US20140031823A1 - Bone fixation device, tools and methods - Google Patents
Bone fixation device, tools and methods Download PDFInfo
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- US20140031823A1 US20140031823A1 US14/020,685 US201314020685A US2014031823A1 US 20140031823 A1 US20140031823 A1 US 20140031823A1 US 201314020685 A US201314020685 A US 201314020685A US 2014031823 A1 US2014031823 A1 US 2014031823A1
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- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
- A61B17/00—Surgical instruments, devices or methods, e.g. tourniquets
- A61B17/56—Surgical instruments or methods for treatment of bones or joints; Devices specially adapted therefor
- A61B17/58—Surgical instruments or methods for treatment of bones or joints; Devices specially adapted therefor for osteosynthesis, e.g. bone plates, screws, setting implements or the like
- A61B17/68—Internal fixation devices, including fasteners and spinal fixators, even if a part thereof projects from the skin
- A61B17/72—Intramedullary pins, nails or other devices
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
- A61B17/00—Surgical instruments, devices or methods, e.g. tourniquets
- A61B17/56—Surgical instruments or methods for treatment of bones or joints; Devices specially adapted therefor
- A61B17/58—Surgical instruments or methods for treatment of bones or joints; Devices specially adapted therefor for osteosynthesis, e.g. bone plates, screws, setting implements or the like
- A61B17/68—Internal fixation devices, including fasteners and spinal fixators, even if a part thereof projects from the skin
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
- A61B17/00—Surgical instruments, devices or methods, e.g. tourniquets
- A61B17/56—Surgical instruments or methods for treatment of bones or joints; Devices specially adapted therefor
- A61B17/58—Surgical instruments or methods for treatment of bones or joints; Devices specially adapted therefor for osteosynthesis, e.g. bone plates, screws, setting implements or the like
- A61B17/68—Internal fixation devices, including fasteners and spinal fixators, even if a part thereof projects from the skin
- A61B17/72—Intramedullary pins, nails or other devices
- A61B17/7208—Flexible pins, e.g. ENDER pins
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
- A61B17/00—Surgical instruments, devices or methods, e.g. tourniquets
- A61B17/56—Surgical instruments or methods for treatment of bones or joints; Devices specially adapted therefor
- A61B17/58—Surgical instruments or methods for treatment of bones or joints; Devices specially adapted therefor for osteosynthesis, e.g. bone plates, screws, setting implements or the like
- A61B17/68—Internal fixation devices, including fasteners and spinal fixators, even if a part thereof projects from the skin
- A61B17/72—Intramedullary pins, nails or other devices
- A61B17/7233—Intramedullary pins, nails or other devices with special means of locking the nail to the bone
- A61B17/7258—Intramedullary pins, nails or other devices with special means of locking the nail to the bone with laterally expanding parts, e.g. for gripping the bone
- A61B17/7266—Intramedullary pins, nails or other devices with special means of locking the nail to the bone with laterally expanding parts, e.g. for gripping the bone with fingers moving radially outwardly
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
- A61B17/00—Surgical instruments, devices or methods, e.g. tourniquets
- A61B17/16—Bone cutting, breaking or removal means other than saws, e.g. Osteoclasts; Drills or chisels for bones; Trepans
- A61B17/17—Guides or aligning means for drills, mills, pins or wires
- A61B17/1725—Guides or aligning means for drills, mills, pins or wires for applying transverse screws or pins through intramedullary nails or pins
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
- A61B17/00—Surgical instruments, devices or methods, e.g. tourniquets
- A61B17/56—Surgical instruments or methods for treatment of bones or joints; Devices specially adapted therefor
- A61B17/58—Surgical instruments or methods for treatment of bones or joints; Devices specially adapted therefor for osteosynthesis, e.g. bone plates, screws, setting implements or the like
- A61B17/68—Internal fixation devices, including fasteners and spinal fixators, even if a part thereof projects from the skin
- A61B17/72—Intramedullary pins, nails or other devices
- A61B17/7216—Intramedullary pins, nails or other devices for bone lengthening or compression
- A61B17/7225—Intramedullary pins, nails or other devices for bone lengthening or compression for bone compression
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
- A61B17/00—Surgical instruments, devices or methods, e.g. tourniquets
- A61B17/56—Surgical instruments or methods for treatment of bones or joints; Devices specially adapted therefor
- A61B17/58—Surgical instruments or methods for treatment of bones or joints; Devices specially adapted therefor for osteosynthesis, e.g. bone plates, screws, setting implements or the like
- A61B17/68—Internal fixation devices, including fasteners and spinal fixators, even if a part thereof projects from the skin
- A61B17/72—Intramedullary pins, nails or other devices
- A61B17/7291—Intramedullary pins, nails or other devices for small bones, e.g. in the foot, ankle, hand or wrist
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
- A61B17/00—Surgical instruments, devices or methods, e.g. tourniquets
- A61B17/56—Surgical instruments or methods for treatment of bones or joints; Devices specially adapted therefor
- A61B17/58—Surgical instruments or methods for treatment of bones or joints; Devices specially adapted therefor for osteosynthesis, e.g. bone plates, screws, setting implements or the like
- A61B17/68—Internal fixation devices, including fasteners and spinal fixators, even if a part thereof projects from the skin
- A61B17/84—Fasteners therefor or fasteners being internal fixation devices
- A61B17/86—Pins or screws or threaded wires; nuts therefor
Definitions
- the present invention relates to devices, tools and methods for providing reinforcement of bones. More specifically, the present invention relates to devices, tools and methods for providing reconstruction and reinforcement of bones, including diseased, osteoporotic and fractured bones.
- Bone fractures are a common medical condition both in the young and old segments of the population.
- osteoporosis has become more of a significant medical concern in part due to the risk of osteoporotic fractures.
- Osteoporosis and osteoarthritis are among the most common conditions to affect the musculoskeletal system, as well as frequent causes of locomotor pain and disability. Osteoporosis can occur in both human and animal subjects (e.g. horses).
- Osteoporosis (OP) and osteoarthritis (OA) occur in a substantial portion of the human population over the age of fifty.
- One current treatment of bone fractures includes surgically resetting the fractured bone.
- the fractured area of the body i.e., where the fractured bone is located
- an external cast for an extended period of time to ensure that the fractured bone heals properly. This can take several months for the bone to heal and for the patient to remove the cast before resuming normal activities.
- an intramedullary (IM) rod or nail is used to align and stabilize the fracture.
- IM intramedullary
- a metal rod is placed inside a canal of a bone and fixed in place, typically at both ends. See, for example, FixionTM IM (Nail), www.disc-o-tech.com. This approach requires incision, access to the canal, and placement of the IM nail.
- the nail can be subsequently removed or left in place.
- a conventional IM nail procedure requires a similar, but possibly larger, opening to the space, a long metallic nail being placed across the fracture, and either subsequent removal, and or when the nail is not removed, a long term implant of the IM nail.
- the outer diameter of the IM nail must be selected for the minimum inside diameter of the space. Therefore, portions of the IM nail may not be in contact with the canal. Further, micro-motion between the bone and the IM nail may cause pain or necrosis of the bone. In still other cases, infection can occur.
- the IM nail may be removed after the fracture has healed. This requires a subsequent surgery with all of the complications and risks of a later intrusive procedure. In general, rigid IM rods or nails are difficult to insert, can damage the bone and require additional incisions for cross-screws to attach the rods or nails to the bone.
- IM nails are inflatable. See, for example, Meta-Fix IM Nailing System, www.disc-o-tech.com. Such IM nails require inflating the rod with very high pressures, endangering the surrounding bone. Inflatable nails have many of the same drawbacks as the rigid IM nails described above.
- External fixation is another technique employed to repair fractures.
- a rod may traverse the fracture site outside of the epidermis.
- the rod is attached to the bone with trans-dermal screws.
- the external fixation is cosmetically intrusive, bulky, and prone to painful inadvertent manipulation by environmental conditions such as, for example, bumping into objects and laying on the device.
- Other concepts relating to bone repair are disclosed in, for example, U.S. Pat. No. 5,108,404 to Scholten for Surgical Protocol for Fixation of Bone Using Inflatable Device; U.S. Pat. No. 4,453,539 to Raftopoulos et al.
- Other fracture fixation devices, and tools for deploying fracture fixation devices have been described in: US Patent Appl. Publ. No. 2006/0254950; U.S. Ser. No. 60/867,011 (filed Nov. 22, 2006); U.S. Ser. No. 60/866,976 (filed Nov. 22, 2006); and U.S. Ser. No. 60/866,920 (filed Nov. 22, 2006).
- the bone fixation device may include an elongate body with a longitudinal axis and having a flexible state and a rigid state.
- the device further may include a plurality of grippers disposed at longitudinally-spaced locations along the elongated body, a rigid hub connected to the elongated body, and an actuator that is operably-connected to the grippers to deploy the grippers from a first shape to an expanded second shape.
- a bone fixation device is provided with an elongate body having a longitudinal axis and having a first state in which at least a portion of the body is flexible and a second state in which the body is generally rigid, an actuateable gripper disposed at a distal location on the elongated body, a hub located on a proximal end of the elongated body, and an actuator operably connected to the gripper to deploy the gripper from a retracted configuration to an expanded configuration.
- One such method comprises inserting a bone fixation device into an intramedullary space of the bone to place at least a portion of an elongate body of the fixation device in a flexible state on one side of the fracture and at least a portion of a hub on another side of the fracture, and operating an actuator to deploy at least one gripper of the fixation device to engage an inner surface of the intramedullary space to anchor the fixation device to the bone.
- One embodiment of the present invention provides a low weight to volume mechanical support for fixation, reinforcement and reconstruction of bone or other regions of the musculo-skeletal system in both humans and animals.
- the method of delivery of the device is another aspect of the invention.
- the method of delivery of the device in accordance with the various embodiments of the invention reduces the trauma created during surgery, decreasing the risks associated with infection and thereby decreasing the recuperation time of the patient.
- the framework may in one embodiment include an expandable and contractible structure to penult re-placement and removal of the reinforcement structure or framework.
- the mechanical supporting framework or device may be made from a variety of materials such as metal, composite, plastic or amorphous materials, which include, but are not limited to, steel, stainless steel, cobalt chromium plated steel, titanium, nickel titanium alloy (nitinol), superelastic alloy, and polymethylmethacrylate (PMMA).
- the device may also include other polymeric materials that are biocompatible and provide mechanical strength, that include polymeric material with ability to carry and delivery therapeutic agents, that include bioabsorbable properties, as well as composite materials and composite materials of titanium and polyetheretherketone (PEEKTM), composite materials of polymers and minerals, composite materials of polymers and glass fibers, composite materials of metal, polymer, and minerals.
- PEEKTM polyetheretherketone
- each of the aforementioned types of device may further be coated with proteins from synthetic or animal source, or include collagen coated structures, and radioactive or brachytherapy materials.
- the construction of the supporting framework or device may include radio-opaque markers or components that assist in their location during and after placement in the bone or other region of the musculo-skeletal systems.
- the reinforcement device may, in one embodiment, be osteo incorporating, such that the reinforcement device may be integrated into the bone.
- a method of repairing a bone fracture comprises: accessing a fracture along a length of a bone through a bony protuberance at an access point at an end of a bone; advancing a bone fixation device into a space through the access point at the end of the bone; bending a portion of the bone fixation device along its length to traverse the fracture; and locking the bone fixation device into place within the space of the bone.
- the method can also include the step of advancing an obturator through the bony protuberance and across the fracture prior to advancing the bone fixation device into the space.
- the step of anchoring the bone fixation device within the space can be included.
- An aspect of the invention discloses a removable bone fixation device that uses a single port of insertion and has a single-end of remote actuation wherein a bone fixation device stabilizes bone after it has traversed the fracture.
- the bone fixation device is adapted to provide a single end in one area or location where the device initiates interaction with bone.
- the device can be deployed such that the device interacts with bone.
- Single portal insertion and single-end remote actuation enables the surgeon to insert and deploy the device, deactivate and remove the device, reduce bone fractures, displace or compress the bone, and lock the device in place.
- the single-end actuation enables the device to grip bone, compresses the rigidizable flexible body, permits axial, torsional and angular adjustments to its position during surgery, and releases the device from the bone during its removal procedure.
- a removable extractor can be provided in some embodiments of the device to enable the device to be placed and extracted by deployment and remote actuation from a single end.
- the device of the invention can be adapted and configured to provide at least one rigidizable flexible body or sleeve. Further the body can be configured to be flexible in all angles and directions. The flexibility provided is in selective planes and angles in the Cartesian, polar, or cylindrical coordinate systems. Further, in some embodiments, the body is configured to have a remote actuation at a single end.
- the body can be configured to have apertures, windings, etc.
- the device may be configured to function with non-flexible bodies for use in bones that have a substantially straight segment or curved segments with a constant radius of curvature.
- Another aspect of the invention includes a bone fixation device in that has mechanical geometry that interacts with bone by a change in the size of at least one dimension of a Cartesian, polar, or spherical coordinate system.
- bioabsorbable materials can be used in conjunction with the devices, for example by providing specific subcomponents of the device configured from bioabsorbable materials.
- a sleeve can be provided in some embodiments where the sleeve is removable, has deployment, remote actuation, and a single end.
- the sleeve can be adapted to provide a deployable interdigitation process or to provide an aperture along its length through which the deployable interdigitation process is adapted to engage bone.
- the deployable interdigitation process is further adapted to engage bone when actuated by the sleeve.
- the bone fixation device further comprises a cantilever adapted to retain the deployable bone fixation device within the space.
- the sleeve can further be adapted to be expanded and collapsed within the space by a user.
- One end of the device can be configured to provide a blunt obturator surface adapted to advance into the bone.
- a guiding tip may also be provided that facilitates guiding the device through the bone.
- the deployable bone fixation device can be adapted to receive external stimulation to provide therapy to the bone.
- the device can further be adapted to provide an integral stimulator which provides therapy to the bone.
- the device can be adapted to receive deliver therapeutic stimulation to the bone.
- the devices disclosed herein may be employed in various regions of the body, including: cranial, thoracic, lower extremities and upper extremities. Additionally, the devices are suitable for a variety of breaks including, metaphyseal and diaphyseal.
- the fracture fixation devices of various embodiments of the invention are adapted to be inserted through an opening of a fractured bone, such as the radius (e.g., through a bony protuberance on a distal or proximal end or through the midshaft) into the intramedullary canal of the bone.
- the fixation device has two main components, one configured component for being disposed on the side of the fracture closest to the opening and one component configured for being disposed on the other side of the fracture from the opening so that the fixation device traverses the fracture.
- the device components cooperate to align, fix and/or reduce the fracture so as to promote healing.
- the device may be removed from the bone after insertion (e.g., after the fracture has healed or for other reasons), or it may be left in the bone for an extended period of time or permanently.
- the fracture fixation device has one or more actuatable anchors or grippers on its proximal and/or distal ends. These anchors may be used to hold the fixation device to the bone while the bone heals.
- At least one component of the fracture fixation device has a substantially flexible state and a substantially rigid state. Once in place, deployment of the device also causes the components to change from the flexible state to a rigid state to aid in proper fixation of the fracture. At least one of the components may be substantially rigid or semi-flexible. At least one component may provide a bone screw attachment site for the fixation device.
- Embodiments of the invention also provide deployment tools with a tool guide for precise alignment of one or more bone screws with the fracture fixation device. These embodiments also provide bone screw orientation flexibility so that the clinician can select an orientation for the bone screw(s) that will engage the fixation device as well as any desired bone fragments or other bone or tissue locations.
- FIG. 1 is a perspective view of an embodiment of a bone fixation device implanted in a bone according to the invention.
- FIG. 2 is another perspective view of the implanted device of FIG. 1 .
- FIG. 3 is a longitudinal cross-section view of the bone fixation device of FIG. 1 in a non-deployed state.
- FIG. 4 is a plan view of a combination deployment tool that may be used with the bone fixation device of FIG. 1 .
- FIG. 5 is a cross-section view of the tool and device shown in FIG. 4 .
- FIG. 6 is a perspective view of the tool and device shown in FIG. 4 .
- FIG. 7 is a cross-section view of the implanted device of FIG. 1 .
- FIG. 8 is a perspective view of an alternative embodiment of the implanted device of FIG. 1 .
- FIG. 9 is a perspective view of another alternative embodiment of the implanted device of FIG. 1 .
- FIG. 10A is a perspective view of another embodiment of a bone fixation device shown deployed in a fractured clavicle.
- FIG. 10B is perspective view of the device shown in FIG. 10A shown in a deployed state.
- FIG. 10C is a side elevation view of the device shown in FIG. 10A shown in a retracted or undeployed state.
- FIG. 10D is a side elevation view of the device shown in FIG. 10A shown in a deployed state.
- FIG. 10E is a cross-sectional view of the device shown in FIG. 10A shown in a retracted or undeployed state.
- FIG. 10F is a cross-sectional view of the device shown in FIG. 10A shown in a deployed state.
- FIG. 10G is a perspective view of a gripper of the device shown in FIG. 10A shown in a retracted or undeployed state.
- FIG. 10H is a side elevation view of a gripper and actuator of the device shown in FIG. 10A shown in a retracted or undeployed state.
- FIG. 10I is a perspective view of a gripper and actuator of the device shown in FIG. 10A shown in a deployed state.
- FIG. 11A is perspective view of another embodiment of a bone fixation device shown in a retracted or undeployed state.
- FIG. 11B is perspective view of the device shown in FIG. 11A shown in a deployed state.
- FIG. 11C is a cross-sectional view of the device shown in FIG. 11A shown in a retracted or undeployed state.
- FIG. 11D is a cross-sectional view of the device shown in FIG. 11A shown in a deployed state.
- FIG. 12A shows an isometric side view of an exemplary embodiment of a bone fixation device hub.
- FIG. 12B shows a side view of the bone fixation device of FIG. 12A .
- FIG. 12C shows a front view of the bone fixation device of FIG. 12A .
- FIG. 12D shows back view of the bone fixation device of FIG. 12A .
- FIG. 12E shows an isometric front view of the bone fixation device of FIG. 12A .
- FIG. 12F shows a plan view of a surface on the bone fixation device of FIG. 12A .
- FIG. 12G shows an isometric side view of the bone fixation device of FIG. 12A implanted in a bone.
- FIG. 12H shows an isometric elevated view of the bone fixation device of FIG. 12A implanted in a bone.
- FIG. 12I shows an isometric view of the bone fixation device of FIG. 12A implanted in a bone.
- FIG. 13A shows an isometric side view of an another exemplary embodiment of a bone fixation device hub.
- FIG. 13B shows a side view of the bone fixation device of FIG. 13A .
- FIG. 13C shows a front view of the bone fixation device of FIG. 13A .
- FIG. 13D shows a back view of the bone fixation device of FIG. 13A .
- FIG. 13E shows an isometric view of the bone fixation device of FIG. 13A .
- FIG. 14A shows an isometric side view of another exemplary embodiment of a bone fixation device hub.
- FIG. 14B shows a side view of the bone fixation device of FIG. 14A .
- FIG. 14C shows a front view of the bone fixation device of FIG. 14A .
- FIG. 14D shows a back side view of the bone fixation device of FIG. 14A .
- FIG. 14E shows an isometric side view of the bone fixation device of FIG. 14A .
- FIG. 14F shows a close up view of a optional portion of the bone fixation device of FIG. 14A .
- FIG. 15A shows an isometric side view of another exemplary embodiment of a bone fixation device hub.
- FIG. 15B shows a side view of the bone fixation device of FIG. 15A .
- FIG. 15C shows a front view of the bone fixation device of FIG. 15A .
- FIG. 15D shows a back view of the bone fixation device of FIG. 15A .
- FIG. 16A shows an isometric side view of another exemplary embodiment of a bone fixation device hub.
- FIG. 16B shows an isometric front view of the bone fixation device of FIG. 16A .
- FIG. 16C shows an isometric top view of the bone fixation device of FIG. 16A .
- FIG. 16D shows a front view of the bone fixation device of FIG. 16A .
- FIG. 16E shows an optional screw for use with the bone fixation device of FIG. 16A .
- FIG. 17A shows an isometric side view of another exemplary embodiment of a bone fixation device hub.
- FIG. 17B shows a side view of the bone fixation device of FIG. 17A .
- FIG. 17C shows a close up side view of the bone fixation device of FIG. 17A .
- FIG. 18A shows an isometric side view of another exemplary embodiment of a bone fixation device hub.
- FIG. 18B shows a side view of the bone fixation device of FIG. 18A .
- FIG. 19A shows an isometric side view of another exemplary embodiment of a bone fixation device hub.
- FIG. 19B shows a side view of the bone fixation device hub of FIG. 19A .
- FIG. 20A shows an isometric side view of another exemplary embodiment of a bone fixation device hub.
- FIG. 20B shows an exploded side view of the bone fixation device of FIG. 20A .
- bone is often described as a specialized connective tissue that serves three major functions anatomically.
- bone provides a mechanical function by providing structure and muscular attachment for movement.
- bone provides a metabolic function by providing a reserve for calcium and phosphate.
- bone provides a protective function by enclosing bone marrow and vital organs.
- Bones can be categorized as long bones (e.g. radius, femur, tibia and humerus) and flat bones (e.g. skull, scapula and mandible). Each bone type has a different embryological template. Further each bone type contains cortical and trabecular bone in varying proportions.
- the devices of this invention can be adapted for use in any of the bones of the body as will be appreciated by those skilled in the art.
- Cortical bone forms the shaft, or diaphysis, of long bones and the outer shell of flat bones.
- the cortical bone provides the main mechanical and protective function.
- the trabecular bone (cancellous) is found at the end of the long bones, or the epiphysis, and inside the cortex of flat bones.
- the trabecular bone consists of a network of interconnecting trabecular plates and rods and is the major site of bone remodeling and resorption for mineral homeostasis. During development, the zone of growth between the epiphysis and diaphysis is the metaphysis.
- woven bone which lacks the organized structure of cortical or cancellous bone, is the first bone laid down during fracture repair.
- the bone segments are positioned in proximity to each other in a manner that enables woven bone to be laid down on the surface of the fracture.
- This description of anatomy and physiology is provided in order to facilitate an understanding of the invention. Persons of skill in the art will also appreciate that the scope and nature of the invention is not limited by the anatomy discussion provided. Further, it will be appreciated there can be variations in anatomical characteristics of an individual patient, as a result of a variety of factors, which are not described herein. Further, it will be appreciated there can be variations in anatomical characteristics between bones which are not described herein.
- FIGS. 1 and 2 are perspective views of an embodiment of a bone fixation device 100 having a proximal end 102 (nearest the surgeon) and a distal end 104 (further from surgeon) and positioned within the bone space of a patient according to the invention.
- device 100 is shown implanted in the upper (or proximal) end of an ulna 106 .
- the proximal end and distal end refers to the position of an end of the device relative to the remainder of the device or the opposing end as it appears in the drawing.
- the proximal end can be used to refer to the end manipulated by the user or physician.
- the distal end can be used to refer to the end of the device that is inserted and advanced within the bone and is furthest away from the physician.
- proximal and distal could change in another context, e.g. the anatomical context in which proximal and distal use the patient as reference, or where the entry point is distal from the surgeon.
- the device When implanted within a patient, the device can be held in place with suitable fasteners such as wire, screws, nails, bolts, nuts and/or washers.
- the device 100 is used for fixation of fractures of the proximal or distal end of long bones such as intracapsular, intertrochanteric, intercervical, supracondular, or condular fractures of the femur; for fusion of a joint; or for surgical procedures that involve cutting a bone.
- the devices 100 may be implanted or attached through the skin so that a pulling force (traction may be applied to the skeletal system).
- the design of the metaphyseal fixation device 100 depicted is adapted to provide a bone engaging mechanism or gripper 108 adapted to engage target bone of a patient from the inside of the bone.
- the device is designed to facilitate bone healing when placed in the intramedullary space within a post fractured bone.
- This device 100 has a gripper 108 positioned distally and shown deployed radially outward against the wall of the intramedullary cavity. On entry into the cavity, gripper 108 is flat and retracted ( FIG. 3 ). Upon deployment, gripper 108 pivots radially outward and grips the diaphyseal bone from the inside of the bone.
- a flexible-to-rigid body portion 114 may also be provided, and in this embodiment is positioned between gripper 108 and hub 112 . It may be provided with wavy spiral cuts 116 for that purpose, as will be described in more detail below.
- FIG. 3 shows a longitudinal cross-section of device 100 in a non-deployed configuration.
- gripper 108 includes two pairs of opposing bendable gripping members 118 . Two of the bendable gripping members 118 are shown in FIG. 3 , while the other two (not shown in FIG. 3 ) are located at the same axial location but offset by 90 degrees. Each bendable gripping member 118 has a thinned portion 120 that permits bending as the opposite distal end 122 of member 118 is urged radially outward, such that member 118 pivots about thinned portion 120 . When extended, distal ends 122 of bendable members 118 contact the inside of the bone to anchor the distal portion of device 100 to the bone.
- the gripper may comprise 1, 2, 3, 4, 5, 6 or more bendable members similar to members 118 shown.
- bendable members 118 of gripper 108 are urged radially outward by a ramped surface on actuator head 124 .
- Actuator head 124 is formed on the distal end of actuator 126 .
- the proximal end of actuator 126 is threaded to engage a threaded bore of drive member 128 .
- the proximal end of drive member 128 is provided with a keyed socket 130 for receiving the tip of a rotary driver tool 132 (shown in FIG. 5 ) through the proximal bore of device 100 .
- rotary driver tool 132 turns drive member 128
- actuator 126 is drawn in a proximal direction to outwardly actuate gripper members 118 .
- a hemispherical tip cover 134 may be provided at the distal end of the device as shown to act as a blunt obturator. This arrangement facilitates penetration of bone (e.g. an intramedullary space) by device 100 while keeping the tip of device 100 from digging into bone during insertion.
- bone e.g. an intramedullary space
- device 100 may include one or more flexible-to-rigid body portions 114 .
- This feature is flexible upon entry into bone and rigid upon application of compressive axial force provided by tensioning actuator 126 .
- Various embodiments of a flexible-to-rigid portion may be used, including dual helical springs whose inner and outer tubular components coil in opposite directions, a chain of ball bearings with flats or roughened surfaces, a chain of cylinders with flats, features, cones, spherical or pointed interdigitating surfaces, wavy-helical cut tubes, two helical cut tubes in opposite directions, linear wires with interdigitating coils, and bellows-like structures.
- the design of the flexible-to-rigid tubular body portion 114 allows a single-piece design to maximize the transformation of the same body from a very flexible member that minimizes strength in bending to a rigid body that maximizes strength in bending and torsion.
- the flexible member transforms to a rigid member when compressive forces are applied in the axial direction at each end, such as by an actuator similar to 126 .
- the body portion 114 is made, for example, by a near-helical cut 116 on a tubular member at an angle of incidence to the axis somewhere between 0 and 180 degrees from the longitudinal axis of the tubular body portion 114 .
- the near-helical cut or wavy-helical cut may be formed by the superposition of a helical curve added to a cyclic curve that produces waves of frequencies equal or greater than zero per turn around the circumference and with cyclic amplitude greater than zero.
- the waves of one segment nest with those on either side of it, thus increasing the torque, bending strength and stiffness of the tubular body when subjective to compressive forces.
- the tapered surfaces formed by the incident angle allow each turn to overlap or interdigitate with the segment on either side of it, thus increasing the bending strength when the body is in compression.
- the cuts can be altered in depth and distance between the cuts on the longitudinal axis along the length of body portion 114 to variably alter the flexible-to-rigid characteristics of the tubular body along its length.
- the cuts 116 in body portion 114 allow an otherwise rigid member to increase its flexibility to a large degree during deployment.
- the tubular member can have constant or varying internal and external diameters. This design reduces the number of parts of the flexible-to-rigid body portion of the device and allows insertion and extraction of the device through a curved entry port in the bone while maximizing its rigidity once inserted.
- Application and removal of compressive forces provided by a parallel member such as wire(s), tension ribbons, a sheath, wound flexible cable, or actuator 126 as shown will transform the body from flexible to rigid and vice versa.
- Body portion 114 may be provided with a solid longitudinal portion 136 (as best seen in FIGS. 3 and 9 ) such that cuts 116 are a series of individual cuts each traversing less than 360 degrees in circumference, rather than a single, continuous helical cut.
- This solid portion 136 can aid in removal of device 100 by keeping body portion 114 from extending axially like a spring.
- FIG. 4 illustrates a combination tool 138 useful for inserting device 100 , actuating gripper 108 , compressing flexible-to-rigid body portion 114 , approximating the fracture in bone 106 , aligning anchor screw(s) 110 , and removing device 100 , if desired.
- tool 138 includes an L-shaped body 140 that mounts the other components of the tool and also serves as a handle.
- the main components of tool 138 are a device attachment portion 142 , a rotary driver 132 , an approximating driver 144 , and a screw alignment portion 146 .
- FIG. 5 shows a cross-section of the tool 138 and device 100 illustrated in FIG. 4 .
- device attachment portion 142 includes a knob 148 rigidly coupled to a tube 150 which is rotatably mounted within sleeve 152 .
- Sleeve 152 in turn is fixedly mounted to tool body 140 .
- the distal end of tube 150 is provided with external threads for engaging the internal threads on the proximal end of device 100 .
- both the distal end of sleeve 152 and the proximal end of device 100 may be provided with semicircular steps that inter-engage to prevent device 100 from rotating with respect to sleeve 152 .
- device 100 can be prevented from rotating when it is secured to tool 138 by tube 150 of device attachment portion 142 .
- the mating semicircular steps also serve to position device 100 in a particular axial and angular orientation with respect to tool 138 for aligning screws with screw holes, as will be later described.
- Rotary driver 132 may be used to actuate gripper 108 and compress flexible-to-rigid body portion 114 after device 100 is inserted into bone 106 .
- Driver 132 may also be used to allow body portion 114 to decompress and gripper 108 to retract if removal of device 100 from bone 106 is desired.
- driver 132 includes knob 154 , torsion spring 156 , hub 158 , bushing 160 and shaft 162 .
- the distal end of shaft 162 is provided with a mating tip 164 , such as one having a hex-key shape, for engaging with keyed socket 130 of device 100 (best seen in FIG. 3 ), such that turning driver shaft 162 turns drive member 128 and axially actuates actuator 126 , as described above.
- the proximal end of shaft 162 may be fitted with a bushing 160 , such as with a press-fit.
- Hub 158 may be secured over bushing 160 , such as with a pin through bushing 160 and shaft 162 .
- knob 154 is rotatably mounted over hub 158 and bushing 160 such that knob 154 can rotate independently from shaft 162 .
- a torsion spring 156 may be used to couple knob 154 to hub 158 as shown to create a torque limiting and/or torque measuring driver. With this indirect coupling arrangement, as knob 154 is rotated about shaft 162 , spring 156 urges hub 158 and shaft 162 to rotate in the same direction.
- Rotational resistance applied by device 100 to shaft tip 164 will increase in this embodiment as gripper 108 engages bone 106 , and flexible-to-rigid body portion 114 compresses. As more torque is applied to knob 154 , it will advance rotationally with respect to hub 158 as torsion spring 156 undergoes more stress. Markings may be provided on knob 154 and hub 158 to indicate the torque being applied. In this manner, a surgeon can use driver 132 to apply torque to device 100 in a predetermined range. This can help ensure that gripper 108 is adequately set in bone 106 , body portion 114 is sufficiently compressed, and excessive torque is not being applied that might damage device 100 , bone 106 or cause slippage therebetween.
- a slip clutch or other mechanism may be provided to allow the applied torque to be limited or indicated.
- driver 132 may be configured to “click” into or out of a detent position when a desired torque is reached, thus allowing the surgeon to apply a desired torque without needing to observe any indicia on the driver.
- the driver knob may be selectably or permanently coupled to shaft 162 directly.
- the approximating driver portion 144 of tool 138 may be used to compress one or more fractures in bone 106 .
- Approximating driver 144 includes knob 166 located on sleeve 152 .
- Knob 166 may be knurled on an outer circumference, and have threads on at least a portion of its axial bore. The internal threads of knob 166 engage with mating external threads on sleeve 152 such that when knob 166 is rotated it advances axially with respect to sleeve 152 .
- sleeve 152 is prevented from moving away from the bone.
- knob 166 As knob 166 is advanced axially toward bone 106 , it serves to approximate bone fractures located between gripper 108 and knob 166 .
- Suitable thread pitch and knob circumference may be selected to allow a surgeon to supply a desired approximating force to bone 106 by using a reasonable rotation force on knob 166 .
- a torque indicating and/or torque limiting mechanism as described above may be incorporated into approximating driver 144 .
- tool 138 may also include a screw alignment portion 146 .
- alignment portion 146 includes a removable alignment tube 168 and two bores 170 and 172 through tool body 140 .
- a single bore or more than two bores may be used, with or without the use of separate alignment tube(s).
- alignment tube 168 is first received in bore 170 as shown. In this position, tube 168 is in axial alignment with angled hole 174 at the distal end 102 of device 100 . As described above, the mating semicircular steps of device 100 and sleeve 152 position angled hole 174 in its desired orientation. With this arrangement, a drill bit, screw driver, screw and/or other fastening device or tool may be inserted through the bore of tube 168 such that the device(s) are properly aligned with hole 174 . The outward end of alignment tube 168 may also serve as a depth guide to stop a drill bit, screw and/or other fastener from penetrating bone 106 beyond a predetermined depth.
- Alignment tube 168 may be withdrawn from bore 170 as shown, and inserted in bore 172 . In this position, tube 168 aligns with hole 176 of device 100 . As described above, a drill bit, screw driver, screw and/or other fastening device may be inserted through the bore of tube 168 such that the device(s) are properly aligned with hole 176 .
- FIG. 6 shows alignment tube 168 of tool 138 aligning screw 110 with angled hole 174 at the distal end of device 100 , as described above.
- FIG. 7 shows a first screw 110 received through angled hole 174 and a second screw 110 received through hole 176 in device 100 and into bone 106 .
- Screws 110 may be installed manually or with the aid of tool 138 as described above.
- the heads of screws 110 may be configured to be self-countersinking such that they remain substantially beneath the outer surface of the bone when installed, as shown, so as to not interfere with adjacent tissue.
- the proximal end 102 of device 100 is secured to bone 106 with two screws 110 , and the distal end 104 is secured by gripper 108 . In this manner, any bone fractures located between the proximal screw 110 and distal gripper 108 may be approximated and rigidly held together by device 100 .
- more than one gripper may be used, or only screws or other fasteners without grippers may be used to secure device 100 within bone 106 .
- the device shown in FIG. 1 could be configured with a second gripper located between screw 110 and the middle of the device if the fracture is located more at the mid-shaft of the bone.
- more than two screws or other fasteners may be used, or only grippers without fasteners may be used.
- holes such as 174 and 176 as shown and described above can be preformed in the implantable device. In other embodiments, some or all of the holes can be drilled or otherwise formed in situ after the device is implanted in the bone.
- combination tool 138 may be removed by turning knob 148 to disengage threads of tube 150 from threads within the proximal end 102 of device 100 .
- An end plug 178 may be threaded into the proximal end 102 of device 100 to preventing growth of tissue into implanted device 100 .
- Device 100 may be left in bone 106 permanently, or it may be removed by performing the above described steps in reverse. In particular, plug 178 is removed, tool 138 is attached, screws 110 are removed, gripper 108 is retracted, and device 100 is pulled out using tool 138 .
- FIGS. 8 and 9 show alternative embodiments similar to device 100 described above.
- Device 100 ′ shown in FIG. 8 is essentially identical to device 100 described above but is shorter in length and utilizes a single anchor screw 110 at its proximal end 102 .
- Device 100 ′′ shown in FIG. 9 is similar to device 100 ′, but is shorter still.
- the devices may be configured to have a nominal diameter of 3 mm, 4 mm, 5 mm or 6 mm. It is envisioned that all three device designs 100 , 100 ′ and 100′′ may each be provided in all three diameters such that the chosen device is best suited for the particular fracture(s) and anatomy in which it is implanted.
- the device may be made from a variety of materials such as metal, composite, plastic or amorphous materials, which include, but are not limited to, steel, stainless steel, cobalt chromium plated steel, titanium, nickel titanium alloy (nitinol), superelastic alloy, and polymethylmethacrylate (PMMA).
- the device may also include other polymeric materials that are biocompatible and provide mechanical strength, that include polymeric material with ability to carry and delivery therapeutic agents, that include bioabsorbable properties, as well as composite materials and composite materials of titanium and polyetheretherketone (PEEKTM), composite materials of polymers and minerals, composite materials of polymers and glass fibers, composite materials of metal, polymer, and minerals.
- PEEKTM polyetheretherketone
- each of the aforementioned types of device may further be coated with proteins from synthetic or animal source, or include collagen coated structures, and radioactive or brachytherapy materials.
- the construction of the supporting framework or device may include radio-opaque markers or components that assist in their location during and after placement in the bone or other region of the musculo-skeletal systems.
- the reinforcement device may, in one embodiment, be osteo incorporating, such that the reinforcement device may be integrated into the bone.
- a low weight to volume device deployed in conjunction with other suitable materials to form a composite structure in-situ.
- suitable materials may include, but are not limited to, bone cement, high density polyethylene, Kapton®, polyetheretherketone (PEEKTM), and other engineering polymers.
- the device may be electrically, thermally, or mechanically passive or active at the deployed site within the body.
- the shape of the device may be dynamically modified using thermal, electrical or mechanical manipulation.
- the nitinol device may be expanded or contracted once deployed, to move the bone or other region of the musculo-skeletal system or area of the anatomy by using one or more of thermal, electrical or mechanical approaches.
- the inventive implantable device, tools and methods may be used in many locations within the body.
- the proximal end of a device in the anatomical context is the end closest to the body midline and the distal end in the anatomical context is the end further from the body midline, for example, on the humerus, at the head of the humerus (located proximal, or nearest the midline of the body) or at the lateral or medial epicondyle (located distal, or furthest away from the midline); on the radius, at the head of the radius (proximal) or the radial styloid process (distal); on the ulna, at the head of the ulna (proximal) or the ulnar styloid process (distal); for the femur, at the greater trochanter (proximal) or the lateral epicondyle or medial epicondyle (distal); for the tibia, at the medial
- access locations other than the ones described herein may also be suitable depending upon the location and nature of the fracture and the repair to be achieved.
- the devices taught herein are not limited to use on the long bones listed above, but can also be used in other areas of the body as well, without departing from the scope of the invention. It is within the scope of the invention to adapt the device for use in flat bones as well as long bones.
- FIGS. 10A-10I show another embodiment of a bone fixation device constructed according to aspects of the invention.
- FIG. 10A is a perspective view showing the exemplary device 200 deployed in a fractured clavicle 202 .
- Device 200 is similar to device 100 described above and shown in FIGS. 1-7 , but has a gripper 204 located near its proximal end, another gripper 206 located at a more distal location, and a flexible-to-rigid body portion 208 located near the distal end of the device.
- a bone screw 210 and gripper 204 are configured to secure device 200 inside bone 202 on the proximal side of fracture 212
- gripper 206 and flexible-to-rigid body portion 208 are configured to secure device 200 on the distal side of fracture 212 .
- construction and operation of device 200 is much like that of device 100 described above.
- each of the two grippers 204 and 206 has four outwardly expanding arms 214 . These arms are spaced at 90 degree intervals around the circumference of the device body.
- the arms 214 of gripper 204 may be offset by 45 degrees from arms 214 of gripper 206 as shown in the figures to distribute the forces applied by grippers 204 and 206 on the bone 202 .
- a single actuator 216 may be used to deploy both grippers 204 and 206 .
- Actuator 216 may also be used to axially compress flexible-to-rigid body portion 208 to make it substantially rigid.
- actuator 216 may be flexible to allow flexible-to-rigid body portion 208 to assume a curved shape, as best seen in FIGS. 10A and 10B .
- the actuator may be rigid and faulted with the desired straight and/or curved shape to match the flexible-to-rigid body portion.
- FIGS. 10G-10I further details of an exemplary gripper 204 are shown.
- FIGS. 10G and 10H show gripper 204 with bendable arms 214 in a retracted state.
- cam 218 of actuator 216 is driven axially into the distal ramped ends of arms 214
- arms 214 bend at thinned portions 220 to move radially outward toward the deployed position shown in FIG. 10I .
- Notches 222 may be provided in the distal ends of arms 214 as shown to allow arms 214 to better grip interior bone surfaces. Without departing from the scope of the invention, one, two, three, or more bendable arms may be used.
- Device 300 includes a curved hub 302 , proximal gripper 304 , flexible-to-rigid body portion 306 , and distal gripper 308 .
- Distal gripper 308 is similar in construction and operation to grippers 204 and 206 described above.
- Proximal gripper 304 is provided with three pairs of scissor arms 310 . Each pair of arms 310 is pivotably interconnected at a mid-portion by a pin. Each arm is pivotably connected with a pin to either proximal end piece 312 or distal end piece 314 .
- arms 310 pivot radially outward from an axially aligned retracted position, as shown in FIGS. 11A and 11C , to a deployed position, as shown in FIGS. 11B and 11D .
- the distal ends of the six arms 310 engage an inner surface of a bone as previously described.
- device 300 In operation, device 300 , with grippers 304 and 308 in a retracted state, may be inserted into the intramedullary space within a bone, such as the radius.
- Device 300 may be inserted through a curved opening formed in the bone, such as an opening formed through a bony protuberance on a distal or proximal end or through the midshaft of the bone.
- Curved hub 302 may be configured with the same geometry of the curved opening in the bone, and when the flexible-to-rigid body portion 306 is in its flexible state, it can assume this same geometry.
- 11C and 11D may be actuated from the proximal end of device 300 by turning drive member 317 in a manner similar to that previously described.
- Longitudinal movement of actuator 315 toward the proximal end of device 300 causes flexible-to-rigid body portion 306 to foreshorten and assume its rigid state, and causes grippers 304 and 308 to outwardly deploy against the bone.
- Bone screws may be inserted through holes 316 shown in curved hub 302 to secure the proximal end of device 300 to the bone. Further details of the construction and operation of a device similar to device 300 may be found in co-pending U.S. application Ser. No. 11/944,366 filed Nov. 21, 2007 and entitled Fracture Fixation Device, Tools and Methods.
- Device 300 is an example of an embodiment utilizing mixed gripper types. In other words, this device uses one scissors-arm tripod gripper 304 and one bendable-arm gripper 308 .
- Other embodiments of the invention use various combinations of gripper(s) and/or flexible-to-rigid body portion(s). Further exemplary gripper embodiments are described in detail in co-pending U.S. application Ser. No. 61/100,652 filed Sep. 26, 2008 and entitled Fracture Fixation Device, Tools and Methods. It is envisioned that virtually any combination of zero, one, two, or more grippers may be used in combination with zero, one, two or more flexible-to-rigid body portions to form a device adapted to a particular bone anatomy, fracture, disease state or fixation purpose.
- the grippers and/or flexible-to-rigid body portions may each be of identical or different construction, and may be placed together or at other locations along the device. Further, a straight, curved, flexible, rigid, or no hub at all may be used with the above combinations. Additionally, screws, K-wires, sutures or no additional fixation may be used with these various devices.
- the devices may be specially designed and constructed for a particular purpose or range of purposes. According to aspects of the invention, the components may also be designed to be interchangeable and/or produced in various sizes so that surgical kits may be provided. Such kits would allow surgical teams to select from a variety of components to build devices themselves, each suited to a particular patient's unique situation.
- FIGS. 12A through 20B further examples of the hubs discussed above are shown and will now be described.
- FIGS. 12A-12F show details of a curved hub 400 similar to hub 302 illustrated in FIGS. 11A-11D .
- hub 400 has an internally threaded portion at its proximal end 402 for engaging with an insertion and removal tool as described above. (The proximal end is referenced as the end closest to the surgeon.)
- the proximal end 402 may also have a keyed feature for mating with the tool for maintaining a desired orientation of hub 400 relative to the tool.
- Hub 400 may also be provided with a counterbore at its distal end 404 for coupling to a gripper or flexible-to-rigid body portion, such as by press fit and/or welding.
- Exemplary hub 400 includes three holes 406 , 408 and 410 through the wall thickness on its concave side, as best seen in FIG. 12C .
- hub 400 includes four holes 412 , 414 , 416 , and 418 through the wall thickness on its convex side, as best seen in FIG. 12D .
- At least a portion of all seven holes may be seen in FIG. 12F .
- Holes 406 and 412 on opposite sides of hub 400 are aligned to allow a bone screw to be inserted through the two holes across the hub to secure hub 400 to the bone and/or to secure bone fragment(s) with the screw.
- holes 408 and 414 are aligned to receive a second bone screw
- holes 410 and 416 are aligned to receive a third bone screw.
- a fourth screw may be inserted through the open proximal end 402 of hub 400 and out through hole 418 .
- Each screw may be passed first through cortical bone, then cancellous bone, then through the two holes of hub 400 , through more cancellous bone and possibly into more cortical bone on the opposite side of the bone from where the screw entered.
- the holes of hub 400 have a diameter of 2.4 mm. In other embodiments, the holes have a diameter of 2.7 mm. In still other embodiments, the holes may have larger or smaller diameters.
- the holes may be threaded during the fabrication of hub 400 , or threads may be formed in vivo.
- Various fixtures, jigs, tools and methods may be used to align the screws with the holes, such as a tool similar to tool 138 shown in FIGS. 4-6 and described above. Further examples of positioning aids are provided in copending U.S. application Ser. No. 11/944,366 filed Nov. 21, 2007 and entitled Fracture Fixation Device, Tools and Methods.
- the heads of the screws may be countersunk into the bone as described in copending U.S. application Ser. No. 61/117,901 filed Nov. 25, 2008 and entitled Bone Fracture Fixation Screws, Systems and Methods of Use.
- FIGS. 12G-12I illustrate an example how bone screws 420 , 422 , 424 may be inserted through hub 400 ′ (which is similar to hub 400 ) as described above to secure the comminuted fracture depicted at the distal end of a radius bone 425 .
- hub 400 ′ which is similar to hub 400
- One, two, three, four, or more screws may be used depending on the anatomy and fracture condition of each particular case. It should be noted that in this particular embodiment, either screw 422 or 424 may be placed through hub 400 ′, but not both at the same time, as their paths intersect inside hub 400 ′. It can be seen that screws 422 and 424 extend across fracture 426 into bone fragment 428 . Accordingly, either screw 422 or 424 may be used to approximate fracture 426 when the screw is tightened.
- FIGS. 13A-13E show another exemplary embodiment of a bone fixation device hub 450 .
- Hub 450 is of similar construction to hub 400 described above and includes proximal end 452 and distal end 454 .
- hub 450 includes four holes 456 , 458 , 460 , and 462 through the wall thickness on its concave side.
- Holes 456 and 458 are located the same longitudinal distance from distal end 454 , but are symmetrically located on opposite sides of a central longitudinal plane. As can be seen, holes 456 and 458 actually overlap to form a single, figure-eight shaped hole.
- Holes 460 and 462 are also located the same longitudinal distance from proximal end 452 , and are symmetrically located on opposite sides of a central longitudinal plane.
- hub 450 also includes six holes 464 , 466 , 468 , 470 , 472 , and 474 through the wall thickness on its convex side.
- Holes 464 and 466 are located the same longitudinal distance from distal end 454 , but are symmetrically located on opposite sides of a central longitudinal plane. Holes 464 and 466 also overlap to form a single, figure-eight shaped hole, similar to holes 456 and 458 described above.
- Holes 468 and 470 are also located the same longitudinal distance from proximal end 452 , and are symmetrically located on opposite sides of a central longitudinal plane.
- holes 472 and 474 are also located the same longitudinal distance from proximal end 452 , and are symmetrically located on opposite sides of a central longitudinal plane.
- Holes 456 and 464 on diagonally opposite sides of hub 450 are aligned to allow a bone screw to be inserted through the two holes across the hub, passing through a centerline of hub 450 .
- holes 458 and 466 on diagonally opposite sides of hub 450 are aligned to allow a bone screw to be inserted through the two holes across the hub, passing through a centerline of hub 450 . Since both of these two screw paths cross the centerline at the same location forming an X-pattern, only one screw may be placed through these two pairs of holes 456 / 464 and 458 / 466 in any particular procedure.
- holes 460 and 468 on diagonally opposite sides of hub 450 are aligned to allow a bone screw to be inserted through the two holes across the hub, passing through a centerline of hub 450 .
- Holes 462 and 470 on diagonally opposite sides of hub 450 are also aligned to allow a bone screw to be inserted through the two holes across the hub, passing through a centerline of hub 450 . Since both of these two screw paths cross the centerline at the same location forming an X-pattern, only one screw may be placed through these two pairs of holes 460 / 468 and 462 / 470 in any particular procedure.
- a third screw may be inserted through the open proximal end 452 of hub 450 and out through either hole 472 or hole 474 . Since these two screw paths also overlap, only one screw may be placed though them at a time.
- exemplary hub 450 is symmetrical about a central plane. Since hub 450 may receive up to three screws, each in one of two positions, there are a total of eight screw patterns that may be used with hub 450 , depending on the situation. Additionally, only one or two screws, or no screws, may be used in a particular procedure, if desired. The positions and orientations of the screw holes of hub 450 relative to previously described hub 400 may take better advantage of cortical bone locations in some procedures for better anchoring of bone screws.
- a screw passing through hole pairs 456 / 464 , 458 / 466 , 460 / 468 or 462 / 470 of hub 450 will have a reduced angle relative to a longitudinal axis of a bone as compared with the screw trajectories of similar screws in hub 400 .
- a screw passing through either hole 472 or 474 will have a different angle from the same screw in hub 400 , which in many cases allows the screw of hub 450 to hit harder bone.
- screw paths of hole pairs 460 / 468 and 462 / 470 are closer to the proximal end of hub 450 than similar screw paths in hub 400 , allowing the screws to fixate in harder bone located near the end of a bone.
- All of the new screw trajectories provided by hub 450 may be used with the in vivo hole forming hubs that will be later described below.
- the trajectories of hole pairs 456 / 464 , 458 / 466 , 460 / 468 or 462 / 470 also form an angle with a central, longitudinal plane containing the curve of hub 450 (in other words, a plane of symmetry of the hole pairs.)
- the hole pairs each form an angle with the plane falling in a range of about 5 to 30 degrees.
- FIGS. 14A-14E show another exemplary embodiment of a bone fixation device hub 500 .
- Hub 500 is of similar construction to hubs 400 and 450 described above and includes proximal end 502 and distal end 504 .
- hub 500 includes slotted holes 506 , 508 , and 510 through the wall
- hub 500 also includes slotted holes 512 , 514 , and 516 , and angled hole 518 through the wall thickness on its convex side. Holes 506 and 512 on opposite sides of hub 500 are aligned to allow a first bone screw to be inserted through the two holes across the hub. Similarly, holes 508 and 514 are aligned to receive a second bone screw, and holes 510 and 516 are aligned to receive a third bone screw. Hole 518 is aligned with the opening in the proximal end 502 of hub 500 to receive a fourth bone screw.
- the slotted configuration of hole pairs 506 / 512 , 508 / 514 , and 510 / 516 allows a bone screw to be received through each of the pairs in a variety of orientations.
- This arrangement permits a surgeon the flexibility to place bone screws where most appropriate in a particular procedure.
- a first bone screw may be placed through holes 506 and 512 such that it resides in the left, middle, or right portion of hole 506 , as viewed in FIG. 14C .
- the same screw will have another section that may reside in the left, middle, or right portion of hole 512 .
- the screw can take one of nine basic orientations through holes 506 and 512 , as well as many other orientations between these nine.
- a slightly enlarged round hole may be provided on one side of the hub while a slotted hole on the opposite side forms the other hole of the pair.
- the width of slotted holes 506 , 508 , 510 , 512 , 514 , and 516 is 2.0 mm. This provides a pilot hole in which a drill bit or screw tip may engage. Material from a portion of the sides of each hole may be removed when the drill bit forms a larger hole in one location of the slotted hole, and/or when a screw is inserted to form threads through the hole. No drilling or threading may be necessary, such as when the slot width is generally the same as the minor diameter of the screw, and the thickness of the hub walls is generally the same as the screw pitch.
- the slotted holes may also stretch or deform when receiving the screw. As shown in FIG.
- relief slit(s) 520 may be provided adjacent to a slotted hole 506 to allow the slot to more easily expand when receiving a screw 522 .
- Such slits may be formed by laser cutting, electron beam melting (EBM), electrical discharge machining (EDM), etching, stamping, milling, or other fabrication techniques.
- FIGS. 15A-15D show another exemplary embodiment of a bone fixation device hub 500 ′.
- Hub 500 ′ is similar to hub 500 described above, but has slotted holes that are oriented longitudinally rather than transversely.
- Hub 500 ′ includes proximal end 502 ′ and distal end 504 ′.
- hub 500 ′ includes slotted holes 506 ′, 508 ′, and 510 ′ through the wall thickness on its concave side.
- hub 500 ′ also includes slotted holes 512 ′, 514 ′, and 516 ′, and angled hole 518 ′ through the wall thickness on its convex side.
- Holes 506 ′ and 512 ′ on opposite sides of hub 500 ′ are aligned to allow a first bone screw to be inserted through the two holes across the hub.
- holes 508 ′ and 514 ′ are aligned to receive a second bone screw
- holes 510 ′ and 516 ′ are aligned to receive a third bone screw.
- Hole 518 ′ is aligned with the opening in the proximal end 502 ′ of hub 500 ′ to receive a fourth bone screw.
- Exemplary axis lines 524 , 526 , 528 , and 530 are shown in FIG. 15A to show examples paths for the first, second, third, and fourth screws, respectively.
- FIGS. 16A-16E show another exemplary embodiment of a bone fixation device hub 550 .
- hub 550 includes at its proximal end 552 a transversely elongated hole 554 .
- Hole 554 allows a screw 556 to be located along the central axis, or off-axis in either direction as may be desired for engaging harder bone or securing additional bone fragment(s).
- This of arrangement of hole 554 may be configured to hold screw 556 tightly at all angles. This may be accomplished, for example, by using a hole 554 slot width that is equal to or smaller than the minor diameter of screw 556 .
- the wall thickness of hub 550 may fit into the screw threads, providing additional locking of screw 556 .
- the angle of elongated hole 554 may be oriented differently as desired.
- screw 558 has a tapered edge 560 below its head 562 . Tapered edge 560 serves to wedge screw 558 into slot 554 , securing the screw in place.
- a screw with an expanding head (not shown) may also be used. With this arrangement, a taper or other expanded section may be created once the screw is in place, thereby locking it in position.
- FIGS. 17A-17C show another exemplary embodiment of a bone fixation hub 600 .
- Hub 600 is provided with an array of pilot holes 602 over most of its surface.
- Each hole 602 may be 0.015 to 0.020 inches in diameter, for example, and serves as a starting point to allow a drill bit or screw tip to penetrate the wall thickness of hub 600 . This makes in vivo screw hole formation possible, while allowing the hub to remain a rigid structure.
- Holes 602 may be closely spaced such that a screw or screws may be positioned in vivo virtually anywhere the surgeon desires during each particular procedure. Once the drill bit and/or screw is inserted, the hole 602 becomes enlarged to generally the minor diameter of the screw thread, such as to 2.7 mm in diameter, for example. Screw holes may be formed in this way on both sides of hub 600 in a continuous operation, allowing screw(s) to be positioned across the hub as previously described.
- pilot holes 602 may be placed closer to one another so that multiple perforations are consumed by the screw diameter 604 when the screw hole is formed. This can make in vivo hole formation even easier.
- Other hole patterns than those shown in FIGS. 17A-17C may be used.
- Holes 602 may be fabricated in hub 600 by laser cutting, electron beam melting (EBM), electrical discharge machining (EDM), etching, stamping, drilling, or other fabrication techniques.
- EBM electron beam melting
- EDM electrical discharge machining
- FIGS. 18A and 18B show another exemplary embodiment of a bone fixation hub 650 .
- Hub 650 has at least a portion that is fabricated from a mesh structure, forming a plurality of diamond or other shaped apertures 652 .
- Apertures 652 may be configured with dimensions smaller than the major diameter of the threads of the bone screws to be used. Aperture dimensions may even be smaller than the minor thread diameter, such that the apertures are stretched and/or deformed as the screw enters the aperture, thereby providing an increased ability to hold the screws in place.
- the use of a mesh hub 650 may reduce the amount or possibility of debris being formed and released inside the body during in vivo screw hole formation.
- Apertures 652 may be fabricated in hub 650 by laser cutting, electron beam melting (EBM), electrical discharge machining (EDM), etching, stamping, drilling, or other fabrication techniques. Apertures 652 may also be fabricated by forming slits in plate or tube stock and expanding the material to form the apertures. Another fabrication technique that may be used is forming wires or bands around a mandrel and then welding, brazing, soldering, pressing, melting, gluing, or otherwise joining the wires or bands to each other at their intersections. Other types of porous structures, either with or without more random aperture locations, may be used as well. Multiple layers of mesh may also be combined.
- FIGS. 19A and 19B show another exemplary embodiment of a bone fixation hub 700 .
- Hub 700 is provided with a plurality of thin slots 702 along its length. Slots 702 permit in vivo screw hole formation by acting as long pilot holes for drill bits or bone screws. A bone screw tip may be inserted into one of the slots 702 without pre-drilling. Upon insertion, the slot and surrounding slots will deform to make way for the screw, and will provide circumferential pressure to retain the screw.
- slots 702 may be fabricated in hub 700 by laser cutting, electron beam melting (EBM), electrical discharge machining (EDM), etching, stamping, drilling, or other fabrication techniques. Thin slots 702 may generally require less material removal than other hub embodiments.
- EBM electron beam melting
- EDM electrical discharge machining
- FIGS. 20A and 20B show another exemplary embodiment of a bone fixation hub 750 .
- Hub 750 comprises three separately formed hubs assembled together: an inner hub 752 , a mid-hub 754 , and an outer hub 756 .
- Mid-hub 754 has a larger diameter than inner hub 752 so that mid-hub 754 may be placed over inner hub 752 , as illustrated in FIGS. 20A and 20B .
- outer hub 756 has a larger diameter than mid-hub 754 so that outer hub 756 may be placed over mid-hub 754 , as also illustrated in the figures.
- all three hub components 752 , 754 , and 756 have the same bend radius and the same arc length.
- the three hub components 752 , 754 , and 756 may be retained at one or both ends by other components of the associated bone fixation device, and/or may be welded or otherwise fastened together.
- inner hub 752 and outer hub 756 have spirally formed slots 758 and 760 , respectively. Slots 758 and 760 may be formed such that they line up when the individual hubs are assembled. Each hub 752 and 756 may also be provided with an upper spine ( 762 and 764 , respectively), and a lower spine (not seen in FIG. 20B ). The spines are solid regions running the length of the hubs that provide rigidity, and are positioned in areas that do not typically receive screws.
- Mid-hub 754 has longitudinally extending slots 766 rather than spiral slots. When the three slot patterns are assembled in a coaxial unit, as shown in FIG. 20A , a hub is formed that may be quite rigid. Pilot holes are formed where slots 760 , 766 , and 758 line up radially to facilitate in vivo screw hole formation. When a screw is inserted in such a pilot hole, one or more of the slots may deform to receive the screw.
- One, two, three, four, or more hub layers may be used in this manner to form a single layer or composite hub.
- Other slot patterns and widths may be used as appropriate.
- Some of the layers may incorporate round or other aperture shapes instead of or in addition to the slots shown in this example.
- one or more screws may be placed into just a single side of the hub, or completely across the hub through both sides.
Abstract
A bone fixation device is provided with an elongate body having a longitudinal axis and having a first state in which at least a portion of the body is flexible and a second state in which the body is generally rigid, an actuateable gripper disposed at one or more locations on the elongated body, a hub located on a proximal end of the elongated body, and an actuator operably connected to the gripper(s) to deploy the gripper(s) from a retracted configuration to an expanded configuration. Methods of repairing a fracture of a bone are also disclosed. One such method comprises inserting a bone fixation device into an intramedullary space of the bone to place at least a portion of an elongate body of the fixation device in a flexible state on one side of the fracture and at least a portion of a hub on another side of the fracture, and operating an actuator to deploy at least one gripper of the fixation device to engage an inner surface of the intramedullary space to anchor the fixation device to the bone. Various hub designs are disclosed that may be used in combination with other fixation device components.
Description
- Any and all applications for which a foreign or domestic priority claim is identified in the Application Data Sheet as filed with the present application are hereby incorporated by reference under 37 CFR 1.57.
- The present invention relates to devices, tools and methods for providing reinforcement of bones. More specifically, the present invention relates to devices, tools and methods for providing reconstruction and reinforcement of bones, including diseased, osteoporotic and fractured bones.
- Bone fractures are a common medical condition both in the young and old segments of the population. However, with an increasingly aging population, osteoporosis has become more of a significant medical concern in part due to the risk of osteoporotic fractures. Osteoporosis and osteoarthritis are among the most common conditions to affect the musculoskeletal system, as well as frequent causes of locomotor pain and disability. Osteoporosis can occur in both human and animal subjects (e.g. horses). Osteoporosis (OP) and osteoarthritis (OA) occur in a substantial portion of the human population over the age of fifty. The National Osteoporosis Foundation estimates that as many as 44 million Americans are affected by osteoporosis and low bone mass, leading to fractures in more than 300,000 people over the age of 65. In 1997 the estimated cost for osteoporosis related fractures was $13 billion. That figure increased to $17 billion in 2002 and is projected to increase to $210-240 billion by 2040. Currently it is expected that one in two women, and one in four men, over the age of 50 will suffer an osteoporosis-related fracture. Osteoporosis is the most important underlying cause of fracture in the elderly. Also, sports and work-related accidents account for a significant number of bone fractures seen in emergency rooms among all age groups.
- One current treatment of bone fractures includes surgically resetting the fractured bone. After the surgical procedure, the fractured area of the body (i.e., where the fractured bone is located) is often placed in an external cast for an extended period of time to ensure that the fractured bone heals properly. This can take several months for the bone to heal and for the patient to remove the cast before resuming normal activities. In some instances, an intramedullary (IM) rod or nail is used to align and stabilize the fracture. In that instance, a metal rod is placed inside a canal of a bone and fixed in place, typically at both ends. See, for example, Fixion™ IM (Nail), www.disc-o-tech.com. This approach requires incision, access to the canal, and placement of the IM nail. The nail can be subsequently removed or left in place. A conventional IM nail procedure requires a similar, but possibly larger, opening to the space, a long metallic nail being placed across the fracture, and either subsequent removal, and or when the nail is not removed, a long term implant of the IM nail. The outer diameter of the IM nail must be selected for the minimum inside diameter of the space. Therefore, portions of the IM nail may not be in contact with the canal. Further, micro-motion between the bone and the IM nail may cause pain or necrosis of the bone. In still other cases, infection can occur. The IM nail may be removed after the fracture has healed. This requires a subsequent surgery with all of the complications and risks of a later intrusive procedure. In general, rigid IM rods or nails are difficult to insert, can damage the bone and require additional incisions for cross-screws to attach the rods or nails to the bone.
- Some IM nails are inflatable. See, for example, Meta-Fix IM Nailing System, www.disc-o-tech.com. Such IM nails require inflating the rod with very high pressures, endangering the surrounding bone. Inflatable nails have many of the same drawbacks as the rigid IM nails described above.
- External fixation is another technique employed to repair fractures. In this approach, a rod may traverse the fracture site outside of the epidermis. The rod is attached to the bone with trans-dermal screws. If external fixation is used, the patient will have multiple incisions, screws, and trans-dermal infection paths. Furthermore, the external fixation is cosmetically intrusive, bulky, and prone to painful inadvertent manipulation by environmental conditions such as, for example, bumping into objects and laying on the device. Other concepts relating to bone repair are disclosed in, for example, U.S. Pat. No. 5,108,404 to Scholten for Surgical Protocol for Fixation of Bone Using Inflatable Device; U.S. Pat. No. 4,453,539 to Raftopoulos et al. for Expandable Intramedullary Nail for the Fixation of Bone Fractures; U.S. Pat. No. 4,854,312 to Raftopolous for Expanding Nail; U.S. Pat. No. 4,932,969 to Frey et al. for Joint Endoprosthesis; U.S. Pat. No. 5,571,189 to Kuslich for Expandable Fabric Implant for Stabilizing the Spinal Motion Segment; U.S. Pat. No. 4,522,200 to Stednitz for Adjustable Rod; U.S. Pat. No. 4,204,531 to Aginsky for Nail with Expanding Mechanism; U.S. Pat. No. 5,480,400 to Berger for Method and Device for Internal Fixation of Bone Fractures; U.S. Pat. No. 5,102,413 to Poddar for Inflatable Bone Fixation Device; U.S. Pat. No. 5,303,718 to Krajicek for Method and Device for the Osteosynthesis of Bones; U.S. Pat. No. 6,358,283 to Hogfors et al. for Implantable Device for Lengthening and Correcting Malpositions of Skeletal Bones; U.S. Pat. No. 6,127,597 to Beyar et al. for Systems for Percutaneous Bone and Spinal Stabilization, Fixation and Repair; U.S. Pat. No. 6,527,775 to Warburton for Interlocking Fixation Device for the Distal Radius; U.S. Patent Publication US2006/0084998 A1 to Levy et al. for Expandable Orthopedic Device; and PCT Publication WO 2005/112804 A1 to Myers Surgical Solutions, LLC for Fracture Fixation and Site Stabilization System. Other fracture fixation devices, and tools for deploying fracture fixation devices, have been described in: US Patent Appl. Publ. No. 2006/0254950; U.S. Ser. No. 60/867,011 (filed Nov. 22, 2006); U.S. Ser. No. 60/866,976 (filed Nov. 22, 2006); and U.S. Ser. No. 60/866,920 (filed Nov. 22, 2006). In view of the foregoing, it would be desirable to have a device, system and method for providing effective and minimally invasive bone reinforcement and fracture fixation to treat fractured or diseased bones, while improving the ease of insertion, eliminating cross-screw incisions and minimizing trauma.
- ASPECTS OF THE INVENTION RELATE TO EMBODIMENTS OF A BONE FIXATION DEVICE AND TO METHODS FOR USING such a device for repairing a bone fracture. The bone fixation device may include an elongate body with a longitudinal axis and having a flexible state and a rigid state. The device further may include a plurality of grippers disposed at longitudinally-spaced locations along the elongated body, a rigid hub connected to the elongated body, and an actuator that is operably-connected to the grippers to deploy the grippers from a first shape to an expanded second shape.
- In one embodiment, a bone fixation device is provided with an elongate body having a longitudinal axis and having a first state in which at least a portion of the body is flexible and a second state in which the body is generally rigid, an actuateable gripper disposed at a distal location on the elongated body, a hub located on a proximal end of the elongated body, and an actuator operably connected to the gripper to deploy the gripper from a retracted configuration to an expanded configuration.
- Methods of repairing a fracture of a bone are also disclosed. One such method comprises inserting a bone fixation device into an intramedullary space of the bone to place at least a portion of an elongate body of the fixation device in a flexible state on one side of the fracture and at least a portion of a hub on another side of the fracture, and operating an actuator to deploy at least one gripper of the fixation device to engage an inner surface of the intramedullary space to anchor the fixation device to the bone.
- One embodiment of the present invention provides a low weight to volume mechanical support for fixation, reinforcement and reconstruction of bone or other regions of the musculo-skeletal system in both humans and animals. The method of delivery of the device is another aspect of the invention. The method of delivery of the device in accordance with the various embodiments of the invention reduces the trauma created during surgery, decreasing the risks associated with infection and thereby decreasing the recuperation time of the patient. The framework may in one embodiment include an expandable and contractible structure to penult re-placement and removal of the reinforcement structure or framework.
- In accordance with the various embodiments of the present invention, the mechanical supporting framework or device may be made from a variety of materials such as metal, composite, plastic or amorphous materials, which include, but are not limited to, steel, stainless steel, cobalt chromium plated steel, titanium, nickel titanium alloy (nitinol), superelastic alloy, and polymethylmethacrylate (PMMA). The device may also include other polymeric materials that are biocompatible and provide mechanical strength, that include polymeric material with ability to carry and delivery therapeutic agents, that include bioabsorbable properties, as well as composite materials and composite materials of titanium and polyetheretherketone (PEEK™), composite materials of polymers and minerals, composite materials of polymers and glass fibers, composite materials of metal, polymer, and minerals.
- Within the scope of the present invention, each of the aforementioned types of device may further be coated with proteins from synthetic or animal source, or include collagen coated structures, and radioactive or brachytherapy materials. Furthermore, the construction of the supporting framework or device may include radio-opaque markers or components that assist in their location during and after placement in the bone or other region of the musculo-skeletal systems.
- Further, the reinforcement device may, in one embodiment, be osteo incorporating, such that the reinforcement device may be integrated into the bone.
- In still another embodiment of the invention, a method of repairing a bone fracture is disclosed that comprises: accessing a fracture along a length of a bone through a bony protuberance at an access point at an end of a bone; advancing a bone fixation device into a space through the access point at the end of the bone; bending a portion of the bone fixation device along its length to traverse the fracture; and locking the bone fixation device into place within the space of the bone. The method can also include the step of advancing an obturator through the bony protuberance and across the fracture prior to advancing the bone fixation device into the space. In yet another embodiment of the method, the step of anchoring the bone fixation device within the space can be included.
- An aspect of the invention discloses a removable bone fixation device that uses a single port of insertion and has a single-end of remote actuation wherein a bone fixation device stabilizes bone after it has traversed the fracture. The bone fixation device is adapted to provide a single end in one area or location where the device initiates interaction with bone. The device can be deployed such that the device interacts with bone. Single portal insertion and single-end remote actuation enables the surgeon to insert and deploy the device, deactivate and remove the device, reduce bone fractures, displace or compress the bone, and lock the device in place. In addition, the single-end actuation enables the device to grip bone, compresses the rigidizable flexible body, permits axial, torsional and angular adjustments to its position during surgery, and releases the device from the bone during its removal procedure. A removable extractor can be provided in some embodiments of the device to enable the device to be placed and extracted by deployment and remote actuation from a single end. The device of the invention can be adapted and configured to provide at least one rigidizable flexible body or sleeve. Further the body can be configured to be flexible in all angles and directions. The flexibility provided is in selective planes and angles in the Cartesian, polar, or cylindrical coordinate systems. Further, in some embodiments, the body is configured to have a remote actuation at a single end. Additionally, the body can be configured to have apertures, windings, etc. The device may be configured to function with non-flexible bodies for use in bones that have a substantially straight segment or curved segments with a constant radius of curvature. Another aspect of the invention includes a bone fixation device in that has mechanical geometry that interacts with bone by a change in the size of at least one dimension of a Cartesian, polar, or spherical coordinate system. Further, in some embodiments, bioabsorbable materials can be used in conjunction with the devices, for example by providing specific subcomponents of the device configured from bioabsorbable materials. A sleeve can be provided in some embodiments where the sleeve is removable, has deployment, remote actuation, and a single end. Where a sleeve is employed, the sleeve can be adapted to provide a deployable interdigitation process or to provide an aperture along its length through which the deployable interdigitation process is adapted to engage bone. In some embodiments, the deployable interdigitation process is further adapted to engage bone when actuated by the sleeve. In some embodiments, the bone fixation device further comprises a cantilever adapted to retain the deployable bone fixation device within the space. The sleeve can further be adapted to be expanded and collapsed within the space by a user. One end of the device can be configured to provide a blunt obturator surface adapted to advance into the bone. A guiding tip may also be provided that facilitates guiding the device through the bone. Further, the deployable bone fixation device can be adapted to receive external stimulation to provide therapy to the bone. The device can further be adapted to provide an integral stimulator which provides therapy to the bone. In still other embodiments, the device can be adapted to receive deliver therapeutic stimulation to the bone.
- The devices disclosed herein may be employed in various regions of the body, including: cranial, thoracic, lower extremities and upper extremities. Additionally, the devices are suitable for a variety of breaks including, metaphyseal and diaphyseal.
- The fracture fixation devices of various embodiments of the invention are adapted to be inserted through an opening of a fractured bone, such as the radius (e.g., through a bony protuberance on a distal or proximal end or through the midshaft) into the intramedullary canal of the bone. In some embodiments, the fixation device has two main components, one configured component for being disposed on the side of the fracture closest to the opening and one component configured for being disposed on the other side of the fracture from the opening so that the fixation device traverses the fracture.
- The device components cooperate to align, fix and/or reduce the fracture so as to promote healing. The device may be removed from the bone after insertion (e.g., after the fracture has healed or for other reasons), or it may be left in the bone for an extended period of time or permanently.
- In some embodiments, the fracture fixation device has one or more actuatable anchors or grippers on its proximal and/or distal ends. These anchors may be used to hold the fixation device to the bone while the bone heals.
- In some embodiments, to aid in insertion into the intramedullary canal, at least one component of the fracture fixation device has a substantially flexible state and a substantially rigid state. Once in place, deployment of the device also causes the components to change from the flexible state to a rigid state to aid in proper fixation of the fracture. At least one of the components may be substantially rigid or semi-flexible. At least one component may provide a bone screw attachment site for the fixation device.
- Embodiments of the invention also provide deployment tools with a tool guide for precise alignment of one or more bone screws with the fracture fixation device. These embodiments also provide bone screw orientation flexibility so that the clinician can select an orientation for the bone screw(s) that will engage the fixation device as well as any desired bone fragments or other bone or tissue locations.
- These and other features and advantages of the present invention will be understood upon consideration of the following detailed description of the invention and the accompanying drawings.
- THE novel features of the invention are set forth with particularity in the appended claims. A better understanding of the features and advantages of the present invention will be obtained by reference to the following detailed description that sets forth illustrative embodiments, in which the principles of the invention are utilized, and the accompanying drawings of which:
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FIG. 1 is a perspective view of an embodiment of a bone fixation device implanted in a bone according to the invention. -
FIG. 2 is another perspective view of the implanted device ofFIG. 1 . -
FIG. 3 is a longitudinal cross-section view of the bone fixation device ofFIG. 1 in a non-deployed state. -
FIG. 4 is a plan view of a combination deployment tool that may be used with the bone fixation device ofFIG. 1 . -
FIG. 5 is a cross-section view of the tool and device shown inFIG. 4 . -
FIG. 6 is a perspective view of the tool and device shown inFIG. 4 . -
FIG. 7 is a cross-section view of the implanted device ofFIG. 1 . -
FIG. 8 is a perspective view of an alternative embodiment of the implanted device ofFIG. 1 . -
FIG. 9 is a perspective view of another alternative embodiment of the implanted device ofFIG. 1 . -
FIG. 10A is a perspective view of another embodiment of a bone fixation device shown deployed in a fractured clavicle. -
FIG. 10B is perspective view of the device shown inFIG. 10A shown in a deployed state. -
FIG. 10C is a side elevation view of the device shown inFIG. 10A shown in a retracted or undeployed state. -
FIG. 10D is a side elevation view of the device shown inFIG. 10A shown in a deployed state. -
FIG. 10E is a cross-sectional view of the device shown inFIG. 10A shown in a retracted or undeployed state. -
FIG. 10F is a cross-sectional view of the device shown inFIG. 10A shown in a deployed state. -
FIG. 10G is a perspective view of a gripper of the device shown inFIG. 10A shown in a retracted or undeployed state. -
FIG. 10H is a side elevation view of a gripper and actuator of the device shown inFIG. 10A shown in a retracted or undeployed state. -
FIG. 10I is a perspective view of a gripper and actuator of the device shown inFIG. 10A shown in a deployed state. -
FIG. 11A is perspective view of another embodiment of a bone fixation device shown in a retracted or undeployed state. -
FIG. 11B is perspective view of the device shown inFIG. 11A shown in a deployed state. -
FIG. 11C is a cross-sectional view of the device shown inFIG. 11A shown in a retracted or undeployed state. -
FIG. 11D is a cross-sectional view of the device shown inFIG. 11A shown in a deployed state. -
FIG. 12A shows an isometric side view of an exemplary embodiment of a bone fixation device hub. -
FIG. 12B shows a side view of the bone fixation device ofFIG. 12A . -
FIG. 12C shows a front view of the bone fixation device ofFIG. 12A . -
FIG. 12D shows back view of the bone fixation device ofFIG. 12A . -
FIG. 12E shows an isometric front view of the bone fixation device ofFIG. 12A . -
FIG. 12F shows a plan view of a surface on the bone fixation device ofFIG. 12A . -
FIG. 12G shows an isometric side view of the bone fixation device ofFIG. 12A implanted in a bone. -
FIG. 12H shows an isometric elevated view of the bone fixation device ofFIG. 12A implanted in a bone. -
FIG. 12I shows an isometric view of the bone fixation device ofFIG. 12A implanted in a bone. -
FIG. 13A shows an isometric side view of an another exemplary embodiment of a bone fixation device hub. -
FIG. 13B shows a side view of the bone fixation device ofFIG. 13A . -
FIG. 13C shows a front view of the bone fixation device ofFIG. 13A . -
FIG. 13D shows a back view of the bone fixation device ofFIG. 13A . -
FIG. 13E shows an isometric view of the bone fixation device ofFIG. 13A . -
FIG. 14A shows an isometric side view of another exemplary embodiment of a bone fixation device hub. -
FIG. 14B shows a side view of the bone fixation device ofFIG. 14A . -
FIG. 14C shows a front view of the bone fixation device ofFIG. 14A . -
FIG. 14D shows a back side view of the bone fixation device ofFIG. 14A . -
FIG. 14E shows an isometric side view of the bone fixation device ofFIG. 14A . -
FIG. 14F shows a close up view of a optional portion of the bone fixation device ofFIG. 14A . -
FIG. 15A shows an isometric side view of another exemplary embodiment of a bone fixation device hub. -
FIG. 15B shows a side view of the bone fixation device ofFIG. 15A . -
FIG. 15C shows a front view of the bone fixation device ofFIG. 15A . -
FIG. 15D shows a back view of the bone fixation device ofFIG. 15A . -
FIG. 16A shows an isometric side view of another exemplary embodiment of a bone fixation device hub. -
FIG. 16B shows an isometric front view of the bone fixation device ofFIG. 16A . -
FIG. 16C shows an isometric top view of the bone fixation device ofFIG. 16A . -
FIG. 16D shows a front view of the bone fixation device ofFIG. 16A . -
FIG. 16E shows an optional screw for use with the bone fixation device ofFIG. 16A . -
FIG. 17A shows an isometric side view of another exemplary embodiment of a bone fixation device hub. -
FIG. 17B shows a side view of the bone fixation device ofFIG. 17A . -
FIG. 17C shows a close up side view of the bone fixation device ofFIG. 17A . -
FIG. 18A shows an isometric side view of another exemplary embodiment of a bone fixation device hub. -
FIG. 18B shows a side view of the bone fixation device ofFIG. 18A . -
FIG. 19A shows an isometric side view of another exemplary embodiment of a bone fixation device hub. -
FIG. 19B shows a side view of the bone fixation device hub ofFIG. 19A . -
FIG. 20A shows an isometric side view of another exemplary embodiment of a bone fixation device hub. -
FIG. 20B shows an exploded side view of the bone fixation device ofFIG. 20A . - By way of background and to provide context for the invention, it may be useful to understand that bone is often described as a specialized connective tissue that serves three major functions anatomically. First, bone provides a mechanical function by providing structure and muscular attachment for movement. Second, bone provides a metabolic function by providing a reserve for calcium and phosphate. Finally, bone provides a protective function by enclosing bone marrow and vital organs. Bones can be categorized as long bones (e.g. radius, femur, tibia and humerus) and flat bones (e.g. skull, scapula and mandible). Each bone type has a different embryological template. Further each bone type contains cortical and trabecular bone in varying proportions. The devices of this invention can be adapted for use in any of the bones of the body as will be appreciated by those skilled in the art.
- Cortical bone (compact) forms the shaft, or diaphysis, of long bones and the outer shell of flat bones. The cortical bone provides the main mechanical and protective function. The trabecular bone (cancellous) is found at the end of the long bones, or the epiphysis, and inside the cortex of flat bones. The trabecular bone consists of a network of interconnecting trabecular plates and rods and is the major site of bone remodeling and resorption for mineral homeostasis. During development, the zone of growth between the epiphysis and diaphysis is the metaphysis. Finally, woven bone, which lacks the organized structure of cortical or cancellous bone, is the first bone laid down during fracture repair. Once a bone is fractured, the bone segments are positioned in proximity to each other in a manner that enables woven bone to be laid down on the surface of the fracture. This description of anatomy and physiology is provided in order to facilitate an understanding of the invention. Persons of skill in the art will also appreciate that the scope and nature of the invention is not limited by the anatomy discussion provided. Further, it will be appreciated there can be variations in anatomical characteristics of an individual patient, as a result of a variety of factors, which are not described herein. Further, it will be appreciated there can be variations in anatomical characteristics between bones which are not described herein.
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FIGS. 1 and 2 are perspective views of an embodiment of abone fixation device 100 having a proximal end 102 (nearest the surgeon) and a distal end 104 (further from surgeon) and positioned within the bone space of a patient according to the invention. In this example,device 100 is shown implanted in the upper (or proximal) end of anulna 106. The proximal end and distal end, as used in this context, refers to the position of an end of the device relative to the remainder of the device or the opposing end as it appears in the drawing. The proximal end can be used to refer to the end manipulated by the user or physician. The distal end can be used to refer to the end of the device that is inserted and advanced within the bone and is furthest away from the physician. As will be appreciated by those skilled in the art, the use of proximal and distal could change in another context, e.g. the anatomical context in which proximal and distal use the patient as reference, or where the entry point is distal from the surgeon. - When implanted within a patient, the device can be held in place with suitable fasteners such as wire, screws, nails, bolts, nuts and/or washers. The
device 100 is used for fixation of fractures of the proximal or distal end of long bones such as intracapsular, intertrochanteric, intercervical, supracondular, or condular fractures of the femur; for fusion of a joint; or for surgical procedures that involve cutting a bone. Thedevices 100 may be implanted or attached through the skin so that a pulling force (traction may be applied to the skeletal system). - In the embodiment shown in
FIG. 1 , the design of themetaphyseal fixation device 100 depicted is adapted to provide a bone engaging mechanism orgripper 108 adapted to engage target bone of a patient from the inside of the bone. As configured for this anatomical application, the device is designed to facilitate bone healing when placed in the intramedullary space within a post fractured bone. Thisdevice 100 has agripper 108 positioned distally and shown deployed radially outward against the wall of the intramedullary cavity. On entry into the cavity,gripper 108 is flat and retracted (FIG. 3 ). Upon deployment,gripper 108 pivots radially outward and grips the diaphyseal bone from the inside of the bone. One ormore screws 110 placed through apertures through thehub 112 lock thedevice 100 to the metaphyseal bone. Hence, the metaphysis and the diaphysis are joined. A flexible-to-rigid body portion 114 may also be provided, and in this embodiment is positioned betweengripper 108 andhub 112. It may be provided withwavy spiral cuts 116 for that purpose, as will be described in more detail below. -
FIG. 3 shows a longitudinal cross-section ofdevice 100 in a non-deployed configuration. In this embodiment,gripper 108 includes two pairs of opposing bendablegripping members 118. Two of the bendablegripping members 118 are shown inFIG. 3 , while the other two (not shown inFIG. 3 ) are located at the same axial location but offset by 90 degrees. Each bendable grippingmember 118 has a thinnedportion 120 that permits bending as the oppositedistal end 122 ofmember 118 is urged radially outward, such thatmember 118 pivots about thinnedportion 120. When extended, distal ends 122 ofbendable members 118 contact the inside of the bone to anchor the distal portion ofdevice 100 to the bone. In alternative embodiments (not shown), the gripper may comprise 1, 2, 3, 4, 5, 6 or more bendable members similar tomembers 118 shown. - During actuation,
bendable members 118 ofgripper 108 are urged radially outward by a ramped surface onactuator head 124.Actuator head 124 is formed on the distal end ofactuator 126. The proximal end ofactuator 126 is threaded to engage a threaded bore ofdrive member 128. The proximal end ofdrive member 128 is provided with akeyed socket 130 for receiving the tip of a rotary driver tool 132 (shown inFIG. 5 ) through the proximal bore ofdevice 100. Asrotary driver tool 132 turns drivemember 128,actuator 126 is drawn in a proximal direction to outwardly actuategripper members 118. - A
hemispherical tip cover 134 may be provided at the distal end of the device as shown to act as a blunt obturator. This arrangement facilitates penetration of bone (e.g. an intramedullary space) bydevice 100 while keeping the tip ofdevice 100 from digging into bone during insertion. - As previously mentioned,
device 100 may include one or more flexible-to-rigid body portions 114. This feature is flexible upon entry into bone and rigid upon application of compressive axial force provided by tensioningactuator 126. Various embodiments of a flexible-to-rigid portion may be used, including dual helical springs whose inner and outer tubular components coil in opposite directions, a chain of ball bearings with flats or roughened surfaces, a chain of cylinders with flats, features, cones, spherical or pointed interdigitating surfaces, wavy-helical cut tubes, two helical cut tubes in opposite directions, linear wires with interdigitating coils, and bellows-like structures. - The design of the flexible-to-rigid
tubular body portion 114 allows a single-piece design to maximize the transformation of the same body from a very flexible member that minimizes strength in bending to a rigid body that maximizes strength in bending and torsion. The flexible member transforms to a rigid member when compressive forces are applied in the axial direction at each end, such as by an actuator similar to 126. Thebody portion 114 is made, for example, by a near-helical cut 116 on a tubular member at an angle of incidence to the axis somewhere between 0 and 180 degrees from the longitudinal axis of thetubular body portion 114. The near-helical cut or wavy-helical cut may be formed by the superposition of a helical curve added to a cyclic curve that produces waves of frequencies equal or greater than zero per turn around the circumference and with cyclic amplitude greater than zero. The waves of one segment nest with those on either side of it, thus increasing the torque, bending strength and stiffness of the tubular body when subjective to compressive forces. The tapered surfaces formed by the incident angle allow each turn to overlap or interdigitate with the segment on either side of it, thus increasing the bending strength when the body is in compression. Additionally, the cuts can be altered in depth and distance between the cuts on the longitudinal axis along the length ofbody portion 114 to variably alter the flexible-to-rigid characteristics of the tubular body along its length. - The
cuts 116 inbody portion 114 allow an otherwise rigid member to increase its flexibility to a large degree during deployment. The tubular member can have constant or varying internal and external diameters. This design reduces the number of parts of the flexible-to-rigid body portion of the device and allows insertion and extraction of the device through a curved entry port in the bone while maximizing its rigidity once inserted. Application and removal of compressive forces provided by a parallel member such as wire(s), tension ribbons, a sheath, wound flexible cable, oractuator 126 as shown will transform the body from flexible to rigid and vice versa. - In operation, as
actuator 126 is tightened,gripper members 118 are extended radially outwardly. Once the distal ends ofgripper members 118 contact bone and stop moving outward, continued rotation ofactuator 126 draws theproximal end 102 and thedistal end 104 ofdevice 100 closer together untilcuts 116 are substantially closed. As this happens,body portion 114 changes from being flexible to rigid to better secure the bone fracture(s), as will be further described below. Rotatingdrive member 128 in the opposite direction causesbody portion 114 to change from a rigid to a flexible state, such as for removingdevice 100 if needed in the initial procedure or during a subsequent procedure after the bone fracture(s) have partially or completely healed.Body portion 114 may be provided with a solid longitudinal portion 136 (as best seen inFIGS. 3 and 9 ) such thatcuts 116 are a series of individual cuts each traversing less than 360 degrees in circumference, rather than a single, continuous helical cut. Thissolid portion 136 can aid in removal ofdevice 100 by keepingbody portion 114 from extending axially like a spring. -
FIG. 4 illustrates acombination tool 138 useful for insertingdevice 100, actuatinggripper 108, compressing flexible-to-rigid body portion 114, approximating the fracture inbone 106, aligning anchor screw(s) 110, and removingdevice 100, if desired. In this exemplary embodiment,tool 138 includes an L-shapedbody 140 that mounts the other components of the tool and also serves as a handle. The main components oftool 138 are adevice attachment portion 142, arotary driver 132, an approximatingdriver 144, and ascrew alignment portion 146. -
FIG. 5 shows a cross-section of thetool 138 anddevice 100 illustrated inFIG. 4 . As shown,device attachment portion 142 includes aknob 148 rigidly coupled to atube 150 which is rotatably mounted withinsleeve 152.Sleeve 152 in turn is fixedly mounted totool body 140. The distal end oftube 150 is provided with external threads for engaging the internal threads on the proximal end ofdevice 100. As best seen inFIG. 4 , both the distal end ofsleeve 152 and the proximal end ofdevice 100 may be provided with semicircular steps that inter-engage to preventdevice 100 from rotating with respect tosleeve 152. With this arrangement,device 100 can be prevented from rotating when it is secured totool 138 bytube 150 ofdevice attachment portion 142. The mating semicircular steps also serve to positiondevice 100 in a particular axial and angular orientation with respect totool 138 for aligning screws with screw holes, as will be later described. -
Rotary driver 132 may be used to actuategripper 108 and compress flexible-to-rigid body portion 114 afterdevice 100 is inserted intobone 106.Driver 132 may also be used to allowbody portion 114 to decompress andgripper 108 to retract if removal ofdevice 100 frombone 106 is desired. In the embodiment shown,driver 132 includesknob 154,torsion spring 156,hub 158,bushing 160 andshaft 162. The distal end ofshaft 162 is provided with amating tip 164, such as one having a hex-key shape, for engaging withkeyed socket 130 of device 100 (best seen inFIG. 3 ), such that turningdriver shaft 162 turns drivemember 128 and axially actuatesactuator 126, as described above. - The proximal end of
shaft 162 may be fitted with abushing 160, such as with a press-fit.Hub 158 may be secured overbushing 160, such as with a pin throughbushing 160 andshaft 162. In this embodiment,knob 154 is rotatably mounted overhub 158 andbushing 160 such thatknob 154 can rotate independently fromshaft 162. Atorsion spring 156 may be used to coupleknob 154 tohub 158 as shown to create a torque limiting and/or torque measuring driver. With this indirect coupling arrangement, asknob 154 is rotated aboutshaft 162,spring 156 urgeshub 158 andshaft 162 to rotate in the same direction. Rotational resistance applied bydevice 100 toshaft tip 164 will increase in this embodiment asgripper 108 engagesbone 106, and flexible-to-rigid body portion 114 compresses. As more torque is applied toknob 154, it will advance rotationally with respect tohub 158 astorsion spring 156 undergoes more stress. Markings may be provided onknob 154 andhub 158 to indicate the torque being applied. In this manner, a surgeon can usedriver 132 to apply torque todevice 100 in a predetermined range. This can help ensure thatgripper 108 is adequately set inbone 106,body portion 114 is sufficiently compressed, and excessive torque is not being applied that might damagedevice 100,bone 106 or cause slippage therebetween. A slip clutch or other mechanism may be provided to allow the applied torque to be limited or indicated. For example,driver 132 may be configured to “click” into or out of a detent position when a desired torque is reached, thus allowing the surgeon to apply a desired torque without needing to observe any indicia on the driver. In alternative embodiments, the driver knob may be selectably or permanently coupled toshaft 162 directly. - After
device 100 is inserted inbone 106 and deployed withtool 138 as described above, the approximatingdriver portion 144 oftool 138 may be used to compress one or more fractures inbone 106. Approximatingdriver 144 includesknob 166 located onsleeve 152.Knob 166 may be knurled on an outer circumference, and have threads on at least a portion of its axial bore. The internal threads ofknob 166 engage with mating external threads onsleeve 152 such that whenknob 166 is rotated it advances axially with respect tosleeve 152. Whendevice 100 is anchored inbone 106,sleeve 152 is prevented from moving away from the bone. Accordingly, asknob 166 is advanced axially towardbone 106, it serves to approximate bone fractures located betweengripper 108 andknob 166. Suitable thread pitch and knob circumference may be selected to allow a surgeon to supply a desired approximating force tobone 106 by using a reasonable rotation force onknob 166. In alternative embodiments (not shown), a torque indicating and/or torque limiting mechanism as described above may be incorporated into approximatingdriver 144. - As previously indicated,
tool 138 may also include ascrew alignment portion 146. In the embodiment depicted in the figures,alignment portion 146 includes aremovable alignment tube 168 and twobores tool body 140. In alternative embodiments (not shown), a single bore or more than two bores may be used, with or without the use of separate alignment tube(s). - In operation,
alignment tube 168 is first received inbore 170 as shown. In this position,tube 168 is in axial alignment withangled hole 174 at thedistal end 102 ofdevice 100. As described above, the mating semicircular steps ofdevice 100 andsleeve 152 positionangled hole 174 in its desired orientation. With this arrangement, a drill bit, screw driver, screw and/or other fastening device or tool may be inserted through the bore oftube 168 such that the device(s) are properly aligned withhole 174. The outward end ofalignment tube 168 may also serve as a depth guide to stop a drill bit, screw and/or other fastener from penetratingbone 106 beyond a predetermined depth. -
Alignment tube 168 may be withdrawn frombore 170 as shown, and inserted inbore 172. In this position,tube 168 aligns withhole 176 ofdevice 100. As described above, a drill bit, screw driver, screw and/or other fastening device may be inserted through the bore oftube 168 such that the device(s) are properly aligned withhole 176. -
FIG. 6 showsalignment tube 168 oftool 138 aligningscrew 110 withangled hole 174 at the distal end ofdevice 100, as described above. -
FIG. 7 shows afirst screw 110 received throughangled hole 174 and asecond screw 110 received throughhole 176 indevice 100 and intobone 106.Screws 110 may be installed manually or with the aid oftool 138 as described above. The heads ofscrews 110 may be configured to be self-countersinking such that they remain substantially beneath the outer surface of the bone when installed, as shown, so as to not interfere with adjacent tissue. In this embodiment, theproximal end 102 ofdevice 100 is secured tobone 106 with twoscrews 110, and thedistal end 104 is secured bygripper 108. In this manner, any bone fractures located between theproximal screw 110 anddistal gripper 108 may be approximated and rigidly held together bydevice 100. In alternative embodiments (not shown), more than one gripper may be used, or only screws or other fasteners without grippers may be used to securedevice 100 withinbone 106. For example, the device shown inFIG. 1 could be configured with a second gripper located betweenscrew 110 and the middle of the device if the fracture is located more at the mid-shaft of the bone. Similarly, more than two screws or other fasteners may be used, or only grippers without fasteners may be used. In various embodiments, holes such as 174 and 176 as shown and described above can be preformed in the implantable device. In other embodiments, some or all of the holes can be drilled or otherwise formed in situ after the device is implanted in the bone. - Once
device 100 is secured withinbone 106,combination tool 138 may be removed by turningknob 148 to disengage threads oftube 150 from threads within theproximal end 102 ofdevice 100. Anend plug 178 may be threaded into theproximal end 102 ofdevice 100 to preventing growth of tissue into implanteddevice 100.Device 100 may be left inbone 106 permanently, or it may be removed by performing the above described steps in reverse. In particular, plug 178 is removed,tool 138 is attached, screws 110 are removed,gripper 108 is retracted, anddevice 100 is pulled out usingtool 138. -
FIGS. 8 and 9 show alternative embodiments similar todevice 100 described above.Device 100′ shown inFIG. 8 is essentially identical todevice 100 described above but is shorter in length and utilizes asingle anchor screw 110 at itsproximal end 102.Device 100″ shown inFIG. 9 is similar todevice 100′, but is shorter still. In various embodiments, the devices may be configured to have a nominal diameter of 3 mm, 4 mm, 5 mm or 6 mm. It is envisioned that all threedevice designs - In accordance with the various embodiments of the present invention, the device may be made from a variety of materials such as metal, composite, plastic or amorphous materials, which include, but are not limited to, steel, stainless steel, cobalt chromium plated steel, titanium, nickel titanium alloy (nitinol), superelastic alloy, and polymethylmethacrylate (PMMA). The device may also include other polymeric materials that are biocompatible and provide mechanical strength, that include polymeric material with ability to carry and delivery therapeutic agents, that include bioabsorbable properties, as well as composite materials and composite materials of titanium and polyetheretherketone (PEEK™), composite materials of polymers and minerals, composite materials of polymers and glass fibers, composite materials of metal, polymer, and minerals.
- Within the scope of the present invention, each of the aforementioned types of device may further be coated with proteins from synthetic or animal source, or include collagen coated structures, and radioactive or brachytherapy materials. Furthermore, the construction of the supporting framework or device may include radio-opaque markers or components that assist in their location during and after placement in the bone or other region of the musculo-skeletal systems.
- Further, the reinforcement device may, in one embodiment, be osteo incorporating, such that the reinforcement device may be integrated into the bone. In a further embodiment, there is provided a low weight to volume device deployed in conjunction with other suitable materials to form a composite structure in-situ. Examples of such suitable materials may include, but are not limited to, bone cement, high density polyethylene, Kapton®, polyetheretherketone (PEEK™), and other engineering polymers.
- Once deployed, the device may be electrically, thermally, or mechanically passive or active at the deployed site within the body. Thus, for example, where the device includes nitinol, the shape of the device may be dynamically modified using thermal, electrical or mechanical manipulation. For example, the nitinol device may be expanded or contracted once deployed, to move the bone or other region of the musculo-skeletal system or area of the anatomy by using one or more of thermal, electrical or mechanical approaches.
- It is contemplated that the inventive implantable device, tools and methods may be used in many locations within the body. Where the proximal end of a device in the anatomical context is the end closest to the body midline and the distal end in the anatomical context is the end further from the body midline, for example, on the humerus, at the head of the humerus (located proximal, or nearest the midline of the body) or at the lateral or medial epicondyle (located distal, or furthest away from the midline); on the radius, at the head of the radius (proximal) or the radial styloid process (distal); on the ulna, at the head of the ulna (proximal) or the ulnar styloid process (distal); for the femur, at the greater trochanter (proximal) or the lateral epicondyle or medial epicondyle (distal); for the tibia, at the medial condyle (proximal) or the medial malleolus (distal); for the fibula, at the neck of the fibula (proximal) or the lateral malleoulus (distal); the ribs; the clavicle; the phalanges; the bones of the metacarpus; the bones of the carpus; the bones of themetatarsus; the bones of the tarsus; the sternum and other bones, the device may be adapted and configured with adequate internal dimension to accommodate mechanical fixation of the target bone and to fit within the anatomical constraints. As will be appreciated by those skilled in the art, access locations other than the ones described herein may also be suitable depending upon the location and nature of the fracture and the repair to be achieved. Additionally, the devices taught herein are not limited to use on the long bones listed above, but can also be used in other areas of the body as well, without departing from the scope of the invention. It is within the scope of the invention to adapt the device for use in flat bones as well as long bones.
-
FIGS. 10A-10I show another embodiment of a bone fixation device constructed according to aspects of the invention.FIG. 10A is a perspective view showing theexemplary device 200 deployed in a fracturedclavicle 202.Device 200 is similar todevice 100 described above and shown inFIGS. 1-7 , but has agripper 204 located near its proximal end, anothergripper 206 located at a more distal location, and a flexible-to-rigid body portion 208 located near the distal end of the device. Abone screw 210 andgripper 204 are configured to securedevice 200 insidebone 202 on the proximal side offracture 212, whilegripper 206 and flexible-to-rigid body portion 208 are configured to securedevice 200 on the distal side offracture 212. In other respects, construction and operation ofdevice 200 is much like that ofdevice 100 described above. - In this exemplary embodiment, each of the two
grippers arms 214. These arms are spaced at 90 degree intervals around the circumference of the device body. Thearms 214 ofgripper 204 may be offset by 45 degrees fromarms 214 ofgripper 206 as shown in the figures to distribute the forces applied bygrippers bone 202. As shown inFIGS. 10E and 10F , asingle actuator 216 may be used to deploy bothgrippers Actuator 216 may also be used to axially compress flexible-to-rigid body portion 208 to make it substantially rigid. At least a portion ofactuator 216 may be flexible to allow flexible-to-rigid body portion 208 to assume a curved shape, as best seen inFIGS. 10A and 10B . Alternatively, it may be desirable in some embodiments to have flexible-to-rigid body portion 208 maintain a straight or a curved configuration regardless of whether it is in a flexible or rigid state. In these embodiments, the actuator may be rigid and faulted with the desired straight and/or curved shape to match the flexible-to-rigid body portion. In some embodiments, it may also be desirable to design at least a portion of the actuator with a high degree of axial elasticity to allow the actuator to continue to expand some gripper(s) and/or compress some flexible-to-rigid body portion(s) after other gripper(s) and/or flexible-to-rigid body portion(s) have already been fully deployed. - Referring to
FIGS. 10G-10I , further details of anexemplary gripper 204 are shown.FIGS. 10G and 10H show gripper 204 withbendable arms 214 in a retracted state. Ascam 218 ofactuator 216 is driven axially into the distal ramped ends ofarms 214,arms 214 bend at thinnedportions 220 to move radially outward toward the deployed position shown inFIG. 10I .Notches 222 may be provided in the distal ends ofarms 214 as shown to allowarms 214 to better grip interior bone surfaces. Without departing from the scope of the invention, one, two, three, or more bendable arms may be used. - Referring to
FIGS. 11A-11D , another embodiment of a bone fixation device is shown.Device 300 includes acurved hub 302,proximal gripper 304, flexible-to-rigid body portion 306, anddistal gripper 308.Distal gripper 308 is similar in construction and operation to grippers 204 and 206 described above.Proximal gripper 304 is provided with three pairs ofscissor arms 310. Each pair ofarms 310 is pivotably interconnected at a mid-portion by a pin. Each arm is pivotably connected with a pin to eitherproximal end piece 312 ordistal end piece 314. Whenend pieces arms 310 pivot radially outward from an axially aligned retracted position, as shown inFIGS. 11A and 11C , to a deployed position, as shown inFIGS. 11B and 11D . In the deployed position, the distal ends of the sixarms 310 engage an inner surface of a bone as previously described. - In operation,
device 300, withgrippers Device 300 may be inserted through a curved opening formed in the bone, such as an opening formed through a bony protuberance on a distal or proximal end or through the midshaft of the bone.Curved hub 302 may be configured with the same geometry of the curved opening in the bone, and when the flexible-to-rigid body portion 306 is in its flexible state, it can assume this same geometry. Oncedevice 300 is in place inside the bone, actuator 315 (shown inFIGS. 11C and 11D ) may be actuated from the proximal end ofdevice 300 by turningdrive member 317 in a manner similar to that previously described. Longitudinal movement ofactuator 315 toward the proximal end ofdevice 300 causes flexible-to-rigid body portion 306 to foreshorten and assume its rigid state, and causesgrippers holes 316 shown incurved hub 302 to secure the proximal end ofdevice 300 to the bone. Further details of the construction and operation of a device similar todevice 300 may be found in co-pending U.S. application Ser. No. 11/944,366 filed Nov. 21, 2007 and entitled Fracture Fixation Device, Tools and Methods. -
Device 300 is an example of an embodiment utilizing mixed gripper types. In other words, this device uses one scissors-arm tripod gripper 304 and one bendable-arm gripper 308. Other embodiments of the invention (not shown) use various combinations of gripper(s) and/or flexible-to-rigid body portion(s). Further exemplary gripper embodiments are described in detail in co-pending U.S. application Ser. No. 61/100,652 filed Sep. 26, 2008 and entitled Fracture Fixation Device, Tools and Methods. It is envisioned that virtually any combination of zero, one, two, or more grippers may be used in combination with zero, one, two or more flexible-to-rigid body portions to form a device adapted to a particular bone anatomy, fracture, disease state or fixation purpose. The grippers and/or flexible-to-rigid body portions may each be of identical or different construction, and may be placed together or at other locations along the device. Further, a straight, curved, flexible, rigid, or no hub at all may be used with the above combinations. Additionally, screws, K-wires, sutures or no additional fixation may be used with these various devices. The devices may be specially designed and constructed for a particular purpose or range of purposes. According to aspects of the invention, the components may also be designed to be interchangeable and/or produced in various sizes so that surgical kits may be provided. Such kits would allow surgical teams to select from a variety of components to build devices themselves, each suited to a particular patient's unique situation. - Referring to
FIGS. 12A through 20B , further examples of the hubs discussed above are shown and will now be described. -
FIGS. 12A-12F show details of acurved hub 400 similar tohub 302 illustrated inFIGS. 11A-11D . In this embodiment,hub 400 has an internally threaded portion at itsproximal end 402 for engaging with an insertion and removal tool as described above. (The proximal end is referenced as the end closest to the surgeon.) Theproximal end 402 may also have a keyed feature for mating with the tool for maintaining a desired orientation ofhub 400 relative to the tool.Hub 400 may also be provided with a counterbore at itsdistal end 404 for coupling to a gripper or flexible-to-rigid body portion, such as by press fit and/or welding. -
Exemplary hub 400 includes threeholes FIG. 12C . Similarly,hub 400 includes fourholes FIG. 12D . At least a portion of all seven holes may be seen inFIG. 12F .Holes hub 400 are aligned to allow a bone screw to be inserted through the two holes across the hub to securehub 400 to the bone and/or to secure bone fragment(s) with the screw. Similarly, holes 408 and 414 are aligned to receive a second bone screw, and holes 410 and 416 are aligned to receive a third bone screw. A fourth screw may be inserted through the openproximal end 402 ofhub 400 and out throughhole 418. Each screw may be passed first through cortical bone, then cancellous bone, then through the two holes ofhub 400, through more cancellous bone and possibly into more cortical bone on the opposite side of the bone from where the screw entered. - In this embodiment, the holes of
hub 400 have a diameter of 2.4 mm. In other embodiments, the holes have a diameter of 2.7 mm. In still other embodiments, the holes may have larger or smaller diameters. The holes may be threaded during the fabrication ofhub 400, or threads may be formed in vivo. Various fixtures, jigs, tools and methods may be used to align the screws with the holes, such as a tool similar totool 138 shown inFIGS. 4-6 and described above. Further examples of positioning aids are provided in copending U.S. application Ser. No. 11/944,366 filed Nov. 21, 2007 and entitled Fracture Fixation Device, Tools and Methods. The heads of the screws may be countersunk into the bone as described in copending U.S. application Ser. No. 61/117,901 filed Nov. 25, 2008 and entitled Bone Fracture Fixation Screws, Systems and Methods of Use. -
FIGS. 12G-12I illustrate an example how bone screws 420, 422, 424 may be inserted throughhub 400′ (which is similar to hub 400) as described above to secure the comminuted fracture depicted at the distal end of aradius bone 425. One, two, three, four, or more screws may be used depending on the anatomy and fracture condition of each particular case. It should be noted that in this particular embodiment, either screw 422 or 424 may be placed throughhub 400′, but not both at the same time, as their paths intersect insidehub 400′. It can be seen that screws 422 and 424 extend acrossfracture 426 intobone fragment 428. Accordingly, either screw 422 or 424 may be used toapproximate fracture 426 when the screw is tightened. -
FIGS. 13A-13E show another exemplary embodiment of a bonefixation device hub 450.Hub 450 is of similar construction tohub 400 described above and includesproximal end 452 anddistal end 454. As best seen inFIG. 13C ,hub 450 includes fourholes Holes distal end 454, but are symmetrically located on opposite sides of a central longitudinal plane. As can be seen, holes 456 and 458 actually overlap to form a single, figure-eight shaped hole.Holes proximal end 452, and are symmetrically located on opposite sides of a central longitudinal plane. - As best seen in
FIG. 13D ,hub 450 also includes sixholes Holes distal end 454, but are symmetrically located on opposite sides of a central longitudinal plane.Holes holes Holes proximal end 452, and are symmetrically located on opposite sides of a central longitudinal plane. Similarly, holes 472 and 474 are also located the same longitudinal distance fromproximal end 452, and are symmetrically located on opposite sides of a central longitudinal plane. -
Holes hub 450 are aligned to allow a bone screw to be inserted through the two holes across the hub, passing through a centerline ofhub 450. Similarly, holes 458 and 466 on diagonally opposite sides ofhub 450 are aligned to allow a bone screw to be inserted through the two holes across the hub, passing through a centerline ofhub 450. Since both of these two screw paths cross the centerline at the same location forming an X-pattern, only one screw may be placed through these two pairs ofholes 456/464 and 458/466 in any particular procedure. - In a similar manner, holes 460 and 468 on diagonally opposite sides of
hub 450 are aligned to allow a bone screw to be inserted through the two holes across the hub, passing through a centerline ofhub 450.Holes hub 450 are also aligned to allow a bone screw to be inserted through the two holes across the hub, passing through a centerline ofhub 450. Since both of these two screw paths cross the centerline at the same location forming an X-pattern, only one screw may be placed through these two pairs ofholes 460/468 and 462/470 in any particular procedure. - A third screw may be inserted through the open
proximal end 452 ofhub 450 and out through eitherhole 472 orhole 474. Since these two screw paths also overlap, only one screw may be placed though them at a time. - As can be appreciated from
FIGS. 13A-13E and the description above,exemplary hub 450 is symmetrical about a central plane. Sincehub 450 may receive up to three screws, each in one of two positions, there are a total of eight screw patterns that may be used withhub 450, depending on the situation. Additionally, only one or two screws, or no screws, may be used in a particular procedure, if desired. The positions and orientations of the screw holes ofhub 450 relative to previously describedhub 400 may take better advantage of cortical bone locations in some procedures for better anchoring of bone screws. In particular, a screw passing through hole pairs 456/464, 458/466, 460/468 or 462/470 ofhub 450 will have a reduced angle relative to a longitudinal axis of a bone as compared with the screw trajectories of similar screws inhub 400. Similarly, a screw passing through eitherhole hub 400, which in many cases allows the screw ofhub 450 to hit harder bone. Additionally, screw paths of hole pairs 460/468 and 462/470 are closer to the proximal end ofhub 450 than similar screw paths inhub 400, allowing the screws to fixate in harder bone located near the end of a bone. All of the new screw trajectories provided byhub 450 may be used with the in vivo hole forming hubs that will be later described below. The trajectories of hole pairs 456/464, 458/466, 460/468 or 462/470 also form an angle with a central, longitudinal plane containing the curve of hub 450 (in other words, a plane of symmetry of the hole pairs.) In some embodiments, the hole pairs each form an angle with the plane falling in a range of about 5 to 30 degrees. -
FIGS. 14A-14E show another exemplary embodiment of a bonefixation device hub 500.Hub 500 is of similar construction tohubs proximal end 502 anddistal end 504. As best seen inFIG. 14C ,hub 500 includes slottedholes - thickness on its concave side. As best seen in
FIG. 14D ,hub 500 also includes slottedholes angled hole 518 through the wall thickness on its convex side.Holes hub 500 are aligned to allow a first bone screw to be inserted through the two holes across the hub. Similarly, holes 508 and 514 are aligned to receive a second bone screw, and holes 510 and 516 are aligned to receive a third bone screw.Hole 518 is aligned with the opening in theproximal end 502 ofhub 500 to receive a fourth bone screw. - The slotted configuration of hole pairs 506/512, 508/514, and 510/516 allows a bone screw to be received through each of the pairs in a variety of orientations. This arrangement permits a surgeon the flexibility to place bone screws where most appropriate in a particular procedure. For example, a first bone screw may be placed through
holes hole 506, as viewed inFIG. 14C . The same screw will have another section that may reside in the left, middle, or right portion ofhole 512. With these various combinations, it can be appreciated that the screw can take one of nine basic orientations throughholes - In this exemplary embodiment, the width of slotted
holes FIG. 14F , relief slit(s) 520 may be provided adjacent to a slottedhole 506 to allow the slot to more easily expand when receiving ascrew 522. Such slits may be formed by laser cutting, electron beam melting (EBM), electrical discharge machining (EDM), etching, stamping, milling, or other fabrication techniques. -
FIGS. 15A-15D show another exemplary embodiment of a bonefixation device hub 500′.Hub 500′ is similar tohub 500 described above, but has slotted holes that are oriented longitudinally rather than transversely.Hub 500′ includesproximal end 502′ anddistal end 504′. As best seen inFIG. 15C ,hub 500′ includes slottedholes 506′, 508′, and 510′ through the wall thickness on its concave side. As best seen inFIG. 15D ,hub 500′ also includes slottedholes 512′, 514′, and 516′, andangled hole 518′ through the wall thickness on its convex side.Holes 506′ and 512′ on opposite sides ofhub 500′ are aligned to allow a first bone screw to be inserted through the two holes across the hub. Similarly, holes 508′ and 514′ are aligned to receive a second bone screw, and holes 510′ and 516′ are aligned to receive a third bone screw.Hole 518′ is aligned with the opening in theproximal end 502′ ofhub 500′ to receive a fourth bone screw.Exemplary axis lines FIG. 15A to show examples paths for the first, second, third, and fourth screws, respectively. -
FIGS. 16A-16E show another exemplary embodiment of a bonefixation device hub 550. As best seen inFIG. 16D ,hub 550 includes at its proximal end 552 a transverselyelongated hole 554.Hole 554 allows ascrew 556 to be located along the central axis, or off-axis in either direction as may be desired for engaging harder bone or securing additional bone fragment(s). This of arrangement ofhole 554 may be configured to holdscrew 556 tightly at all angles. This may be accomplished, for example, by using ahole 554 slot width that is equal to or smaller than the minor diameter ofscrew 556. The wall thickness ofhub 550 may fit into the screw threads, providing additional locking ofscrew 556. In other embodiments, the angle ofelongated hole 554 may be oriented differently as desired. - Special screws may be used to provide additional locking. As shown in
FIG. 16E ,screw 558 has a taperededge 560 below itshead 562.Tapered edge 560 serves to wedgescrew 558 intoslot 554, securing the screw in place. A screw with an expanding head (not shown) may also be used. With this arrangement, a taper or other expanded section may be created once the screw is in place, thereby locking it in position. -
FIGS. 17A-17C show another exemplary embodiment of abone fixation hub 600.Hub 600 is provided with an array ofpilot holes 602 over most of its surface. Eachhole 602 may be 0.015 to 0.020 inches in diameter, for example, and serves as a starting point to allow a drill bit or screw tip to penetrate the wall thickness ofhub 600. This makes in vivo screw hole formation possible, while allowing the hub to remain a rigid structure.Holes 602 may be closely spaced such that a screw or screws may be positioned in vivo virtually anywhere the surgeon desires during each particular procedure. Once the drill bit and/or screw is inserted, thehole 602 becomes enlarged to generally the minor diameter of the screw thread, such as to 2.7 mm in diameter, for example. Screw holes may be formed in this way on both sides ofhub 600 in a continuous operation, allowing screw(s) to be positioned across the hub as previously described. - As shown in
FIG. 17C ,pilot holes 602 may be placed closer to one another so that multiple perforations are consumed by thescrew diameter 604 when the screw hole is formed. This can make in vivo hole formation even easier. Other hole patterns than those shown inFIGS. 17A-17C may be used. -
Holes 602 may be fabricated inhub 600 by laser cutting, electron beam melting (EBM), electrical discharge machining (EDM), etching, stamping, drilling, or other fabrication techniques. -
FIGS. 18A and 18B show another exemplary embodiment of abone fixation hub 650.Hub 650 has at least a portion that is fabricated from a mesh structure, forming a plurality of diamond or other shapedapertures 652.Apertures 652 may be configured with dimensions smaller than the major diameter of the threads of the bone screws to be used. Aperture dimensions may even be smaller than the minor thread diameter, such that the apertures are stretched and/or deformed as the screw enters the aperture, thereby providing an increased ability to hold the screws in place. The use of amesh hub 650 may reduce the amount or possibility of debris being formed and released inside the body during in vivo screw hole formation. -
Apertures 652 may be fabricated inhub 650 by laser cutting, electron beam melting (EBM), electrical discharge machining (EDM), etching, stamping, drilling, or other fabrication techniques.Apertures 652 may also be fabricated by forming slits in plate or tube stock and expanding the material to form the apertures. Another fabrication technique that may be used is forming wires or bands around a mandrel and then welding, brazing, soldering, pressing, melting, gluing, or otherwise joining the wires or bands to each other at their intersections. Other types of porous structures, either with or without more random aperture locations, may be used as well. Multiple layers of mesh may also be combined. -
FIGS. 19A and 19B show another exemplary embodiment of abone fixation hub 700.Hub 700 is provided with a plurality ofthin slots 702 along its length.Slots 702 permit in vivo screw hole formation by acting as long pilot holes for drill bits or bone screws. A bone screw tip may be inserted into one of theslots 702 without pre-drilling. Upon insertion, the slot and surrounding slots will deform to make way for the screw, and will provide circumferential pressure to retain the screw. - Although shown staggered and in the longitudinal direction, in other embodiments (not shown) thin slots may be provided in a transverse or other orientation, and/or in other patterns.
Slots 702 may be fabricated inhub 700 by laser cutting, electron beam melting (EBM), electrical discharge machining (EDM), etching, stamping, drilling, or other fabrication techniques.Thin slots 702 may generally require less material removal than other hub embodiments. -
FIGS. 20A and 20B show another exemplary embodiment of abone fixation hub 750.Hub 750 comprises three separately formed hubs assembled together: aninner hub 752, a mid-hub 754, and anouter hub 756.Mid-hub 754 has a larger diameter thaninner hub 752 so that mid-hub 754 may be placed overinner hub 752, as illustrated inFIGS. 20A and 20B . Similarly,outer hub 756 has a larger diameter than mid-hub 754 so thatouter hub 756 may be placed overmid-hub 754, as also illustrated in the figures. In this embodiment, all threehub components hub components - As seen in
FIG. 20B ,inner hub 752 andouter hub 756 have spirally formedslots Slots hub FIG. 20B ). The spines are solid regions running the length of the hubs that provide rigidity, and are positioned in areas that do not typically receive screws.Mid-hub 754 has longitudinally extendingslots 766 rather than spiral slots. When the three slot patterns are assembled in a coaxial unit, as shown inFIG. 20A , a hub is formed that may be quite rigid. Pilot holes are formed whereslots - One, two, three, four, or more hub layers may be used in this manner to form a single layer or composite hub. Other slot patterns and widths may be used as appropriate. Some of the layers may incorporate round or other aperture shapes instead of or in addition to the slots shown in this example.
- In many of the hub embodiments described above, one or more screws may be placed into just a single side of the hub, or completely across the hub through both sides.
- While exemplary embodiments of the present invention have been shown and described herein, it will be obvious to those skilled in the art that such embodiments are provided by way of example only. Numerous variations, changes, and substitutions will now occur to those skilled in the art without departing from the invention. It should be understood that various alternatives to the embodiments of the invention described herein may be employed in practicing the invention.
Claims (20)
1. (canceled)
2. An implantable bone fixation device comprising:
an elongate hub comprising a mesh structure and a tubular portion,
wherein the mesh structure comprises a flexible state and a locked state,
wherein the tubular portion is proximal of the mesh structure,
the tubular portion comprising a wall with an outer surface and an inner surface, the outer surface with a round cross-sectional shape, the inner surface with a round cross-sectional shape,
wherein the wall extends along the mesh structure, the mesh structure comprising a plurality of apertures over at least a portion of the outer surface,
wherein the plurality of apertures are configured to deform to hold a fastener connected to the hub; and
an actuator operably connected to the elongate hub for changing the mesh structure from the flexible state to the locked state.
3. The implantable bone fixation device of claim 2 , wherein the flexible state comprises any of the group of bending, stretching, and deforming a material of the mesh structure.
4. The implantable bone fixation device of claim 2 , wherein the mesh structure takes on a rigid state in the locked state.
5. The implantable bone fixation device of claim 2 , wherein the mesh structure comprises a plurality of diamond shaped apertures.
6. The implantable bone fixation device of claim 2 , wherein at least one aperture expands upon receipt of said fastener to a diameter of 2.7 mm.
7. The implantable bone fixation device of claim 2 , wherein the tubular portion is rigid.
8. The implantable bone fixation device of claim 2 , wherein the mesh structure comprises at least two layers, each layer comprising a plurality of apertures.
9. The implantable bone fixation device of claim 8 , wherein at least a portion of the plurality of apertures in a second layer of the mesh structure overlap a portion of the plurality of apertures in a first layer of the mesh structure.
10. The implantable bone fixation device of claim 9 , wherein at least one aperture forms a pilot hole in the elongate hub.
11. An implantable bone fixation device comprising:
an elongate body having a flexible state, a rigid state, and a tubular portion,
the elongate body comprising an outer surface and an inner surface of a tubular wall, the tubular wall comprising an array of holes over a portion of the outer surface, each of the holes being configured to expand upon receipt of a fastener there-through, wherein the elongate body comprises a mesh structure forming the array of holes; and
an actuator operably connected to the elongate body for changing the elongate body from the flexible state to the rigid state,
wherein a first position of the actuator places the elongate body in the flexible state and a second position of the actuator places the elongate body in the rigid state.
12. The implantable bone fixation device of claim 11 , wherein said holes are longitudinally formed.
13. The implantable bone fixation device of claim 11 , wherein at least one hole is elongated to form a slot.
14. The implantable bone fixation device of claim 11 , wherein the rigid state is a locked state.
15. The implantable bone fixation device of claim 11 , wherein the flexible state comprises any of the group of bending, stretching, and deforming a material of the elongate body.
16. The implantable bone fixation device of claim 11 , wherein the rigid state comprises limiting any of the group of bending, stretching, and deforming the material of the elongate body.
17. The implantable bone fixation device of claim 11 , wherein the elongate body comprises at least two layers, each layer comprising an array of slots, wherein the slots of the layers overlap to form the array of holes in the elongate body.
18. The implantable bone fixation device of claim 17 , wherein each layer comprises a separately formed mesh structure.
19. The implantable bone fixation device of claim 11 , wherein at least one hole expands upon receipt of said fastener to a diameter of 2.7 mm.
20. The implantable bone fixation device of claim 11 , wherein the tubular portion is rigid.
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