US20060173545A1 - Spinal disc annulus reconstruction method and deformable spinal disc annulus stent - Google Patents

Abstract

A spinal disc annulus repair stent for repair and reconstruction of the spinal disc wall (annulus) after surgical invasion or pathologic rupture, which may incorporate suture closure or other means of stent insertion and fixation, designed to reduce the failure rate of conventional surgical procedures on the spinal discs. In an illustrative embodiment, the design of the spinal disc annulus stent advantageously allows ingrowth of normal cells of healing in an enhanced fashion strengthening the normal reparative process.

Description

CROSS-REFERENCE TO A RELATED APPLICATION
• This application is a continuation of U.S. application Ser. No. 10/352,981, filed Jan. 29, 2003, now pending. U.S. patent application Ser. No. 10/352,981 is a continuation-in-part of U.S. patent application Ser. No. 10/133,339, filed Apr. 29, 2002, now pending, which is a continuation-in-part of U.S. patent application Ser. No. 09/947,078, filed Sep. 5, 2001, now U.S. Pat. No. 6,592,625, which is a continuation of U.S. patent application Ser. No. 09/484,706, filed Jan. 18, 2000, now abandoned, which claims the benefit of U.S. Provisional Application No. 60/160,710, filed Oct. 20, 1999. U.S. patent application Ser. No. 10/352,981 is also a continuation-in-part of U.S. patent application Ser. No. 10/075,615, filed on Feb. 15, 2002, now pending, and it also claims the benefit of U.S. Provisional Application No. 60/309,105, filed Jul. 31, 2001. The entire contents of each of the above are incorporated herein by reference.
FIELD OF THE INVENTION
• The invention generally relates to methods and implantable medical devices for the closure, sealing, and/or repair of an aperture in the intervertebral disc annulus. The term “aperture” refers to a hole in the annulus that is a result of a surgical incision into the intervertebral disc annulus, or the consequence of a naturally occurring tear (rent). The invention generally relates to surgical devices and methods for intervertebral disc wall repair or reconstruction. The invention further relates to an annular repair device, or stent, for annular disc repair. These stents can be of natural or synthetic materials. The effects of said reconstruction are restoration of disc wall integrity and reduction of the failure rate (3-21%) of a common surgical procedure (disc fragment removal or discectomy). This surgical procedure is performed about 390,000 times annually in the United States.
BACKGROUND OF THE INVENTION
• The spinal column is formed from a number of bony vertebrae, which in their normal state are separated from each other by intervertebral discs. These discs are comprised of the annulus fibrosus, and the nucleus pulposus, both of which are soft tissue. The intervertebral disc acts in the spine as a crucial stabilizer, and as a mechanism for force distribution between adjacent vertebral bodies. Without the disc, collapse of the intervertebral space occurs in conjunction with abnormal joint mechanics and premature development of arthritic changes.
• The normal intervertebral disc has an outer ligamentous ring called the annulus surrounding the nucleus pulposus. The annulus binds the adjacent vertebrae together and is constituted of collagen fibers that are attached to the vertebrae and cross each other so that half of the individual fibers will tighten as the vertebrae are rotated in either direction, thus resisting twisting or torsional motion. The nucleus pulposus is constituted of loose tissue, having about 85% water content, which moves about during bending from front to back and from side to side.
• The aging process contributes to gradual changes in the intervertebral discs. The annulus loses much of its flexibility and resilience, becoming more dense and solid in composition. The aging annulus may also be marked by the appearance or propagation of cracks or fissures in the annular wall. Similarly, the nucleus desiccates, increasing viscosity and thus losing its fluidity. In combination, these features of the aged intervertebral discs result in less dynamic stress distribution because of the more viscous nucleus pulposus, and less ability to withstand localized stresses by the annulus fibrosus due to its desiccation, loss of flexibility, and the presence of fissures. Fissures can also occur due to disease or other pathological conditions. Occasionally fissures may form rents through the annular wall. In these instances, the nucleus pulposus is urged outwardly from the subannular space through a rent, often into the spinal column. Extruded nucleus pulposus can, and often does, mechanically press on the spinal cord or spinal nerve rootlet. This painful condition is clinically referred to as a ruptured or herniated disc.
• In the event of annulus rupture, the subannular nucleus pulposus migrates along the path of least resistance forcing the fissure to open further, allowing migration of the nucleus pulposus through the wall of the disc, with resultant nerve compression and leakage of chemicals of inflammation into the space around the adjacent nerve roots supplying the extremities, bladder, bowel, and genitalia. The usual effect of nerve compression and inflammation is intolerable back or neck pain, radiating into the extremities, with accompanying numbness, weakness, and in late stages, paralysis and muscle atrophy, and/or bladder and bowel incontinence. Additionally, injury, disease, or other degenerative disorders may cause one or more of the intervertebral discs to shrink, collapse, deteriorate, or become displaced, herniated, or otherwise damaged and compromised.
• The surgical standard of care for treatment of herniated, displaced, or ruptured intervertebral discs is fragment removal and nerve decompression without a requirement to reconstruct the annular wall. While results are currently acceptable, they are not optimal. Various authors report 3.1-21% recurrent disc herniation, representing a failure of the primary procedure and requiring re-operation for the same condition. An estimated 10% recurrence rate results in 39,000 re-operations in the United States each year.
• An additional method of relieving the symptoms is thermal annuloplasty, involving the heating of sub-annular zones in the non-herniated painful disc, seeking pain relief, but making no claim of reconstruction of the ruptured, discontinuous annulus wall.
• Some have also suggested that the repair of a damaged intervertebral disc might include the augmentation of the nucleus pulposus, and various efforts at nucleus pulposus replacement have been reported. The present invention is directed at the repair of the annulus, whether or not a nuclear augmentation is also warranted.
• In addition, there has been experimentation in animals to assess various surgical incisions with and without the direct surgical repair of the annulus. These studies were performed on otherwise healthy animals and involved no removal or augmentation of nucleus pulposus. The authors of these experiments conclude that direct repair of the annulus does not influence the healing of the disc.
• There is currently no known method of annulus reconstruction, either primarily or augmented with an annulus stent.
BRIEF SUMMARY OF THE INVENTION
• The present invention provides methods and related materials for reconstruction of the disc wall in cases of displaced, herniated, ruptured, or otherwise damaged intervertebral discs. In accordance with the invention, a method is disclosed for intervertebral disc reconstruction for treating a disc having an aperture in the wall of the annulus fibrosis, wherein the aperture provides a path for the migration of nucleus pulposus from the subannular space, the method including the steps of providing an expandable patch having a first configuration dimensioned to pass through the aperture and a second expanded configuration having at least one dimension at least as large as the aperture and having at least one dimension larger than a corresponding dimension in said first configuration; inserting the patch through the aperture into the subannular space when the device is in the first collapsed configuration; and causing or allowing the patch to expand in the subannular space into the second expanded configuration to bridge the aperture, thereby occluding the aperture and preventing the migration of nucleus pulposus therethrough.
• The objects and various advantages of the invention will be apparent in consideration of the description which follows. In general, the implantable medical device is placed, positioned, and affixed to the annulus to reduce re-extrusion of the nucleus through the aperture by: acting as a mechanical barrier; restoring the natural integrity of the wall of the annulus; and promoting the healing of the annulus through the reapproximation of disc wall tissue. Increased integrity and faster and/or more thorough healing of the aperture is intended to reduce future recurrence of herniation of the disc nucleus from the intervertebral disc, and the recurrence of resulting back pain. In addition, it is believed that the repair of the aperture could promote enhanced biomechanics and reduce the possibility of intervertebral disc height collapse and segmental instability, thus resulting in a decrease in the recurrence of back pain after a surgical procedure.
• Moreover, the repair of the aperture with the reduction of the re-extrusion of the nucleus may also advantageously reduce adhesion formation surrounding the nerve roots. The nuclear material of the disc is toxic to the nerves and is believed to cause increased inflammation surrounding the nerves, which in turn can cause increased scar formation (adhesions or epidural fibrosis) upon healing. Adhesions created around the nerve roots can cause continued back pain. Any reduction in adhesion formation is believed to reduce future recurrence of pain.
• One of the objects of the present inventions is to act as a mechanical barrier to the extrusion of the nucleus from the disc space, add mechanical integrity to the annulus and the tissue surrounding the aperture, and to promote faster and a more complete healing of the aperture.
• Although much of the discussion is directed toward the repair of the intervertebral disc after a surgical procedure, such as discectomy (a surgical procedure performed to remove herniated fragments of the disc nucleus), it is contemplated that the device could be used in other procedures that involve incisions into the annulus of the intervertebral disc. An example of another procedure that could require a repair technique involves the replacement of the nucleus—nucleus replacement—with an implantable nucleus to replace the functioning of the natural nucleus when it is degenerated. The object of the invention in this case would be similar in that the repair would maintain the replacement nucleus within the disc space.
• According to the invention, a sub-annular patch/stent can be employed to repair an intervertebral disc annulus. In its simplest form, the repair of the annulus involves the placement and fixation of a fascial autograft patch to the sub-annular space which can additionally employ two or more sutures, while re-approximating the tissues surrounding the aperture. The invention, through involvement of the sub-annular space and wall for the repair of the aperture, has several advantages over the prior art; for example, sealing the aperture only on the outer surface, or sealing the aperture only within the aperture. The first advantage of a repair that involves the sub-annular surface derives itself from the physical nature of a circular (or an elliptical) compressed chamber with a radius, like an intervertebral disc. Sealing the inside wall has the inherent advantage of being at a smaller radius of curvature versus the outer wall and thus, according to LaPlace's Law, the patch would be subjected to lower stresses at any given pressure, all else held equal.
• Another advantage of utilizing the inner surface to accomplish sealing is that the natural pressure within the disc can enhance the sealing of the device against the inner wall of the disc space. Conversely, if the repair is performed on the outer surface of the annulus there is an inherent risk of leakage around the periphery of the device, with the constant exposure to the pressure of the disc.
• Another advantage of the present invention over the prior art in utilizing the inner surface of the annulus is the reduction of the risk of having a portion of the device protruding from the exterior surface of the annulus. Device materials protruding from the exterior of the annulus pose a risk of damaging the nerve root and/or spinal canal which are in close proximity. Damage to these structures can result in continued pain, incontinence, bowel dysfunction, and paralysis.
• The present invention also incorporates the concept of pulling the tissues together that surround the aperture, the inner surface, and the outer surface of the annulus to help increase the integrity of the repair.
• An example of the technique and placement of the device according to the invention is as follows:
• 1. An aperture is created measuring approximately, for example, 6 mm×2 mm in the wall of the annulus after performing a discectomy procedure in which a portion of the nucleus is also removed from the disc space, as shown inFIGS. 32a,32b,33aand33b.
• 2. Two or more sutures are passed through the upper and lower surfaces of the aperture and they are pushed within the intervertebral disc space to create a “sling” to receive the fascial autograft as shown for example inFIG. 34.
• 3. A piece of para-spinal fascial tissue is removed from the patient measuring approximately, for example, 10 mm×5 mm.
• 4. The autograft is folded and compressed to pass through the aperture in the annulus, as shown for example inFIG. 35.
• 5. The autograft takes a second shape, within the annulus that is uncompressed and oriented to be in proximity of the subannular wall of the annulus, within the sling, as shown for example inFIG. 36. The autograft may be inserted entirely into the subannular space, or a portion may extend into the rent as depicted inFIG. 36.
• 6. The sutures are tightened, as shown for example inFIG. 37, thus tightening the sling surrounding the autograft, to bring the autograft in close proximity with the subannular wall, while providing tension to bring the patch at the subannular surface together with the outer surface of the annular wall, thus creating increased integrity of the annulus surrounding the aperture, as well as causing the autograft to take a second shape that is larger than the aperture. Furthermore, the tightening, and eventual tying of the sutures also promotes the re-approximation of the tissue at the outer surface of the annulus and within the aperture.
• 7. The sutures are tied and the ends of the sutures are cut.
• 8. A piece of autograft fat tissue may be placed over the discectomy site for the prevention of adhesion formation, a typical surgical technique.
• 9. Standard surgical techniques are utilized to close the access site of the surgical procedures.
• Several devices according to the present invention can be used to practice the above illustrative inventive steps to accomplish the sealing and/or repair of the intervertebral disc. In each of the representative devices described herein, there is: an expandable patch/stent (note: patch, stent and device are used interchangeably) that has, in use, at least a portion of the device in proximity to the sub-annular space of the intervertebral disc annulus; a means to affix the patch to stay in proximity with the annulus; a means to draw the patch and the annular tissue together and fasten in tension; and a means to help reduce the relative motion of the surfaces of the aperture after fixation, and thus promote healing. According to one feature and object of the present invention, close approximation of tissue, while reducing the motion of the surfaces, provides the optimal environment for healing.
• The concepts disclosed hereinbelow accomplish these objectives, as well as advantageously additionally incorporating design elements to reduce the number of steps (and time), and/or simplify the surgical technique, and/or reduce the risk of causing complications during the repair of the intervertebral disc annulus. In addition, it is an objective of the following devices to become incorporated by the surrounding tissues, or to act as a scaffold in the short-term (3-6 months) for tissue incorporation.
• In an exemplary embodiment, one or more mild biodegradable surgical sutures can be placed at about equal distances along the sides of a pathologic aperture in the ruptured disc wall (annulus) or along the sides of a surgical incision in the annular wall, which may be weakened or thinned.
• Sutures are then tied in such fashion as to draw together the sides of the aperture, effecting reapproximation or closure of the opening, to enhance natural healing and subsequent reconstruction by natural tissue (fibroblasts) crossing the now surgically narrowed gap in the disc annulus.
• A 25-30% reduction in the rate of recurrence of disc nucleus herniation through this aperture has been achieved using this method.
• In another exemplary embodiment, the method can be augmented by creating a subannular barrier in and across the aperture by placement of a patch of human muscle fascia (muscle connective tissue) or any other autograft, allograft, or xenograft acting as a bridge or a scaffold, providing a platform for traverse of fibroblasts or other normal cells of repair existing in and around the various layers of the disc annulus, prior to closure of the aperture.
• A 30-50% reduction in the rate of recurrence of disc herniation has been achieved using the aforementioned fascial augmentation with this embodiment.
• In still another embodiment, a braided patch can be formed having a first collapsed configuration having a major longitudinal dimension with first and second ends. When these ends are moved toward each other along the longitudinal axis, a portion of the device between the ends can deploy outwardly to form an expanded configuration.
• Having demonstrated that human muscle fascia is adaptable for annular reconstruction, other biocompatible membranes can be employed as a bridge, stent, patch or barrier to subsequent migration of the disc nucleus through the aperture. Such biocompatible materials may be, for example, medical grade biocompatible fabrics, biodegradable polymeric sheets, or form fitting or non-form fitting fillers for the cavity created by removal of a portion of the disc nucleus pulposus in the course of the disc fragment removal or discectomy. The prosthetic material can be placed in and around the intervertebral space, created by removal of the degenerated disc fragments.
• Additional objects and advantages of the invention will be set forth in part in the description which follows, and in part will be obvious from the description, or may be learned by practice of the invention. The objects and advantages of the invention will be realized and attained by means of the elements and combinations particularly pointed out in the appended claims.
• It is to be understood that both the foregoing general description and the following detailed description are exemplary and explanatory only and are not restrictive of the invention, as claimed.
BRIEF DESCRIPTION OF THE DRAWINGS
• The accompanying drawings, which are incorporated in and constitute a part of this specification, illustrate illustrative embodiments of the invention and, together with the description, serve to explain the principles of the invention.
• FIG. 1 shows a perspective view of an illustrative embodiment of an annulus stent.
• FIG. 2 shows a front view of the annulus stent ofFIG. 1.
• FIG. 3 shows a side view of the annulus stent ofFIG. 1.
• FIGS. 4A-4C show a front view of alternative illustrative embodiments of an annulus stent.
• FIGS. 5A-5B show the alternative embodiment of a further illustrative embodiment of an annulus stent.
• FIGS. 6A-6B show the alternative embodiment of a further illustrative embodiment of an annulus stent.
• FIG. 7 shows a primary closure of an opening in the disc annulus.
• FIGS. 8A-8B show a primary closure with a stent.
• FIG. 9 shows a method of suturing an annulus stent into the disc annulus utilizing fixation points on vertebral bodies.
• FIGS. 10A-10B show a further illustrative embodiment of an annulus stent with flexible bladder being expanded into the disc annulus.
• FIGS. 11A-11D show an annulus stent being inserted into and expanded within the disc annulus.
• FIGS. 12A-12B show an annulus stent with a flexible bladder being expanded.
• FIG. 13 shows a perspective view of a further illustrative embodiment of an annulus stent.
• FIG. 14 shows a first collapsed view of the annulus stent ofFIG. 13.
• FIG. 15 shows a second collapsed view of the annulus stent ofFIG. 13.
• FIGS. 16A-16C show the annulus stent ofFIG. 13 being inserted into the disc annulus.
• FIGS. 17A-17C show a method of inserting the annulus stent ofFIG. 13 into the disc annulus.
• FIGS. 18A-18B show a further illustrative embodiment of an annulus stent with a flexible bladder.
• FIGS. 19A-19B show another illustrative embodiment of an annulus stent with a flexible bladder.
• FIG. 20 shows an expanded annulus stent with barbs on the radial extension.
• FIG. 21 shows a still further illustrative embodiment of an annulus stent with a compressible core.
• FIG. 22 shows a still further illustrative embodiment of an introduction device for an annulus stent.
• FIG. 23 shows a modification of the device depicted inFIG. 22.
• FIG. 24 shows an exemplary introduction tool for use with the devices ofFIGS. 22 and 23 with a stent deflected proximally.
• FIG. 25 shows an exemplary introduction tool for use with the devices ofFIGS. 22 and 23 with a stent deflected distally.
• FIG. 26 shows an exemplary introduction tool for use with the devices ofFIGS. 22 and 23 with a stent deflected partially distally and partially proximally.
• FIG. 27 shows a still further illustrative embodiment of a stent device having a grasping feature and fixation devices in the form of barbs.
• FIG. 28 shows the illustrative embodiment inFIG. 27 deployed subannularly.
• FIG. 29 shows a still further illustrative embodiment of an annulus stent employing a secondary barbed fixation device.
• FIG. 30 shows a still further illustrative embodiment of an annulus stent employing another example of a secondary barbed fixation device.
• FIG. 31 shows the frame of a still further illustrative embodiment of an annulus stent having a metal substrate being machined from flat stock.
• FIG. 32ashows a herniated disc in perspective view, andFIG. 32bshows the same disc after discectomy.
• FIG. 33ashows a top view of the disc post-discectomy, andFIG. 33bshows a posteriolateral view of the disk showing an incision.
• FIG. 34 shows schematically the creation of a subannular sling using sutures.
• FIG. 35 schematically shows the introduction of a compressed autograft stent/patch into the subannular space.
• FIG. 36 schematically shows the autograft ofFIG. 35 in an expanded shape within the annulus.
• FIG. 37 schematically shows the tightening of the sutures to reapproximate the annulus aperture and draw the stent/patch ofFIG. 35 toward the annular wall.
• FIG. 38 shows an exemplary collar for use in repairing a disc annulus.
• FIG. 39 schematically depicts the collar ofFIG. 38 in use for disc annulus repair.
• FIG. 40 shows a still further exemplary embodiment of the present invention using a bag to contain the patch/stent.
• FIG. 41a-eshow still further illustrative embodiments of the present invention having frames.
• FIG. 42 shows an illustrative method for placing a barbed expandable patch in the subannular disc space.
• FIG. 43 shows the patch ofFIG. 42 being fixed to the inside wall of the annulus fibrosus.
• FIGS. 44a-gshow a still further illustrative embodiment of an introduced and expanded annulus stent/patch being fixated and the aperture reapproximated.
• FIGS. 45a-cschematically depict a still further embodiment of the present invention where an expandable stent/patch is tethered in situ using a cinch line.
• FIGS. 46a-cschematically depict the cinch line ofFIG. 45 being fixated through use of a surgical staple device.
• FIGS. 47a-bshow an illustrative embodiment of a suturing arrangement for securing a patch/stent in the annulus.
• FIG. 48a-bdepict a still further illustrative embodiment where fixation sutures are placed into the vertebral body or the Sharpey fibers.
• FIGS. 49a-cschematically depict a still further embodiment of the present invention where an expandable stent/patch is tethered in situ using a cinch line.
• FIGS. 50a-cschematically depict the cinch line ofFIG. 49 being fixated through use of a barbed surgical staple device that penetrates the patch/stent.
• FIG. 51 depicts an exemplary use of filler tissue within the aperture during placement of a patch/stent tethered by a cinch line.
• FIGS. 52a-eshows exemplary embodiments of various additional patch/stent fixation techniques.
• FIG. 53 shows a still further illustrative embodiment of a stent/patch having a frame.
• FIG. 54a-fshows a still further illustrative embodiment of an annular stent/patch having a self-contained fixation tightening feature.
• FIG. 55 shows a still further exemplary embodiment of the present invention having external fixation anchors.
• FIG. 56a-cshows a still further exemplary embodiment of the present invention having external fixation anchors.
• FIG. 57a-cshows a still further exemplary embodiment of the present invention having external fixation anchors.
• FIG. 58 shows a still further exemplary embodiment of the present invention having external fixation anchors.
• FIG. 59 shows a still further exemplary embodiment of the present invention having a springing arrangement.
• FIG. 60 shows a lateral view of a still further exemplary embodiment of the present invention having a braided arrangement in a collapsed configuration.
• FIG. 61 shows an axial view of the exemplary embodiment ofFIG. 60 in an expanded configuration.
• FIG. 62 shows a lateral view of the exemplary embodiment ofFIG. 60 in a collapsed configuration mounted on an illustrative delivery device.
• FIG. 63 shows a lateral cutaway view of the exemplary embodiment ofFIG. 60 in a collapsed configuration.
• FIG. 64 shows a lateral cutaway view of the exemplary embodiment ofFIG. 60 in an expanded configuration.
• FIG. 65 shows a lateral view of an illustrative delivery member as shown in the exemplary embodiment ofFIGS. 63 and 64.
• FIG. 66 shows a lateral view of an exemplary embodiment of the invention in an expanded configuration subannularly.
DETAILED DESCRIPTION OF THE INVENTION
• Reference will now be made in detail to an illustrative embodiment of the invention, which appears in the accompanying drawings. Wherever possible, the same reference numbers will be used throughout the drawings to refer to the same or like parts.
• In one embodiment of the present invention, as shown inFIG. 7, a damagedannulus42 is repaired by use ofsurgical sutures40. One or moresurgical sutures40 are placed at about equal distances along the sides of apathologic aperture44 in theannulus42. Reapproximation or closure of theaperture44 is accomplished by tying thesutures40 so that the sides of theaperture44 are drawn together. The reapproximation or closure of theaperture44 enhances the natural healing and subsequent reconstruction by the natural tissue (e.g., fibroblasts) crossing the now surgically narrowed gap in theannulus42. Preferably, thesurgical sutures40 are biodegradable, but permanent non-biodegradable may be utilized.
• Additionally, to repair a weakened or thinned wall of adisc annulus42, a surgical incision can be made along the weakened or thinned region of theannulus42 and one or moresurgical sutures40 can be placed at about equal distances laterally from the incision. Reapproximation or closure of the incision is accomplished by tying thesutures40 so that the sides of the incision are drawn together. The reapproximation or closure of the incision enhances the natural healing and subsequent reconstruction by the natural tissue crossing the now surgically narrowed gap in theannulus42. Preferably, thesurgical sutures40 are biodegradable, but permanent non-biodegradable materials may be utilized.
• In an alternative embodiment, the method can be augmented by the placement of a patch of human muscle fascia or any other autograft, allograft or xenograft in and across theaperture44. The patch acts as a bridge in and across theaperture44, providing a platform for traverse of fibroblasts or other normal cells of repair existing in and around the various layers of thedisc annulus42, prior to closure of theaperture44.
• In a further embodiment, as shown in FIGS.8A-B a biocompatible membrane can be employed as anannulus stent10, being placed in and across theaperture44. Theannulus stent10 acts as a bridge in and across theaperture44, providing a platform for a traverse of fibroblasts or other normal cells of repair existing in and around the various layers of thedisc annulus42, prior to closure of theaperture44. In some embodiments the device, stent or patch can act as a scaffold to assist in tissue growth that healingly scars the annulus.
• In an illustrative embodiment, as shown inFIGS. 1-3, theannulus stent10 comprises a centralizedvertical extension12, with anupper section14 and alower section16. The centralizedvertical extension12 can be trapezoid in shape through the width and may be from about 8 mm-12 mm in length.
• Additionally, theupper section14 of the centralizedvertical extension12 may be any number of different shapes, as shown inFIGS. 4A through 4C, with the sides of theupper section14 being curved or with theupper section14 being circular in shape. Furthermore, theannulus stent10 may contain a recess between theupper section14 and thelower section16, enabling theannulus stent10 to form a compatible fit with the edges of theaperture44.
• Theupper section14 of the centralizedvertical extension12 can comprise aslot18, where theslot18 forms an orifice through theupper section14. Theslot18 is positioned within theupper section14 such that it traverses the upper section's14 longitudinal axis. Theslot18 is of such a size and shape that sutures, tension bands, staples or any other type of fixation device known in the art may be passed through, to affix theannulus stent10 to thedisc annulus42.
• In an alternative embodiment, theupper section14 of the centralizedvertical extension12 may be perforated. The perforatedupper section14 contains a plurality of holes that traverse the longitudinal axis ofupper section14. The perforations are of such a size and shape that sutures, tension bands, staples or any other type of fixation device known in the art may be passed through, to affix theannulus stent10 to thedisc annulus42.
• Thelower section16 of the centralizedvertical extension12 can comprise a pair of lateral extensions, a leftlateral extension20 and a rightlateral extension22. Thelateral extensions20 and22 comprise aninside edge24, anoutside edge26, anupper surface28, and alower surface30. Thelateral extensions20 and22 can have an essentially constant thickness throughout. Theinside edge24 is attached to and is about the same length as thelower section16. Theoutside edge26 can be about 8 mm-16 mm in length. Theinside edge24 and thelower section16 meet to form a horizontal plane, essentially perpendicular to the centralizedvertical extension12. Theupper surface28 of thelateral extensions20 and22 can form an angle from about 0°-60° below the horizontal plane. The width of theannulus stent10 may be from about 3 mm-8 mm.
• Additionally, theupper surface28 of thelateral extensions20 and22 may be barbed for fixation to the inside surface of thedisc annulus42 and to resist expulsion through theaperture44.
• In an alternative embodiment, as shown inFIG. 4B, thelateral extensions20 and22 have a greater thickness at theinside edge24 than at theoutside edge26.
• In an illustrative embodiment, theannulus stent10 is a solid unit, formed from one or more of the flexible resilient biocompatible or bioresorbable materials well know in the art. The selection of appropriate stent materials may be partially predicated on specific stent construction and the relative properties of the material such that, after fixed placement of the stent, the repair may act to enhance the healing process at the aperture by relatively stabilizing the tissue and reducing movement of the tissue surrounding the aperture.
• For example, theannulus stent10 may be made from:
• A porous matrix or mesh of biocompatible and bioresorbable fibers acting as a scaffold to regenerate disc tissue and replace annulus fibrosus as disclosed in, for example, U.S. Pat. No. 5,108,438 (Stone) and U.S. Pat. No. 5,258,043 (Stone), a strong network of inert fibers intermingled with a bioresorbable (or bioabsorbable) material which attracts tissue ingrowth as disclosed in, for example, U.S. Pat. No. 4,904,260 (Ray et al.).
• a biodegradable substrate as disclosed in, for example, U.S. Pat. No. 5,964,807 (Gan at al.); or
• an expandable polytetrafluoroethylene (ePTFE), as used for conventional vascular grafts, such as those sold by W.L. Gore and Associates, Inc. under the trademarks GORE-TEX and PRECLUDE, or by Impra, Inc. under the trademark IMPRA.
• Furthermore, the annulus,stent10, may contain hygroscopic material for a controlled limited expansion of theannulus stent10 to fill the evacuated disc space cavity.
• Additionally, theannulus stent10 may comprise materials to facilitate regeneration of disc tissue, such as bioactive silica-based materials that assist in regeneration of disc tissue as disclosed in U.S. Pat. No. 5,849,331 (Ducheyne, et al.), or other tissue growth factors well known in the art.
• Many of the materials disclosed and described above represent embodiments where the device actively promotes the healing process. It is also possible that the selection of alternative materials or treatments may modulate the role in the healing process, and thus promote or prevent healing as may be required. It is also contemplated that these modulating factors could be applied to material substrates of the device as a coating, or similar covering, to evoke a different tissue response than the substrate without the coating.
• In further embodiments, as shown in FIGS.5AB-6AB, the left and rightlateral extensions20 and22 join to form a solid pyramid or cone. Additionally, the left and rightlateral extensions20 and22 may form a solid trapezoid, wedge, or bullet shape. The solid formation may be a solid biocompatible or bioresorbable flexible material, allowing thelateral extensions20 and22 to be compressed for insertion intoaperture44, then to expand conforming to the shape of the annulus'42 inner wall.
• Alternatively, a compressible core may be attached to thelower surface30 of thelateral extensions20 and22, forming a pyramid, cone, trapezoid, wedge, or bullet shape. The compressible core may be made from one of the biocompatible or bioresorbable resilient foams well known in the art. The core can also comprise a fluid-expandable membrane, e.g., a balloon. The compressible core allows thelateral extensions20 and22 to be compressed for insertion intoaperture44, then to expand conforming to the shape of the annulus'42 inner wall and to the cavity created by pathologic extrusion or surgical removal of the disc fragment.
• In an illustrative method of use, as shown in FIGS.11A-D, thelateral extensions20 and22 are compressed together for insertion into theaperture44 of thedisc annulus42. Theannulus stent10 is then inserted into theaperture44, where thelateral extensions20,22 expand. In an expanded configuration, theupper surface28 can substantially conform to the contour of the inside surface of thedisc annulus42. Theupper section14 is positioned within theaperture44 so that theannulus stent10 may be secured to thedisc annulus42, using means well known in the art.
• In an alternative method, where the length of theaperture44 is less than the length of theoutside edge26 of theannulus stent10, theannulus stent10 can be inserted laterally into theaperture44. Thelateral extensions20 and22 are compressed, and theannulus stent10 can then be laterally inserted into theaperture44. Theannulus stent10 can then be rotated inside thedisc annulus42, such that theupper section14 can be held back through theaperture44. Thelateral extensions20 and22 are then allowed to expand, with theupper surface28 contouring to the inside surface of thedisc annulus42. Theupper section14 can be positioned within, or proximate to, theaperture44 in the subannular space such that theannulus stent10 may be secured to the disc annulus, using means well known in the art.
• In an alternative method of securing theannulus stent10 in theaperture44, as shown inFIG. 9, a firstsurgical screw50 and secondsurgical screw52, witheyeholes53 located at the top of thescrews50 and52, are inserted into the vertebral bodies, illustratively depicted asadjacent vertebrae54 and56. After insertion of theannulus stent10 into theaperture44, asuture40 is passed down though thedisc annulus42, adjacent to theaperture44, through theeye hole53 on thefirst screw50 then back up through thedisc annulus42 and through theorifice18 on theannulus stent10. This is repeated for thesecond screw52, after which thesuture40 is secured. One or moresurgical sutures40 are placed at about equal distances along the sides of theaperture44 in thedisc annulus42. Reapproximation or closure of theaperture44 is accomplished by tying thesutures40 in such a fashion that the sides of theaperture44 are drawn together. The reapproximation or closure of theaperture44 enhances the natural healing and subsequent reconstruction by the natural tissue crossing the now surgically narrowed gap in theannulus42. Preferably, thesurgical sutures40 are biodegradable but permanent non-biodegradable forms may be utilized. This method should decrease the strain on thedisc annulus42 adjacent to theaperture44, precluding the tearing of the sutures through thedisc annulus42.
• It is anticipated that fibroblasts will engage the fibers of the polymer or fabric of theintervertebral disc stent10, forming a strong wall duplicating the currently existing condition of healing seen in the normal reparative process.
• In an additional embodiment, as shown in FIGS.1A-B, aflexible bladder60 is attached to thelower surface30 of theannulus stent10. Theflexible bladder60 comprises aninternal cavity62 surrounded by amembrane64, where themembrane64 is made from a thin flexible biocompatible material. Theflexible bladder60 is attached to thelower surface30 of theannulus stent10 in an unexpanded condition. Theflexible bladder60 is expanded by injecting a biocompatible fluid or expansive foam, as known in the art, into theinternal cavity62. The exact size of theflexible bladder60 can be varied for different individuals. The typical size of an adult nucleus is about 2 cm in the semi-minor axis, 4 cm in the semi-major axis, and 1.2 cm in thickness.
• In an alternative embodiment, themembrane64 is made of a semi-permeable biocompatible material. The mechanical properties of the injectate material may influence the performance of the repair and it is contemplated that materials which are “softer” or more compliant as well as materials that are less soft and less compliant than healthy nucleus are contemplated within the scope of certain embodiments of the invention. It must be understood that in certain embodiments the volume added to the subannular space may be less than equal to or larger than the nucleus volume removed. The volume of the implant may vary over time as well in certain embodiments.
• In an illustrative embodiment, a hydrogel is injected into theinternal cavity62 of theflexible bladder60. A hydrogel is a substance formed when an organic polymer (natural or synthetic) is cross-linked via, covalent, ionic, or hydrogen bonds to create a three-dimensional open-lattice structure, which entraps water molecules to form a gel. The hydrogel may be used in either the hydrated or dehydrated form.
• In a method of use, where theannulus stent10 has been inserted into theaperture44, as has been previously described and shown in FIGS.12 A-B, an injection instrument, as known in the art, such as a syringe, is used to inject the biocompatible fluid or expansive foam into theinternal cavity62 of theflexible bladder60. The biocompatible fluid or expansive foam is injected through theannulus stent10 into theinternal cavity62 of theflexible bladder60. Sufficient material is injected into theinternal cavity62 to expand theflexible bladder60 to fill the void in the intervertebral disc cavity. The use of theflexible bladder60 is particularly useful when it is required to remove all or part of the intervertebral disc nucleus.
• The surgical repair of an intervertebral disc may require the removal of the entire disc nucleus, being replaced with an implant, or the removal of a portion of the disc nucleus thereby leaving a void in the intervertebral disc cavity. Theflexible bladder60 allows for the removal of only the damaged section of the disc nucleus, with the expandedflexible bladder60 filling the resultant void in the intervertebral disc cavity. A major advantage of theannulus stent10 with theflexible bladder60 is that the incision area in theannulus42 can be reduced in size, as there is no need for the insertion of an implant into the intervertebral disc cavity.
• In an alternative method of use, a dehydrated hydrogel is injected into theinternal cavity62 of theflexible bladder60. Fluid, from the disc nucleus, passes through thesemipermeable membrane64 hydrating the dehydrated hydrogel. As the hydrogel absorbs the fluid theflexible bladder60 expands, filling the void in the intervertebral disc cavity.
• In an alternative embodiment, as shown inFIG. 13, theannulus stent10 is substantially umbrella shaped, having acentral hub66 with radially extendingstruts67. Each of thestruts67 is joined to theadjacent struts67 by awebbing material65, forming aradial extension76 about thecentral hub66. Theradial extension76 has anupper surface68 and alower surface70, where theupper surface68 contours to the shape of the disc annulus'42 inner wall when inserted as shown inFIG. 17A-C, and where thelower surface70 contours to the shape of the disc annulus'42 inner wall when inserted as shown inFIG. 16A-C. Theradial extension76 may be substantially circular, elliptical, or rectangular in plan shape. Additionally, as shown inFIG. 20, theupper surface68 of theradial extension76 may be barbed82 for fixation to the disc annulus'42 inner wall and to resist expulsion through theaperture42.
• As shown inFIGS. 14 and 15, thestruts67 are formed from flexible material, allowing theradial extension76 to be collapsed for insertion intoaperture44, then the expand conforming to the shape of the inner wall ofdisc annulus42. In the collapsed position, theannulus stent10 is substantially frustoconical or shuttlecock shaped, and having afirst end72, comprising thecentral hub66, and asecond end74.
• In an alternative embodiment, theradial extension76 has a greater thickness at thecentral hub66 edge than at the outside edge.
• In an embodiment, theannulus stent10 is a solid unit, formed from one or more of the flexible resilient biocompatible or bioresorbable materials well known in the art.
• Additionally, theannulus stent10 may comprise materials to facilitate regeneration of disc tissue, such as bioactive silica based materials that assist in regeneration of disc tissue as disclosed in U.S. Pat. No. 5,849,331 (Ducheyne, et al.), or other tissue growth factors well known in the art.
• Alternatively, as shown inFIG. 21, acompressible core84 may be attached to thelower surface70 of theradial extension76. Thecompressible core84 may be made from one of the biocompatible or bioresorbable resilient foams well known in the art. Thecompressible core84 allows theradial extension76 to be compressed for insertion intoaperture44 then to expand conforming to the shape of the disc annulus'42 inner wall and to the cavity created by pathologic extrusion or surgical removal of the disc fragment.
• In an additional embodiment, as shown inFIGS. 18A and 18B, aflexible bladder80 is attached to thelower surface70 of theannulus stent10. Theflexible bladder80 comprises aninternal cavity86 surrounded by amembrane88, where themembrane88 is made from a thin flexible biocompatible material. Theflexible bladder86 is attached to thelower surface70 of theannulus stent10 in an unexpanded condition. Theflexible bladder80 is expanded by injecting a biocompatible fluid or expansive foam, as known in the art, into theinternal cavity86. The exact size of theflexible bladder80 can be varied for different individuals. The typical size of an adult nucleus is 2 cm in the semi-minor axis, 4 cm in the semi-major axis and 1.2 cm in thickness.
• In an alternative embodiment, themembrane88 is made of a semi-permeable biocompatible material.
• In a method of use, as shown inFIGS. 16A-16C, theradial extension76 is collapsed together, for insertion into theaperture44 of thedisc annulus42. Theradial extension76 is folded such theupper surface68 forms the outer surface of the cylinder. Theannulus stent10 is then inserted into theaperture44, inserting the leadingend72 though theaperture44 until theentire annulus stent10 is within thedisc annulus42. Theradial extension76 is released, expanding within thedisc44. Thelower surface70 of theannulus stent10 contours to the inner wall ofdisc annulus42. Thecentral hub66 is positioned within theaperture44 so that theannulus stent10 may be secured to thedisc annulus42 using means well known in the art.
• It is anticipated that fibroblasts will engage the fibers of the polymer of fabric of theannulus stent10, forming a strong wall duplicating the currently existing condition of healing seen in the normal reparative process.
• In an alternative method of use, as shown inFIGS. 17A-17C, theradial extension76 is collapsed together for insertion into theaperture44 of thedisc annulus42. Theradial extension76 is folded such that theupper surface68 forms the outer surface of the stent, for example in a frustoconical configuration as illustrated. Theannulus stent10 is then inserted into theaperture44, inserting thetail end74 through theaperture44 until theentire annulus stent10 is in the disc. Theradial extension76 is released, expanding within the disc. Theupper surface68 of theannulus stent10 contours to the disc annulus'42 inner wall. Thecentral hub66 is positioned within theaperture44 so that theannulus stent10 may be secured to thedisc annulus42, using means well known in the art.
• In one illustrative embodiment, thebarbs82 on theupper surface68 of one ormore strut67 or other feature of theradial extension76, engage the disc annulus'42 inner wall, holding theannulus stent10 in position.
• In a method of use, as shown inFIGS. 12A-12B, where theannulus stent10 has been inserted into theaperture44, as has been previously described. Similarly, for the stent shown inFIGS. 18 through 21, an injection instrument, as known in the art, such as a syringe, can be used to inject the biocompatible fluid or expansive foam into theinternal cavity86 of theflexible bladder80. The biocompatible fluid or expansive foam is injected through theannulus stent10 into theinternal cavity86 of theflexible bladder80. Sufficient material is injected into theinternal cavity86 to expand theflexible bladder80 to fill the void in the intervertebral disc cavity. The material can be curable (i.e., glue). The use of theflexible bladder80 is particularly useful when it is required to remove all or part of the intervertebral disc nucleus.
• It should be noted that in any of the “bag” embodiments described herein one wall or barrier can be made stiffer and less resilient than others. This relatively stiff wall member can then be placed proximate the annulus wall and can advantageously promote, in addition to its reparative properties, bag containment within the annulus.
• FIG. 22 shows a further aspect of the present invention. According to a further illustrative embodiment, a simplified schematic cross section of a vertebral pair is depicted including an uppervertebral body110, a lowervertebral body112 and anintervertebral disc114. An aperture or rent116 in the annulus fibrosus (AF) is approached by atube118, which is used to deliver adevice120 according to a further aspect of the present invention. Thedevice120 may be captured by adelivery tool122 through the use of a ring or other fixation feature124 mounted on therepair device120.
• FIG. 23 shows a delivery method similar to that depicted inFIG. 22, with the exception that thetube118A has a reduced diameter so that it may enter into the sub-annular space of thedisc114 through the aperture or rent.
• Turning toFIG. 25, according to a further aspect of the present invention, the delivery of thedevice120 through thedelivery tube118 or118A may be facilitated by folding the arms orlateral extensions128,130 of the device to fit within the lumen of thetube118 or118A so that the stent ordevice120 is introduced in a collapsed configuration. Thedevice120 is moved through the lumen of thetubes118 or118A through the use ofdelivery tool122.FIG. 25 shows the arms deflected in a distal, or forward direction for insertion into thedelivery tube118 or118A whileFIG. 24 shows thearms128,130 deflected into a proximal position.FIG. 26 shows thedevice120 curled so that onearm128 is projecting distally, or in a forward direction, and theother arm130 is projecting proximally, or in a rearward direction. Because the lateral extent of the device is relatively flexible, whether the device is of natural or synthetic material, other collapsible configurations consistent with the intent of this invention are also possible, including twisting, balling, crushing, etc.
• FIG. 27 shows thedevice120 having a series of peripheral barb structures typified bybarb132 located at the edges. In operation, these barbs may be forced into the annulus fibrosus as seen in connection withFIG. 28. Barb placement can be anywhere on thedevice120 provided that at least some number of barbs are likely to find annulus fibrosus tissue to anchor in during placement. For a simple aperture or rent, placement on the periphery of the device body is a reasonable choice, but for complex tears, it may be desirable to place a plurality of barbs on the device not knowing in advance which barbs will find tissue to anchor in during placement.
• FIG. 29 shows an alternative fixation strategy where a pair ofbarbs134 and136 are plunged into the annulus fibrosus from the exterior of the annulus while thedevice120 is retained in the sub-annular space by means of atether142. Although there are a wide variety of fixation devices in this particular example, atether142 may be knotted145 with theband144 holding thebarbs134 and136 together to fix the device in the sub-annular space. The knot is shown in an uncinched position to clarify the relationship between thetether142 and thebands144. Using this approach, the device can be maintained in a subannular position by the barbed bands while the tether knot is cinched, advantageously simultaneously reapproximating the annulus to close the aperture while drawing the device into sealing, bridging engagement with the subannular wall of the annulus fibrosus.
• FIG. 30 shows an alternative fixation strategy where thebarbs148 and150 are sufficiently long that they can pierce the body of thedevice120 and extend all the way through the annulus fibrosus into thedevice120. In this configuration, theband144 connecting thebarbs148 and150 may be tightened to gently restrain and position thedevice120 in the sub-annular space, or tightened with greater force to reapproximate the aperture or rent.
• FIG. 31 shows a still further illustrative embodiment according to another aspect of the present invention. In this embodiment, ametal substrate160 is incorporated into thedevice120. This piece can be machined from flat stock and includes theloop162 as well as barbs typified bybarb164. When formed in to thedevice120 the structure shown inFIG. 31 is used in a manner analogous toFIG. 27 andFIG. 28.
• Stents can expand to be planar, for example as shown hereinabove inFIGS. 4, 8,9,11 and12, or they can expand to be three-dimensional as shown hereinabove inFIGS. 5 and 10.FIGS. 34-36 depict a further three dimensional patch/stent using an autograft formed of fascial tissue.FIG. 34 shows the superiorvertebral body202 and the inferiorvertebral body204 surrounding a disc having anannulus fibrosus206 andnucleus pulposus203 in the subannular space. According to this illustrative embodiment of the invention, asuture210 is passed from outside the annulus through the wall of the annulus on one side of anaperture208 and into the subannular space as shown. The suture is then passed back out through the annular wall on an opposing side of theaperture208 leaving a loop orsling212 of suture in the subannular space. As shown in the posterior view on the right side ofFIG. 34, more than one suture can be applied. Turning toFIG. 35, afascial autograft214 is then inserted through theaperture208 into the subannular space using, for example,forceps216.FIG. 36 shows the fascial stent/patch214 fully inserted into the subannular space within thesuture sling212. The closure of the aperture is accomplished simultaneously with pulling theautograft214 toward the annular wall as shown inFIG. 37. Thesuture210 can be cinched218 or tied to maintain the closure and the fixation of the patch/stent.
• Patches can be folded and expanded in a single plane or in three dimensions. As shown inFIGS. 24-25 and41 for example, collapsing the patch can be accomplished laterally, whether the device is a single material or composite. Other embodiments, such as that shown inFIG. 1 can collapse vertically, and still others such as that shown inFIG. 26, longitudinally. Others can collapse in three dimensions, such as those shown inFIGS. 13-15 and36. Devices which expand in three dimensions can be packaged in a restraining jacket, such as a gelatine shell or “gelcap” for example, or a mesh of biosorbable or dissolvable material, that would allow for facile placement and subsequent expansion.
• Patches can also be constructed of a single component, as shown for example inFIG. 36, made of autograft or a synthetic material such as Dacron, or for example where the stent is a gelcap. They can be made of multiple components. An exemplary stent (not shown) can be made from a polymeric material, for example silicone rubber, which can be formed to have a natural unstressed shape, for example that of a “Bulb”. A stylet or push-rod can, for example, be inserted on the inside of the bulb to stretch the bulb into a second shape which is thinner and elongated. The second shape is sufficient to place within the aperture in the annulus. Upon placement of the device within the sub-annular space, the push-rod is removed and the bulb assumes it natural, unstressed state, assuming a larger dimension within the sub-annular space. Although silicone is used in this example, other metallic constructs could also be envisioned such as a Nitinol braided device that has a natural unstressed shape and assumes a second shape under tension for the delivery of the device. It is also contemplated that the opposite scenario can also accomplish the similar objective. In this alternative embodiment, the device can have a first configuration that is unstressed and elongated and assumes a second, larger configuration (bulb) under stress. In this embodiment, a portion of the stylet or rod that is used to mechanically activate the device would be left behind to hold the expansion element in its stressed configuration.
• Multiple components could include a frame to help with expansion of the device and a covering to obtain biocompatibility and tissue ingrowth. Examples of different frame configurations might include an expandable “Butterfly” or “Figure-8” configuration that could be constructed of wire material, such as Nitinol or multiple wires. Exemplary embodiments showingframe members502 are depicted inFIG. 41A-E. Of course, other configurations such as diamonds or other rounded or polygonal shapes can be used. The diamond frame is a construct that takes a first form that is smaller and expands to a larger frame. The diamond elements could be constructed from a single wire or from multiple wires. Alternatively, the members could be constructed of elements that are moveable fixed at each of the ends to allow expansion. A tether orattachment device504 is also depicted, which may be a suture, a wire, a screw, or other attachment means known in the art.
• The frame could be cut from a single material, such as flat stock Nitinol to accomplish the same objective, as shown for example inFIG. 31. Such shapes can be cut from flat stock using known methods, for example, laser cutting. A heat forming step could also be employed, as known in the art, to formbarbs132 in a shape that passes out of the flat plane of the stock material, as shown inFIG. 27 for example.
• Another frame configuration, also not shown, is that of a spiral or coil. The “Coil” design can be, for example, a spring steel or other biocompatible material that is wrapped to a first “wound” smaller configuration and expands to a larger unwrapped, unwound configuration.
• Depending on the size of the openings in the frames described above, each of these concepts may or may not have a covering over them in order to assure that the nucleus does not re-extrude from the intervertebral disc space after placement of the device, as well as to serve as substrate for the surrounding tissue to naturally incorporate the device. Coverings might include ePTFE, polyester, silicone, or other biocompatible materials. Coverings could also include natural materials such as collagen, cellulose, autograft, xenograft, allograft or similar materials. The covering could also be biodegradable in nature, such as polyvinyl lactic acid.
• Frames that are not covered may be permeable, such as a patch that is porous and allow for normal movement of fluids and nutrients through the patch into and out of the annular ring while maintaining nucleus fragments larger than the porosity of the stent/patch within the subannular space. Depending on the material that the frame is constructed, a surface finish may be added to promote tissue ingrowth into the patch. For example, a titanium sputtering of the device may allow it to be more easily incorporated within the disc space. Alternatively, a NiTi or tantalum foam could be added to the outer surface of the patch to promote tissue ingrowth.
• It is understood that there can be a variety of device designs of patches to accomplish the expansion of a device from a first configuration, to a second configuration to occupy the sub-annular space and reduce re-extrusion of the nucleus. The following device concepts are further discussed for additional embodiments of a device and/or system for the repair of an intervertebral disc annulus.
• As mentioned hereinabove, the stent/patch according to the present invention may comprise a mass of fascial autograft, and that autograft may be contained in a covering of material to form what will be referred to herein as a “bag”. Of course, this term is used not necessarily to connote a five-sided closed container so much as to denote the notion of flexibly surrounding the volume of a patch/stent material so that it can be manipulated in space.
• In the most simplistic form, a prefabricated device of sutures could be used to form the “sling” to hold the fascial implant as discussed above. The advantage of this design over simple placement of sutures to hold the autograft is better containment and control of the autograft during and after implantation. The “sling” or a “bag” surrounds the fascial autograft to hold it in place. It is contemplated that other materials, such as a polyester mesh, could be used instead of the fascial autograft.
• FIG. 38 shows an example of apre-fabricated sling300. There are three sutures used in this example,302,304, and306, although there could be more or less sutures as would be understood by one of ordinary skill in the art. Acollar member308 has apertures or other features for attaching to the sutures. In this example, thethird suture306 passes along or within thecollar308 to form a loop extending from the lateral extent of thecollar308. The first andsecond sutures302,304 form loops from the superior and inferior extents of thecollar308.Intersections310 can secure the loops to each other with small loops or knots in the sutures, small fabric attachment pieces, or by small preformed devices resembling grommets placed on the suture to aid in securement. Other knot tying techniques known in the art can also be employed. Turning toFIG. 39, the collar is depicted within the subannular space where the loops surround afascial autograft314 which by pulling proximally thesutures302,304,306 the graft is collapsed into contact with the annular wall in a sealing manner. The sutures can be made of known materials, e.g., biodegradable, bioabsorbable or bioresorbable Vicryl or biocompatible nylon. The collar can be made of a fabric material, e.g., polyester. During placement, one end of some or each suture can be passed through the inferior wall of the annulus and the other end can be passed through the superior wall surrounding the aperture. After the placement of the sling into the wall of the annulus, the fascial autograft is placed within the sling. The sutures are tightened to bring the tissues together and also to help reapproximate the aperture, as the collar size will be selected based on the surgeon's judgment according to the degree of reapproximation desired.
• Other constructions can also be used to accomplish the same objective, such as a “bag”404 formed of expandable PTFE as shown inFIG. 40. The bag is placed through an aperture in theannulus402. Additionally, a oneway seal406 can be positioned behind theaperture408. Suturing techniques for introducing cardiac valves could be employed to place the seal. It is understood that there could be multiple constructs to accomplish the same objective and this is only given as an example.
• The are a variety of ways to affix the device to the sub-annular wall of the annulus in addition to those discussed hereinabove. The following exemplary embodiments are introduced here to provide inventive illustrations of the types of techniques that can be employed to reduce the time and skill required to affix the patch to the annulus, versus suturing and tying a knot. Discussed hereinabove is the use of sutures, staples and other fixation devices, such as those passed throughslot18 to affix the patch to the annulus as shown inFIG. 1.FIG. 20 also depicts the use of “barbs” on the surface of the stent to facilitate fixation to the annulus. In a simple example, as shown inFIG. 20, a patch/stent could be compressed, passed through a guide tube such astubes18,18A shown inFIGS. 22 and 23, and expanded within the sub-annular space. As shown inFIG. 42, the expandedpatch602 is shown havingbarbs604, along withdetachable delivery tool608 and guidetube606. Once expanded,barbs604 on the outer surface ofpatch602 can be used to fix the patch into theinner wall610 of theannulus612 by pulling the patch back proximally, into thesub-annular wall610, and pushing forward distally on theguide tube606, thus driving thebarbs604 into the annulus and drawing the inner and outer tissues of the annulus together and reapproximating the disc on either side of the aperture, as shown inFIG. 43. After the placement of the patch, the delivery tool and guide tube are removed.
• The advantage of this design described above is that it requires very little time and skill to place and secure the patch to the annulus while also drawing the tissues together.
• Materials of the patch could be similar to materials discussed hereinabove. Anchoring barbs could be made of a biocompatible material, for example a metallic material (e.g., NiTi alloy, Stainless steel, Titanium), or a polymeric material (e.g., polypropylene, polyethylene, polyurethane). Anchoring barbs could also be a biodegradable/bioabsorbable material, such as a polyglycolic acid (PGA), a polylevolactic acid (PPLA), a polydioxanone (PDA) or for example a racemic polylactic acid (PDLLA). If the barbs included a biodegradable/bioabsorbable material, it is anticipated that the barbs might have sufficient holding strength for a sufficient period of time to allow the patch to be incorporated into the annulus during the healing process. The advantage of having the anchoring barb ofFIGS. 42 and 43 being biodegradable/bioabsorbable is that after the incorporation of the patch into the annulus there may be no need for the barbs to provide fixation. However, barbs pointing toward the outer surface of the annulus could pose a long term risk of penetration out of the annulus due to migration, and potentially impinging on the nerve root and spinal canal. Biodegradable/bioabsorbable barbs address and advantageously reduce any long-term risk in this regard.
• It is also possible that the barbs could be made of both a biocompatible component and a biodegradable/bioabsorbable component. For example, the very tip of the barb could be made of a biodegradable material. The barb could penetrate the annulus wall with a rather sharp point, but after degradation the point of the barb would become dull. In this embodiment, the point would no longer induce continued scar formation after the patch has been incorporated, nor pose a risk of penetrating out of the annulus onto the nerve root.
• Another fixation means includes the passing of “anchoring bands” into the wall of the annulus, vertebral bodies (superior, inferior, or both), or the Sharpey's Fibers (collagenous fibers between the junction of the annular fibers and vertebral bodies). In the following example of anchors, the barbs or bands are affixed to the annulus/vertebral bodies/Sharpey's fibers. Another element, for example a suture, cinch line, or a staple is utilized to attach the anchor bands to the patch, and thus hold the patch in proximity to the inner wall of the annulus. In addition, these bands may re-approximate the tissues at the aperture.
• Revisiting one example of using barbs to anchor the device is shown inFIG. 9, described hereinabove. Barbs or bone anchor screws50ands52 are passed into the superior and inferiorvertebral bodies54 and56, respectively. Superiorly,suture40 is passed through the outer wall of the annulus, to the sub-annular space. The suture is then passed through theeyelet53 ofbone anchor52 and then passed through the wall of the annulus from the sub-annular space to the outer wall of the annulus. The inferior end of the suture is similarly passed through the annulus, eyelet of the bone anchor, and back through the wall of the annulus. Both ends ofsuture40 are tightened and tied. The advantage of this concept is that it allows for fixation of the device to a surface that is known to be present in all discectomy procedures—the vertebral bodies. Whereas, it is possible, depending on the location and size of a natural rent that there may not be sufficient annulus accessible to fixate the device directly to the annulus. In addition to providing a location for fixation, anchoring into the vertebral bodies may provide a more stable anchor surface.
• Another example of fixating the device to inner wall of the annulus is shown inFIG. 29, and is further illustrated byFIGS. 44-47. As discussed hereinabove, with reference toFIGS. 22-30, apatch120 is placed with adelivery tool122, through the inner lumen of aguide tube118, into the sub-annular space and then expanded. This step can also be seen inFIGS. 45 and 46, where apatch702 is folded and passed through aguide tube706 and is held by adelivery tool704. Also shown is a anchor band orstaple709 and an anchorband delivery device708. Within the guide tube, or within the delivery tool, there is a suture line orcinch line710 that is attached to the center of thepatch702. This can be seen inFIG. 44awith theguide tube706 removed. As seen inFIGS. 45C and 46A, theguide tube706 is retracted after thepatch702 has been expanded and deployed. Next, an anchorband delivery tool708 is used to deliver one or more “bands”709 onto the outer surface of the annulus. These are intended to be anchored into the wall of the annulus with barb shapes that do not allow for the barbs to be pulled back through the annulus. The anchor bands resemble a construction of a “staple”. The bands could actually be constructed by connecting two barbed elements with, for example, a suture between the two barbed elements. The barbs and the connection band between the barbs could be constructed of the same material or of different materials. For example, the barbed part of the anchor band could be a biodegradable/bioabsorbable material (such as polyglycolic acid) or could be constructed of a metallic or polymeric biocompatible material (e.g., titanium, NiTi alloy, stainless steel, polyurethane, polypropylene). In addition, the band that connects these barbs can be constructed of materials that are similar to the barbs, or different materials. For example, the connection band could be a biodegradable/bioabsorbable suture, such as Vicryl, or a biocompatible material such as polypropylene. In addition, it is possible that these elements are constructed from multiple materials to accomplish the objective of anchoring into the annulus and providing for a fixation site to draw the patch within proximity of the sub-annular wall.
• FIGS. 44B and 44C show the placement of theanchor bands709 into theannulus712 with the anchorband delivery tool708.FIGS. 46A and 46B schematically show the placement of theanchor bands709 into the wall of theannulus712 and the retraction of the anchorband delivery device708, with thepatch delivery tool704 still in place.FIG. 44D depicts arepresentative anchor band709, having a pair ofstainless steel barbs709″ connected by asuture709′.FIG. 44E shows thepatch702,anchor bands709, and cinch line orsuture710 with the delivery tools removed, prior to drawing the patch and the tissues of the annulus together. In this embodiment there is apre-fabricated knot714 on the cinch line, which is described further inFIG. 47B, although other knots are possible.FIG. 47aalso shows a posterior view of the patching of the annulus with this device withknot714. In this stent/patch702 a pair of loops of 7mm suture709 are shown, which engage the cinch line and slip knot. These suture loops connect to the barbs directly, as inFIG. 44, or loop to surgical staples, or are placed directly into the annulus. The presence of a pre-fabricated knot on the cinch line makes the process of repairing quicker since there is no need to tie a knot. It also facilitates drawing the tissues together. The use of the cinch line and a pre-fabricated knot can be placed by, for example, an external tube such as a knot pusher.FIG. 44E is similar to theFIG. 29 described hereinabove prior to “tying” theknot145.FIG. 44F shows the drawing of the patch and the annular tissues together by pulling on the suture in the direction “A” indicated by the arrow. In this case, the Knot Pusher has been removed from thecinch line710. Thesuture710 is drawn proximally to draw thepatch702 into engagement with the inner wall of the annulus to seal the aperture from within, as well as draw the walls of the annulus together to reapproximate the annular aperture.FIG. 46C andFIG. 44G show thecinch line suture710 tied and drawing the annular tissues together, after the excess suture line has been cut. It is also apparent from this device, fixation and delivery system that the outer surfaces of the aperture are also drawn together for re-approximation.
• The cinching of the bands and the patch also allows for taking-up the slack that allows for the accommodation of varying sizes. For example, the thickness of the annular wall surrounding the aperture can vary from 1 mm up to 10 mm. Therefore, if the anchor bands have a set length, this design with an cinch line accommodates different dimensions of the thickness of the wall of the annulus by drawing the “slack” of the bands together within the aperture.
• Although it has been described here as patch placement that involves two lateral anchor bands with a suture to draw the patch, bands and tissues together, one or more bands could be used and two bands is only an example. Furthermore, the anchor bands were placed with the barbs in a superior-inferior fashion. One skilled in the art would recognize that these could be placed at different locations surrounding the aperture. Moreover, although it was described that the bands are placed into the annulus, these anchor bands could also be placed in the vertebral bodies as shown inFIG. 48A generally at800, or the Sharpey'sFibers802, as shown inFIG. 48B generally at804.
• Although the patch depicted in the example above does not have barbs attached to the patch, it is also possible to have the barbs as described hereinabove to further promote the fixation of the patch to the inner wall of the annulus.
• Finally, although the drawings depict an aperture that lends itself to re-approximating the tissues, it is conceivable that some apertures, whether natural or surgically made, may be relatively large and therefore might require the placement of additional material within the aperture to act as a scaffold for tissue in growth, between the patch on the inner wall of the annulus and the anchor bands located on the outer wall. An example of material to fill the aperture might include autograft para-spinal fascial tissue, xenograft, allograft, or other natural collagenous materials. The filler material could also be of a biocompatible material such as a Dacron material.FIG. 51 shows the illustrative filling of an aperture withimplant material716 prior to cinching thesuture710.
• As an alternative embodiment of the present invention, theanchor bands709 as described previously (anchor bands into annulus) could be sufficiently long enough to pass through the annulus and then through the patch. The barbs in this embodiment have an engaging involvement with the patch. This concept was previously discussed hereinabove in connection withFIG. 30. Further illustration of such a system is schematically shown in FIGS.49 and50. Passing the barbs through the patch, in this embodiment, provides additional security and safety of reducing the possibility that the barbs may migrate after implantation. In this application of the invention, the suture cinch line may (FIG. 50) or may not (FIG. 30) be used in addition to the anchor bands to draw the tissues together and reduce tissue movement surrounding the aperture.
• In addition, although the bands shown inFIGS. 49 and 50 take the form of a “barb”, they could as easily take a form of a simple T-barb720, as shown inFIG. 52E, or a C-type element wherein the object is to have irrevocable engagement with thepatch device702 after the penetration through the patch. A T-type attachment, when aligned longitudinally with the suture, passes through the patch. The T section then rotates to prevent the suture anchor from being pulled back through the patch. In another embodiment a “C’ retainer made of a superelastic material may be attached to the end of the suture band. The C retainer is loaded into a needle wherein it is held straight. The needle is used to pass the C retainer and suture through the patch and deploy the retainer in a second configuration in the shape of a “C”.
• It is also foreseen within the scope of the invention that there may be patch designs which will accommodate the placement and securement of the anchor to the fabric that covers the frame of the patch. For example, a frame for a patch that is made out of metal such as Nitinol can provide for “windows”. The device, covered with a mesh fabric, for example silicone or Dacron, would therefore allow the anchoring barbs to be passed through the “windows” in the frame of the patch. In this case, the barb can be secured to the patch in the fabric covering the frame.
• Alternatively, the patch can be secured by passing barbs that engage the lattice of the patch frame. These embodiments of the invention illustrate designs in which the barbs engage with the vertical, horizontal or criss-crossed structures/members of the frame. In this case, the barbs would pass through the mesh or lattice of the frame and they would be unable to pass back out of the structure.
• Although this discussion refers to “anchor bands” that are shown to be two anchors connected by a suture, it is also contemplated that single barbs with sutures are placed and the sutures' ends, at the outer surface of the annulus, are tied after placement through the patch.
• One objective in the designs discussed hereinabove is to provide a way to “pull up the slack” in a system to adjust the length of sutures and for anchor bands. According to the present invention, a technique referred to as the “Lasso Cinch Knot” was developed as a means to draw the anchor bands together with a suture cinch line that is incorporated into the patch design.FIG. 53 gives further description of the use of the Lasso embodiment. In essence, patch and frame constructs are used that incorporate the “barbs through the patch” design. Once the barbs have passed through the patch, aninternal lasso722 is drawn tight around the sutures of the anchor bands and thus draws the extra suture material within the patch. The internal lasso gathers the sutures of the bands, and as the lasso is tightened, it cinches together the sutures of the bands and therefore tightens them and eliminates slack, bringing the patch/stent into closer or tighter engagement with the annulus wall. The patch inFIG. 53 additionally provides for a diamond shape grid pattern, which advantageously provides a grid which will while allowing a probe or similar instrument to pass through with little resistance, provides resistance to a barb or other restraining feature on the instrument. The frame shown can be made from nitinol, and the locking and holding windows shown at the center of the figure would allow for rotation about the z-axis during placement. A slipknot technique using, for example a knot pusher, would aid in the loop pulling process by the lasso. The internal loop (lasso) can be tacked to the outside corners of the patch/stent, in order to hold the loop at the outer edges of the patch frame. When cinching the lasso knot, the loop can be pulled free from some or all of its tacked attachment points to the frame, to prevent deformation of the planar shape of the frame when cinching the lasso. As above, the frame can be a composite structure or sandwich formed with some type of mesh fabric. The proximal mesh fabric can be bonded fully to the patch frame, for example through the use of an adhesive, for instance a silicone. Adhesive, advantageously, can fill the interstices of the grid pattern while allowing for easy probe penetration and protection of the suture lines. Protection of the suture lines is advantageous when the lasso is used to pull and bunch a group of band sutures together.
• It is also contemplated within the scope of the present invention that sutures710′ can be preattached directly to a stent/patch. As shown inFIG. 52A severalseparate barbs709′″ into theannulus712 can be directly attached to thepatch702. Each “barb” ofFIG. 52A can be independently placed into the annulus after the patch is deployed. This can be seen to be similar to theembodiment including barbs709″″ ofFIG. 55.
• An alternative embodiment for securing apatch902 and reapproximating a rent is providing each of the separate barbs with sutures having variable lengths as shown inFIG. 56. Eachindependent suture barb904 is placed into theannulus906 or into thepatch902 with thebarb delivery tool908. After the placement, all of thesuture lines910 are drawn taught, by drawing on the free ends that exit thepatch delivery tool912. A lockingelement914 that uses agasket916 and threading mechanism is attached to thepatch902 and is used to tighten thegasket916 around the distal ends of thesutures910. Thepatch delivery tool912 is removed and the extra suture length is cut. It is also possible that the gasket mechanism could be a press-fit to accommodate the tightening of the sutures to the patch.
• Alternatively, the locking mechanism can be as shown inFIG. 57, although in this case the engagement of thelocking element914′ takes part on the patch. Pulling thesuture910 in the direction of arrow B will tighten and lockingly hold in tension to aid in securement and reapproximation. The adjustable length suture band between the two anchors allows slack to be taken up between theanchors916. Two T-type anchors are illustratively shown in this example, but multiple anchors of differing configurations could be used. The locking features can be included on the feature band, as depicted here, and allow for substantially one-way locking engagement with the anchor members. This adjustability advantageously promotes for the accommodation of varying thickness of the annulus from patient to patient. The suture slack in this embodiment may be taken up to close the defect in the annulus and/or to shorten the band between anchors for a secondary cinching of multiple tensioned suture bands as described hereinabove.
• The cinch line and the Lasso concepts in essence try to facilitate the re-approximation and drawing of tissues together in a fast and simple way. Other contemplated embodiments for “tension” elements include using an elastic coupler as a part of the anchor band used to fixate the device. The elastic coupler can be expanded for placement, and upon release, can draw tension to pull the tissues together. The coupler could be made of a biocompatible metal or polymer, or could be constructed of a biodegradable/bioabsorbable material.
• Similarly, an alternative embodiment to cause tension within the device and draw the tissues together after placement of the anchor bands might include an elastic band or band with a spring which one end can be attached to the anchor bands and the other end attached to the patch. Alternatively, the anchor bands might, in and of themselves may be made of an elastic band between the barbs, or may contain a spring element between the barbs. Such an embodiment can be made to resemble a so-called “Bobber Spring.” Again, it is contemplated that the elastic or resilient element could be made from a wide variety of metals, polymeric, or biodegradable/bioabsorbable material.
• FIG. 59 describes an embodiment where thepatch element1002 takes the form of a mesh seal. The securement is effected by a hook having abarb element1004 that penetrates the inner surface of theannulus1006, while the inner connection of the hook (barb)1004 is attached to the patch in such a fashion as to add tension between the outer surface of the annulus and the inner surface in proximity to the patch, thus drawing the annular tissues together. The patch/stent1002 contains aspring ribbon element1008 which can be formed from nitinol or other spring material.Hooks1010 are then deployed to “grab” the annulus, either through penetration or through grasping into theaperture1012 as shown.
• FIGS. 54a-fshows another embodiment of a means to draw the suture lines together to cause tension between the inner and outer tissues of the annulus. Anchor bands, for example T-barbs720′ are placed through the annulus and the patch, and they are secured to thepatch702. “Slack” in the suture of the anchor band is “rotated” around a detachable portion of thedelivery tool704′ and a locking element, for example ascrew configuration724 as shown in the drawing, is used to lock the extra suture line in place affixed tothreads726 with thepatch702. Thedelivery tool704′ is then removed.
• FIG. 58 shows alternative embodiments for tightening “anchoring barbs” with different configurations of sutures and cinch lines. For example inFIG. 58B each independent barb has a looped suture attached to it. Through each of these loops is passed a cinch line, which contains a knot. After placement of the barbs within the annulus, and possibly through the patch, the cinch line draws the loops of the barbs together. The advantage of this embodiment is that it allows for the independent placement of multiple barbs and the ability to draw all of them together.
• Although cinch lines have been described as using a knot to “lock” the length of the suture, other mechanisms could also lock the length, as shown inFIG. 57. The locking of the suture length is accomplished through a mechanical element located on the barb which engages with three dimensional elements attached to the suture line which mechanically press fit through the engagement element on the barb, thus locking the length of the suture line into place.
• Although the embodiments ofFIG. 57 andFIG. 58 depict the use of a single locking mechanism (e.g., knot on cinch line), it is conceivable that various designs could use more than one locking element to achieve the re-approximation and drawing together the tissue surrounding an aperture.
• A further exemplary embodiment of the invention further describes a concept illustrated byFIG. 41e, for example. Abraided patch1100 such as depicted inFIGS. 60 through 66, is a further illustrative embodiment of the present invention that can be deployed into the subannular space to act as a barrier to the extrusion of the nucleus pulposus.
• The “patch”1100 is constructed from a braided tube offilaments1102. The ends1104 of the braided tube are heat-sealed to keep the braid from unraveling and the seals also provide structural integrity to the patch when deployed. Thebraided patch1100 is woven on a braiding machine withmultiple filaments1102 to create the structure. For example, the patch can be woven with 72 polyester filaments in order to create the construct that readily deploys into the annular defect, promotes cell ingrowth into the device, and retains an anchor after it has been placed through the wall of the annulus and through the patch. Changing the number offilaments1102 in the patch, the material of the filaments, the dimension of the filaments (e.g., diameter), as well as the configuration of the filaments (e.g., cross-sectional area), or changing the braid pattern, can create differences in the characteristics of the patch. The braided patch can be made on a standard Steeger braider, or similar type braiding machine, that can handle braiding from anywhere from 16 filaments at a time, to up to 196 filaments. Preferably the patch is braided with between 32 to 144 filaments.
• Thefilaments1102 of the patch can be made of different materials or all of the filaments in a patch can be of like material and dimensions. The filaments can be metallic, such as a stainless steel, a nickel titanium alloy, or other metallic materials. Thepatch1100 can also be made from biocompatible polymeric material such as polyethyleneteraphthalate, polyester, polyethylene, or polypropylene, for example. It is also conceivable that the patch can be braided from biodegradable materials, such as polyglycolic acid (PGA), polylactic acid (PLA), or other material that may degrade and be re-absorbed by the body over time.
• It is also possible to braid thepatch1100 with multiple materials and/or multiple dimensions of the filaments. For example, the patch can be braided with 32 filaments of a polymeric PET material and 32 filaments of polyester yarn material to create a patch that is optimal for sealing an annulus. The combination of different filament materials, sizes, cross-sectional configuration, number of filaments, and braiding pattern can be used to construct a braided patch that can be delivered into the sub-annular space, while acting as a scaffold to induce healing of the aperture.
• The braided patch has advantages in that it can be placed through an aperture in the wall of the annulus that is relatively small, but then expand to a dimension that is substantially greater than the aperture. For example, it is possible to construct the braided tube to be less than 5 mm in diameter, whereas in its fully deployed state it could be greater than, for example, 20 mm.
• Referring toFIG. 62, thenon-deployed braided patch1100 is affixed on the distal end of thepatch delivery tool1200. It is situated in a fashion that is co-axial with the delivery tool's delivery members. Further detail of the deployment mechanism can be seen inFIG. 63. Thebraided patch1100 is placed on the distal end of theinner delivery member1202. The heat-setdistal cuff1104 of the patch is situated within a depressed region on the distal region of theinner delivery member1216. The distal portion of thedelivery member1216 is slotted as shown inFIG. 65, and, in the non-deployed state, contains aco-axial retention member1208 that acts to press the slotted potions of the inner delivery member apart, and thus securing the distal cuff of thepatch1104 on the distal region of theinner delivery member1202. The proximal portion of the patch abuts and is in contact with anouter pusher member1204. In the non-deployed state, the delivery device is passed into the aperture of the annulus. Once inside the annular aperture, theouter pusher member1204 of thedelivery device1200 is pushed toward the distal end of the device, while theinner delivery member1202 is pulled proximally. This action of moving these members in such a fashion results in the braided patch expanding perpendicular to tube's axis, as shown inFIGS. 61 and 64.
• Once thepatch1100 has been expanded to its fully expanded state, acinch line1212 that is connected to the distal and proximal ends of the patch can be tightened and a knot, such as a Roeder knot, can be used to hold the braided patch in its expanded configuration. Although, the device is shown with acinch knot1214, it is possible that a locking element may not be needed, depending on the means used to fixate the patch into the annulus. It is possible that no locking means is necessary. It is also possible that alternative locking means can be contemplated to keep the braided patch in its expanded form. Aknot pusher1210 can also be employed to manipulate theknot locking device1214.
• Once the device patch has been expanded into its final configuration in the aperture and subannular space, the retention member can be removed from the distal portion of the inner member by slidably pulling the proximal end of the retention member in a proximal direction. Removing the retention member relieves the stress holding the distal cuff of the patch in place and allows the patch to be slideably removed from the distal end of the delivery device, and thus deployed into the subannular space.
• As depicted inFIG. 66, thepatch1100 can be affixed to the inner surface either before or after the deployment of the patch from the delivery device. It is also contemplated that this patch can be affixed to the inner surface of the annulus by the various fixation means described in other parts of this application. For example, anchor bands as shown inFIG. 29 could be used to penetrate the annulus and the patch to anchor the patch into the sub-annular space. It is also conceivable that single T-anchors1310 with a band1314 (e.g., suture) could be delivered through theannulus1306 andpatch1100 with the portion of the suture on the outer surface of the annulus locked to the outer surface with a knot, pledget, orother locking device1316. It is also conceivable that the patch could be affixed to the inner surface of the annulus through the use of adhesives, such as cyanoacrylate, fibrin glue, polymer protein, polyurethane or other material used to cure the patch in the subannular space in situ.Path1312 illustrated another possible suture path through the bone of the vertebra to penetrate and hold a T-anchor member1310 in the patch.
• A device suitable for affixing a stent or patch to a disc annulus is disclosed in copending U.S. patent application Ser. No. 10/327,106, filed on Dec. 24, 2002, and commonly assigned herein, the contents of which are incorporated herein by reference.
• The advantages of this design, given the right selection of filament dimension, configuration, material, braid pattern, and number of filaments is that it can be easily delivered to the annular repair site, have the flexibility to take the shape of the annular defect while maintaining the mechanical integrity needed to remain within the disc space upon loading. Another advantage, again with the appropriate selection of material, filament configuration, braiding, dimensional considerations, and multiple filament weaves, is that one can construct a patch that is conducive, in its deployed state, for incorporation of fibrosis and the fibrotic healing of the annular defect. Finally, the patch can be designed so that when it is in its delivered state, it can easily receive one or more anchor bands through the braided filaments while retaining the T-anchor or other similar type fixation device, after passing the fixation device through the patch.
• All patents referred to or cited herein are incorporated by reference in their entirety to the extent they are not inconsistent with the explicit teachings of this specification, including; U.S. Pat. No. 5,108,438 (Stone), U.S. Pat. No. 5,258,043 (Stone), U.S. Pat. No. 4,904,260 (Ray et al.), U.S. Pat. No. 5,964,807 (Gan et al.), U.S. Pat. No. 5,849,331 (Ducheyne et al.), U.S. Pat. No. 5,122,154 (Rhodes), U.S. Pat. No. 5,204,106 (Schepers at al.), U.S. Pat. No. 5,888,220 (Felt et al.) and U.S. Pat. No. 5,376,120 (Sarver et al.).
• Various materials know to those skilled in the art can be employed in practicing the present invention. By means of example only, the body portions of the stent could be made of NiTi alloy, plastics including polypropylene and polyethylene, stainless steel and other biocompatible metals, chromium cobalt alloy, or collagen. Webbing materials can include silicone, collagen, ePTFE, DACRON, polyester, polypropylene, polyethylene, and other biocompatible materials and can be woven or non-woven. Membranes might be fashioned of silicone, propylene, polyester, SURLYN, PEBAX, polyethylene, polyurethane or other biocompatible materials. Inflation fluids for membranes can include gases, liquids, foams, emulsions, and can be or contain bioactive materials and can also be for mechanical, biochemical and medicinal purposes. The stent body, webbing and/or membrane can be drug eluting or bioabsorbable, as known in the medical implant arts.
• Other embodiments of the invention will be apparent to those skilled in the art from consideration of the specification and practice of the invention disclosed herein. It is intended that the specification and examples be considered as exemplary only, with a true scope and spirit of the invention being indicated by the following claims.

Claims (8)

1. A device for treating an aperture in the annulus of a patient's intervertebral disc, said device comprising a cylindrical body formed of a plurality of filamentous elements, said body having a radial diameter, a first end and a second end subtending a longitudinal dimension, said device having a first configuration, and a second configuration, wherein the second configuration, in use, is characterized by a relatively larger radial diameter along at least a portion of said longitudinal dimension.

2. The device ofclaim 1, wherein said body is sized to be inserted through said aperture in a intervertebral disc into the subannular space in said first configuration and then placed in said second configuration to at least partially cover said aperture.

3. The device ofclaim 1, wherein said second configuration is additionally characterized by a relatively smaller longitudinal dimension in said second configuration than in said first configuration.

4. The device ofclaim 1, wherein at least a portion of the stent is formed at least in part of flexible biocompatible material.

5. The device ofclaim 1, wherein at least a portion of the stent is formed at least in part of bioresorbable material.

6. The device ofclaim 1, wherein at least a portion of the stent is formed at least in part of nylon.

7. The device ofclaim 1, wherein at least a portion of the stent is formed at least in part by weaving.

8. The device ofclaim 1, wherein at least a portion of the stent is formed at least in part by braiding.

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