open distal end 26 is at an angle of about 45 ° to the longitudinal axis 30 the deployment device 10 beveled.
  • The insert tube fourteen if necessary, a continuous slot 32 which extends from the open distal end 26 extends distally and in front of the proximal end portion 22 of the insert tube fourteen ends. The continuous slot 32 is in the direction parallel to the longitudinal axis 30 the deployment device 10 running trained.
  • According to 1 is the insert device 10 shown in the open position. In contrast, in 3 the insert device 10 shown in the closed position. In closed position, the feed chamber includes 12 a headpiece 32 That's a combination of the top surfaces 34 and 36 a first wing 38 or a second wing 40 of the first link 16 or the second member 18 represents. The first and second wings 38 and 40 serve the user of the deployment device 10 for holding and manipulating the insert device 10 during use, as described below.
  • The insert device 10 is in detail in 4 shown. This shows the insert device in combination with a handpiece 50 , wherein the feed chamber 12 the deployment device 10 is in the closed position. When the loading chamber 12 is in the closed position, and the head member 32 located in the topmost position of the loading chamber, then is the distal end 26 of the insert tube fourteen at an angle of 45 ° relative to the longitudinal axis 30 the deployment device 10 such that the open distal end is generally perpendicular (when the deployment device is viewed from above). In addition, the through slot cuts 32 the open distal end 26 at the most proximal portion of the open distal end, as in Figs 1 . 3 and 5 shown.
  • If according to 5 the feed chamber 12 is in the closed position, then the feed chamber has an inner wall 51 on, which is a first lumen 52 defined in the direction parallel to the longitudinal axis 30 the deployment device 10 runs. The insert tube fourteen has a tapered inner wall 53 which has a second lumen distally tapering 54 forms. The average cross section of the second lumen 54 transverse to the longitudinal axis 30 is smaller than the average cross-sectional area of the first lumen 52 ,
  • The first lumen 52 is on the second lumen 54 aligned so that a folded IOL in the first lumen can be moved directly from the first lumen into the second lumen. The taper of the proximal section 58 of the second lumen 54 is steeper than the slight taper in the distal section 60 of the second lumen extends. The steeper taper in the proximal section 58 causes further folding of the intraocular lens when the IOL is the second lumen 54 passes. This further folding is advantageous because the folded IOL can be introduced into the eye through a smaller incision. The improved lubricity of the amphiphilic block copolymer 19 This allows for further folding so that little force is needed to further fold the IOL and / or the extent of further retention of the IOL can be increased so that eventually the IOL can be inserted through an even smaller incision , The amphiphilic block copolymer 19 also advantageously reduces the risk of Tearing and / or otherwise damaging the IOL when the IOL is the first lumen 52 and the second lumen 54 passes.
  • In 4 is the insert device 10 in combination with the handpiece 70 and the push rod 72 shown. The hand piece 70 has a relatively large continuous first passage opening 74 and a relatively small second passage opening 76 on. The hand piece 70 has a through hole 78 on, extending from the proximal end 80 after the distal end 82 of the handpiece extends. The proximal end section 84 of the handpiece 70 has an internal thread 86 on, that an external thread 88 of the proximal segment 90 a push rod 72 receives. The rod element 92 the push rod 72 stands through the hole 78 , the first lumen 52 , the second lumen 54 and into the open distal end 26 one. The hand piece 70 and the push rod 72 are made of metal, for example of a surgical stainless steel or similar metals.
  • The insert device 10 will open and work as follows: If it is intended to insert an IOL into the deployment device 10 insert, then the insert device, for example, manually arranged as in 3 is shown. When the loading chamber 12 is in the open position, becomes an IOL 100 For example, using tweezers, between the first and second links 16 and 18 inserted. The insert is such that the front surface 102 the optics 104 as in 1 shown facing up. The optics 104 consists of a polymeric silicone material. The haptic threads 106 and 108 the IOL 100 be like in 1 aligned so that the fixation members are generally parallel to the longitudinal axis 30 instead of being aligned across it.
  • If the IOL 100 according to 1 is inserted, the first and second parts 16 and 18 pivoted relative to each other, for example, manually by the first and second wings 38 and 40 be brought together to the loading chamber 12 in the closed position according to 3 to convict. When the loading chamber 12 is in the closed position, then the IOL 100 folded, that is the optics 104 is folded. The relative movement of the first and second link 16 and 18 to move the loading chamber from the open position to the closed position, this folding causes the lens. The folded IOL 100 is now in the first lumen 52 , For the sake of clarity, the folded IOL is in the 3 . 4 . 5 or 6 not shown.
  • When the insert device 10 according to 3 is arranged, and the folded IOL 100 in the first lumen 52 lies, then the insert device 10 in the handpiece 70 inserted as in 4 is shown. In this configuration, the end portion extends 24 of the insert tube fourteen distal over the distal end 82 of the handpiece 70 out. How out 5 can be seen, the distal section 85 of the handpiece 70 an inner wall 87 on, which is designed to hold the reinforcing sleeve 28 adjoining.
  • When the insert device 10 relative to the handpiece 70 is arranged, then the push rod 72 through the hole 78 of the handpiece, beginning at the proximal end 80 , Once the threads 88 into the threads 86 intervene, the push rod becomes 72 turned off, like out 6 seen, so that the thread the push rod to the proximal end portion 84 of the handpiece 70 shifts. By gradual movement of the push rod 92 through the hole 78 of the handpiece 70 , will the folded IOL 100 from the first lumen 52 into the second lumen 56 moved and then through the open distal end 26 in the eye.
  • According to 6 becomes the IOL 100 in the eye 120 used in an area formerly taken by the natural lens of the eye. 6 shows the sclera 122 with an incision through which the distal end portion 24 of the insert tube fourteen is introduced. Instead, the incision can also be made through the cornea. The distal end section 24 has a small enough cross section to get into the eye 122 through a 3.0 mm long incision in the sclera 122 to be used.
  • The insert tube fourteen gets inside the eye 122 manipulated until it lies so that the IOL 100 in the eye 122 can be correctly positioned, that is in the anterior chamber, the posterior chamber, the lacrimal sac 124 or in the sulcus, after release of the lens. This enables the surgeon to reach the distal end portion 24 of the insert tube fourteen in a controlled manner, with the IOL 100 in the first lumen 52 the loading chamber 12 lies. After the distal end section 24 positioned in this way, the rod element becomes 92 advanced distally by the butt member 72 in the handpiece 70 is screwed in, leaving the IOL 100 into the second lumen 54 and through it, and through the open distal end 26 of the insert tube fourteen in the eye 120 can be inserted. The front 102 the IOL 100 is generally in the eye 120 after when the IOL is out of the deployment device 10 is released. In other words, the IOL 100 goes through the first lumen 52 , the second lumen 54 and the open distal end 26 and gets into the eye 120 without the lens tipping over or being otherwise mispositioned. If anything, then only a very slight adjustment is necessary to the IOL 100 in the eye 120 to position correctly.
  • After the IOL 100 inserted into the eye, the push rod becomes 92 in the proximal direction into the insert tube fourteen moves, and the distal end portion 24 of the insert tube is removed from the eye. If necessary, the IOL 100 in the eye by a small curved needle or similar tool, which is inserted in the same incision.
  • After the IOL 100 in the eye 120 properly aligned, and the deployment device 10 withdrawn from the eye, then the incision in the sclera can be repaired using conventional techniques, for example. After use, the insert device becomes 10 preferably thrown away, the handpiece 70 and the push rod 72 can be reused after sterilization and disinfection.

Claims (10)

  1. Insert device ( 10 ) an apparatus for inserting an intraocular lens through an incision in an eye, comprising a polymer mixture containing or consisting of at least one thermoplastic polymer and at least one amphiphilic block copolymer selected from the group consisting of amphiphilic block copolymers having a hydrocarbon block of the formula CH 3 CH 2 (CH 2 CH 2 ) a , where "a" is 10, 11, 12, 13, 14, 15, 16, 17, 18, 19, 20, 21, 22, 23, 24 or 25 and a hydrophilic B Block.
  2. Insert device ( 10 ) according to claim 1, characterized in that at least one thermoplastic polymer is selected from the group consisting of polyolefins, PVC, polyurethanes (PUR), styrene-butadiene copolymer (SBC), thermoplastic elastomer, styrene-ethylene-butylene-styrene copolymers (SEBS) and mixtures or combinations thereof.
  3. Insert device ( 10 ) according to any one of the preceding claims, characterized in that the polyolefins are selected from the group consisting of polyethylene, polypropylene and blends thereof.
  4. Insert device ( 10 ) according to one of the preceding claims, characterized in that the B block is a hydrophilic oligomer, in particular a homo or co-oligomer containing or consisting of 2 to 10 monomer units derived from monomers selected from the group consisting of ethylene oxide, Propylene oxide, ethylene glycol, propylene glycol, epichlorohydrin, acrylic acid, methacrylic acid, ethyleneimine, caprolactone, vinyl alcohol and vinyl acetate.
  5. Insert device ( 10 ) according to one of the preceding claims, characterized in that the amphiphilic block copolymer constitutes 1.5 to 25 wt .-%, preferably 2 to 20 wt .-%, particularly preferably 3 to 15 wt .-% of the polymer mixture.
  6. Insert device ( 10 ) according to one of the preceding claims, characterized by a surface friction of less than 0.4 m, preferably less than 0.2, particularly preferably less than 0.1.
  7. Insert device ( 10 ) according to one of the preceding claims, characterized in that the polymer mixture has a gradient with respect to the B block, wherein the concentration of the B block on the surface of the insert device formed from the polymer mixture ( 10 ) is more than 2 to 60 times as high as the concentration of the B block in the center of the insert device ( 10 ).
  8. Insert device ( 10 ) according to one of the preceding claims, characterized in that the wear resistance of the insert device ( 10 ) compared to the wear resistance of a coated article surface of 1: 5 to 100: 1.
  9. Insert device ( 10 ) according to one of the preceding claims, comprising an insert tube ( fourteen ), which has an inner wall ( 53 ) having a cavity ( 54 ) defined by an intraocular lens ( 100 ) and one outlet ( 26 ), through which the intraocular lens from the cavity ( 54 ) is transferred to an eye, a loading chamber ( 12 ), which is a first link ( 16 ) and a second member ( 18 ), which are pivotally connected to each other.
  10. Device for inserting an intraocular lens through an incision in an eye, comprising an insertion device ( 10 ) according to one of the preceding claims, a handpiece ( 50 . 70 ), which has a through hole ( 78 ) extending from a proximal end ( 80 ) to a distal end ( 82 ) of the handpiece ( 50 . 70 ) and which has a receiving opening ( 5 ) for receiving an insert device ( 10 ) and a push rod ( 72 ), which in about the proximal end ( 80 ) into the hole ( 78 ) of the handpiece ( 50 . 70 ) can be introduced.
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Citations (2)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
DE69729450T2 (en) * 1996-07-10 2005-06-23 Advanced Medical Optics, Inc., Santa Ana An apparatus for inserting an intraocular lens and manufacturing method thereof
EP2316498A1 (en) * 2009-10-30 2011-05-04 Unomedical A/S A medical hollow tube article

Family Cites Families (1)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US4681102A (en) 1985-09-11 1987-07-21 Bartell Michael T Apparatus and method for insertion of an intra-ocular lens

Patent Citations (2)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
DE69729450T2 (en) * 1996-07-10 2005-06-23 Advanced Medical Optics, Inc., Santa Ana An apparatus for inserting an intraocular lens and manufacturing method thereof
EP2316498A1 (en) * 2009-10-30 2011-05-04 Unomedical A/S A medical hollow tube article

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