US20170172794A1 - Reservoir Device for Intraocular Drug Delivery - Google Patents
Reservoir Device for Intraocular Drug Delivery Download PDFInfo
- Publication number
- US20170172794A1 US20170172794A1 US15/366,982 US201615366982A US2017172794A1 US 20170172794 A1 US20170172794 A1 US 20170172794A1 US 201615366982 A US201615366982 A US 201615366982A US 2017172794 A1 US2017172794 A1 US 2017172794A1
- Authority
- US
- United States
- Prior art keywords
- reservoir
- agent
- eye
- delivery
- therapeutic agent
- Prior art date
- Legal status (The legal status is an assumption and is not a legal conclusion. Google has not performed a legal analysis and makes no representation as to the accuracy of the status listed.)
- Abandoned
Links
Images
Classifications
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61F—FILTERS IMPLANTABLE INTO BLOOD VESSELS; PROSTHESES; DEVICES PROVIDING PATENCY TO, OR PREVENTING COLLAPSING OF, TUBULAR STRUCTURES OF THE BODY, e.g. STENTS; ORTHOPAEDIC, NURSING OR CONTRACEPTIVE DEVICES; FOMENTATION; TREATMENT OR PROTECTION OF EYES OR EARS; BANDAGES, DRESSINGS OR ABSORBENT PADS; FIRST-AID KITS
- A61F9/00—Methods or devices for treatment of the eyes; Devices for putting-in contact lenses; Devices to correct squinting; Apparatus to guide the blind; Protective devices for the eyes, carried on the body or in the hand
- A61F9/0008—Introducing ophthalmic products into the ocular cavity or retaining products therein
- A61F9/0017—Introducing ophthalmic products into the ocular cavity or retaining products therein implantable in, or in contact with, the eye, e.g. ocular inserts
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61M—DEVICES FOR INTRODUCING MEDIA INTO, OR ONTO, THE BODY; DEVICES FOR TRANSDUCING BODY MEDIA OR FOR TAKING MEDIA FROM THE BODY; DEVICES FOR PRODUCING OR ENDING SLEEP OR STUPOR
- A61M31/00—Devices for introducing or retaining media, e.g. remedies, in cavities of the body
- A61M31/002—Devices for releasing a drug at a continuous and controlled rate for a prolonged period of time
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61M—DEVICES FOR INTRODUCING MEDIA INTO, OR ONTO, THE BODY; DEVICES FOR TRANSDUCING BODY MEDIA OR FOR TAKING MEDIA FROM THE BODY; DEVICES FOR PRODUCING OR ENDING SLEEP OR STUPOR
- A61M39/00—Tubes, tube connectors, tube couplings, valves, access sites or the like, specially adapted for medical use
- A61M39/02—Access sites
- A61M39/0208—Subcutaneous access sites for injecting or removing fluids
-
- 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
- A61F2250/00—Special features of prostheses classified in groups A61F2/00 - A61F2/26 or A61F2/82 or A61F9/00 or A61F11/00 or subgroups thereof
- A61F2250/0058—Additional features; Implant or prostheses properties not otherwise provided for
- A61F2250/0067—Means for introducing or releasing pharmaceutical products into the body
-
- 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
- A61F2250/00—Special features of prostheses classified in groups A61F2/00 - A61F2/26 or A61F2/82 or A61F9/00 or A61F11/00 or subgroups thereof
- A61F2250/0058—Additional features; Implant or prostheses properties not otherwise provided for
- A61F2250/0067—Means for introducing or releasing pharmaceutical products into the body
- A61F2250/0068—Means for introducing or releasing pharmaceutical products into the body the pharmaceutical product being in a reservoir
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61M—DEVICES FOR INTRODUCING MEDIA INTO, OR ONTO, THE BODY; DEVICES FOR TRANSDUCING BODY MEDIA OR FOR TAKING MEDIA FROM THE BODY; DEVICES FOR PRODUCING OR ENDING SLEEP OR STUPOR
- A61M39/00—Tubes, tube connectors, tube couplings, valves, access sites or the like, specially adapted for medical use
- A61M39/02—Access sites
- A61M2039/0205—Access sites for injecting media
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61M—DEVICES FOR INTRODUCING MEDIA INTO, OR ONTO, THE BODY; DEVICES FOR TRANSDUCING BODY MEDIA OR FOR TAKING MEDIA FROM THE BODY; DEVICES FOR PRODUCING OR ENDING SLEEP OR STUPOR
- A61M2205/00—General characteristics of the apparatus
- A61M2205/04—General characteristics of the apparatus implanted
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61M—DEVICES FOR INTRODUCING MEDIA INTO, OR ONTO, THE BODY; DEVICES FOR TRANSDUCING BODY MEDIA OR FOR TAKING MEDIA FROM THE BODY; DEVICES FOR PRODUCING OR ENDING SLEEP OR STUPOR
- A61M2210/00—Anatomical parts of the body
- A61M2210/06—Head
- A61M2210/0612—Eyes
Definitions
- the present invention relates to improved delivery devices and methods of use. More particularly, the present invention relates to minimally invasive, refillable, sustained release delivery devices particularly suitable for the delivery of therapeutic agents to limited access regions, such as the posterior chamber of the eye.
- the delivery of drugs to the eye presents many challenges.
- the ocular absorption of systemically administered pharmacologic agents is limited by the blood ocular barrier, namely the tight junctions of the retinal pigment epithelium and vascular endothelial cells. High systemic doses can penetrate this blood ocular barrier in relatively small amounts, but expose the patient to the risk of systemic toxicity.
- Topical delivery of drugs often results in limited ocular absorption due to the complex hydrophobic/hydrophilic properties of the cornea and sclera. Additionally, topical agents are mechanically removed by the blink mechanism such that only approximately 15% of a single drop is absorbed. Diffusion of topically administered drugs to the posterior chamber occurs, but often at sub-therapeutic levels.
- Intravitreal injection of drugs is an effective means of delivering a drug to the posterior segment in high concentrations.
- these repeated intraocular injections carry the risk of infection, hemorrhage and retinal detachment. Patients also find this procedure somewhat difficult to endure.
- U.S. Pat. No. 4,300,557 describes an intraocular implant in the form of a silicone capsule which can be filled with a drug to be delivered.
- the capsule is inserted in the vitreous region of the eye by making an incision in the eye, inserting the capsule and closing the incision.
- the capsule remains in place for a period of time and may be removed by making a second surgical incision into the eye and retrieving the device.
- the capsule has an attached tube which passes through the surface of the eye and extends outward from the eye useful for the subsequent injection of a drug. While in the vitreous, the device is not anchored and may move about freely.
- U.S. Pat. No. 5,378,475 (often referred to as Vitrasert) describes a device 15 which has been developed for insertion in the vitreous region of the eye, and is described in T. J. Smith et al., Sustained-Release Ganciclovir, Arch. Ophthalmol, 110, 255-258 (1992) and G. E. Sanborn, et al., Sustained-Release Ganciclovir Therapy for Treatment of Cytomegalovirus Retinitis. Use of an Intravitreal Device, Arch. Ophthalmol, 110, 188-195 (1992). This device consists of an inner core of pharmacologic agent surrounded by two coatings with different permeabilities.
- Drug diffuses through a small opening in one of these coatings achieving near-order release kinetics. It is implanted in the region of the pars plana through a 3.5-5.0 mm scleral incision. The implant must be removed and replaced every 6 months in the operating room as the drug becomes depleted. There is an approximately 25% complication rate from these procedures.
- the device is membrane diffusion drug delivery system that relies on EVA/PVA polymers to mediate release rate.
- EVA/PVA polymers to mediate release rate.
- Many agents cannot be effectively delivered from such a system because their permeation rate through the rate controlling material of the system is too small to produce a useful effect.
- Other agents cannot be satisfactorily delivered by diffusional devices because of a particular chemical characteristic of the agent. This includes salts, because of their ionic character, and unstable polar compounds that cannot be formulated into a composition suitable for storage and delivery from such systems.
- U.S. Pat. No. 5,098,443 describes a series of C-shaped rings that are inserted through incisions made in the eye wall or sutured around the globe of the eye. These rings may be formed from biodegradable polymers containing microparticles of drug. Alternatively, the implant may be in the form of a hollow flexible polymeric cocoon with the drug disposed therewithin for slow release by osmosis. No anchoring device is described.
- U.S. Pat. No. 5,466,233 describes a tack for intraocular drug delivery.
- This device has an end that is positioned in the vitreous cavity while the head remains external to the eye and abuts the scleral surface.
- the drug is contained in the vitreous end of the device and could be contained within a biodegradable or nonbiodegradable scaffold.
- the device may have a hollow core filled with a drug that could diffuse through the wall of the tack into the eye. This core could be refillable.
- the head of the tack may further have a suture hole for anchoring the sclera.
- the present invention provides a delivery device and methods of use. More particularly, the present invention relates to a sustained release delivery device that is minimally invasive and refillable.
- the delivery device of the present invention is particularly suitable for the delivery of therapeutic agents to the posterior chamber of the eye and other limited access regions.
- An exemplary embodiment of the delivery device includes a reservoir having an inlet port at its proximal end for insertion of the agent.
- a scleral hub, or similar fixation element may further be located near the proximal end for suturing or otherwise securing the device at a desired location.
- the agent inserted into the reservoir through the inlet port is delivered to a treatment area by a delivery mechanism located along the reservoir and/or at the distal end of the reservoir.
- the agent may be delivered through the reservoir by, for example, forming the reservoir of a material that is permeable to the agent or, for example, providing one or more apertures in the reservoir through which the agent may flow.
- the delivery mechanism is located at the distal end of the reservoir by, for example, forming the distal end of the reservoir of a semi-permeable membrane or providing one or more apertures in the distal end of the reservoir.
- the reservoir is preferably fabricated of a pliable material that allows the reservoir to be compressed for insertion through a small incision. Once inside the incision, the reservoir may automatically unfold and/or as agent is injected through the inlet port, the reservoir may unfold as it is filled with the agent.
- the drug delivery device may further include a hollow body or tube inside the reservoir, wherein the proximal end of the hollow body or tube forms the inlet port.
- hollow body or tube may provide structural rigidity that facilitates insertion of the device through a small incision.
- the reservoir covers at least a portion of the length of the hollow body or tube and is preferably pliable so that it may be folded, rolled and/or compressed about the hollow body or tube to enable insertion of the device through a small incision not much larger than the size of the hollow body or tube.
- At least one aperture in the hollow body or tube provides communication between the contents of the hollow body or tube and the reservoir such that, as the agent is inserted through the inlet port, it travels through the hollow body or tube, through the aperture(s) and into the reservoir. As the agent fills the reservoir, the reservoir unfolds.
- the distal end of the hollow body or tube extends outside the reservoir and forms a delivery port through which the agent is delivered to the patient.
- the therapeutic agent is delivered to the patient through the reservoir by, for example, forming the reservoir of a material that is permeable to the agent or, for example, providing one or more apertures in the reservoir through which agent may flow.
- a scleral hub, or similar fixation element may further be located near the proximal end of the hollow body or tube for suturing or otherwise securing the device at a desired location.
- Methods for the delivery of an agent involve delivery of agents to the eye to treat a variety of ocular conditions such as, for example, retinal detachment, vascular occlusions, proliferative retinopathy, diabetic retinopathy, inflammations such as uveitis, choroiditis and retinitis, degenerative disease, vascular diseases and various tumors including neoplasms.
- ocular conditions such as, for example, retinal detachment, vascular occlusions, proliferative retinopathy, diabetic retinopathy, inflammations such as uveitis, choroiditis and retinitis, degenerative disease, vascular diseases and various tumors including neoplasms.
- the methods comprise making a small incision in the eye to provide access to the treatment site.
- the delivery device is provided in an “empty” state, with the reservoir empty and preferably compressed tightly as shown in FIG. 1 a. Compressing the reservoir is desirable since it allows the delivery device to be passed through a small incision that requires few or no sutures for closure.
- the delivery device is then inserted through the incision distal end first until the scleral hub or fixation mechanism abuts the incision.
- the scleral hub or fixation mechanism may then be sutured or secured to the sclera to assist in maintaining the device at the treatment site. Once inside the incision, the reservoir may automatically unfold.
- the therapeutic agent is then injected into the device through the inlet port by use of a syringe or similar mechanism containing with the agent.
- the agent travels into the reservoir, thereby further unfolding the reservoir.
- the syringe may be disconnected from the inlet port and the inlet port closed.
- the agent is then delivered to the patient either through a delivery port or through the reservoir.
- the device may be refilled for further delivery of agent or removed.
- the reservoir is preferably empty and compressed, thereby allowing the device to be removed through a small incision that requires few or no sutures for closure.
- the device may be designed to deliver a desired dose of agent at a particular rate, for example, by providing various sized reservoirs, reservoirs with various permeabilities to the agent, delivery apertures or ports with smaller or larger diameters and delivery ports with rate controlling covers.
- the present delivery device and methods of use are minimally invasive.
- the delivery device has a small profile that allows it to be inserted through a small opening.
- Such an insertion procedure eliminates the risks associated with more invasive surgery, and, further, enables such procedures to take place in an office setting.
- the device can be removed from a small insertion site, requiring few or no sutures for scleral closure. This is a dramatic improvement over state of the art technologies which require surgery for both implantation and removal.
- the delivery device of the present invention is a refillable device easily filled and refilled by injection. This feature allows the physician to easily titrate dosage to the need of the individual patient. Additionally, a single device may be used with a wide range of agents, because the present device avoids implantation of the agent into the structure of the device during the manufacturing process.
- the present device lends itself to the delivery of agents that do not readily permeate through polymeric membranes, such as ionic drugs or proteins.
- FIG. 1A illustrates an empty delivery device in accordance with an embodiment of the present invention.
- FIG. 1B illustrates the delivery device of FIG. 1 a holding an agent.
- FIG. 2 depicts the final location of the device of FIGS. 1 a and 1 b within the eye.
- FIG. 3 depicts the final location of the device within the eye in accordance with another embodiment of the present invention.
- FIG. 4A illustrates an empty delivery device in accordance with another embodiment of the present invention.
- FIG. 4B illustrates the drug delivery device of FIG. 4 a holding an agent.
- FIG. 5 shows a cross-sectional schematic view of an eye illustrating one 10 technique of pulling back of the conjunctiva to provide access into the eye for insertion of the delivery device of the present invention.
- the delivery device 1 includes a reservoir 2 having a proximal end 3 and a distal end 4 . Located near the proximal end 3 of the reservoir 2 is an inlet port 5 for injection of a desired agent into the reservoir 1 . Agent injected through the inlet port 5 is delivered to the treatment area through delivery mechanism 6 .
- the delivery device 1 may further include a hollow body or tube 10 housed at least partially within the reservoir 2 .
- the hollow body or tube 10 has a proximal end 11 and a distal end 12 .
- the proximal end 11 of the hollow body or tube 10 extends outside the reservoir 2 , as shown in FIGS. 1-3 , and serves as the inlet port 5 through which the agent is injected into the device.
- the materials used in fabricating the reservoir 2 are not particularly limited, provided these materials are biocompatible and preferably insoluble in the body fluids and tissues that the device comes into contact with.
- the materials used in fabricating the reservoir 2 are pliable materials that allows the reservoir 2 to be folded, rolled and/or compressed for insertion through a small incision that requires few or no sutures for closure. Once inside the incision, the reservoir 2 may automatically unfold or unroll to some extent. Additionally, as agent is injected through the inlet port 5 into the reservoir 2 , the reservoir 2 may unfold or unroll and expand as it is filled with the agent.
- the reservoir 2 is in the form of a balloon and is fabricated of an elastic material.
- the agent As the agent is injected into the inlet port 5 , the agent passes into the expandable reservoir 2 or balloon, thereby inflating and expanding the reservoir 2 or balloon. Pressure of the elastic material against the agent within the reservoir 2 provides a driving force for delivery of agent through the delivery mechanism 6 .
- Suitable materials for use in forming an elastic reservoir are well known and may be readily determined by one of skill in the art. For example, some suitable include thin-walled nondistensible materials, such as PET, and more elastomeric materials, such as polyurethane.
- flow through the delivery mechanism 6 is primarily driven by diffusion and/or intraocular pressure force.
- delivery of the agent may be driven, a least in part, by the spring-like properties of the material forming the reservoir 2 .
- the delivery mechanism comprises at least a portion of the reservoir 2 .
- this may be accomplished by fabricating at least a portion of the reservoir 2 of a material that is permeable to the agent.
- Such materials may vary depending on the particular application and the agent to be delivered and may be readily determined by one of skill in the art.
- this may be accomplished by fabricating at least a portion of the reservoir 2 of a material that is permeable to the agent.
- Such materials may vary depending on the particular application and the agent to be delivered and may be readily determined by one of skill in the art.
- some suitable permeable materials may include polycarbonates, polyolefins, polyurethanes, copolymers of acrylonitrile, copolymers of polyvinyl chloride, polyamides, polysuiphones, polystyrenes, polyvinyl fluorides, polyvinyl alcohols, polyvinyl esters, polyvinyl butyrate, polyvinyl acetate, polyvinylidene chlorides, polyvinylidene fluorides, polyimides, polyisoprene, polyisobutylene, polybutadiene, polyethylene, polyethers, polytetrafluoroethylene, polychloroethers, polymethylmethacrylate, polybutylmethacrylate, polyvinyl acetate, nylons, cellulose, gelatin, silicone rubbers and porous rubbers.
- the particular material may be chosen to provide a particular rate of delivery of the agent, which may be readily determined by one of skill in the art.
- the rate of delivery of an agent may also be increased or decreased by varying the percentage of the reservoir 2 formed of the material permeable to the agent.
- the reservoir 2 may be fabricated of 50% or less permeable material.
- the reservoir 2 may be fabricated of 1%, 5%, 10%, 20%, 30%, 40% or 50% of permeable material.
- the reservoir may be fabricated of greater than 50% of permeable material.
- the reservoir 2 may be fabricated of 51%, 55%, 60%, 70%, 80%, 90% or 100% of permeable material.
- the delivery mechanism 6 comprises one or more apertures 7 in the reservoir 2 formed, for example, with a laser, hot wire, drilling device or similar mechanism.
- the one or more apertures 7 may be located along the length of the reservoir 2 and/or at the distal end 4 of the reservoir 2 .
- the number and size of the one or more apertures 7 may vary depending on the desired rate of delivery of the agent and may be readily determined by one of skill in the art.
- the distal end 12 of the hollow body or tube 10 may extend outside the reservoir 2 , as shown in FIGS. 1-3 , and may serve as the delivery mechanism 6 through which the agent is delivered to the treatment site.
- one or more apertures 13 are located through the wall of the hollow body or tube 10 to provide communication between the contents of the hollow body or tube 10 and the reservoir 2 .
- the device 1 is designed such that as the agent is injected into the delivery device 1 , all or a majority of the agent injected through the inlet port 5 passes through the hollow body or tube 10 into the reservoir 2 rather than passing directly out of the device through the distal end of the hollow body or tube 10 .
- This may be accomplished by, for example, providing one or more apertures 13 in wall of the hollow body or tube 10 that are larger than or that accommodate greater flow of agent than the delivery mechanism 6 .
- a valve (not shown) or similar mechanism may be located at the delivery mechanism 6 for closing off the delivery mechanism 6 during injection of the agent.
- the distal end 12 of the hollow body or tube 10 is designed to provide controlled delivery of agent from the device. This may be achieved by, for example, providing a distal end 12 with small holes and/or, for example, placing a covering or lining (not shown) over the distal end 12 , wherein the covering or lining has a particular porosity to the agent or wherein the covering or lining is fabricated of a diffusion or rate-limiting membrane, matrix material or similar material.
- the distal end 12 of the hollow body or tube 10 extends outside the reservoir 2
- the distal end 12 and the reservoir 2 form the delivery mechanism 6 .
- the distal end 12 may be designed as set out above to deliver the agent and, for example, the reservoir 2 may be fabricated of a permeable material or one or more apertures 7 may be formed in the reservoir 2 .
- distal end 12 of the hollow body or tube 10 extend outside the reservoir 2 , wherein the distal end 12 is closed off and does not serve as a delivery mechanism but, rather, the reservoir 2 serves as the delivery mechanism 6 by, for example, fabricating the reservoir 2 of a permeable material or forming one or more apertures 7 in the reservoir 2 .
- the distal end 12 of the hollow body or tube 10 may be contained within the reservoir 2 , as shown in FIGS. 4 a and 4 b .
- the delivery mechanism 6 may comprises at least a portion of the reservoir 2 by, for example, forming at least a portion of the reservoir 2 or the entire reservoir 2 of a material that is permeable to the agent, or one or more apertures 7 may be fabricated in the reservoir 2 as described above.
- the distal end 12 may have an opening through which the agent travels from the inlet port 5 into the reservoir 2 .
- At least one aperture 13 may alternatively or may also be located along the hollow body or tube 10 through which agent may travel from the inlet port 5 into the reservoir 2 .
- the hollow body or tube 10 is preferably rigid and provides structural support beneath the reservoir 2 for easier implantation of the device 1 through the incision.
- the hollow body or tube 10 may be formed of rigid materials including, for example, stainless steel, titanium, nitinol, polymers and other similar materials.
- the hollow body or tube 10 is preferably cylindrical in shape, with a circular cross-section.
- the shape of the hollow body or tube 10 is not limited and, for example, the hollow body or tube 10 may alternatively have, for example, square, rectangular, octagonal or other cross-sectional shapes.
- the reservoir 2 is bonded to the hollow body or tube 10 forming a fluid-tight seal that does not separate from the hollow body or tube 10 during use, thereby preventing leakage of agent out of the device between the hollow body or tube 10 and reservoir 2 .
- a fluid-tight seal that does not separate from the hollow body or tube 10 during use, thereby preventing leakage of agent out of the device between the hollow body or tube 10 and reservoir 2 .
- the inlet port 5 of the delivery device 1 is designed such that the needle of a syringe, or similar injection mechanism, may be inserted through the inlet port 5 and the agent housed within the syringe or injection mechanism may be injected through the inlet port 5 and into the reservoir 2 .
- the inlet port 5 preferably forms a snug seal about the needle of the syringe or injection mechanism to prevent leakage of the agent out of the inlet port around the syringe needle or injection mechanism and to provide sterile injection of agent into the delivery device 1 .
- fittings or collars (not shown), through which a syringe needle or injection mechanism may be inserted and which form a snug seal about the syringe needle or injection mechanism, may be mounted on the inlet port 5 .
- the needle of the syringe or the injection mechanism is removed from the inlet port 5 and the inlet port 5 sealed. This may be accomplished by providing a removable cover (not shown) on the inlet port 5 that may be removed for injection of the agent and replaced when the agent has been injected.
- the inlet port 5 is composed of an injectable self-sealing material through which the needle or injection mechanism may be inserted and which seals off automatically when the needle or injection mechanism is removed.
- Such materials are known and include, for example, silicone rubber, silicone elastomers and polyolefin.
- a fixation mechanism 8 such as, for example, a scleral hub, may further be located near the inlet port 5 to assist in stabilizing the device 1 near the delivery site.
- the delivery device 1 is inserted into the incision until the fixation mechanism 8 abuts the incision.
- the fixation mechanism 8 is in the form of extensions from the proximal end 11 of the hollow body or tube 10 . These extensions rest on the surface surrounding the incision, as shown in FIGS. 2-3 . These extensions may be of any shape, for example, circular, rectangular, triangular, etc.
- the extensions are shown as extending approximately perpendicularly from the hollow body of tube 10 , the extensions are not limited to such an arrangement and may, for example, be curved away from the device so as to conform to the curvature in the surface of the eye.
- the overall shape and size of the fixation mechanism 8 is not limited as long as irritation and damage to the surface of the eye or other area of the body that it is in contact with are minimized.
- the delivery device 1 may further include a tube 14 having a first end 16 and a second end 18 , for the delivery of therapeutic agent directly to a target site.
- the first end 16 of the tube 14 may be connected to the distal end 4 of the reservoir 2 or the distal end 12 of the hollow body or tube 10 and the second end 18 of the tube may be secured to or located proximal to the target site (e.g. the choroids and retinal pigment epithelial cells).
- the tube 14 may be sized as so as to limit delivery rate, to minimize trauma to the retina, and to minimize leaking of the agent.
- the tube 14 is preferably fabricated of a flexible material so that small movements of the delivery device 1 will not be translated to the retina, thereby minimizing the risk of retinal tearing, detachment and other damage.
- the agent may also be desirable to deliver the agent through both the reservoir 2 and the tube 14 .
- at least a portion of the reservoir 2 may be fabricated of a material permeable to the agent or the reservoir 2 may have one or more apertures 7 through which the agent may be delivered from the reservoir 2 as discussed above.
- the dimensions of the delivery device 1 will depend on the intended application of the device, and will be readily apparent to those having ordinary skill in the art.
- the device when the delivery device 1 is used to deliver therapeutic agents to the eye, the device is designed for insertion through a small incision, preferably ranging from about 0.25 mm to about 1 mm in diameter, more preferably less than 0.5 mm in diameter, thereby requiring few or no sutures for scleral closure at the conclusion of the procedure.
- the cross-section of the device 1 with the reservoir 2 compressed preferably ranges from about 0.25 mm to about 1 mm in diameter, and, more preferably, is no greater than 0.5 mm.
- the hollow body or tube 10 has diameter ranging from about 0.5 to about 1.0 mm, and the reservoir 2 may be compressed to the hollow body or tube 10 so as to provide an overall cross section no greater than 1.0 mm. If the hollow body or tube 10 is not tubular, the largest dimension of the cross section can be used to approximate the diameter for this purpose.
- the device 1 When used to deliver agents to the posterior chamber of the eye, the device 1 preferably has a length ranging from about 0.5 cm to about 1.5 cm such that when the fixation mechanism 8 is sutured or otherwise secured to the sclera in the region of the pars plana, the delivery mechanism 6 is positioned near the posterior chamber of the eye.
- the dimensions of the tube 14 will depend on the intended application of the device, and will be readily apparent to those having ordinary skill in the art.
- the tube 14 when used to deliver an agent to the choroids and retinal pigment epithelial cells of the eye, the tube 14 is preferably sized so as to limit delivery rate, to minimize trauma to the retina, and to minimize leaking of agent.
- the tube 14 preferably has a length ranging from about 1 cm to about 2.5 cm, an outer diameter less than about 0.1 mm, and an inner diameter ranging from about 0.001 mm to about 0.007 mm, and more preferably, from about 0.005 mm to about 0.001.
- the use of the delivery device 1 of the present invention can be further understood from the following discussion relating to a method for treating chronic diseases of the eye by sustained release of therapeutic agent to the eye and with reference to FIGS. 1-5 .
- the delivery device 1 is generally used by the following procedure: the delivery device 1 is prepared with the reservoir 2 empty and preferably compressed, as shown in FIGS. 1 a and 4 a. If a hollow body or tube 10 is included in the device, the reservoir 2 is preferably compressed about the hollow body or tube 10 as shown in FIG. 1 a, to provide a low profile that allows the delivery device 1 to be implanted and removed through a small access incision that requires few or no sutures for closure. If a tube 14 is used for direct delivery of the therapeutic agent to the target site, the first end 16 of the tube 14 is connected to the distal end 4 of the reservoir 2 or the distal end 12 of the hollow body or tube 10 .
- An incision is made to provide access to the treatment site.
- a sclerotomy is created for insertion of the delivery device 1 .
- Conventional techniques may be used for the creation of the sclerotomy. Such techniques require the dissection of the conjunctiva 44 and the creation of pars plana scleral incisions through the sclera 46 . As shown in FIG. 5 , the dissection of the conjunctiva 44 typically involves pulling back the conjunctiva 44 about the eye 42 so as to expose large areas of the sclera 46 and the clipping or securing of the conjunctiva 44 in that pulled back state (normal position of conjunctiva shown in phantom).
- the sclera 46 is not exposed only in the areas where the pars plana scleral incisions are to be made. Surgical instruments used in the procedure are then passed through these incisions. Thus, the incisions created for the procedure must be made large enough to accommodate the instruments required for the procedure.
- the creation of the sclerotomy may be accomplished by use of an alignment device and method, such as that described in U.S. Ser. No. 09/523,767 the teachings of which are incorporated herein by reference, that enables sutureless surgical methods and devices therefore.
- an alignment device and method such as that described in U.S. Ser. No. 09/523,767 the teachings of which are incorporated herein by reference, that enables sutureless surgical methods and devices therefore.
- such methods and devices do not require the use of sutures to seal the openings through which instruments are inserted.
- the alignment devices are inserted through the conjunctiva and sclera to form one or more entry apertures.
- the alignment devices are metal or polyimide cannulas through which the surgical instruments used in the procedure are inserted into the eye.
- the delivery device 1 is then inserted through the incision either by hand or using a variety of insertion devices, e.g. syringe-like devices, known to those of skill in the art.
- insertion devices e.g. syringe-like devices, known to those of skill in the art.
- microforceps or similar positioning mechanisms may be used to position the tube 14 at the treatment location.
- the fixation mechanism 8 may then be sutured or otherwise secured to the sclera to hold the delivery device 1 in place. If a cover is used to close the inlet port 5 , it is removed at this time, and, if used, a collar for providing a snug fit about the syringe or other injection mechanism is mounted on the inlet port 5 . The syringe or other injection mechanism is then connected to the inlet port 5 for injection of the agent into the delivery device 1 .
- the inlet port 5 is composed of an injectable self-sealing material through which the needle of a syringe or other injection mechanism may be inserted and which seals off automatically when the needle other injection mechanism is removed, the needle or other injection mechanism is simply inserted through the inlet port 5 and the agent injected. Following injection, the conjunctiva may be adjusted to cover the distal end of the device.
- some agents suitable for delivery to the eye may include, for example, antibiotics such as tetracycline, chlortetracycline, bacitracin, neomycin, polymyxin, gramicidin, cephalexin, oxytetracycline, chloramphenicol, rifampicin, ciprofloxacin, tobramycin, gentamycin, and erythromycin and penicillin; antifungals such as amphotericin B and miconazole; antibacterials such as sulfonamides, sulfadiazine, sulfacetamide, sulfam
- additives may further be included in the agent and, for example, some suitable additives may include water, saline, dextrose, carriers, preservatives, stabilizing agents, wetting agents, emulsifying agents or other similar materials.
- the delivery device 1 comprises a reservoir 2 having an inlet port 5 located near the proximal end 3 of the reservoir 2
- the agent injected through the inlet port 5 travels into the reservoir 2 .
- the reservoir 2 is fabricated of an elastic material, the reservoir 2 inflates/expands as it is filled.
- the needle or other injection mechanism is removed from the inlet port 5 and the inlet port 5 sealed.
- the agent in the reservoir 2 is then delivered gradually via the delivery mechanism 6 .
- tube 14 is included, the agent is delivered through the tube 14 and/or reservoir 2 .
- the delivery device 1 may be refilled for further delivery or removed if the required dose of agent has been delivered for treatment of the condition. If required, an aspirating device or similar mechanism (not shown) may be used to further compress the reservoir 2 , thereby enabling removal of the delivery device 1 through a small incision that requires few or no sutures are required for sclera' closure.
- the agent injected through the inlet port 5 travels through the hollow body or tube 10 and into the reservoir 2 through either the one or more apertures 13 in the hollow body or tube 10 or the distal end 12 of the hollow body or tube.
- the needle or other injection mechanism is then removed from the inlet port 5 and the inlet port 5 sealed.
- the agent in the reservoir 2 is then delivered to the treatment area gradually through the reservoir 2 and/or through the distal end 12 of the hollow body or tube 10 .
- tube 14 is included, the agent is delivered through the tube 14 and/or reservoir 2 . Once the therapeutic agent had been delivered to the treatment area, the delivery device 1 may be refilled for further delivery or removed if the required dose of agent has been delivered for treatment of the condition.
- an aspirating device or similar mechanism may be used to further compress the reservoir 2 about the hollow body or tube 10 , thereby enabling removal of the delivery device 1 through a small incision that requires few or no sutures are required for scleral closure.
- the invention is not be limited to ocular applications, and is particularly useful in other limited access regions such as the inner ear.
- kits that comprise one or more device of the invention, preferably packaged in sterile condition.
- Kits of the invention also may include, for example, one or more tubes 14 , one or more reservoirs 2 , means for suturing or securing the fixation mechanism 8 to the sclera, etc. for use with the device, preferably packaged in sterile condition, and/or written instructions for use of the device and other components of the kit.
Landscapes
- Health & Medical Sciences (AREA)
- Engineering & Computer Science (AREA)
- Heart & Thoracic Surgery (AREA)
- Public Health (AREA)
- Veterinary Medicine (AREA)
- Biomedical Technology (AREA)
- Life Sciences & Earth Sciences (AREA)
- Animal Behavior & Ethology (AREA)
- General Health & Medical Sciences (AREA)
- Vascular Medicine (AREA)
- Ophthalmology & Optometry (AREA)
- Hematology (AREA)
- Anesthesiology (AREA)
- Medicinal Chemistry (AREA)
- Chemical & Material Sciences (AREA)
- Bioinformatics & Cheminformatics (AREA)
- Pulmonology (AREA)
- Prostheses (AREA)
- Media Introduction/Drainage Providing Device (AREA)
- Infusion, Injection, And Reservoir Apparatuses (AREA)
- Materials For Medical Uses (AREA)
- Pharmaceuticals Containing Other Organic And Inorganic Compounds (AREA)
- Medicinal Preparation (AREA)
Abstract
A delivery device that allows for the sustained release of an agent, particularly useful for the sustained release of a therapeutic agent to limited access regions, such as the posterior chamber of the eye and inner ear. The delivery device is minimally invasive, refillable and may be easily fixed to the treatment area. The delivery device includes a hollow body with an inlet port at its proximal end for insertion of the agent, a reservoir for holding the agent and a delivery mechanism for the sustained delivery of the agent from the reservoir to the patient.
Description
- The present application is a Continuation of co-pending U.S. patent application Ser. No. 15/060,532, filed Mar. 3, 2016, which is a continuation of U.S. patent application Ser. No. 14/268,723, filed May 2, 2014, now abandoned, which is a continuation of U.S. patent application Ser. No. 13/942,610, filed Jul. 15, 2013, now U.S. Pat. No. 9,180,046, issued Nov. 10, 2015, which is a continuation of U.S. patent application Ser. No. 12/979,185, filed Dec. 27, 2010, now U.S. Pat. No. 8,486,052, issued Jul. 16, 2013, which is a Divisional of U.S. patent application Ser. No. 10/171,406, filed Jun. 12, 2002, now U.S. Pat. No. 7,883,717, issued Feb. 8, 2011, which claims the benefit of U.S. Provisional Application Ser. No. 60/297,499, filed Jun. 12, 2001. The priority of the filing dates is hereby claimed, and the disclosures of each of the above-mentioned patent applications are hereby incorporated by reference in their entirety.
- The present invention relates to improved delivery devices and methods of use. More particularly, the present invention relates to minimally invasive, refillable, sustained release delivery devices particularly suitable for the delivery of therapeutic agents to limited access regions, such as the posterior chamber of the eye.
- The delivery of drugs to the eye presents many challenges. The ocular absorption of systemically administered pharmacologic agents is limited by the blood ocular barrier, namely the tight junctions of the retinal pigment epithelium and vascular endothelial cells. High systemic doses can penetrate this blood ocular barrier in relatively small amounts, but expose the patient to the risk of systemic toxicity. Topical delivery of drugs often results in limited ocular absorption due to the complex hydrophobic/hydrophilic properties of the cornea and sclera. Additionally, topical agents are mechanically removed by the blink mechanism such that only approximately 15% of a single drop is absorbed. Diffusion of topically administered drugs to the posterior chamber occurs, but often at sub-therapeutic levels. Intravitreal injection of drugs is an effective means of delivering a drug to the posterior segment in high concentrations. However, these repeated intraocular injections carry the risk of infection, hemorrhage and retinal detachment. Patients also find this procedure somewhat difficult to endure.
- Local sustained delivery of therapeutics to the posterior chamber is critical in managing several chronic diseases of the eye. To address this need, several drug delivery devices have been developed for intraocular insertion into the vitreous region of the eye.
- U.S. Pat. No. 4,300,557, for example, describes an intraocular implant in the form of a silicone capsule which can be filled with a drug to be delivered. The capsule is inserted in the vitreous region of the eye by making an incision in the eye, inserting the capsule and closing the incision. The capsule remains in place for a period of time and may be removed by making a second surgical incision into the eye and retrieving the device. The capsule has an attached tube which passes through the surface of the eye and extends outward from the eye useful for the subsequent injection of a drug. While in the vitreous, the device is not anchored and may move about freely.
- U.S. Pat. No. 5,378,475 (often referred to as Vitrasert) describes a device 15 which has been developed for insertion in the vitreous region of the eye, and is described in T. J. Smith et al., Sustained-Release Ganciclovir, Arch. Ophthalmol, 110, 255-258 (1992) and G. E. Sanborn, et al., Sustained-Release Ganciclovir Therapy for Treatment of Cytomegalovirus Retinitis. Use of an Intravitreal Device, Arch. Ophthalmol, 110, 188-195 (1992). This device consists of an inner core of pharmacologic agent surrounded by two coatings with different permeabilities. Drug diffuses through a small opening in one of these coatings achieving near-order release kinetics. It is implanted in the region of the pars plana through a 3.5-5.0 mm scleral incision. The implant must be removed and replaced every 6 months in the operating room as the drug becomes depleted. There is an approximately 25% complication rate from these procedures. The device is membrane diffusion drug delivery system that relies on EVA/PVA polymers to mediate release rate. Thus, many agents cannot be effectively delivered from such a system because their permeation rate through the rate controlling material of the system is too small to produce a useful effect. Other agents cannot be satisfactorily delivered by diffusional devices because of a particular chemical characteristic of the agent. This includes salts, because of their ionic character, and unstable polar compounds that cannot be formulated into a composition suitable for storage and delivery from such systems.
- U.S. Pat. No. 5,098,443 describes a series of C-shaped rings that are inserted through incisions made in the eye wall or sutured around the globe of the eye. These rings may be formed from biodegradable polymers containing microparticles of drug. Alternatively, the implant may be in the form of a hollow flexible polymeric cocoon with the drug disposed therewithin for slow release by osmosis. No anchoring device is described.
- U.S. Pat. No. 5,466,233 describes a tack for intraocular drug delivery. This device has an end that is positioned in the vitreous cavity while the head remains external to the eye and abuts the scleral surface. The drug is contained in the vitreous end of the device and could be contained within a biodegradable or nonbiodegradable scaffold. Alternatively, the device may have a hollow core filled with a drug that could diffuse through the wall of the tack into the eye. This core could be refillable. The head of the tack may further have a suture hole for anchoring the sclera.
- While intraocular devices exist which allow delivery of therapeutic agents to the eye, a need still remains for a device which accomplishes controlled, sustained delivery to the posterior chamber, is implantable and removable without requiring long full thickness scleral incisions, does not cause undue patient irritation or discomfort, is stable within the vitreous region of the eye, is refillable and dose titratable, and is capable of delivering a wide range of small molecule, gene and protein therapeutics.
- The present invention provides a delivery device and methods of use. More particularly, the present invention relates to a sustained release delivery device that is minimally invasive and refillable. The delivery device of the present invention is particularly suitable for the delivery of therapeutic agents to the posterior chamber of the eye and other limited access regions.
- An exemplary embodiment of the delivery device includes a reservoir having an inlet port at its proximal end for insertion of the agent. A scleral hub, or similar fixation element, may further be located near the proximal end for suturing or otherwise securing the device at a desired location. The agent inserted into the reservoir through the inlet port is delivered to a treatment area by a delivery mechanism located along the reservoir and/or at the distal end of the reservoir. For example, in one embodiment, the agent may be delivered through the reservoir by, for example, forming the reservoir of a material that is permeable to the agent or, for example, providing one or more apertures in the reservoir through which the agent may flow. In another embodiment, the delivery mechanism is located at the distal end of the reservoir by, for example, forming the distal end of the reservoir of a semi-permeable membrane or providing one or more apertures in the distal end of the reservoir. The reservoir is preferably fabricated of a pliable material that allows the reservoir to be compressed for insertion through a small incision. Once inside the incision, the reservoir may automatically unfold and/or as agent is injected through the inlet port, the reservoir may unfold as it is filled with the agent.
- The drug delivery device may further include a hollow body or tube inside the reservoir, wherein the proximal end of the hollow body or tube forms the inlet port. In this embodiment, hollow body or tube may provide structural rigidity that facilitates insertion of the device through a small incision. The reservoir covers at least a portion of the length of the hollow body or tube and is preferably pliable so that it may be folded, rolled and/or compressed about the hollow body or tube to enable insertion of the device through a small incision not much larger than the size of the hollow body or tube. At least one aperture in the hollow body or tube provides communication between the contents of the hollow body or tube and the reservoir such that, as the agent is inserted through the inlet port, it travels through the hollow body or tube, through the aperture(s) and into the reservoir. As the agent fills the reservoir, the reservoir unfolds. In one embodiment, the distal end of the hollow body or tube extends outside the reservoir and forms a delivery port through which the agent is delivered to the patient. In another embodiment, the therapeutic agent is delivered to the patient through the reservoir by, for example, forming the reservoir of a material that is permeable to the agent or, for example, providing one or more apertures in the reservoir through which agent may flow. A scleral hub, or similar fixation element, may further be located near the proximal end of the hollow body or tube for suturing or otherwise securing the device at a desired location.
- Methods for the delivery of an agent are also disclosed. In particular, the methods involve delivery of agents to the eye to treat a variety of ocular conditions such as, for example, retinal detachment, vascular occlusions, proliferative retinopathy, diabetic retinopathy, inflammations such as uveitis, choroiditis and retinitis, degenerative disease, vascular diseases and various tumors including neoplasms.
- The methods comprise making a small incision in the eye to provide access to the treatment site. The delivery device is provided in an “empty” state, with the reservoir empty and preferably compressed tightly as shown in
FIG. 1 a. Compressing the reservoir is desirable since it allows the delivery device to be passed through a small incision that requires few or no sutures for closure. The delivery device is then inserted through the incision distal end first until the scleral hub or fixation mechanism abuts the incision. The scleral hub or fixation mechanism may then be sutured or secured to the sclera to assist in maintaining the device at the treatment site. Once inside the incision, the reservoir may automatically unfold. The therapeutic agent is then injected into the device through the inlet port by use of a syringe or similar mechanism containing with the agent. The agent travels into the reservoir, thereby further unfolding the reservoir. Once reservoir is filled to a desired level, the syringe may be disconnected from the inlet port and the inlet port closed. The agent is then delivered to the patient either through a delivery port or through the reservoir. After delivery of the contents of the reservoir to the patient, the device may be refilled for further delivery of agent or removed. At the time of removal, the reservoir is preferably empty and compressed, thereby allowing the device to be removed through a small incision that requires few or no sutures for closure. - Depending on the particular application, the device may be designed to deliver a desired dose of agent at a particular rate, for example, by providing various sized reservoirs, reservoirs with various permeabilities to the agent, delivery apertures or ports with smaller or larger diameters and delivery ports with rate controlling covers.
- The present delivery device and methods of use are minimally invasive. In particular, the delivery device has a small profile that allows it to be inserted through a small opening. Such an insertion procedure eliminates the risks associated with more invasive surgery, and, further, enables such procedures to take place in an office setting. Also, the device can be removed from a small insertion site, requiring few or no sutures for scleral closure. This is a dramatic improvement over state of the art technologies which require surgery for both implantation and removal.
- Further, while many existing devices for ocular delivery incorporate the therapeutic agent into the structure of the implant for release via diffusion or bioerosion of the carrier, the delivery device of the present invention is a refillable device easily filled and refilled by injection. This feature allows the physician to easily titrate dosage to the need of the individual patient. Additionally, a single device may be used with a wide range of agents, because the present device avoids implantation of the agent into the structure of the device during the manufacturing process.
- Still further, because release of the agent using the present delivery device is not necessarily membrane diffusion regulated, the present device lends itself to the delivery of agents that do not readily permeate through polymeric membranes, such as ionic drugs or proteins.
- Other aspects and embodiments of the invention are discussed infra.
-
FIG. 1A illustrates an empty delivery device in accordance with an embodiment of the present invention. -
FIG. 1B illustrates the delivery device ofFIG. 1a holding an agent. -
FIG. 2 depicts the final location of the device ofFIGS. 1a and 1b within the eye. -
FIG. 3 depicts the final location of the device within the eye in accordance with another embodiment of the present invention. -
FIG. 4A illustrates an empty delivery device in accordance with another embodiment of the present invention. -
FIG. 4B illustrates the drug delivery device ofFIG. 4a holding an agent. -
FIG. 5 shows a cross-sectional schematic view of an eye illustrating one 10 technique of pulling back of the conjunctiva to provide access into the eye for insertion of the delivery device of the present invention. - Referring now to the various figures of the drawing, wherein like reference characters refer to like parts, there is shown various views of a
delivery device 1, in accordance with the invention. - As shown in
FIGS. 1-3 , thedelivery device 1 includes areservoir 2 having aproximal end 3 and adistal end 4. Located near theproximal end 3 of thereservoir 2 is aninlet port 5 for injection of a desired agent into thereservoir 1. Agent injected through theinlet port 5 is delivered to the treatment area throughdelivery mechanism 6. - The
delivery device 1 may further include a hollow body ortube 10 housed at least partially within thereservoir 2. The hollow body ortube 10 has aproximal end 11 and adistal end 12. Preferably, theproximal end 11 of the hollow body ortube 10 extends outside thereservoir 2, as shown inFIGS. 1-3 , and serves as theinlet port 5 through which the agent is injected into the device. - The materials used in fabricating the
reservoir 2 are not particularly limited, provided these materials are biocompatible and preferably insoluble in the body fluids and tissues that the device comes into contact with. In some embodiments, it is further preferred that the materials used in fabricating thereservoir 2 are pliable materials that allows thereservoir 2 to be folded, rolled and/or compressed for insertion through a small incision that requires few or no sutures for closure. Once inside the incision, thereservoir 2 may automatically unfold or unroll to some extent. Additionally, as agent is injected through theinlet port 5 into thereservoir 2, thereservoir 2 may unfold or unroll and expand as it is filled with the agent. - In one preferred embodiment, the
reservoir 2 is in the form of a balloon and is fabricated of an elastic material. As the agent is injected into theinlet port 5, the agent passes into theexpandable reservoir 2 or balloon, thereby inflating and expanding thereservoir 2 or balloon. Pressure of the elastic material against the agent within thereservoir 2 provides a driving force for delivery of agent through thedelivery mechanism 6. Suitable materials for use in forming an elastic reservoir are well known and may be readily determined by one of skill in the art. For example, some suitable include thin-walled nondistensible materials, such as PET, and more elastomeric materials, such as polyurethane. When thereservoir 2 is fabricated of a material such as PET, flow through thedelivery mechanism 6 is primarily driven by diffusion and/or intraocular pressure force. When thereservoir 2 is fabricated of a material such as polyurethane, delivery of the agent may be driven, a least in part, by the spring-like properties of the material forming thereservoir 2. - In one embodiment, the delivery mechanism comprises at least a portion of the
reservoir 2. For example, this may be accomplished by fabricating at least a portion of thereservoir 2 of a material that is permeable to the agent. Such materials may vary depending on the particular application and the agent to be delivered and may be readily determined by one of skill in the art. For example, this may be accomplished by fabricating at least a portion of thereservoir 2 of a material that is permeable to the agent. Such materials may vary depending on the particular application and the agent to be delivered and may be readily determined by one of skill in the art. By way of example, some suitable permeable materials may include polycarbonates, polyolefins, polyurethanes, copolymers of acrylonitrile, copolymers of polyvinyl chloride, polyamides, polysuiphones, polystyrenes, polyvinyl fluorides, polyvinyl alcohols, polyvinyl esters, polyvinyl butyrate, polyvinyl acetate, polyvinylidene chlorides, polyvinylidene fluorides, polyimides, polyisoprene, polyisobutylene, polybutadiene, polyethylene, polyethers, polytetrafluoroethylene, polychloroethers, polymethylmethacrylate, polybutylmethacrylate, polyvinyl acetate, nylons, cellulose, gelatin, silicone rubbers and porous rubbers. - The particular material may be chosen to provide a particular rate of delivery of the agent, which may be readily determined by one of skill in the art. The rate of delivery of an agent may also be increased or decreased by varying the percentage of the
reservoir 2 formed of the material permeable to the agent. Preferably, to provide a slower rate of delivery, thereservoir 2 may be fabricated of 50% or less permeable material. For example, thereservoir 2 may be fabricated of 1%, 5%, 10%, 20%, 30%, 40% or 50% of permeable material. For a faster rate of delivery, the reservoir may be fabricated of greater than 50% of permeable material. For example, thereservoir 2 may be fabricated of 51%, 55%, 60%, 70%, 80%, 90% or 100% of permeable material. - In another embodiment, for example, as shown in
FIG. 4b , thedelivery mechanism 6 comprises one ormore apertures 7 in thereservoir 2 formed, for example, with a laser, hot wire, drilling device or similar mechanism. The one ormore apertures 7 may be located along the length of thereservoir 2 and/or at thedistal end 4 of thereservoir 2. The number and size of the one ormore apertures 7 may vary depending on the desired rate of delivery of the agent and may be readily determined by one of skill in the art. - When the
delivery device 1 includes a hollow body ortube 10, thedistal end 12 of the hollow body ortube 10 may extend outside thereservoir 2, as shown inFIGS. 1-3 , and may serve as thedelivery mechanism 6 through which the agent is delivered to the treatment site. In this embodiment, one ormore apertures 13 are located through the wall of the hollow body ortube 10 to provide communication between the contents of the hollow body ortube 10 and thereservoir 2. Thus, as the agent is injected through theproximal end 11 of the hollow body ortube 10, which forms theinlet port 5, the agent flows through the hollow body ortube 10 and into thereservoir 2 through the one ormore apertures 13 in the wall of the hollow body ortube 10. Preferably, thedevice 1 is designed such that as the agent is injected into thedelivery device 1, all or a majority of the agent injected through theinlet port 5 passes through the hollow body ortube 10 into thereservoir 2 rather than passing directly out of the device through the distal end of the hollow body ortube 10. This may be accomplished by, for example, providing one ormore apertures 13 in wall of the hollow body ortube 10 that are larger than or that accommodate greater flow of agent than thedelivery mechanism 6. Alternatively, a valve (not shown) or similar mechanism may be located at thedelivery mechanism 6 for closing off thedelivery mechanism 6 during injection of the agent. - In a preferred embodiment, the
distal end 12 of the hollow body ortube 10 is designed to provide controlled delivery of agent from the device. This may be achieved by, for example, providing adistal end 12 with small holes and/or, for example, placing a covering or lining (not shown) over thedistal end 12, wherein the covering or lining has a particular porosity to the agent or wherein the covering or lining is fabricated of a diffusion or rate-limiting membrane, matrix material or similar material. - In another embodiment, wherein the
distal end 12 of the hollow body ortube 10 extends outside thereservoir 2, it is also possible to design the device such that both thedistal end 12 and thereservoir 2 form thedelivery mechanism 6. Thus, for example, thedistal end 12 may be designed as set out above to deliver the agent and, for example, thereservoir 2 may be fabricated of a permeable material or one ormore apertures 7 may be formed in thereservoir 2. Still further, it is possible to have thedistal end 12 of the hollow body ortube 10 extend outside thereservoir 2, wherein thedistal end 12 is closed off and does not serve as a delivery mechanism but, rather, thereservoir 2 serves as thedelivery mechanism 6 by, for example, fabricating thereservoir 2 of a permeable material or forming one ormore apertures 7 in thereservoir 2. - In another embodiment wherein the
delivery device 1 includes a hollow body ortube 10, thedistal end 12 of the hollow body ortube 10 may be contained within thereservoir 2, as shown inFIGS. 4a and 4b . In this embodiment, thedelivery mechanism 6 may comprises at least a portion of thereservoir 2 by, for example, forming at least a portion of thereservoir 2 or theentire reservoir 2 of a material that is permeable to the agent, or one ormore apertures 7 may be fabricated in thereservoir 2 as described above. In this embodiment, thedistal end 12 may have an opening through which the agent travels from theinlet port 5 into thereservoir 2. At least oneaperture 13 may alternatively or may also be located along the hollow body ortube 10 through which agent may travel from theinlet port 5 into thereservoir 2. - The hollow body or
tube 10 is preferably rigid and provides structural support beneath thereservoir 2 for easier implantation of thedevice 1 through the incision. As such, the hollow body ortube 10 may be formed of rigid materials including, for example, stainless steel, titanium, nitinol, polymers and other similar materials. As shown inFIGS. 1-4 b, the hollow body ortube 10 is preferably cylindrical in shape, with a circular cross-section. However, the shape of the hollow body ortube 10 is not limited and, for example, the hollow body ortube 10 may alternatively have, for example, square, rectangular, octagonal or other cross-sectional shapes. - The
reservoir 2 is bonded to the hollow body ortube 10 forming a fluid-tight seal that does not separate from the hollow body ortube 10 during use, thereby preventing leakage of agent out of the device between the hollow body ortube 10 andreservoir 2. Thus may be accomplished by using a variety of adhesives and epoxies. - The
inlet port 5 of thedelivery device 1 is designed such that the needle of a syringe, or similar injection mechanism, may be inserted through theinlet port 5 and the agent housed within the syringe or injection mechanism may be injected through theinlet port 5 and into thereservoir 2. Theinlet port 5 preferably forms a snug seal about the needle of the syringe or injection mechanism to prevent leakage of the agent out of the inlet port around the syringe needle or injection mechanism and to provide sterile injection of agent into thedelivery device 1. If desired, fittings or collars (not shown), through which a syringe needle or injection mechanism may be inserted and which form a snug seal about the syringe needle or injection mechanism, may be mounted on theinlet port 5. - Upon injection of the agent into the
drug delivery device 1, the needle of the syringe or the injection mechanism is removed from theinlet port 5 and theinlet port 5 sealed. This may be accomplished by providing a removable cover (not shown) on theinlet port 5 that may be removed for injection of the agent and replaced when the agent has been injected. In a preferred embodiment, theinlet port 5 is composed of an injectable self-sealing material through which the needle or injection mechanism may be inserted and which seals off automatically when the needle or injection mechanism is removed. Such materials are known and include, for example, silicone rubber, silicone elastomers and polyolefin. - As shown in
FIGS. 1-4 b, afixation mechanism 8, such as, for example, a scleral hub, may further be located near theinlet port 5 to assist in stabilizing thedevice 1 near the delivery site. Preferably, thedelivery device 1 is inserted into the incision until thefixation mechanism 8 abuts the incision. In one embodiment, as shown inFIGS. 1-4 b, thefixation mechanism 8 is in the form of extensions from theproximal end 11 of the hollow body ortube 10. These extensions rest on the surface surrounding the incision, as shown inFIGS. 2-3 . These extensions may be of any shape, for example, circular, rectangular, triangular, etc. and are sized to provide a surface on which the device I stably rests and to provide a portion that may be sutured or otherwise secured to the surface surrounding the incision. While the extensions are shown as extending approximately perpendicularly from the hollow body oftube 10, the extensions are not limited to such an arrangement and may, for example, be curved away from the device so as to conform to the curvature in the surface of the eye. The overall shape and size of thefixation mechanism 8 is not limited as long as irritation and damage to the surface of the eye or other area of the body that it is in contact with are minimized. - As shown in
FIG. 3 , thedelivery device 1 may further include atube 14 having afirst end 16 and asecond end 18, for the delivery of therapeutic agent directly to a target site. For example, thefirst end 16 of thetube 14 may be connected to thedistal end 4 of thereservoir 2 or thedistal end 12 of the hollow body ortube 10 and thesecond end 18 of the tube may be secured to or located proximal to the target site (e.g. the choroids and retinal pigment epithelial cells). Thetube 14 may be sized as so as to limit delivery rate, to minimize trauma to the retina, and to minimize leaking of the agent. Thetube 14 is preferably fabricated of a flexible material so that small movements of thedelivery device 1 will not be translated to the retina, thereby minimizing the risk of retinal tearing, detachment and other damage. - In some embodiments, it may also be desirable to deliver the agent through both the
reservoir 2 and thetube 14. In such embodiments, for example, in addition to atube 14 extending from thedistal end 4 of thereservoir 2 or thedistal end 12 of the hollow body ortube 10, at least a portion of thereservoir 2 may be fabricated of a material permeable to the agent or thereservoir 2 may have one ormore apertures 7 through which the agent may be delivered from thereservoir 2 as discussed above. - The dimensions of the
delivery device 1 will depend on the intended application of the device, and will be readily apparent to those having ordinary skill in the art. By way of example, when thedelivery device 1 is used to deliver therapeutic agents to the eye, the device is designed for insertion through a small incision, preferably ranging from about 0.25 mm to about 1 mm in diameter, more preferably less than 0.5 mm in diameter, thereby requiring few or no sutures for scleral closure at the conclusion of the procedure. As such, the cross-section of thedevice 1 with thereservoir 2 compressed preferably ranges from about 0.25 mm to about 1 mm in diameter, and, more preferably, is no greater than 0.5 mm. Preferably, the hollow body ortube 10 has diameter ranging from about 0.5 to about 1.0 mm, and thereservoir 2 may be compressed to the hollow body ortube 10 so as to provide an overall cross section no greater than 1.0 mm. If the hollow body ortube 10 is not tubular, the largest dimension of the cross section can be used to approximate the diameter for this purpose. When used to deliver agents to the posterior chamber of the eye, thedevice 1 preferably has a length ranging from about 0.5 cm to about 1.5 cm such that when thefixation mechanism 8 is sutured or otherwise secured to the sclera in the region of the pars plana, thedelivery mechanism 6 is positioned near the posterior chamber of the eye. - When included in the
device 1, the dimensions of thetube 14 will depend on the intended application of the device, and will be readily apparent to those having ordinary skill in the art. By way of example, when used to deliver an agent to the choroids and retinal pigment epithelial cells of the eye, thetube 14 is preferably sized so as to limit delivery rate, to minimize trauma to the retina, and to minimize leaking of agent. As such, thetube 14 preferably has a length ranging from about 1 cm to about 2.5 cm, an outer diameter less than about 0.1 mm, and an inner diameter ranging from about 0.001 mm to about 0.007 mm, and more preferably, from about 0.005 mm to about 0.001. - The use of the
delivery device 1 of the present invention can be further understood from the following discussion relating to a method for treating chronic diseases of the eye by sustained release of therapeutic agent to the eye and with reference toFIGS. 1-5 . - The
delivery device 1 is generally used by the following procedure: thedelivery device 1 is prepared with thereservoir 2 empty and preferably compressed, as shown inFIGS. 1a and 4 a. If a hollow body ortube 10 is included in the device, thereservoir 2 is preferably compressed about the hollow body ortube 10 as shown inFIG. 1 a, to provide a low profile that allows thedelivery device 1 to be implanted and removed through a small access incision that requires few or no sutures for closure. If atube 14 is used for direct delivery of the therapeutic agent to the target site, thefirst end 16 of thetube 14 is connected to thedistal end 4 of thereservoir 2 or thedistal end 12 of the hollow body ortube 10. - An incision is made to provide access to the treatment site. For example, when used to deliver therapeutic agent to the posterior chamber of the eye, a sclerotomy is created for insertion of the
delivery device 1. Conventional techniques may be used for the creation of the sclerotomy. Such techniques require the dissection of theconjunctiva 44 and the creation of pars plana scleral incisions through thesclera 46. As shown inFIG. 5 , the dissection of theconjunctiva 44 typically involves pulling back theconjunctiva 44 about theeye 42 so as to expose large areas of thesclera 46 and the clipping or securing of theconjunctiva 44 in that pulled back state (normal position of conjunctiva shown in phantom). In other words, thesclera 46 is not exposed only in the areas where the pars plana scleral incisions are to be made. Surgical instruments used in the procedure are then passed through these incisions. Thus, the incisions created for the procedure must be made large enough to accommodate the instruments required for the procedure. - Alternatively, the creation of the sclerotomy may be accomplished by use of an alignment device and method, such as that described in U.S. Ser. No. 09/523,767 the teachings of which are incorporated herein by reference, that enables sutureless surgical methods and devices therefore. In particular, such methods and devices do not require the use of sutures to seal the openings through which instruments are inserted. The alignment devices are inserted through the conjunctiva and sclera to form one or more entry apertures. Preferably, the alignment devices are metal or polyimide cannulas through which the surgical instruments used in the procedure are inserted into the eye.
- The
delivery device 1 is then inserted through the incision either by hand or using a variety of insertion devices, e.g. syringe-like devices, known to those of skill in the art. Once safely inside the eye, if thetube 14 is utilized in the application, microforceps or similar positioning mechanisms may be used to position thetube 14 at the treatment location. - The
fixation mechanism 8 may then be sutured or otherwise secured to the sclera to hold thedelivery device 1 in place. If a cover is used to close theinlet port 5, it is removed at this time, and, if used, a collar for providing a snug fit about the syringe or other injection mechanism is mounted on theinlet port 5. The syringe or other injection mechanism is then connected to theinlet port 5 for injection of the agent into thedelivery device 1. If theinlet port 5 is composed of an injectable self-sealing material through which the needle of a syringe or other injection mechanism may be inserted and which seals off automatically when the needle other injection mechanism is removed, the needle or other injection mechanism is simply inserted through theinlet port 5 and the agent injected. Following injection, the conjunctiva may be adjusted to cover the distal end of the device. - When the device is used to deliver agents to the eye for the treatment of a variety of ocular conditions such as, for example, retinal detachment, occlusions, proliferative retinopathy, diabetic retinopathy, inflammations such as uveitis, choroiditis and retinitis, degenerative disease, vascular diseases and various tumors including neoplasms, some agents suitable for delivery to the eye may include, for example, antibiotics such as tetracycline, chlortetracycline, bacitracin, neomycin, polymyxin, gramicidin, cephalexin, oxytetracycline, chloramphenicol, rifampicin, ciprofloxacin, tobramycin, gentamycin, and erythromycin and penicillin; antifungals such as amphotericin B and miconazole; antibacterials such as sulfonamides, sulfadiazine, sulfacetamide, sulfamethizole and sulfisoxazole, nitrofurazone and sodium propionate; antivirals, such as idoxuridine trifluorotymidine, acyclovir, ganciclovir and interferon; antibacterial agents such as nitrofurazone and sodium propionate; antiallergenics such as sodium cromoglycate, antazoline, methapyriline, chlorpheniramine, cetirizine, pyrilamine and prophenpyridamine; anti-inflammatories such as hydrocortisone, hydrocortisone acetate, dexamethasone 21-phosphate, fluocinolone, medrysone, methylprednisolone, prednisolone 21-phosphate, prednisolone acetate, fluoromethalone, betamethasone and triamcinolone; non-steroidal anti-inflammatories such as salicylate, indomethacin, ibuprofen, diclofenac, flurbiprofen and piroxicam; decongestants such as phenylephrine, naphazoline and tetrahydrozoline; decongestants such as phenylephrine, naphazoline, and tetrahydrazoline; miotics and anti-cholinesterase such as pilocarpine, salicylate, carbachol, acetylcholine chloride, physostigmine, eserine, diisopropyl fluorophosphate, phospholine iodine, and demecarium bromide; mydriatics such as atropine sulfate, cyclopentolate, homatropine, scopolamine, tropicamide, eucatropine, and hydroxyamphetamine; sympathomimetics such as epinephrine; antineoplastics such as carmustine, cisplatin and fluorouracil; immunological drugs such as vaccines and immune stimulants; hormonal agents such as estrogens, estradiol, progestational, progesterone, insulin, calcitonin, parathyroid hormone and peptide and vasopressin hypothalamus releasing factor; beta adrenergic blockers such as timolol maleate, levobunolol HCI and betaxolol HCI; growth factors such as epidermal growth factor, fibroblast growth factor, platelet derived growth factor, transforming growth factor beta, somatotropin and fibronectin; carbonic anhydrase inhibitors such as dichlorophenamide, acetazolamide and methazolamide; inhibitors of angiogenesis such as angiostatin, anecortave acetate, thrombospondin, and anti-VEGF antibody; and other therapeutic agents such as prostaglandins, antiprostaglandins and prostaglandin precursors.
- In some applications, additives may further be included in the agent and, for example, some suitable additives may include water, saline, dextrose, carriers, preservatives, stabilizing agents, wetting agents, emulsifying agents or other similar materials.
- In one embodiment, wherein the
delivery device 1 comprises areservoir 2 having aninlet port 5 located near theproximal end 3 of thereservoir 2, the agent injected through theinlet port 5 travels into thereservoir 2. If thereservoir 2 is fabricated of an elastic material, thereservoir 2 inflates/expands as it is filled. When the agent has been injected, the needle or other injection mechanism is removed from theinlet port 5 and theinlet port 5 sealed. The agent in thereservoir 2 is then delivered gradually via thedelivery mechanism 6. Iftube 14 is included, the agent is delivered through thetube 14 and/orreservoir 2. Once the therapeutic agent had been delivered to the treatment area, thedelivery device 1 may be refilled for further delivery or removed if the required dose of agent has been delivered for treatment of the condition. If required, an aspirating device or similar mechanism (not shown) may be used to further compress thereservoir 2, thereby enabling removal of thedelivery device 1 through a small incision that requires few or no sutures are required for sclera' closure. - In the embodiment that further comprises a hollow body or
tube 10, the agent injected through theinlet port 5 travels through the hollow body ortube 10 and into thereservoir 2 through either the one ormore apertures 13 in the hollow body ortube 10 or thedistal end 12 of the hollow body or tube. The needle or other injection mechanism is then removed from theinlet port 5 and theinlet port 5 sealed. The agent in thereservoir 2 is then delivered to the treatment area gradually through thereservoir 2 and/or through thedistal end 12 of the hollow body ortube 10. Iftube 14 is included, the agent is delivered through thetube 14 and/orreservoir 2. Once the therapeutic agent had been delivered to the treatment area, thedelivery device 1 may be refilled for further delivery or removed if the required dose of agent has been delivered for treatment of the condition. If required, an aspirating device or similar mechanism (not shown) may be used to further compress thereservoir 2 about the hollow body ortube 10, thereby enabling removal of thedelivery device 1 through a small incision that requires few or no sutures are required for scleral closure. - The invention is not be limited to ocular applications, and is particularly useful in other limited access regions such as the inner ear.
- The present invention also includes kits that comprise one or more device of the invention, preferably packaged in sterile condition. Kits of the invention also may include, for example, one or
more tubes 14, one ormore reservoirs 2, means for suturing or securing thefixation mechanism 8 to the sclera, etc. for use with the device, preferably packaged in sterile condition, and/or written instructions for use of the device and other components of the kit. - All documents mentioned herein are incorporated by reference herein in their entirety.
- The foregoing description of the invention is merely illustrative thereof, and it is understood that variations and modifications can be effected without departing from the scope or spirit of the invention as set forth in the following claims.
Claims (20)
1. A method of delivering at least a first therapeutic agent into an interior chamber of a patient's eye having an ocular disorder, comprising:
inserting a distal portion of an implant through a sclera of the eye and into the interior chamber, the implant comprising:
a refillable reservoir made of one or more biocompatible materials and adapted to contain the first therapeutic agent, the reservoir comprising a proximal portion and a distal portion, the distal portion comprising a non-permeable body having multiple apertures formed through the body, such that, when implanted, the first therapeutic agent flows or diffuses through the apertures into the eye, wherein the multiple apertures are adapted to achieve a desired rate of controlled, sustained delivery of the first therapeutic agent to the eye to treat the disorder; and
an inlet portion coupled to the proximal portion of the reservoir and in fluid communication with the reservoir, the inlet portion being injectable and capable of self-sealing upon retraction of a needle, the inlet portion adapted, when implanted, to remain external to and adjacent the sclera;
wherein at least the distal portion of the reservoir extends into the eye upon insertion; and
treating the disorder for an initial treatment period of time through the controlled, sustained delivery of the first therapeutic agent.
2. The method of claim 1 , further comprising introducing a needle through the inlet portion to aspirate the reservoir.
3. The method of claim 1 , wherein the patient's eye comprises a vitreous cavity, wherein the distal portion of the implant is inserted into the vitreous cavity, and wherein the agent flows or diffuses into vitreous in the cavity through the apertures.
4. The method of claim 1 , further comprising removing the implant from the eye after a desired dose of agent has been delivered, and closing a scleral incision.
5. The method of claim 4 , wherein the scleral incision requires few or no sutures to close the sclera upon removal.
6. The method of claim 1 , wherein the implant is sufficiently structurally rigid to facilitate insertion into the eye.
7. The method of claim 6 , wherein the rigidity is provided to the implant by at least one of stainless steel, titanium and nitinol.
8. The method of claim 1 , wherein each of the apertures is formed in the reservoir by laser, hot wire, drilling device or similar mechanism.
9. The method of claim 1 ,wherein the inlet portion comprises a scleral hub.
10. The method of claim 9 , wherein the scleral hub is circular.
11. The method of claim 9 , wherein the scleral hub conforms to a curvature of the eye.
12. The method of claim 1 , further comprising, after the initial treatment period, injecting additional therapeutic agent into the reservoir through the inlet portion, to continue to treat the patient for an additional treatment period without removing the implant from the eye.
13. The method of claim 1 , wherein each of the apertures has a length corresponding to a thickness of a wall of the body of the reservoir.
14. The method of claim 12 , wherein the additional therapeutic agent comprises a second therapeutic agent different from the first therapeutic agent.
15. The method of claim 1 , wherein the multiple apertures are adapted to achieve the desired rate of controlled, sustained delivery by varying at least one of the number and size of the apertures.
16. The method of claim 1 , wherein the distal portion of the reservoir is non-permeable to the therapeutic agent.
17. The method of claim 16 , wherein the non-permeable portion comprises at least 90% of the surface area of the reservoir.
18. The method of claim 1 , wherein the distal portion of the implant is roughly cylindrical upon insertion into the eye.
19. The method of claim 1 , wherein the desired rate of controlled, sustained delivery of the agent is determined based on an individual need of the patient.
20. The method of claim 12 , wherein the injecting additional agent is performed if further dose of agent is required for treatment of the disorder.
Priority Applications (2)
Application Number | Priority Date | Filing Date | Title |
---|---|---|---|
US15/366,982 US20170172794A1 (en) | 2001-06-12 | 2016-12-01 | Reservoir Device for Intraocular Drug Delivery |
US15/730,537 US10470924B2 (en) | 2001-06-12 | 2017-10-11 | Reservoir device for intraocular drug delivery |
Applications Claiming Priority (7)
Application Number | Priority Date | Filing Date | Title |
---|---|---|---|
US29749901P | 2001-06-12 | 2001-06-12 | |
US10/171,406 US7883717B2 (en) | 2001-06-12 | 2002-06-12 | Reservoir device for intraocular drug delivery |
US12/979,185 US8486052B2 (en) | 2001-06-12 | 2010-12-27 | Reservoir device for intraocular drug delivery |
US13/942,610 US9180046B2 (en) | 2001-06-12 | 2013-07-15 | Reservoir device for intraocular drug delivery |
US14/268,723 US20140243795A1 (en) | 2001-06-12 | 2014-05-02 | Reservoir Device for Intraocular Drug Delivery |
US15/060,532 US9522082B2 (en) | 2001-06-12 | 2016-03-03 | Reservoir device for intraocular drug delivery |
US15/366,982 US20170172794A1 (en) | 2001-06-12 | 2016-12-01 | Reservoir Device for Intraocular Drug Delivery |
Related Parent Applications (1)
Application Number | Title | Priority Date | Filing Date |
---|---|---|---|
US15/060,532 Continuation US9522082B2 (en) | 2001-06-12 | 2016-03-03 | Reservoir device for intraocular drug delivery |
Related Child Applications (1)
Application Number | Title | Priority Date | Filing Date |
---|---|---|---|
US15/730,537 Continuation US10470924B2 (en) | 2001-06-12 | 2017-10-11 | Reservoir device for intraocular drug delivery |
Publications (1)
Publication Number | Publication Date |
---|---|
US20170172794A1 true US20170172794A1 (en) | 2017-06-22 |
Family
ID=23146563
Family Applications (7)
Application Number | Title | Priority Date | Filing Date |
---|---|---|---|
US10/171,406 Active 2024-07-22 US7883717B2 (en) | 2001-06-12 | 2002-06-12 | Reservoir device for intraocular drug delivery |
US12/979,185 Expired - Lifetime US8486052B2 (en) | 2001-06-12 | 2010-12-27 | Reservoir device for intraocular drug delivery |
US13/942,610 Expired - Fee Related US9180046B2 (en) | 2001-06-12 | 2013-07-15 | Reservoir device for intraocular drug delivery |
US14/268,723 Abandoned US20140243795A1 (en) | 2001-06-12 | 2014-05-02 | Reservoir Device for Intraocular Drug Delivery |
US15/060,532 Expired - Lifetime US9522082B2 (en) | 2001-06-12 | 2016-03-03 | Reservoir device for intraocular drug delivery |
US15/366,982 Abandoned US20170172794A1 (en) | 2001-06-12 | 2016-12-01 | Reservoir Device for Intraocular Drug Delivery |
US15/730,537 Expired - Fee Related US10470924B2 (en) | 2001-06-12 | 2017-10-11 | Reservoir device for intraocular drug delivery |
Family Applications Before (5)
Application Number | Title | Priority Date | Filing Date |
---|---|---|---|
US10/171,406 Active 2024-07-22 US7883717B2 (en) | 2001-06-12 | 2002-06-12 | Reservoir device for intraocular drug delivery |
US12/979,185 Expired - Lifetime US8486052B2 (en) | 2001-06-12 | 2010-12-27 | Reservoir device for intraocular drug delivery |
US13/942,610 Expired - Fee Related US9180046B2 (en) | 2001-06-12 | 2013-07-15 | Reservoir device for intraocular drug delivery |
US14/268,723 Abandoned US20140243795A1 (en) | 2001-06-12 | 2014-05-02 | Reservoir Device for Intraocular Drug Delivery |
US15/060,532 Expired - Lifetime US9522082B2 (en) | 2001-06-12 | 2016-03-03 | Reservoir device for intraocular drug delivery |
Family Applications After (1)
Application Number | Title | Priority Date | Filing Date |
---|---|---|---|
US15/730,537 Expired - Fee Related US10470924B2 (en) | 2001-06-12 | 2017-10-11 | Reservoir device for intraocular drug delivery |
Country Status (7)
Country | Link |
---|---|
US (7) | US7883717B2 (en) |
EP (2) | EP1404297B1 (en) |
JP (4) | JP4677538B2 (en) |
AT (1) | ATE506929T1 (en) |
CA (1) | CA2450771C (en) |
DE (1) | DE60239868D1 (en) |
WO (1) | WO2002100318A2 (en) |
Cited By (28)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
US9931243B2 (en) | 2011-12-19 | 2018-04-03 | Ivantis, Inc. | Delivering ocular implants into the eye |
US10363168B2 (en) | 2011-06-14 | 2019-07-30 | Ivantis, Inc. | Ocular implants for delivery into the eye |
US10406025B2 (en) | 2009-07-09 | 2019-09-10 | Ivantis, Inc. | Ocular implants and methods for delivering ocular implants into the eye |
US10492949B2 (en) | 2009-07-09 | 2019-12-03 | Ivantis, Inc. | Single operator device for delivering an ocular implant |
US10537474B2 (en) | 2008-03-05 | 2020-01-21 | Ivantis, Inc. | Methods and apparatus for treating glaucoma |
US10603209B2 (en) | 2012-02-03 | 2020-03-31 | Forsight Vision4, Inc. | Insertion and removal methods and apparatus for therapeutic devices |
US10617558B2 (en) | 2012-11-28 | 2020-04-14 | Ivantis, Inc. | Apparatus for delivering ocular implants into an anterior chamber of the eye |
US10653554B2 (en) | 2011-09-16 | 2020-05-19 | Forsight Vision4, Inc. | Fluid exchange apparatus and methods |
US10656152B2 (en) | 2009-01-29 | 2020-05-19 | Forsight Vision4, Inc. | Posterior segment drug delivery |
US10709547B2 (en) | 2014-07-14 | 2020-07-14 | Ivantis, Inc. | Ocular implant delivery system and method |
US10765677B2 (en) | 2014-08-08 | 2020-09-08 | Forsight Vision4, Inc. | Stable and soluble formulations of receptor tyrosine kinase inhibitors, and methods of preparation thereof |
US10874548B2 (en) | 2010-11-19 | 2020-12-29 | Forsight Vision4, Inc. | Therapeutic agent formulations for implanted devices |
US11026836B2 (en) | 2012-04-18 | 2021-06-08 | Ivantis, Inc. | Ocular implants for delivery into an anterior chamber of the eye |
US11110001B2 (en) | 2014-11-10 | 2021-09-07 | Forsight Vision4, Inc. | Expandable drug delivery devices and methods of use |
US11197779B2 (en) | 2015-08-14 | 2021-12-14 | Ivantis, Inc. | Ocular implant with pressure sensor and delivery system |
US11337853B2 (en) | 2014-07-15 | 2022-05-24 | Forsight Vision4, Inc. | Ocular implant delivery device and method |
US11351058B2 (en) | 2017-03-17 | 2022-06-07 | W. L. Gore & Associates, Inc. | Glaucoma treatment systems and methods |
US11419759B2 (en) | 2017-11-21 | 2022-08-23 | Forsight Vision4, Inc. | Fluid exchange apparatus for expandable port delivery system and methods of use |
US11432959B2 (en) | 2015-11-20 | 2022-09-06 | Forsight Vision4, Inc. | Porous structures for extended release drug delivery devices |
US11540940B2 (en) | 2021-01-11 | 2023-01-03 | Alcon Inc. | Systems and methods for viscoelastic delivery |
US11617680B2 (en) | 2016-04-05 | 2023-04-04 | Forsight Vision4, Inc. | Implantable ocular drug delivery devices |
US11617644B2 (en) | 2014-10-13 | 2023-04-04 | W. L. Gore & Associates, Inc. | Prosthetic valved conduit |
US11679027B2 (en) | 2010-08-05 | 2023-06-20 | Forsight Vision4, Inc. | Combined drug delivery methods and apparatus |
US11678983B2 (en) | 2018-12-12 | 2023-06-20 | W. L. Gore & Associates, Inc. | Implantable component with socket |
US11744734B2 (en) | 2007-09-24 | 2023-09-05 | Alcon Inc. | Method of implanting an ocular implant |
US11786396B2 (en) | 2010-08-05 | 2023-10-17 | Forsight Vision4, Inc. | Injector apparatus and method for drug delivery |
US11813196B2 (en) | 2011-06-28 | 2023-11-14 | Forsight Vision4, Inc. | Diagnostic methods and apparatus |
US11938058B2 (en) | 2015-12-15 | 2024-03-26 | Alcon Inc. | Ocular implant and delivery system |
Families Citing this family (211)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
EP1154691A4 (en) * | 1999-01-05 | 2004-07-07 | Massachusetts Eye & Ear Infirm | Targeted transscleral controlled release drug delivery to the retina and choroid |
US7943162B2 (en) | 1999-10-21 | 2011-05-17 | Alcon, Inc. | Drug delivery device |
DE60135352D1 (en) * | 2000-08-30 | 2008-09-25 | Univ Johns Hopkins | DEVICE FOR INTRA-OCCULAR ACTIVE AGGREGATION |
DE10105592A1 (en) * | 2001-02-06 | 2002-08-08 | Achim Goepferich | Placeholder for drug release in the frontal sinus |
US7431710B2 (en) | 2002-04-08 | 2008-10-07 | Glaukos Corporation | Ocular implants with anchors and methods thereof |
DE60239868D1 (en) | 2001-06-12 | 2011-06-09 | Univ Johns Hopkins Med | RESERVOIR DEVICE FOR INTRAOCULAR DRUG DELIVERY |
DK1409065T3 (en) | 2001-07-23 | 2007-05-21 | Alcon Inc | Ophthalmic drug delivery device |
BR0210287A (en) | 2001-07-23 | 2005-12-13 | Alcon Inc | Ophthalmic drug delivery device |
GB2399753B (en) | 2002-01-18 | 2006-04-19 | Michael E Snyder | Method of making a sustained release ophthalmological device |
WO2003092665A2 (en) * | 2002-05-02 | 2003-11-13 | Massachusetts Eye And Ear Infirmary | Ocular drug delivery systems and use thereof |
US20070027537A1 (en) * | 2002-08-02 | 2007-02-01 | David Castillejos | Method and intra-sclera implant for treatment of glaucoma and presbyopia |
AU2003273339B2 (en) * | 2002-09-17 | 2008-08-14 | Iscience Interventional Corporation | Apparatus and method for surgical bypass of aqueous humor |
CA2689424A1 (en) * | 2002-09-29 | 2004-04-08 | Surmodics, Inc. | Methods for treatment and/or prevention of retinal disease |
US8317816B2 (en) | 2002-09-30 | 2012-11-27 | Acclarent, Inc. | Balloon catheters and methods for treating paranasal sinuses |
AR043356A1 (en) * | 2003-01-24 | 2005-07-27 | Control Delivery Sys Inc | SUSTAINED RELEASE DEVICE FOR THE OCULAR ADMINISTRATION OF CARBON ANHYDRATION INHIBITORS AND USE OF CARBON ANHYDRATION INHIBITORS FOR PREPARATION |
US20060167435A1 (en) * | 2003-02-18 | 2006-07-27 | Adamis Anthony P | Transscleral drug delivery device and related methods |
US8404269B2 (en) | 2003-04-11 | 2013-03-26 | Michael Snyder | Sustained release implantable eye device |
DE602004028638D1 (en) * | 2003-05-02 | 2010-09-23 | Surmodics Inc | System for the controlled release of a bioactive agent in the back of the eye |
US8246974B2 (en) * | 2003-05-02 | 2012-08-21 | Surmodics, Inc. | Medical devices and methods for producing the same |
US20050148948A1 (en) * | 2003-12-19 | 2005-07-07 | Caputa Steven G. | Sutureless ophthalmic drug delivery system and method |
US7976520B2 (en) | 2004-01-12 | 2011-07-12 | Nulens Ltd. | Eye wall anchored fixtures |
IL159818A0 (en) * | 2004-01-12 | 2004-06-20 | Nulens Ltd | Intraocular structure |
US7276050B2 (en) * | 2004-03-02 | 2007-10-02 | Alan Franklin | Trans-scleral drug delivery method and apparatus |
US7803150B2 (en) | 2004-04-21 | 2010-09-28 | Acclarent, Inc. | Devices, systems and methods useable for treating sinusitis |
US8894614B2 (en) | 2004-04-21 | 2014-11-25 | Acclarent, Inc. | Devices, systems and methods useable for treating frontal sinusitis |
US9089258B2 (en) * | 2004-04-21 | 2015-07-28 | Acclarent, Inc. | Endoscopic methods and devices for transnasal procedures |
US7462175B2 (en) | 2004-04-21 | 2008-12-09 | Acclarent, Inc. | Devices, systems and methods for treating disorders of the ear, nose and throat |
US9399121B2 (en) | 2004-04-21 | 2016-07-26 | Acclarent, Inc. | Systems and methods for transnasal dilation of passageways in the ear, nose or throat |
US10188413B1 (en) | 2004-04-21 | 2019-01-29 | Acclarent, Inc. | Deflectable guide catheters and related methods |
US7419497B2 (en) | 2004-04-21 | 2008-09-02 | Acclarent, Inc. | Methods for treating ethmoid disease |
US7410480B2 (en) * | 2004-04-21 | 2008-08-12 | Acclarent, Inc. | Devices and methods for delivering therapeutic substances for the treatment of sinusitis and other disorders |
US8764729B2 (en) * | 2004-04-21 | 2014-07-01 | Acclarent, Inc. | Frontal sinus spacer |
US7654997B2 (en) | 2004-04-21 | 2010-02-02 | Acclarent, Inc. | Devices, systems and methods for diagnosing and treating sinusitus and other disorders of the ears, nose and/or throat |
US7361168B2 (en) * | 2004-04-21 | 2008-04-22 | Acclarent, Inc. | Implantable device and methods for delivering drugs and other substances to treat sinusitis and other disorders |
US8932276B1 (en) | 2004-04-21 | 2015-01-13 | Acclarent, Inc. | Shapeable guide catheters and related methods |
US8747389B2 (en) * | 2004-04-21 | 2014-06-10 | Acclarent, Inc. | Systems for treating disorders of the ear, nose and throat |
US20060063973A1 (en) | 2004-04-21 | 2006-03-23 | Acclarent, Inc. | Methods and apparatus for treating disorders of the ear, nose and throat |
US20190314620A1 (en) | 2004-04-21 | 2019-10-17 | Acclarent, Inc. | Apparatus and methods for dilating and modifying ostia of paranasal sinuses and other intranasal or paranasal structures |
US20070208252A1 (en) * | 2004-04-21 | 2007-09-06 | Acclarent, Inc. | Systems and methods for performing image guided procedures within the ear, nose, throat and paranasal sinuses |
US8702626B1 (en) | 2004-04-21 | 2014-04-22 | Acclarent, Inc. | Guidewires for performing image guided procedures |
US9101384B2 (en) | 2004-04-21 | 2015-08-11 | Acclarent, Inc. | Devices, systems and methods for diagnosing and treating sinusitis and other disorders of the ears, Nose and/or throat |
US9554691B2 (en) | 2004-04-21 | 2017-01-31 | Acclarent, Inc. | Endoscopic methods and devices for transnasal procedures |
US20070167682A1 (en) | 2004-04-21 | 2007-07-19 | Acclarent, Inc. | Endoscopic methods and devices for transnasal procedures |
US8146400B2 (en) | 2004-04-21 | 2012-04-03 | Acclarent, Inc. | Endoscopic methods and devices for transnasal procedures |
US20060004323A1 (en) | 2004-04-21 | 2006-01-05 | Exploramed Nc1, Inc. | Apparatus and methods for dilating and modifying ostia of paranasal sinuses and other intranasal or paranasal structures |
US7559925B2 (en) * | 2006-09-15 | 2009-07-14 | Acclarent Inc. | Methods and devices for facilitating visualization in a surgical environment |
US9351750B2 (en) | 2004-04-21 | 2016-05-31 | Acclarent, Inc. | Devices and methods for treating maxillary sinus disease |
EP2380622A1 (en) * | 2004-04-29 | 2011-10-26 | iScience Interventional Corporation | Method for ocular treatment |
CA2564806A1 (en) * | 2004-04-29 | 2005-11-17 | Iscience Surgical Corporation | Apparatus and method for surgical enhancement of aqueous humor drainage |
US20100173866A1 (en) * | 2004-04-29 | 2010-07-08 | Iscience Interventional Corporation | Apparatus and method for ocular treatment |
US20060024350A1 (en) * | 2004-06-24 | 2006-02-02 | Varner Signe E | Biodegradable ocular devices, methods and systems |
US20060110428A1 (en) * | 2004-07-02 | 2006-05-25 | Eugene Dejuan | Methods and devices for the treatment of ocular conditions |
US7117870B2 (en) * | 2004-07-26 | 2006-10-10 | Clarity Corporation | Lacrimal insert having reservoir with controlled release of medication and method of manufacturing the same |
WO2006023130A2 (en) * | 2004-08-12 | 2006-03-02 | Surmodics, Inc. | Biodegradable controlled release bioactive agent delivery device |
US8246569B1 (en) | 2004-08-17 | 2012-08-21 | California Institute Of Technology | Implantable intraocular pressure drain |
KR20080016780A (en) * | 2004-11-24 | 2008-02-22 | 테라킨 리미티드 | An implant for intraocular drug delivery |
US20060134168A1 (en) * | 2004-12-07 | 2006-06-22 | Chappa Ralph A | Coatings with crystallized active agent(s) and methods |
US9788978B2 (en) * | 2004-12-20 | 2017-10-17 | Nicholas A. Rojo | Implantable systems and stents containing cells for therapeutic uses |
US20060198868A1 (en) * | 2005-01-05 | 2006-09-07 | Dewitt David M | Biodegradable coating compositions comprising blends |
US20060147491A1 (en) * | 2005-01-05 | 2006-07-06 | Dewitt David M | Biodegradable coating compositions including multiple layers |
ES2564194T3 (en) | 2005-02-09 | 2016-03-18 | Santen Pharmaceutical Co., Ltd. | Liquid formulations for the treatment of diseases or ailments |
JP2008535847A (en) * | 2005-04-08 | 2008-09-04 | サーモディクス,インコーポレイティド | Sustained release implant for subretinal delivery |
US20060258994A1 (en) * | 2005-05-12 | 2006-11-16 | Avery Robert L | Implantable delivery device for administering pharmacological agents to an internal portion of a body |
US8951225B2 (en) | 2005-06-10 | 2015-02-10 | Acclarent, Inc. | Catheters with non-removable guide members useable for treatment of sinusitis |
US8663673B2 (en) | 2005-07-29 | 2014-03-04 | Surmodics, Inc. | Devices, articles, coatings, and methods for controlled active agent release or hemocompatibility |
US20070212397A1 (en) * | 2005-09-15 | 2007-09-13 | Roth Daniel B | Pharmaceutical delivery device and method for providing ocular treatment |
US8114113B2 (en) * | 2005-09-23 | 2012-02-14 | Acclarent, Inc. | Multi-conduit balloon catheter |
WO2007059144A1 (en) * | 2005-11-15 | 2007-05-24 | Surmodics, Inc. | Ultrasonic nozzles for applying two-component coatings |
CA2637602C (en) * | 2006-01-17 | 2014-09-16 | Forsight Labs, Llc | Drug delivery treatment device |
EP3005996B1 (en) | 2006-01-17 | 2019-12-04 | Novartis Ag | Glaucoma treatment device |
US20070179518A1 (en) * | 2006-02-02 | 2007-08-02 | Becker Bruce B | Balloon Catheters and Methods for Treating Paranasal Sinuses |
BRPI0707612B8 (en) | 2006-02-09 | 2021-05-25 | Macusight Inc | sealed vessel and liquid formulations contained therein |
US7887508B2 (en) | 2006-03-14 | 2011-02-15 | The University Of Southern California | MEMS device and method for delivery of therapeutic agents |
US8222271B2 (en) | 2006-03-23 | 2012-07-17 | Santen Pharmaceutical Co., Ltd. | Formulations and methods for vascular permeability-related diseases or conditions |
US8190389B2 (en) | 2006-05-17 | 2012-05-29 | Acclarent, Inc. | Adapter for attaching electromagnetic image guidance components to a medical device |
US7909789B2 (en) | 2006-06-26 | 2011-03-22 | Sight Sciences, Inc. | Intraocular implants and methods and kits therefor |
US8968782B2 (en) * | 2006-06-28 | 2015-03-03 | Surmodics, Inc. | Combination degradable and non-degradable matrices for active agent delivery |
WO2008079440A2 (en) | 2006-07-10 | 2008-07-03 | Medipacs, Inc. | Super elastic epoxy hydrogel |
WO2008022258A2 (en) * | 2006-08-16 | 2008-02-21 | Surmodics, Inc. | Methods and materials for increasing the adhesion of elution control matrices to substrates |
US9820688B2 (en) | 2006-09-15 | 2017-11-21 | Acclarent, Inc. | Sinus illumination lightwire device |
US20080075753A1 (en) * | 2006-09-25 | 2008-03-27 | Chappa Ralph A | Multi-layered coatings and methods for controlling elution of active agents |
WO2008088593A2 (en) * | 2006-09-27 | 2008-07-24 | Surmodics, Inc. | Additives and methods for enhancing active agent elution kinetics |
US8439687B1 (en) | 2006-12-29 | 2013-05-14 | Acclarent, Inc. | Apparatus and method for simulated insertion and positioning of guidewares and other interventional devices |
WO2008124787A2 (en) | 2007-04-09 | 2008-10-16 | Acclarent, Inc. | Ethmoidotomy system and implantable spacer devices having therapeutic substance delivery capability for treatment of paranasal sinusitis |
US8118757B2 (en) | 2007-04-30 | 2012-02-21 | Acclarent, Inc. | Methods and devices for ostium measurement |
US8485199B2 (en) | 2007-05-08 | 2013-07-16 | Acclarent, Inc. | Methods and devices for protecting nasal turbinate during surgery |
US20090030409A1 (en) * | 2007-07-27 | 2009-01-29 | Eric Goldfarb | Methods and devices for facilitating visualization in a surgical environment |
JP2011505520A (en) | 2007-12-03 | 2011-02-24 | メディパックス インコーポレイテッド | Fluid metering device |
US10206821B2 (en) | 2007-12-20 | 2019-02-19 | Acclarent, Inc. | Eustachian tube dilation balloon with ventilation path |
MX2010006840A (en) * | 2007-12-20 | 2010-08-12 | Univ Southern California | Apparatus and methods for delivering therapeutic agents. |
ES2546192T3 (en) * | 2008-01-03 | 2015-09-21 | University Of Southern California | Implantable drug delivery devices and devices and methods for recharging the devices |
CA2714985C (en) * | 2008-01-07 | 2018-05-15 | Salutaris Medical Devices, Inc. | Methods and devices for minimally-invasive extraocular delivery of radiation to the posterior portion of the eye |
US10022558B1 (en) | 2008-01-07 | 2018-07-17 | Salutaris Medical Devices, Inc. | Methods and devices for minimally-invasive delivery of radiation to the eye |
US9056201B1 (en) | 2008-01-07 | 2015-06-16 | Salutaris Medical Devices, Inc. | Methods and devices for minimally-invasive delivery of radiation to the eye |
US8602959B1 (en) | 2010-05-21 | 2013-12-10 | Robert Park | Methods and devices for delivery of radiation to the posterior portion of the eye |
US9873001B2 (en) | 2008-01-07 | 2018-01-23 | Salutaris Medical Devices, Inc. | Methods and devices for minimally-invasive delivery of radiation to the eye |
US8608632B1 (en) | 2009-07-03 | 2013-12-17 | Salutaris Medical Devices, Inc. | Methods and devices for minimally-invasive extraocular delivery of radiation and/or pharmaceutics to the posterior portion of the eye |
US20090186059A1 (en) * | 2008-01-14 | 2009-07-23 | Johnson Elizabeth E | Devices and methods for elution of nucleic acid delivery complexes |
US8182432B2 (en) | 2008-03-10 | 2012-05-22 | Acclarent, Inc. | Corewire design and construction for medical devices |
WO2009126830A2 (en) * | 2008-04-09 | 2009-10-15 | Surmodics, Inc. | Delivery of nucleic acid complexes from materials including negatively charged groups |
CA2723192A1 (en) * | 2008-05-07 | 2009-11-12 | Surmodics, Inc. | Delivery of nucleic acid complexes from particles |
EP2323716B1 (en) * | 2008-05-08 | 2015-03-04 | MiniPumps, LLC | Drug-delivery pumps |
MX2010012213A (en) * | 2008-05-08 | 2011-05-03 | Minipumps Llc | Implantable pumps and cannulas therefor. |
US9333297B2 (en) | 2008-05-08 | 2016-05-10 | Minipumps, Llc | Drug-delivery pump with intelligent control |
CN103394142B (en) * | 2008-05-08 | 2015-08-19 | 迷你泵有限责任公司 | Implantable drug delivery devices with for filling equipment and the method for this device |
JP5676446B2 (en) | 2008-07-30 | 2015-02-25 | アクラレント インコーポレイテッド | Sinus mouth finder |
JP5584687B2 (en) | 2008-09-18 | 2014-09-03 | アクラレント インコーポレイテッド | Method and apparatus for treating ear, nose and throat disorders |
JP2012509737A (en) * | 2008-11-26 | 2012-04-26 | サーモディクス,インコーポレイティド | Implantable ophthalmic drug delivery device and ophthalmic drug delivery method |
MX2011006726A (en) * | 2009-01-02 | 2011-07-20 | Alcon Res Ltd | In-situ refillable ophthalmic implant. |
USD691270S1 (en) | 2009-01-07 | 2013-10-08 | Salutaris Medical Devices, Inc. | Fixed-shape cannula for posterior delivery of radiation to an eye |
USD691267S1 (en) | 2009-01-07 | 2013-10-08 | Salutaris Medical Devices, Inc. | Fixed-shape cannula for posterior delivery of radiation to eye |
USD691268S1 (en) | 2009-01-07 | 2013-10-08 | Salutaris Medical Devices, Inc. | Fixed-shape cannula for posterior delivery of radiation to eye |
USD691269S1 (en) | 2009-01-07 | 2013-10-08 | Salutaris Medical Devices, Inc. | Fixed-shape cannula for posterior delivery of radiation to an eye |
US20100191177A1 (en) * | 2009-01-23 | 2010-07-29 | Iscience Interventional Corporation | Device for aspirating fluids |
US8425473B2 (en) | 2009-01-23 | 2013-04-23 | Iscience Interventional Corporation | Subretinal access device |
US8623395B2 (en) | 2010-01-29 | 2014-01-07 | Forsight Vision4, Inc. | Implantable therapeutic device |
US20100241155A1 (en) | 2009-03-20 | 2010-09-23 | Acclarent, Inc. | Guide system with suction |
US8435290B2 (en) | 2009-03-31 | 2013-05-07 | Acclarent, Inc. | System and method for treatment of non-ventilating middle ear by providing a gas pathway through the nasopharynx |
US7978742B1 (en) | 2010-03-24 | 2011-07-12 | Corning Incorporated | Methods for operating diode lasers |
US10206813B2 (en) | 2009-05-18 | 2019-02-19 | Dose Medical Corporation | Implants with controlled drug delivery features and methods of using same |
CN102576385B (en) | 2009-08-18 | 2016-02-24 | 迷你泵有限责任公司 | There is the electrolytic drug discharge pump of adaptive control |
US9238102B2 (en) | 2009-09-10 | 2016-01-19 | Medipacs, Inc. | Low profile actuator and improved method of caregiver controlled administration of therapeutics |
US8419673B2 (en) | 2009-09-21 | 2013-04-16 | Alcon Research, Ltd. | Glaucoma drainage device with pump |
US8721580B2 (en) * | 2009-09-21 | 2014-05-13 | Alcon Research, Ltd. | Power saving glaucoma drainage device |
US8257295B2 (en) | 2009-09-21 | 2012-09-04 | Alcon Research, Ltd. | Intraocular pressure sensor with external pressure compensation |
US8545431B2 (en) * | 2009-09-21 | 2013-10-01 | Alcon Research, Ltd. | Lumen clearing valve for glaucoma drainage device |
US8382750B2 (en) * | 2009-10-28 | 2013-02-26 | Vivant Medical, Inc. | System and method for monitoring ablation size |
WO2011053908A1 (en) * | 2009-11-02 | 2011-05-05 | Salutaris Medical Devices, Inc. | Methods and devices for delivering appropriate minimally-invasive extraocular radiation |
US20110160740A1 (en) * | 2009-12-28 | 2011-06-30 | Acclarent, Inc. | Tissue Removal in The Paranasal Sinus and Nasal Cavity |
US20110172639A1 (en) * | 2010-01-08 | 2011-07-14 | Ratio, Inc. | Device and method for delivery of microneedle to desired depth within the skin |
US20110172637A1 (en) * | 2010-01-08 | 2011-07-14 | Ratio, Inc. | Drug delivery device including tissue support structure |
US20110172609A1 (en) * | 2010-01-08 | 2011-07-14 | Ratio, Inc. | Microneedle component assembly for drug delivery device |
US20110172645A1 (en) * | 2010-01-08 | 2011-07-14 | Ratio, Inc. | Wearable drug delivery device including integrated pumping and activation elements |
US9500186B2 (en) | 2010-02-01 | 2016-11-22 | Medipacs, Inc. | High surface area polymer actuator with gas mitigating components |
US8038650B2 (en) * | 2010-02-22 | 2011-10-18 | Microsert Ltd. | Slow release liquid drug delivery device |
WO2012019176A2 (en) * | 2010-08-05 | 2012-02-09 | Forsight Vision4 Inc. | Implantable therapeutic device |
US9155492B2 (en) | 2010-09-24 | 2015-10-13 | Acclarent, Inc. | Sinus illumination lightwire device |
JPWO2012043081A1 (en) | 2010-09-27 | 2014-02-06 | テルモ株式会社 | Medical device |
US20120100187A1 (en) | 2010-10-26 | 2012-04-26 | Surmodics, Inc. | Coatings and methods for controlled elution of hydrophilic active agents |
US8668675B2 (en) | 2010-11-03 | 2014-03-11 | Flugen, Inc. | Wearable drug delivery device having spring drive and sliding actuation mechanism |
US20140033800A1 (en) | 2010-11-11 | 2014-02-06 | Forsight Vision4, Inc. | Methods and apparatus to determine diffusion properties of porous structures for drug delivery |
US8901092B2 (en) | 2010-12-29 | 2014-12-02 | Surmodics, Inc. | Functionalized polysaccharides for active agent delivery |
US9603997B2 (en) | 2011-03-14 | 2017-03-28 | Minipumps, Llc | Implantable drug pumps and refill devices therefor |
US10286146B2 (en) | 2011-03-14 | 2019-05-14 | Minipumps, Llc | Implantable drug pumps and refill devices therefor |
US9919099B2 (en) | 2011-03-14 | 2018-03-20 | Minipumps, Llc | Implantable drug pumps and refill devices therefor |
WO2012142318A1 (en) * | 2011-04-14 | 2012-10-18 | The Regents Of The University Of California | Multilayer thin film drug delivery device and methods of making and using the same |
EP2709672B1 (en) | 2011-05-18 | 2019-12-18 | The Regents of The University of California | Compositions and methods for treating retinal diseases |
US10245178B1 (en) | 2011-06-07 | 2019-04-02 | Glaukos Corporation | Anterior chamber drug-eluting ocular implant |
EP2739252A4 (en) | 2011-08-05 | 2015-08-12 | Forsight Vision4 Inc | Small molecule delivery with implantable therapeutic device |
US8585631B2 (en) | 2011-10-18 | 2013-11-19 | Alcon Research, Ltd. | Active bimodal valve system for real-time IOP control |
US8579848B2 (en) | 2011-12-09 | 2013-11-12 | Alcon Research, Ltd. | Active drainage systems with pressure-driven valves and electronically-driven pump |
US8840578B2 (en) | 2011-12-09 | 2014-09-23 | Alcon Research, Ltd. | Multilayer membrane actuators |
WO2013090197A1 (en) | 2011-12-12 | 2013-06-20 | Alcon Research, Ltd. | Active drainage systems with dual-input pressure-driven valves |
WO2013090231A1 (en) | 2011-12-13 | 2013-06-20 | Alcon Research, Ltd. | Active drainage systems with dual-input pressure-driven valves |
US9339187B2 (en) | 2011-12-15 | 2016-05-17 | Alcon Research, Ltd. | External pressure measurement system and method for an intraocular implant |
US9241829B2 (en) | 2011-12-20 | 2016-01-26 | Abbott Medical Optics Inc. | Implantable intraocular drug delivery apparatus, system and method |
US10000605B2 (en) | 2012-03-14 | 2018-06-19 | Medipacs, Inc. | Smart polymer materials with excess reactive molecules |
ES2842454T3 (en) | 2012-03-20 | 2021-07-14 | Sight Sciences Inc | Eye delivery systems |
WO2013181498A1 (en) | 2012-06-01 | 2013-12-05 | Surmodics, Inc. | Apparatus and method for coating balloon catheters |
US9827401B2 (en) | 2012-06-01 | 2017-11-28 | Surmodics, Inc. | Apparatus and methods for coating medical devices |
US11090468B2 (en) | 2012-10-25 | 2021-08-17 | Surmodics, Inc. | Apparatus and methods for coating medical devices |
US9528633B2 (en) | 2012-12-17 | 2016-12-27 | Novartis Ag | MEMS check valve |
US9572712B2 (en) | 2012-12-17 | 2017-02-21 | Novartis Ag | Osmotically actuated fluidic valve |
US9295389B2 (en) | 2012-12-17 | 2016-03-29 | Novartis Ag | Systems and methods for priming an intraocular pressure sensor in an intraocular implant |
AU2014236455B2 (en) | 2013-03-14 | 2018-07-12 | Forsight Vision4, Inc. | Systems for sustained intraocular delivery of low solubility compounds from a port delivery system implant |
US9629684B2 (en) | 2013-03-15 | 2017-04-25 | Acclarent, Inc. | Apparatus and method for treatment of ethmoid sinusitis |
US9433437B2 (en) | 2013-03-15 | 2016-09-06 | Acclarent, Inc. | Apparatus and method for treatment of ethmoid sinusitis |
US9597227B2 (en) * | 2013-03-15 | 2017-03-21 | Abbott Medical Optics Inc. | Trans-sclera portal for delivery of therapeutic agents |
JP6385423B2 (en) | 2013-03-28 | 2018-09-05 | フォーサイト・ビジョン フォー・インコーポレーテッド | Ocular graft for therapeutic substance delivery |
US20140336619A1 (en) * | 2013-05-13 | 2014-11-13 | Abbott Cardiovascular Systems Inc. | Ophthalmic shunt and method |
US20160130321A1 (en) | 2013-06-20 | 2016-05-12 | Gabriela Burian | Use of a vegf antagonist in treating macular edema |
US20160129080A1 (en) | 2013-06-20 | 2016-05-12 | Aaron Osborne | Treatment of polypoidal chroidal vasculopathy |
EP3010525A1 (en) | 2013-06-20 | 2016-04-27 | Novartis AG | Use of a vegf antagonist in treating choroidal neovascularisation |
KR20160029794A (en) | 2013-07-11 | 2016-03-15 | 노파르티스 아게 | Use of a vegf antagonist in treating chorioretinal neovascular and permeability disorders in paediatric patients |
US9226851B2 (en) | 2013-08-24 | 2016-01-05 | Novartis Ag | MEMS check valve chip and methods |
US9283115B2 (en) | 2013-08-26 | 2016-03-15 | Novartis Ag | Passive to active staged drainage device |
US9289324B2 (en) | 2013-08-26 | 2016-03-22 | Novartis Ag | Externally adjustable passive drainage device |
US10376413B2 (en) * | 2013-10-27 | 2019-08-13 | Microsert Ltd. | Implantable drug delivery device and a system and method for deployment of such devices |
US9445941B2 (en) | 2013-11-07 | 2016-09-20 | Drug Delivery Company, Llc | Bioresorbable drug eluting intravitreal implant system and method |
US9681983B2 (en) | 2014-03-13 | 2017-06-20 | Novartis Ag | Debris clearance system for an ocular implant |
US9603742B2 (en) | 2014-03-13 | 2017-03-28 | Novartis Ag | Remote magnetic driven flow system |
EP3677229A1 (en) | 2014-05-29 | 2020-07-08 | Glaukos Corporation | Implants with controlled drug delivery features |
CN111374821B (en) * | 2014-06-19 | 2022-05-03 | 加州理工学院 | Small molecule transport device for delivering drugs or removing waste |
US10299958B2 (en) | 2015-03-31 | 2019-05-28 | Sight Sciences, Inc. | Ocular delivery systems and methods |
US9655777B2 (en) | 2015-04-07 | 2017-05-23 | Novartis Ag | System and method for diagphragm pumping using heating element |
US11925578B2 (en) | 2015-09-02 | 2024-03-12 | Glaukos Corporation | Drug delivery implants with bi-directional delivery capacity |
TWI799366B (en) | 2015-09-15 | 2023-04-21 | 美商建南德克公司 | Cystine knot scaffold platform |
US11564833B2 (en) | 2015-09-25 | 2023-01-31 | Glaukos Corporation | Punctal implants with controlled drug delivery features and methods of using same |
US11857461B2 (en) * | 2015-11-23 | 2024-01-02 | The Regents Of The University Of Colorado, A Body Corporate | Lacrimal system for drug delivery |
KR101750651B1 (en) * | 2016-01-28 | 2017-06-23 | 동국대학교 산학협력단 | Intraocular drug injection device having a drug residue prevention and a refill function |
JP7003110B2 (en) | 2016-04-20 | 2022-01-20 | ドーズ メディカル コーポレーション | Bioabsorbable eye drug delivery device |
USD815285S1 (en) | 2016-05-11 | 2018-04-10 | Salutaris Medical Devices, Inc. | Brachytherapy device |
USD814638S1 (en) | 2016-05-11 | 2018-04-03 | Salutaris Medical Devices, Inc. | Brachytherapy device |
USD814637S1 (en) | 2016-05-11 | 2018-04-03 | Salutaris Medical Devices, Inc. | Brachytherapy device |
US11213430B2 (en) * | 2016-05-26 | 2022-01-04 | Cochlear Limited | Inner ear plug |
USD808528S1 (en) | 2016-08-31 | 2018-01-23 | Salutaris Medical Devices, Inc. | Holder for a brachytherapy device |
USD808529S1 (en) | 2016-08-31 | 2018-01-23 | Salutaris Medical Devices, Inc. | Holder for a brachytherapy device |
US11753623B2 (en) | 2017-06-05 | 2023-09-12 | The Regents Of The University Of California | Compositions for treating retinal diseases and methods for making and using them |
WO2019023617A1 (en) * | 2017-07-27 | 2019-01-31 | University Of Utah Research Foundation | Therapeutic delivery device |
US11534283B2 (en) * | 2017-09-06 | 2022-12-27 | Children's National Medical Center | Porous implantable devices |
AU2019256527A1 (en) | 2018-04-19 | 2020-11-12 | Spiral Therapeutics, Inc. | Inner ear drug delivery devices and methods of use |
CN112996468A (en) * | 2018-08-29 | 2021-06-18 | W.L.戈尔及同仁股份有限公司 | Drug therapy delivery systems and methods |
US11583627B1 (en) | 2018-10-18 | 2023-02-21 | University Of South Florida | Implantable drug storage devices for drug delivery |
WO2020112816A1 (en) | 2018-11-29 | 2020-06-04 | Surmodics, Inc. | Apparatus and methods for coating medical devices |
CN109431678B (en) * | 2018-12-17 | 2021-05-28 | 中国医学科学院北京协和医院 | Transscleral drug delivery system |
US11779739B2 (en) * | 2018-12-21 | 2023-10-10 | Perfect Ip, Llc | Drug delivery system and method |
US11819590B2 (en) | 2019-05-13 | 2023-11-21 | Surmodics, Inc. | Apparatus and methods for coating medical devices |
US11504270B1 (en) | 2019-09-27 | 2022-11-22 | Sight Sciences, Inc. | Ocular delivery systems and methods |
CN112569457B (en) * | 2020-12-10 | 2024-02-13 | 北京大学第三医院(北京大学第三临床医学院) | Continuous administration cyst tube system |
EP4346757A1 (en) * | 2021-05-27 | 2024-04-10 | W. L. Gore & Associates, Inc. | Drug therapy delivery systems and methods |
US20220378612A1 (en) * | 2021-05-28 | 2022-12-01 | Sight Sciences, Inc. | Intraocular devices, systems, and methods |
Family Cites Families (209)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
US2585815A (en) | 1947-01-16 | 1952-02-12 | Mclintock Duncan Menzies | Injection syringe |
US2564977A (en) | 1949-01-19 | 1951-08-21 | Hu Quang Hsi | Medical injecting apparatus |
US3232117A (en) | 1962-09-14 | 1966-02-01 | Roger Gilmont Instr Inc | Micrometer buret |
US3416530A (en) | 1966-03-02 | 1968-12-17 | Richard A. Ness | Eyeball medication dispensing tablet |
US3618604A (en) | 1969-06-09 | 1971-11-09 | Alza Corp | Ocular insert |
US3641237A (en) | 1970-09-30 | 1972-02-08 | Nat Patent Dev Corp | Zero order release constant elution rate drug dosage |
US4034756A (en) | 1971-01-13 | 1977-07-12 | Alza Corporation | Osmotically driven fluid dispenser |
US3831583A (en) * | 1971-03-05 | 1974-08-27 | Univ California | Implantable bulb for inflation of surgical implements |
US3986510A (en) | 1971-09-09 | 1976-10-19 | Alza Corporation | Bioerodible ocular device |
US3995635A (en) | 1971-09-09 | 1976-12-07 | Alza Corporation | Ocular insert |
US3828777A (en) | 1971-11-08 | 1974-08-13 | Alza Corp | Microporous ocular device |
US3826258A (en) | 1972-02-07 | 1974-07-30 | S Abraham | Gradual release medicine carrier |
US3845201A (en) | 1972-04-24 | 1974-10-29 | S Loucas | Solid state ophthalmic medication delivery method |
US3916899A (en) | 1973-04-25 | 1975-11-04 | Alza Corp | Osmotic dispensing device with maximum and minimum sizes for the passageway |
US3914402A (en) | 1973-06-14 | 1975-10-21 | Alza Corp | Ophthalmic dosage form, for releasing medication over time |
US4179497A (en) | 1973-12-17 | 1979-12-18 | Merck & Co., Inc. | Solid state ophthalmic medication |
US3902495A (en) | 1974-01-28 | 1975-09-02 | Cavitron Corp | Flow control system |
US3961628A (en) | 1974-04-10 | 1976-06-08 | Alza Corporation | Ocular drug dispensing system |
US3949748A (en) | 1974-09-26 | 1976-04-13 | Oscar Malmin | Injection syringe having aspirating and metering capabilities |
US3949750A (en) | 1974-10-07 | 1976-04-13 | Freeman Jerre M | Punctum plug and method for treating keratoconjunctivitis sicca (dry eye) and other ophthalmic aliments using same |
US3926188A (en) | 1974-11-14 | 1975-12-16 | Alza Corp | Laminated drug dispenser |
US4142526A (en) | 1974-12-23 | 1979-03-06 | Alza Corporation | Osmotic releasing system with means for changing release therefrom |
US4014335A (en) * | 1975-04-21 | 1977-03-29 | Alza Corporation | Ocular drug delivery device |
US4057619A (en) | 1975-06-30 | 1977-11-08 | Alza Corporation | Ocular therapeutic system with selected membranes for administering ophthalmic drug |
NL188266C (en) | 1975-07-29 | 1992-05-18 | Merck & Co Inc | PROCESS FOR THE PREPARATION OF AN ORGANIC IMPLANT. |
US3977404A (en) | 1975-09-08 | 1976-08-31 | Alza Corporation | Osmotic device having microporous reservoir |
US4034758A (en) | 1975-09-08 | 1977-07-12 | Alza Corporation | Osmotic therapeutic system for administering medicament |
US4014333A (en) | 1975-09-22 | 1977-03-29 | Mcintyre David J | Instrument for aspirating and irrigating during ophthalmic surgery |
US4077407A (en) | 1975-11-24 | 1978-03-07 | Alza Corporation | Osmotic devices having composite walls |
US4008719A (en) | 1976-02-02 | 1977-02-22 | Alza Corporation | Osmotic system having laminar arrangement for programming delivery of active agent |
US4014334A (en) | 1976-02-02 | 1977-03-29 | Alza Corporation | Laminated osmotic system for dispensing beneficial agent |
US4111201A (en) | 1976-11-22 | 1978-09-05 | Alza Corporation | Osmotic system for delivering selected beneficial agents having varying degrees of solubility |
US4111203A (en) | 1976-11-22 | 1978-09-05 | Alza Corporation | Osmotic system with means for improving delivery kinetics of system |
US4256108A (en) | 1977-04-07 | 1981-03-17 | Alza Corporation | Microporous-semipermeable laminated osmotic system |
US4160452A (en) | 1977-04-07 | 1979-07-10 | Alza Corporation | Osmotic system having laminated wall comprising semipermeable lamina and microporous lamina |
US4164559A (en) | 1977-09-21 | 1979-08-14 | Cornell Research Foundation, Inc. | Collagen drug delivery device |
US4186184A (en) | 1977-12-27 | 1980-01-29 | Alza Corporation | Selective administration of drug with ocular therapeutic system |
US4220152A (en) | 1978-05-08 | 1980-09-02 | Pfizer Inc. | Delivery system |
US4220153A (en) | 1978-05-08 | 1980-09-02 | Pfizer Inc. | Controlled release delivery system |
US4200098A (en) | 1978-10-23 | 1980-04-29 | Alza Corporation | Osmotic system with distribution zone for dispensing beneficial agent |
US4298000A (en) | 1978-11-08 | 1981-11-03 | Minnesota Mining And Manufacturing Company | Fluid dispensing device |
US4300557A (en) * | 1980-01-07 | 1981-11-17 | The United States Of America As Represented By The Secretary Of The Department Of Health And Human Services | Method for treating intraocular malignancies |
ATE9059T1 (en) | 1980-01-28 | 1984-09-15 | Merck & Co. Inc. | SUPPLEMENTS CONTAINING OPHTHALMIC ANHYDRASE INHIBITORS TO REDUCE INTRAOCULAR HYPERTENSION. |
US4309776A (en) | 1980-05-13 | 1982-01-12 | Ramon Berguer | Intravascular implantation device and method of using the same |
US4326525A (en) | 1980-10-14 | 1982-04-27 | Alza Corporation | Osmotic device that improves delivery properties of agent in situ |
US4327725A (en) | 1980-11-25 | 1982-05-04 | Alza Corporation | Osmotic device with hydrogel driving member |
US4484922A (en) | 1981-06-25 | 1984-11-27 | Rosenwald Peter L | Occular device |
US4439198A (en) | 1981-07-09 | 1984-03-27 | University Of Illinois Foundation | Biodegradable ocular insert for controlled delivery of ophthalmic medication |
US4730013A (en) | 1981-10-08 | 1988-03-08 | Merck & Co., Inc. | Biosoluble ocular insert |
US4439196A (en) | 1982-03-18 | 1984-03-27 | Merck & Co., Inc. | Osmotic drug delivery system |
US4475916A (en) | 1982-03-18 | 1984-10-09 | Merck & Co., Inc. | Osmotic drug delivery system |
US4519801A (en) | 1982-07-12 | 1985-05-28 | Alza Corporation | Osmotic device with wall comprising cellulose ether and permeability enhancer |
US4673405A (en) | 1983-03-04 | 1987-06-16 | Alza Corporation | Osmotic system with instant drug availability |
US4883459A (en) | 1983-07-29 | 1989-11-28 | Reynaldo Calderon | Retrograde perfusion |
US4774091A (en) | 1983-10-14 | 1988-09-27 | Sumitomo Pharmaceuticals Company, Ltd. | Long-term sustained-release preparation |
US4627850A (en) | 1983-11-02 | 1986-12-09 | Alza Corporation | Osmotic capsule |
US4777049A (en) | 1983-12-01 | 1988-10-11 | Alza Corporation | Constant release system with pulsed release |
US4634418A (en) | 1984-04-06 | 1987-01-06 | Binder Perry S | Hydrogel seton |
US4851228A (en) | 1984-06-20 | 1989-07-25 | Merck & Co., Inc. | Multiparticulate controlled porosity osmotic |
US4634427A (en) | 1984-09-04 | 1987-01-06 | American Hospital Supply Company | Implantable demand medication delivery assembly |
US5049142A (en) | 1984-11-07 | 1991-09-17 | Herrick Robert S | Intracanalicular implant for horizontal canalicular blockade treatment of the eye |
US5053030A (en) * | 1984-11-07 | 1991-10-01 | Herrick Robert S | Intracanalicular implant for horizontal canalicular blockade treatment of the eye |
US4712550A (en) | 1985-04-08 | 1987-12-15 | Sinnett Kevin B | Retinal tack |
US4693886A (en) | 1985-04-22 | 1987-09-15 | Alza Corporation | Osmotic device with inert core |
US4609374A (en) | 1985-04-22 | 1986-09-02 | Alza Corporation | Osmotic device comprising means for governing initial time of agent release therefrom |
EP0201611A1 (en) | 1985-05-10 | 1986-11-20 | B. Braun-SSC AG | Two cannulae syringe |
FR2582221B1 (en) | 1985-05-21 | 1987-09-25 | Applied Precision Ltd | IMPLANTABLE CHRONIC INJECTION DEVICE FOR A SUBSTANCE, ESPECIALLY THERAPEUTIC |
US4861335A (en) * | 1985-07-26 | 1989-08-29 | Duoject Medical Systems Inc. | Syringe |
US4840615A (en) | 1985-09-30 | 1989-06-20 | Mcghan Medical Corporation | Self-sealing injection reservoir |
US4781675A (en) | 1985-11-27 | 1988-11-01 | White Thomas C | Infusion cannula |
DE3672981D1 (en) * | 1985-11-27 | 1990-08-30 | Thomas C White | TISSUE-IMPLANTABLE LIQUID DISTRIBUTION DEVICE. |
US4959217A (en) | 1986-05-22 | 1990-09-25 | Syntex (U.S.A.) Inc. | Delayed/sustained release of macromolecules |
US5322691A (en) | 1986-10-02 | 1994-06-21 | Sohrab Darougar | Ocular insert with anchoring protrusions |
US5147647A (en) | 1986-10-02 | 1992-09-15 | Sohrab Darougar | Ocular insert for the fornix |
US4863457A (en) | 1986-11-24 | 1989-09-05 | Lee David A | Drug delivery device |
DE3751871D1 (en) | 1986-12-23 | 1996-09-19 | Liposome Co Inc | Liposomes containing guanidine aminoglycoside |
US4781680A (en) | 1987-03-02 | 1988-11-01 | Vir Engineering | Resealable injection site |
US4853229A (en) | 1987-10-26 | 1989-08-01 | Alza Corporation | Method for adminstering tiny pills |
JP2702953B2 (en) * | 1988-01-30 | 1998-01-26 | オリンパス光学工業株式会社 | Chemical impregnated ceramics |
US4865846A (en) | 1988-06-03 | 1989-09-12 | Kaufman Herbert E | Drug delivery system |
US5174999A (en) | 1988-12-13 | 1992-12-29 | Alza Corporation | Delivery system comprising fluid ingress and drug egress |
AU4951690A (en) | 1988-12-30 | 1990-08-01 | David M. Anderson | Stabilized microporous materials and hydrogel materials |
US5141748A (en) | 1989-02-17 | 1992-08-25 | Hoffmann-La Roche, Inc. | Implant drug delivery device |
US5098443A (en) | 1989-03-23 | 1992-03-24 | University Of Miami | Method of implanting intraocular and intraorbital implantable devices for the controlled release of pharmacological agents |
US4979938A (en) | 1989-05-11 | 1990-12-25 | Iomed, Inc. | Method of iontophoretically treating acne, furuncles and like skin disorders |
US5164188A (en) | 1989-11-22 | 1992-11-17 | Visionex, Inc. | Biodegradable ocular implants |
US5092837A (en) | 1989-12-20 | 1992-03-03 | Robert Ritch | Method for the treatment of glaucoma |
US5171270A (en) | 1990-03-29 | 1992-12-15 | Herrick Robert S | Canalicular implant having a collapsible flared section and method |
US5324280A (en) | 1990-04-02 | 1994-06-28 | Alza Corporation | Osmotic dosage system for delivering a formulation comprising liquid carrier and drug |
US5128145A (en) | 1990-06-13 | 1992-07-07 | Alza Corporation | Dosage form for Parkinson's disease, spasticity and muscle spasms |
US5238687A (en) | 1990-07-11 | 1993-08-24 | Alza Corporation | Delivery device with a protective sleeve |
US5084021A (en) | 1990-11-02 | 1992-01-28 | Baldwin Brian E | Patient controlled infusion apparatus and method |
US5378475A (en) * | 1991-02-21 | 1995-01-03 | University Of Kentucky Research Foundation | Sustained release drug delivery devices |
AU650113B2 (en) | 1991-04-05 | 1994-06-09 | Eli Lilly And Company | Sustained release capsule and formulations |
US5334189A (en) | 1991-06-03 | 1994-08-02 | Wade Stephen E | Device for controlled diffusion of a chemical substance |
US5213576A (en) * | 1991-06-11 | 1993-05-25 | Cordis Corporation | Therapeutic porous balloon catheter |
US5282829A (en) | 1991-08-15 | 1994-02-01 | United States Surgical Corporation | Hollow body implants |
FR2682090B1 (en) | 1991-10-03 | 1993-12-31 | Holzstoff Holding Sa | RESERVOIR SYSTEM FOR EXTENDED BROADCASTING OF AN ACTIVE INGREDIENT. |
US5681572A (en) | 1991-10-18 | 1997-10-28 | Seare, Jr.; William J. | Porous material product and process |
US5830492A (en) | 1992-02-24 | 1998-11-03 | Encelle, Inc. | Bioartificial devices and cellular matrices therefor |
US5178635A (en) | 1992-05-04 | 1993-01-12 | Allergan, Inc. | Method for determining amount of medication in an implantable device |
US6096756A (en) | 1992-09-21 | 2000-08-01 | Albert Einstein College Of Medicine Of Yeshiva University | Method of simultaneously enhancing analgesic potency and attenuating dependence liability caused by morphine and other bimodally-acting opioid agonists |
US5336175A (en) | 1992-10-29 | 1994-08-09 | Mames Robert N | Method for the treatment of retinal detachments |
US5576480A (en) | 1992-11-06 | 1996-11-19 | Pall Corporation | System and method for testing the integrity of porous elements |
US5443505A (en) * | 1993-11-15 | 1995-08-22 | Oculex Pharmaceuticals, Inc. | Biocompatible ocular implants |
CA2140053C (en) | 1994-02-09 | 2000-04-04 | Joel S. Rosenblatt | Collagen-based injectable drug delivery system and its use |
US5985328A (en) | 1994-03-07 | 1999-11-16 | Regents Of The University Of California | Micromachined porous membranes with bulk support |
US5770076A (en) | 1994-03-07 | 1998-06-23 | The Regents Of The University Of California | Micromachined capsules having porous membranes and bulk supports |
US5516522A (en) | 1994-03-14 | 1996-05-14 | Board Of Supervisors Of Louisiana State University | Biodegradable porous device for long-term drug delivery with constant rate release and method of making the same |
US5578042A (en) * | 1994-03-14 | 1996-11-26 | Cumming; J. Stuart | Ophthalmic kit and method for lens insertion |
US5466233A (en) | 1994-04-25 | 1995-11-14 | Escalon Ophthalmics, Inc. | Tack for intraocular drug delivery and method for inserting and removing same |
AUPM897594A0 (en) | 1994-10-25 | 1994-11-17 | Daratech Pty Ltd | Controlled release container |
CA2204789C (en) | 1994-11-10 | 2002-11-12 | Paul Ashton | Implantable refillable controlled release device to deliver drugs directly to an internal portion of the body |
US5725493A (en) | 1994-12-12 | 1998-03-10 | Avery; Robert Logan | Intravitreal medicine delivery |
US5704915A (en) | 1995-02-14 | 1998-01-06 | Therex Limited Partnership | Hemodialysis access device |
US5554132A (en) | 1995-03-30 | 1996-09-10 | Abbott Laboratories | Hand grip for use with syringe |
US5651979A (en) | 1995-03-30 | 1997-07-29 | Gel Sciences, Inc. | Apparatus and method for delivering a biologically active compound into a biological environment |
CN1283324C (en) * | 1995-05-14 | 2006-11-08 | 奥普通诺尔有限公司 | Intraocular implant, delivery device, and method of implantation |
IL113723A (en) | 1995-05-14 | 2002-11-10 | Optonol Ltd | Intraocular implant |
US5609629A (en) | 1995-06-07 | 1997-03-11 | Med Institute, Inc. | Coated implantable medical device |
US5989216A (en) | 1995-06-29 | 1999-11-23 | Sims Deltec, Inc. | Access portal and method |
US6685940B2 (en) | 1995-07-27 | 2004-02-03 | Genentech, Inc. | Protein formulation |
US5773019A (en) | 1995-09-27 | 1998-06-30 | The University Of Kentucky Research Foundation | Implantable controlled release device to deliver drugs directly to an internal portion of the body |
US6283951B1 (en) | 1996-10-11 | 2001-09-04 | Transvascular, Inc. | Systems and methods for delivering drugs to selected locations within the body |
US6641708B1 (en) | 1996-01-31 | 2003-11-04 | Board Of Regents, The University Of Texas System | Method and apparatus for fractionation using conventional dielectrophoresis and field flow fractionation |
GB2310149A (en) | 1996-02-15 | 1997-08-20 | Nomix Chipman Ltd | Spray gun |
US5904144A (en) | 1996-03-22 | 1999-05-18 | Cytotherapeutics, Inc. | Method for treating ophthalmic diseases |
US5951512A (en) | 1996-05-28 | 1999-09-14 | Horizon Medical Products, Inc. | Infusion port with modified drug reservoir |
US5797898A (en) | 1996-07-02 | 1998-08-25 | Massachusetts Institute Of Technology | Microchip drug delivery devices |
US5928662A (en) * | 1996-07-31 | 1999-07-27 | Phillips; Andrew F. | Ocular drug delivery device |
AU7533696A (en) | 1996-12-13 | 1998-06-18 | Ciba-Geigy Ag | New materials |
ATE246489T1 (en) | 1997-03-31 | 2003-08-15 | Alza Corp | IMPLANTABLE DIFFUSION DELIVERY SYSTEM |
US7160687B1 (en) | 1997-05-29 | 2007-01-09 | Cellomics, Inc. | Miniaturized cell array methods and apparatus for cell-based screening |
US5968008A (en) | 1997-08-04 | 1999-10-19 | Grams; Guenter A. | Cannula with parallel channels and sliding sheath |
US6306426B1 (en) | 1997-08-11 | 2001-10-23 | Allergan Sales, Inc. | Implant device with a retinoid for improved biocompatibility |
US5902598A (en) * | 1997-08-28 | 1999-05-11 | Control Delivery Systems, Inc. | Sustained release drug delivery devices |
US6183461B1 (en) | 1998-03-11 | 2001-02-06 | Situs Corporation | Method for delivering a medication |
US6331523B1 (en) | 1998-03-12 | 2001-12-18 | Genentech, Inc. | Method of enhancing the survival of retinal neurons and treating ocular diseases using FGF-5 |
US6196993B1 (en) | 1998-04-20 | 2001-03-06 | Eyelab Group, Llc | Ophthalmic insert and method for sustained release of medication to the eye |
US5993414A (en) | 1998-04-23 | 1999-11-30 | Medtronic, Inc. | Implantable device |
FR2784296B1 (en) | 1998-09-18 | 2001-01-05 | Imedex Biomateriaux | DEVICE FOR FORMULATING AND DELIVERING A MIXTURE, PARTICULARLY FOR THE SURGICAL APPLICATION OF THIS MIXTURE |
US7973068B2 (en) | 1998-10-20 | 2011-07-05 | Omeros Corporation | Arthroscopic irrigation solution and method for peripheral vasoconstriction and inhibition of pain and inflammation |
DE69917484T2 (en) | 1998-12-14 | 2005-05-12 | Tre Esse Progettazione Biomedica S.R.L. | CATHETER SYSTEM FOR CARRYING OUT INTRAMYOCARDIAL THERAPEUTIC TREATMENT |
DE19948783C2 (en) | 1999-02-18 | 2001-06-13 | Alcove Surfaces Gmbh | Implant |
US7914442B1 (en) | 1999-03-01 | 2011-03-29 | Gazdzinski Robert F | Endoscopic smart probe and method |
US20050119601A9 (en) | 1999-04-26 | 2005-06-02 | Lynch Mary G. | Shunt device and method for treating glaucoma |
US6395300B1 (en) | 1999-05-27 | 2002-05-28 | Acusphere, Inc. | Porous drug matrices and methods of manufacture thereof |
US6472162B1 (en) | 1999-06-04 | 2002-10-29 | Thermogenesis Corp. | Method for preparing thrombin for use in a biological glue |
AU770975B2 (en) | 1999-06-18 | 2004-03-11 | Alcon Laboratories, Inc. | Topical ophthalmic mast cell stabilizers for treating allergic eye diseases |
US6551291B1 (en) | 1999-08-04 | 2003-04-22 | Johns Hopkins University | Non-traumatic infusion cannula and treatment methods using same |
US6638263B1 (en) | 1999-10-12 | 2003-10-28 | Durect Corporation | Regulation of drug delivery through flow diversion |
WO2001028472A1 (en) | 1999-10-21 | 2001-04-26 | Alcon Universal Ltd. | Drug delivery device |
US6416777B1 (en) | 1999-10-21 | 2002-07-09 | Alcon Universal Ltd. | Ophthalmic drug delivery device |
US6331313B1 (en) | 1999-10-22 | 2001-12-18 | Oculex Pharmaceticals, Inc. | Controlled-release biocompatible ocular drug delivery implant devices and methods |
IL150630A0 (en) | 2000-01-12 | 2003-02-12 | Becton Dickinson Co | Systems and methods for reducing intraocular pressure |
US20050119737A1 (en) | 2000-01-12 | 2005-06-02 | Bene Eric A. | Ocular implant and methods for making and using same |
US20030212383A1 (en) | 2001-01-05 | 2003-11-13 | Dana Cote | System and methods for reducing intraocular pressure |
DE10008826C2 (en) | 2000-02-25 | 2002-03-14 | Disetronic Licensing Ag | Micro perfusion device with collection container |
US7077848B1 (en) | 2000-03-11 | 2006-07-18 | John Hopkins University | Sutureless occular surgical methods and instruments for use in such methods |
EP1186439A4 (en) | 2000-03-13 | 2004-12-08 | Seiko Epson Corp | Method for surface treatment, surface-treated article and device for surface treatment |
US7141152B2 (en) | 2000-03-16 | 2006-11-28 | Le Febre David A | Analyte species separation system |
US6945969B1 (en) | 2000-03-31 | 2005-09-20 | Medtronic, Inc. | Catheter for target specific drug delivery |
US7708711B2 (en) | 2000-04-14 | 2010-05-04 | Glaukos Corporation | Ocular implant with therapeutic agents and methods thereof |
US20040208910A1 (en) | 2000-04-26 | 2004-10-21 | Control Delivery Systems, Inc. | Sustained release device and method for ocular delivery of adrenergic agents |
US6375972B1 (en) * | 2000-04-26 | 2002-04-23 | Control Delivery Systems, Inc. | Sustained release drug delivery devices, methods of use, and methods of manufacturing thereof |
DE60135352D1 (en) | 2000-08-30 | 2008-09-25 | Univ Johns Hopkins | DEVICE FOR INTRA-OCCULAR ACTIVE AGGREGATION |
WO2002019992A2 (en) | 2000-09-06 | 2002-03-14 | Alcon, Inc. | Switchable tackiness coating compositions for ophthalmic implants |
US6303290B1 (en) | 2000-09-13 | 2001-10-16 | The Trustees Of The University Of Pennsylvania | Encapsulation of biomaterials in porous glass-like matrices prepared via an aqueous colloidal sol-gel process |
CA2434156A1 (en) | 2000-12-29 | 2002-07-25 | Bausch & Lomb Incorporated | Sustained release drug delivery devices |
US6756058B2 (en) | 2001-01-03 | 2004-06-29 | Bausch & Lomb Incorporated | Sustained release drug delivery devices with multiple agents |
US6964781B2 (en) | 2001-01-03 | 2005-11-15 | Bausch & Lomb Incorporated | Sustained release drug delivery devices with prefabricated permeable plugs |
US20020086051A1 (en) | 2001-01-03 | 2002-07-04 | Santos Viscasillas | Sustained release drug delivery devices with coated drug cores |
AU2002241834B2 (en) | 2001-01-09 | 2006-11-09 | Microchips, Inc. | Flexible microchip devices for opthalmic and other applications |
US6872198B1 (en) | 2001-01-24 | 2005-03-29 | Arrow International, Inc. | Double-y-shaped multi-lumen catheter with selectively attachable hubs |
WO2002058667A2 (en) | 2001-01-26 | 2002-08-01 | Bausch & Lomb Incorporated | Improved process for the production of sustained release drug delivery devices |
US7181287B2 (en) | 2001-02-13 | 2007-02-20 | Second Sight Medical Products, Inc. | Implantable drug delivery device |
US6713081B2 (en) | 2001-03-15 | 2004-03-30 | The United States Of America As Represented By The Department Of Health And Human Services | Ocular therapeutic agent delivery devices and methods for making and using such devices |
DE60239868D1 (en) | 2001-06-12 | 2011-06-09 | Univ Johns Hopkins Med | RESERVOIR DEVICE FOR INTRAOCULAR DRUG DELIVERY |
KR100892333B1 (en) | 2001-07-10 | 2009-04-08 | 테바 파마슈티컬 인더스트리즈 리미티드 | Drug delivery system for zero order, zero order-biphasic, ascending or descending drug delivery |
IL144446A0 (en) | 2001-07-19 | 2002-05-23 | Prochon Biotech Ltd | Plasma protein matrices and methods for their preparation |
DK1409065T3 (en) | 2001-07-23 | 2007-05-21 | Alcon Inc | Ophthalmic drug delivery device |
BR0210287A (en) | 2001-07-23 | 2005-12-13 | Alcon Inc | Ophthalmic drug delivery device |
BR0215382A (en) | 2001-08-03 | 2005-05-17 | Glaucoma Res Tecnologies Inc | Intrasclerotic Method and Implant for the Treatment of Glaucoma and Presbyopia |
US7749528B2 (en) | 2001-08-29 | 2010-07-06 | Ricardo Azevedo Pontes De Carvalho | Implantable and sealable medical device for unidirectional delivery of therapeutic agents to tissues |
RU2311892C2 (en) | 2001-08-29 | 2007-12-10 | КАРВАЛХО Рикардо А. П. ДЕ | Implantable sealable system for one-way delivery of therapeutic preparations to tissues |
KR20110025239A (en) | 2001-09-28 | 2011-03-09 | 산텐 세이야꾸 가부시키가이샤 | Injections for eye tissue containing drug bound to polyethylene glycol |
AU2002341959A1 (en) | 2001-10-04 | 2003-04-14 | Case Western Reserve University | Drug delivery devices and methods |
US8663687B2 (en) | 2001-10-12 | 2014-03-04 | Monosol Rx, Llc | Film compositions for delivery of actives |
EP1444338A4 (en) | 2001-11-15 | 2007-07-04 | Arryx Inc | Sample chip |
GB2399753B (en) | 2002-01-18 | 2006-04-19 | Michael E Snyder | Method of making a sustained release ophthalmological device |
KR101191254B1 (en) | 2002-03-11 | 2012-10-16 | 알콘, 인코퍼레이티드 | Implantable drug delivery system |
US7074426B2 (en) | 2002-03-27 | 2006-07-11 | Frank Kochinke | Methods and drug delivery systems for the treatment of orofacial diseases |
US7968569B2 (en) | 2002-05-17 | 2011-06-28 | Celgene Corporation | Methods for treatment of multiple myeloma using 3-(4-amino-1-oxo-1,3-dihydro-isoindol-2-yl)-piperidine-2,6-dione |
US7939094B2 (en) | 2002-06-19 | 2011-05-10 | Boston Scientific Scimed, Inc. | Multiphase polymeric drug release region |
US20040019325A1 (en) | 2002-07-29 | 2004-01-29 | Medrip Ltd. | Syringe Pump |
US7468065B2 (en) | 2002-09-18 | 2008-12-23 | Allergan, Inc. | Apparatus for delivery of ocular implants |
US7094222B1 (en) | 2003-04-28 | 2006-08-22 | The United States Of America As Represented By The Secretary Of Navy | Syringe device for simultaneous infusion and withdrawal |
US20110076278A1 (en) | 2005-08-02 | 2011-03-31 | Mehran Khodadoust | Modulators of Hypoxia Inducible Factor-1 and Related Uses for the Treatment of Ocular Disorders |
US20070212397A1 (en) | 2005-09-15 | 2007-09-13 | Roth Daniel B | Pharmaceutical delivery device and method for providing ocular treatment |
AU2007237905A1 (en) | 2006-04-18 | 2007-10-25 | Cascade Ophthalmics | Intraocular pressure attenuation device |
CA2674076A1 (en) | 2006-12-26 | 2008-07-10 | Qlt Plug Delivery, Inc. | Drug delivery implants for inhibition of optical defects |
WO2008137236A2 (en) | 2007-04-30 | 2008-11-13 | Alcon Research, Ltd. | Treatment of age-related macular degeneration using inhibitors of complement factor d |
US7901726B2 (en) | 2007-08-31 | 2011-03-08 | Boston Scientific Scimed, Inc. | Porous medical articles for therapeutic agent delivery |
GB0718737D0 (en) | 2007-09-25 | 2007-11-07 | Glaxo Group Ltd | Antibodies |
US20100100043A1 (en) | 2007-10-05 | 2010-04-22 | Racenet Danyel J | Flexible Access Device For Use In Surgical Procedure |
MX2011006726A (en) | 2009-01-02 | 2011-07-20 | Alcon Res Ltd | In-situ refillable ophthalmic implant. |
EP4289416A3 (en) | 2009-05-18 | 2024-01-03 | Dose Medical Corporation | Drug eluting ocular implant |
US8821474B2 (en) | 2010-02-22 | 2014-09-02 | Microsert Ltd. | Slow release liquid drug delivery device |
US8038650B2 (en) | 2010-02-22 | 2011-10-18 | Microsert Ltd. | Slow release liquid drug delivery device |
-
2002
- 2002-06-12 DE DE60239868T patent/DE60239868D1/en not_active Expired - Lifetime
- 2002-06-12 US US10/171,406 patent/US7883717B2/en active Active
- 2002-06-12 WO PCT/US2002/018642 patent/WO2002100318A2/en active Application Filing
- 2002-06-12 JP JP2003503145A patent/JP4677538B2/en not_active Expired - Lifetime
- 2002-06-12 EP EP02734784A patent/EP1404297B1/en not_active Expired - Lifetime
- 2002-06-12 AT AT02734784T patent/ATE506929T1/en not_active IP Right Cessation
- 2002-06-12 CA CA2450771A patent/CA2450771C/en not_active Expired - Lifetime
- 2002-06-12 EP EP10184729.1A patent/EP2316394B1/en not_active Expired - Lifetime
-
2010
- 2010-07-09 JP JP2010157037A patent/JP5416048B2/en not_active Expired - Lifetime
- 2010-12-27 US US12/979,185 patent/US8486052B2/en not_active Expired - Lifetime
-
2012
- 2012-01-10 JP JP2012002591A patent/JP2012096056A/en not_active Ceased
-
2013
- 2013-07-15 US US13/942,610 patent/US9180046B2/en not_active Expired - Fee Related
- 2013-09-10 JP JP2013187604A patent/JP5896966B2/en not_active Expired - Lifetime
-
2014
- 2014-05-02 US US14/268,723 patent/US20140243795A1/en not_active Abandoned
-
2016
- 2016-03-03 US US15/060,532 patent/US9522082B2/en not_active Expired - Lifetime
- 2016-12-01 US US15/366,982 patent/US20170172794A1/en not_active Abandoned
-
2017
- 2017-10-11 US US15/730,537 patent/US10470924B2/en not_active Expired - Fee Related
Cited By (39)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
US11744734B2 (en) | 2007-09-24 | 2023-09-05 | Alcon Inc. | Method of implanting an ocular implant |
US11504275B2 (en) | 2008-03-05 | 2022-11-22 | Alcon Inc. | Methods and apparatus for treating glaucoma |
US10537474B2 (en) | 2008-03-05 | 2020-01-21 | Ivantis, Inc. | Methods and apparatus for treating glaucoma |
US10656152B2 (en) | 2009-01-29 | 2020-05-19 | Forsight Vision4, Inc. | Posterior segment drug delivery |
US11642310B2 (en) | 2009-01-29 | 2023-05-09 | Forsight Vision4, Inc. | Posterior segment drug delivery |
US11596546B2 (en) | 2009-07-09 | 2023-03-07 | Alcon Inc. | Ocular implants and methods for delivering ocular implants into the eye |
US10492949B2 (en) | 2009-07-09 | 2019-12-03 | Ivantis, Inc. | Single operator device for delivering an ocular implant |
US10406025B2 (en) | 2009-07-09 | 2019-09-10 | Ivantis, Inc. | Ocular implants and methods for delivering ocular implants into the eye |
US11918514B2 (en) | 2009-07-09 | 2024-03-05 | Alcon Inc. | Single operator device for delivering an ocular implant |
US11464675B2 (en) | 2009-07-09 | 2022-10-11 | Alcon Inc. | Single operator device for delivering an ocular implant |
US11679027B2 (en) | 2010-08-05 | 2023-06-20 | Forsight Vision4, Inc. | Combined drug delivery methods and apparatus |
US11786396B2 (en) | 2010-08-05 | 2023-10-17 | Forsight Vision4, Inc. | Injector apparatus and method for drug delivery |
US10874548B2 (en) | 2010-11-19 | 2020-12-29 | Forsight Vision4, Inc. | Therapeutic agent formulations for implanted devices |
US11065151B2 (en) | 2010-11-19 | 2021-07-20 | Forsight Vision4, Inc. | Therapeutic agent formulations for implanted devices |
US10363168B2 (en) | 2011-06-14 | 2019-07-30 | Ivantis, Inc. | Ocular implants for delivery into the eye |
US11813196B2 (en) | 2011-06-28 | 2023-11-14 | Forsight Vision4, Inc. | Diagnostic methods and apparatus |
US10653554B2 (en) | 2011-09-16 | 2020-05-19 | Forsight Vision4, Inc. | Fluid exchange apparatus and methods |
US11135088B2 (en) | 2011-12-19 | 2021-10-05 | Ivantis Inc. | Delivering ocular implants into the eye |
US9931243B2 (en) | 2011-12-19 | 2018-04-03 | Ivantis, Inc. | Delivering ocular implants into the eye |
US10603209B2 (en) | 2012-02-03 | 2020-03-31 | Forsight Vision4, Inc. | Insertion and removal methods and apparatus for therapeutic devices |
US11026836B2 (en) | 2012-04-18 | 2021-06-08 | Ivantis, Inc. | Ocular implants for delivery into an anterior chamber of the eye |
US11992437B2 (en) | 2012-04-18 | 2024-05-28 | Alcon Inc. | Ocular implants for delivery into an anterior chamber of the eye |
US11712369B2 (en) | 2012-11-28 | 2023-08-01 | Alcon Inc. | Apparatus for delivering ocular implants into an anterior chamber of the eye |
US10617558B2 (en) | 2012-11-28 | 2020-04-14 | Ivantis, Inc. | Apparatus for delivering ocular implants into an anterior chamber of the eye |
US10709547B2 (en) | 2014-07-14 | 2020-07-14 | Ivantis, Inc. | Ocular implant delivery system and method |
US11337853B2 (en) | 2014-07-15 | 2022-05-24 | Forsight Vision4, Inc. | Ocular implant delivery device and method |
US10765677B2 (en) | 2014-08-08 | 2020-09-08 | Forsight Vision4, Inc. | Stable and soluble formulations of receptor tyrosine kinase inhibitors, and methods of preparation thereof |
US11617644B2 (en) | 2014-10-13 | 2023-04-04 | W. L. Gore & Associates, Inc. | Prosthetic valved conduit |
US11110001B2 (en) | 2014-11-10 | 2021-09-07 | Forsight Vision4, Inc. | Expandable drug delivery devices and methods of use |
US11197779B2 (en) | 2015-08-14 | 2021-12-14 | Ivantis, Inc. | Ocular implant with pressure sensor and delivery system |
US11432959B2 (en) | 2015-11-20 | 2022-09-06 | Forsight Vision4, Inc. | Porous structures for extended release drug delivery devices |
US11938058B2 (en) | 2015-12-15 | 2024-03-26 | Alcon Inc. | Ocular implant and delivery system |
US11617680B2 (en) | 2016-04-05 | 2023-04-04 | Forsight Vision4, Inc. | Implantable ocular drug delivery devices |
US11523940B2 (en) | 2017-03-17 | 2022-12-13 | W. L. Gore & Associates, Inc. | Delivery aids for glaucoma shunts |
US11406533B2 (en) | 2017-03-17 | 2022-08-09 | W. L. Gore & Associates, Inc. | Integrated aqueous shunt for glaucoma treatment |
US11351058B2 (en) | 2017-03-17 | 2022-06-07 | W. L. Gore & Associates, Inc. | Glaucoma treatment systems and methods |
US11419759B2 (en) | 2017-11-21 | 2022-08-23 | Forsight Vision4, Inc. | Fluid exchange apparatus for expandable port delivery system and methods of use |
US11678983B2 (en) | 2018-12-12 | 2023-06-20 | W. L. Gore & Associates, Inc. | Implantable component with socket |
US11540940B2 (en) | 2021-01-11 | 2023-01-03 | Alcon Inc. | Systems and methods for viscoelastic delivery |
Also Published As
Publication number | Publication date |
---|---|
US9522082B2 (en) | 2016-12-20 |
WO2002100318A3 (en) | 2003-11-20 |
JP5416048B2 (en) | 2014-02-12 |
ATE506929T1 (en) | 2011-05-15 |
EP1404297A4 (en) | 2004-07-14 |
WO2002100318A2 (en) | 2002-12-19 |
JP2012096056A (en) | 2012-05-24 |
US20160184134A1 (en) | 2016-06-30 |
US20110098686A1 (en) | 2011-04-28 |
CA2450771A1 (en) | 2002-12-19 |
EP2316394B1 (en) | 2016-11-23 |
US20180243131A1 (en) | 2018-08-30 |
JP4677538B2 (en) | 2011-04-27 |
CA2450771C (en) | 2010-09-07 |
JP2010264273A (en) | 2010-11-25 |
US8486052B2 (en) | 2013-07-16 |
EP2316394A1 (en) | 2011-05-04 |
US20130304031A1 (en) | 2013-11-14 |
US9180046B2 (en) | 2015-11-10 |
US7883717B2 (en) | 2011-02-08 |
US20030014036A1 (en) | 2003-01-16 |
EP1404297A2 (en) | 2004-04-07 |
JP5896966B2 (en) | 2016-03-30 |
US10470924B2 (en) | 2019-11-12 |
DE60239868D1 (en) | 2011-06-09 |
US20140243795A1 (en) | 2014-08-28 |
EP1404297B1 (en) | 2011-04-27 |
JP2005500097A (en) | 2005-01-06 |
JP2014039834A (en) | 2014-03-06 |
Similar Documents
Publication | Publication Date | Title |
---|---|---|
US10470924B2 (en) | Reservoir device for intraocular drug delivery | |
EP1313415B1 (en) | Devices for intraocular drug delivery | |
AU2001271417A1 (en) | Devices for intraocular drug delivery | |
ES2538838T3 (en) | Method for preparing drug inserts for sustained release of therapeutic agents | |
US20230000676A1 (en) | Fluid exchange apparatus for expandable port delivery system and methods of use | |
US20230225903A1 (en) | Implantable ocular drug delivery devices | |
AU2002306153B2 (en) | Reservoir device for intraocular drug delivery | |
AU2002306153A1 (en) | Reservoir device for intraocular drug delivery |
Legal Events
Date | Code | Title | Description |
---|---|---|---|
AS | Assignment |
Owner name: THE JOHNS HOPKINS UNIVERSITY, MARYLAND Free format text: ASSIGNMENT OF ASSIGNORS INTEREST;ASSIGNORS:VARNER, SIGNE ERICKSON;DE JUAN, EUGENE;BARNES, AARON CHRISTOPHER;AND OTHERS;SIGNING DATES FROM 20020815 TO 20020910;REEL/FRAME:042254/0864 |
|
STCB | Information on status: application discontinuation |
Free format text: ABANDONED -- FAILURE TO RESPOND TO AN OFFICE ACTION |