WO2012068115A2 - Dérivations intraoculaires et procédés pour placer une dérivation intraoculaire dans l'espace intra-tenon - Google Patents

Dérivations intraoculaires et procédés pour placer une dérivation intraoculaire dans l'espace intra-tenon Download PDF

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Publication number
WO2012068115A2
WO2012068115A2 PCT/US2011/060798 US2011060798W WO2012068115A2 WO 2012068115 A2 WO2012068115 A2 WO 2012068115A2 US 2011060798 W US2011060798 W US 2011060798W WO 2012068115 A2 WO2012068115 A2 WO 2012068115A2
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WO
WIPO (PCT)
Prior art keywords
shunt
eye
intraocular
hollow shaft
tenon
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Application number
PCT/US2011/060798
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English (en)
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WO2012068115A3 (fr
Inventor
Christopher Horvath
Laszlo O. Romoda
Ronald D. Bache
Richard A. Lewis
Original Assignee
Aquesys, Inc.
Priority date (The priority date is an assumption and is not a legal conclusion. Google has not performed a legal analysis and makes no representation as to the accuracy of the date listed.)
Filing date
Publication date
Priority claimed from US12/946,572 external-priority patent/US8852256B2/en
Priority claimed from US12/946,542 external-priority patent/US20120123316A1/en
Application filed by Aquesys, Inc. filed Critical Aquesys, Inc.
Publication of WO2012068115A2 publication Critical patent/WO2012068115A2/fr
Publication of WO2012068115A3 publication Critical patent/WO2012068115A3/fr

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Classifications

    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61F—FILTERS IMPLANTABLE INTO BLOOD VESSELS; PROSTHESES; DEVICES PROVIDING PATENCY TO, OR PREVENTING COLLAPSING OF, TUBULAR STRUCTURES OF THE BODY, e.g. STENTS; ORTHOPAEDIC, NURSING OR CONTRACEPTIVE DEVICES; FOMENTATION; TREATMENT OR PROTECTION OF EYES OR EARS; BANDAGES, DRESSINGS OR ABSORBENT PADS; FIRST-AID KITS
    • 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
    • A61F9/007—Methods or devices for eye surgery
    • A61F9/00781—Apparatus for modifying intraocular pressure, e.g. for glaucoma treatment

Definitions

  • the present invention generally relates to devices and methods for reducing intraocular pressure by creating a drainage pathway between the anterior chamber of the eye and the intra- Tenon's space.
  • Glaucoma is a disease in which the optic nerve is damaged, leading to progressive, irreversible loss of vision. It is typically associated with increased pressure of the fluid (i.e., aqueous humor) in the eye. Untreated glaucoma leads to permanent damage of the optic nerve and resultant visual field loss, which can progress to blindness. Once lost, this damaged visual field cannot be recovered. Glaucoma affects 1 in 200 people aged fifty and younger, and 1 in 10 over the age of eighty for a total of approximately 70 million people worldwide, and glaucoma is the second leading cause of blindness in the world.
  • IOP intraocular pressure
  • Surgical filtration methods for lowering intraocular pressure by creating a fluid flow-path between the anterior chamber and the subconjunctival tissue have been described.
  • One particular ab interno glaucoma filtration method has been described whereby an intraocular shunt is implanted by directing a needle which holds the shunt through the cornea, across the anterior chamber, and through the trabecular meshwork and sclera, and into the subconjunctival space. See, for example, U.S. patent number 6,544,249, U.S.
  • a healthy conjunctiva allows drainage channels to form and less opportunity for inflammation and scar tissue formation, which are frequent causes of failure in subconjunctival filtration surgery. See, for example, Yu et al., Progress in Retinal and Eye Research, 28: 303-328 (2009).
  • the present invention provides intraocular shunts that are designed to avoid contact with the conjunctiva when deployed into the subconjunctival space.
  • the present invention provides intraocular shunts that are configured to form a drainage pathway between the anterior chamber of the eye and the intra-Tenon's space.
  • shunt inlet i.e., the portion of the shunt that receives fluid from an anterior chamber of the eye
  • shunt outlet i.e., the portion of the shunt that directs fluid to the intra-Tenon's space
  • the intraocular shunts of the invention define a hollow body comprising an inlet and an outlet, and the hollow body is configured to form a passage from the anterior chamber of the eye to the intra-Tenon's space.
  • the hollow body has a length sufficient to provide a passageway between the anterior chamber and the intra-Tenon's space.
  • the invention generally provides shunts composed of a material that has an elasticity modulus that is compatible with an elasticity modulus of tissue surrounding the shunt.
  • shunts of the invention are flexibility matched with the surrounding tissue, and thus will remain in place after implantation without the need for any type of anchor that interacts with the surrounding tissue. Consequently, shunts of the invention will maintain fluid flow away for an anterior chamber of the eye after implantation without causing irritation or inflammation to the tissue surrounding the eye.
  • the invention generally provides shunts in which a portion of the shunt is composed of a flexible material that is reactive to pressure, i.e., an inner diameter of the shunt fluctuates depending upon the pressures exerted on that portion of the shunt.
  • the flexible portion of the shunt acts as a valve that regulates fluid flow through the shunt.
  • intraocular shunts have pressure exerted upon them by tissues surrounding the shunt (e.g., scleral tissue) and pressure exerted upon them by aqueous humor flowing through the shunt.
  • tissues surrounding the shunt e.g., scleral tissue
  • the flexible portion decreases in diameter, restricting flow through the shunt. The restricted flow results in aqueous humor leaving the anterior chamber at a reduced rate.
  • the flexible portion of the shunt may be any portion of the shunt.
  • the flexible portion is a distal portion of the shunt.
  • the entire shunt is composed of the flexible material.
  • the shunt includes a hollow body defining a flow path and more than two ports, in which the body is configured such that a proximal portion receives fluid from the anterior chamber of an eye and a distal portion directs the fluid to a location of lower pressure with respect to the anterior chamber.
  • the shunt may have many different configurations.
  • the proximal portion of the shunt i.e., the portion disposed within the anterior chamber of the eye
  • the distal portion of the shunt i.e., the portion that is located in the intra-Tenon's space
  • the proximal portion includes a single port
  • the distal portion includes more than one port.
  • the proximal and the distal portions include more than one port.
  • the ports may be positioned in various different orientations and along various different portions of the shunt.
  • at least one of the ports is oriented at an angle to the length of the body.
  • at least one of the ports is oriented 90° to the length of the body.
  • the ports may have the same or different inner diameters. In certain embodiments, at least one of the ports has an inner diameter that is different from the inner diameters of the other ports.
  • shunts with overflow ports.
  • Those shunts are configured such that the overflow port remains closed until there is a pressure build- up within the shunt sufficient to force open the overflow port.
  • Such pressure build-up typically results from particulate partially or fully clogging an entry or an exit port of the shunt.
  • Such shunts reduce probability of the shunt clogging after implantation because fluid can enter or exit the shunt by the overflow port even in one port of the shunt becomes clogged with particulate.
  • the shunt includes a hollow body defining an inlet configured to receive fluid from an anterior chamber of the eye and an outlet configured to direct the fluid to a location of lower pressure with respect to the anterior chamber, the body further including at least one slit.
  • the slit may be located at any place along the body of the shunt. In certain embodiments, the slit is located in proximity to the inlet. In other embodiments, the slit is located in proximity to the outlet. In certain embodiments, there is a slit in proximity to both the inlet and the outlet of the shunt.
  • the slit has a width that is substantially the same or less than an inner diameter of the inlet. In other embodiments, the slit has a width that is substantially the same or less than an inner diameter of the outlet.
  • the slit does not direct the fluid unless the outlet is obstructed.
  • the shunt may be configured such that the slit does direct at least some of the fluid even if the inlet or outlet is not obstructed.
  • the invention generally provides a shunt having a variable inner diameter.
  • the diameter increases from inlet to outlet of the shunt.
  • the shunt includes a hollow body defining a flow path and having an inlet configured to receive fluid from an anterior chamber of an eye and an outlet configured to direct the fluid to the intra-Tenon's space, in which the body further includes a variable inner diameter that increases along the length of the body from the inlet to the outlet. In certain embodiments, the inner diameter continuously increases along the length of the body. In other embodiments, the inner diameter remains constant along portions of the length of the body.
  • the present invention also generally relates to methods for deploying intraocular shunts into the subconjunctival space the eye while avoiding or minimizing contact with the
  • the present invention provides methods for deploying an intraocular shunt into the eye such that the shunt forms a drainage pathway from the anterior chamber of the eye to the region of the eye that is bound between the sclera and Tenon's capsule, referred to herein as the intra-Tenon's space.
  • shunt inlet i.e., the portion of the shunt that receives fluid from an anterior chamber of the eye
  • shunt outlet i.e., the portion of the shunt that directs fluid to the intra-Tenon's space
  • the methods of the invention involve inserting into the eye a hollow shaft that is configured to hold an intraocular shunt, deploying the shunt from the shaft such that the shunt forms a passage from the anterior chamber to the intra-Tenon's space, and withdrawing the hollow shaft from the eye.
  • the hollow shaft may hold the shunt within the interior of hollow shaft.
  • the hollow shaft may hold the shunt on an outer surface of the shaft.
  • the methods of the invention involve the use of a hollow shaft configured to hold an intraocular shunt, as previously described, wherein a portion of the hollow shaft extends linearly along a longitudinal axis and at least one other portion of the shaft extends off the longitudinal axis, to insert and deploy the intraocular shunt into the eye such that the shunt forms a passage from the anterior chamber to the intra-Tenon's space.
  • an aqueous fluid is injected into the eye simultaneously with or prior to the insertion and deployment steps of the methods of the invention.
  • an aqueous solution may be injected below Tenon's capsule to balloon the capsule away from the sclera and allow positioning of the intraocular shunt in the intra-Tenon's space.
  • Methods of the invention are typically conducted using an ab interno approach by inserting the hollow shaft configured to hold the intraocular shunt through the cornea, across the anterior chamber, through the sclera and into the intra-Tenon's space.
  • an ab interno approach which involves inserting the shaft from the outside of the eye through the conjunctiva and inward through the sclera to reach a drainage structure such Schlemm's canal.
  • methods of the invention may be conducted using an ab externo approach.
  • Methods of the invention may be performed such that the shaft is inserted above or below the corneal limbus. Methods of the invention may also be performed such that the shaft is inserted into the eye without removing an anatomical feature of the eye, such as the trabecular meshwork, the iris, the cornea, or the aqueous humor. In certain embodiments, methods of the invention may be conducted without inducing substantial ocular inflammation such as, for example, subconjunctival blebbing or endophthalmitis. In other certain embodiments, methods of the invention may be conducted without the use of an optical apparatus, particularly an optical apparatus that directly contacts the eye, such as a goniolens. In yet other certain embodiments, the methods of the invention may be conducted using an optical apparatus that does not directly contact the eye, such as an ophthalmic microscope.
  • Figure 1 provides a cross-sectional diagram of the general anatomy of the eye.
  • Figure 2 provides another cross-sectional view the eye, and certain anatomical structures of the eye.
  • Figure 3 depicts, implantation of an intraocular shunt with a distal end of a deployment device holding a shunt, shown in cross-section.
  • Figure 4 depicts an example of a hollow shaft configured to hold an intraocular shunt.
  • Figure 5A depicts a hollow shaft having a bend in a distal portion of the shaft.
  • Figure 5B depicts a hollow shaft having a U-shape.
  • Figure 5C depicts a hollow shaft having a V-shape.
  • Figure 6A depicts a simulation of the exit site distance from the limbus and height above the iris after needle entry at the limbus using an ab interno procedure.
  • Figure 6B depicts a simulation of the exit site distance from the limbus and height above the iris after needle entry above the limbus using an ab interno procedure.
  • Figure 7 A depicts the tip bevel portion of a triple-ground needle tip.
  • Figure 7B depicts the flat bevel portion of a triple-ground needle tip.
  • Figure 7C depicts an intraocular shunt within a triple-ground needle tip.
  • Figure 7D depicts 100% penetration of the flat bevel portion of a triple-ground needle tip through the sclera of an eye.
  • Figure 8A depicts an intraocular shunt inserted into the scleral channel using a beveled needle tip to completely penetrate the scleral tissue prior to insertion of the shunt.
  • Figure 8B depicts an intraocular shunt inserted into the scleral channel using a beveled needle tip to partially penetrate the scleral tissue prior to insertion of the shunt.
  • Figure 9 provides a schematic of a shunt having a flexible portion.
  • Figures 10A, 10B and IOC provide schematics of a shunt implanted into an eye for regulation of fluid flow from the anterior chamber of the eye to a drainage structure of the eye.
  • Figure 11 shows different embodiments of multi-port shunts.
  • Figure 11 A shows an embodiment of a shunt in which the proximal portion of the shunt includes more than one port and the distal portion of the shunt includes a single port.
  • Figure 1 IB shows another embodiment of a shunt in which the proximal portion includes a single port and the distal portion includes more than one port.
  • Figure 11C shows another embodiment of a shunt in which the proximal portions include more than one port and the distal portions include more than one port.
  • Figures 12A and 12B show different embodiments of multi-port shunts having different diameter ports.
  • Figures 13 A, 13B and 13C provide schematics of shunts having a slit located along a portion of the length of the shunt.
  • Figure 14 depicts a shunt having multiple slits along a length of the shunt.
  • Figure 15 depicts a shunt having a slit at a proximal end of the shunt.
  • Figure 16 provides a schematic of a shunt that has a variable inner diameter.
  • Figure 17 is a schematic showing an embodiment of a shunt deployment device according to the invention.
  • Figure 18 shows an exploded view of the device shown in Figure 17.
  • Figures 19A to 19D are schematics showing different enlarged views of the deployment mechanism of the deployment device.
  • Figures 20A to 20C are schematics showing interaction of the deployment mechanism with a portion of the housing of the deployment device.
  • Figure 21 shows a cross sectional view of the deployment mechanism of the deployment device.
  • Figures 22A and 22B show schematics of the deployment mechanism in a pre- deployment configuration.
  • Figure 22C shows an enlarged view of the distal portion of the deployment device of Figure 22A. This figure shows an intraocular shunt loaded within a hollow shaft of the deployment device.
  • Figures 23A and 23B show schematics of the deployment mechanism at the end of the first stage of deployment of the shunt from the deployment device.
  • Figure 23C shows an enlarged view of the distal portion of the deployment device of Figure 23 A. This figure shows an intraocular shunt partially deployed from within a hollow shaft of the deployment device.
  • Figure 24A shows a schematic of the deployment device after deployment of the shunt from the device.
  • Figure 24B show a schematic of the deployment mechanism at the end of the second stage of deployment of the shunt from the deployment device.
  • Figure 24C shows an enlarged view of the distal portion of the deployment device after retraction of the shaft with the pusher abutting the shunt.
  • Figure 24D shows an enlarged view of the distal portion of the deployment device after deployment of the shunt.
  • Figures 25 and 26 show an intraocular shunt deployed within the eye.
  • a proximal portion of the shunt resides in the anterior chamber and a distal portion of the shunt resides within the intra-Tenon's space.
  • a middle portion of the shunt resides in the sclera.
  • Figure 1 provides a schematic diagram of the general anatomy of the eye.
  • An anterior aspect of the anterior chamber 1 of the eye is the cornea 2, and a posterior aspect of the anterior chamber 1 of the eye is the iris 4. Beneath the iris 4 is the lens 5.
  • the anterior chamber 1 is filled with aqueous humor 3.
  • the aqueous humor 3 drains into a space(s) 6 below the conjunctiva 7 through the trabecular meshwork (not shown in detail) of the sclera 8.
  • the aqueous humor is drained from the space(s) 6 below the conjunctiva 7 through a venous drainage system (not shown).
  • Figure 2 provides a cross-sectional view of a portion of the eye, and provides greater detail regarding certain anatomical structures of the eye.
  • Figure 2 shows the relationship of the conjunctiva 12 and Tenon's capsule 13.
  • Tenon's capsule 13 is a fascial layer of connective tissue surrounding the globe and extra-ocular muscles. As shown in Figure 2, it is attached anteriorly to the limbus of the eye and extends posteriorly over the surface of the globe until it fuses with the dura surrounding the optic nerve.
  • number 9 denotes the limbal fusion of the conjunctiva 12 and Tenon's capsule 13 to the sclera 11.
  • the conjunctiva 12 and Tenon's capsule 13 are separate membranes that start at the limbal fusion 9 and connect to tissue at the posterior of the eye.
  • the space formed below the conjunctiva 12 is referred to as the subconjunctival space, denoted as number 14.
  • the space between Tenon's capsule 13 and the sclera 11 where the Tenon's adhesions connect the Tenon's capsule 13 to the sclera 11 is referred to as the intra-Tenon's space, denoted as number 10.
  • the pressure of the aqueous humor in the eye increases and this resultant increase of pressure can cause damage to the vascular system at the back of the eye and especially to the optic nerve.
  • the treatment of glaucoma and other diseases that lead to elevated pressure in the anterior chamber involves relieving pressure within the anterior chamber to a normal level.
  • Glaucoma filtration surgery is a surgical procedure typically used to treat glaucoma.
  • the procedure involves placing a shunt in the eye to relieve intraocular pressure by creating a fluid- flow pathway for draining aqueous humor from the anterior chamber of the eye.
  • the shunt is typically positioned in the eye such that it creates a drainage pathway between the anterior chamber of the eye and a region of lower pressure.
  • Various structures and/or regions of the eye having lower pressure that have been targeted for aqueous humor drainage include Schlemm's canal, the subconjunctival space, the episcleral vein, the suprachoroidal space, or the
  • Shunts may be implanted using an ab externo approach (entering through the conjunctiva and inwards through the sclera) or an ab interno approach (entering through the cornea, across the anterior chamber, through the trabecular meshwork and sclera).
  • Ab interno approaches for implanting an intraocular shunt in the subconjunctival space are shown for example in Yu et al. (U.S. patent number 6,544,249 and U.S. patent publication number 2008/0108933) and Prywes (U.S. patent number 6,007,511), the contents of each of which are incorporated by reference herein in its entirety.
  • a surgical intervention to implant the shunt involves inserting into the eye a deployment device 15 that holds an intraocular shunt, and deploying the shunt within the eye 16.
  • a deployment device 15 holding the shunt enters the eye 16 through the cornea 17 (ab interno approach).
  • the deployment device 15 is advanced across the anterior chamber 20 (as depicted by the broken line) in what is referred to as a transpupil implant insertion.
  • the deployment device 15 is advanced through the sclera 21 until a distal portion of the device is in proximity to the subconjunctival space.
  • the shunt is then deployed from the deployment device, producing a conduit between the anterior chamber and the subconjunctival space to allow aqueous humor to drain through the conjunctival lymphatic system.
  • shunts that are currently utilized in such procedures are not ideal for ab interno subconjunctival placement due to the length of the shunt (i.e., too long) and/or the materials used to make the shunt (e.g., gold, polymer, titanium, or stainless steel), and can cause significant irritation to the tissue surrounding the shunt, as well as the conjunctiva, if deployed too close.
  • the present invention provides intraocular shunts that are designed to form a drainage pathway between the anterior chamber of the eye and the intra-Tenon's space and are suitable for use in an ab interno glaucoma filtration procedure.
  • the present invention further provides methods for deploying an intraocular shunt into an eye such that the shunt forms a passage from the anterior chamber of the eye to the intra-Tenon's space. Deployment and/or design of an intraocular shunt such that the inlet terminates in the anterior chamber and the outlet terminates in the intra-Tenon's space safeguards the integrity of the conjunctiva to allow subconjunctival drainage pathways to successfully form.
  • the conjunctiva is protected from direct contact with the shunt by Tenon's capsule. Additionally, drainage into the intra-Tenon's space provides access to more lymphatic channels than just the conjunctival lymphatic system, such as the episcleral lymphatic network. Moreover, deployment and/or design of an intraocular shunt such that the outlet terminates in the intra-Tenon's space avoids having to pierce Tenon's capsule which can otherwise cause complications during glaucoma filtration surgery due to its tough and fibrous nature.
  • the methods of the invention involve inserting into the eye a hollow shaft configured to hold an intraocular shunt.
  • the hollow shaft is a component of a deployment device that may deploy the intraocular shunt.
  • the shunt is then deployed from the shaft into the eye such that the shunt forms a passage from the anterior chamber to the intra- Tenon's space.
  • the hollow shaft is then withdrawn from the eye.
  • FIGS 25 and 26 which show an intraocular shunt placed into the eye such that the shunt forms a passage for fluid drainage from the anterior chamber to the intra-Tenon's space.
  • a surgical intervention to implant the shunt is performed that involves inserting into the eye 202 a deployment device 200 that holds an intraocular shunt 201, and deploying at least a portion of the shunt 201 within intra-Tenon's space 208, within the subconjunctival space 209 beneath the conjunctiva 210.
  • a hollow shaft 206 of a deployment device 200 holding the shunt 201 enters the eye 202 through the cornea 203 (ab interno approach).
  • the shaft 206 is advanced across the anterior chamber 204 (as depicted by the broken line) in what is referred to as a transpupil implant insertion.
  • the shaft 206 is advanced through the sclera 205 until a distal portion of the shaft 206 is in proximity to Tenon's capsule 207.
  • resistance to advancement of the shaft 206 encountered by an operator of the deployment device 200 informs the operator that the shaft 206 has contacted Tenon's capsule 207 and is thus in proximity to Tenon's capsule 207.
  • the methods of the invention involve the use of a hollow shaft 206, in which a portion of the hollow shaft extends linearly along a longitudinal axis and at least one other portion of the shaft extends off the longitudinal axis.
  • the hollow shaft 206 may have a bend in the distal portion of the shaft, a U-shape, or an arcuate or V-shape in at least a portion of the shaft. Examples of such hollow shafts 206 suitable for use with the methods of the invention include but are not limited to the hollow shafts 206 depicted in Figures 5A-5C.
  • intra-Tenon's shunt placement can be achieved by using the bent distal portion of the shaft 206 to push Tenon's capsule 207 away from the sclera 205 without penetrating Tenon's capsule 207.
  • the tip of the distal end of the shaft 206 does not contact Tenon's capsule 207.
  • a straight hollow shaft 206 having a beveled tip is employed.
  • the angle of the beveled tip of the hollow shaft is oriented such that after piercing the sclera 205, the hollow shaft 206 does not pierce Tenon's capsule 207.
  • the shaft 206 is inserted into the eye 202 and through the sclera 205 at an angle such that the bevel of the tip is oriented to be parallel to Tenon's capsule 207, thereby pushing Tenon's capsule 207 away from the sclera 205, rather than penetrating Tenon's capsule 207, and allowing for deployment of a distal portion of the shunt 201 into the intra-Tenon's space 208.
  • the shunt 201 is then deployed from the shaft 206 of the deployment device 200, producing a conduit between the anterior chamber 204 and the intra-Tenon's space 208 to allow aqueous humor to drain from the anterior chamber 204 (See Figures 25 and 26).
  • FIG 4 provides an exemplary schematic of a hollow shaft for use in accordance with the methods of the invention.
  • This figure shows a hollow shaft 22 that is configured to hold an intraocular shunt 23.
  • the shaft may hold the shunt within the hollow interior 24 of the shaft, as is shown in Figure 4.
  • the hollow shaft may hold the shunt on an outer surface 25 of the shaft.
  • the shunt is held within the hollow interior of the shaft 24, as is shown in Figure 4.
  • the intraocular shunts are of a cylindrical shape and have an outside cylindrical wall and a hollow interior.
  • the shunt may have an inside diameter of approximately 10-250 ⁇ , an outside diameter of approximately 190-300 ⁇ , and a length of approximately 0.5 mm to 20 mm.
  • the hollow shaft 22 is configured to at least hold a shunt of such shape and such dimensions.
  • the hollow shaft 22 may be configured to hold shunts of different shapes and different dimensions than those described above, and the invention encompasses a shaft 22 that may be configured to hold any shaped or dimensioned intraocular shunt.
  • the methods of the invention are conducted by making an incision in the eye prior to insertion of the deployment device.
  • the methods of the invention may be conducted without making an incision in the eye prior to insertion of the deployment device.
  • the shaft that is connected to the deployment device has a sharpened point or tip.
  • the hollow shaft is a needle. Exemplary needles that may be used are commercially available from Terumo Medical Corp.
  • the needle has a hollow interior and a beveled tip, and the intraocular shunt is held within the hollow interior of the needle.
  • the needle has a hollow interior and a triple ground point or tip.
  • the methods of the invention are preferably conducted without needing to remove an anatomical portion or feature of the eye, including but not limited to the trabecular meshwork, the iris, the cornea, or aqueous humor.
  • the methods of the invention are also preferably conducted without inducing substantial ocular inflammation, such as subconjunctival blebbing or endophthalmitis.
  • Such methods can be achieved using an ab interno approach by inserting the hollow shaft through the cornea, across the anterior chamber, through the trabecular meshwork and sclera and into the intra-Tenon's space.
  • the methods of the invention may be conducted using an ab externo approach.
  • the methods of the invention further involves injecting an aqueous solution into the eye below Tenon's capsule in order to balloon the capsule away from the sclera.
  • the increase in intra-Tenon's space caused by the ballooning of Tenon's capsule is helpful for positioning of the outlet of the shunt in the intra-Tenon's space.
  • the solution is injected prior to the shaft piercing the sclera and entering the intra-Tenon's space.
  • Suitable aqueous solutions include but are not limited to Dulbecco's Phosphate Buffered Saline (DPBS), Hank's Balanced Salt Solution (HBSS), Phosphate-Buffered Saline (PBS), Earle's Balanced Salt Solution (EBSS), or other balanced salt solutions known in the art.
  • DPBS Dulbecco's Phosphate Buffered Saline
  • HBSS Hank's Balanced Salt Solution
  • PBS Phosphate-Buffered Saline
  • EBSS Earle's Balanced Salt Solution
  • the methods of the invention involve injecting a viscoelastic fluid into the eye.
  • the methods of the invention are conducted without the use of a viscoelastic fluid.
  • the angle of entry through the cornea affects optimal placement of the shunt in the intra-Tenon's space.
  • the hollow shaft is inserted into the eye at an angle above or below the corneal limbus, in contrast with entering through the corneal limbus.
  • the hollow shaft is inserted approximately 0.25 to 3.0 mm, preferably approximately 0.5 to 2.5 mm, more preferably approximately 1.0 mm to 2.0 mm above the corneal limbus, or any specific value within said ranges, e.g., approximately 1.0 mm, approximately 1.1 mm, approximately 1.2 mm,
  • placement of the shunt farther from the limbus at the exit site, as provided by an angle of entry above the limbus, is believed to provide access to more lymphatic channels for drainage of aqueous humor, such as the episcleral lymphatic network, in addition to the conjunctival lymphatic system.
  • a higher angle of entry also results in flatter placement in the intra-Tenon's space so that there is less bending of the shunt, less pressure on Tenon's capsule, and subsequently less erosion pressure on the conjunctiva via Tenon's capsule.
  • shaft entry at the limbus 52 results in exit site distance 53 of approximately 1.6 mm from the limbus, and very close proximity to the iris 4.
  • exit site distance 53 of approximately 1.6 mm from the limbus, and very close proximity to the iris 4.
  • a high angle of entry 54 above the limbus 52 e.g., 2 mm above the limbus 52
  • Such placement results in flatter placement in the intra-Tenon's space so that there is less bending of the shunt, less pressure on Tenon's capsule, and subsequently less erosion pressure on the conjunctiva via Tenon's capsule.
  • the depth of penetration through the sclera is important when conducting the methods of the invention.
  • the distal tip of the hollow shaft pierces the sclera without coring, removing or causing major tissue distortion of the surrounding eye tissue.
  • the shunt is then deployed from the shaft.
  • a distal portion of the hollow shaft (as opposed to the distal tip) completely penetrates the sclera before the shunt is deployed from the hollow shaft.
  • the hollow shaft is a flat bevel needle, such as a needle having a triple- ground point. The tip bevel first pierces through the sclera making a horizontal slit.
  • the needle is advanced even further such that the entire flat bevel penetrates through the sclera, as shown in Figure 7D, to spread and open the tissue to a full circular diameter.
  • the tip bevel and flat bevel portions of a triple ground needle point, and the configuration of the shunt disposed in the needle point, are exemplified as the gray shaded areas in Figures 7A-7C.
  • the scleral channel is not completely forced open by the flat bevel portion of the needle, the material around the opening may not be sufficiently stretched and a pinching of the implant in that zone will likely occur, causing the shunt to fail.
  • Full penetration of the flat bevel through the sclera causes minor distortion and trauma to the local area. However, this area ultimately surrounds and conforms to the shunt once the shunt is deployed in the eye.
  • Figure 8 A depicts an example of an intraocular shunt implanted in an eye in accordance with the methods of the invention using a triple ground need point with 100% penetration of the flat bevel in the scleral channel.
  • Figure 8B depicts an example of a shunt implanted in an eye in accordance with the methods of the invention using a triple ground needle point with
  • the methods of the invention may be conducted using any commercially available shunts, such as the Optonol Ex-P ESS mini Glaucoma shunt, and the Solx DeepLight Gold Micro-Shunt. However, the methods of the invention are preferably conducted using the intraocular shunts of the present invention, as described herein.
  • the present invention also provides intraocular shunts that are configured to form a drainage pathway from the anterior chamber of the eye to the intra-Tenon's space.
  • the intraocular shunts of the invention have a length that is sufficient to form a drainage pathway from the anterior chamber of the eye to the intra-Tenon's space.
  • the length of the shunt is important in achieving placement specifically in the intra-Tenon's space. A shunt that is too long will extend beyond the intra-Tenon's space and irritate the conjunctiva, which can cause the filtration procedure to fail, as previously described. A shunt that is too short will not provide sufficient access to drainage pathways such as the episcleral lymphatic system or the
  • Shunts of the invention may be any length that allows for drainage of aqueous humor from an anterior chamber of an eye to the intra-tenon's space.
  • Exemplary shunts range in length from approximately 0.5 mm to approximately 20 mm or between approximately 4 mm to approximately 16 mm, or any specific value within said ranges.
  • the length of the shunt is between approximately 6 to 8 mm, or any specific value within said range, e.g., 6.0 mm, 6.1 mm, 6.2 mm, 6.3 mm, 6.4 mm, 6.5 mm, 6.6 mm, 6.7 mm, 6.8 mm, 6.9 mm, 7 mm, 7.1 mm, 7.2 mm, 7.3 mm, 7.4 mm, 7.5 mm, 7.6 mm, 7.7 mm, 7.8 mm. 7.9 mm, or 8.0 mm.
  • the intraocular shunts of the invention are particularly suitable for use in an ab interno glaucoma filtration procedure.
  • Commercially available shunts that are currently used in ab interno filtration procedures are typically made of a hard, inflexible material such as gold, polymer, titanium, or stainless steel, and cause substantial irritation of the eye tissue, resulting in ocular inflammation such as subconjunctival blebbing or endophthalmitis.
  • the intraocular shunts of the invention are flexible, and have an elasticity modulus that is
  • the intraocular shunts of the invention are easily bendable, do not erode or cause a tissue reaction, and do not migrate once implanted.
  • the intraocular shunts of the invention do not induce substantial ocular inflammation such as subconjunctival blebbing or
  • the invention generally provides shunts composed of a material that has an elasticity modulus that is compatible with an elasticity modulus of tissue surrounding the shunt.
  • shunts of the invention are flexibility matched with the surrounding tissue, and thus will remain in place after implantation without the need for any type of anchor that interacts with the surrounding tissue. Consequently, shunts of the invention will maintain fluid flow away for an anterior chamber of the eye after implantation without causing irritation or inflammation to the tissue surrounding the eye.
  • Elastic modulus or modulus of elasticity, is a mathematical description of an object or substance's tendency to be deformed elastically when a force is applied to it.
  • the elastic modulus of an object is defined as the slope of its stress-strain curve in the elastic deformation region: ⁇ stress
  • lambda ( ⁇ ) is the elastic modulus
  • stress is the force causing the deformation divided by the area to which the force is applied
  • strain is the ratio of the change caused by the stress to the original state of the object.
  • the elasticity modulus may also be known as Young's modulus (E), which describes tensile elasticity, or the tendency of an object to deform along an axis when opposing forces are applied along that axis. Young's modulus is defined as the ratio of tensile stress to tensile strain.
  • the elasticity modulus of any tissue can be determined by one of skill in the art. See for example Samani et al. (Phys. Med. Biol. 48:2183, 2003); Erkamp et al. (Measuring The Elastic Modulus Of Small Tissue Samples, Biomedical Engineering Department and Electrical
  • the elasticity modulus of tissues of different organs is known in the art. For example,
  • Shunts of the invention are composed of a material that is compatible with an elasticity modulus of tissue surrounding the shunt.
  • the material has an elasticity modulus that is substantially identical to the elasticity modulus of the tissue surrounding the shunt.
  • the material has an elasticity modulus that is greater than the elasticity modulus of the tissue surrounding the shunt.
  • Exemplary materials includes biocompatible polymers, such as polycarbonate, polyethylene, polyethylene terephthalate, polyimide, polystyrene, polypropylene, poly(styrene-b-isobutylene-b-styrene), or silicone rubber.
  • shunts of the invention are composed of a material that has an elasticity modulus that is compatible with the elasticity modulus of tissue in the eye, particularly scleral tissue.
  • compatible materials are those materials that are softer than scleral tissue or marginally harder than scleral tissue, yet soft enough to prohibit shunt migration.
  • the elasticity modulus for anterior scleral tissue is approximately 2.9 ⁇ 1.4 x 10 6 N/m 2 , and 1.8 ⁇ 1.1 x 10 6 N/m 2 for posterior scleral tissue. See Friberg (Experimental Eye Research, 473:429-436, 1988).
  • An exemplary material is cross linked gelatin derived from Bovine or Porcine Collagen.
  • the invention encompasses shunts of different shapes and different dimensions, and the shunts of the invention may be any shape or any dimension that may be accommodated by the eye.
  • the intraocular shunt is of a cylindrical shape and has an outside cylindrical wall and a hollow interior.
  • the shunt may have an inside diameter from
  • the invention generally provides shunts in which a portion of the shunt is composed of a flexible material that is reactive to pressure, i.e., the diameter of the flexible portion of the shunt fluctuates depending upon the pressures exerted on that portion of the shunt.
  • Figure 9 provides a schematic of a shunt 23 having a flexible portion 51 (thicker black lines).
  • the flexible portion 51 is shown in the middle of the shunt 23.
  • the flexible portion 51 may be located in any portion of the shunt, such as the proximal or distal portion of the shunt.
  • the entire shunt is composed of the flexible material, and thus the entire shunt is flexible and reactive to pressure.
  • the flexible portion 51 of the shunt 23 acts as a valve that regulates fluid flow through the shunt.
  • the human eye produces aqueous humor at a rate of about 2 ⁇ /min for approximately 3 ml/day. The entire aqueous volume is about 0.25 ml.
  • venous backpressure prevents any significant outflow through normal drainage structures (e.g., the trabecular meshwork).
  • intraocular shunts After implantation, intraocular shunts have pressure exerted upon them by tissues surrounding the shunt (e.g., scleral tissue such as the sclera channel and the sclera exit) and pressure exerted upon them by aqueous humor flowing through the shunt.
  • tissues surrounding the shunt e.g., scleral tissue such as the sclera channel and the sclera exit
  • the flow through the shunt, and thus the pressure exerted by the fluid on the shunt is calculated by the equation:
  • ⁇ is the volumetric flow rate; Vis a volume of the liquid poured (cubic meters); t is the time (seconds); V is mean fluid velocity along the length of the tube (meters/second); X is a distance in direction of flow (meters); R is the internal radius of the tube (meters); AP is the pressure difference between the two ends (pascals); ⁇ is the dynamic fluid viscosity (pascal- second (Pa-s)); and L is the total length of the tube in the x direction (meters).
  • Figure 10A provides a schematic of a shunt 26 implanted into an eye for regulation of fluid flow from the anterior chamber of the eye to an area of lower pressure (e.g., the intra- Tenon's space, the subconjunctival space, the episcleral vein, the suprachoroidal space, or Schlemm's canal).
  • the area of lower pressure is the subarachnoid space.
  • the shunt is implanted such that a proximal end 27 of the shunt 26 resides in the anterior chamber 28 of the eye, and a distal end 29 of the shunt 26 resides outside of the anterior chamber to conduct aqueous humor from the anterior chamber to an area of lower pressure.
  • a flexible portion 30 (thicker black lines) of the shunt 26 spans at least a portion of the sclera of the eye. As shown in Figure 10A, the flexible portion spans an entire length of the sclera 21.
  • the invention encompasses shunts of different shapes and different dimensions, and the shunts of the invention may be any shape or any dimension that may be accommodated by the eye.
  • the intraocular shunt is of a cylindrical shape and has an outside cylindrical wall and a hollow interior.
  • the shunt may have an inside diameter from
  • the shunt has a length of about 6 mm and an inner diameter of about 64 ⁇ . With these dimensions, the pressure difference between the proximal end of the shunt that resides in the anterior chamber and the distal end of the shunt that resides outside the anterior chamber is about 4.3 mmHg. Such dimensions thus allow the implant to act as a controlled valve and protect the integrity of the anterior chamber.
  • shunts that range in length from about 0.5 mm to about 20 mm and have a range in inner diameter from about 10 ⁇ to about 100 ⁇ allow for pressure control from approximately 0.5 mmHg to approximately 20 mmHg.
  • the material of the flexible portion and the thickness of the wall of the flexible portion will determine how reactive the flexible portion is to the pressures exerted upon it by the surrounding tissue and the fluid flowing through the shunt. Generally, with a certain material, the thicker the flexible portion, the less responsive the portion will be to pressure.
  • the flexible portion is a gelatin or other similar material, and the thickness of the gelatin material forming the wall of the flexible portion ranges from about 10 ⁇ thick to about 100 ⁇ thick.
  • the gelatin used for making the flexible portion is known as gelatin Type B from bovine skin.
  • An exemplary gelatin is PB Leiner gelatin from bovine skin, Type B, 225 Bloom, USP.
  • Another material that may be used in the making of the flexible portion is a gelatin Type A from porcine skin, also available from Sigma Chemical. Such gelatin is available from Sigma Chemical Company of St. Louis, Mo. under Code G-9382.
  • Still other suitable gelatins include bovine bone gelatin, porcine bone gelatin and human-derived gelatins.
  • the flexible portion may be made of hydroxypropyl methycellulose (HPMC), collagen, polylactic acid, polylglycolic acid, hyaluronic acid and glycosaminoglycans.
  • HPMC hydroxypropyl methycellulose
  • the gelatin is cross-linked.
  • Cross-linking increases the inter- and intramolecular binding of the gelatin substrate. Any method for cross-linking the gelatin may be used.
  • the formed gelatin is treated with a solution of a cross-linking agent such as, but not limited to, glutaraldehyde.
  • a cross-linking agent such as, but not limited to, glutaraldehyde.
  • Other suitable compounds for cross-linking include l-ethyl-3-[3-(dimethyamino)propyl]carbodiimide (EDC).
  • EDC l-ethyl-3-[3-(dimethyamino)propyl]carbodiimide
  • Cross-linking by radiation such as gamma or electron beam (e-beam) may be alternatively employed.
  • the gelatin is contacted with a solution of approximately 25% glutaraldehyde for a selected period of time.
  • glutaraldehyde is a grade 1G5882 glutaraldehyde available from Sigma Aldridge Company of Germany, although other glutaraldehyde solutions may also be used.
  • the pH of the glutaraldehyde solution should be in the range of 7 to 7.8 and, more particularly, 7.35-7.44 and typically approximately 7.4 +/- 0.01. If necessary, the pH may be adjusted by adding a suitable amount of a base such as sodium hydroxide as needed.
  • the flexible portion may be made by dipping a core or substrate such as a wire of a suitable diameter in a solution of gelatin.
  • the gelatin solution is typically prepared by dissolving a gelatin powder in de-ionized water or sterile water for injection and placing the dissolved gelatin in a water bath at a temperature of approximately 55°C. with thorough mixing to ensure complete dissolution of the gelatin.
  • the ratio of solid gelatin to water is approximately 10% to 50% gelatin by weight to 50% to 90% by weight of water.
  • the gelatin solution includes approximately 40%) by weight, gelatin dissolved in water.
  • the resulting gelatin solution should be devoid of air bubbles and has a viscosity that is between approximately 200-500 cp and more particularly between approximately 260 and 410 cp (centipoise).
  • supporting structures such as wires having a selected diameter are dipped into the solution to form the flexible portion.
  • Stainless steel wires coated with a biocompatible, lubricious material such as polytetrafluoroethylene (Teflon) are preferred.
  • Teflon polytetrafluoroethylene
  • the wires are gently lowered into a container of the gelatin solution and then slowly withdrawn. The rate of movement is selected to control the thickness of the coat.
  • the wires may be rotated in a stream of cool air which helps to set the gelatin solution and affix film onto the wire. Dipping and withdrawing the wire supports may be repeated several times to further ensure even coating of the gelatin.
  • the resulting gelatin films on the wire may be dried at room temperature for at least 1 hour, and more preferably, approximately 10 to 24 hours. Apparatus for forming gelatin tubes are described in Yu et al. (U.S. patent application number 2008/0108933).
  • the formed flexible portions may be treated with a cross-linking agent.
  • the formed flexible portion may be cross-linked by dipping the wire (with film thereon) into the 25% glutaraldehyde solution, at pH of approximately 7.0-7.8 and more preferably approximately 7.35-7.44 at room temperature for at least 4 hours and preferably between approximately 10 to 36 hours, depending on the degree of cross-linking desired.
  • the formed flexible portion is contacted with a cross-linking agent such as gluteraldehyde for at least approximately 16 hours.
  • Cross-linking can also be accelerated when it is performed a high temperatures. It is believed that the degree of cross-linking is proportional to the bioabsorption time of the shunt once implanted. In general, the more cross-linking, the longer the survival of the shunt in the body.
  • the residual glutaraldehyde or other cross-linking agent is removed from the formed flexible portion by soaking the tubes in a volume of sterile water for injection.
  • the water may optionally be replaced at regular intervals, circulated or re-circulated to accelerate diffusion of the unbound glutaraldehyde from the tube.
  • the tubes are washed for a period of a few hours to a period of a few months with the ideal time being 3-14 days.
  • the now cross-linked gelatin tubes may then be dried (cured) at ambient temperature for a selected period of time. It has been observed that a drying period of approximately 48-96 hours and more typically 3 days (i.e., 72 hours) may be preferred for the formation of the cross-linked gelatin tubes.
  • a cross-linking agent it may be desirable to include a quenching agent in the method of making the flexible portion. Quenching agents remove unbound molecules of the cross-linking agent from the formed flexible portion. In certain cases, removing the cross-linking agent may reduce the potential toxicity to a patient if too much of the cross-linking agent is released from the flexible portion. In certain embodiments, the formed flexible portion is contacted with the quenching agent after the cross-linking treatment and, may be included with the washing/rinsing solution. Examples of quenching agents include glycine or sodium borohydride.
  • the formed and cross-linked flexible portion is removed from the underlying supports or wires.
  • wire tubes may be cut at two ends and the formed gelatin flexible portion slowly removed from the wire support.
  • wires with gelatin film thereon may be pushed off using a plunger or tube to remove the formed gelatin flexible portion.
  • the shunt includes a hollow body defining a flow path and more than two ports, in which the body is configured such that a proximal portion receives fluid from the anterior chamber of an eye and a distal portion directs the fluid to the intra-Tenon's space.
  • the shunt may have many different configurations.
  • Figure 11 A shows an embodiment of a shunt 32 in which the proximal portion of the shunt (i.e., the portion disposed within the anterior chamber of the eye) includes more than one port (designated as numbers 33a to 33e) and the distal portion of the shunt (i.e., the portion that is located in the intra-Tenon's space) includes a single port 34.
  • Figure 1 IB shows another embodiment of a shunt 32 in which the proximal portion includes a single port 33 and the distal portion includes more than one port (designated as numbers 34a to 34e).
  • Figure 11C shows another embodiment of a shunt 32 in which the proximal portions include more than one port (designated as numbers 33a to 33e) and the distal portions include more than one port (designated as numbers 34a to 34e). While Figure 11 shows shunts have five ports at the proximal portion, distal portion, or both, those shunts are only exemplary embodiments.
  • the ports may be located along any portion of the shunt, and shunts of the invention include all shunts having more than two ports.
  • shunts of the invention may include at least three ports, at least four ports, at least five ports, at least 10 ports, at least 15 ports, or at least 20 ports.
  • the ports may be positioned in various different orientations and along various different portions of the shunt. In certain embodiments, at least one of the ports is oriented at an angle to the length of the body. In certain embodiments, at least one of the ports is oriented 90° to the length of the body. See for example Figure 11 A, which depicts ports 33a, 33b, 33d, and 33e as being oriented at a 90° angle to port 33c.
  • the ports may have the same or different inner diameters. In certain embodiments, at least one of the ports has an inner diameter that is different from the inner diameters of the other ports.
  • Figure 12 shows an embodiment of a shunt 32 having multiple ports (33a and 33b) at a proximal end and a single port 34 at a distal end.
  • Figure 12A shows that port 33b has an inner diameter that is different from the inner diameters of ports 33a and 34.
  • the inner diameter of port 33b is less than the inner diameter of ports 33a and 34.
  • An exemplary inner diameter of port 33b is from about 20 ⁇ to about 40 ⁇ , particularly about 30 ⁇ . In other embodiments, the inner diameter of port 33b is greater than the inner diameter of ports 33a and 34. See for example Figure 12B.
  • the invention encompasses shunts of different shapes and different dimensions, and the shunts of the invention may be any shape or any dimension that may be accommodated by the eye.
  • the intraocular shunt is of a cylindrical shape and has an outside cylindrical wall and a hollow interior.
  • the shunt may have an inside diameter from
  • Shunts of the invention may be made from any biocompatible material.
  • An exemplary material is gelatin. Methods of making shunts composed of gelatin are described above.
  • shunts with overflow ports.
  • Those shunts are configured such that the overflow port remains partially or completely closed until there is a pressure build-up within the shunt sufficient to force open the overflow port.
  • Such pressure build-up typically results from particulate partially or fully clogging an entry or an exit port of the shunt.
  • Such shunts reduce probability of the shunt clogging after implantation because fluid can enter or exit the shunt by the overflow port even in one port of the shunt becomes clogged with particulate.
  • the shunt includes a hollow body defining an inlet configured to receive fluid from an anterior chamber of an eye and an outlet configured to direct the fluid to the intra-Tenon's space, the body further including at least one slit.
  • the slit may be located at any place along the body of the shunt.
  • Figure 13A shows a shunt 35 having an inlet 36, an outlet 37, and a slit 38 located in proximity to the inlet 36.
  • Figure 13B shows a shunt 35 having an inlet 36, an outlet 37, and a slit 39 located in proximity to the outlet 37.
  • Figure 13C shows a shunt 35 having an inlet 36, an outlet 37, a slit 38 located in proximity to the inlet 36, and a slit 39 located in proximity to the outlet 37.
  • Figure 13 shows shunts have only a single overflow port at the proximal portion, the distal portion, or both the proximal and distal portions, those shunts are only exemplary embodiments.
  • the overflow port(s) may be located along any portion of the shunt, and shunts of the invention include shunts having more than one overflow port. In certain embodiments, shunts of the invention include more than one overflow port at the proximal portion, the distal portion, or both.
  • Figure 14 shows a shunt 40 having an inlet 41, an outlet 42, and slits 43a and 43b located in proximity to the inlet 41.
  • Shunts of the invention may include at least two overflow ports, at least three overflow ports, at least four overflow ports, at least five overflow ports, at least 10 overflow ports, at least 15 overflow ports, or at least 20 overflow ports.
  • shunts of the invention include two slits that overlap and are oriented at 90° to each other, thereby forming a cross.
  • the slit may be at the proximal or the distal end of the shunt, producing a split in the proximal or the distal end of the implant.
  • Figure 15 shows an
  • a shunt 44 having an inlet 45, outlet 46, and a slit 47 that is located at the proximal end of the shunt, producing a split in the inlet 45 of the shunt.
  • the slit has a width that is substantially the same or less than an inner diameter of the inlet. In other embodiments, the slit has a width that is substantially the same or less than an inner diameter of the outlet. In certain embodiments, the slit has a length that ranges from about 0.05 mm to about 2 mm, and a width that ranges from about 10 ⁇ to about 200 ⁇ . Generally, the slit does not direct the fluid unless the outlet is obstructed.
  • the shunt may be configured such that the slit does direct at least some of the fluid even if the inlet or outlet is not obstructed.
  • the invention encompasses shunts of different shapes and different dimensions, and the shunts of the invention may be any shape or any dimension that may be accommodated by the eye.
  • the intraocular shunt is of a cylindrical shape and has an outside cylindrical wall and a hollow interior.
  • the shunt may have an inside diameter from
  • Shunts of the invention may be made from any biocompatible material.
  • An exemplary material is gelatin. Methods of making shunts composed of gelatin are described above.
  • the invention generally provides a shunt having a variable inner diameter.
  • the diameter increases from inlet to outlet of the shunt.
  • Figure 16 shows an embodiment of a shunt 48 having an inlet 49 configured to receive fluid from an anterior chamber of an eye and an outlet 50 configured to direct the fluid to a location of lower pressure with respect to the anterior chamber, in which the body further includes a variable inner diameter that increases along the length of the body from the inlet 49 to the outlet 50.
  • the inner diameter continuously increases along the length of the body, for example as shown in Figure 16. In other embodiments, the inner diameter remains constant along portions of the length of the body.
  • the inner diameter may range in size from about 10 ⁇ to about 200 ⁇ , and the inner diameter at the outlet may range in size from about 15 ⁇ to about 300 ⁇ .
  • the invention encompasses shunts of different shapes and different dimensions, and the shunts of the invention may be any shape or any dimension that may be accommodated by the eye.
  • the intraocular shunt is of a cylindrical shape and has an outside cylindrical wall and a hollow interior. The shunt may have an inside diameter from
  • Shunts of the invention may be made from any biocompatible material.
  • An exemplary material is gelatin. Methods of making shunts composed of gelatin are described above.
  • shunts of the invention may be coated or impregnated with at least one pharmaceutical and/or biological agent or a combination thereof.
  • the pharmaceutical and/or biological agent may coat or impregnate an entire exterior of the shunt, an entire interior of the shunt, or both.
  • the pharmaceutical or biological agent may coat and/or impregnate a portion of an exterior of the shunt, a portion of an interior of the shunt, or both.
  • the exterior portion of the shunt that resides in the anterior chamber after implantation (e.g., about 1 mm of the proximal end of the shunt) is coated and/or impregnated with the pharmaceutical or biological agent.
  • the exterior of the shunt that resides in the scleral tissue after implantation of the shunt is coated and/or impregnated with the pharmaceutical or biological agent.
  • the exterior portion of the shunt that resides in the intra-Tenon's space or the subconjunctival space after implantation is coated and/or impregnated with the pharmaceutical or biological agent.
  • the agent may be flushed through the shunt and into the area of lower pressure (e.g., the intra-Tenon's space or the subconjunctival space).
  • Any pharmaceutical and/or biological agent or combination thereof may be used with shunts of the invention.
  • the pharmaceutical and/or biological agent may be released over a short period of time (e.g., seconds) or may be released over longer periods of time (e.g., days, weeks, months, or even years).
  • Exemplary agents include anti-mitotic pharmaceuticals such as
  • Mitomycin-C or 5-Fluorouracil such as Lucintes, Macugen, Avastin, VEGF or steroids.
  • Deployment Devices Deployment into the eye of an intraocular shunt as embodied in the invention and in accordance with the methods of the invention can be achieved using a hollow shaft configured to hold the shunt, as described herein.
  • the hollow shaft can be coupled to a deployment device or part of the deployment device itself.
  • Deployment devices that are suitable for use with the methods of the invention include but are not limited to the deployment devices described in U.S. Patent No. 6,007,511, U.S. Patent No. 6,544,249, and U.S. Publication No. US2008/0108933, the contents of each of which are hereby incorporated by reference in their entireties.
  • the deployment devices are devices as described in co-pending and co-owned U.S. nonprovisional patent application serial number 12/946,222 filed on November 15, 2010, and having Attorney Docket No. AQUE-002/01US 29053/15, the entire content of which is incorporated by reference herein.
  • deployment device 100 includes a generally cylindrical body or housing 101, however, the body shape of housing 101 could be other than cylindrical. Housing 101 may have an ergonomical shape, allowing for comfortable grasping by an operator. Housing 101 is shown with optional grooves 102 to allow for easier gripping by a surgeon.
  • Housing 101 is shown having a larger proximal portion that tapers to a distal portion.
  • the distal portion includes a hollow sleeve 105.
  • the hollow sleeve 105 is configured for insertion into an eye and to extend into an anterior chamber of an eye.
  • the hollow sleeve is visible within an anterior chamber of an eye.
  • the sleeve may include an edge at a distal end that provides resistance feedback to an operator upon insertion of the deployment device 100 within an eye of a person.
  • the hollow sleeve 105 Upon advancement of the device 100 across an anterior chamber of the eye, the hollow sleeve 105 will eventually contact the sclera, providing resistance feedback to an operator that no further advancement of the device 100 is necessary.
  • the edge of the sleeve 105 prevents the shaft 104 from accidentally being pushed too far through the sclera.
  • a temporary guard 108 is configured to fit around sleeve 105 and extend beyond an end of sleeve 105.
  • the guard is used during shipping of the device and protects an operator from a distal end of a hollow shaft 104 that extends beyond the end of the sleeve 105. The guard is removed prior to use of the device.
  • Housing 101 is open at its proximal end, such that a portion of a deployment mechanism 103 may extend from the proximal end of the housing 101.
  • a distal end of housing 101 is also open such that at least a portion of a hollow shaft 104 may extend through and beyond the distal end of the housing 101.
  • Housing 101 further includes a slot 106 through which an operator, such as a surgeon, using the device 100 may view an indicator 107 on the deployment mechanism 103.
  • Housing 101 may be made of any material that is suitable for use in medical devices.
  • housing 101 may be made of a lightweight aluminum or a biocompatible plastic material.
  • suitable plastic materials include polycarbonate and other polymeric resins such as DELRIN and ULTEM.
  • housing 101 is made of a material that may be autoclaved, and thus allow for housing 101 to be re-usable.
  • device 100 may be sold as a one-time-use device, and thus the material of the housing does not need to be a material that is autoclavable.
  • Housing 101 may be made of multiple components that connect together to form the housing.
  • Figure 18 shows an exploded view of deployment device 100.
  • housing 101 is shown having three components 101a, 101b, and 101c. The components are designed to screw together to form housing 101.
  • Figure 18 also shows deployment mechanism 103.
  • the housing 101 is designed such that deployment mechanism 103 fits within assembled housing
  • Housing 101 is designed such that components of deployment mechanism 103 are movable within housing 101.
  • FIGS 19A to 19D show different enlarged views of the deployment mechanism 103.
  • Deployment mechanism 103 may be made of any material that is suitable for use in medical devices.
  • deployment mechanism 103 may be made of a lightweight aluminum or a biocompatible plastic material. Examples of such suitable plastic materials include
  • polycarbonate and other polymeric resins such as DELRIN and ULTEM.
  • deployment mechanism 103 is made of a material that may be autoclaved, and thus allow for deployment mechanism 103 to be re-usable.
  • device 100 may be sold as a one-time-use device, and thus the material of the deployment mechanism does not need to be a material that is autoclavable.
  • Deployment mechanism 103 includes a proximal portion 109 and a distal portion 110.
  • the deployment mechanism 103 is configured such that proximal portion 109 is movable within distal portion 110. More particularly, proximal portion 109 is capable of partially retracting to within distal portion 110.
  • the proximal portion 109 is shown to taper to a connection with a hollow shaft 104.
  • This embodiment is illustrated such that the connection between the hollow shaft 104 and the proximal portion 109 of the deployment mechanism 103 occurs inside the housing 101.
  • the connection between hollow shaft 104 and the proximal portion 109 of the deployment mechanism 103 may occur outside of the housing 101.
  • Hollow shaft 104 may be removable from the proximal portion 109 of the deployment mechanism 103.
  • the hollow shaft 104 may be permanently coupled to the proximal portion 109 of the deployment mechanism 103.
  • hollow shaft 104 is configured to hold an intraocular shunt, such as the intraocular shunts according to the invention.
  • the shaft 104 may be any length.
  • a usable length of the shaft may be anywhere from about 5 mm to about 40 mm, and is 15 mm in certain embodiments.
  • the shaft is straight.
  • shaft is of a shape other than straight, for example a shaft having a bend along its length or a shaft as depicted in Figures 5A-5C.
  • a distal portion of the deployment mechanism includes optional grooves 116 to allow for easier gripping by an operator for easier rotation of the deployment mechanism, which will be discussed in more detail below.
  • the distal portion 110 of the deployment mechanism also includes at least one indicator that provides feedback to an operator as to the state of the deployment mechanism.
  • the indicator may be any type of indicator know in the art, for example a visual indicator, an audio indicator, or a tactile indicator.
  • Figure 19 shows a deployment mechanism having two indicators, a ready indicator 111 and a deployed indicator 119.
  • Ready indicator 111 provides feedback to an operator that the deployment mechanism is in a configuration for deployment of an intraocular shunt from the deployment device 100.
  • the indicator 111 is shown in this embodiment as a green oval having a triangle within the oval.
  • Deployed indicator 119 provides feedback to the operator that the deployment mechanism has been fully engaged and has deployed the shunt from the deployment device 100.
  • the deployed indicator 119 is shown in this embodiment as a yellow oval having a black square within the oval.
  • the indicators are located on the deployment mechanism such that when assembled, the indicators 111 and 119 may be seen through slot 106 in housing 101.
  • the distal portion 110 includes a stationary portion 110b and a rotating portion 110a.
  • the distal portion 110 includes a channel 112 that runs part of the length of stationary portion 110b and the entire length of rotating portion 110a.
  • the channel 112 is configured to interact with a protrusion 117 on an interior portion of housing component 101a ( Figures 20A and 20B).
  • the protrusion 117 on housing component 101a is aligned with channel 112 on the stationary portion 110b and rotating portion 110a of the deployment mechanism 103.
  • the distal portion 110 of deployment mechanism 103 is slid within housing component 101a until the protrusion 117 sits within stationary portion 110b ( Figure 20C).
  • the protrusion 117 interacts with the stationary portion 110b of the deployment mechanism 103 and prevents rotation of stationary portion 110b.
  • rotating portion 110a is free to rotate within housing component 101a.
  • deployment mechanism 103 also includes channels 113a, 113b, and 113c.
  • Channel 113a includes a first portion 113al that is straight and runs perpendicular to the length of the rotating portion 110a, and a second portion 113a2 that runs diagonally along the length of rotating portion 110a, downwardly toward a distal end of the deployment mechanism 103.
  • Channel 113b includes a first portion 113bl that runs diagonally along the length of the rotating portion 110a, upwardly toward a proximal end of the deployment mechanism 103, and a second portion that is straight and runs perpendicular to the length of the rotating portion 110a.
  • the point at which first portion 113al transitions to second portion 113a2 along channel 113a is the same as the point at which first portion 113bl transitions to second portion 113b2 along channel 113b.
  • Channel 113c is straight and runs perpendicular to the length of the rotating portion 110a.
  • channels 113a, 113b, and 113c sit members 114a, 114b, and 114c respectively.
  • Members 114a, 114b, and 114c are movable within channels 113a, 113b, and 113c.
  • Members 114a, 114b, and 114c also act as stoppers that limit movement of rotating portion 110a, which thereby limits axial movement of the shaft 104.
  • Figure 21 shows a cross-sectional view of deployment mechanism 103.
  • Member 114a is connected to the proximal portion 109 of the deployment mechanism 103. Movement of member 114a results in retraction of the proximal portion 109 of the deployment mechanism 103 to within the distal portion 110 of the deployment mechanism 103.
  • Member 114b is connected to a pusher component 118.
  • the pusher component 118 extends through the proximal portion 109 of the deployment mechanism 103 and extends into a portion of hollow shaft 104.
  • the pusher component is involved in deployment of a shunt from the hollow shaft 104.
  • An exemplary pusher component is a plunger. Movement of member 114b engages pusher 118 and results in pusher 118 advancing within hollow shaft 104.
  • FIG. 22 A shows deployment device 100 is a pre-deployment configuration.
  • shunt 115 is loaded within hollow shaft 104 (Figure 22C).
  • shunt 115 is only partially within shaft 104, such that a portion of the shunt is exposed. However, the shunt 115 does not extend beyond the end of the shaft 104.
  • the shunt 115 is completely disposed within hollow shaft 104.
  • the shunt 115 is loaded into hollow shaft 104 such that the shunt abuts pusher component 118 within hollow shaft 104.
  • a distal end of shaft 104 is beveled to assist in piercing tissue of the eye.
  • a portion of the shaft 104 extends beyond the housing 101 ( Figure 22C).
  • the deployment mechanism is configured such that member 114a abuts a proximal end of the first portion 113al of channel 113a, and member 114b abut a proximal end of the first portion 113bl of channel 113b ( Figure 22B).
  • the ready indicator 111 is visible through slot 106 of the housing 101, providing feedback to an operator that the deployment mechanism is in a configuration for deployment of an intraocular shunt from the deployment device 100 ( Figure 22A).
  • the device 100 is ready for insertion into an eye (insertion configuration or pre-deployment configuration). Methods for inserting and implanting shunts are discussed in further detail below.
  • the deployment mechanism 103 is a two-stage system. The first stage is engagement of the pusher component 118 and the second stage is retraction of the proximal portion 109 to within the distal portion 110 of the deployment mechanism 103. Rotation of the rotating portion 110a of the distal portion 110 of the deployment mechanism 103 sequentially engages the pusher component and then the retraction component.
  • the pusher component In the first stage of shunt deployment, the pusher component is engaged and the pusher partially deploys the shunt from the deployment device.
  • rotating portion 110a of the distal portion 110 of the deployment mechanism 103 is rotated, resulting in movement of members 114a and 114b along first portions 113al and 113bl in channels 113a and 113b. Since the first portion 113al of channel 113a is straight and runs perpendicular to the length of the rotating portion 110a, rotation of rotating portion 110a does not cause axial movement of member 114a. Without axial movement of member 114a, there is no retraction of the proximal portion 109 to within the distal portion 110 of the deployment mechanism 103.
  • first portion 113bl of channel 113b runs diagonally along the length of the rotating portion 110a, upwardly toward a proximal end of the deployment mechanism 103, rotation of rotating portion 110a causes axial movement of member 114b toward a proximal end of the device. Axial movement of member 114b toward a proximal end of the device results in forward advancement of the pusher component 118 within the hollow shaft 104. Such movement of pusher component 118 results in partially deployment of the shunt 115 from the shaft 104.
  • Figures 23 A to 23 C show schematics of the deployment mechanism at the end of the first stage of deployment of the shunt from the deployment device.
  • members 114a and 114b have finished traversing along first portions 113al and 113bl of channels 113a and 113b.
  • pusher component 118 has advanced within hollow shaft 104 ( Figure 23B), and shunt 115 has been partially deployed from the hollow shaft 104 ( Figure 23 C). As is shown in these figures, a portion of the shunt 115 extends beyond an end of the shaft 104.
  • the retraction component is engaged and the proximal portion of the deployment mechanism is retracted to within the distal portion of the deployment mechanism, thereby completing deployment of the shunt from the deployment device.
  • rotating portion 110a of the distal portion 110 of the deployment mechanism 103 is further rotated, resulting in movement of members 114a and 114b along second portions 113a2 and 113b2 in channels 113a and 113b. Since the second portion 113b2 of channel 113b is straight and runs perpendicular to the length of the rotating portion 110a, rotation of rotating portion 110a does not cause axial movement of member 114b. Without axial movement of member 114b, there is no further advancement of pusher 112.
  • Figure 24 A shows a schematic of the device 100 after deployment of the shunt 115 from the device 100.
  • Figure 24B shows a schematic of the deployment mechanism at the end of the second stage of deployment of the shunt from the deployment device.
  • members 114a and 114b have finished traversing along second portions 113al and 113bl of channels 113a and 113b.
  • proximal portion 109 has retracted to within distal portion 110, thus resulting in retraction of the hollow shaft 104 to within the housing 101.
  • Figure 24D shows an enlarged view of the distal portion of the deployment device after deployment of the shunt. This figure shows that the hollow shaft 104 is not fully retracted to within the housing 101 of the deployment device 100. However, in certain embodiments, the shaft 104 may completely retract to within the housing 101.

Abstract

La présente invention concerne de manière générale des dérivations intraoculaires et la diminution de la pression intraoculaire, en particulier, des dérivations intraoculaires conçues pour former une voie de drainage entre la chambre antérieur et l'espace intra-Tenon, et des procédés pour insérer de telles dérivations intraoculaires pour traiter le glaucome.
PCT/US2011/060798 2010-11-15 2011-11-15 Dérivations intraoculaires et procédés pour placer une dérivation intraoculaire dans l'espace intra-tenon WO2012068115A2 (fr)

Applications Claiming Priority (4)

Application Number Priority Date Filing Date Title
US12/946,542 2010-11-15
US12/946,572 US8852256B2 (en) 2010-11-15 2010-11-15 Methods for intraocular shunt placement
US12/946,572 2010-11-15
US12/946,542 US20120123316A1 (en) 2010-11-15 2010-11-15 Intraocular shunts for placement in the intra-tenon's space

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WO2012068115A2 true WO2012068115A2 (fr) 2012-05-24
WO2012068115A3 WO2012068115A3 (fr) 2014-04-10

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CN112998944A (zh) * 2015-06-03 2021-06-22 阿奎西斯公司 外路眼内分流器放置

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US20070123812A1 (en) * 2004-12-03 2007-05-31 Leonard Pinchuk Glaucoma Implant Device
US20090036818A1 (en) * 2002-05-29 2009-02-05 University Of Saskatchewan Shunt and Method Treatment of Glaucoma
US20100010416A1 (en) * 2006-01-17 2010-01-14 Juan Jr Eugene De Glaucoma treatment device
US20100234790A1 (en) * 2000-04-14 2010-09-16 Glaukos Corporation Ocular implant with therapeutic agents and methods thereof

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US20100234790A1 (en) * 2000-04-14 2010-09-16 Glaukos Corporation Ocular implant with therapeutic agents and methods thereof
US20090036818A1 (en) * 2002-05-29 2009-02-05 University Of Saskatchewan Shunt and Method Treatment of Glaucoma
US20070123812A1 (en) * 2004-12-03 2007-05-31 Leonard Pinchuk Glaucoma Implant Device
US20100010416A1 (en) * 2006-01-17 2010-01-14 Juan Jr Eugene De Glaucoma treatment device

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CN112998944A (zh) * 2015-06-03 2021-06-22 阿奎西斯公司 外路眼内分流器放置
US11612517B2 (en) 2015-06-03 2023-03-28 Aquesys, Inc. Ab externo intraocular shunt placement
CN112998944B (zh) * 2015-06-03 2023-08-22 阿奎西斯公司 外路眼内分流器放置

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