STEERABLE CURVABLE VERTEBROPLASTY DRILL
Disclosed herein is a steerable and curvable drill that can be used for various applications including vertebroplasty. The drill can include an elongate, tubular body, having a proximal end, a distal end, and a central lumen extending therethrough; a deflectable zone on the distal end of the tubular body including one or more laser cuts, deflectable through an angular range; an insertable wire insertable into at least a portion of the central lumen of the elongate, tubular body; a handle on the proximal end of the tubular body; a deflection control on the handle; a drill control on the handle; a drive shaft within the elongate tubular body having a proximal end and a distal end; and a boring element on the distal end of the device for creating a cavity within bone. The boring element can be operably connected to the distal end of the drive shaft via a crimping mechanism. Systems and methods involving the drill are also disclosed.
This application claims priority under 35 U.S.C. §120 as a continuation application of U.S. patent application Ser. No. 12/983,771 filed on Jan. 3, 2011, which is in turn a continuation application of U.S. patent application Ser. No. 12/784,422 filed on May 20, 2010, which is a continuation-in-part of U.S. patent application Ser. No. 12/469,611 filed on May 20, 2009. All of the aforementioned priority applications are hereby incorporated by reference in their entireties.
BACKGROUND OF THE INVENTIONAccording to the National Osteoporosis Foundation ten million Americans have osteoporosis, and an estimated 34 million with low bone mass are at risk of developing osteoporosis (http://www.nof.org/osteoporosis/diseasefacts.htm). Called the “silent disease,” OSP develops slowly over a number of years without symptoms. Eighty percent of those affected are women, particularly petite Caucasian and Asian women, although older men and women of all races and ethnicities are at significant risk.
In the United States, 700,000 people are diagnosed with vertebral compression fractures as a result of OSP each year. Morbidity associated with vertebral fractures includes severe back pain, loss of height and deformity, all of which negatively affect quality of life.
Once microfracture of the vertebra begins, there is little the clinician can do except palliative medical treatment using analgesics, bed rest and/or restriction of activity. With time, the microfractures widen at one level and without surgical intervention, the fractures cascade downward with increasing kyphosis or “hunching” of the back. Once a mechanical lesion develops, surgery is the only option. Vertebroplasty or kyphoplasty are the primary minimally-invasive surgical procedures performed for the treatment of compression-wedge fractures due to OSP.
Vertebroplasty stabilizes the collapsed vertebra by injecting polymethylmethacrylate (PMMA) or a substantially equivalent bone cement into cancellous bone space of the vertebrae. Besides providing structural support to the vertebra, the exothermic reaction of PMMA polymerization is said to kill off the nociceptors or pain receptors in the bone, although no proof of this hypothesis has been provided in the literature. This procedure is typically performed as an outpatient procedure and requires only a short-acting local or general anesthetic. Once the surgical area of the spine is anesthetized, the physician inserts one or two needles through small skin incisions into either the pedicle (uni-transpedicular) or the pedicles of the vertebral body i.e., bi-transpedicular. PMMA is injected through the needle and into the cancellous-bone space of the vertebra.
Kyphoplasty mirrors the vertebroplasty procedure but has the additional step of inserting and expanding a nylon balloon in the interior of the vertebral body. Expansion of the balloon under pressure reduces the compression fracture and creates a cavity. After withdrawal of the balloon, PMMA is injected into the cavity to stabilize the reduction. The kyphoplasty procedure may restore the vertebral body height. Kyphoplasty is an in-patient surgery that requires hospitalization and a general anesthetic. Kyphon Inc. claims over 275,000 spinal fractures have been treated using their PMMA derivative and their “balloon” kyphoplasty procedure worldwide (Sunnyvale, Calif., Sep. 5, 2006, (PR NEWSWIRE) Kyphon study 2006).
Bone cement for both vertebroplasty and kyphoplasty procedures currently employ variations of standard PMMA in a powder and a methyl methacrylate monomer liquid. When the powder and liquid monomer are mixed, an exothermic polymerization takes place resulting in the formation of a “dough-like” material, which is then inserted into the cancellous bone space. The dough, when hardened, becomes either the reinforcing structure or the grout between the bone and prosthesis.
The average clinical in vivo life of the PMMA grout is approximately 10 years due to corrosion fatigue of either the bone-cement/prosthesis and/or the bone cement/bone interfaces. Jasty et al. (1991) showed that in cemented total hip replacements: “Fractures in the cement mantle itself were found on cut sections around all prostheses which had been in use for over three years.” Jasty et al. also noted: “In general, specimens less than 10 years in situ showed small incomplete fractures while the specimens in place more than 10 years all showed large complete cement mantle fractures.”
When an implant fails, a revision becomes mandatory. After removal of the cement and hardware, a cemented arthroplasty can be repeated if enough cancellous bone matrix exists to grip the new PMMA. Alternatively, cement-less prosthesis can be installed. Such a revision, however, can only be applied to total joint replacement failures. For vertebroplasty and/or kyphoplasty, a classical screw and plate internal fixation with autograft fusion is necessary.
Despite advances in the foregoing procedures, there remains a need for improved bone cement delivery systems which enable rapid and controllable deployment of bone cement for the treatment of conditions such as vertebral compression fractures.
SUMMARY OF THE INVENTIONSome embodiments of the present invention relate to a steerable and curvable vertebroplasty drill comprising a proximal handle and a distal elongate body. This distal elongate body is divided into a relatively rigid proximal portion that is coaxial with the handle, and a flexible distal portion capable of being deflected to an angle relative to the proximal portion. At the distal end of the device there is a boring element that can penetrate bone or other tissue. This boring element is turned by a drive shaft that is operably coupled to a knob, crank, or other device turned by the operator. Motorized steerable and curvable vertebroplasty drills are also within the scope of the invention.
In some embodiments, the operator can control the angle of deflection of the boring element, the distal end of the elongate body, and the portion of the drive shaft therein, relative to that of the proximal end of the elongate body and handle. The deflection of the distal end can be controlled by turning a portion of the handle that is threadably engaged with a second portion of the handle. The rotation of these two parts of the handle separates these components, thereby increasing the overall length of the handle as well as the overall length of the device itself. This increase in the length of the device increases the tension exerted by a pull wire that is proximally affixed near the proximal portion of the handle, and distally affixed near the distal end of the elongate body. As the tension exerted by this pull wire on the flexible distal end of the elongate body increases, the distal end can be deflected, and the angle of actuation of the boring element adjusted. In some embodiments, the distal end of the elongate body can passively return to a coaxial configuration relative to the proximal end of the elongate body when the tension on the pull wire is reduced by rotating the handle in the other direction and thereby reducing the overall length of the handle.
In some embodiments, the drive shaft is capable of a degree of axial motion so as to keep the drive shaft operably coupled with the crank, handle, motor or other source of power despite the changes in the length of the handle.
Within the scope of the present invention is a method of treating bone using the steerable and curvable vertebroplasty drill. In some embodiments, this method comprises the creation of a cavity in a vertebral body by creating an access channel, inserting an introducer cannula, inserting the steerable and curvable vertebroplasty drill through the cannula, and drilling through cancellous bone in the interior of the vertebral body. By changing the deflection angle of the distal end of the device, multiple cavities can be drilled at different angles from a single insertion site and angle of approach. The cavity thereby created can then be filled with bone cement or other compounds following the withdrawal of the device.
In some embodiments, the steerable and curvable vertebroplasty drill can be part of a vertebroplasty kit that further comprises devices to mix various bone cement compounds, devices to inject the bone cement into the bone cavity, devices to facilitate the insertion of the steerable and curvable vertebroplasty drill into the patient's body, and various other devices to facilitate the performance of surgical procedures involving the device herein disclosed.
In some embodiments, a steerable and curvable vertebroplasty drill is provided. The drill comprises an elongate tubular body having a proximal end, a distal end, and a central lumen extending therethrough; a handle on the proximal end of the tubular body, the handle comprising a deflection control for deflecting a deflectable zone on a distal end of the tubular body; and a drive shaft housed in the central lumen of the tubular body, the drive shaft including a distal portion comprising one or more slit apertures on the surface of the drive shaft. The slit apertures can be helical, or can comprise chevrons. An angular distance between the slit apertures can be 90 degrees. A pitch of the slit apertures can be between 0.055″ and 0.075″. The drill can further comprise an insertable wire insertable through a lumen of the drive shaft and configured to provide radial support to the distal portion of the drive shaft comprising one or more slits. The insertable wire can comprise Nitinol. The drive shaft can be configured to flex via the slit apertures upon flexing of the deflectable zone of the tubular body.
In some embodiments, a steerable and curvable vertebroplasty drill is provided. The drill comprises an elongate tubular body having a proximal end, a distal end and a central lumen extending therethrough; a first crimp member on the distal end of the tubular body; a boring member; and a second crimp member on the boring member, wherein the second crimp member is configured to be interlocking with the first crimp member to form a single continuous body between the tubular body and boring member. The elongate tubular body can comprise a drive shaft. The first crimp member can comprise a plurality of raised surfaces. The second crimp member can comprise a plurality of apertures for receiving the raised surfaces.
In some embodiments, a method of treating a bone is provided. The method comprises creating an access channel to access the interior of a vertebral body; inserting an introducer cannula into the access channel; inserting a steerable and curvable drill through the introducer cannula into the interior of the vertebral body, the steerable and curvable drill comprising an elongate body having a proximal end and a distal end, the distal end comprising a deflectable zone; rotating a control to deflect the deflectable zone of the steerable and curvable drill in the vertebral body; removing the steerable and curvable drill from the interior of the vertebral body; and flowing bone cement through an injection needle into the interior of the vertebral body.
The present invention provides improved delivery systems for delivery of a bone cement or bone cement composite for the treatment of vertebral compression fractures due to osteoporosis (OSP), osteo-trauma, and benign or malignant lesions such as metastatic cancers and myeloma, and associated access and deployment tools and procedures.
The primary materials in the preferred bone cement composite are methyl methacrylate and inorganic cancellous and/or cortical bone chips or particles. Suitable inorganic bone chips or particles are sold by Allosource, Osteotech and LifeNet (K053098); all have been cleared for marketing by FDA The preferred bone cement also may contain the additives: barium sulfate for radio-opacity, benzoyl peroxide as an initiator, N,N-dimethyl-p-toluidine as a promoter and hydroquinone as a stabilizer. Other details of bone cements and systems are disclosed in U.S. patent application Ser. No. 11/626,336, filed Jan. 23, 2007, the disclosure of which is hereby incorporated in its entirety herein by reference.
One preferred bone cement implant procedure involves a two-step injection process with two different concentrations of the bone particle impregnated cement. To facilitate the implant procedure the bone cement materials are packaged in separate cartridges containing specific bone cement and inorganic bone particle concentrations for each step. Tables 1 and 2, infra, list one example of the respective contents and concentrations in Cartridges 1A and 1B for the first injection step, and Cartridges 2A and 2B for the second injection step.
The bone cement delivery system generally includes at least three main components: 1) stylet; 2) introducer cannula; and 3) steerable and curvable injection needle. See
The stylet is used to perforate a hole into the pedicle of the vertebra to gain access to the interior of the vertebral body.
The introducer cannula is used for bone access and as a guide for the steerable and curvable injection needle. The introducer cannula is sized to allow physicians to perform vertebroplasty or kyphoplasty on vertebrae with small pedicles such as the thoracic vertebra T5 as well as larger vertebrae. In addition, this system is designed for uni-transpedicular access and/or bi-pedicular access.
Once bone access has been achieved, the steerable and curvable injection needle can be inserted through the introducer cannula into the vertebra. The entire interior vertebral body may be accessed using the steerable and curvable injection needle. The distal end of the needle can be manually shaped to any desired radius within the product specifications. The radius is adjusted by means of a knob on the proximal end of the device.
The hand-held cement dispensing pump may be attached to the steerable and curvable injection needle by a slip-ring luer fitting. The pre-filled 2-chambered cartridges (1A and 1B, and 2A and 2B) are loaded into the dispensing pump. As the handle of the dispensing pump is squeezed, each piston pushes the cartridge material into the spiral mixing tube. The materials are mixed in the spiral mixing nozzle prior to entering the steerable and curvable injection needle. The ratio of diameters of the cartridge chambers determines the mixing ratio for achieving the desired viscosity.
The bone cement implant procedures described herein use established vertebroplasty and kyphoplasty surgical procedures to stabilize the collapsed vertebra by injecting bone cement into cancellous bone.
The preferred procedure is designed for uni-transpedicular access and may be accomplished under either a local anesthetic or short-duration general anesthetic. Once the area of the spine is anesthetized, an incision is made and the stylet is used to perforate the vertebral pedicle and gain access to the interior of the vertebral body. The introducer cannula is then inserted and acts as a guide for the steerable and curvable injection needle.
Injection of the preferred bone cement involves a two-step procedure. The pre-filled Cartridges 1A and 1B are loaded into the dispensing pump. As the dispensing pump handle is squeezed, each piston pushes material into the spiral mixing tube. The diameter of each chamber may be utilized to determine the mixing ratio for achieving the desired viscosity.
The first step involves injecting a small quantity of PMMA with more than about 35%, e.g., 60% inorganic bone particles, onto the outer periphery of the cancellous bone matrix, i.e., next to the inner wall of the cortical bone of the vertebral body. The cement composite is designed to harden relatively quickly, forming a firm but still pliable shell. This shell is intended to prevent bone marrow/PMMA content from being ejected through any venules or micro-fractures in the vertebral body wall. The second step of the procedure involves a second injection of PMMA with an approximately 30% inorganic bone particles to stabilize the remainder of the weakened, compressed cancellous bone.
Alternatively, the steerable and curvable needle disclosed herein and discussed in greater detail below, can be used in conventional vertebroplasty procedures, using a single step bone cement injection.
Injection control for the first and second steps is provided by a 2 mm ID flexible injection needle, which is coupled to the hand operated bone cement injection pump. The 60% (>35%) and 30% ratio of inorganic bone particle to PMMA concentrations may be controlled by the pre-filled cartridge sets 1A and 1B, and 2A and 2B. At all times, the amount of the injectate is under the direct control of the surgeon or intervention radiologist and visualized by fluoroscopy. The introducer cannula is slowly withdrawn from the cancellous space as the second injection of bone cement begins to harden, thus preventing bone marrow/PMMA content from exiting the vertebral body. The procedure concludes with closure of the surgical incision with bone filler. In vitro and in vivo studies have shown that the 60% (>35%) bone-particle impregnated bone cement hardens in 2-3 minutes and 30% bone-particle impregnated bone cement hardens between 4 to 10 minutes.
Details of the system components will be discussed below.
There is provided in accordance with the present invention a steerable and curvable injection device that can be used to introduce any of a variety of materials or devices for diagnostic or therapeutic purposes. In one embodiment, the system is used to inject bone cement, e.g., PMMA or any of the bone cement compositions disclosed elsewhere herein. The injection system most preferably includes a tubular body with a steerable and curvable (i.e., deflectable) distal portion for introducing bone cement into various locations displaced laterally from the longitudinal axis of the device within a vertebral body during a vertebroplasty procedure.
Referring to
The manifold 18 is additionally provided with a control 26 such as a rotatable knob, slider, or other moveable control, for controllably deflecting a deflection zone 24 on the distal end 16 of the tubular body 12. As is described elsewhere herein, the deflection zone 24 may be advanced from a relatively linear configuration as illustrated in
Referring to
The central lumen 38 has an inside diameter which is adapted to slideably axially receive the steerable and curvable injection needle 10 therethrough. This enables placement of the distal end 34 adjacent a treatment site within the body, to establish an access pathway from outside of the body to the treatment site. As will be appreciated by those of skill in the art, the introducer 30 enables procedures deep within the body such as within the spine, through a minimally invasive and/or percutaneous access. The steerable and curvable injection needle 10 and/or other procedure tools may be introduced into port 40, through lumen 38 and out of port 42 to reach the treatment site.
The proximal end 32 of introducer 30 may be provided with a handle 44 for manipulation during the procedure. Handle 44 may be configured in any of a variety of ways, such as having a frame 46 with at least a first aperture 48 and a second aperture 50 to facilitate grasping by the clinician.
Referring to
As will be appreciated by those of skill in the art, the stylet 60 has an outside diameter which is adapted to coaxially slide within the central lumen on introducer 30. When block 68 is nested within recess 70, a distal end 64 of stylet 60 is exposed beyond the distal end 34 of introducer 30. The distal end 64 of stylet 60 may be provided with a pointed tip 72, such as for anchoring into the surface of a bone.
Referring to
The shaft 702 defines at least one lumen therethrough that is preferably configured to carry a flowable bone cement prior to hardening. Proximal portion 710 of shaft 702 is preferably relatively rigid, having sufficient column strength to push through cancellous bone. Distal portion 712 of shaft 702 is preferably flexible and/or deflectable and reversibly actuatable between a relatively straight configuration and one or more deflected configurations or curved configurations as illustrated, for example, in
Input port 704 may be provided with a Luer lock connector although a wide variety of other connector configurations, e.g., hose barb or slip fit connectors can also be used. Lumen 705 of input port 704 is fluidly connected to central lumen 720 of shaft 702 such that material can flow from a source, through input port 704 into central lumen 720 of the shaft 702 and out the open distal end or out of a side opening on distal portion 712. Input port 704 is preferably at least about 20 gauge and may be at least about 18, 16, 14, or 12 gauge or larger in diameter.
Input port 704 advantageously allows for releasable connection of the steerable and curvable injection device 700 to a source of hardenable media, such as a bone cement mixing device described herein. In some embodiments, a plurality of input ports 704, such as 2, 3, 4, or more ports are present, for example, for irrigation, aspiration, introduction of medication, hardenable media precursors, hardenable media components, catalysts or as a port for other tools, such as a light source, cautery, cutting tool, visualization devices, or the like. A first and second input port may be provided, for simultaneous introduction of first and second bone cement components such as from a dual chamber syringe or other dispenser. A mixing chamber may be provided within the injection device 700, such as within the proximal handle, or within the tubular shaft 702
A variety of adjustment controls 706 may be used with the steerable and curvable injection system, for actuating the curvature of the distal portion 712 of the shaft 702. Preferably, the adjustment control 706 advantageously allows for one-handed operation by a physician. In one embodiment, the adjustment control 706 is a rotatable member, such as a thumb wheel or dial. The dial can be operably connected to a proximal end of an axially movable actuator such as pull wire 724. See
In some embodiments, the adjustment control 706 allows for continuous adjustment of the curvature of the distal portion 712 of shaft 702 throughout a working range. In other embodiments, the adjustment control is configured for discontinuous (i.e., stepwise) adjustment, e.g., via a ratcheting mechanism, preset slots, deflecting stops, a rack and pinion system with stops, ratcheting band (adjustable zip-tie), adjustable cam, or a rotating dial of spring loaded stops. In still other embodiments, the adjustment control 706 may include an automated mechanism, such as a motor or hydraulic system to facilitate adjustment.
The adjustment control may be configured to allow deflection of the distal portion 712 through a range of angular deviations from 0 degrees (i.e., linear) to at least about 15°, and often at least about 25°, 35°, 60°, 90°, 120°, 150°, or more degrees from linear.
In some embodiments, the length X of the flexible distal portion 712 of shaft 702 is at least about 10%, in some embodiments at least about 15%, 25%, 35%, 45%, or more of the length Y of the entire shaft 702 for optimal delivery of bone cement into a vertebral body. One of ordinary skill in the art will recognize that the ratio of lengths X:Y can vary depending on desired clinical application. In some embodiments, the maximum working length of needle 702 is no more than about 15″, 10″, 8″, 7″, 6″, or less depending upon the target and access pathway. In one embodiment, when the working length of needle 702 is no more than about 8″, the adjustable distal portion 712 of shaft has a length of at least about 1″ and preferably at least about 1.5″ or 2″.
In some embodiments, the slots 718 can be machined or laser cut out of the tube stock that becomes shaft 702, and each slot may have a linear, chevron or other shape. In other embodiments, the distal portion 712 of shaft 702 may be created from an elongate coil rather than a continuous tube.
Slots 718 provide small compression hinge joints to assist in the reversible deflection of distal portion 712 of shaft 702 between a relatively straightened configuration and one or more curved configurations. One of ordinary skill in the art will appreciate that adjusting the size, shape, and/or spacing of the slots 718 can impart various constraints on the radius of curvature and/or limits of deflection for a selected portion of the distal portion 712 of shaft 702. For example, the distal portion 712 of shaft 702 may be configured to assume a second, fully deflected shape with a relatively constant radius of curvature throughout its length. In other embodiments, the distal portion 712 may assume a progressive curve shape with a variable radius of curvature which may, for example, have a decreasing radius distally. In some embodiments, the distal portion may be laterally displaced through an arc having a radius of at least about 0.5″, 0.75″, 1.0″, 1.25″, or 1.5″ minimum radius (fully deflected) to ∞ (straight) to optimize delivery of bone cement within a vertebral body. Wall patterns and deflection systems for bendable slotted tubes are disclosed, for example, in U.S. Patent Publication No. 2005/0060030 A1 to Lashinski et al., the disclosure of which is incorporated in its entirety by reference herein.
Still referring to
A distal opening 728 is provided on shaft 702 in communication with central lumen 720 to permit expression of material, such as bone cement, from the injector 700. Some embodiments may include a filter such as mesh 812. Mesh structure 812 can advantageously control cement output by controlling bubbles and/or preventing undesired large or unwieldy aggregations of bone cement from being released at one location and thus promote a more even distribution of bone cement within the vertebral body. The mesh 812 may be created by a laser-cut cris-crossing pattern within distal end as shown, or can alternatively be separately formed and adhered, welded, or soldered on to the distal opening 728. Referring to
In some embodiments, the distal shaft 712 can generate a lateral force of at least about 0.125 pounds, 0.25 pounds, 0.5 pounds, 1 pound, 1.5 pounds, 2 pounds, 3 pounds, 4 pounds, 5 pounds, 6 pounds, 7 pounds, 8 pounds, 9 pounds, 10 pounds, or more by activating control 706. This can be advantageous to ensure that the distal portion 712 is sufficiently navigable laterally through cancellous bone to distribute cement to the desired locations. In some embodiments, the distal shaft 712 can generate a lateral force of at least about 0.125 pounds but no more than about 10 pounds; at least about 0.25 pounds but no more than about 7 pounds; or at least about 0.5 pounds but no more than about 5 pounds.
In some embodiments, the distal portion 712 of shaft 702 (or end cap 730) has visible indicia, such as, for example, a marker visible via one or more imaging techniques such as fluoroscopy, ultrasound, CT, or MRI.
The distal curved portion 734 may be configured to be axially movably received within an outer tubular sheath 738. The sheath 738 is preferably configured to have sufficient rigidity and radial strength to maintain the curved distal portion 734 of shaft 732 in a relatively straightened configuration while the outer tubular sheath 738 coaxially covers the curved distal portion 734. Sheath 738 can be made of, for example, a metal such as stainless steel or various polymers known in the catheter arts. Axial proximal withdrawal of the sheath 738 with respect to tubular shaft 736 will expose an unconstrained portion of the shape memory distal end 734 which will revert to its unstressed arcuate configuration. Retraction of the sheath 738 may be accomplished by manual retraction by an operator at the proximal end, retraction of a pull wire attached to a distal portion of the sheath 738, or other ways as known in the art. The straightening function of the outer sheath 738 may alternatively be accomplished using an internal stiffening wire, which is axially movably positionable within a lumen extending through the tubular shaft 736. The length, specific curvature, and other details of the distal end may be as described elsewhere herein.
In another embodiment, as shown in
Introducer 800 includes a needle-redirecting element 804 such as an inclined surface near its distal end. Needle-redirecting element 804 can be, for example, a laser-cut tang or a plug having a proximal surface configured such that when needle 802 is advanced distally into introducer 800 and comes in contact with the needle-redirecting element 804, a distal portion 814 of needle 802 is redirected out an exit port 806 of introducer 800 at an angle 808, while proximal portion 816 of needle 802 remains in a relatively straightened configuration, as shown in
The illustrated embodiment of
The interior sleeve 709 is preferably in the form of a continuous, tubular flexible material, such as nylon or polyethylene. In an embodiment in which the needle 702 has an outside diameter of 0.095 inches (0.093 inch coil with a 0.001 inch thick outer sleeve) and an inside diameter of 0.077 inches, the interior tubular sleeve 709 may have an exterior diameter in the area of about 0.074 inches and an interior diameter in the area of about 0.069 inches. The use of this thin walled tube 705 on the inside of the needle shaft 702 is particularly useful for guiding a fiber through the needle shaft 702. The interior tube 705 described above is additionally preferably fluid-tight, and can be used to either protect the implements transmitted therethrough from moisture, or can be used to transmit bone cement through the steerable and curvable needle.
In some embodiments, an outer tubular coating or sleeve (not shown) is provided for surrounding the steerable and curvable needle shaft at least partially throughout the distal end of the needle. The outer tubular sleeve may be provided in accordance with techniques known in the art and, in one embodiment, is a thin wall polyester (e.g., ABS) heat shrink tubing such as that available from Advanced Polymers, Inc. in Salem, N.H. Such heat shrink tubings have a wall thickness of as little as about 0.0002 inches and tube diameter as little as about 0.010 inches. The outer tubular sleeve enhances the structural integrity of the needle, and also provides a fluid seal and improved lubricity at the distal end over embodiments with distal joints 718. Furthermore, the outer tubular sleeve tends to prevent the device from collapsing under a proximal force on a pull wire. The sleeve also improves pushability of the tubular members, and improves torque transmission.
In other embodiments, instead of a slotted tube, the needle shaft of a vertebroplasty injection system may include a metal or polymeric coil. Steerable and curvable helical coil-type devices are described, for example, in U.S. Pat. No. 5,378,234 or 5,480,382 to Hammerslag et al., which are both incorporated by reference herein in their entirety.
An interior tubular sleeve (not illustrated) may be provided to facilitate flow of media through the central lumen as described elsewhere in the application. In some embodiments, a heat-shrink outer tubular sleeve as described elsewhere in the application is also provided to enhance the structural integrity of the sheath, provide a fluid seal across the chevrons or slots, as well as improve lubricity.
The steerable and curvable injection needle (also referred to as the injection shaft) may have an outside diameter, of between about 8 to 24 gauge, more preferably between about 10 to 18 gauge, e.g., 12 gauge, 13 gauge (0.095″ or 2.41 mm), 14 gauge, 15 gauge, or 16 gauge. In some embodiments, the inside diameter (luminal diameter) of the injection needle is between about 9 to 26 gauge, more preferably between about 11 to 19 gauge, e.g., 13 gauge, 14 gauge, 15 gauge, 16 gauge, or 17 gauge. In some embodiments, the inside diameter of the injection needle is no more than about 4 gauge, 3 gauge, 2 gauge, or 1 gauge smaller than the outside diameter of the injection needle.
The inside luminal diameter of all of the embodiments disclosed herein is preferably optimized to allow a minimal exterior delivery profile while maximizing the amount of bone cement that can be carried by the needle. In one embodiment, the outside diameter of the injection needle is 13 gauge (0.095″ or 2.41 mm) with a 0.077″ (1.96 mm) lumen. In some embodiments, the percentage of the inside diameter with respect to the outside diameter of the injection needle is at least about 60%, 65%, 70%, 75%, 80%, 85%, or more.
Referring to
Input port 704 is in fluid communication with a distal opening 728 on a distal tip 730, by way of an elongate central lumen 720. Input port 704 may be provided with any of a variety of releasable connectors, such as a luer or other threaded or mechanically interlocking connector known in the art. Bone cement or other media advanced through lumen 720 under pressure may be prevented from escaping through the plurality of slots 718 in the steering region 24 by the provision of a thin flexible tubular membrane carried either by the outside of tubular shaft 702, or on the interior surface defining central lumen 720.
Referring to
Slider 734 is provided with at least one axially extending keyway or spline 742 for slideably engaging a slide dowel pin 744 linked to the handle 708. This allows rotation of the rotatable control 706, yet prevents rotation of the slider 734 while permitting axial reciprocal movement of the slider 734 as will be apparent to those of skill in the art. One or more actuating knob dowel pins 746 permits rotation of the rotatable control 706 with respect to the handle 708 but prevents axial movement of the rotatable control 706 with respect to the handle 708.
Referring to
In general, the distal tip 730 includes a proximal opening 750 for receiving media from the central lumen 720, and advancing media through distal opening 728. Distal opening 728 may be provided on a distally facing surface, on a laterally facing surface, or on an inclined surface of the distal tip 730.
Referring to
Referring to
In the illustrated embodiment, the inclined aperture 728 is defined by an aperture plane 772 intersecting the longitudinal axis 770 at an angle θ which is at least about 5°, often at least about 15°, and in many embodiments, at least about 25° or more. Intersection angles within the range of from about 15° to about 45° may often be used, depending upon the desired clinical performance.
Referring to
Referring to
Referring to
In use, the distal tip 730 may be distally advanced through soft tissue, cortical or cancellous bone, with the distal opening 728 being maintained in a closed orientation. Following appropriate positioning of the distal tip 30, the introduction of bone cement or other media under pressure through the central lumen 720 forces the distal opening 728 open by radially outwardly inclining each leaflet 758 about its flection point 762. This configuration enables introduction of the needle without “coring” or occluding with bone or other tissue, while still permitting injection of bone cement or other media in a distal direction.
Any of the forgoing or other tip configurations may be separately formed and secured to the distal end of the tubular body 702, or may be machined, molded or otherwise formed integrally with the tube 702. Other examples of tip configurations that can be used with injectors as described herein are illustrated and described in connection with FIGS. 15I to 15Y of U.S. Provisional Application No. 61/300,401 filed on Feb. 1, 2010, which is hereby incorporated by reference in its entirety.
Alternatively, a distal opening aperture may be occluded by a blunt plug or cap, which prevents coring during distal advance of the device. Once positioned as desired, the distal cap may be pushed off of the distal end of the injector such as under the pressure of injected bone cement. The deployable cap may take any of a variety of forms depending upon the injector design. For example, it may be configured as illustrated in
As a further alternative, coring during insertion of an injector having a distal opening may be prevented by positioning a removable obturator in the distal opening. The obturator comprises an elongate body, extending from a proximal end throughout the length of the injector to a blunt distal tip. The obturator is advanced axially in a distal direction through the central lumen, until the distal tip of the obturator extends slightly distally of the distal opening in the injector. This provides a blunt atraumatic tip for distal advance of the injector through tissue. Following positioning of the injector, the obturator may be proximally withdrawn from the central lumen, and discarded. The obturator may be provided with any of a variety of structures for securing the obturator within the central lumen during the insertion step, such as a proximal cap for threadably engaging a complementary luer connector on the proximal opening of the central lumen.
In accordance with another aspect of the present invention, there is provided a combination device in which a steerable and curvable injector is additionally provided with a cavity formation element. Thus, the single device may be advanced into a treatment site within a bone, expanded to form a cavity, and used to infuse bone cement or other media into the cavity. Either or both of the expansion step and the infusion step may be accomplished following or with deflection of the distal portion of the injector.
Referring to
The slots 308 oppose a column strength element such as an axially extending spine 310, for resisting axial elongation or compression of the device. A pull wire 312 axially moveably extends throughout the length of the tubular body, and is secured with respect to the tubular body distally of the transverse slots 308. The proximal end of the pull wire is operatively connected to a control on a proximal handpiece or manifold. The control may be any of a variety of structures, such as a lever, trigger, slider switch or rotatable thumb wheel or control knob. Axial proximal traction (or distal advance) of the pull wire 312 with respect to the tubular body causes a lateral deflection of the distal steering section 306, by axial compression or expansion of the transverse slots 308 relative to the spine 310.
A distal aperture 314 is in communication via a central lumen 316 with the proximal end of the steerable and curvable injector 300. Any of a variety of tip configurations may be used such as those disclosed elsewhere herein. The proximal end of the central lumen 316 may be provided with a luer connector, or other connection port to enable connection to a source of media such as bone cement to be infused. In the illustrated embodiment, the aperture 314 faces distally from the steerable and curvable injector 302, although other exit angles may be used as will be discussed below.
The steerable and curvable injector 300 is optionally provided with a cavity forming element 320, such as an inflatable balloon 322. In the illustrated embodiment, the inflatable balloon 322 is positioned in the vicinity of the steerable and curvable distal section 306. Preferably, the axial length of a distal leading segment 307 is minimized, so that the balloon 322 is relatively close to the distal end of the steerable and curvable injector 300. In this embodiment, the plurality of transverse slots 308 are preferably occluded, to prevent inflation media from escaping into the central lumen 316 or bone cement or other injectable media from escaping into the balloon 322. Occlusion of the transverse slots 308 may be accomplished in any of variety of ways, such as by positioning a thin tubular membrane coaxially about the exterior surface of the tubular body and heat shrinking or otherwise securing the membrane across the openings. Any of a variety of heat shrinkable polymeric sleeves, comprising high density polyethylene or other materials, are well known in the catheter arts. Alternatively, a tubular liner may be provided within the central lumen 316, to isolate the central lumen from the transverse slots 308.
The balloon 322 is secured at a distal neck 309 to the leading segment 307 as is understood in the balloon catheter arts. The distal neck 309 may extend distally from the balloon, as illustrated, or may invert and extend proximally along the tubular body. In either event, the distal neck 309 of the balloon 322 is preferably provided with an annular seal 324 either directly to the tubular body 301 or to a polymeric liner positioned concentrically about the tubular body, depending upon the particular device design. This will provide an isolated chamber within balloon 322, which is in fluid communication with a proximal source of inflation media by way of an inflation lumen 326.
In the illustrated embodiment, the balloon 322 is provided with an elongate tubular proximal neck which extends throughout the length of the steerable and curvable injector 300, to a proximal port or other site for connection to a source of inflation media. This part can be blow molded within a capture tube as is well understood in the balloon catheter arts, to produce a one piece configuration. Alternatively, the balloon can be separately formed and bonded to a tubular sleeve. During assembly, the proximal neck or outer sleeve 328 may conveniently be proximally slipped over the tubular body 301, and secured thereto, as will be appreciated by those of skill in the catheter manufacturing arts.
Referring to
Referring to
As a further alternative, the distal aperture or apertures 314 may be provided in any of a variety of configurations on a distal cap or tip, adapted to be secured to the tubular body.
The steerable and curvable injection systems described above are preferably used in conjunction with a mixing and dispensing pump for use with a multi-component cement. In some embodiments, a cement dispensing pump is a hand-held device having an interface such as a tray or chamber for receiving one or more cartridges. In one embodiment, the pump is configured to removably receive a double-barreled cartridge for simultaneously dispensing first and second bone cement components. The system additionally includes a mixing chamber, for mixing the components sufficiently and reproducibly to fully automate the mixing and dispensing process within a closed system.
Bone cement components have conventionally been mixed, such as by hand, e.g., in mixing bowls in the operating room, which can be a time-consuming and unelegant process. The devices disclosed herein may be used with conventional bone cement formulations, such as manually mixed liquid-powder PMMA formulations. Alternatively, the use of a closed mixing device such as a double-barreled dispensing pump as disclosed herein is highly advantageous in reducing bone cement preparation time, preventing escape of fumes or ingredients, ensuring that premature cement curing does not occur (i.e., the components are mixed immediately prior to delivery into the body), and ensuring adequate mixing of components.
Two separate chambers contain respective materials to be mixed in a specific ratio. Manual dispensing (e.g., rotating a knob or squeezing a handle) forces both materials into a mixing nozzle, which may be a spiral mixing chamber within or in communication with a nozzle. In the spiral mixing nozzle, all or substantially all mixing preferably occurs prior to the bone cement entering the steerable and curvable injection needle and, subsequently, into the vertebra. The cement dispensing hand pump may be attached to the steerable and curvable injection needle permanently, or removably via a connector, such as slip-ring Luer fittings. A wide range of dispensing pumps can be modified for use with the present invention, including dispensing pumps described in, for example, U.S. Pat. Nos. 5,184,757, 5,535,922, 6,484,904, and Patent Publication No. 2007/0114248, all of which are incorporated by reference in their entirety.
Currently favored bone cement compositions are normally stored as two separate components or precursors, for mixing at the clinical site shortly prior to implantation. As has been described above, mixing of the bone cement components has traditionally been accomplished manually, such as by expressing the components into a mixing bowl in or near the operating room. In accordance with the present invention, the bone cement components may be transmitted from their storage and/or shipping containers, into a mixing chamber, and into the patient, all within a closed system. For this purpose, the system of the present invention includes at least one mixing chamber positioned in the flow path between the bone cement component container and the distal opening on the bone cement injection needle. This permits uniform and automated or semi-automated mixing of the bone cement precursors, within a closed system, and thus not exposing any of the components or the mixing process at the clinical site.
Thus, the mixing chamber may be formed as a part of the cartridge, may be positioned downstream from the cartridge, such as in-between the cartridge and the proximal manifold on the injection needle, or within the proximal manifold on the injection needle or the injection needle itself, depending upon the desired performance of the device. The mixing chamber may be a discrete component which may be removably or permanently coupled in series flow communication with the other components of the invention, or may be integrally formed within any of the foregoing components.
In general, the mixing chamber includes an influent flow path for accommodating at least two bone cement components. The first and second incoming flow path are combined, and mixing structures for facilitating mixing of the components are provided. This may include any of a variety of structures, such as a helical flow path, baffles and or additional turbulence inducing structures.
Tables 1-2 below depict the contents and concentrations of one exemplary embodiment of bone cement precursors. Chambers 1A and 1B contain precursors for a first cement composition for distribution around the periphery of the formed in place vertebral body implant with a higher particle concentration to promote osteoinduction, as discussed previously in the application. Chambers 2A and 2B contain precursors for a second cement composition for expression more centrally within the implanted mass within the vertebral body, for stability and crack arresting, as discussed previously in the application.
One of ordinary skill in the art will recognize that a wide variety of chamber or cartridge configurations, and bone cements, can be used with the present injection system. For example, in one embodiment, a first cartridge includes pre-polymerized PMMA and a polymerization catalyst, while a second cartridge includes a liquid monomer of MMA as is common with some conventional bone cement formulations.
In some embodiments, the contents of two cartridges can be combined into a single cartridge having multiple (e.g., four) chambers. Chambers may be separated by a frangible membrane (e.g., 1A and 2A in a first cartridge and 1B and 2B in a second cartridge, each component separated by the frangible membrane or other pierceable or removable barrier). In other embodiments, contents of the below cartridges can be manually pre-mixed and loaded into the input port of the injection system without the use of a cement mixing dispenser.
As illustrated in
The stylet may have a diameter of between about 0.030″ to 0.300″, 0.050″ to about 0.200″ and preferably about 0.100″ in some embodiments. The introducer cannula 800 is between about 8-14 gauge, preferably between about 10-12 gauge, more preferably 11 gauge in some embodiments. The introducer cannula 800, which may be made of any appropriate material, such as stainless steel (e.g., 304 stainless steel) may have a maximum working length of no more than about 12″, 8″, or 6″ in some embodiments. One or two or more bone cement cartridges, each having one or two or more chambers, may also be provided. Various other details of the components have been described above in the application.
One embodiment of a method for delivering bone cement into a vertebral body is now described, and illustrated in
The cement implantation procedure is designed for uni-transpedicular access and generally requires either a local anesthetic or short-duration general anesthetic for minimally invasive surgery. Once the area of the spine is anesthetized, as shown in
Once bone access has been achieved, as shown in
The actual injection procedure may utilize either one or two basic steps. In a one step procedure, a homogenous bone cement is introduced as is done in conventional vertebroplasty. The first step in the two step injection involves injection of a small quantity of PMMA with more than about 35%, e.g., 60% particles such as inorganic bone particles onto the periphery of the treatment site, i.e., next to the cortical bone of the vertebral body as shown in
Injection control for the first and second steps is provided by an approximately 2 mm inside diameter flexible introducer cannula 800 coupled to a bone cement injection pump (not shown) that is preferably hand-operated. Two separate cartridges containing respective bone cement and inorganic bone particle concentrations that are mixed in the 60% and 30% ratios are utilized to control inorganic bone particle to PMMA concentrations. The amount of the injectate is under the direct control of the surgeon or interventional radiologist by fluoroscopic observation. The introducer cannula 800 is slowly withdrawn from the cancellous space as the bolus begins to harden, thus preventing bone marrow/PMMA content from exiting the vertebral body 1308. The procedure concludes with the surgical incision being closed, for example, with bone void filler 1306 as shown in
The foregoing method can alternatively be accomplished utilizing the combination steerable and curvable needle of
At any time in the process, whether utilizing an injection needle having a cavity formation element or not, the steerable and curvable injector may be proximally withdrawn or distally advanced, rotated, and inclined to a greater degree or advanced into its linear configuration, and further distally advanced or proximally retracted, to position the distal opening 314 at any desired site for infusion of additional bone cement or other media. More than one cavity, such as two, or three or more, may be sequentially created using the cavity formation element, as will be appreciated by those of skill in the art.
The aforementioned bone cement implant procedure process eliminates the need for the external mixing of PMMA powder with MMA monomer. This mixing process sometimes entraps air in the dough, thus creating porosity in the hardened PMMA in the cancellous bone area. These pores weaken the PMMA. Direct mixing and hardening of the PMMA using an implant procedure such as the above eliminates this porosity since no air is entrapped in the injectate. This, too, eliminates further weakening, loosening, or migration of the PMMA.
Steerable, Curvable Vertebroplasty DrillAlso disclosed herein is a steerable and curvable drill that can be used to drill through tissue, such as bone, in a wide variety of applications including vertebroplasty or kyphoplasty. In some embodiments, prior to or concurrent with an orthopedic procedure such as vertebroplasty or kyphoplasty, it may be advantageous to remove bone, such as sclerotic cancellous bone, in order to facilitate adequate filling of the interior of a vertebral body with bone cement or to create or enhance cavity formation in a kyphoplasty procedure. Systems, devices, and methods to facilitate removal of such tissue such as sclerotic cancellous bone will now be described.
Referring to
In some embodiments, as illustrated, rotation of the front handle 901 relative to the mid-handle 905 increases the tension on one or more internal pull wires 903 that can exert a force on the distal end of the laser cut tube 923 and thereby adjust the curvature of the distal segment 923 thus defining an angle between the longitudinal axis of the proximal portion 924 of the elongate member 902 and the longitudinal axis of the distal segment 923 of the elongate member 902.
As illustrated in
In some embodiments, the elongate member 902 of the drill 900 may have an outside diameter of between about 8 to 24 gauge, more preferably between about 10 to 18 gauge, e.g., 12 gauge, 13 gauge (0.095″ or 2.41 mm), 14 gauge, 15 gauge, or 16 gauge. In some embodiments, the inside diameter (luminal diameter) is between about 9 to 26 gauge, more preferably between about 11 to 19 gauge, e.g., 13 gauge, 14 gauge, 15 gauge, 16 gauge, or 17 gauge. In some embodiments, the inside diameter is no more than about 4 gauge, 3 gauge, 2 gauge, or 1 gauge smaller than the outside diameter of the elongate member 902.
The inside luminal diameter of all of the embodiments disclosed herein is preferably optimized to allow a minimal exterior delivery profile while maximizing the space for the drive shaft 916. In one embodiment, the outside diameter of the elongate member 902 is 13 gauge (0.095″ or 2.41 mm) with a 0.077″ (1.96 mm) lumen. In some embodiments, the percentage of the inside diameter of the lumen with respect to the outside diameter of the elongate member 902 is at least about 60%, 65%, 70%, 75%, 80%, 85%, or more.
In some embodiments, the maximum length of the drill 900 is no more than about 15″, 10″, 8″, 7″, 6″, or less depending upon the target and access pathway. In one embodiment, when the length of drill 900 is no more than about 8″, the adjustable distal portion 923 of the elongate member 902 has a length of at least about 1″ and preferably at least about 1.5″ or 2″ or more.
To operate the drill, the operator actuates the drill control, such as by moving the handle lever 913 and attached crank knob 914 (similar to that of a fishing reel) in an appropriate direction thereby rotating the operably coupled actuation knob 910 operably connected to the drill bushing 909, which in turn rotates the drive shaft 916 and ultimately the drill tip 919. The crank knob 914 is attached to the handle lever 913 using a screw 921 or other method of attachment. In some embodiments, handle lever 913 and crank knob 914 can be integrally formed. In some embodiments, the presence of a friction-reducing element such as a Teflon washer 915 reduces friction between the crank knob 914 and handle lever 913 while these components are in motion. In some embodiments, the handle lever 913 with associated crank knob 914 is sized and positioned so that it may be easily manipulated and rotated with one hand while the operator can stabilize the proximal end of the steerable and curvable vertebroplasty drill 900 with the other hand. While the drill 900 is described herein as manually operable, motorized drills are also within the scope of the invention.
The actuating knob 910 is operably coupled to a drive bushing 909 which rotates a drive shaft 916 in the vicinity of the mid-handle 905. The actuating knob 910 can be secured to the mid-handle 905 with one or more dowel pins 920 that enable the actuating knob 910 to rotate freely around the axis of the mid-handle 905. Likewise, the operably coupled drive shaft 916 and drive bushing 909 can rotate axially relative to the mid-handle 905 when the operator turns the handle lever 913 attached to the crank knob 914. In some embodiments, a friction reducing element such as one or more Teflon washers 911 reduce friction between the actuating knob 910 and the mid-handle so as to facilitate the free rotation of the actuating knob 910 relative to the mid-handle 905.
As illustrated in
As illustrated in
The drill tip 919 is positioned so that, in use it extends at least partially beyond the distal end of the distal elongate member 902 of the drill. This enables the drill tip 919 to bore through the desired bone or other tissue. While described herein as a drill bit, burrs, augurs, abraders, cutters, or other elements configured to rotate at a suitable speed to bore through cancellous and/or cortical bone or other tissue can be used as well in the invention. For example, various cutters as described, for example in paragraphs [0039] to [0043] of U.S. Pat. Pub. No. 2006/0149268 A1 to Truckai et al., hereby incorporated by reference in its entirety, can be used with embodiments of the disclosed drill instead of a drill bit. While some embodiments of the steerable and curvable vertebroplasty drill 900 will have a permanently fixed drill tip 919 set at the point of manufacture, in other embodiments the drill tip 919 is detachable so that an alternate drill tip 919 may be substituted in the operating room depending on the desired clinical result.
The drill tip 919 can be secured, such as via a half bushing 904 at or near the distal end of the laser cut tube 923. The proximal portion of drill tip 919 is positioned within the distal portion 923 of the elongate member 902 and operably coupled with the distal shaft end 918 as noted above. In some embodiments, the drill tip 919 has a diameter greater than that of the lumen at the location of the half bushing 904. In such embodiments, there is a depression or groove around the circumference of the lateral surface of the drill tip 919 wherein the half bushing 904 can fit in a complementary manner. This configuration can limit any possible axial motion while not impeding the rotation of said drill tip 919.
In some embodiments, the distal portion 923 of the elongate member 902 may have a curved bias, and kept in a relatively straightened configuration by an outer tubular member having column strength sufficient to keep the distal segment in 923 in a relatively straightened position while the outer tubular member encompasses the distal end 923 of the elongate member 902, as described, for example, in connection with
In order to facilitate the deflection of the distal end of the laser cut tube 923, this portion of the device can include a plurality of transverse slots 922 cut into a portion of or the entire circumference of the laser cut tube 923. These slots 922 can be machined or laser cut out of the tube stock that becomes the elongate member 902. In some embodiments, these slots 922 can have a linear, chevron-shape or other configuration. In some embodiments, the distal end of the laser cut tube 923 may be created from an elongate coil rather than a continuous tube so as to facilitate flexibility. In other embodiments, the distal end of the laser cut tube may comprise a combination of a coil along with a slotted tubular structure.
As shown, when the front handle 901 is rotated relative to the mid-handle 905, these two components will move apart axially from one another opening a progressively expanding gap D1 to D3 between these two components and thus increasing the overall length of the proximal handle 1000. In some embodiments, the front handle 901 and mid-handle 905 articulate by means of complementary, screw-like, threaded surfaces so that rotation in one direction moves the two components apart while rotation in the opposite direction moves them closer together thereby decreasing the axial gap distance (e.g., from D3 until front handle 901 and mid-handle 905 abut each other). In alternative embodiments, instead of rotation of the mid handle 905 and/or front handle 901, a ratcheting system with stops or other mechanism could be used to separate the components. In some embodiments, the maximal distance D3 that the mid-handle 905 is configured to move axially proximally relative to front handle 901 is at least about 1 cm, 2 cm, 3 cm, 4 cm, 5 cm, or more. In some embodiments, the maximal distance D3 is at least about 2%, 3%, 5%, 8%, 10%, 15%, 20%, 25%, 30%, or more of the total axial length of the drill.
In many embodiments, the deflection of the distal end 923 of the elongate member 902 is controlled by adjusting the tension exerted by the pull wire 903. The distal end of the pull wire 903 is attached to the half bushing 904 located near the distal end of the elongate member 902. The proximal end of the pull wire 903 is attached to the drill bushing 908 and held secure by, for example, a tapered dowel pin 912. As the distance D1 to D3 between the front handle 901 and mid-handle 905 increases, the tension exerted by the proximally attached pull wire 903 on the distal half bushing 904 increases. The tension can deflect the flexible distal elongate segment 923 to an angle relative to the rigid, coaxial, proximal region of the tube 924. Continued rotation of the front handle 901 relative to the mid-handle 905 will progressively enlarge the distance between these components from D1 to D3, thereby increasing the tension exerted by the pull wire 903 on the half bushing 904, and ultimately increase and the angle of deflection of the distal elongate segment 923 of the elongate tube 902.
As shown in
To facilitate the axially “floating” feature, in some embodiments, the drive shaft 916 (and/or the inside diameter lumen of the drive bushing 909) can have a cross-sectional shape other than circular. Such shapes can include, triangular, square, hexagonal, octagonal, star shaped, D shaped or a variety of other configurations.
In some embodiments, the steerable and curvable vertebroplasty drill 900 can be used to create a cavity in a vertebral body wherein various types of bone cements can be injected as described supra in the application as well as those disclosed in U.S. patent application Ser. No. 11/626,336, filed Jan. 23, 2007, the disclosure of which is hereby incorporated in its entirety herein by reference.
The steerable and curvable vertebroplasty drill 900 can be used to drill into or through bones and tissues other than vertebrae and can be used in a variety of minimally invasive or open surgical applications. In addition, the device can be used for the purpose of cavity creation for the purpose of introducing implants, drugs, chemotherapeutic or radiologic agents. The device can also be used for the purposes of mass reduction of various pathological tissues or bone biopsy. The disclosures herein should not be construed as limiting the possible medical uses of the steerable and curvable vertebroplasty drill 900.
The steerable and curvable drill 900 in
Additional components come into view in the exploded view of
In some embodiments, the wire insert 975 is inserted within the central lumen of the drive shaft 916 and extends through a length of the drive shaft that can be at least as long as the length of the portion of the drive shaft 916 having slit apertures 972. While in some embodiments, the wire insert 975 can extend the entire length of the drive shaft 916, in other embodiments, the wire insert 975 extends only a portion of the length of the drive shaft 916. For example, the wire insert 975 can extend a length between about 10% and 70% of the length of the drive shaft 916, or between about 20% and 40% of the length of the drive shaft 916 in some embodiments. The insert 975 could be made of any appropriate material, such as various metals, including nickel, titanium, copper, aluminum, steel, or various alloys thereof. In some embodiments, the wire insert 975 is formed of a flexible biocompatible material, such as Nitinol, MP35N or Elgiloy. High strength, flexible polymeric materials such as polyamide can also be used. In some embodiments, the wire insert 975 can be coated with a material to improve biocompatibility, including phosphorylcholine or polyurethane. In some embodiments, the wire insert has a diameter of from about 0.010 in. to about 0.200 in.
The slit apertures 972 are formed along at least a distal portion of the drive shaft 916, such as between about 0.5 inches to 6 inches, or between about 1 inch to 3 inches of the length of the drive shaft 916. In some embodiments, the slit apertures 972 extend along a length that is at least about 5%, 10%, 15%, 20%, 25%, 30%, or more of the entire length of the drive shaft 916. The drive shaft, in some embodiments, has a sidewall thickness of from about 0.002 in. to about 0.050 in. and an inside diameter of a central lumen in which the wire insert 975 can be placed therethrough of from about 0.010 in. to about 0.200 in. The slit apertures 972 advantageously help to transfer torque along the drive shaft 916, while the drive shaft insert 975 assists in preventing radial collapse of the drive shaft 916 along the length of the slit apertures 972. The direction of the helical filament formed by cutting a slit or wrapping wire or ribbon around a mandrel is matched to the direction of rotation of the drill such that rotation under lead has a tendency to tighten rather than unwind the helical filament. In addition, the slit apertures 972 can help to increase the flexibility of the drive shaft 916 relative to certain drive shafts without the slit apertures. This is particularly useful since the drive shaft 916 can be configured in some embodiments to flex in conjunction with the deflectable distal portion 923 of the elongate member 902. While in some embodiments, the drive shaft 916 is configured to flex when the deflectable distal portion 923 of the elongate member 902 flexes, in other embodiments, the drive shaft 916 can be flexed independently (e.g., such as by its own independent pull wire).
As best shown in
While the embodiments in
In some embodiments and as illustrated in
In operation, the crimp 1001 is formed of two mateable members, a first crimp member 1024 located on the distal end of the drive shaft 916 and a second crimp member 1028 located on the shaft of the boring element 919. By using the crimp 1001, a secure coupling can be formed between the drive shaft 916 and the boring element 919.
The first and second crimp members are mateable members that secure the drive shaft 916 to the boring element 919. In one embodiment, the first crimp member 1024 and the second crimp member 1028 can include one, two, or more complementary interlocking surfaces. In some embodiments, the first crimp member 1024 includes one, two, or more raised surfaces 1025 or bumps formed on or attached on to the drive shaft 916. The second crimp member 1028 can comprise one or more complementary apertures 1027 formed on or attached on to the boring element 919. Placing the second crimp member 1028 over the first crimp member 1024 effectively creates an interference fit, interlocking the two members and reduces the risk of loosening, for example, by wedging the drive shaft to the boring element. While in the illustrated embodiments the first crimp member 1024 comprises one or more raised surfaces 1025 and the second crimp member 1028 comprises one or more receiving apertures 1027, in other embodiments, the raised surfaces 1025 could be on the second crimp member 1028 and the receiving apertures 1027 can be located on the first crimp member 1024. In some embodiments, the raised surfaces 1025 and apertures 1027 need not necessarily be circular as illustrated, and can be oval, square, rectangular, or other shapes.
In some embodiments, the first crimp member 1024 comprises between two and eight raised surfaces 1025, such as four raised surfaces 1025. The second crimp member 1028 comprises an equal number of complementary apertures 1027 to create a friction fit with the raised surfaces 1025 of the first crimp member 1024. In some embodiments, and as shown in
In addition, it is possible to have a crimp 1001 formed of two interlocking members that interlock by means other than a bump and corresponding aperture. For example, the crimp 1001 can comprise a first crimp member formed of a clasp, while the second crimp member is formed of a clasp receiver.
In some embodiments, this procedure for creating a cavity for inserting one or more of the bone cements described above is performed by making an incision in an appropriate location and advancing the distal portion of the steerable and curvable vertebroplasty drill 900 alone or through a lumen in an access cannula to the desired osteotomy site. A number of features of this device minimize the degree of invasiveness required to perform this procedure: While the relatively low-profile diameter of the laser cut tube 902 minimizes the size of the incision required to guide the device to this location, the ability to change the angle of actuation of the drill tip 919 gives the user significant flexibility in determining the surgical approach for the desired location for making the osteotomy. Once the operator has maneuvered the tip of the steerable and curvable vertebroplasty drill 900 to the desired osteotomy site, the operator is then able to drill into the bone and/or other tissue by rotating the drill tip 919 by manually turning the actuation knob 910. The operator can create a cavity therein by drilling multiple holes in the interior of the vertebral body thereby crushing and/or extracting the diseased bone. This can be facilitated through the use of the deflectable distal portion 923 of the tube 902 that enables the user to change the angle of deflection of the drill tip 919 without changing the angle of primary approach and without having to drill multiple holes through the surface of the bone. In this manner, a relatively large cavity can advantageously be created within the bone with only a minimally invasive approach and single entry site. This procedure is depicted in
Once a cavity of sufficient size or desired number of bores have been created within the vertebral body or other bone, the operator can then straighten and withdraw the steerable and curvable vertebroplasty drill 900 and introduce a device capable of injecting the desired bone cement or other compound media or device into the cavity as described, for example, elsewhere in the application. In some embodiments, features of the steerable drill 900 can be incorporated with the bone cement delivery elements disclosed herein on a single catheter such that the drill need not be withdrawn prior to infusion of cement media. For example, the steerable and curvable drill as described herein could additionally include a closed cement delivery system with an input port such as a proximal Luer lock and one or more cement delivery lumens within the catheter body separated from the drive shaft and one or more distal exit ports for cement delivery as also described herein.
In accordance with
In accordance with
In accordance with
In some embodiments, a vertebroplasty system includes a steerable and curvable drill 1000, and a steerable and curvable injector 10 configured to removably receive the steerable and curvable drill 1000 therethrough. A schematic illustration of such a system is illustrated in
While described herein primarily in the context of vertebroplasty, one of ordinary skill in the art will appreciate that the disclosed drill can be used or modified in a wide range of clinical applications, such as, for example, other orthopedic applications such as kyphoplasty, treatment of any other bones, pulmonary, cardiovascular, gastrointestinal, gynecological, or genitourinary applications. While this invention has been particularly shown and described with references to embodiments thereof, it will be understood by those skilled in the art that various changes in form and details may be made therein without departing from the scope of the invention. For all of the embodiments described above, the steps of the methods need not be performed sequentially. Additionally, the skilled artisan will recognize that any of the above-described methods can be carried out using any appropriate apparatus. Further, the disclosure herein of any particular feature in connection with an embodiment can be used in all other disclosed embodiments set forth herein. Thus, it is intended that the scope of the present invention herein disclosed should not be limited by the particular disclosed embodiments described above.
Claims
1.-13. (canceled)
14. A method of treating a bone, comprising:
- creating an access channel to access the interior of a vertebral body;
- inserting an introducer cannula into the access channel;
- inserting a drill through the introducer cannula into the interior of the vertebral body, the drill comprising an elongate body having a proximal end and a distal end, the distal end comprising a deflectable zone; the drill further comprising a drive shaft housed in a central lumen of the elongate body, the drive shaft including a distal portion comprising one or more slit apertures on the surface of the drive shaft; the drill further comprising a first crimp member on the distal end of the tubular body; a boring member; and a second crimp member on the boring member, wherein the second crimp member is configured to be interlocking with the first crimp member to form a continuous body between the tubular body and boring member;
- actuating a control to deflect the deflectable zone of the steerable and curvable drill in the vertebral body;
- removing the steerable and curvable drill from the interior of the vertebral body; and
- flowing bone cement through an injection needle into the interior of the vertebral body.
15. A vertebroplasty drill, comprising:
- an elongate tubular body having a proximal end, a distal end comprising a deflectable zone carrying a boring element configured to displace cancellous bone, and a central lumen extending therethrough;
- a handle on the proximal end of the tubular body, the handle comprising a deflection control for deflecting a deflectable zone on a distal end of the tubular body, and a drill control for actuating the boring element; and
- a drive shaft housed within the central lumen of the tubular body, the drive shaft including a distal portion comprising one or more slit apertures on the surface of the drive shaft, wherein the drive shaft is operably connected to the drill control proximally and the boring element distally.
Type: Application
Filed: Aug 22, 2011
Publication Date: Jul 26, 2012
Inventors: Keith Burger (San Francisco, CA), Shixin Chen (Santa Rosa, CA), Joshua Cheatwood (Windsor, CA)
Application Number: 13/215,098
