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WO1995002378A1 - Cristallin artificiel a blocage d'haptique ameliore - Google Patents

Cristallin artificiel a blocage d'haptique ameliore Download PDF

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Publication number
WO1995002378A1
WO1995002378A1 PCT/US1994/007798 US9407798W WO9502378A1 WO 1995002378 A1 WO1995002378 A1 WO 1995002378A1 US 9407798 W US9407798 W US 9407798W WO 9502378 A1 WO9502378 A1 WO 9502378A1
Authority
WO
WIPO (PCT)
Prior art keywords
haptic
haptics
distal end
optic body
pair
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/US1994/007798
Other languages
English (en)
Inventor
Robert Scott Rheinish
Allan R. Tonks
Thomas P. Richards
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.)
Kabi Pharmacia Ophthalmics Inc
Original Assignee
Kabi Pharmacia Ophthalmics Inc
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 Kabi Pharmacia Ophthalmics Inc filed Critical Kabi Pharmacia Ophthalmics Inc
Priority to EP94922529A priority Critical patent/EP0667755A4/fr
Priority to JP7504662A priority patent/JPH08501972A/ja
Publication of WO1995002378A1 publication Critical patent/WO1995002378A1/fr
Anticipated expiration legal-status Critical
Ceased legal-status Critical Current

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Classifications

    • 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
    • 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
    • A61F2002/1681—Intraocular lenses having supporting structure for lens, e.g. haptics
    • 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
    • A61F2002/1681—Intraocular lenses having supporting structure for lens, e.g. haptics
    • A61F2002/1683—Intraocular lenses having supporting structure for lens, e.g. haptics having filiform haptics
    • 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
    • A61F2002/1681—Intraocular lenses having supporting structure for lens, e.g. haptics
    • A61F2002/16903—Having means to temporarily stabilize haptic
    • 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
    • A61F2002/1681—Intraocular lenses having supporting structure for lens, e.g. haptics
    • A61F2002/16905—Having means on lens to reduce overall dimension of lens for insertion into small incision

Definitions

  • the present invention is in the field of intraocular lenses. More particularly, the present invention relates to intraocular lenses having elongate cantilevered haptic portions which at one proximal end thereof secure to an optic body of the lens, and at a distal end thereof are free. A distal end portion of the haptics define a foot portion whereat the haptic engages surrounding eye tissues to support and center the lens optic body in the eye.
  • the lens includes provisions to retain or lock the haptics at or adjacent their free distal ends into a constrained position in which the haptics are disposed more closely to the optic body.
  • Intraocular lenses are implanted in human eyes following removal of the natural lens because of injury, or more freguently, because of cataract.
  • the natural lens capsular hexis is incised, and the natural lens material is removed.
  • this natural lens removal is achieved with a phfacoemulsifier accompanied with irrigation and suction of the emulsified lens particles.
  • a surgical technigue which reduces trauma and speeds recovery time for the patient is favored. This technigue also allows sutureless or single-stitch closure of the principal surgical incision site.
  • the intraocular lens is reduced in size 5 by constraining the support structures, or haptics, of the lens.
  • the intraocular lens as so constrained is passed through the surgical tunnel incision inwardly and forwardly toward the inner surface of the cornea, and then is tipped inwardly to pass through the dilated iris and
  • This procedure involves the sequential release of the constrained lens so that a leading one of the haptics extends through the pupil of the iris and into the capsular bag. This leading haptic is followed by the optic body of the intraocular lens, and
  • the lens is rotated slightly to enter the trailing haptic into the capsular bag.
  • the intraocular lens provides an effective optical diameter which is as large as is practicable while retaining a diameter for the optic body which is still
  • the effective diameter of the lens support structure in the capsular bag may be from 10 to about 14 mm in order to supportingly engage the surrounding eye tissues.
  • the lens may have to pass
  • the optic body diameter of the lens may ' be limited to a diameter of about 5.5 or 6 mm, and the lens will be passed through a surgical tunnel made with an incision tool having a width equal to or just slightly
  • a conventional intraocular lens is known in accord with United States patent 4,615,701, issued 7 October 1986, to R. L. Woods. This patent to Woods is believed to teach a variety of intraocular lens designs which include
  • these lens designs include plural axially extending holes which allow the implanting physician after inserting the lens through an incision into the anterior chamber of the eye, to maneuver the lens through the iris into the ciliary sulcus, or more particularly, within the capsular bag, by use of a hooked manipulation tool.
  • the free ends of the haptics include axially extending end portions which hook into the axially extending holes at a peripheral portion of the lens optic body to temporarily constrain the haptics while the lens is inserted through the incision into the eye. Subsequently, the haptic distal ends are unhooked from the holes to allow the haptics to extend outwardly into supporting engagement with the surrounding eye tissues.
  • Such axially extending maneuvering holes present an optical difficulty for an intraocular lens.
  • This difficulty involves the refraction of light from the holes and the creation of objectionable glares, stars, or sunbursts, depending on the particulars of the lighting conditions, and the perceptions of the patient.
  • such lenses generally include a central portion of the optic body which is considered the optically active part of this body, and a peripheral portion integral with the optic body which is for physical attachment of the haptics, for the maneuvering holes, and for haptic constraint features.
  • this provision of a central optic portion and a surrounding peripheral portion of the optic body means that in order to provide an optic of a certain size, the lens must be larger by at least the size of the peripheral portion.
  • This increase in lens size above the active optic portion of the optic body is a great disadvantage because surgeons desire to keep the size of the surgical incision as small as possible.
  • the axially extending distal end portions of the haptics can irritate delicate eye tissues. This aspect is especially a concern with the tunnel-type of sutureless or single-stitch type of incision for lens insertion. With this type of incision the tunnel extends from the sclera somewhat upwardly toward the inner surface of the cornea.
  • the physician tips it downwardly to pass through the iris and into the capsular bag. Under these circumstances, the physician must be careful not to abrade or otherwise injure the inner surface of the cornea. Were a haptic to come loose at this time its distal end could damage the cornea inner surface. For this reason, reliable securement of the haptics is especially important. Also, in the event that securement of the haptics is lost at this moment in the procedure, preferably the haptics have a configuration of their distal end portions which inflicts only minimal or no trauma on the inner surface of the cornea.
  • the axially extending maneuvering holes of conventional intraocular lenses, as well as the peripheral haptic constraint features, such as holes, recesses, and cavities, taught by the Woods patent have a certain degree of undesirability because these features provide a possible sheltered and inaccessible harbor for bacteria, and for other contaminants in the surgical environment. While intraocular lenses having such holes and recess have been used successfully for years, a desirable objective in the art is to eliminate as much as is practicable such harbors for bacterial growth which also can capture and hold foreign contaminants.
  • an improved intraocular lens which includes features for temporarily constraining cantilevered haptic portions of the lens while the latter is inserted through an incision into an eye.
  • the haptics should be constrained temporarily and without damage in a position adjacent to the optic body of the lens to ease insertion of the lens through the surgical incision.
  • the constrain features should be easily and controllably disengageable once the lens is within the eye, while avoiding unintended disengagement while the lens is being inserted through the surgical incision.
  • the haptic constraint features should avoid as much as is possible the creation of refractive discontinuities of the optic body of the lens.
  • a primary object for the present invention is to provide an intraocular lens which substantially satisfies the above desirable goals for such a lens.
  • an objective for the present 5 invention is to provide an intraocular lens which includes an optic body and a support haptic at a proximal portion securing to the optic body and extending outwardly and circumferentially to supportingly engage eye tissue.
  • the intraocular lens includes temporary constraint features
  • This lens also includes either or both of a peripheral portion of the lens optic body which is circumferentially
  • the lens optic body is fully optically active, without a peripheral portion compromised in its optical performance by the presence of any holes, cavities, recesses, or other such features which could interfere
  • a pair of haptics secure to the optic body at diametrically opposite locations and extend outwardly and circumferentially to distal ends thereof. Each of the haptics adjacent its distal end defines a distal end portion with a small
  • the distal ends of the haptics are connected together by a loop of suture material, and are drawn together close to the periphery of the optic body. After the lens is within
  • the loop of suture material is clipped and removed.
  • the haptics then return toward their unconstrained positions to supportingly engage surrounding eye tissue.
  • the securement of the haptics is very reliable, and the distal ends of the haptics are free of features potentially damaging to eye tissues should the haptics get free inadvertently.
  • the full diameter of the optic body is optically active without compromising features.
  • one version of the present lens uses distal end portions of the haptics which are formed into almost completely closed shepherd's hooks. These hooks may be engaged very securely with one another in order to constrain the haptics for insertion of the lens through a surgical tunnel.
  • the shepherd's hook configuration of the haptic distal ends presents a rounded configuration with virtually no free haptic end which could gouge delicate eye tissues. That is, the end of the haptic is shielded from gouging into eye tissues by a closely adjacent medial shaft portion of the haptic.
  • FIG. 1 A radial boss outwardly of the optic body so that the full diameter of the optic body is optically active without compromising features.
  • This boss defines an axially open generally circumferential groove into which a medial shaft portion of the opposite haptic is receivable to constrain the haptic for surgical insertion into an eye.
  • the circumferential groove is not nearly so likely to catch bacteria or foreign matter contamination as is the peripheral edge features of conventional lenses.
  • the boss is defined by a portion of the haptics themselves which portion provides a transition to the optic body.
  • Other versions of the present lens provide a bite between the haptic and optic body which closes as the haptics are moved toward their constrained positions.
  • the distal end portions of the haptics are configured to capture in these bites, so that the haptics mutually constrain one another.
  • Yet another lens version uses a shallow groove formed by a bore nearly tangential to the lens optic body and extending therein as a complete bore only a short distance. A distal end of a haptic is captured in this shallow groove and bore.
  • the shallowness of the groove and bore avoids significant compromise of the optical function of the optic body, and also avoids harboring bacteria and other contamination at the surgical site.
  • Figures 1A and IB provide respective plan and side elevation views of an intraocular lens embodying the present invention
  • Figure 2 provides a plan view of the lens of Figures 1 in a condition with haptic portions thereof constrained preparatory to surgical implantation of the intraocular lens;
  • Figures 3 and 4 provide respective plan views of an alternative embodiment of intraocular lens according to the present invention in unconstrained and constrained conditions, respectively;
  • Figures 5 and 6 show respective plan views of yet another alternative embodiment of intraocular lens according to the present invention in unconstrained and constrained conditions, respectively;
  • Figure 5A is a fragmentary cross sectional view taken along line A-A of Figure 5;
  • Figures 7 and 8 provide respective plan views of still another alternative embodiment of intraocular lens according to the present invention in unconstrained and constrained conditions, respectively;
  • Figure 7A is a fragmentary cross sectional view taken along line A-A of Figure 7;
  • Figures 9 and 10 are respective plan views of an additional alternative embodiment of intraocular lens according to the present invention in unconstrained and constrained conditions, respectively;
  • Figures 11 and 12 show yet another alternative embodiment of the present intraocular lens in unconstrained and constrained positions, respectively;
  • Figures 13 and 14 provide plan views of yet another alternative embodiment of intraocular lens embodying the present invention in respective unconstrained and constrained positions;
  • Figure 13A is an enlarged fragmentary view of a portion of Figure 13;
  • Figures 15 and 16 likewise provide plan views of still another alternative embodiment of intraocular lens embodying the present invention, and in respective unconstrained and constrained conditions;
  • an intraocular lens 10 is seen in respective plan and elevation view.
  • the plan view of Figure 1A provides a view along the optic axis which the lens 10 will have when implanted in an eye.
  • the lens 10 includes a transparent optic body 12 of bi-convex configuration, and of selected dioptic strength to correct the vision of a patient whose natural lens has been removed, as is well understood.
  • the optic body portion 12 need not be of bi-convex configuration, but may equally be of plano-convex, concavo-convex, or of other configuration without departure from the present invention.
  • the optic body has an optically active zone, indicated with the numeral 12a, which encompasses the entire diameter of the optic body in the embodiment shown in Figures 1.
  • the optic body 12 is free of a conventional circumferential peripheral portion of the optic body, which portion is at least compromised (or perhaps is ineffective) optically because of, for example, axially extending maneuvering holes, vent holes, or various peripheral haptic constraint features defined in this peripheral portion of the optic body.
  • the haptics 14 may be integral with the optic body 12.
  • the entire lens 10 may be formed of a single piece of polymer material having acceptable optical and physical properties. Examples of such materials are polymethylmethacralate (PMMA) , and polypropylene.
  • PMMA polymethylmethacralate
  • these haptics 14 may also be joined to the optic body by thermal stake welding, adhesive or solvent bonding, ultrasonic welding, or other joining methods without departure from the present invention.
  • the optic body 12 may be made of a material such as PMMA which has outstanding optical properties and organic inertness, and the haptics may be made of a more flexible material such as polypropylene, which is also acceptably benign biologically.
  • the haptics 14 include a proximal transition portion 16 joining with the optic body 12, and a proximal curve section 18 leading to a medial shaft section 20.
  • the medial shaft section leads to a distal end foot portion 22, which terminates at a distal end 24.
  • the haptic 14 is an elongate, somewhat filamentary structure, which at its foot portion 22 supportingly engages and is pressed inwardly slightly toward the optic body by surrounding eye tissues when the lens 10 is in an eye. That is, when the lens 10 is implanted in an eye, the haptics 14 do not occupy their unconstrained positions as illustrated in Figure 1A, but are compressed inwardly radially toward the optic body 12.
  • the haptics 14 provide support and centration for the optic body 12 within the eye.
  • Figure 1A also illustrates that the haptics 14 at the distal foot portions 22 immediately adjacent to the distal ends 24 each define an aperture 26.
  • the entire optic body 12 of the lens 10 is of uniform optical integrity, and is without axially extending maneuvering holes which 'are conventionally used to move the lens 10 during a surgical procedure.
  • the optic body 12 defines an optically active and optically integral zone 12a which encompasses the entire diameter of this optic body. Accordingly, it is seen that the zone 12a of optical integrity for the optic body 12, and the diameter of this body are one and the same.
  • the lens 10 provides the largest possible optic diameter for a given size of lens which must be inserted through a surgical incision. It follows that the surgical incision which must be made in the eye in order to insert the lens 10 is as small as practicable for each particular optical diameter of lens required for various patients.
  • FIG 2 depicts that in preparation for surgical implantation of the lens 10, the haptics 14 are connected to one another by a loop 30 of suture thread.
  • This loop 30 is drawn taught to pull the haptics 14 at their distal end foot portions 22 adjacent to the peripheral edge surface 28 of the optic body 12.
  • the lens 10 may be advanced through a surgical incision, and particularly through a tunnel-type of sutureless or single-stitch incision, and into the capsular bag of an eye.
  • the loop 30 of suture material provides very secure constraint of the haptics 14, with virtually no risk that the haptics will inadvertently become freed and damage eye tissues as they return toward their unconstrained positions seen in Figure 1A.
  • the constrained lens of Figure 2 defines a diameter essentially the same as the diameter of optical zone 12a. This is the size of diameter which must be passed through the surgical incision and into the capsular bag of the eye. Consequently, the required incision need be no bigger than that required to pass the effective optical diameter 12a of the optic body 12.
  • the lens 10 does not include the conventional peripheral portion which is of compromised optical performance for the patient. Additionally, it follows that for a certain size of surgical incision, the lens 10 provides a larger centration error margin for positioning of the optic body 12. So long as the optic body 12 is within this centration error margin, the patients vision will not be compromised because the entire diameter of the optic body 12 has optical integrity not compromised by peripheral features.
  • FIGS 3 and 4 depict another alternative embodiment of the present inventive intraocular lens.
  • the intraocular lens 10' includes an optic body 12' having a fully effective optic diameter 12a'.
  • a pair of haptics 14' extend outwardly and circumferentially from proximal transition portions 16' which are disposed diametrically opposite to one another.
  • the haptics 14' include proximal curve sections 18', medial shaft sections 20', and distal end foot portions 22' terminating at respective distal ends 24'.
  • Lens 10' also includes a circumferential peripheral edge surface 28', which is continuous without interruption by holes, cavities, recesses or other features with exception of the transition portions 16', which are outside of the optical diameter 12a'.
  • the embodiment of Figures 3 and 4 does not include a distal end portion aperture 26 like the embodiment described above.
  • the haptics 14' each include a respective shepherd's crook feature, which is generally referenced with the numeral 32.
  • This shepherd's crook feature is formed by a portion 34 of the distal end portion 22' of the haptic which curls around inwardly toward the optic body 12 almost to the extent of having a free end 36 thereof contact the distal end portion 22'. Accordingly, in Figure 3 a dashed line 38 schematically depicts the ark of the surrounding eye tissues of the capsular bag. As can easily be seen 1 , when the haptics 14' are in the eye and supportingly engaging eye tissues, the shepherd's crook feature 32 presents only rounded and nonirritating surfaces to the eye tissues.
  • the shepherd's crook features 32 are engaged with one another to dispose the haptic distal end portions 22' adjacent the optic body 12'.
  • the distal end portions 22' of the haptics 14' actually cross over or under the optic body 12' to engage one another.
  • the lens 10' in its constrained haptic condition may pass through a tunnel incision which is only wide enough to pass the optic diameter 12a' of the optic body 12'. That is, this embodiment of the inventive intraocular lens also has no peripheral rim portion which is of compromised optical quality.
  • the lens 10' After the lens 10' is passed through the surgical incision and into the anterior chamber of the eye, it is tipped edge-on toward the dilated iris, and the haptics 14' are unhooked from one another to allow the leading one of the haptics to extend into the capsular bag.
  • the trailing haptic is constrained by a surgical tool, usually by a pair of forceps, and is released after or as the optic body follows the leading haptic into the posterior chamber. As before, a slight rotation of the lens 10' will ordinarily be sufficient to cause the trailing haptic to follow the lens optic 12 into the posterior chamber and to seat this haptic in the capsular bag.
  • an intraocular lens 10 includes an optic body 12 having a fully effective optic diameter 12a.
  • a pair of haptics 14 extend outwardly and circumferentially from proximal transition portions 16 which are disposed diametrically opposite to one another.
  • the haptics 14 include proximal curve sections 18, medial shaft sections 20, and distal end foot portions 22 terminating at respective distal ends 24.
  • Lens 10 also includes a circumferential peripheral edge surface 28, which is continuous without interruption by holes, cavities, recesses or other features with exception of the transition portions 16, and two other features yet to be explained, but all of which are outside of the optical diameter 12a.
  • the distal end portions 22 include a rounded bulbular end portion 40 which is advantageously gentle to contacted eye tissues.
  • Figures 5, and 5A illustrate that the lens 10 includes a pair of bosses, each referenced with the numeral 42, and each extending radially outwardly and circumferentially outside of the edge surface 28. That is, the bosses 42 lie outside of the diameter 12a of the optic body, and preferably are integral therewith. Each boss 42 defines an arcuate and axially opening groove 44, which is best seen in Figure 5A. Preferably, the grooves 44 open posteriorly. Viewing Figure 5A, it is seen that the bosses 42 define a radially outer and axially extending wall portion 46, which radially outwardly bounds the groove 44.
  • Figure 6 illustrates, in order to constrain the haptics for insertion of the lens through a surgical incision and into an eye, the haptics are temporarily forced radially inwardly at their distal end foot portions 22, so that these portions are received into the grooves and engage the wall portions 46.
  • the dashed line outline of Figure 5A shows the cross section of the haptic 14 as it appears when the haptic is captured and constrained in the groove 44 of boss 42.
  • the lens 10 seen in Figure 6 is only slightly larger in diameter than the diameter 12a of the optic body 12, which is the same as the effective optical diameter of the optic body 12. Because the radial dimension of the haptics 14 is small in comparison to the diameter of the optic body 12, the lens 10 can be passed through a surgical incision which is only very slightly larger than the diameter 12a of the optical body 12.
  • the haptics 14 are released from the bosses 42, and the insertion of the lens into the capsular bag of the eye is completed much as described above.
  • Figures 7, 7A, and 8 depict another alternative embodiment of the present inventive intraocular lens in which the functions of the transitions portions 16 of the lens and of the bosses 42 seen in the embodiment of Figures 5, 5A, and 6 are combined into a single structural feature. Because these structural features combine functions described above, primes are used in referring to these features so that the reader will understand that a functionally equivalent, but not necessarily structurally identical, feature is being referenced.
  • the transition portions 16' are , provided with a circumferentially extending and axially opening groove 44'. Again, this groove is bounded radially outwardly by a wall portion 46' of the transition portion 16'.
  • FIG 8 illustrates, in the constrained-haptic condition of the lens 10, the distal foot portions 22 of the haptics 14 are forced radially inwardly and into the grooves 44'. As so captured, the haptics 14 lie immediately outwardly of the peripheral edge surface 28 of the optic body 12. Consequently, the lens 10 of Figures 7-8 can be inserted into an eye through an incision which is only slightly larger than the diameter and effective optical diameter of the optic body 12.
  • Figures 9 and 10 depict an alternative embodiment of the present inventive intraocular lens. Again, reference numerals introduced above are used to refer to features of the lens of these drawing Figures which are analogous in structure or function to those described above. Consequently, it is seen that the lens 10 includes an optic body 12 having a fully effective optic diameter 12a.
  • a pair of haptics 14 extend outwardly and circumferentially from proximal transition portions 16 which are disposed diametrically opposite to one another.
  • the haptics 14 include proximal curve sections 18, medial shaft sections 20, and distal end foot portions 22 terminating at respective distal ends 24.
  • Lens 10 also includes a circumferential peripheral edge surface 28, which is continuous without interruption by holes, cavities, recesses or other features with exception of the transition portions 16, which are outside of the optical diameter 12a.
  • the distal end portions 22 include a rounded bulbular end portion 40 which is advantageously gentle to contacted eye tissues.
  • the transition portions 16 and proximal curve sections 18 are swept circumferentially with respect to the optic body 12. That is, these transition and proximal curve features are disposed somewhat tangentially with respect to a tangent at the diameter of peripheral outer surface 28. Consequently, the outer surface 28 in conjunction with the medial section 20 of haptic 14 immediately adjacent to the proximal curve section 18 cooperatively define a bite, which is referenced with the numeral 48.
  • This bite 48 is configured to be slightly larger in radial dimension 50 than the radial thickness 52 of the distal foot portion 22 of the haptics 14.
  • the bulbular distal end portion 40 is sized to be slightly larger than the bite 48.
  • Figure 10 illustrates the constrained-haptic condition for the lens of Figures 9 and 10.
  • the haptics 14 are forced radially inwardly at their distal end foot portions 22. This radially inward movement of the haptics 14 slightly closes the bites 48. Additionally, the distal foot portions 22 are forced slightly out of the plane of the optic body 12 so that the bulbular end portion 40 passes the bite 48 far enough to be received between the surface 28 of the optic body 12 and the medial shaft portion 20 of the other haptic.
  • the bulbular end portion 40 is placed axially into and slightly beyond the space between the optic body 12 and the other haptic, and is moved into the bite 48.
  • the haptics at their transition portions 16 and proximal curve sections 18, and in cooperation with the peripheral surface 28 of the optic body 12 defining bites 48 capture each other in the constrained-haptic condition of the lens 10.
  • the haptics 14 are easily released from their condition of Figure 10, and extend toward their condition of Figure 9. Consequently, the haptics 14 of Figures 9 and 10 also present gently rounded surfaces at the bulbular end features 40 to the engaged eye tissue.
  • Intraocular lens 10 includes an optic body 12 having a fully effective optic diameter 12a.
  • a pair of haptics 14 extend outwardly and circumferentially from proximal transition portions 16 which are disposed diametrically opposite to one another.
  • the haptics 14 include proximal curve sections 18, medial shaft sections 20, and distal end foot portions 22 terminating at respective distal ends 24.
  • Lens 10 also includes a circumferential peripheral edge surface 28, which is continuous without interruption by holes, cavities, recesses or other features with the exception of the transition portions 16, which are outside of the optical diameter 12a.
  • the distal end portions 22 include a rounded bulbular end portion 40 which is advantageously gentle to contacted eye tissues.
  • the embodiment of Figures 11 and 12 includes a radially inwardly concave reentrant curve 54 defined by the medial shaft section 20 of the haptics 14. This reentrant curve 54 of the shaft section 20 cooperates with the adjacent proximal curve section 18 to define a cove 56.
  • the medial shaft portion 20 defines a radially inwardly convex curve 58, so that a radially inward projection 60 is defined by the shaft portion 20 distally of the cove 56.
  • the foot portion 22 of the haptics 14 and distally in succession along the length of the haptic, the latter define a radially inwardly concave curve 62, a radially inwardly convex curve 64, and a radially inwardly concave curve 66.
  • the foot portion 22 includes a radially outwardly disposed recess at 68, and a radially outwardly extending projection 70 disposed immediately distally of the recess 68 and proximally of the bulbular end 40.
  • the haptics 14 present only gently rounded surface features to supporting eye tissues in the foot portions 22.
  • the lens 10 can be placed in a constrained-haptic condition by forcing the distal foot portions 22 radially inwardly so that the recess 68 is disposed at the reentrant curve 54 of the medial haptic portion adjacent to proximal curve section 18, and at cove
  • the lens 10 of Figures 11 and 12 may be passed into an eye through an incision which is only slightly larger than the diameter of the optic body 12. Once inside the eye, the haptics 14 are easily released from their constrained condition, and extend toward their unconstrained condition seen in Figure 11. Implantation of the lens 10 of Figures 11 and 12 is completed much as described above.
  • Intraocular lens 10 includes an optic body 12 having a substantially fully effective optic diameter 12a.
  • a pair of haptics 14 extend outwardly and circumferentially from proximal transition portions 16 which are disposed diametrically opposite to one another.
  • the haptics 14 include proximal curve sections 18, medial shaft sections 20, and distal end foot portions 22 terminating at respective distal ends 24.
  • Lens 10 also includes a circumferential peripheral edge surface 28, which in this instance is interrupted by a pair of shallow circumferentially extending grooves 72.
  • the grooves 72 are shallow because they are formed by the transection of surface 28 by a pair of comparatively short blind bores 74 extending along lines 76 which are tangent to a circle 78 at a diameter only slightly less than the diameter 12a of the optic body 12.
  • the diameter of the bores 74 is selected to snugly receive the distal end foot portion 22 of the haptics 14.
  • the distal end foot portions 22 of the haptics 14 are essentially of a constant dimension along their length and follow a smooth spiral curve.
  • the diameter of circle 78 is selected with a view to the dimension of the distal end portion 22 of the haptics 14 so that a blind end wall 80 of the bore is spaced only slightly from an adjacent end 82 of the groove 72, and the bore 74 defines a short side wall 84.
  • the end 82 of groove 72 is also an end of the side wall 84.
  • the length of side wall 84 is that length of the bores 74 which is completely surrounded by the material of the optic body 12. Outwardly of the end 82 of the wall 84, the bores 74 break through the surface 28, and define the grooves 72 on the surfaces 28.
  • the lines 76 are tangent to the circle 78 at a diameter just slightly less than the full diameter of the optic body 12, the latter has an optically effective diameter which is substantially the same as the diameter of the optic body 12 itself. That is, the encroachment of the bores 74 into the optically effective diameter of the optic body 12 is not very much in the radial sense, and is of very limited circumferential extent so that the great majority of the optic body 12 is fully effective optically and is not compromised by the presence of the bores 74.
  • Figure 14 illustrates that the lens 10 of Figures 13 and 14 may be placed into its constrained-haptic condition by forcing the distal end foot portions 22 of the haptics 14 radially inwardly toward the peripheral surface 28, and then axially along the length of the haptic at its distal end foot portion 22 into the respective bores 74.
  • the haptics 14 may have to be sprung slightly radially inwardly at their foot portions to align these portions with the bores 74.
  • the bores 74 are sized to snugly receive the distal end foot portions 22 of the haptics 14.
  • the foot portions may be a snug slip fit into the bores 74, or a slight interference fit may be employed to retain the foot portions 22 in the bores 74.
  • the snugness of the fit between the bores 74 and the foot portions 22, along with a possible misalignment of the foot portion with the bores 74 may be effective to bind and retain the foot portions in the bores 74. If a slight interference fit is employed between the foot portions 22 and the bores 74, then these features will be engaged with one another forcefully by the use of forceps or other tools. However, recalling the small scale of the intraocular lens 10 and its haptics 14, as well as the polymeric nature of the materials of construction, it is to be appreciated that the force level necessary to engage the haptic foot portions 22 into the bores 74 will not be very great.
  • FIG. 15 and 16 illustrate another alternative embodiment of the intraocular lens according to the present invention.
  • the lens 10 of Figures 15 and 16 is just like that of Figures 13 and 14, with the exception of features to be described. Consequently, the by-now familiar reference numerals are again used to refer to features which are analogous in structure or function to features described above.
  • the lens 10 of Figures 15 and 16 includes haptics 14 with a radially inwardly extending boss 86 defined at the distal extent of the medial haptic section about where the distal end foot portion of the haptic begins. This boss 86 defines an aperture 88.
  • Figure 16 illustrates that the lens 10 of Figures 15 and 16 may be placed in its constrained-haptic condition by forming a loop 30 of suture material through the apertures 88 and connecting the bosses 86.
  • This suture material loop is similar to the feature seen in Figure 2, except that the lens 10 of Figures 15 and 16 includes the bores 74 for additionally receiving the distal end portions 22 of the haptics 14. Consequently, as the loop 30 is drawn tight, the distal end portions 22 are inserted into the bores 74, and the lens 10 in its constrained-haptic condition is without free or exposed haptic ends which might catch on eye tissues at the surgical incision.

Landscapes

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

Abstract

Un cristallin artificiel (10) comprend un corps optique (12) et une paire d'haptiques-support (14) allongés diamétralement opposés s'étendant radialement vers l'extérieur et sur la circonférence du corps optique (12) afin de former la base (22) de l'extrémité distale venant en contact par appui avec le tissu occulaire et se terminant en une extrémité distale (24) destinée à l'haptique. Dans une première position des haptiques, les bases (22) des extrémités distales sont espacées du corps optique (12). Une partie du corps optique (12) et des haptiques-support (14) forme des éléments de contrainte libérables qui viennent en contact avec une partie du corps optique (12) ou l'une des paires d'haptiques (14) afin de contraindre l'haptique (14) en une seconde position où la base (22) de l'extrémité distale de celle-ci est adjacente au corps optique (12). Dans la seconde configuration du cristallin artificiel (10), il est possible d'introduire le cristallin artificiel (10) dans l'÷il en pratiquant une incision à peine légèrement plus grande que la taille du corps optique.
PCT/US1994/007798 1993-07-13 1994-07-11 Cristallin artificiel a blocage d'haptique ameliore Ceased WO1995002378A1 (fr)

Priority Applications (2)

Application Number Priority Date Filing Date Title
EP94922529A EP0667755A4 (fr) 1993-07-13 1994-07-11 Cristallin artificiel a blocage d'haptique ameliore.
JP7504662A JPH08501972A (ja) 1993-07-13 1994-07-11 改良された支持固定装置を有する眼内レンズ

Applications Claiming Priority (2)

Application Number Priority Date Filing Date Title
US9161893A 1993-07-13 1993-07-13
US091,618 1993-07-13

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WO1995002378A1 true WO1995002378A1 (fr) 1995-01-26

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JP (1) JPH08501972A (fr)
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US7107106B2 (en) 1995-05-15 2006-09-12 Cardinal Health 303, Inc. System and method for collecting data and managing patient care
WO2012037550A1 (fr) * 2010-09-17 2012-03-22 Henry Ford Health System Anneau pour pupille
RU2550002C2 (ru) * 2013-08-02 2015-05-10 федеральное государственное бюджетное учреждение "Межотраслевой научно-технический комплекс "Микрохирургия глаза" имени академика С.Н. Федорова" Министерства здравоохранения Российской Федерации Искусственный хрусталик глаза
WO2017079733A1 (fr) * 2015-11-06 2017-05-11 Powervision, Inc. Lentilles intraoculaires d'accommodation et procédés de fabrication
US9795473B2 (en) 2002-12-12 2017-10-24 Powervision, Inc. Accommodating intraocular lenses
US9855139B2 (en) 2007-07-23 2018-01-02 Powervision, Inc. Intraocular lens delivery systems and methods of use
US9872762B2 (en) 2002-12-12 2018-01-23 Powervision, Inc. Accommodating intraocular lenses
US9872763B2 (en) 2004-10-22 2018-01-23 Powervision, Inc. Accommodating intraocular lenses
US10045844B2 (en) 2002-02-02 2018-08-14 Powervision, Inc. Post-implant accommodating lens modification
CN109124828A (zh) * 2018-09-05 2019-01-04 厦门大学附属厦门眼科中心有限公司 巩膜固定型人工晶体及其对准方法
US10195020B2 (en) 2013-03-15 2019-02-05 Powervision, Inc. Intraocular lens storage and loading devices and methods of use
GB2565152A (en) * 2017-08-04 2019-02-06 Rayner Intraocular Lenses Ltd Intraocular lens
US10299913B2 (en) 2009-01-09 2019-05-28 Powervision, Inc. Accommodating intraocular lenses and methods of use
US10390937B2 (en) 2007-07-23 2019-08-27 Powervision, Inc. Accommodating intraocular lenses
US10433949B2 (en) 2011-11-08 2019-10-08 Powervision, Inc. Accommodating intraocular lenses
US10433950B2 (en) 2002-02-02 2019-10-08 Powervision, Inc. Accommodating intraocular lenses
US10534113B2 (en) 2003-03-06 2020-01-14 Powervision, Inc. Adaptive optic lens and method of making
US10595989B2 (en) 2010-07-09 2020-03-24 Powervision, Inc. Intraocular lens delivery devices and methods of use
US10835373B2 (en) 2002-12-12 2020-11-17 Alcon Inc. Accommodating intraocular lenses and methods of use
US10980629B2 (en) 2010-02-23 2021-04-20 Alcon Inc. Fluid for accommodating intraocular lenses
US11471272B2 (en) 2019-10-04 2022-10-18 Alcon Inc. Adjustable intraocular lenses and methods of post-operatively adjusting intraocular lenses
US12059342B2 (en) 2015-06-10 2024-08-13 Alcon Inc. Intraocular lens materials and components
US12245930B2 (en) 2023-06-30 2025-03-11 Alcon Inc. System and methods for compensating for intraocular lens tilt
US12446774B2 (en) 2021-04-06 2025-10-21 Alcon Inc. Apparatus, systems, and methods for objectively assessing accommodation in an eye

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US7036931B2 (en) * 2003-01-29 2006-05-02 Novartis Ag Ophthalmic lenses
JP5398092B1 (ja) * 2012-06-15 2014-01-29 株式会社中京メディカル 眼内レンズ
US9445891B2 (en) 2014-04-24 2016-09-20 Chukyo Medical Co., Inc. Intraocular lens
US11622850B2 (en) * 2017-11-01 2023-04-11 Alcon Inc. Intraocular lenses and peripheral portion stabilization
JP7122790B1 (ja) * 2022-04-14 2022-08-22 株式会社中京メディカル 眼内レンズ及び眼内レンズ支持部の製造方法

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Publication number Priority date Publication date Assignee Title
US7107106B2 (en) 1995-05-15 2006-09-12 Cardinal Health 303, Inc. System and method for collecting data and managing patient care
US10433950B2 (en) 2002-02-02 2019-10-08 Powervision, Inc. Accommodating intraocular lenses
US10045844B2 (en) 2002-02-02 2018-08-14 Powervision, Inc. Post-implant accommodating lens modification
US10835373B2 (en) 2002-12-12 2020-11-17 Alcon Inc. Accommodating intraocular lenses and methods of use
US9795473B2 (en) 2002-12-12 2017-10-24 Powervision, Inc. Accommodating intraocular lenses
US9855137B2 (en) 2002-12-12 2018-01-02 Powervision, Inc. Accommodating intraocular lenses and methods of use
US9872762B2 (en) 2002-12-12 2018-01-23 Powervision, Inc. Accommodating intraocular lenses
US11751991B2 (en) 2002-12-12 2023-09-12 Alcon Inc. Accommodating intraocular lenses and methods of use
US10534113B2 (en) 2003-03-06 2020-01-14 Powervision, Inc. Adaptive optic lens and method of making
US9872763B2 (en) 2004-10-22 2018-01-23 Powervision, Inc. Accommodating intraocular lenses
US10368979B2 (en) 2006-12-19 2019-08-06 Powervision, Inc. Accommodating intraocular lenses
US9855139B2 (en) 2007-07-23 2018-01-02 Powervision, Inc. Intraocular lens delivery systems and methods of use
US10350060B2 (en) 2007-07-23 2019-07-16 Powervision, Inc. Lens delivery system
US10390937B2 (en) 2007-07-23 2019-08-27 Powervision, Inc. Accommodating intraocular lenses
US11759313B2 (en) 2007-07-23 2023-09-19 Alcon Inc. Lens delivery system
US12318279B2 (en) 2007-07-23 2025-06-03 Alcon Inc. Lens delivery system
US11166808B2 (en) 2009-01-09 2021-11-09 Alcon Inc. Accommodating intraocular lenses and methods of use
US10299913B2 (en) 2009-01-09 2019-05-28 Powervision, Inc. Accommodating intraocular lenses and methods of use
US10357356B2 (en) 2009-01-09 2019-07-23 Powervision, Inc. Accommodating intraocular lenses and methods of use
US10980629B2 (en) 2010-02-23 2021-04-20 Alcon Inc. Fluid for accommodating intraocular lenses
US11737862B2 (en) 2010-02-23 2023-08-29 Alcon Inc. Fluid for accommodating intraocular lenses
US12419738B2 (en) 2010-02-23 2025-09-23 Alcon Inc. Fluid for accommodating intraocular lenses
US10595989B2 (en) 2010-07-09 2020-03-24 Powervision, Inc. Intraocular lens delivery devices and methods of use
US11779456B2 (en) 2010-07-09 2023-10-10 Alcon Inc. Intraocular lens delivery devices and methods of use
WO2012037550A1 (fr) * 2010-09-17 2012-03-22 Henry Ford Health System Anneau pour pupille
US10433949B2 (en) 2011-11-08 2019-10-08 Powervision, Inc. Accommodating intraocular lenses
US11484402B2 (en) 2011-11-08 2022-11-01 Alcon Inc. Accommodating intraocular lenses
US11071622B2 (en) 2013-03-15 2021-07-27 Alcon Inc. Intraocular lens storage and loading devices and methods of use
US10195020B2 (en) 2013-03-15 2019-02-05 Powervision, Inc. Intraocular lens storage and loading devices and methods of use
US12226309B2 (en) 2013-03-15 2025-02-18 Alcon Inc. Intraocular lens storage and loading devices and methods of use
US11793627B2 (en) 2013-03-15 2023-10-24 Alcon Inc. Intraocular lens storage and loading devices and methods of use
RU2550002C2 (ru) * 2013-08-02 2015-05-10 федеральное государственное бюджетное учреждение "Межотраслевой научно-технический комплекс "Микрохирургия глаза" имени академика С.Н. Федорова" Министерства здравоохранения Российской Федерации Искусственный хрусталик глаза
US12059342B2 (en) 2015-06-10 2024-08-13 Alcon Inc. Intraocular lens materials and components
US11426270B2 (en) 2015-11-06 2022-08-30 Alcon Inc. Accommodating intraocular lenses and methods of manufacturing
CN108348328B (zh) * 2015-11-06 2020-04-10 力景公司 可调节人工晶状体和制造方法
WO2017079733A1 (fr) * 2015-11-06 2017-05-11 Powervision, Inc. Lentilles intraoculaires d'accommodation et procédés de fabrication
CN108348328A (zh) * 2015-11-06 2018-07-31 力景公司 可调节人工晶状体和制造方法
GB2565152B (en) * 2017-08-04 2020-06-03 Rayner Intraocular Lenses Ltd Intraocular lens
GB2565152A (en) * 2017-08-04 2019-02-06 Rayner Intraocular Lenses Ltd Intraocular lens
CN109124828A (zh) * 2018-09-05 2019-01-04 厦门大学附属厦门眼科中心有限公司 巩膜固定型人工晶体及其对准方法
CN109124828B (zh) * 2018-09-05 2024-04-23 厦门眼科中心有限公司 巩膜固定型人工晶体及其对准方法
US11660182B2 (en) 2019-10-04 2023-05-30 Alcon Inc. Adjustable intraocular lenses and methods of post-operatively adjusting intraocular lenses
US12167959B2 (en) 2019-10-04 2024-12-17 Alcon Inc. Adjustable intraocular lenses and methods of post-operatively adjusting intraocular lenses
US12370040B2 (en) 2019-10-04 2025-07-29 Alcon Inc. Adjustable intraocular lenses and methods of post-operatively adjusting intraocular lenses
US11471272B2 (en) 2019-10-04 2022-10-18 Alcon Inc. Adjustable intraocular lenses and methods of post-operatively adjusting intraocular lenses
US12446774B2 (en) 2021-04-06 2025-10-21 Alcon Inc. Apparatus, systems, and methods for objectively assessing accommodation in an eye
US12245930B2 (en) 2023-06-30 2025-03-11 Alcon Inc. System and methods for compensating for intraocular lens tilt

Also Published As

Publication number Publication date
EP0667755A1 (fr) 1995-08-23
EP0667755A4 (fr) 1996-03-27
JPH08501972A (ja) 1996-03-05

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