WO2013085643A1

WO2013085643A1 - Devices and methods for placing a shunt into the intra-scleral space

Info

Publication number: WO2013085643A1
Application number: PCT/US2012/063280
Authority: WO
Inventors: Christopher Horvath
Original assignee: Aquesys, Inc.
Priority date: 2011-12-08
Filing date: 2012-11-02
Publication date: 2013-06-13
Also published as: US9271869B2; US8852136B2; US20150045714A1; US20160135993A1; US20130150770A1; US9883969B2

Abstract

The present invention generally relates to intraocular shunts, and in particular, to intraocular shunts configured to form a drainage pathway between the anterior chamber and the intra-scleral space.

Description

DEVICES AND METHODS FOR PLACING A SHUNT INTO THE INTRA-SCLERAL

SPACE

Related Application

The present application claims the benefit of and priority to U.S. nonpro visional application serial number 13/314,939, filed December 8, 2011, the content of which is incorporated by reference herein in its entirety.

Field of the Invention

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- scleral space.

Background

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 is the second leading cause of blindness in the world, affecting 1 in 200 people under the age of fifty, and 1 in 10 over the age of eighty for a total of approximately 70 million people worldwide.

The importance of lowering intraocular pressure (IOP) in delaying glaucomatous progression has been well documented. When drug therapy fails, or is not tolerated, surgical intervention is warranted. 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. patent application publication number 2008/0108933, and U.S. patent number 6,007,511. Proper positioning of a shunt in the subconjunctival space is critical in determining the success or failure of subconjunctival glaucoma filtration surgery for a number of reasons. In particular, the location of the shunt has been shown to play a role in stimulating the formation of active drainage structures such as veins or lymph vessels. See, for example, U.S. patent application publication number 2008/0108933. In addition, it has been suggested that the conjunctiva itself plays a critical role in glaucoma filtration surgery. 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).

Summary

The present invention provides methods for implanting intraocular shunts in the intra- scleral space, thereby avoiding contact with the conjunctiva. Intra-scleral shunt placement safeguards the integrity of the conjunctiva to allow subconjunctival drainage pathways to successfully form. Additionally, the intra-scleral space is less prone to fibrosis than the subconjunctival space and placement in the intra-scleral space eliminates the risk of hypotony and related side effects.

Methods of the invention involve inserting into the eye a hollow shaft configured to hold an intraocular shunt, deploying the shunt from the hollow shaft such that the shunt forms a passage from the anterior chamber of the eye to the intra-scleral space of the eye, and

withdrawing the hollow shaft from the eye. The implanted shunt allows drainage of aqueous humor from an anterior chamber of the eye into the episcleral vessel complex, a traditional fluid drainage channel. Such placement also allows diffusion of fluid into the subconjunctival and suprachoroidal spaces.

Systems of the invention include a hollow shaft and an intraocular shunt, in which the hollow shaft is configured to hold the intraocular shunt. In the system, the shunt is configured to be deployed from the hollow shaft such that the shunt forms a passage from the anterior chamber of the eye to the intra-scleral space of the eye. The hollow shaft is configured to be inserted into the eye to deploy the shunt and withdrawn from the eye after the shunt is deployed. The shunt may be configured to be deployed between a sclera and a ciliary muscle of the eye. The hollow shaft may be configured for ab interno insertion into the eye. In certain embodiments, the hollow shaft is configured for ab interno insertion into the eye above the corneal limbus.

Alternatively, the hollow shaft is configured for ab interno insertion into the eye below the corneal limbus. The hollow shaft may be inserted into the eye without removing an anatomical feature of the eye, such as the trabecular meshwork, the iris, the cornea, and the aqueous humor. The system may be configured to deploy the shunt without inducing subconjunctival blebbing or endophthalmitis.

The intraocular shunts used with methods of the invention define a hollow body including 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-scleral space. In particular, the hollow body has a length sufficient to provide a passageway between the anterior chamber and the intra-scleral space.

In certain aspects, 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. In this manner, 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.

In other aspects, 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. Thus, the flexible portion of the shunt acts as a valve that regulates fluid flow through the shunt. After

implantation, 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. When the pressure exerted on the flexible portion of the shunt by the surrounding tissue is greater than the pressure exerted on the flexible portion of the shunt by the fluid flowing through the shunt, 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.

When the pressure exerted on the flexible portion of the shunt by the fluid flowing through the shunt is greater than the pressure exerted on the flexible portion of the shunt by the surrounding tissue, the flexible portion increases in diameter, increasing flow through the shunt. The increased flow results in aqueous humor leaving the anterior chamber at an increased rate. The flexible portion of the shunt may be any portion of the shunt. In certain embodiments, the flexible portion is a distal portion of the shunt. In certain embodiments, the entire shunt is composed of the flexible material.

Other aspects of the invention generally provide multi-port shunts. Such shunts reduce probability of the shunt clogging after implantation because fluid can enter or exit the shunt even if one or more ports of the shunt become clogged with particulate. In certain embodiments, 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. In certain embodiments, the proximal portion of the shunt (i.e., the portion disposed within the anterior chamber of the eye) includes more than one port and the distal portion of the shunt (i.e., the portion that is located in the intra-scleral space) includes a single port. In other embodiments, the proximal portion includes a single port and the distal portion includes more than one port. In still other embodiments, 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. 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.

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.

Other aspects of the invention generally provide shunts with overflow ports. Those shunts are configured such that the overflow port remains closed until there is a pressure buildup 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.

In certain embodiments, 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.

In certain embodiments, 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. Generally, the slit does not direct the fluid unless the outlet is obstructed. However, 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.

In other aspects, the invention generally provides a shunt having a variable inner diameter. In particular embodiments, the diameter increases from inlet to outlet of the shunt. By having a variable inner diameter that increases from inlet to outlet, a pressure gradient is produced and particulate that may otherwise clog the inlet of the shunt is forced through the inlet due to the pressure gradient. Further, the particulate will flow out of the shunt because the diameter only increases after the inlet.

In certain embodiments, 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-scleral 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 shunts discussed above and herein are described relative to the eye and, more particularly, in the context of treating glaucoma and solving the above identified problems relating to intraocular shunts. Nonetheless, it will be appreciated that shunts described herein may find application in any treatment of a body organ requiring drainage of a fluid from the organ and are not limited to the eye.

In other aspects, the invention generally provides shunts for facilitating conduction of fluid flow away from an organ, the shunt including a body, in which at least one end of the shunt is shaped to have a plurality of prongs. Such shunts reduce probability of the shunt clogging after implantation because fluid can enter or exit the shunt by any space between the prongs even if one portion of the shunt becomes clogged with particulate.

The shunt may have many different configurations. In certain embodiments, the proximal end of the shunt (i.e., the portion disposed within the anterior chamber of the eye) is shaped to have the plurality of prongs. In other embodiments, the distal end of the shunt (i.e., the portion that is located in an area of lower pressure with respect to the anterior chamber such as the intra-scleral space) is shaped to have the plurality of prongs. In other embodiments, both a proximal end and a distal end of the shunt are shaped to have the plurality of prongs. In particular embodiments, the shunt is a soft gel shunt.

In other aspects, the invention generally provides a shunt for draining fluid from an anterior chamber of an eye that 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 shunt being configured such that at least one end of the shunt includes a longitudinal slit. Such shunts reduce probability of the shunt clogging after implantation because the end(s) of the shunt can more easily pass particulate which would generally clog a shunt lacking the slits.

The shunt may have many different configurations. In certain embodiments, the proximal end of the shunt (i.e., the portion disposed within the anterior chamber of the eye) includes a longitudinal slit. In other embodiments, the distal end of the shunt (i.e., the portion that is located in an area of lower pressure with respect to the anterior chamber such as intra- scleral space) includes a longitudinal slit. In other embodiments, both a proximal end and a distal end of the shunt includes a longitudinal slit. In particular embodiments, the shunt is a soft gel shunt.

In certain embodiments, 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. Alternatively, the pharmaceutical and/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. Methods of coating and/or impregnating an intraocular shunt with a pharmaceutical and/or biological agent are known in the art. See for example, Darouiche (U.S. patent numbers

7,790,183; 6,719,991; 6,558,686; 6,162,487; 5,902,283; 5,853,745; and 5,624,704) and Yu et al. (U.S. patent application serial number 2008/0108933). The content of each of these references is incorporated by reference herein its entirety.

In certain embodiments, 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. In other embodiments, 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. In other embodiments, the exterior portion of the shunt that resides in the area of lower pressure (e.g., the intra-scleral space) after implantation is coated and/or impregnated with the pharmaceutical or biological agent. In embodiments in which the pharmaceutical or biological agent coats and/or impregnates the interior of the shunt, the agent may be flushed through the shunt and into the area of lower pressure (e.g., the intra-scleral 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, anti-VEGF (such as Lucintes, Macugen, Avastin, VEGF or steroids). Brief Description of the Drawings

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 along with an implanted intraocular shunt.

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 the tip bevel portion of a triple-ground needle tip. Figure 5B depicts the flat bevel portion of a triple-ground needle tip. Figure 5C depicts an intraocular shunt within a triple- ground needle tip.

Figure 6 provides a schematic of a shunt having a flexible portion. Figures 7A, 7B and 7C 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 8 shows different embodiments of multi-port shunts. Figure 8 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 8B 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 8C 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 9A and 9B show different embodiments of multi-port shunts having different diameter ports.

Figures 10A, 10B and IOC provide schematics of shunts having a slit located along a portion of the length of the shunt.

Figure 11 depicts a shunt having multiple slits along a length of the shunt.

Figure 12 depicts a shunt having a slit at a proximal end of the shunt.

Figure 13 provides a schematic of a shunt that has a variable inner diameter.

Figures 14A-D depict a shunt having multiple prongs at a distal and/or proximal end.

Figures 15A-D depict a shunt having a longitudinal slit at a distal and/or proximal end.

Figure 16 is a schematic showing an embodiment of a shunt deployment device according to the invention.

Figure 17 shows an exploded view of the device shown in Figure 16.

Figures 18A to 18D are schematics showing different enlarged views of the deployment mechanism of the deployment device.

Figures 19A to 19C are schematics showing interaction of the deployment mechanism with a portion of the housing of the deployment device.

Figure 20 shows a cross sectional view of the deployment mechanism of the deployment device.

Figures 21A and 21B show schematics of the deployment mechanism in a pre- deployment configuration. Figure 21C shows an enlarged view of the distal portion of the deployment device of Figure 21A. This figure shows an intraocular shunt loaded within a hollow shaft of the deployment device.

Figures 22A and 22B show schematics of the deployment mechanism at the end of the first stage of deployment of the shunt from the deployment device. Figure 22C shows an enlarged view of the distal portion of the deployment device of Figure 22A. This figure shows an intraocular shunt partially deployed from within a hollow shaft of the deployment device.

Figure 23A shows a schematic of the deployment device after deployment of the shunt from the device. Figure 23B show a schematic of the deployment mechanism at the end of the second stage of deployment of the shunt from the deployment device. Figure 23C shows an enlarged view of the distal portion of the deployment device after retraction of the shaft with the pusher abutting the shunt. Figure 23D shows an enlarged view of the distal portion of the deployment device after deployment of the shunt.

Detailed Description

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. In particular, Figure 2 shows a shunt 12 implanted in the sclera 8 (i.e., intra-scleral implantation). Placement of shunt 12 within the sclera 8 allows aqueous humor 3 to drain into traditional fluid drainage channels of the eye (e.g., the intra-scleral vein 9, the collector channel 10, Schlemm's canal 11, the trabecular outflow 13a, and the uveoscleral outflow 13b to the ciliary muscle 14.

In conditions of glaucoma, the pressure of the aqueous humor in the eye (anterior chamber) 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 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

subarachnoid space. Methods of implanting intraocular shunts are known in the art. 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. Briefly and with reference to Figure 3, 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.

While such ab interno subconjunctival filtration procedures have been successful in relieving intraocular pressure, there is a substantial risk that the intraocular shunt may be deployed too close to the conjunctiva, resulting in irritation and subsequent inflammation and/or scarring of the conjunctiva, which can cause the glaucoma filtration procedure to fail (See Yu et al., Progress in Retinal and Eye Research, 28: 303-328 (2009)). Additionally, commercially available 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 methods for implanting intraocular shunts within the sclera (i.e., intra-scleral implantation) and are thus suitable for use in an ab interno glaucoma filtration procedure. In methods of the invention, the implanted shunt forms a passage from the anterior chamber of the eye into the sclera (i.e., intra-scleral space). Design and/or deployment of an intraocular shunt such that the inlet terminates in the anterior chamber and the outlet terminates intra-scleral safeguards the integrity of the conjunctiva to allow subconjunctival drainage pathways to successfully form. Additionally, drainage into the intra-scleral space provides access to more lymphatic channels than just the conjunctival lymphatic system, such as the episcleral lymphatic network. Moreover, design and/or deployment of an intraocular shunt such that the outlet terminates in the intra-scleral space avoids having to pierce Tenon's capsule which can otherwise cause complications during glaucoma filtration surgery due to its tough and fibrous nature.

Devices and Methods for Intra-scleral Shunt Placement

The devices and methods of the invention involve inserting into the eye a hollow shaft configured to hold an intraocular shunt. In certain embodiments, 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 into the sclera (i.e., the intra-scleral space). The hollow shaft is then withdrawn from the eye.

Referring to Figure 2, 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-scleral space. To place the shunt within the eye, a surgical intervention to implant the shunt is performed that involves inserting into the eye a deployment device that holds an intraocular shunt, and deploying at least a portion of the shunt within intra-scleral space. In certain embodiments, a hollow shaft of a deployment device holding the shunt enters the eye through the cornea (ab interno approach). The shaft is advanced across the anterior chamber in what is referred to as a transpupil implant insertion. The shaft is advanced into the sclera 8 until a distal portion of the shaft is in proximity to the trabecular outflow 13b. Insertion of the shaft of the deployment device into the sclera 8 produces a long scleral channel of about 3mm to about 5mm in length. Withdrawal of the shaft of the deployment device prior to deployment of the shunt 12 from the device produces a space in which the shunt 12 may be deployed. Deployment of the shunt 12 allows for aqueous humor 3 to drain into traditional fluid drainage channels of the eye (e.g., the intra-scleral vein 9, the collector channel 10, Schlemm's canal 11, the trabecular outflow 13a, and the uveoscleral outflow 13b to the ciliary muscle 14.

Figure 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. Alternatively, the hollow shaft may hold the shunt on an outer surface 25 of the shaft. In particular embodiments, the shunt is held within the hollow interior of the shaft 24, as is shown in Figure 4. Generally, in one embodiment, 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 μιη, an outside diameter of approximately 100-450 μιη, and a length of approximately 1-12 mm. In particular embodiments, the shunt has a length of approximately 2-10 mm and an outside diameter of approximately 150-400 μιη. The hollow shaft 22 is configured to at least hold a shunt of such shape and such dimensions. However, 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.

Preferably, the methods of the invention are conducted by making an incision in the eye prior to insertion of the deployment device. Although in particular embodiments, the methods of the invention may be conducted without making an incision in the eye prior to insertion of the deployment device. In certain embodiments, the shaft that is connected to the deployment device has a sharpened point or tip. In certain embodiments, the hollow shaft is a needle. Exemplary needles that may be used are commercially available from Terumo Medical Corp. (Elkington Md). In a particular embodiment, the needle has a hollow interior and a beveled tip, and the intraocular shunt is held within the hollow interior of the needle. In another particular embodiment, 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 configured to hold the intraocular shunt through the cornea, across the anterior chamber, through the trabecular meshwork and into the sclera. However, the methods of the invention may be conducted using an ab externo approach.

When the methods of the invention are conducted using an ab interno approach, the angle of entry through the cornea affects optimal placement of the shunt in the intra-scleral space. Preferably, 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. For example, 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,

approximately 1.3 mm, approximately 1.4 mm, approximately 1.5 mm, approximately 1.6 mm, approximately 1.7 mm, approximately 1.8 mm, approximately 1.9 mm or approximately 2.0 mm above the corneal limbus.

Without intending to be bound by any theory, 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-scleral space so that there is less bending of the shunt.

In certain embodiments, to ensure proper positioning and functioning of the intraocular shunt, the depth of penetration into the sclera is important when conducting the methods of the invention. In one embodiment, 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. Preferably, a distal portion of the hollow shaft (as opposed to the distal tip) completely enters the sclera before the shunt is deployed from the hollow shaft. In certain embodiments, 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. In a preferred embodiment of the methods of the invention, the needle is advanced even further such that the entire flat bevel penetrates into the sclera, 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 5A-5C. Without intending to be bound by any theory, if 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 entry of the flat bevel into 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.

Intraocular Shunts of the Invention

The present invention provides intraocular shunts that are configured to form a drainage pathway from the anterior chamber of the eye to the intra-scleral space. In particular, 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-scleral space. The length of the shunt is important for achieving placement specifically in the intra-scleral space. A shunt that is too long will extend beyond the intra-scleral 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

conjunctival lymphatic system.

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-scleral space. Exemplary shunts range in length from approximately 2 mm to approximately 10 mm or between approximately 4 mm to approximately 8 mm, or any specific value within said ranges. In certain embodiments, 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 methods of the invention may be conducted using any commercially available shunts, such as the Optonol Ex-

PRESS mini Glaucoma shunt, and the Solx DeepLight Gold Micro-Shunt.

In particular embodiments, the intraocular shunts of the invention are flexible, and have an elasticity modulus that is substantially identical to the elasticity modulus of the surrounding tissue in the implant site. As such, the intraocular shunts of the invention are easily bendable, do not erode or cause a tissue reaction, and do not migrate once implanted. Thus, when implanted in the eye using an ab interno procedure, such as the methods described herein, the intraocular shunts of the invention do not induce substantial ocular inflammation such as subconjunctival blebbing or endophthalmitis. Additional exemplary features of the intraocular shunts of the invention are discussed in further detail below.

Tissue compatible shunts

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:

d stress

A ----- —

strain

where lambda (λ) is the elastic modulus; stress is the force causing the deformation divided by the area to which the force is applied; and 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. For further description regarding elasticity modulus and Young's modulus, see for example Gere (Mechanics of Materials, 6 Edition, 2004, Thomson), the content of which is incorporated by reference herein in its entirety.

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

Engineering and Computer Science Department University of Michigan Ann Arbor, MI 48109- 2125; and Institute of Mathematical Problems in Biology Russian Academy of Sciences, Pushchino, Moscow Region 142292 Russia); Chen et al. (IEEE Trans. Ultrason. Ferroelec. Freq. Control 43: 191-194, 1996); Hall, (In 1996 Ultrasonics Symposium Proa, pp.1193-1196, IEEE Cat. No. 96CH35993, IEEE, New York, 1996); and Parker (Ultrasound Med. Biol. 16:241-246, 1990), each of which provides methods of determining the elasticity modulus of body tissues. The content of each of these is incorporated by reference herein in its entirety.

The elasticity modulus of tissues of different organs is known in the art. For example, Pierscionek et al. (Br J Ophthalmol, 91:801-803, 2007) and Friberg (Experimental Eye Research, 473:429-436, 1988) show the elasticity modulus of the cornea and the sclera of the eye. The content of each of these references is incorporated by reference herein in its entirety. Chen, Hall, and Parker show the elasticity modulus of different muscles and the liver. Erkamp shows the elasticity modulus of the kidney.

Shunts of the invention are composed of a material that is compatible with an elasticity modulus of tissue surrounding the shunt. In certain embodiments, the material has an elasticity modulus that is substantially identical to the elasticity modulus of the tissue surrounding the shunt. In other embodiments, 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.

In particular embodiments, 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. In certain embodiments, 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 10⁶ N/m², and 1.8 + 1.1 x 10⁶ N/m² 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. In certain embodiments, 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

approximately 10 μιη to approximately 250 μιη, an outside diameter from approximately 100 μιη to approximately 450 μιη, and a length from approximately 2 mm to approximately 10 mm.

Shunts reactive to pressure

In other aspects, 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 6 provides a schematic of a shunt 23 having a flexible portion 51 (thicker black lines). In this figure, the flexible portion 51 is shown in the middle of the shunt 23. However, the flexible portion 51 may be located in any portion of the shunt, such as the proximal or distal portion of the shunt. In certain embodiments, 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 μΐ/min for approximately 3 ml/day. The entire aqueous volume is about 0.25 ml. When the pressure in the anterior chamber falls after surgery to about 7-8 mmHg, it is assumed the majority of the aqueous humor is exiting the eye through the implant since venous backpressure prevents any significant outflow through normal drainage structures (e.g., the trabecular meshwork).

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. The flow through the shunt, and thus the pressure exerted by the fluid on the shunt, is calculated by the equation:

where Φ 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); T| is the dynamic fluid viscosity (pascal- second (Pa- s)); and L is the total length of the tube in the x direction (meters).

Figure 7A 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-scleral 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 7 A, the flexible portion spans an entire length of the sclera 31.

When the pressure exerted on the flexible portion 30 of the shunt 26 by sclera 31 (vertical arrows) is greater than the pressure exerted on the flexible portion 30 of the shunt 26 by the fluid flowing through the shunt (horizontal arrow), the flexible portion 30 decreases in diameter, restricting flow through the shunt 26 (Figure 7B). The restricted flow results in aqueous humor leaving the anterior chamber 28 at a reduced rate.

When the pressure exerted on the flexible portion 20 of the shunt 26 by the fluid flowing through the shunt (horizontal arrow) is greater than the pressure exerted on the flexible portion 30 of the shunt 26 by the sclera 31 (vertical arrows), the flexible portion 30 increases in diameter, increasing flow through the shunt 26 (Figure 7C). The increased flow results in aqueous humor leaving the anterior chamber 28 at an increased rate.

In a particular embodiments, the shunt has a length of about 6 mm and an inner diameter of about 64 μιη. 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.

It will be appreciated that different dimensioned implants may be used. For example, shunts that range in length from about 2 mm to about 10 mm and have a range in inner diameter from about 10 μιη to about 100 μιη 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. In certain embodiments, 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 μιη thick to about 100 μιη thick.

In a certain embodiment, 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. In addition to gelatins, the flexible portion may be made of hydroxypropyl methycellulose (HPMC), collagen, polylactic acid, polylglycolic acid, hyaluronic acid and glycosaminoglycans.

In certain embodiments, 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. In a particular embodiment, the formed gelatin is treated with a solution of 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). Cross-linking by radiation, such as gamma or electron beam (e-beam) may be alternatively employed.

In one embodiment, the gelatin is contacted with a solution of approximately 25% glutaraldehyde for a selected period of time. One suitable form of 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.

Methods for forming the flexible portion of the shunt are shown for example in Yu et al.

(U.S. patent application number 2008/0108933), the content of which is incorporated by reference herein in its entirety. In an exemplary protocol, 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. In one embodiment, the ratio of solid gelatin to water is approximately 10% to 50% gelatin by weight to 50% to 90% by weight of water. In an embodiment, 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).

Once the gelatin solution has been prepared, in accordance with the method described above, 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.

Typically, 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. In addition, it is preferred that a the tube be removed at a constant rate in order to provide the desired coating. To ensure that the gelatin is spread evenly over the surface of the wire, in one embodiment, 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. Once the wires have been sufficiently coated with 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).

Once dried, the formed flexible portions may be treated with a cross-linking agent. In one embodiment, 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. In one embodiment, 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.

Where a cross-linking agent is used, 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.

After the requisite drying period, the formed and cross-linked flexible portion is removed from the underlying supports or wires. In one embodiment, wire tubes may be cut at two ends and the formed gelatin flexible portion slowly removed from the wire support. In another embodiment, wires with gelatin film thereon, may be pushed off using a plunger or tube to remove the formed gelatin flexible portion. Multi-port shunts

Other aspects of the invention generally provide multi-port shunts. Such shunts reduce probability of the shunt clogging after implantation because fluid can enter or exit the shunt even if one or more ports of the shunt become clogged with particulate. In certain embodiments, 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 drainage structures associated with the intra-scleral space.

The shunt may have many different configurations. Figure 8 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-scleral space) includes a single port 34. Figure 8B 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 8C 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 8 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. For example, 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 8A, 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 9 A 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 9A shows that port 33b has an inner diameter that is different from the inner diameters of ports 33a and 34. In this figure, 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 μιη to about 40 μιη, particularly about 30 μιη. In other embodiments, the inner diameter of port 33b is greater than the inner diameter of ports 33a and 34. See for example Figure 9B.

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

Other aspects of the invention generally provide 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.

In certain embodiments, 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-scleral space, the body further including at least one slit. The slit may be located at any place along the body of the shunt. Figure 10A shows a shunt 35 having an inlet 36, an outlet 37, and a slit 38 located in proximity to the inlet 36. Figure 10B shows a shunt 35 having an inlet 36, an outlet 37, and a slit 39 located in proximity to the outlet 37. Figure IOC 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.

While Figure 10 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. For example, Figure 11 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. In certain embodiments, shunts of the invention include two slits that overlap and are oriented at 90° to each other, thereby forming a cross.

In certain embodiments, 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 12 shows an

embodiment of 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.

In certain embodiments, 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 μιη to about 200 μιη. Generally, the slit does not direct the fluid unless the outlet is obstructed.

However, 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.

approximately 10 μιη to approximately 250 μιη, an outside diameter from approximately 100 μιη to approximately 450 μιη, and a length from approximately 2 mm to approximately 10 mm. 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 having a variable inner diameter In other aspects, the invention generally provides a shunt having a variable inner diameter. In particular embodiments, the diameter increases from inlet to outlet of the shunt. By having a variable inner diameter that increases from inlet to outlet, a pressure gradient is produced and particulate that may otherwise clog the inlet of the shunt is forced through the inlet due to the pressure gradient. Further, the particulate will flow out of the shunt because the diameter only increases after the inlet.

Figure 13 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. In certain embodiments, the inner diameter continuously increases along the length of the body, for example as shown in Figure 13. In other embodiments, the inner diameter remains constant along portions of the length of the body.

In exemplary embodiments, the inner diameter may range in size from about 10 μιη to about 200 μιη, and the inner diameter at the outlet may range in size from about 15 μιη to about 300 μιη. 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. In certain embodiments, 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

approximately 10 μιη to approximately 250 μιη, an outside diameter from approximately 100 μιη to approximately 450 μιη, and a length from approximately 2 mm to approximately 10 mm. 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 having pronged ends

In other aspects, the invention generally provides shunts for facilitating conduction of fluid flow away from an organ, the shunt including a body, in which at least one end of the shunt is shaped to have a plurality of prongs. Such shunts reduce probability of the shunt clogging after implantation because fluid can enter or exit the shunt by any space between the prongs even if one portion of the shunt becomes clogged with particulate. Figures 14A-D show embodiments of a shunt 52 in which at least one end of the shunt 52 includes a plurality of prongs 53a-d. Figures 14A-D show an embodiment in which both a proximal end and a distal end of the shunt are shaped to have the plurality of prongs. However, numerous different configurations are envisioned. For example, in certain embodiments, only the proximal end of the shunt is shaped to have the plurality of prongs. In other embodiments, only the distal end of the shunt is shaped to have the plurality of prongs.

Prongs 53a-d can have any shape (i.e., width, length, height). Figures 14A-B show prongs 53a-d as straight prongs. In this embodiment, the spacing between the prongs 53a-d is the same. In another embodiment shown in Figures 14C-D, prongs 53a-d are tapered. In this embodiment, the spacing between the prongs increases toward a proximal and/or distal end of the shunt 52.

Figures 14A-D show embodiments that include four prongs. However, shunts of the invention may accommodate any number of prongs, such as two prongs, three prongs, four prongs, five prongs, six prongs, seven prongs, eight prongs, nine prongs, ten prongs, etc. The number of prongs chosen will depend on the desired flow characteristics of the shunt.

approximately 10 μιη to approximately 250 μιη, an outside diameter from approximately 100 μιη to approximately 450 μιη, and a length from approximately 2 mm to approximately 10 mm. 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 having a longitudinal slit

Figures 15A-D show embodiments of a shunt 54 in which at least one end of the shunt 54 includes a longitudinal slit 55 that produces a top portion 56a and a bottom portion 56b in a proximal and/or distal end of the shunt 54. Figures 15A-D show an embodiment in which both a proximal end and a distal end include a longitudinal slit 55 that produces a top portion 56a and a bottom portion 56b in both ends of the shunt 54. However, numerous different configurations are envisioned. For example, in certain embodiments, only the proximal end of the shunt includes longitudinal slit 55. In other embodiments, only the distal end of the shunt includes longitudinal slit 55.

Longitudinal slit 55 can have any shape (i.e., width, length, height). Figures 15A-B show a longitudinal slit 55 that is straight such that the space between the top portion 56a and the bottom portion 56b remains the same along the length of the slit 55. In another embodiment shown in Figures 15C-D, longitudinal slit 55 is tapered. In this embodiment, the space between the top portion 45a and the bottom portion 56b increases toward a proximal and/or distal end of the shunt 54.

approximately 10 μιη to approximately 250 μιη, an outside diameter from approximately 100 μιη to approximately 450 μιη, and a length from approximately 2 mm to approximately 10 mm. 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.

Pharmaceutical A ents

In certain embodiments, 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. Alternatively, 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. Methods of coating and/or impregnating an intraocular shunt with a pharmaceutical and/or biological agent are known in the art. See for example, Darouiche (U.S. patent numbers

In certain embodiments, 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. In other embodiments, 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. In other embodiments, the exterior portion of the shunt that resides in the intra- scleral space after implantation is coated and/or impregnated with the pharmaceutical or biological agent. In embodiments in which the pharmaceutical or biological agent coats and/or impregnates the interior of the shunt, the agent may be flushed through the shunt and into the area of lower pressure (e.g., the intra-scleral space).

Mitomycin-C or 5-Fluorouracil, anti-VEGF (such as Lucintes, Macugen, Avastin, VEGF or steroids).

Deployment Devices

Deployment into the eye of an intraocular shunt according to 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 deploying shunts according to 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 which are each incorporated herein by reference in their entireties. In other embodiments, the deployment devices are devices as described in co-pending and co-owned U.S. nonpro visional patent application serial number 12/946,222 filed on November 15, 2010, or deployment devices described in co-pending and co-owned U.S. nonpro visional patent application serial number 12/946,645 filed on November 15, 2010, the entire content of each of which is incorporated by reference herein.

In still other embodiments, the shunts according to the invention are deployed into the eye using the deployment device 100 depicted in Figure 16. While Figure 16 shows a handheld manually operated shunt deployment device, it will be appreciated that devices of the invention may be coupled with robotic systems and may be completely or partially automated. As shown in Figure 16, 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. 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. For example, housing 101 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. In certain embodiments, housing 101 is made of a material that may be autoclaved, and thus allow for housing 101 to be re-usable. Alternatively, 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 17 shows an exploded view of deployment device 100. In this figure, 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 101. Housing 101 is designed such that components of deployment mechanism 103 are movable within housing 101.

Figures 18A to 18D 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. For example, 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. In certain

embodiments, deployment mechanism 103 is made of a material that may be autoclaved, and thus allow for deployment mechanism 103 to be re-usable. Alternatively, 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.

In this embodiment, 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. In other embodiments, 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. Alternatively, the hollow shaft 104 may be permanently coupled to the proximal portion 109 of the deployment mechanism 103.

Generally, 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. In certain embodiments, the shaft is straight. In other embodiments, shaft is of a shape other than straight, for example a shaft having a bend along its length.

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 18 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 19A and 19B). During assembly, 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 19C). Assembled, the protrusion 117 interacts with the stationary portion 110b of the deployment mechanism 103 and prevents rotation of stationary portion 110b. In this configuration, rotating portion 110a is free to rotate within housing component 101a.

Referring back to Figure 18, the rotating portion 110a of distal portion 110 of 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.

Within each of 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 20 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.

Reference is now made to Figures 21-23, which accompany the following discussion regarding deployment of a shunt 115 from deployment device 100. Figure 21A shows deployment device 100 is a pre-deployment configuration. In this configuration, shunt 115 is loaded within hollow shaft 104 (Figure 21C). As shown in Figure 21C, 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. In other embodiments, 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.

Additionally, in the pre-deployment configuration, a portion of the shaft 104 extends beyond the housing 101 (Figure 21C). 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 21B). In this

configuration, 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 21A). In this configuration, 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.

Once the device has been inserted into the eye and advanced to a location to where the shunt will be deployed, the shunt 115 may be deployed from the device 100. 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.

In the first stage of shunt deployment, the pusher component is engaged and the pusher partially deploys the shunt from the deployment device. During the first stage, 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. Since the 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 22A to 22C show schematics of the deployment mechanism at the end of the first stage of deployment of the shunt from the deployment device. As is shown Figure 22A, members 114a and 114b have finished traversing along first portions 113al and 113bl of channels 113a and 113b. Additionally, pusher component 118 has advanced within hollow shaft 104 (Figure 22B), and shunt 115 has been partially deployed from the hollow shaft 104 (Figure 22C). As is shown in these figures, a portion of the shunt 115 extends beyond an end of the shaft 104.

In the second stage of shunt deployment, 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. During the second stage, 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. Since the second portion 113a2 of channel 113a runs diagonally along the length of the rotating portion 110a, downwardly toward a distal end of the deployment mechanism 103, rotation of rotating portion 110a causes axial movement of member 114a toward a distal end of the device. Axial movement of member 114a toward a distal end of the device results in retraction of the proximal portion 109 to within the distal portion 110 of the deployment mechanism 103.

Retraction of the proximal portion 109, results in retraction of the hollow shaft 104. Since the shunt 115 abuts the pusher component 118, the shunt remains stationary at the hollow shaft 104 retracts from around the shunt 115 (Figure 22C). The shaft 104, retracts almost completely to within the housing 101. During both stages of the deployment process, the housing 101 remains stationary and in a fixed position.

Figure 22A shows a schematic of the device 100 after deployment of the shunt 115 from the device 100. Figure 22B shows a schematic of the deployment mechanism at the end of the second stage of deployment of the shunt from the deployment device. As is shown in Figure 22B, members 114a and 114b have finished traversing along second portions 113al and 113bl of channels 113a and 113b. Additionally, 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 22D 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.

Incorporation by Reference

References and citations to other documents, such as patents, patent applications, patent publications, journals, books, papers, web contents, have been made throughout this disclosure. All such documents are hereby incorporated herein by reference in their entirety for all purposes.

Equivalents

The invention may be embodied in other specific forms without departing from the spirit or essential characteristics thereof. The foregoing embodiments are therefore to be considered in all respects illustrative rather than limiting on the invention described herein. Scope of the invention is thus indicated by the appended claims rather than by the foregoing description, and all changes which come within the meaning and range of equivalency of the claims are therefore intended to be embraced therein.

Claims

What is Claimed is:

1. A system for deploying an intraocular shunt into an eye, the system comprising:

a hollow shaft and an intraocular shunt, wherein the hollow shaft is configured to hold the intraocular shunt;

the shunt is configured to be deployed from the hollow shaft such that the shunt forms a passage from the anterior chamber of the eye to the intra-scleral space of the eye; and

the hollow shaft is configured to be inserted into the eye to deploy the shunt and withdrawn from the eye after the shunt is deployed.

2. The system according to claim 1, wherein the shunt is configured to be deployed between a sclera and a ciliary muscle of the eye.

3. The system according to claim 1, wherein the shunt is a soft gel shunt.

4. The system of claim 1, wherein the hollow shaft is configured for ab interno insertion into the eye.

5. The system of claim 4, wherein the hollow shaft is configured for ab interno insertion into the eye above the corneal limbus.

6. The system of claim 4, wherein the hollow shaft is configured for ab interno insertion into the eye below the corneal limbus.

7. The system of claim 1, characterized in that the hollow shaft is inserted into the eye without removing an anatomical feature of the eye.

8. The system of claim 7, characterized in that the anatomical feature of the eye is selected from the group consisting of: the trabecular meshwork, the iris, the cornea, and the aqueous humor.

9. The system of claim 1, wherein the system is configured to deploy the shunt without inducing subconjunctival blebbing or endophthalmitis.

10. The system according to claim 1, wherein the shunt is configured to drain fluid from an anterior chamber into an episcleral vessel complex of the eye.

11. The system according to claim 1, wherein the shunt is from about 2mm to about 10 mm.

12. The system according to claim 1, wherein the shunt comprising a material that has an elasticity modulus that is compatible with an elasticity modulus of tissue surrounding the shunt.

13. The system according to claim 12, wherein the material has an elasticity modulus that is substantially identical to the elasticity modulus of the tissue surrounding the shunt.

14. The system according to claim 12, wherein the material has an elasticity modulus that is greater than the elasticity modulus of the tissue surrounding the shunt.

15. The system according to claim 1, wherein the shunt comprises a hollow body, wherein at least a portion of the body is comprised of a flexible material that allows for fluctuation of an inner diameter of the portion of the shaft based upon pressure exerted from surrounding tissue and/or fluid in the organ.

16. The system according to claim 15, wherein the portion of the body that is comprised of the flexible material is a distal portion of the body.

17. The system according to claim 15, wherein the portion of the body that is comprised of the flexible material is a middle portion of the body.

18. The system according to claim 15, wherein the entire shaft comprises the flexible material.

19. The system according to claim 1, wherein the shunt comprises more than two ports.

20. The system according to claim 19, wherein the proximal portion comprises more than one port and the distal portion comprises a single port.

21. The system according to claim 19, wherein the proximal portion comprises a single port and the distal portion comprises more than one port.

22. The system according to claim 19, wherein the proximal and the distal portions comprise more than one port.

23. The system according to claim 19, wherein at least one of the ports is oriented 90° to the length of the body.

24. The system according to claim 19, wherein at least one of the ports is oriented at an angle to the length of the body.

25. The system according to claim 1, wherein the shunt comprises a body having at least one slit.

26. The system according to claim 25, wherein the slit is located in proximity to the inlet.

27. The system according to claim 26, wherein the slit has a width that is substantially the same or less than an inner diameter of the inlet.

28. The system according to claim 25, wherein the slit is located in proximity to the outlet.

29. The system according to claim 28, wherein the slit has a width that is substantially the same or less than an inner diameter of the outlet.

30. The system according to claim 28, wherein the slit does not direct the fluid unless the outlet is obstructed.

31. The system according to claim 25, wherein both the inlet and the outlet comprise a slit.

32. The system according to claim 1, wherein shunt comprises a body having a variable inner diameter that increases along the length of the body length from the inlet to the outlet.

33. The system according to claim 32, wherein the inner diameter continuously increases along the length of the body.

34. The system according to claim 32, wherein the inner diameter remains constant along portions of the length of the body.

35. A method of deploying an intraocular shunt into an eye, the method comprising the steps of: inserting into the eye a hollow shaft configured to hold the intraocular shunt,

deploying the shunt from the hollow shaft such that the shunt forms a passage from the anterior chamber of the eye to the intra-scleral space of the eye; and

withdrawing the hollow shaft from the eye.

36. The method according to claim 35, wherein the shunt is deployed between a sclera and a ciliary muscle of the eye.

37. The method according to claim 35, wherein the shunt is a soft gel shunt.

38. The method of claim 35, wherein the inserting step comprises ab interno insertion of the hollow shaft into the eye.

39. The method of claim 38, wherein ab interno insertion comprises inserting the hollow shaft into the eye above the corneal limbus.

40. The method of claim 38, wherein ab interno insertion comprises inserting the hollow shaft into the eye below the corneal limbus.

41. The method of claim 35, wherein the hollow shaft is inserted into the eye without removing an anatomical feature of the eye.

42. The method of claim 41, wherein the anatomical feature of the eye is selected from the group consisting of: the trabecular meshwork, the iris, the cornea, and the aqueous humor.

43. The method of claim 35, wherein the method is performed without inducing

subconjunctival blebbing or endophthalmitis.

44. The method according to claim 35, wherein the shunt drains fluid from an anterior chamber into an episcleral vessel complex of the eye.

45. The method according to claim 35, wherein the shunt is from about 2mm to about 10 mm.

46. The method according to claim 35, wherein the shunt comprising a material that has an elasticity modulus that is compatible with an elasticity modulus of tissue surrounding the shunt.

47. The method according to claim 46, wherein the material has an elasticity modulus that is substantially identical to the elasticity modulus of the tissue surrounding the shunt.

48. The method according to claim 46, wherein the material has an elasticity modulus that is greater than the elasticity modulus of the tissue surrounding the shunt.

49. The method according to claim 35, wherein the shunt comprising a hollow body, wherein at least a portion of the body is comprised of a flexible material that allows for fluctuation of an inner diameter of the portion of the shaft based upon pressure exerted from surrounding tissue and/or fluid in the organ.

50. The method according to claim 49, wherein the portion of the body that is comprised of the flexible material is a distal portion of the body.

51. The method according to claim 49, wherein the portion of the body that is comprised of the flexible material is a middle portion of the body.

52. The method according to claim 49, wherein the entire shaft comprises the flexible material.

53. The method according to claim 35, wherein the shunt comprises more than two ports.

54. The method according to claim 53, wherein the proximal portion comprises more than one port and the distal portion comprises a single port.

55. The method according to claim 53, wherein the proximal portion comprises a single port and the distal portion comprises more than one port.

56. The method according to claim 53, wherein the proximal and the distal portions comprise more than one port.

57. The method according to claim 53, wherein at least one of the ports is oriented 90° to the length of the body.

58. The method according to claim 53, wherein at least one of the ports is oriented at an angle to the length of the body.

59. The method according to claim 35, wherein the shunt comprises a body having at least one slit.

60. The method according to claim 59, wherein the slit is located in proximity to the inlet.

61. The method according to claim 60, wherein the slit has a width that is substantially the same or less than an inner diameter of the inlet.

62. The method according to claim 60, wherein the slit is located in proximity to the outlet.

63. The method according to claim 62, wherein the slit has a width that is substantially the same or less than an inner diameter of the outlet.

64. The method according to claim 62, wherein the slit does not direct the fluid unless the outlet is obstructed.

65. The method according to claim 59, wherein both the inlet and the outlet comprise a slit.

66. The method according to claim 35, wherein shunt comprises a body having a variable inner diameter that increases along the length of the body length from the inlet to the outlet.

67. The method according to claim 66, wherein the inner diameter continuously increases along the length of the body.

68. The method according to claim 66, wherein the inner diameter remains constant along portions of the length of the body.