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US20060095136A1 - Bone fusion device - Google Patents

Bone fusion device Download PDF

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Publication number
US20060095136A1
US20060095136A1 US11/264,958 US26495805A US2006095136A1 US 20060095136 A1 US20060095136 A1 US 20060095136A1 US 26495805 A US26495805 A US 26495805A US 2006095136 A1 US2006095136 A1 US 2006095136A1
Authority
US
United States
Prior art keywords
fusion device
bone fusion
bone
tab
bones
Prior art date
Legal status (The legal status is an assumption and is not a legal conclusion. Google has not performed a legal analysis and makes no representation as to the accuracy of the status listed.)
Abandoned
Application number
US11/264,958
Other languages
English (en)
Inventor
Gary McLuen
Current Assignee (The listed assignees may be inaccurate. Google has not performed a legal analysis and makes no representation or warranty as to the accuracy of the list.)
McLuen Design Inc
Original Assignee
McLuen Design Inc
Priority date (The priority date is an assumption and is not a legal conclusion. Google has not performed a legal analysis and makes no representation as to the accuracy of the date listed.)
Filing date
Publication date
Family has litigation
First worldwide family litigation filed litigation Critical https://patents.darts-ip.com/?family=36263100&utm_source=google_patent&utm_medium=platform_link&utm_campaign=public_patent_search&patent=US20060095136(A1) "Global patent litigation dataset” by Darts-ip is licensed under a Creative Commons Attribution 4.0 International License.
Priority to US11/264,958 priority Critical patent/US20060095136A1/en
Application filed by McLuen Design Inc filed Critical McLuen Design Inc
Assigned to MCLUEN DESIGN, INC. reassignment MCLUEN DESIGN, INC. ASSIGNMENT OF ASSIGNORS INTEREST (SEE DOCUMENT FOR DETAILS). Assignors: MCLUEN, GARY R.
Priority to PCT/US2005/039984 priority patent/WO2006050500A2/fr
Priority to US11/357,319 priority patent/US7727280B2/en
Publication of US20060095136A1 publication Critical patent/US20060095136A1/en
Priority to US11/484,379 priority patent/US8187332B2/en
Priority to US13/482,778 priority patent/US8597360B2/en
Priority to PCT/US2013/042066 priority patent/WO2013181024A1/fr
Priority to US14/067,813 priority patent/US9186262B2/en
Priority to US14/885,777 priority patent/US9974665B2/en
Priority to US15/954,414 priority patent/US10682240B2/en
Priority to US16/798,098 priority patent/US11583414B2/en
Priority to US18/111,561 priority patent/US12491087B2/en
Abandoned legal-status Critical Current

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    • A61F2250/00—Special features of prostheses classified in groups A61F2/00 - A61F2/26 or A61F2/82 or A61F9/00 or A61F11/00 or subgroups thereof
    • A61F2250/0004—Special features of prostheses classified in groups A61F2/00 - A61F2/26 or A61F2/82 or A61F9/00 or A61F11/00 or subgroups thereof adjustable
    • A61F2250/0006—Special features of prostheses classified in groups A61F2/00 - A61F2/26 or A61F2/82 or A61F9/00 or A61F11/00 or subgroups thereof adjustable for adjusting angular orientation
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61F—FILTERS IMPLANTABLE INTO BLOOD VESSELS; PROSTHESES; DEVICES PROVIDING PATENCY TO, OR PREVENTING COLLAPSING OF, TUBULAR STRUCTURES OF THE BODY, e.g. STENTS; ORTHOPAEDIC, NURSING OR CONTRACEPTIVE DEVICES; FOMENTATION; TREATMENT OR PROTECTION OF EYES OR EARS; BANDAGES, DRESSINGS OR ABSORBENT PADS; FIRST-AID KITS
    • A61F2250/00—Special features of prostheses classified in groups A61F2/00 - A61F2/26 or A61F2/82 or A61F9/00 or A61F11/00 or subgroups thereof
    • A61F2250/0004—Special features of prostheses classified in groups A61F2/00 - A61F2/26 or A61F2/82 or A61F9/00 or A61F11/00 or subgroups thereof adjustable
    • A61F2250/0009—Special features of prostheses classified in groups A61F2/00 - A61F2/26 or A61F2/82 or A61F9/00 or A61F11/00 or subgroups thereof adjustable for adjusting thickness
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61F—FILTERS IMPLANTABLE INTO BLOOD VESSELS; PROSTHESES; DEVICES PROVIDING PATENCY TO, OR PREVENTING COLLAPSING OF, TUBULAR STRUCTURES OF THE BODY, e.g. STENTS; ORTHOPAEDIC, NURSING OR CONTRACEPTIVE DEVICES; FOMENTATION; TREATMENT OR PROTECTION OF EYES OR EARS; BANDAGES, DRESSINGS OR ABSORBENT PADS; FIRST-AID KITS
    • A61F2310/00—Prostheses classified in A61F2/28 or A61F2/30 - A61F2/44 being constructed from or coated with a particular material
    • A61F2310/00005—The prosthesis being constructed from a particular material
    • A61F2310/00011—Metals or alloys
    • A61F2310/00023—Titanium or titanium-based alloys, e.g. Ti-Ni alloys
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61F—FILTERS IMPLANTABLE INTO BLOOD VESSELS; PROSTHESES; DEVICES PROVIDING PATENCY TO, OR PREVENTING COLLAPSING OF, TUBULAR STRUCTURES OF THE BODY, e.g. STENTS; ORTHOPAEDIC, NURSING OR CONTRACEPTIVE DEVICES; FOMENTATION; TREATMENT OR PROTECTION OF EYES OR EARS; BANDAGES, DRESSINGS OR ABSORBENT PADS; FIRST-AID KITS
    • A61F2310/00—Prostheses classified in A61F2/28 or A61F2/30 - A61F2/44 being constructed from or coated with a particular material
    • A61F2310/00389—The prosthesis being coated or covered with a particular material
    • A61F2310/00976—Coating or prosthesis-covering structure made of proteins or of polypeptides, e.g. of bone morphogenic proteins BMP or of transforming growth factors TGF

Definitions

  • This invention relates generally to bone fusion devices. More specifically, the present invention relates to devices for fusing vertebrae of the spine that can be inserted arthroscopically.
  • the spinal column is made up of vertebrae stacked on top of one another. Between the vertebrae are discs which are gel-like cushions that act as shock-absorbers and keep the spine flexible. Damage, disease, or excessive pressure on the discs can cause degenerative disc disease or other disorders where the disc becomes thinner and allows the vertebrae to move closer together or become misaligned. As a result, nerves may become pinched, causing pain that radiates into other parts of the body, or instability of the vertebrae may ensue.
  • the fusion cage is typically a hollow metal device usually made of titanium. Once inserted, the fusion cage maintains the proper separation between the vertebrae to prevent nerves from being pinched and provides structural stability to the spine. Also, the inside of the cage is filled with bone graft material which eventually fuses permanently with the adjacent vertebrae into a single unit.
  • U.S. Pat. No. 4,961,740 to Ray, et al. entitled, “V-Thread Fusion Cage and Method of Fusing a Bone Joint,” discloses a fusion cage with a threaded outer surface, where the crown of the thread is sharp and cuts into the bone. Perforations are provided in valleys between adjacent turns of the thread.
  • the cage can be screwed into a threaded bore provided in the bone structure at the surgical site and then packed with bone chips which promote fusion.
  • U.S. Pat. No. 5,015,247 to Michelson entitled, “Threaded Spinal Implant,” discloses a fusion implant comprising a cylindrical member having a series of threads on the exterior of the cylindrical member for engaging the vertebrae to maintain the implant in place and a plurality of openings in the cylindrical surface.
  • U.S. Pat. No. 6,342,074 to Simpson entitled, “Anterior Lumbar Underbody Fusion Implant and Method For Fusing Adjacent Vertebrae,” discloses a one-piece spinal fusion implant comprising a hollow body having an access passage for insertion of bone graft material into the intervertebral space after the implant has been affixed to adjacent vertebrae.
  • the implant provides a pair of screw-receiving passages that are oppositely inclined relative to a central plane.
  • the screw-receiving passages enable the head of an orthopaedic screw to be retained entirely within the access passage.
  • U.S. Pat. No. 5,885,287 to Bagby entitled, “Self-tapping Interbody Bone Implant,” discloses a bone joining implant with a rigid, implantable base body having an outer surface with at least one bone bed engaging portion configured for engaging between a pair of bone bodies to be joined, wherein at least one spline is provided by the bone bed engaging portion, the spline being constructed and arranged to extend outwardly of the body and having an undercut portion.
  • U.S. Pat. No. 6,582,467 to Teitelbaum et al. entitled,“Expandable Fusion Cage,” discloses an expandable fusion cage where the surfaces of the cage have multiple portions cut out of the metal to form sharp barbs. As the cage is expanded, the sharp barbs protrude into the subcortical bone of the vertebrae to secure the cage in place.
  • the cage is filled with bone or bone matrix material.
  • U.S. Pat. No. 5,800,550 to Sertich entitled, “Interbody Fusion Cage,” discloses a prosthetic device which includes an inert generally rectangularly shaped support body adapted to be seated on hard end plates of vertebrae.
  • the support body has top and bottom faces.
  • a first peg is movably mounted in a first aperture located in the support body, and the first aperture terminates at one of the top and bottom faces of the support body. Further, the first peg projects away from the one of the top and bottom faces and into an adjacent vertebra to secure the support body in place relative to the vertebra.
  • U.S. Pat. No. 6,436,140 to Liu et al. entitled, “Expandable Interbody Fusion Cage and Method for Insertion,” discloses an expandable hollow interbody fusion device, wherein the body is divided into a number of branches connected to one another at a fixed end and separated at an expandable end.
  • the expandable cage may be inserted in its substantially cylindrical form and may be expanded by movement of an expansion member to establish lordosis of the spine.
  • An expansion member interacts with the interior surfaces of the device to maintain the cage in the expanded condition and provide a large internal chamber for receiving bone in-growth material.
  • the present invention is a bone fusion device for insertion between bones that are to be fused together, such as, for example, the vertebrae of a spinal column.
  • the bone fusion device comprises one or more extendable tabs.
  • the bone fusion device is in its most compact state when the tabs are aligned with the body of the device such that the tabs lie within the exterior of the device.
  • the bone fusion device is preferably inserted between the vertebrae by using an arthroscopic procedure.
  • the bone fusion device of some embodiments is filled with bone graft material. In these embodiments, the bone graft material is typically relocated from the interior to the exterior of the bone fusion device by using a lead screw.
  • each tab typically has an associated rotating means.
  • the position of each tab relative to the bone fusion device is adjustable depending upon the configuration of the associated rotating means. In this way, the tabs are advantageously positioned in the confined space between the vertebrae to help brace the device until the bone has fused. Further, the tabs of the bone fusion device provide a larger surface area to which the bones attach and fuse during a healing period.
  • the body of the bone fusion device is a round cylinder with end faces.
  • the bone fusion device has conduits or holes that allow the bone graft material within the device to flow to the exterior of the device where the material contacts and grafts to the vertebrae.
  • the extendable tabs are arranged in various configurations on the exterior of the bone fusion device, including the end faces.
  • the tabs are attached to the body of the device on more than one side to optimally brace the device from multiple directions between the adjacent vertebrae.
  • the bone fusion device has a rectangular shape with end faces and extendable tabs attached to multiple exterior surfaces.
  • the bone fusion device of some embodiments includes protrusions, threading, and/or sharp features on the exterior surface and/or the extendable tabs. These features are configured to engage the adjacent vertebrae to provide a tighter interface between the device and the vertebrae.
  • FIG. 1 illustrates a bone fusion device in accordance with some embodiments of the invention.
  • FIG. 2 illustrates a bone fusion device according to an alternative embodiment of the present invention.
  • FIGS. 3 A-B illustrate a section of a vertebral column showing the bone fusion device inserted between two adjacent vertebrae in place of an intervertebral disc.
  • FIGS. 4 A-B illustrate a detailed view of the worm screw drive and the extendable tabs of some embodiments.
  • FIGS. 5 A-B illustrate the small form factor of some embodiments.
  • FIGS. 7 A-B are perspective drawings illustrating the tabs and tab bays of some embodiments.
  • FIG. 8 illustrates a process flow in accordance with some embodiments of the invention.
  • FIG. 1 illustrates a bone fusion device 100 in accordance with some embodiments of the invention.
  • the bone fusion device 100 has a round cylindrical shape and has two end faces, including the end face 140 .
  • the bone fusion device 100 is preferably constructed from a high strength biocompatible material, such as titanium, which has the strength to withstand compressive and shear forces in the spine that are generated by a patient's body weight and daily movements.
  • the base biocompatible material is often textured or coated with a porous material conducive to the growth of new bone cells on the bone fusion device 100 .
  • the end face 140 has an opening 145 which allows the insertion of bone graft material into the bone fusion device 100 .
  • the bone graft material includes bone chips from the same patient (autograft), bone chips from a donor (allograft or xenograft), and/or a synthetic bone matrix.
  • the bone graft material typically promotes bone growth during a recovery period after the patient receives bone fusion surgery.
  • the bone fusion device 100 has several conduits or holes 150 , which permit the bone graft material to contact the vertebral bone after the device 100 has been inserted between the vertebrae of the patient.
  • the bone graft material and the surface texturing of the device 100 encourage the growth and fusion of bone from the neighboring vertebrae.
  • the fusion and healing process will result in the bone fusion device 100 becoming embedded within the two adjacent vertebrae of the spine which eventually fuse together during the healing period.
  • tabs 131 , 132 , 133 , 134 , 135 , and 136 are distributed along the round cylindrical body of the bone fusion device 100 .
  • These tabs 131 - 136 are each attached to the bone fusion device 100 by a respective rotating means 111 , 112 , 113 , 114 , 115 , and 116 .
  • the rotating means 111 - 116 is typically a turn screw type assembly.
  • the unextended tabs 121 - 126 of the bone fusion device 100 provide a compact assembly that is suitable for insertion into the patient's body through an arthroscopic surgical procedure.
  • An arthroscopic procedure is considered minimally invasive and has certain advantages over more invasive conventional surgical procedures.
  • a smaller surgical incision is employed as compared to the size of the incision required for conventional invasive surgery.
  • arthroscopic procedures minimize or eliminate the need for excessive retraction of a patient's tissues such as muscles and nerves, thereby minimizing trauma and injury to the muscles and nerves and further reducing the patient's recovery time.
  • each tab's 131 - 136 position is individually adjustable so as to optimally brace the device 100 between the vertebrae. Due to the compressive forces commonly associated with spinal column vertebrae, some embodiments include a range of motion for each tab that is slightly greater than 90 degrees.
  • the tabs of these embodiments are preferably rotated to an angle that is slightly more than about 90 degrees with respect to the surface of the bone fusion device.
  • the tabs extended in this configuration were found to be capable of withstanding the greatest amount of compressive force.
  • the tabs 131 - 136 when extended, abut tightly against the surfaces of the vertebrae that are immediately adjacent to the bone fusion device 100 .
  • the tabs 131 - 136 have sharp protrusions along the length of the tab for engaging the adjacent vertebrae, while the tabs 131 - 136 of some embodiments have screw-type threads for screwing into and engaging the vertebrae.
  • the tabs of some embodiments have surface texturing to encourage and enhance the growth of new bone on the tabs 131 - 136 . This surface texturing is often similar to the surface texturing used on the main body of the device 100 .
  • the tabs 131 - 136 advantageously wedge the bone fusion device 100 in a fixed position between the vertebrae and provide a larger surface area with which the adjacent vertebrae fuses during the healing period.
  • bone growth material such as protein, is typically applied to the tabs 131 - 136 to stimulate the regeneration of bone cells needed for bone fusion. The application of bone growth material is described further in relation to FIG. 4 .
  • the tabs of the device 100 have sharp ridges or threads which bite into the adjacent vertebrae, further helping to brace the device between the vertebrae.
  • the body and the tabs 131 - 136 of the bone fusion device 100 employs different numbers and/or configurations of tabs in different embodiments.
  • the tabs 131 - 136 depicted in FIG. 1 are merely exemplary.
  • the tabs 131 - 136 are located anywhere over the exterior surface of the bone fusion device 100 , in a variety of orientations.
  • the tabs 131 - 136 are preferably arranged such that when they are extended, the tabs 131 - 136 act to stabilize the bone fusion device 100 against the vertebrae from several points and directions. Typically, the tighter the bone fusion device 100 is wedged between the adjacent vertebrae by the tabs 131 - 136 , the more stability the device 100 provides to the vertebrae and the spine of the patient.
  • the tabs 131 - 136 of the embodiments described above are critical to insure that the device 100 is not dislodged, since movement of the device 100 could cause serious injury to the patient, and especially because the inserted device is situated near the patient's spinal cord.
  • FIG. 2 shows an alternative embodiment of the bone fusion device 200 .
  • the bone fusion device 200 of some embodiments has a rectangular shape. Similar to the round cylindrical shaped bone fusion device 100 shown in FIG. 1 , the rectangular bone fusion device 200 has two end faces, including the end face 245 visible in FIG. 2 , and multiple tabs 211 , 212 , 213 , 214 , 215 , 216 , 217 , and 218 that are attached by rotating means to the exterior surface.
  • the rotating means are screw type assemblies in some embodiments.
  • the tabs 211 - 218 are also selectively extended after insertion of the bone fusion device 200 between the vertebrae.
  • the insertion of the bone fusion device 200 and the extension of the selected tabs 211 - 218 are typically performed by a surgeon during an arthroscopic surgical procedure.
  • the procedure of some embodiments is further described in relation to FIG. 8 .
  • the rotation of a respective rotating means associated with each tab 211 - 218 individually adjusts the position of the associated tab 211 - 218 such that the device 200 is firmly braced between the two adjacent vertebrae.
  • the tabs 211 - 218 are distributed over the exterior surfaces of the bone fusion device 200 in a variety of configurations, which include the ends and the surfaces of the device 200 that are not readily visible in FIG. 2 .
  • different numbers of tabs 211 - 218 are distributed over each surface of the bone fusion device 200 of different embodiments.
  • the surfaces of the bone fusion device 200 and/or the tabs 211 - 218 are coated with a porous surface texturing which promotes bone growth.
  • the end face 245 has an opening 240 , which provides access to a cavity within the interior of the bone fusion device 200 .
  • bone graft materials such as the bone chips and/or the synthetic bone matrix that were mentioned above, are pre-loaded into the cavity within the bone fusion device 200 through the opening 240 .
  • conduits or holes 250 in the bone fusion device 200 permit the bone graft material to flow from the interior cavity to the exterior surfaces of the device 200 that are in contact with the vertebral bone.
  • the bone graft material is relocated from the interior cavity to the exterior of the bone fusion device 200 , after the device 200 has been positioned between the vertebrae.
  • FIG. 3A illustrates a section of a vertebral column that has a bone fusion device 300 positioned between two vertebrae 330 and 335 .
  • the bone fusion device 300 is positioned in a location where an intervertebral disc would normally reside.
  • a flexible disc is typically sandwiched between the two vertebrae of a normal healthy spinal column.
  • the normal, healthy disc 340 is sandwiched between the vertebrae 337 and 330 .
  • the intervertebral disc that normally resides between the vertebrae 330 and 335 has been excised and surgical insertion of the bone fusion device 300 has replaced the disc as the supporting structure between the vertebrae 330 and 335 .
  • FIG. 3A further illustrates that the damaged disc that is normally sandwiched between vertebrae 330 and 335 has been totally removed.
  • complete removal of the disc is not necessary in order to use the bone fusion device 300 of some embodiments.
  • a sufficient amount of the disc is typically removed that allows access to the rotating means 311 , 312 , 313 , and 314 , which control the extension of the tabs 321 , 322 , 323 , and 324 , of the bone fusion device 300 .
  • additional numbers and configurations of the tabs are distributed over the exterior surfaces of the bone fusion device 300 , including the surfaces that are not visible in FIG. 3A .
  • the tabs 321 - 324 are deposed in a position aligned along the body of the bone fusion device 300 , such that the tabs 321 - 324 lie substantially within the exterior surfaces of the device 300 .
  • the tabs 321 - 324 are flush with the exterior surface.
  • the form factor of the bone fusion device 300 is configured to be as compact as possible.
  • the form factor of some embodiments has a diameter of approximately 0.28 inches and a length of approximately 1.0 inch.
  • the form factor of these same embodiments has a diameter of approximately 0.48 inches when the tabs 321 - 324 are fully extended.
  • the cross-section of the bone fusion device 300 has different shapes in various embodiments.
  • a more circular bone fusion device such as the device 100 illustrated in FIG. 1 , or a device having another shape is employed in conjunction with a set of extendable tabs that are located in various configurations in additional embodiments of the invention.
  • some embodiments have four rows of tabs, where each row is positioned on a side of the bone fusion device. In some of these embodiments, each row preferably has four tabs.
  • FIG. 3B a first set of four tabs 311 - 314 lock the bone fusion device 300 against the vertebra 330
  • a second set of tabs 315 - 318 lock the bone fusion device 300 against the vertebra 335 .
  • FIG. 4A illustrates the bone fusion device 400 of some embodiments in further detail.
  • the bone fusion device 400 includes an interior cavity 405 for the insertion of a lead screw 415 , and one or more tabs 431 each deposed in a tab bay 421 , 422 , 423 , 424 .
  • the tab bays 421 - 424 allow the tabs 431 to lie flush and/or within the exterior surface 420 of the bone fusion device 400 when not extended. Also when not extended, the tab 431 and tab bay 421 provides a conduit 450 from the interior cavity 405 to the exterior surface 420 of the bone fusion device 400 , such that the bone graft and/or growth material within the interior cavity 405 has a directed path to the exterior surface 420 . Typically, the insertion of the lead screw 415 forces the material within the interior cavity 405 to relocate to the exterior surface 420 .
  • the tab 431 includes a rotating means 411 and gear teeth 455 .
  • the gear teeth 455 provide a series of passive grooves by which the lead screw 415 traverses the interior cavity 405 .
  • the tab 431 remains fixed as the lead screw 415 is screwed into the interior cavity 405 .
  • the threading of the lead screw 415 does not address or affect the gear teeth 455 during the insertion of the lead screw 415 .
  • the rotating means 411 is turned to raise the tab 431 .
  • the rotating means 411 for the tab 431 typically comprises a turn screw type mechanism such that when the rotating means 411 is turned, the gear teeth 455 drive or rotate against the stationary threads of the inserted lead screw 415 . Similarly, due to the angle of the stationary lead screw's spiral threads, the gear teeth 455 cause the tab 431 to elevate and extend above the exterior surface 420 of the bone fusion device 400 .
  • the tabs 431 of some embodiments have a range of motion that exceeds 90 degrees with respect to the exterior surface 420 of the bone fusion device 400 . Accordingly, FIG. 4B illustrates the tab 431 extended slightly past 90 degrees, which is the optimum position to withstand the compressive force exerted on the vertebrae of some embodiments.
  • FIG. 5A illustrates a closed view of the small form factor for a bone fusion device 500 in accordance with some embodiments.
  • the bone fusion device 500 has a tab 531 that is not extended and lies within the exterior surface of the device 500 .
  • FIG. 5B illustrates the form factor for the bone fusion device 500 with the tab 531 extended, as described above.
  • FIG. 6A illustrates a cross section view of the bone fusion device 600 having a small form factor, while FIG. 6B illustrates the cross section view with the tab 631 extended.
  • FIG. 7A is a perspective drawing illustrating the bone fusion device 700 with four tab bays on four opposite sides of the device 700 , according to some embodiments of the invention.
  • a tab is deposed in each tab bay and secured by a rotating means.
  • the tab 731 is deposed in the tab bay 721 and secured by the rotating means 711 .
  • a lead screw 715 is preferably driven into the cavity.
  • the lead screw 715 provides the thread by which the gear teeth 755 elevate the tabs 731 - 733 .
  • FIG. 7B illustrates the bone fusion device 700 with the tabs 731 - 733 elevated.
  • FIG. 8 is a process flow diagram that summarizes the insertion and use of the bone fusion device according to some embodiments.
  • the process 800 begins at the step 805 where a small, minimally invasive surgical incision is performed.
  • the small incision is typically only large enough to permit entry of an arthroscopic surgical tool.
  • the process 800 transitions to the step 810 , where the bone fusion device is inserted through the small incision and delivered to a region between two vertebrae that are to be fused together. Insertion and delivery of the bone fusion device are preferably performed by using arthroscopic tool(s).
  • the bone fusion device is positioned in the region where bone fusion is to occur, also typically by using one or more arthroscopic tool(s).
  • the process 800 transitions to the step 820 , where the lead screw is inserted and driven into the bone fusion device.
  • the lead screw is typically driven into a cavity in the center of the bone fusion device.
  • the cavity contains a bone growth material comprising collagen and/or a matrix for the promotion of bone growth. Accordingly, insertion of the lead screw into the cavity causes the bone growth material to be relocated from the interior cavity to the exterior surface of the bone growth device.
  • the bone fusion device of some embodiments has a particular pattern of conduits or pores that extend from the interior cavity to the exterior surface for facilitating the relocation of bone growth material to particular locations at the exterior of the device. For instance, some embodiments have pores that facilitate the relocation of bone growth material to particular tabs.
  • the tabs are selectively extended to lock the bone fusion device in place in the region between the two vertebrae.
  • the tabs of some embodiments are extended by using the worm screw drive mechanism described above in relation to FIG. 4 .
  • the small incision and minimally invasive (arthroscopic) surgical procedure advantageously promote health and rapid recovery by the patient.
  • bone growth occurs around the bone fusion device and particularly at the locations of the extended tabs, such that the bone fusion device is further secured by the bone growth, which further promotes a superior, robust bone fusion result.

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  • Health & Medical Sciences (AREA)
  • Engineering & Computer Science (AREA)
  • Biomedical Technology (AREA)
  • Neurology (AREA)
  • Orthopedic Medicine & Surgery (AREA)
  • Cardiology (AREA)
  • Oral & Maxillofacial Surgery (AREA)
  • Transplantation (AREA)
  • Heart & Thoracic Surgery (AREA)
  • Vascular Medicine (AREA)
  • Life Sciences & Earth Sciences (AREA)
  • Animal Behavior & Ethology (AREA)
  • General Health & Medical Sciences (AREA)
  • Public Health (AREA)
  • Veterinary Medicine (AREA)
  • Prostheses (AREA)
  • Surgical Instruments (AREA)
US11/264,958 2004-11-03 2005-11-01 Bone fusion device Abandoned US20060095136A1 (en)

Priority Applications (11)

Application Number Priority Date Filing Date Title
US11/264,958 US20060095136A1 (en) 2004-11-03 2005-11-01 Bone fusion device
PCT/US2005/039984 WO2006050500A2 (fr) 2004-11-03 2005-11-02 Dispositif pour la fusion des os
US11/357,319 US7727280B2 (en) 2004-11-03 2006-02-16 Bone fusion device
US11/484,379 US8187332B2 (en) 2004-11-03 2006-07-10 Bone fusion device
US13/482,778 US8597360B2 (en) 2004-11-03 2012-05-29 Bone fusion device
PCT/US2013/042066 WO2013181024A1 (fr) 2004-11-03 2013-05-21 Dispositif de fusion osseuse
US14/067,813 US9186262B2 (en) 2004-11-03 2013-10-30 Bone fusion device
US14/885,777 US9974665B2 (en) 2004-11-03 2015-10-16 Bone fusion device
US15/954,414 US10682240B2 (en) 2004-11-03 2018-04-16 Bone fusion device
US16/798,098 US11583414B2 (en) 2004-11-03 2020-02-21 Bone fusion device
US18/111,561 US12491087B2 (en) 2023-02-18 Bone fusion device

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US11/264,958 US20060095136A1 (en) 2004-11-03 2005-11-01 Bone fusion device

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US11/484,379 Active 2027-05-26 US8187332B2 (en) 2004-11-03 2006-07-10 Bone fusion device

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US20060142859A1 (en) 2006-06-29
US7727280B2 (en) 2010-06-01
US20060253201A1 (en) 2006-11-09
US8187332B2 (en) 2012-05-29
WO2006050500A3 (fr) 2006-09-28

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