Patent Grant
10874606
The present application is related to implants for use in or near the nasolacrimal drainage system, with embodiments providing canalicular implants, lacrimal sac implants, punctal plugs and punctal plugs with drug delivery capabilities.
A variety of challenges face patients and physicians in the area of ocular drug delivery. In particular, the repetitive nature of the therapies (multiple injections, instilling multiple eye drop regimens per day), the associated costs, and the lack of patient compliance may significantly impact the efficacy of the therapies available, leading to reduction in vision and many times blindness.
Patient compliance in taking the medications, for example instilling the eye drops, can be erratic, and in some cases, patients may not follow the directed treatment regime. Lack of compliance can include, failure to instill the drops, ineffective technique (instilling less than required), excessive use of the drops (leading to systemic side effects), and use of non-prescribed drops or failure to follow the treatment regime requiring multiple types of drops. Many of the medications may require the patient to instill them up to 4 times a day.
In addition to compliance, the cost of at least some eye drop medications is increasing, leading some patients on limited incomes to be faced with the choice of buying basic necessities or instead getting their prescriptions filled. Many times insurance does not cover the total cost of the prescribed eye drop medication, or in some cases eye drops containing multiple different medications.
Further, in many cases, topically applied medications have a peak ocular effect within about two hours, after which additional applications of the medications should be performed to maintain the therapeutic benefit. In addition, inconsistency in self-administered or ingested medication regimes can result in a suboptimal therapy. PCT Publication WO 06/014434 (Lazar), which is incorporated herein by reference in its entirety, may be relevant to these and/or other issues associated with eye drops.
One promising approach to ocular drug delivery is to place an implant that releases a drug in tissue near the eye. Although this approach can offer some improvement over eye drops, some potential problems of this approach may include implantation of the implant at the desire tissue location, retention of the implant at the desired tissue location, and sustaining release of the drug at the desired therapeutic level for an extended period of time. For example in the case of glaucoma treatment, undetected and premature loss of an implant can result in no drug being delivered, and the patient can potentially suffer a reduction in vision, possibly even blindness.
In light of the above, it would be desirable to provide improved drug delivery implants that overcome at least some of the above mentioned shortcomings.
The present invention provides improved implant devices, systems and methods for insertion into a punctum of a patient. In many embodiments, the implant device can be reliably retained in the eye such that the therapeutic agent can be delivered for an extended period of time.
In a first aspect, embodiments of the present invention provide an implant for insertion into a punctum of a patient. The implant comprises a drug core having a distal end and a proximal end. The distal end of the drug core has a cross section suitable for insertion through a punctum. The drug core comprises a therapeutic agent deliverable into the eye. A sheath is disposed over a portion of the drug core to define at least one exposed surface of the drug core. The at least one exposed surface of the drug core can be located near the proximal end to contact a tear or tear film fluid and release the therapeutic agent at therapeutic levels over a sustained period when the implant is implanted for use.
In many embodiments, a retention structure is attached to the drug core to retain the drug core near and/or in the punctum. The retention structure may be attached to the drug core via the sheath. The retention structure can comprise a hydrogel adapted to expand when the retention structure is placed in the punctum. The retention structure can comprise an attachment member having an axially oriented surface. Expansion of the hydrogel can urge against the axially oriented surface to retain the hydrogel while the hydrogel is hydrated. The attachment member can comprise at least one of a protrusion, a flange, a rim, or an opening through a portion of the retention structure.
In many embodiments, the retention structure comprises a flange near the at least one exposed surface to retain the surface near the punctum. The retention structure may have a size suitable to fit at least partially within the canalicular lumen. The retention structure can be expandable between a small profile configuration suitable for insertion and a large profile configuration to anchor the retention structure in the lumen, and the retention structure can be attached near the distal end of the drug core. In specific embodiments, the retention structure can slide along the drug core near the proximal end when the retention structure expands from the small profile configuration to the large profile configuration. A length of the retention structure along the drug core can be shorter in the large profile configuration than the small profile configuration.
In some embodiments, the retention structure is resiliently expandable. The small profile may have a cross section of no more than about 0.2 mm, and the large profile may have a cross section of no more than about 2.0 mm. The retention structure may comprise a tubular body having arms separated by slots. An occlusive element can be mounted to and expandable with the retention structure to inhibit tear flow. The retention structure can be disposed at least partially over the drug core. An occlusive element may inhibit tear flow through the lumen, and the occlusive element may cover at least a portion of the retention structure to protect the lumen from the retention structure.
In many embodiments, the sheath body may comprise a layer disposed over the drug core to inhibit release of the therapeutic agent through the layer. The drug core can release the therapeutic agent through the exposed surface. The drug core may releases the therapeutic agent at therapeutic levels throughout a time period of at least one week when the implant is implanted with the surface exposed to the tear or tear film fluid. The drug core can comprise inclusions of the agent and the agent is soluble in the drug core to provide a substantially uniform release rate when the drug core is implanted.
In some embodiments, an occlusive element may inhibit tear fluid flow through the canalicular lumen. For example, the occlusive element can shaped to block tear flow through the canalicular lumen.
In many embodiments, an implant for insertion into a punctum of a patient is provided. The implant comprises a therapeutic agent, and a material to hold the therapeutic agent. A retention structure is disposed over at least a portion of the material, and the retention structure is expandable from the material to retain the material near the punctum.
In many embodiments, the material holds the therapeutic agent in at least one of a reservoir or a matrix. An occlusive element may be supported by the retention structure. The retention structure may be expandable between a small profile configuration suitable for insertion and a large profile configuration to anchor the retention structure in the lumen, and the occlusive element may expand with the retention structure.
In another aspect, embodiments of the present invention provide a method of treating an eye with a therapeutic agent. The method comprises inserting a retention structure and a distal end of a drug core of an implant into a punctum. A therapeutic agent is delivered from the drug core to the eye. An exposed surface of the drug core is limited near the proximal end of the drug core with a sheath. The exposed surface may contact the tear or tear film fluid such that the treatment agent migrates from the exposed surface to the eye over a sustained period while the drug core is retained near the punctum by the retention structure.
In many embodiments, a method of treating an eye with a therapeutic agent is provided. The method comprises inserting a retention structure and a distal end of a drug core through a punctum so that the drug core is retained near the punctum. The drug core comprises a therapeutic agent deliverable to the eye and wherein an exposed surface of the drug core located near the proximal end of the drug core. The exposed surface contacts the tear or tear film fluid and the treatment agent migrates from the exposed surface to the eye over a sustained period while the drug core is retained near the punctum.
In many embodiments, the retention structure expands from a narrow profile configuration to a wide profile configuration. The retention structure hydrates when inserted through the punctum to expand from a narrow profile configuration to a wide profile configuration.
In many embodiments, a method of treating an eye with a therapeutic agent is provided, the method comprises inserting a retention structure through a punctum into a canalicular lumen so that a drug core is anchored to the lumen with the retention structure and releases effective amounts of a therapeutic agent into a tear or tear film fluid of the eye. The drug core is removed from the retention structure while the retention structure remains anchored to the lumen. A replacement drug core is attached to the retention structure while the retention structure remains anchored to the lumen. At least one exposed surface of the replacement drug core releases the therapeutic agent at therapeutic levels over a sustained period.
In many embodiments, a method for treating an eye is provided. The method comprises inserting a distal end of an implant into a punctum. A retention structure of the implant is expanded so as to inhibit expulsion of the implant. The expansion of the implant helps to occlude a flow of tear fluid through the punctum. A therapeutic agent is delivered from a proximal end of the implant to the tear fluid adjacent the eye. Delivery of the therapeutic agent is inhibited distally of the proximal end.
In many embodiments, delivery of the therapeutic agent to the tear is inhibited with a sheath having a portion exposed to the tear fluid. In specific embodiments, the retention structure may comprise a superelastic or shape memory alloy. The retention structure comprise a hydrogel and extends distally of the drug core.
In another aspect many embodiments of the present invention provide an implant for treating an eye. The eye has a tear fluid and a punctum. The implant comprises a drug core having a proximal end, a distal end, and a cross section suitable for insertion into the punctum. A sheath is disposed over the drug core distally of the proximal end. A swellable material is disposed distally of the proximal end. The swellable material is adapted to swell after insertion into the punctum to retain the drug core and occlude the tears in fluid communication with the drug core.
In many embodiments, wings are connected to the sheath near the proximal end of the drug core. The wings can be sized to remain outside the punctum so as to retain the proximal end of the drug core near the punctum.
In many embodiments, an implant for treating an eye is provided. The eye has a tear fluid and a punctum. The implant comprises a drug core having a proximal end, a distal end, and a cross section suitable for insertion into the punctum. A sleeve is disposed over the drug core at least distally of the proximal end. A swellable material is disposed distally of the proximal end and at least partially covered by the sleeve. The swellable material is adapted to swell after insertion into the punctum to retain the drug core and occlude the tears in fluid communication with the drug core.
In many embodiments, the sleeve comprises tabs to retain the punctal plug upon expansion of the swellable material.
In many embodiments, a punctal plug for treating an eye is provided. The eye has a tear fluid and a punctum. The plug comprises a plug body, and a drug core inside the plug body. The drug core comprises a mixture of therapeutic agent and a matrix. A surface of the core is exposed to the tear fluid to treat the eye.
In specific embodiments, the drug core is capable of resilient expansion to accommodate a needle inserted therein while the plug is inserted into a punctum of the eye.
In many embodiments, a punctal plug for treating an eye is provided. The eye has a tear fluid and a punctum. The plug comprises an expandable retention element to expand and engage the punctum when positioned in the eye. A body is connected to the expandable retention element and comprises a protrusion for removal of the retention element from the punctum.
In many embodiments, the expandable retention element comprises a swellable material and the body is adapted to retain the swellable material while the body is removed. In specific embodiments, the swellable material may comprise a hydrogel.
The anatomical tissue structures shown in
Drug core 110 is surrounded by a sheath body 120. Sheath body 120 is can be substantially impermeable to the therapeutic agent, so that the therapeutic agent is often released from an exposed surface on an end of drug core 110 that is not covered with sheath body 120. A retention structure 130 is connected to drug core 110 and sheath body 120. Retention structure 130 is shaped to retain the implant in a hollow tissue structure, for example, a punctum of a canaliculus as described above.
An occlusive element 140 is disposed on and around retention structure 130. Occlusive element 140 is impermeable to tear flow and occludes the hollow tissue structure and may also serve to protect tissues of the tissue structure from retention structure 130 by providing a more benign tissue-engaging surface. Sheath body 120 includes a sheath body portion 150 that connects to retention structure 130 to retain sheath body 120 and drug core 110. Sheath body portion 150 can include a stop to limit movement of sheath body 120 and drug core 110. In many embodiments, sheath body portion 150 can be formed with a bulbous tip 150B. Bulbous tip 150B can comprise a convex rounded external portion that provides atraumatic entry upon 11 introduction into the canaliculus. In many embodiments, sheath body portion 150B can be integral with occlusive element 140.
In an embodiment, the drug core is implanted between sclera 8 and conjunctiva 9 without sheath body 128. In this embodiment without the sheath body, the physical characteristics of the drug core can be adjusted to compensate for the increased exposed surface of drug core, for example by reducing the concentration of dissolved therapeutic agent in the drug core matrix as described herein.
The cores and sheath bodies described herein can be implanted in a variety of tissues in several ways. Many of the cores and sheaths described herein, in particular the structures described with reference to
As shown in
As shown in
Once implant 620 has been positioned in the canalicular lumen at the desired depth in relation to the punctum, sheath 610 is retracted to expose implant 620 at the desired location in the canalicular lumen. A plunger 630 can be used to retract sheath 610. A shaft 640 mechanically couples sheath 610 to plunger 630. Thus, retraction of plunger 630 in the proximal direction can retract sheath 610 in the proximal direction to expose implant 620 at the desired location in the canalicular lumen. Implant 620 can be any of the implants as described herein. Often, implant 620 will comprise a resilient member that expands to a large profile configuration when sheath 610 is retracted. In many embodiments, insertion tool 600 can include a dilator to dilate the punctum prior to insertion of the implant, and the dilator can be positioned on an end of the insertion tool that opposes the end loaded with the implant, as described herein above.
In many embodiments, the drug delivery system comprises a modular system that includes a drug insert and a commercially available punctum plug that can accommodate the drug insert. The drug insert can be adapted to be placed in the bore of the punctum plug, and can be held in place via an interference fit between the outer diameter of the drug insert and the inner diameter of the silicone plug bore. The assembled system can be packaged and sterilized and delivered to the physician in this configuration.
In many embodiments, a punctal plug for treating dry eye comprises a swellable material connected to a sleeve body without a drug core, for example many of the swellable materials and sleeve bodies described in
The drug insert may comprise a thin-walled polyimide tube with a drug core comprising Latanoprost dispersed in Nusil 6385 (MAF 970), a medical grade solid silicone that serves as the matrix for drug delivery. The distal end of the drug insert can be sealed with a cured film of solid Loctite 4305 medical grade adhesive. Since the drug insert can be placed within the bore of the punctum plug, the Loctite 4305 adhesive may not come into contact with either tissue or the tear film. The inner diameter of the drug insert can be 0.32 mm; the length can be 0.95 mm. In three embodiments, the Latanoprost concentration can be tested clinically: Drug core containing 3.5, 7 or 14 μg Latanoprost. In many embodiments, an overall elution rate can be approximately 100 ng/day, and the drug core can comprise 14 μg of Latanoprost, such that the drug can be delivered for ˜120 days. The overall weight of the drug core, including Latanoprost, can be approximately 70 μg. The weight of the drug insert including the polyimide sleeve can be approximately 100 μg.
All materials currently being used in the construction of the drug insert are medical grade materials that have passed a battery of safety/toxicity tests. The table below summarizes the biocompatibility testing performed by the manufacturers on the drug insert materials.
In many embodiments, the drug core can comprise silicone. Latanoprost, at the desired concentration, can be dispersed in uncured Nusil 6385 silicone, injected into a polyimide sleeve, and cured at room temperature. This method can result in a solid silicone matrix comprising the desired concentration of Latanoprost.
In many embodiments, the sleeve can comprise polyimide. The polyimide sleeve can house the drug core so as to provide structural support and a barrier to lateral drug diffusion. The inner diameter of the sleeve can be 0.32 mm, and the wall thickness can be 0.013 mm.
The sheath body comprises appropriate shapes and materials to control migration of the therapeutic agent from the drug core. The sheath body houses the core and can fit snugly against the core. The sheath body is made from a material that is substantially impermeable to the therapeutic agent so that the rate of migration of the therapeutic agent may be largely controlled by the exposed surface area of the drug core that is not covered by the sheath body. In many embodiments, migration of the therapeutic agent through the sheath body can be about one tenth of the migration of the therapeutic agent through the exposed surface of the drug core, or less, often being one hundredth or less. In other words, the migration of the therapeutic agent through the sheath body is at least about an order of magnitude less that the migration of the therapeutic agent through the exposed surface of the drug core. Suitable sheath body materials include polyimide, polyethylene terephthalate” (hereinafter “PET”). The sheath body has a thickness, as defined from the sheath surface adjacent the core to the opposing sheath surface away from the core, from about 0.00025″ to about 0.0015″. The total diameter of the sheath that extends across the core ranges from about 0.2 mm to about 1.2 mm. The core may be formed by dip coating the core in the sheath material. Alternatively or in combination, the sheath body can comprise a tube and the core introduced into the sheath, for example as a liquid or solid that can be slid, injected and/or extruded into the sheath body tube. The sheath body can also be dip coated around the core, for example dip coated around a pre-formed core.
The sheath body can be provided with additional features to facilitate clinical use of the implant. For example, the sheath may receive a drug core that is exchangeable while the retention structure and sheath body remain implanted in the patient. The sheath body is often rigidly attached to the retention structure as described above, and the core is exchangeable while the retention structure retains the sheath body. In specific embodiments, the sheath body can be provided with external protrusions that apply force to the sheath body when squeezed and eject the core from the sheath body. Another drug core can then be positioned in the sheath body. In many embodiments, the sheath body and/or retention structure may have a distinguishing feature, for example a distinguishing color, to show placement such that the placement of the sheath body and/or retention structure in the canaliculus or other body tissue structure can be readily detected by the patient. The retention element and/or sheath body may comprise at least one mark to indicate the depth of placement in the canaliculus such that the retention element and/or sheath body can be positioned to a desired depth in the canaliculus based on the at least one mark.
The retention structure comprises an appropriate material that is sized and shaped so that the implant can be easily positioned in the desired tissue location, for example the canaliculus. The retention structure is mechanically deployable and typically expands to a desired cross sectional shape, for example with the retention structure comprising a super elastic shape memory alloy such as Nitinol™. Other materials in addition to Nitinol™ can be used, for example resilient metals or polymers, plastically deformable metals or polymers, shape memory polymers, and the like, to provide the desired expansion. In some embodiments shapeable polymers and coated fibers available from Biogeneral, Inc. of San Diego, Calif. may be used. Many metals such as stainless steels and non-shape memory alloys can be used and provide the desired expansion. This expansion capability permits the implant to fit in hollow tissue structures of varying sizes, for example canaliculae ranging from 0.3 mm to 1.2 mm (i.e. one size fits all). Although a single retention structure can be made to fit canaliculae from 0.3 to 1.2 mm across, a plurality of alternatively selectable retention structures can be used to fit this range if desired, for example a first retention structure for canaliculae from 0.3 to about 0.9 mm and a second retention structure for canaliculae from about 0.9 to 1.2 mm. The retention structure has a length appropriate to the anatomical structure to which the retention structure attaches, for example a length of about 3 mm for a retention structure positioned near the punctum of the canaliculus. For different anatomical structures, the length can be appropriate to provide adequate retention force, e.g. 1 mm to 15 mm lengths as appropriate.
Although the sheath body and drug core are attached to one end of the retention structure as described above, in many embodiments the other end of retention structure is not attached to drug core and sheath body so that the retention structure can slide over the sheath body and drug core while the retention structure expands. This sliding capability on one end is desirable as the retention structure may shrink in length as the retention structure expands in width to assume the desired cross sectional width. However, it should be noted that many embodiments may employ a sheath body that does not slide in relative to the core.
In many embodiments, the retention structure can be retrieved from tissue. A protrusion, for example a hook, a loop, or a ring, can extend from the retention structure to facilitate removal of the retention structure.
In many embodiments the sheath and retention structure can comprise two parts.
The occlusive element comprises an appropriate material that is sized and shaped so that the implant can at least partially inhibit, even block, the flow of fluid through the hollow tissue structure, for example lacrimal fluid through the canaliculus. The occlusive material shown is a thin walled membrane of a biocompatible material, for example silicone, that can expand and contract with the retention structure. The occlusive element is formed as a separate thin tube of material that is slid over the end of the retention structure and anchored to one end of the retention structure as described above. Alternatively, the occlusive element can be formed by dip coating the retention structure in a biocompatible polymer, for example silicone polymer. The thickness of the occlusive element can be in a range from about 0.01 mm to about 0.15 mm, and often from about 0.05 mm to 0.1 mm.
A “therapeutic agent” can comprise a drug may be any of the following or their equivalents, derivatives or analogs, including, anti-glaucoma medications, (e.g. adrenergic agonists, adrenergic antagonists (beta blockers), carbonic anhydrase inhibitors (CAIs, systemic and topical), parasympathomimetics, prostaglandins and hypotensive lipids, and combinations thereof), antimicrobial agent (e.g., antibiotic, antiviral, antiparacytic, antifungal, etc.), a corticosteroid or other anti-inflammatory (e.g., an NSAID), a decongestant (e.g., vasoconstrictor), an agent that prevents of modifies an allergic response (e.g., an antihistamine, cytokine inhibitor, leucotriene inhibitor, IgE inhibitor, immunomodulator), a mast cell stabilizer, cycloplegic or the like. Examples of conditions that may be treated with the therapeutic agent(s) include but are not limited to glaucoma, pre and post surgical treatments, dry eye and allergies. In some embodiments, the therapeutic agent may be a lubricant or a surfactant, for example a lubricant to treat dry eye.
Exemplary therapeutic agents include, but are not limited to, thrombin inhibitors; antithrombogenic agents; thrombolytic agents; fibrinolytic agents; vasospasm inhibitors; vasodilators; antihypertensive agents; antimicrobial agents, such as antibiotics (such as tetracycline, chlortetracycline, bacitracin, neomycin, polymyxin, gramicidin, cephalexin, oxytetracycline, chloramphenicol, rifampicin, ciprofloxacin, tobramycin, gentamycin, erythromycin, penicillin, sulfonamides, sulfadiazine, sulfacetamide, sulfamethizole, sulfisoxazole, nitrofurazone, sodium propionate), antifungals (such as amphotericin B and miconazole), and antivirals (such as idoxuridine trifluorothymidine, acyclovir, gancyclovir, interferon); inhibitors of surface glycoprotein receptors; antiplatelet agents; antimitotics; microtubule inhibitors; anti-secretory agents; active inhibitors; remodeling inhibitors; antisense nucleotides; anti-metabolites; antiproliferatives (including antiangiogenesis agents); anticancer chemotherapeutic agents; anti-inflammatories (such as hydrocortisone, hydrocortisone acetate, dexamethasone 21-phosphate, fluocinolone, medrysone, methylprednisolone, prednisolone 21-phosphate, prednisolone acetate, fluoromethalone, betamethasone, triamcinolone, triamcinolone acetonide); non steroidal anti-inflammatories (NSAIDs) (such as salicylate, indomethacin, ibuprofen, diclofenac, flurbiprofen, piroxicam indomethacin, ibuprofen, naxopren, piroxicam and nabumetone). Such anti inflammatory steroids contemplated for use in the methodology of the present invention, include triamcinolone acetonide (generic name) and corticosteroids that include, for example, triamcinolone, dexamethasone, fluocinolone, cortisone, prednisolone, flumetholone, and derivatives thereof.); antiallergenics (such as sodium chromoglycate, antazoline, methapyriline, chlorpheniramine, cetrizine, pyrilamine, prophenpyridamine); anti proliferative agents (such as 1,3-cis retinoic acid, 5-fluorouracil, taxol, rapamycin, mitomycin C and cisplatin); decongestants (such as phenylephrine, naphazoline, tetrahydrazoline); miotics and anti-cholinesterase (such as pilocarpine, salicylate, carbachol, acetylcholine chloride, physostigmine, eserine, diisopropyl fluorophosphate, phospholine iodine, demecarium bromide); antineoplastics (such as carmustine, cisplatin, fluorouracil3; immunological drugs (such as vaccines and immune stimulants); hormonal agents (such as estrogens, —estradiol, progestational, progesterone, insulin, calcitonin, parathyroid hormone, peptide and vasopressin hypothalamus releasing factor); immunosuppressive agents, growth hormone antagonists, growth factors (such as epidermal growth factor, fibroblast growth factor, platelet derived growth factor, transforming growth factor beta, somatotrapin, fibronectin); inhibitors of angiogenesis (such as angiostatin, anecortave acetate, thrombospondin, anti-VEGF antibody); dopamine agonists; radiotherapeutic agents; peptides; proteins; enzymes; extracellular matrix; components; ACE inhibitors; free radical scavengers; chelators; antioxidants; anti polymerases; photodynamic therapy agents; gene therapy agents; and other therapeutic agents such as prostaglandins, antiprostaglandins, prostaglandin precursors, including antiglaucoma drugs including beta-blockers such as Timolol, betaxolol, levobunolol, atenolol, and prostaglandin analogues such as Bimatoprost, travoprost, Latanoprost etc; carbonic anhydrase inhibitors such as acetazolamide, dorzolamide, brinzolamide, methazolamide, dichlorphenamide, diamox; and neuroprotectants such as lubezole, nimodipine and related compounds; and parasympathomimetrics such as pilocarpine, carbachol, physostigmine and the like.
The amount of drug associated with the drug-delivery device may vary depending on the particular agent, the desired therapeutic benefit and the time during which the device is intended to deliver the therapy. Since the devices of the present invention present a variety of shapes, sizes and delivery mechanisms, the amount of drug associated with the device will depend on the particular disease or condition to be treated, and the dosage and duration that is desired to achieve the therapeutic effect. Generally, the amount of drug is at least the amount of drug that upon release from the device, is effective to achieve the desired physiological or pharmacological local or systemic effects.
Embodiments of the drug delivery devices of the present invention can be adapted to provide delivery of drug at a daily rate that is substantially below the therapeutically effective drop form of treatment so as to provide a large therapeutic range with a wide safety margin. For example, many embodiments treat the eye with therapeutic levels for extended periods that are no more than 5 or 10 percent of the daily drop dosage. Consequently, during an initial bolus or washout period of about one to three days, the implant can elute the therapeutic agent at a rate that is substantially higher than the sustained release levels and well below the daily drop form dosage. For example, with an average sustained release level of 100 ng per day, and an initial release rate of 1000 to 1500 ng per day, the amount of drug initially released is less than the 2500 ng of drug that may be present in a drop of drug delivered to the eye. This used use of sustained release levels substantially below the amount of drug in a drop and/or drops administered daily allows the device to release a therapeutically beneficial amount of drug to achieve the desired therapeutic benefit with a wide safety margin, while avoiding an inadequate or excessive amount of drug at the intended site or region.
An extended period of time may mean a relatively short period of time, for example minutes or hours (such as with the use of an anesthetic), through days or weeks (such as the use of pre-surgical or post-surgical antibiotics, steroids, or NSAIDs and the like), or longer (such as in the case of glaucoma treatments), for example months or years (on a recurring basis of use of the device).
For example, a drug such as Timolol maleate, a beta1 and beta2 (non-selective) adrenergic receptor blocking agent can be used in the device for a release over an extended period of time such as 3 months. Three months is a relatively typical elapsed time between physician visits for a glaucoma patient undergoing topical drop therapy with a glaucoma drug, although the device could provide treatment for longer or shorter durations. In the three month example, a 0.25% concentration of Timolol translates to from 2.5 to 5 mg/1000 μL, typically being 2.5 mg/1000 μL. A drop of Timolol for topical application is usually in the range of 40-60 μL, typically being 50 μL. Thus, there may be 0.08-0.15 mg, typically being 0.125 mg of Timolol in a drop. There may be approximately 8% (optionally 6-10%) of the drop left in the eye after 5 minutes, so about 10 μg of the drug is available at that time. Timolol may have a bioavailability of 30-50%, which means that from 1.5 to 7.5 μg, for example 4 μg of the drug is available to the eye. Timolol is generally applied twice a day, so 8 (or 3-15) μg is available to the eye each day. Therefore, a delivery device might contain from 270 to 1350 μg, for example 720 μg, of the drug for a 90 day, or 3 month, extended release. The drug would be contained within the device and eluted based on the polymer or drug/hydrogel concentration. The drug can be similarly contained on the device and eluted for olopatadine hydrochloride (Patanol®) and other drugs in a manner similar to Timolol.
Commercially available solutions of Timolol maleate are available in 0.25% and 0.5% preparations, and the initial dosage can be 1 drop twice per day of 0.25% solution. A 0.25% concentration of Timolol is equivalent to 2.5 mg per 1000 μl. A sustained release quantity of Timolol released each day from the drug core can be from about 3 to 15 ug each day. Although the sustained release quantity delivered each day from the device may vary, a sustained release delivery of about 8 μg per day corresponds to about 3.2% of the 0.250 mg of Timolol applied with two drops of a 0.25% solution.
For example, in the case of Latanoprost (Xalatan), a prostaglandin F2α analogue, this glaucoma medication has concentrations that are about 1/10th that of Timolol. Therefore, the amount of drug on the implantable device, depending on the bioavailability, would be significantly less—approximately 20-135 μg and typically 50-100 μg—for Latanoprost and other prostaglandin analogues. This also translates to a device that can either be smaller than one required for a beta blocker delivery or can house more drug for a longer release period.
A drop of Xalatan contains about 2.5 μg of Latanoprost, assuming a 50 μL drop volume. Therefore, assuming that about 8% of 2.5 μg is present 5 minutes after instillation, only about 200 ng of drug remains on the eye. Based on the Latanoprost clinical trials, this amount is effective in lowering IOP for at least 24 hours. Pfizer/Pharmacia conducted several dose-response studies in support of the NDA for Xalatan. The doses ranged from 12.5 μg/mL to 115 μg/mL of Latanoprost. The current dose of Latanoprost, 50 μg/mL, given once per day, was shown to be optimal. However, even the lowest doses of 12.5 μg/mL QD or 15 μg/mL BID consistently gave about 60-75% of the IOP reduction of the 50 μg/mL QD dose. Based on the assumptions above, a 12.5-μg/mL concentration provides 0.625 μg of Latanoprost in a 50 μL drop, which results in only about 50 ng (8%) of drug remaining in the eye after 5 minutes.
In many embodiments, the concentrations of Latanoprost are about 1/100th, or 1 percent, that of Timolol, and in specific embodiments the concentrations of Latanoprost may be about 1/50th, or 2 percent, that of Timolol. For example, commercially available solution preparations of Latanoprost are available at concentrations 0.005%, often delivered with one drop per day. In many embodiments, the therapeutically effective concentration of drug released from the device per day can be about 1/100th of Timolol, about 30 to 150 ng per day, for example about 80 ng, assuming tear washout and bioavailability similar to Timolol. For example, the amount of drug on the implantable device, can be significantly less—approximately 1% to 2% of Timolol, for example 2.7 to 13.5 μg, and can also be about 3 to 20 μg, for Latanoprost and other prostaglandin analogues. Although the sustained release amount of Latanoprost released each day can vary, a sustained release of 80 ng per day corresponds to about 3.2% of the 2.5 μg of Latanoprost applied with a single drop of a 0.005% solution
For example, in the case of Bimatoprost (Lumigan), a synthetic prostamide prostaglandin analogue, this glaucoma medication may have concentrations that are 1/20th or less than that of Timolol. Therefore, the amount of drug loaded on the extended release device for a 3 to 6 month extended release, depending on the bioavailability, can be significantly less, approximately 5-30 μg and typically 10-20 μg—for Bimatoprost and analogues and derivatives thereof. In many embodiments, the implant can house more drug for a longer sustained release period, for example 20-40 μg for a sustained release period of 6 to 12 months with Bimatoprost and its derivatives. This decrease in drug concentration can also translate to a device that can be smaller than one required for a beta blocker delivery.
Commercially available solution concentrations of Bimatoprost are 0.03% by weight, often delivered once per day. Although the sustained release amount of Bimatnoprost released each day can vary, a sustained release of 300 μg per day corresponds to about 2% of the 15 μg of Bimatoprost applied with a single drop of a 0.03% solution. Work in relation with the present invention suggests that even lower sustained release doses of Bimatoprost can provide at least some reduction in intraocular pressure, for example 20 to 200 ng of Bimatoprost and daily sustained release dosages of 0.2 to 2% of the daily drop dosage.
For example, in the case of Travoprost (Travatan), a prostaglandin F2α analogue, this glaucoma medication may have concentrations that are 2% or less than that of Timolol. For example, commercially available solution concentrations are 0.004%, often delivered once per day. In many embodiments, the therapeutically effective concentration of drug released from the device per day can be about 65 ng, assuming tear washout and bioavailability similar to Timolol. Therefore, the amount of drug on the implantable device, depending on the bioavailability, would be significantly less. This also translates to a device that can either be smaller than one required for a beta blocker delivery or can house more drug for a longer release period. For example, the amount of drug on the implantable device, can be significantly less-approximately 1/100 of Timolol, for example 2.7 to 13.5 μg, and typically about 3 to 20 μg, for Travoprost, Latanoprost and other prostaglandin F2α analogues. Although the sustained release amount of Latanoprost released each day can vary, a sustained release of 65 ng per day corresponds to about 3.2% of the 2.0 μg of Travoprost applied with a single drop of a 0.004% solution.
In some embodiments, the therapeutic agent may comprise a cortico steroid, for example fluocinolone acetonide, to treat a target ocular tissue. In specific embodiments, fluocinolone acetonide can be released from the canaliculus and delivered to the retina as a treatment for diabetic macular edema (DME).
It is also within the scope of this invention to modify or adapt the devices to deliver a high release rate, a low release rate, a bolus release, a burst release, or combinations thereof. A bolus of the drug may be released by the formation of an erodable polymer cap that is immediately dissolved in the tear or tear film. As the polymer cap comes in contact with the tear or tear film, the solubility properties of the polymer enable the cap to erode and the drug is released all at once. A burst release of a drug can be performed using a polymer that also erodes in the tear or tear film based on the polymer solubility. In this example, the drug and polymer may be stratified along the length of the device so that as the outer polymer layer dissolves, the drug is immediately released. A high or low release rate of the drug could be accomplished by changing the solubility of the erodable polymer layer so that the drug layer released quickly or slowly. Other methods to release the drug could be achieved through porous membranes, soluble gels (such as those in typical ophthalmic solutions), microparticle encapsulations of the drug, or nanoparticle encapsulation, depending on the size of the drug molecule.
The drug core comprises the therapeutic agent and materials to provide sustained release of the therapeutic agent. The therapeutic agent migrates from the drug core to the target tissue, for example ciliary muscles of the eye. The therapeutic agent may optionally be only slightly soluble in the matrix so that a small amount of therapeutic agent is dissolved in the matrix and available for release from the surface of drug core 110. As the therapeutic agent diffuses from the exposed surface of the core to the tear or tear film, the rate of migration from the core to the tear or tear film can be related to the concentration of therapeutic agent dissolved in the matrix. In addition or in combination, the rate of migration of therapeutic agent from the core to the tear or tear film can be related to properties of the matrix in which the therapeutic agent dissolves. In specific embodiments, the rate of migration from the drug core to the tear or tear film can be based on a silicone formulation. In some embodiments, the concentration of therapeutic agent dissolved in the drug core may be controlled to provide the desired rate of release of the therapeutic agent. The therapeutic agent included in the core can include liquid, solid, solid gel, solid crystalline, solid amorphous, solid particulate, and/or dissolved forms of the therapeutic agent. In a preferred embodiment, the drug core comprises a silicone matrix containing the therapeutic agent. The therapeutic agent may comprise liquid or solid inclusions, for example liquid Latanoprost droplets or solid Bimatoprost particles, respectively, dispersed in the silicone matrix.
The drug core can comprise one or more biocompatible materials capable of providing a sustained release of the therapeutic agent. Although the drug core is described above with respect to an embodiment comprising a matrix with a substantially non-biodegradable silicone matrix with inclusions of the drug located therein that dissolve, the drug core can include structures that provide sustained release of the therapeutic agent, for example a biodegradable matrix, a porous drug core, liquid drug cores and solid drug cores. A matrix that contains the therapeutic agent can be formed from either biodegradable or non-biodegradable polymers. A non-biodegradable drug core can include silicone, acrylates, polyethylenes, polyurethane, polyurethane, hydrogel, polyester (e.g., DACRON® from E. I. Du Pont de Nemours and Company, Wilmington, Del.), polypropylene, polytetrafluoroethylene (PTFE), expanded PTFE (ePTFE), polyether ether ketone (PEEK), nylon, extruded collagen, polymer foam, silicone rubber, polyethylene terephthalate, ultra high molecular weight polyethylene, polycarbonate urethane, polyurethane, polyimides, stainless steel, nickel-titanium alloy (e.g., Nitinol), titanium, stainless steel, cobalt-chrome alloy (e.g., ELGILOY® from Elgin Specialty Metals, Elgin, Ill.; CONICHROME® from Carpenter Metals Corp., Wyomissing, Pa.). A biodegradable drug core can comprise one or more biodegradable polymers, such as protein, hydrogel, polyglycolic acid (PGA), polylactic acid (PLA), poly(L-lactic acid) (PLLA), poly(L-glycolic acid) (PLGA), polyglycolide, poly-L-lactide, poly-D-lactide, poly(amino acids), polydioxanone, polycaprolactone, polygluconate, polylactic acid-polyethylene oxide copolymers, modified cellulose, collagen, polyorthoesters, polyhydroxybutyrate, polyanhydride, polyphosphoester, poly(alpha-hydroxy acid) and combinations thereof. In some embodiments the drug core can comprise at least one of hydrogel polymer.
The rate of release of the therapeutic agent can be related to the concentration of therapeutic agent dissolved in the drug core. In many embodiments, the drug core comprises non-therapeutic agents that are selected to provide a desired solubility of the therapeutic agent in the drug core. The non-therapeutic agent of the drug core can comprise polymers as described herein and additives. A polymer of the core can be selected to provide the desired solubility of the therapeutic agent in the matrix. For example, the core can comprise hydrogel that may promote solubility of hydrophilic treatment agent. In some embodiments, functional groups can be added to the polymer to provide the desired solubility of the therapeutic agent in the matrix. For example, functional groups can be attached to silicone polymer.
In some embodiments, additives may be used to control the release kinetics of therapeutic agent. For example, the additives may be used to control the concentration of therapeutic agent by increasing or decreasing solubility of the therapeutic agent in the drug core so as to control the release kinetics of the therapeutic agent. The solubility may be controlled by providing appropriate molecules and/or substances that increase and/or decrease the solubility of the dissolved from of the therapeutic agent to the matrix. The solubility of the dissolved from the therapeutic agent may be related to the hydrophobic and/or hydrophilic properties of the matrix and therapeutic agent. For example, surfactants, tinuvin, salts and water can be added to the matrix and may increase the solubility of hydrophilic therapeutic agent in the matrix. In addition, oils and hydrophobic molecules and can be added to the matrix and may increase the solubility of hydrophobic treatment agent in the matrix.
Instead of or in addition to controlling the rate of migration based on the concentration of therapeutic agent dissolved in the matrix, the surface area of the drug core can also be controlled to attain the desired rate of drug migration from the core to the target site. For example, a larger exposed surface area of the core will increase the rate of migration of the treatment agent from the drug core to the target site, and a smaller exposed surface area of the drug core will decrease the rate of migration of the therapeutic agent from the drug core to the target site. The exposed surface area of the drug core can be increased in any number of ways, for example by any of castellation of the exposed surface, a porous surface having exposed channels connected with the tear or tear film, indentation of the exposed surface, protrusion of the exposed surface. The exposed surface can be made porous by the addition of salts that dissolve and leave a porous cavity once the salt dissolves. Hydrogels may also be used, and can swell in size to provide a larger exposed surface area. Such hydrogels can also be made porous to further increase the rate of migration of the therapeutic agent.
Further, an implant may be used that includes the ability to release two or more drugs in combination, such as the structure disclosed in U.S. Pat. No. 4,281,654 (Shell). For example, in the case of glaucoma treatment, it may be desirable to treat a patient with multiple prostaglandins or a prostaglandin and a cholinergic agent or an adrenergic antagonist (beta blocker), such as Alphagan®, or a prostaglandin and a carbonic anhydrase inhibitor.
In addition, drug impregnated meshes may be used such as those disclosed in US Patent Publication No. 2002/0055701 or layering of biostable polymers as described in US Patent Publication No. 2005/0129731. Certain polymer processes may be used to incorporate drug into the devices of the present invention such as, so-called “self-delivering drugs” or PolymerDrugs (Polymerix Corporation, Piscataway, N.J.) are designed to degrade only into therapeutically useful compounds and physiologically inert linker molecules, further detailed in US Patent Publication No. 2005/0048121 (East), hereby incorporated by reference in its entirety. Such delivery polymers may be employed in the devices of the present invention to provide a release rate that is equal to the rate of polymer erosion and degradation and is constant throughout the course of therapy. Such delivery polymers may be used as device coatings or in the form of microspheres for a drug depot injectable (such as a reservoir of the present invention). A further polymer delivery technology may also be adapted to the devices of the present invention such as that described in US Patent Publication No. 2004/0170685 (Carpenter), and technologies available from Medivas (San Diego, Calif.).
In specific embodiments, the drug core matrix comprises a solid material, for example silicone, that encapsulates inclusions of the drug. The drug comprises molecules which are very insoluble in water and slightly soluble in the encapsulating drug core matrix. The inclusions encapsulated by the drug core can be micro-particles having dimensions from about 1 μm to about 100 μm across. The drug inclusions can comprise crystals, for example Bimatoprost crystals, and/or droplets of oil, for example with Latanoprost oil. The drug inclusions can dissolve into the solid drug core matrix and substantially saturate the drug core matrix with the drug, for example dissolution of Latanoprost oil into the solid drug core matrix. The drug dissolved in the drug core matrix is transported, often by diffusion, from the exposed surface of the drug core into the tear film. As the drug core is substantially saturated with the drug, in many embodiments the rate limiting step of drug delivery is transport of the drug from the surface of the drug core matrix exposed to the tear film. As the drug core matrix is substantially saturated with the drug, gradients in drug concentration within the matrix are minimal and do not contribute significantly to the rate of drug delivery. As surface area of the drug core exposed to the tear film is nearly constant, the rate of drug transport from the drug core into the tear film can be substantially constant. Work in relation with the present invention suggests that the solubility of the therapeutic agent in water and molecular weight of the drug can effect transport of the drug from the solid matrix to the tear. In many embodiments, the therapeutic agent is nearly insoluble in water and has a solubility in water of about 0.03% to 0.002% by weight and a molecular weight from about 400 grams/mol. to about 1200 grams/mol.
In many embodiments the therapeutic agent has a very low solubility in water, for example from about 0.03% by weight to about 0.002% by weight, a molecular weight from about 400 grams per mole (g/mol.) to about 1200 g/mol, and is readily soluble in an organic solvent. Cyclosporin A (CsA) is a solid with an aqueous solubility of 27.67 μg/mL at 25° C., or about 0.0027% by weight, and a molecular weight (M.W.) of 1202.6 g/mol. Latanoprost (Xalatan) is a prostaglandin F2α analogue, a liquid oil at room temperature, and has an aqueous solubility of 50 μg/mL in water at 25° C., or about 0.005% by weight and a M.W. of 432.6 g/mol. Bimatoprost (Lumigan) is a synthetic prostamide analogue, a solid at room temperature solubility in water of 300 μg/mL in water at 25° C., or 0.03% by weight, and has a M.W. of 415.6 g/mol.
Work in relation with the present invention indicates that naturally occurring surfactants in the tear film, for example surfactant D and phospholipids, may effect transport of the drug dissolved in the solid matrix from the core to the tear film. The drug core can be adapted in response to the surfactant in the tear film to provide sustained delivery of the drug into the tear film at therapeutic levels. For example, empirical data can be generated from a patient population, for example 10 patients whose tears are collected and analyzed for surfactant content. Elution profiles in the collected tears for a drug that is sparingly soluble in water, for example cyclosporine, can also be measured and compared with elution profiles in buffer and surfactant such that an in vitro model of tear surfactant is developed. An in vitro solution with surfactant based on this empirical data can be used to adjust the drug core in response to the surfactant of the tear film.
The drug cores may also be modified to utilize carrier vehicles such as nanoparticles or microparticles depending on the size of the molecule to be delivered such as latent-reactive nanofiber compositions for composites and nanotextured surfaces (Innovative Surface Technologies, LLC, St. Paul, Minn.), nanostructured porous silicon, known as BiuSilicon®, including micron sized particles, membranes, woven fivers or micromachined implant devices (pSividia, Limited, UK) and protein nanocage systems that target selective cells to deliver a drug (Chimeracore).
In many embodiments, the drug insert comprises of a thin-walled polyimide tube sheath with a drug core comprising Latanoprost dispersed in Nusil 6385 (MAF 970), a medical grade solid silicone that serves as the matrix for drug delivery. The distal end of the drug insert is sealed with a cured film of solid Loctite 4305 medical grade adhesive. The drug insert may be placed within the bore of the punctum plug, the Loctite 4305 adhesive does not come into contact with either tissue or the tear film. The inner diameter of the drug insert can be 0.32 mm; and the length can be 0.95 mm. Three Latanoprost concentrations in the finished drug product can be tested clinically: Drug cores can comprise 3.5, 7 or 14 μg Latanoprost, with percent by weight concentrations of 5, 10 and 20% respectively. Assuming an overall elution rate of approximately 100 ng/day, the drug core comprising 14 μg of Latanoprost is adapted to deliver drug for approximately at least 100 days, for example 120 days. The overall weight of the drug core, including Latanoprost, can be ˜70 μg. The weight of the drug insert including the polyimide sleeve can be approximately 100 μg.
In many embodiments, the drug core may elute with an initial elevated level of therapeutic agent followed by substantially constant elution of the therapeutic agent. In many instances, an amount of therapeutic agent released daily from the core may be below the therapeutic levels and still provide a benefit to the patient. An elevated level of eluted therapeutic agent can result in a residual amount of therapeutic agent and/or residual effect of the therapeutic agent that is combined with a sub-therapeutic amount of therapeutic agent to provide relief to the patient. In embodiments where therapeutic level is about 80 ng per day, the device may deliver about 100 ng per day for an initial delivery period. The extra 20 ng delivered per day can have a beneficial effect when therapeutic agent is released at levels below the therapeutic level, for example at 60 ng per day. As the amount of drug delivered can be precisely controlled, an initial elevated dose may not result in complications and/or adverse events to the patient.
While the exemplary embodiments have been described in some detail, by way of example and for clarity of understanding, those of skill in the art will recognize that a variety of modification, adaptations, and changes may be employed. Hence, the scope of the present invention should be limited solely by the appending claims.
This application is a continuation application of U.S. patent application Ser. No. 15/852,619 filed 22 Dec. 2017, which is a continuation of U.S. patent application Ser. No. 15/405,991 filed 13 Jan. 2017, which is a continuation of U.S. patent application Ser. No. 14/858,555 filed 18 Sep. 2015, which is a continuation of U.S. patent application Ser. No. 14/265,071 filed 29 Apr. 2014, which is a continuation of U.S. patent application Ser. No. 13/184,690, filed 18 Jul. 18 2011, which is a continuation of U.S. patent application Ser. No. 11/695,545, filed 2 Apr. 2007, which claims the benefit under 35 USC 119(e) of U.S. Provisional Application No. 60/787,775 filed on 31 Mar. 2006, and U.S. Provisional Application No. 60/871,864, filed on 26 Dec. 2006, the full disclosures of which are incorporated herein by reference.
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