US20140232025A1 - Manufacturing method for shape memory polymer intraocular devices - Google Patents

Manufacturing method for shape memory polymer intraocular devices Download PDF

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Publication number
US20140232025A1
US20140232025A1 US13/500,884 US201213500884A US2014232025A1 US 20140232025 A1 US20140232025 A1 US 20140232025A1 US 201213500884 A US201213500884 A US 201213500884A US 2014232025 A1 US2014232025 A1 US 2014232025A1
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smp
lens
intraocular device
canceled
intraocular
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US13/500,884
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Malik Y. Kahook
Naresh Mandava
Robin Shandas
Bryan Rech
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University of Colorado
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University of Colorado
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Priority to US13/500,884 priority Critical patent/US20140232025A1/en
Assigned to THE REGENTS OF THE UNIVERSITY OF COLORADO, A BODY CORPORATE reassignment THE REGENTS OF THE UNIVERSITY OF COLORADO, A BODY CORPORATE ASSIGNMENT OF ASSIGNORS INTEREST (SEE DOCUMENT FOR DETAILS). Assignors: SHANDAS, ROBIN, RECH, BRYAN, KAHOOK, MALIK Y., MANDAVA, Naresh
Assigned to THE REGENTS OF THE UNIVERSITY OF COLORADO, A BODY CORPORATE reassignment THE REGENTS OF THE UNIVERSITY OF COLORADO, A BODY CORPORATE ASSIGNMENT OF ASSIGNORS INTEREST (SEE DOCUMENT FOR DETAILS). Assignors: SHANDAS, ROBIN, RECH, BRYAN, KAHOOK, MALIK Y., MANDAVA, Naresh
Publication of US20140232025A1 publication Critical patent/US20140232025A1/en
Priority to US15/157,214 priority patent/US10286105B2/en
Priority to US15/157,141 priority patent/US10272176B2/en
Priority to US15/157,260 priority patent/US10286106B2/en
Priority to US15/157,290 priority patent/US10286107B2/en
Priority to US16/012,663 priority patent/US20180296726A1/en
Abandoned legal-status Critical Current

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    • B—PERFORMING OPERATIONS; TRANSPORTING
    • B29—WORKING OF PLASTICS; WORKING OF SUBSTANCES IN A PLASTIC STATE IN GENERAL
    • B29D—PRODUCING PARTICULAR ARTICLES FROM PLASTICS OR FROM SUBSTANCES IN A PLASTIC STATE
    • B29D11/00—Producing optical elements, e.g. lenses or prisms
    • B29D11/02—Artificial eyes from organic plastic material
    • B29D11/023—Implants for natural eyes
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    • A61F2/00—Filters implantable into blood vessels; Prostheses, i.e. artificial substitutes or replacements for parts of the body; Appliances for connecting them with the body; Devices providing patency to, or preventing collapsing of, tubular structures of the body, e.g. stents
    • A61F2/02—Prostheses implantable into the body
    • A61F2/14—Eye parts, e.g. lenses, corneal implants; Implanting instruments specially adapted therefor; Artificial eyes
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    • 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
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    • A—HUMAN NECESSITIES
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    • A61L—METHODS 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
    • A61L27/00—Materials for grafts or prostheses or for coating grafts or prostheses
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    • A61L—METHODS 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
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    • B29C61/00—Shaping by liberation of internal stresses; Making preforms having internal stresses; Apparatus therefor
    • B29C61/003—Shaping by liberation of internal stresses; Making preforms having internal stresses; Apparatus therefor characterised by the choice of material
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    • A61F2/142—Cornea, e.g. artificial corneae, keratoprostheses or corneal implants for repair of defective corneal tissue
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    • 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
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    • A61F2210/00—Particular material properties of prostheses classified in groups A61F2/00 - A61F2/26 or A61F2/82 or A61F9/00 or A61F11/00 or subgroups thereof
    • A61F2210/0014—Particular material properties of prostheses classified in groups A61F2/00 - A61F2/26 or A61F2/82 or A61F9/00 or A61F11/00 or subgroups thereof using shape memory or superelastic materials, e.g. nitinol
    • A—HUMAN NECESSITIES
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    • A61F2210/00—Particular material properties of prostheses classified in groups A61F2/00 - A61F2/26 or A61F2/82 or A61F9/00 or A61F11/00 or subgroups thereof
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    • A61F2210/0019—Particular material properties of prostheses classified in groups A61F2/00 - A61F2/26 or A61F2/82 or A61F9/00 or A61F11/00 or subgroups thereof using shape memory or superelastic materials, e.g. nitinol operated at only one temperature whilst inside or touching the human body, e.g. constrained in a non-operative shape during surgery, another temperature only occurring before the operation
    • 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
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    • A61L2430/00—Materials or treatment for tissue regeneration
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    • C08F220/00—Copolymers of compounds having one or more unsaturated aliphatic radicals, each having only one carbon-to-carbon double bond, and only one being terminated by only one carboxyl radical or a salt, anhydride ester, amide, imide or nitrile thereof
    • C08F220/02—Monocarboxylic acids having less than ten carbon atoms; Derivatives thereof
    • C08F220/10—Esters
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    • C08F220/16—Esters of monohydric alcohols or phenols of phenols or of alcohols containing two or more carbon atoms
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    • C08F220/00—Copolymers of compounds having one or more unsaturated aliphatic radicals, each having only one carbon-to-carbon double bond, and only one being terminated by only one carboxyl radical or a salt, anhydride ester, amide, imide or nitrile thereof
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    • C08F220/302—Esters containing oxygen in addition to the carboxy oxygen containing aromatic rings in the alcohol moiety and two or more oxygen atoms in the alcohol moiety

Definitions

  • the technology described herein relates to artificial intraocular lenses.
  • the human eye functions to provide vision by transmitting light through a clear outer portion called the cornea, and focusing the image by way of a crystalline lens onto a retina.
  • the quality of the focused image depends on many factors including the size and shape of the eye, and the transparency of the cornea and the lens.
  • IOL intraocular lens
  • Intraocular lenses are employed as replacements for the crystalline lens after either extracapsular or intracapsular surgery for the removal of a cataract.
  • the majority of cataractous lenses are removed by a surgical technique called phacoemulsification.
  • phacoemulsification a surgical technique used to remove cataractous lenses.
  • an opening is made in the anterior capsule and a thin phacoemulsification cutting tip is inserted into the diseased lens and vibrated ultrasonically.
  • the vibrating cutting tip liquefies or emulsifies the lens so that the lens may be aspirated out of the eye.
  • the diseased lens once removed, is replaced by an artificial lens.
  • Intraocular lenses are generally of two types, those that are placed in the anterior chamber, i.e., between the iris and the cornea, and those that are placed in the posterior chamber, i.e., behind the iris. Both types of lenses are conventionally employed with the choice between an anterior chamber and a posterior chamber lens being partly dictated by requirements of the patient and partly dictated by the preferences of the physician inserting the lens.
  • a third type of lens known as iris-fixated lenses because they are secured to the iris periphery, can be thought of as being within one of the two types above, in that their optic portion is in either the anterior or posterior chamber.
  • Intraocular lenses normally consist of an optic with at least one and preferably two or more haptics that extend generally radially from the optic and contain distal portions that normally seat in the scleral spur for an anterior chamber lens and either in the ciliary sulcus or within the lens capsule for a posterior chamber lens.
  • the optic normally comprises a circular transparent optical lens.
  • the haptic in most lenses is a flexible fiber or filament having a proximate end affixed to the lens and having a distal end extending radially away from the periphery of the lens to form a seating foot.
  • Several haptic designs are currently in use, for example, a pair of C-shaped loops in which both ends of each loop are connected to the lens, and, for example, J-shaped loops in which only one end of the loop is affixed to the lens.
  • Haptics are usually radially resilient and extend outwardly from the periphery of the lens and gently, but elastically, engage appropriate circumferential eye structures adjacent the iris or within the capsular bag. This resiliency is due to the conventional elastic properties of the materials of the haptic. The result is a haptic which when compressed and released will uncontrollably spring back immediately. This property makes the process of implantation and final positioning of the lens difficult since the haptics must be constrained during implantation. Also, once situated, the flexibility of the conventional haptic material makes the lens susceptible to decentration from being pushed by vitreous pressure from behind the lens or shifting due to pressure from adjacent ocular tissue. Also, the forces generated by the elastic recoil of the haptic release may damage the delicate local tissue.
  • the optimum position for a posterior chamber lens is in the capsular bag. This is an extremely difficult maneuver for the surgeon to accomplish.
  • a posterior chamber lens When a posterior chamber lens is employed it must be placed through the small pupillary opening, and the final haptic position is hidden behind the iris and not visible to the surgeon. It is therefore highly desirable to keep the overall dimensions of the posterior chamber lens as small as possible during implantation, letting it expand when it is finally situated where the surgeon intends, usually in the capsular bag.
  • a small device is easier to manipulate in the eye, reduces the chance of the haptics coming in contact with the corneal endothelial tissue, and allows the surgeon ease of insertion, as he must often insert a lens with a 14 mm overall dimension through a pupil of 5 to 8 mm diameter.
  • a smaller lens also reduces the lens/iris contact and can better guarantee that the intraocular lens and its haptics will be in the capsular bag.
  • intraocular lenses with and without haptics having relatively soft body portions have been provided such that the body portion could be folded generally across the diameter thereof for insertion into a smaller opening during implantation of the lens.
  • Lenses formed of liquid or hydrogel constrained within a sheath have been designed which allow the lens body to be folded before insertion and then subsequently filled when in position.
  • the soft materials used for the bodies of these lenses lack the restorative strength sometimes required to return to their original shape.
  • these lens types are typically deployed using either an elastic release mechanism, wherein mechanical energy stored by bending the elastic material is released when the mechanical constraint is removed, or through water uptake, also known as hydration, wherein the lens gradually absorbs water through an osmotic diffusion process. Both processes are difficult to control.
  • the elastic recoil may damage local tissue or may move the lens away from the center.
  • the ultimate shape of the lens may become distorted if the expanding lens comes into contact with surrounding tissue.
  • hydrating materials are known to possess poor shape recovery properties.
  • the natural lens In the natural lens, bifocality of distance and near vision is provided by a mechanism known as accommodation.
  • the natural lens early in life, is soft and contained within the capsular bag.
  • the bag is suspended from the ciliary muscle by the zonules. Relaxation of the ciliary muscle tightens the zonules, and stretches the capsular bag. As a result, the natural lens tends to flatten. Tightening of the ciliary muscle relaxes the tension on the zonules, allowing the capsular bag and the natural lens to assume a more rounded shape. In this way, the natural lens can be focused alternatively on near and far objects.
  • Presbyopia affects nearly all adults over the age of 45 or 50.
  • the IOL is a monofocal lens, requiring that the patient use a pair of spectacles or contact lenses for near vision.
  • Some bifocal IOLs have been created, but are not been widely accepted.
  • Some IOL designs are single optic lenses having flexible haptics that allow the optic to move forward and backward in reaction to movement of the ciliary muscle.
  • the amount of movement of the optic in these single-lens systems may be insufficient to allow for a useful range of accommodation.
  • the eye must be medicated for one to two weeks to decrease eye movement in order for capsular fibrosis to entrap the lens that thereby provide for a rigid association between the lens and the capsular bag.
  • the commercial models of these lenses are made from a hydrogel or silicone material. Such materials are not resistive to the formation of posterior capsule opacification (“PCO”).
  • PCO posterior capsule opacification
  • the treatment for PCO is a capsulotomy using a Nd: YAG laser that vaporizes a portion of the posterior capsule. Such destruction of the posterior capsule may destroy the mechanism of accommodation of these lenses.
  • Known accommodative lenses also lack extended depth of focus in addition to having poor accommodation performance. Such known lenses further require precise lens sizing for proper function over a range of capsular bag sizes and lack long-term capsular fixation and stability. Further, as current lens replacement surgeries move towards smaller incision size, IOLs in general require the ability to be delivered through such small incisions.
  • Dual-optic lenses leverage the ability of the ciliary body-zonule complex to change the shape of the capsular bag. This allows the inter-lens distance to change, thereby allowing a change in refractive error. These dual-optic lenses can be large secondary to the optical hardware needed to create this optical system and requires larger corneal incisions to insert into the eye.
  • Intracorneal lenses are designed to treat refractive error or presbyopia.
  • Intracorneal lenses include corneal implants and lenses, which are inserted through a small incision in the cornea created by a blade or a laser. The pocket formed by the incision in the cornea is used to position the implant to change the shape of the cornea. In the case of a lens implant, the pocket is used to position the refractive lens in the optically effective location. Some lenses create a pinhole-type effect to treat presbyopia. As current intraocorneal lenses move towards smaller incision size, devices in general require the ability to be delivered through such small incisions. Laser technology such as the femtosecond laser has enhanced the ability to create these smaller corneal wounds and pockets for implantation.
  • Phakic intraocular lenses are implanted either in the anterior chamber supported by the angle structures or in the posterior sulcus immediately posterior to the iris and anterior to the native lens.
  • the lens is implanted through a minimally invasive wound at the limbus and inserted into or through the anterior chamber.
  • the lenses are used to treat refractive error and have the risk of causing trauma to the lens and/or angle structures. Smaller incisions require folding the lens and then lens deployment in the eye, which increases the risk of damage to intraocular structures.
  • Shape-memory polymers are a class of smart materials that can be tailored to have significant mechanical property changes in response to a given stimulus. The ability to recover from large deformations and adapt to differing environmental conditions greatly facilitates use of SMP devices in minimally invasive surgery.
  • Current shape memory polymer formulations can be created to have independently programmed modulus and glass transition temperatures (Tg).
  • Tg modulus and glass transition temperatures
  • the ability to precisely control mechanical properties of SMP along with the transparent nature of the material, a refractive index in ranges very similar to the range of a human lens (1.386-1.406 and greater), and proven biocompatibility allows for the creation of unique solutions for treatment of various ophthalmic diseases. Therefore, there are many aspects of a hydrophobic, acrylate-based, SMP intraocular lens which are appealing in view of other lens options.
  • One clear advantage of the SMP systems disclosed herein is the dramatic capability to vary mechanical properties by changing material properties such as cross-linked weight percentage, fractions of each component co-monomer, and other ingredient properties. This provides the capability to design the required mechanical properties for the specific application into the material. For example, varying Tg for particular SMP formulations affects resultant rubbery modulus. Additional property changes can be incorporated, for example, by varying the weight percentage of the co-monomers forming the SMP.
  • the SMP material qualities may also be leveraged to change the radius of curvature of the anterior and posterior surfaces of particular IOL designs with heat, UV light, or other processes to change the central and/or paracentral power of the particular lens.
  • a variety of intraocular lenses may be formed of a shape memory polymer with high degrees of “shape certainty” or “shape-fixity” (i.e., the accuracy of the recovered shape after transition from the deformed shape back to the permanent shape).
  • the lenses are deformed and compressed into a compact preoperative shape that allows for implantation through a small incision, gently unfurl and expand into guaranteed post-operative shapes (permanent shapes), and provide an integrated haptic for a stable and nontraumatic apposition to ciliary sulcus, capsular bag, or anterior chamber angle structures.
  • the SMP lenses may be deformed and compressed to sizes smaller than currently known and available for implantation through an incision size under 2 mm, which is currently the lower limit.
  • a method of manufacturing an intraocular device includes providing a shape memory polymer (SMP) material with a Tg, forming the SMP material in a permanent intraocular device form, mechanically compressing the intraocular device at a temperature above Tg to deform the intraocular device into a smaller volume; and cooling the deformed intraocular device while still in compression to a temperature below Tg to thereby create a stable deformed intraocular device with a delivery profile allowing for insertion through an incision of 2 mm or less.
  • the intraocular device may be rolled at a temperature above Tg of the SMP material.
  • the rolled intraocular device may then be cooled while still in a rolled form to a temperature below Tg to thereby create a stable rolled intraocular device.
  • the intraocular device may then be mechanically compressed to a diameter of less than 1.8 mm.
  • the intraocular device may be rolled at a temperature above Tg of the SMP material.
  • the intraocular device may then be radially compressed within a die to a diameter of less than 1.8 mm while maintaining the temperature above Tg.
  • a shape memory polymer (SMP) intraocular lens may have a refractive index above 1.45, a Tg between 15° C. and 40° C., inclusive, de minimis or an absence of glistening, and substantially 100% transmissivity of light in the visible spectrum.
  • the SMP intraocular lens may be formed of a combination of 50 weight percent tBA, 28 weight percent isobutyl acrylate, and 22 weight percent PEGDMA 1000.
  • the SMP intraocular lens may be formed of a combination of 22 weight percent tBA and 78 weight percent PEGDMA 1000.
  • the SMP intraocular lens may be formed of a combination of 65 weight percent tBA, 13 weight percent butyl acrylate, and 22 weight percent PEGDMA 1000.
  • a method of implanting an intraocular lens device includes making an incision in a cornea or sclera less than 2 mm wide.
  • an intraocular lens is into the capsular bag through the incision.
  • an intraocular lens is inserted into the ciliary sulcus through the incision.
  • a method of implanting an intraocular lens device includes making an incision into a cornea less than 2 mm wide to access the anterior chamber. An intraocular lens is then inserted into the anterior chamber through the incision.
  • a method of implanting an intracorneal implant device includes making an incision into a cornea less than 2 mm wide to create a tunnel in the cornea. An intracorneal implant device is then inserted into the anterior chamber through the incision.
  • FIG. 1 is a graph depicting the storage modulus vs. temperature attributes for several exemplary SMP formulations.
  • FIG. 2 is a graph depicting the UV blocking properties and optical clarity of the exemplary SMP formulations of FIG. 9 as a percentage of transmission over a range of wavelengths in the UV and visible spectrum.
  • FIG. 3 is a graph depicting the storage modulus vs. temperature attributes for several exemplary SMP formulations.
  • FIG. 4 is a graph depicting the UV blocking properties and optical clarity of the exemplary SMP formulations of FIG. 11 as a percentage of transmission over a range of wavelengths in the UV and visible spectrum.
  • FIG. 5 is a graph depicting the compression properties of the exemplary SMP formulations of FIG. 11 .
  • FIG. 6 is a graph depicting the tensile properties of an exemplary SMP formulation at two different rates of strain.
  • FIG. 7 is an optical profilometry image of a sample SMP IOL lens surface showing average surface roughness.
  • FIG. 8A is an isometric view of an exemplary shape memory polymer (SMP) intraocular lens (IOL) with placement haptics in a permanent or deployed configuration.
  • SMP shape memory polymer
  • IOL intraocular lens
  • FIG. 8B is a top plan view of the SMP IOL of FIG. 1A .
  • FIG. 8C is a front elevation view of the SMP IOL of FIG. 1A
  • FIG. 8D is a side elevation view of the SMP IOL of FIG. 1A .
  • FIG. 9A is a top plan view of an exemplary SMP IOL placed on a rolling die with a channel for rolling the SMP IOL.
  • FIG. 9B is a front elevation view of the rolling die of FIG. 2A with the SMP IOL folded into the channel under compression by a wire running axially down the channel.
  • FIG. 10A is a schematic front elevation view of the rolling die of FIG. 2A with the edges of the SMP IOL folded over and the rolling die cooled below Tg.
  • FIG. 10B is a schematic elevation view of the SMP IOL removed from the rolling die and maintaining a deformed, rolled configuration.
  • FIG. 11 is a schematic diagram of the rolled SMP IOL placed in a fabric sock.
  • FIG. 12A is a top plan view, in cross section of the SMP IOL within the fabric sock being pulled through a tube of decreasing diameter formed in a compression die heated above Tg.
  • FIG. 12B is a is a top plan view, in cross section of the SMP IOL within the fabric sock compressed within the smallest diameter section of the tube while the compression die is cooled below Tg.
  • FIG. 13 is a schematic elevation view of the SMP IOL removed from the compression die and sock maintaining a deformed, rolled, extended, and radially compressed configuration.
  • FIG. 14A is a schematic top plan view of a folding and compression tool used to fold a SMP IOL in conjunction with a temperature-regulated compression system.
  • FIG. 14B is a schematic side elevation view in cross section of the tool of FIG. 7A used in conjunction with a temperature-regulated compression tool.
  • FIG. 14C is a schematic side elevation view in cross section of the folding and compression tool in a compressed position with the temperature-regulated compression tool.
  • the SMP IOLs disclosed herein are actually more deformable (in some cases greater than 65% compression and greater than 250% tensile strain) and thus the volume displaced by such devices can actually be reduced for implantation. This allows for implantation through reduced incision sizes (sub 2 mm and even sub 1.8 mm) and thus reduced trauma to the human eye.
  • SMP IOLs Several other benefits are also achievable by using SMP IOLs. It is notable that the refractive index of many of the formulations (n 0 ⁇ 1.464) is relatively high (higher than the refractive index of human lens tissue) and thus allows for the possibility of reducing the thickness of the lens and therefore of the size of the delivery profile.
  • the refractive index of SMP IOLs can further be modified by formulation of the SMP material.
  • the formulations of the SMP materials can also be adjusted to slow or time delay the shape recovery process in order to reduce trauma to tissue in the implant location and to allow the surgeon adequate time for manipulation and placement of the IOL in the proper location.
  • post implant modification is possible, e.g., to change the curvature of the optic or the index of refraction. This may be realized through application of non-intrusive heating of the SMP IOL, or portions thereof, post-implant via laser or ultrasound.
  • Such heating may be applied to particular sections of the SMP IOL which have different cross-link weight percentages of material (and thus different Tg in those areas) to allow activation of a secondary or tertiary shape change, which may be used to effect changes to the refractive index, the curvature of the optic, or the expansion of the haptics.
  • a secondary or tertiary shape change which may be used to effect changes to the refractive index, the curvature of the optic, or the expansion of the haptics.
  • the configuration of the haptic-optic junction may be changed to modify the vault of the optic by heating the junction.
  • Such secondary or tertiary shape changes may also be used to promote interaction with the lens capsule, vitreous, zonules and surrounding tissues to help in accommodation.
  • the baseline positioning of the two optics in a dual optic accommodative intraocular lens system can be changed even after implantation.
  • some SMP IOL formulations may be impregnated with various drugs that may be eluted from the SMP IOL once implanted in vivo to assist with the healing process of the optical tissue traumatized during implantation or to deliver therapeutic medications to treat other ocular diseases.
  • the medication or active ingredient e.g., a biologic agent
  • Exemplary drugs that may be impregnated in the SMP IOL may include antibiotics, anti-inflammatories, anti-histamines, anti-allergy, biologic agents (e.g., anti-VEGF agents, siRNAs, etc), and glaucoma medications (i.e., medications to decrease eye pressure, which include, but are not limited to, prostaglandins, parasympathetic/sympathetic-based medications, alpha agonists, beta blockers, carbonic anhydrase inhibitors, Rho Kinase inhibitors, adenosine agonists, endothelin agonists and antagonists, etc).
  • Other agents that may be linked to an SMP IOL include viral vectors and cell-based therapeutics.
  • SMP materials have significant capacity to change shape or otherwise activate with a mechanical force in response to an external stimulus.
  • the stimulus may be light, heat, chemical, or other types of energy or stimuli.
  • the thermomechanical response of SMP materials may be controlled through formulation to predict and optimize shape-memory properties.
  • Shape memory polymer devices may be designed and optimized to a high degree of tailorability that are capable of adapting and responding to particular biomedical applications and patient physiology.
  • a polymer may be considered a SMP if the original shape of the polymer can be deformed and remain stable in the deformed state until acted upon by an external stimulus, and then the original shape can be recovered by exposing the material to the appropriate stimulus.
  • the stimulus may be heat.
  • the original shape may be set by molding, extruding, stamping, or other typical polymer processing process.
  • a disc, rod, or other configuration of the material may be formed by the above processes and then shaped into a final shape with cryolathing, which is a process involving freezing of the material followed by laser and/or mechanical cutting of the material into a final shape.
  • the temporary shape may be set by thermo-mechanical deformation.
  • Heating the deformed SMP material above a shape deformation recovery temperature results in recovery of the original shape, even if the original molded shape of the polymer is altered mechanically at a lower temperature than the deformation recovery temperature.
  • SMP materials disclosed for use in the applications herein have the ability to recover large deformation upon heating and in appropriate formulations with greater than 99% accuracy of the original shape.
  • a polymer transition temperature may be tailored to provide for a deformation recovery temperature, at body temperature, about 37° C.; i.e., the glass transition temperature, Tg, of the polymer is designed to be about 37° C.
  • Tg glass transition temperature
  • the distinct advantage of this approach is the utilization of the thermal energy of the human body to naturally activate the SMP material.
  • the mechanical properties (e.g., stiffness) of the material are strongly dependent on Tg.
  • the recovery temperature is higher than the body temperature, i.e., Tg>37° C.
  • Tg the body temperature
  • the storage temperature can be equal to room temperature facilitating easy storage of the device and avoiding unwanted deployments before use.
  • the folded shape may be retained through the use of a constraining device which does not allow the device to deploy into its initially molded shape.
  • local heating of the material upon deployment may be needed to induce recovery of the SMP material.
  • Local damage to some tissues in the human body may occur at temperatures approximately 5 degrees above the body temperature through a variety of mechanisms including apoptosis and protein denaturing. Local heating bursts may be used to minimize exposure to elevated temperatures and circumvent tissue damage.
  • the use of one method over the other is a design decision that depends on the targeted body system and other device design constraints such as required in-vivo mechanical properties.
  • a SMP material or network may include dissolving materials which may include part of the network or may be included in the formulation of the network before the network is polymerized (e.g., as an aggregate, mixed into the formulation). Dissolving materials may include materials that disperse over time, even if the material or part of the material does not actually dissolve or enter into a solution with a solvent.
  • a dissolving material as used herein may be any material that may be broken down by an anticipated external environment of the polymer.
  • a dissolving material is a drug which elutes out of a SMP network.
  • a dissolving material may be attached by chemical or physical bonds to the polymer network and may become disassociated with the polymer network over time.
  • Dissolving materials through their dissolution over time, may be used for many purposes.
  • the dissolution of a material may affect a dissolution or break-up of a biomedical device over time.
  • the dissolution of a material may elute a drug, achieving a pharmacological purpose.
  • Medications or drugs can be infused into SMP devices to aid in healing (e.g., anti-inflammatory), avoid complications (e.g., anti-thrombotic), or to combat potential infection (e.g., antibiotic).
  • Medications may be added by injection into the liquid polymer before curing. Medications may also be added to SMP devices post-polymerization using various surface modification or coating techniques, for example, plasma deposition.
  • the SMP polymer segments can be natural or synthetic, although synthetic polymers are preferred.
  • the polymer segments may be non-biodegradable.
  • Non-biodegradable polymers used for medical applications preferably do not include aromatic groups, other than those present in naturally occurring amino acids.
  • the SMP utilized in the IOLs disclosed herein may be nonbiodegradable.
  • the polymers are selected based on the desired glass transition temperature(s) (if at least one segment is amorphous) or the melting point(s) (if at least one segment is crystalline), which in turn is based on the desired application, taking into consideration the environment of use.
  • Representative natural polymer blocks or polymers include proteins such as zein, modified zein, casein, gelatin, gluten, serum albumin, and collagen, and polysaccharides such as alginate, celluloses, dextrans, pullulane, and polyhyaluronic acid, as well as chitin, poly(3-hydroxyalkanoate), especially poly( ⁇ -hydroxybutyrate), poly(3-hydroxyoctanoate), and poly(3-hydroxyfatty acids).
  • Representative natural biodegradable polymer blocks or polymers include polysaccharides such as alginate, dextran, cellulose, collagen, and chemical derivatives thereof (substitutions, additions of chemical groups, for example, alkyl, alkylene, hydroxylations, oxidations, and other modifications routinely made by those skilled in the art), and proteins such as albumin, zein, and copolymers and blends thereof, alone or in combination with synthetic polymers.
  • Representative synthetic polymer blocks or polymers include polyphosphazenes, poly(vinyl alcohols), polyamides, polyester amides, poly(amino acid)s, synthetic poly(amino acids), polyanhydrides, polycarbonates, polyacrylates, polyalkylenes, polyacrylamides, polyalkylene glycols, polyalkylene oxides, polyalkylene terephthalates, polyortho esters, polyvinyl ethers, polyvinyl esters, polyvinyl halides, polyvinyl pyrrolidone, polyesters, polylactides, polyglycolides, polysiloxanes, polyurethanes and copolymers thereof.
  • polyacrylates examples include poly(methyl methacrylate), poly(ethyl methacrylate), poly(butyl methacrylate), poly(isobutyl methacrylate), poly(ethylene glycol dimethacrylate) (PEGDMA), diethylene glycol dimethacrylate (DEGDMA), poly(ethylene glycol) diacrylate (PEGDA), poly(hexyl methacrylate), poly(isodecyl methacrylate), poly(lauryl methacrylate), poly(phenyl methacrylate), poly(ethyl acrylate), poly(methyl acrylate), poly(isopropyl acrylate), butyl acrylate, poly(butyl acrylate), poly (tert-butyl acrylate), poly(isobutyl acrylate), poly(isobornyl acrylate) and poly(octadecyl acrylate).
  • PEGDMA poly(ethylene glycol dimethacrylate)
  • DEGDMA diethylene glycol dime
  • Synthetically modified natural polymers include cellulose derivatives such as alkyl celluloses, hydroxyalkyl celluloses, cellulose ethers, cellulose esters, nitrocelluloses, and chitosan.
  • suitable cellulose derivatives include methyl cellulose, ethyl cellulose, hydroxypropyl cellulose, hydroxypropyl methyl cellulose, hydroxybutyl methyl cellulose, cellulose acetate, cellulose propionate, cellulose acetate butyrate, cellulose acetate phthalate, carboxymethyl cellulose, cellulose triacetate, and cellulose sulfate sodium salt. These are collectively referred to herein as “celluloses.”
  • Representative synthetic degradable polymer segments include polyhydroxy acids, such as polylactides, polyglycolides and copolymers thereof poly(ethylene terephthalate); polyanhydrides, poly(hydroxybutyric acid); poly(hydroxyvaleric acid); poly[lactide-co-( ⁇ -caprolactone)]; poly[glycolide-co-( ⁇ -caprolactone)]; polycarbonates, poly(pseudo amino acids); poly(amino acids); poly(hydroxyalkanoate)s; polyanhydrides; polyortho esters; and blends and copolymers thereof.
  • Polymers containing labile bonds, such as polyanhydrides and polyesters are well known for their hydrolytic reactivity. The hydrolytic degradation rates of these polymer segments can generally be altered by simple changes in the polymer backbone and their sequence structure.
  • non-biodegradable synthetic polymer segments include ethylene vinyl acetate, poly(meth)acrylic acid, polyamides, polyethylene, polypropylene, polystyrene, polyvinyl chloride, polyvinylphenol, and copolymers and mixtures thereof.
  • the polymers can be obtained from commercial sources such as Sigma Chemical Co., St. Louis, Mo.; Polysciences, Warrenton, Pa.; Aldrich Chemical Co., Milwaukee, Wis.; Fluka, Ronkonkoma, N.Y.; and BioRad, Richmond, Calif. Alternately, the polymers can be synthesized from monomers obtained from commercial sources, using standard techniques.
  • thiol-vinyl and thiol-yne polymer compounds as disclosed in international application no. PCT/US2009/041359 entitled “Thiol-vinyl and thiol-yne systems for shape memory polymers” filed 22 Apr. 2009, which is hereby incorporated by reference herein in its entirety, may be used to form IOLs.
  • polymer formulations may undergo a two-stage curing process in which a second, photo-induced polymerization of still unreacted functional groups is undertaken after an initial cure stage.
  • Such a dual cure system for manufacturing SMP materials is described in U.S. provisional patent application No. 61/410,192 entitled “Dual-cure polymer systems” filed 10 Nov. 2010, which is hereby incorporated by reference herein in its entirety.
  • SMP formulations Tailoring of specific SMP formulations allows IOLs to be created to meet specific design requirements and to be manufactured using scalable liquid injection manufacturing techniques. SMP formulations were developed to optimize the following properties:
  • recovery time is controlled by the relationship of the glass transition temperature (Tg) of the SMP material used to the environmental temperature (Te) in which an SMP device is deployed.
  • Tg glass transition temperature
  • Tg of the material may be controlled from ⁇ 35° C. up to 114° C. allowing a wide range of control over the deployment rate into the body. Desirable ranges for Tg in IOL devices may be between 10° C. and 60° C., and even more desirably between 15° C. and 45° C. Devices have been created that deploy in less than a second all the way up to several minutes to fully deploy.
  • the mechanical properties of the SMP devices may be developed to achieve high levels of recoverable strain.
  • tension up to 180% strain can be achieved for 10% cross-linked systems and up to 60% strain can be achieved in 40% cross-linked systems.
  • compression 80% or more strain can be achieved with the above percentage cross-link.
  • the desired levels of strain in tension and compression are determined by the level of deformation required to fit the SMP IOL into the delivery system. Formulations with lower amounts of cross-linking can undergo higher levels of deformation without failure. Current IOLs utilize 5%-40% cross-linking to achieve the material properties for the desired level of recoverable strain.
  • Manufacturing of SMP IOLs may be achieved through either thermal initiation or photo-initiation or a combination of the two processes.
  • thermal initiation both peroxides and azo initiators have been utilized.
  • 2,2-dimethoxy-2-phenylacetophenone (DMPA) may be used for photo-initiation.
  • Formulations vary in quantity from 0.01% by weight to 1% by weight of initiator. These are varied to optimize cycle time during the manufacturing process and still maintain desired thermomechanical properties.
  • Colorant can also be added to the formulations.
  • SMP materials with SPECTRAFLO (trademark of Ferro) liquid colors have been created.
  • Formulations with 0.1% to 2% by weight have been created, which allows various colors to be added yet maintain desired thermomechanical properties.
  • Table B provides data on the refractive index of the different components used in several exemplary formulations.
  • FIG. 1 is a graph showing the storage modulus and the tan delta (the ratio of the storage modulus to the loss modulus) of the following three material formulations over a range of temperatures from 0 to 100° C.:
  • SMP122 SMP106 with 0.5 weight % BTA functionalized UV blocker added
  • SMP123 SMP106 with 1.0 weight % BTA functionalized UV blocker added.
  • the upper curve is the storage modulus and the lower curve is the tan delta.
  • the addition of the small amounts of BTA as a UV blocker has little if any effect on the modulus of the SMP materials and the Tg (the peak of the tan delta curve) is constant for all three formulations.
  • FIG. 2 shows the effect of the addition of the BTA UV blocker on the SMP materials of FIG. 1 .
  • the addition of the UV blocker has negligible effect on light transmission in the visible wavelengths, but sharply attenuates wavelengths below about 380 nm, which is the upper end of the UV spectrum.
  • FIG. 3 is a graph showing the storage modulus and the tan delta of two additional SMP formulations over a range of temperatures from ⁇ 20 to 100° C. in comparison to SMP 106:
  • SMP126 50 wt % tBA, 28 wt % isobutyl acrylate, 22 wt % PEGDMA 1000.
  • the upper curve is the storage modulus and the lower curve is the tan delta.
  • the difference in formulas provide different Tg for use in different environments and for different applications in which it may be useful to have a lower transition temperature.
  • SMP119 has a Tg of about 25° C.
  • SMP126 has a Tg of about 17° C.
  • the storage moduli of the SMP119 and SMP126 formulations compare favorably to the SMP106 material.
  • FIG. 4 also indicates that the light transmission properties of SMP119 and SMP126 compare favorably to the SMP106 formula.
  • FIG. 5 is a graph depicting stress-strain data curves for SMP106, SMP119, and SMP126 for the materials under compression.
  • the SMP119 and SMP126 formulas exhibit significantly less stress under a compressive strain of 65% compared to the SMP106 formula. This allows these materials to be more easily deformed at lower temperatures, such as room temperature.
  • FIG. 6 is another stress-strain curve for SMP106 for two separate rates of elongation under tension, i.e., for rates of 10 mm/min and 20 mm/min. As shown in the graph, SMP106 performs quite well under tension and withstood up to and over 250% strain at both rates.
  • the post deployment shape should be highly controlled to maximize the optical characteristics of the device.
  • the higher the shape fixity defined as the percent change in recovered shape compared to the original molded shape, the higher the reproducibility and confidence that the deployed IOL will function as intended.
  • the SMP materials disclosed herein provide extremely high shape fixity (>95-99%). This is in large part because the SMP materials deploy using a non-elastic, non-melt shape recovery process (i.e., it is not a phase change using fluid properties). Further, the SMP materials are not a hydrogel or other type of hydrating material.
  • the SMP materials transform from one highly-reproducible, non-changing, non-creeping, non-deforming, storage shape, to another highly-reproducible, non-changing, non-creeping, non-deforming, secondary (permanent) shape.
  • the SMP materials have a pre-programmed shape; post-deployment the SMP devices release internal stored energy to move to the programmed shape, which may or may not be adaptive to the local tissue.
  • the local tissue does not play a part in shaping the form of the SMP devices.
  • the SMP devices return to their “permanent” shape as originally formed when molded, before being deformed for smaller profile delivery.
  • the speed of full deployment from the deformed state to the glass (permanent) state can be varied over a wide range from less than a second to over 600 seconds depending upon the SMP formulation.
  • the processes of packaging, shipping, storing, and ultimately implanting SMP devices does not require refrigerated storage or ice or an otherwise low-temperature operating environment.
  • a significant advantage of the SMP materials described herein is that they can be stored in the stored shape for extended periods of time, they can be packaged in constrained forms within a customized delivery system, and they can be deployed without need for prior refrigeration or other temperature changes. For example, during shipping of a device, the environmental effect of cycling of temperatures and inadvertent deployment of a device can be eliminating by constraining the device in a delivery system or packaging system.
  • intraocular lens types can be made of SMP materials according to the formulations described above with selected material properties to meet the needs of the particular lens type or design. Several of these lens options are described below
  • SMP intraocluar lenses are designed to be inserted through significantly smaller incisions than other currently commercially available foldable lens technologies.
  • An exemplary SMP intraocular lens 100 is depicted in FIGS. 1 and 2 and will be discussed in greater detail herein below.
  • An intracapsular bag lens may have a shape that creates contact with the anterior capsular leaflet as well as the capsule just posterior to the equator allowing for a decrease in posterior capsule opacity formation.
  • a ciliary sulcus lens may have a vault which allows it to avoid trauma to the iris.
  • An anterior chamber lens may have an appropriate vault to decrease the risk of pupillary block and decrease the risk of trauma to the anterior chamber angle support structures.
  • the intraocular lens is compressible and deformable. This ability to compress the material and configure it in a small platform allows for smaller incision sizes for delivery.
  • Such SMP lenses which fit through smaller incisions, offer significant benefit. For example, with cataract surgery there is less astigmatism, quicker recovery, and less trauma to the eye with smaller incisions. Also, with laser technology and improved ultrasound technology, cataract surgery can be performed with smaller incisions; the limiting factor with present options is the larger incision size needed for the replacement lens.
  • a second advantage to the shape memory polymer technology in intraocular lens is that deployment of the lens uses thermomechanical recovery rather than an elastic recovery process.
  • the formulation can be modified to change the time or speed of deployment of the lens. This can vary depending upon the location of needed deployment. For example, deployment near delicate structures, such as in the capsular bag or near the corneal endothelium, may require slower, surgeon-tailored deployment to avoid damage to these structures. This modification of deployment speed is not possible with other currently available lens technologies.
  • the modulus of the SMP material can be modified to optimize the softness of lens material to minimize trauma to eye structures. For each of the lens types described above, the SMP material properties allow for a slow, tailored deployment, which results in less trauma to the areas with which the lens optic or haptics come in contact.
  • a third advantage is the ability to easily modify the refractive index of the lens.
  • the refractive index can he changed through modifications of SMP formulation.
  • the surface curvature of the lens which is important in designing optical power, can be modified through the liquid injection molding process or post molding with cutting such as with a laser.
  • the curvature of lens as well as the refractive index of the lens can be modified post implantation with heat, UV, or laser light modification.
  • FIG. 7 is an optical profilometry image of a sample SMP lens surface showing average surface roughness of 16 nanometers. This low roughness measure minimizes optical artifacts such as spectral filtering and maximizes optical clarity of the lens.
  • the darker areas surrounded by the circles are areas toward the higher end of the measured roughness on the right-hand scale (i.e., toward the 203 nm measurement) while the other dark areas in the image are toward the lower end of measured roughness (i.e., toward the ⁇ 186 nm measurement).
  • an intracapsular SMP IOL will have contact with the capsular bag to decrease the movement of the lens, but the smoothness of the surface retards the migration of epithelial cells and subsequent formation of posterior capsular opacification.
  • the lenses may be also modified with surface polishing as well as other known mechanisms to reduce the proliferation of cells on the surface of intraocular lenses.
  • the slow deployment of an SMP lens can minimize cellular opacification.
  • an intracapsular lens will have contact with the capsular bag in a fashion to decrease the migrations of the lens, but the contact with epithelial cells can lead to subsequent formation of posterior capsular opacification, especially if the fit is tight and the material is unable to pass around the lens.
  • Dual optic lenses are generally constructed with a primary intraocular lens having an optic with a primary optical power and refractive index, and a secondary intraocular lens having an optic with a secondary optical power and possibly a different refractive index.
  • the secondary optic is typically attached to and spaced apart from the primary optic by material struts or similar structures about the periphery of the lenses.
  • the two lenses to act synergistically to allow for both near and distance vision depending on the relationship (e.g., separation distance) between the two optics as well as the geometric association between the two optics which also may (or may not) be adjustable in each individual patient post implantation.
  • These dual optic lenses often require larger than conventional incisions for entry into the eye.
  • These larger platform lenses may be made with SMP materials, which are highly compressible and deformable allowing for smaller incisions sizes, and thus can improve surgical outcomes for the reasons stated above.
  • SMP materials which are highly compressible and deformable allowing for smaller incisions sizes, and thus can improve surgical outcomes for the reasons stated above.
  • these larger lenses can be deployed more slowly allowing the surgeon to position the lens in such a fashion as to avoid inadvertent trauma to important eye structures and careful apposition to structures in the target location. This decreases the trauma risk that these larger platform lenses could cause in the eye.
  • these lenses are quite complex and require high precision optics capabilities, which are conserved because of the high shape fixity of the SMP materials.
  • accommodative lenses strive to replicate the functions of the normal human lens. Mechanisms of accommodation are thought to be secondary to ciliary body contraction and zonular deformation of the lens capsule and a change in lens shape as well as an anterior-posterior movement of the lens complex.
  • SMP materials a lens may be created which has close apposition to the lens capsule in multiple areas so that there is an ability to replicate the actions of the native lens.
  • an SMP lens may be made which expands in the intracapsular space, fills either the whole space or a larger area of the space, and responds to the ciliary body-zonule actions.
  • an SMP lens can be inserted through a smaller anterior capsular opening, which may help preserve the responsiveness of the lens to the native accommodative process.
  • the local dimensions, thickness in particular, of the SMP lens may be modified post implantation (which may affect local stiffness) if a change in shape is needed to replicate the accommodation process by adding SMP material into the IOL that is of different cross-link density and therefore different activation temperature (Tg) and/or different modulus.
  • a phakic intraocular lens is a lens which is placed in the anterior chamber through a corneal incision.
  • an SMP phakic lens may be compressed for implantation through a much smaller incision than presently available lenses.
  • a SMP phakic lens may also be designed to deploy slowly so there is little to no corneal endothelial or native lens trauma. The tailored surgeon-controlled deployment allows for positioning of the haptics against the anterior chamber structures without damaging the trabecular meshwork or iris. The force placed on the angle structures by the haptics is consistent and more reproducible than with a conventional lens, which deploys by elastic recovery.
  • a SMP phakic lens may also be designed to deploy in the anterior chamber for placement behind the iris plane during deployment. With current phakic IOL technology, if placed behind the iris, there is a known higher incidence of cataract formation. This incidence can be reduced or eliminated with slow tailored deployment and positioning of an SMP lens.
  • Intracorneal implant devices have not achieved great success in the national and international markets due to several limitations which include: (a) difficulty with implantation; (b) requirement for large incisions in the cornea to accommodate current devices; (c) inability to correct “refractive surprises” without returning to the procedure or operating room; and (d) limitation in geometrical configurations of current devices due to inherent material properties.
  • SMP intracorneal implants may be designed to leverage the benefits of the compressibility and deformability of SMP materials.
  • a laser or blade is used to make an intracorneal incision, tunnel, and pocket to deliver the intracorneal implant.
  • One of the current challenges is the severe trauma often seen to the corneal tissues during insertion of these devices.
  • a “tight fit” is needed as well as an adequate intracorneal passageway to advance the intracorneal implant.
  • the intracorneal implants are designed to be small enough to atraumatically be passed through a corneal incision and into the desired pocket. Then, the thermomechanical deployment and decompression of the implant occurs allowing for a secure positioning of the implant.
  • Extrusion and displacement of the intracorneal implants may be decreased with the SMP technology as well as decreasing infection rates because of the minimization of corneal trauma as well as the presence of a smaller incision, tunnel, and pocket.
  • Advantages of using SMP materials for intracorneal implants compared to traditional devices may include the ability to implant devices through minimally invasive approaches (e.g., through incisions created by femtosecond lasers) with subsequent shape change achieving larger device diameters for refractive correction.
  • Another advantage is the ability to change the shape and size of SMP intracorneal implant devices post implantation in the cornea, for example, if a “refractive surprise” occurs or if further changes in refractive correction are needed.
  • intracorneal implants with different material formulas in different areas to provide differing Tg and refractive index values for each of the areas as described above with respect to SMP IOLs.
  • a further advantage is the ability to implant the devices in a more “rubbery” state, thus causing less trauma to the stromal tissue of the cornea.
  • FIGS. 8A-13 depict exemplary steps in a process to deform a SMP IOL into a compressed shape for packaging and implantation, at which point the SMP IOL will deploy and expand to return to its permanent shape with an extremely high degree of shape fixity.
  • the SMP IOL 100 has a center optic 102 and haptics 104 extending symmetrically from opposing sides of the optic 102 .
  • Each of the haptics 104 may be formed in sections including a shoulder 106 connected with the optic 102 , an arm 108 , and a terminal end 110 .
  • the haptics 104 unfurl from their rolled and compressed conditions to press the terminal ends 110 against the tissue forming the cavity of implantation to secure the optic in an appropriate position.
  • the SMP IOL is formed by injection molding one of the formulations described above.
  • an 80-20 (tBA-PEGDMA 550) combination is used to create a 6 mm diameter optic 102 with extending haptics 104 .
  • the tBA-PEGDMA 550 mixture has extremely low viscosity when heated in the mold and is thus able to easily flow through and fill the mold to form the very small diameter haptics 104 .
  • a combination of tBA (78%) and PEGDMA 1000 (22%), with or without a UV blocker BTA (0.5-1.0%) e.g., SMP106, SMP122, and SMP123, respectively
  • These formulas similarly have extremely low viscosities.
  • the mold may be oversized by 0.1-20% to account for a 5-20% volume shrinkage that typically occurs for these polymer chemistries during the polymerization process.
  • ultra-high pressures e.g., >500-40,000 psi
  • the combination of injection molding with pre-polymization techniques may be implemented to further minimize volume shrinkage during the polymerization process.
  • the cure temperature and de-molding temperature may be the same to avoid thermal cycling.
  • the mold may be cooled to an optimal de-mold temperature where the material exhibits the greatest robustness, typically somewhere slightly (e.g., 8° C.) below Tg.
  • the SMP IOL 100 is in its permanent form.
  • FIGS. 9A and 9B schematically depict a first step in the deformation process for the SMP IOL 202 to package the SMP IOL 202 into a deformed shape for storage and ultimately implantation.
  • a rolling die 204 defining a longitudinal channel 206 therein may be used to initially roll the SMP IOL 202 .
  • the SMP IOL 202 is placed over the channel oriented with the haptics extending across the channel as well.
  • a tension wire 208 is placed parallel to and directly above the channel 206 over the SMP IOL 202 while the ends of the tension wire 208 are position coaxially with the longitudinal center of the channel 206 .
  • the rolling die 204 and SMP IOL 202 are then heated to approximately Tg.
  • the tension on the wire 208 is increased, drawing the entire length of the tension wire 208 into the channel 206 the tension wire is coaxial with the longitudinal center of the channel.
  • the tension wire 208 thereby pushes the SMP IOL 202 within the channel 206 , folding the SMP IOL 202 in half around the tension wire 208 and deforming the SMP IOL 202 into a U-shape 202 ′ as shown in FIG. 9B .
  • a first side of the U-shaped SMP IOL 202 ′ (labeled “b” in FIG. 2B ) is folded over the wire 208 in the channel 206 .
  • a second side of the U-shaped SMP IOL 202 ′ (labeled “c” in FIG.
  • the channel may be 1.8 mm wide by 2.0 mm deep resulting in an SMP IOL 202 ′ that has maximum diametrical dimensions of 1.8 mm by 2.0 mm.
  • the rolled SMP IOL 302 is next cooled below Tg while remaining within the channel 306 in the rolling die 304 .
  • the cooling of the SMP IOL 302 while in the die channel locks the SMP IOL 302 in the rolled configuration.
  • the SMP IOL 302 can then be removed from the channel 306 in the rolling die 304 and will maintain its rolled shape as shown in FIG. 10B .
  • the rolled SMP IOL 402 is next placed within a fabric sheath or sock 404 as shown in FIG. 11 for transmission of the rolled SMP IOL 402 through a compression die.
  • the fabric sock 404 may be closed at one end and open at an opposite end and sized to fit snugly around the rolled SMP IOL 402 .
  • the fabric sock 404 may be significantly longer than the length of the rolled SMP IOL 402 in order to assist in pulling the SMP IOL 402 through a compression die.
  • the fabric sock 404 may be made of a silk fabric.
  • FIGS. 12A and 12B depict the SMP IOL 402 in the fabric sock 404 being pulled through a compression die 502 .
  • the compression die 502 defines a borehole 508 extending laterally therethrough from an entrance side 504 to and exit side 506 .
  • the borehole 508 in the compression die 502 may be divided into several sections of varying diameter.
  • An entrance section 510 opening up to the entrance side 504 may be of a constant diameter of slightly larger than the diameter of the rolled SMP IOL 402 such that the SMP IOL 402 can be easily inserted into the borehole 508 of the compression die 502 .
  • a middle section 512 of the borehole 508 tapers in diameter from the diameter of the entrance section 510 to a smaller diameter that transitions into and is congruent with a diameter of an exit section 514 that opens the exit side 506 .
  • the diameter w of the entrance section 510 may be formed as 2.0 mm or slightly greater.
  • the middle section 512 may then transition from 2.0 mm to 1.5 mm in diameter, and the diameter w′ of the exit section may be a constant 1.5 mm in diameter.
  • the open end of the fabric sock 404 is placed within the borehole 508 from the entrance side 504 and is long enough to extend the length of the borehole 508 and extend out of the exit side 506 .
  • the open end of the fabric sock 404 may then be grasped to pull the rolled SMP IOL 402 within the fabric sock 404 into the entrance section 510 of the borehole 508 .
  • the compression die 502 is heated to a temperature greater than Tg for the SMP formulation used until the SMP IOL 402 reaches a temperature greater than Tg and is softened.
  • the fabric sock 404 is then pulled through the borehole 508 whereby the rolled SMP IOL 402 is likewise pulled through the middle section 512 and radially compressed.
  • the compressed SMP IOL 402 ′ is then left in the reduced diameter exit section 514 while the compression die and the compressed SMP IOL 402 therein are cooled to a temperature below Tg, thereby locking the compressed SMP IOL 402 ′ in the compressed state.
  • Tg a temperature below Tg
  • an SMP IOL with a 6 mm diameter optic was rolled and compressed to a final diameter, w′, of 1.5 mm.
  • the compressed SMP IOL was loaded into a 15 gauge hypodermic tube.
  • the compressed SMP IOL in the tube was then introduced into a heated water bath at body temperature.
  • a rod was inserted within the hypodermic tube to push the IOL out the end of the tube and deliver it into the water bath.
  • the SMP IOL expanded and unfurled to return to its original form with a 6 mm diameter optic with >98% accuracy in size and form.
  • FIG. 14A depicts a first step in the deformation process for an SMP IOL 702 to package the SMP IOL 702 into a deformed shape for storage and ultimately implantation.
  • a rolling die 710 is formed with a pair of parallel walls 704 extending above a top surface of the die 710 to define a longitudinal channel 706 therein.
  • the base of the channel 706 may be arcuate or semicircular in cross section in order to aid in the folding and achieve a relatively cylindrical SMP IOL 702 in the final compressed form.
  • the SMP IOL 702 is placed on the walls 704 over the channel 706 and oriented with the haptics extending across the channel 706 as well.
  • the rolling die 710 and SMP IOL 702 are then heated to approximately Tg.
  • the lateral edges of the SMP IOL 702 may then be folded over within the channel 706 between the walls 704 to form a rolled shape similar to the configuration of the IOL 302 in FIG. 10B .
  • the IOL 702 may be folded by hand using a tweezers or forceps.
  • a tension wire as described with respect to FIGS. 9A and 9B may be used to depress the IOL 702 into the channel 706 .
  • the channel 706 may be 1.8 mm wide by 2.0 mm deep resulting in an SMP IOL 702 that has maximum diametrical dimensions of 1.8 mm by 2.0 mm.
  • FIG. 14B depicts a second component of the deformation device, a second compression die 720 that works in cooperation with the roll die 710 to further compress the IOL 702 .
  • a pair of parallel channels 728 are formed within a top surface of the compression die 720 that are complementary to or slightly larger in size (i.e., length, width, and depth) than the size of the walls 704 (i.e., length, width, and height) of the rolling die 710 .
  • a recessed wall 724 is thus formed within the top surface of the compression die 720 that separates and defines the channels 728 .
  • the recessed wall 724 may thus be of a complementary width to or slightly smaller in width than the channel 706 on the rolling die 710 .
  • the top surface of the recessed wall 724 may further define a shallow trough 726 with a curved or semi-circular cross section.
  • the compression die 720 may further be formed with one or more fluid channels 722 with inlet and outlet fittings in order to maintain the compression die 720 at or above the Tg of the SMP IOL 702 .
  • the rolling die 710 is inverted and placed on top of the compression die 720 .
  • the walls 704 of the rolling die 710 fit within the channels 728 of the compression die 720 .
  • the recessed wall 724 of the compression die 720 extends into the channel 706 of the rolling die 710 and the trough 726 contacts the SMP IOL 702 within the channel 706 .
  • the rolling die 710 and the compression die 720 are then pressed together and the SMP IOL 702 is further compressed in size when measured in cross-sectional diameter (however, the SMP IOL may increase in axial length slightly when under radial compression between the rolling die 710 and the compression die 720 .
  • the top surface of the rolling die 710 and the top surface of the compression die 720 reach an interface and halt the compression of the SMP IOL 702 .
  • the depth of the trough 726 and the depth of the channel 706 are chosen to define a separation distance between the base of the channel 706 and the base of the trough 726 that corresponds to a desired final diameter of the compressed SMP IOL 702 .
  • an SMP IOL with a 6 mm diameter optic was compressed using this method to a final diameter of 1.6 mm. The compressed SMP IOL can then be loaded into an injection tool for ab interno delivery.
  • an SMP IOL folded by this technique may be loaded into a lens injector for implantation.
  • a small incision may be made at the corneal limbus with a blade or laser and the tip of the injector may be inserted into the anterior chamber. Because of the slow deployment of the SMP IOL, the surgeon can place the haptics and the optic in the correct location during lens deployment to avoid extensive manipulation of the SMP IOL after full deployment.
  • cataract extraction and lens implantation can be performed with a smaller anterior capsular opening—as small as less than 1.8 mm in diameter. A smaller capsular opening with less disruption of the anterior capsule will increase the accommodative ability of the implanted lens as the physiology of accommodation is less disrupted.
  • the injector tip may be placed through the cornea incision, across the anterior chamber, into the small anterior capsular opening.
  • the lens may be injected directly into the capsular bag and slowly deploy without significant trauma to the lens capsule. This is not possible with rapid deployment of known expanding lenses which often leads to capsular tears.
  • a sulcus SMP IOL will be supported in the ciliary sulcus with gentle pressure and apposition of the haptics to the ciliary sulcus structures.
  • an anterior chamber SMP IOL will be supported by the anterior chamber angle structures with gentle pressure and apposition of the haptics to the anterior chamber angle structures. The slow, gradual deployment of an SMP IOL will significantly reduce the trauma to these tissue structures as compared to the rapid, elastic deployment of present IOL materials.

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US13/500,884 US20140232025A1 (en) 2011-03-07 2012-03-07 Manufacturing method for shape memory polymer intraocular devices
US15/157,214 US10286105B2 (en) 2011-03-07 2016-05-17 Shape memory polymer intraocular lenses
US15/157,141 US10272176B2 (en) 2011-03-07 2016-05-17 Shape memory polymer intraocular lenses
US15/157,260 US10286106B2 (en) 2011-03-07 2016-05-17 Intraocular lenses
US15/157,290 US10286107B2 (en) 2011-03-07 2016-05-17 Shape memory polymer intraocular lenses
US16/012,663 US20180296726A1 (en) 2011-03-07 2018-06-19 Shape memory polymer intraocular lenses

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US13/500,884 US20140232025A1 (en) 2011-03-07 2012-03-07 Manufacturing method for shape memory polymer intraocular devices
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US9427493B2 (en) 2011-03-07 2016-08-30 The Regents Of The University Of Colorado Shape memory polymer intraocular lenses
US9364318B2 (en) 2012-05-10 2016-06-14 Z Lens, Llc Accommodative-disaccommodative intraocular lens
WO2015038940A1 (fr) * 2013-09-13 2015-03-19 Abbott Medical Optics Inc. Lentilles intraoculaires en polymère à mémoire de forme
WO2015073150A1 (fr) * 2013-11-12 2015-05-21 Serdarevic Olivia Vitrification cornéenne, procédés et dispositifs pour produire une vitrification cornéenne et leurs procédés d'utilisation
WO2015170278A1 (fr) 2014-05-07 2015-11-12 Tubitak Formulation et procédé de fabrication de lentilles, pour la production de lentilles intraoculaires (iol)
JP2018519003A (ja) * 2015-05-01 2018-07-19 メディセム オフサルミック （シーワイ） リミテッド 眼の球面収差のカスタマイズによる視覚の最適化のための方法およびデバイス
US10500370B2 (en) * 2015-09-02 2019-12-10 Syracuse University Antifouling urinary catheters with shape-memory topographic patterns
CN105997301A (zh) * 2016-04-25 2016-10-12 哈尔滨工业大学 基于形状记忆聚合物的人工假体的智能可变形方法
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CN103797117B (zh) 2016-09-07
JP2016172080A (ja) 2016-09-29
CA2829390A1 (fr) 2012-09-13
AU2012225499A1 (en) 2013-09-26
AU2012225499B2 (en) 2016-12-15
US20120232651A1 (en) 2012-09-13
EP2683819A2 (fr) 2014-01-15
EP2683819B1 (fr) 2019-12-11
JP6212601B2 (ja) 2017-10-11
CN105726166A (zh) 2016-07-06
CN105726166B (zh) 2017-10-27
EP2683819A4 (fr) 2015-06-24
US20120232648A1 (en) 2012-09-13

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