US20050240193A1 - Devices for creating voids in interior body regions and related methods - Google Patents
Devices for creating voids in interior body regions and related methods Download PDFInfo
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- US20050240193A1 US20050240193A1 US10/893,155 US89315504A US2005240193A1 US 20050240193 A1 US20050240193 A1 US 20050240193A1 US 89315504 A US89315504 A US 89315504A US 2005240193 A1 US2005240193 A1 US 2005240193A1
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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
- A61B17/88—Osteosynthesis instruments; Methods or means for implanting or extracting internal or external fixation devices
- A61B17/885—Tools for expanding or compacting bones or discs or cavities therein
- A61B17/8852—Tools for expanding or compacting bones or discs or cavities therein capable of being assembled or enlarged, or changing shape, inside the bone or disc
- A61B17/8855—Tools for expanding or compacting bones or discs or cavities therein capable of being assembled or enlarged, or changing shape, inside the bone or disc inflatable, e.g. kyphoplasty balloons
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- A61B17/56—Surgical instruments or methods for treatment of bones or joints; Devices specially adapted therefor
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- A—HUMAN NECESSITIES
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- 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
-
- A—HUMAN NECESSITIES
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- 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
- A61B17/1604—Chisels; Rongeurs; Punches; Stamps
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- A61B17/1613—Component parts
- A61B17/1615—Drill bits, i.e. rotating tools extending from a handpiece to contact the worked material
- A61B17/1617—Drill bits, i.e. rotating tools extending from a handpiece to contact the worked material with mobile or detachable parts
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- A61B17/16—Bone cutting, breaking or removal means other than saws, e.g. Osteoclasts; Drills or chisels for bones; Trepans
- A61B17/1662—Bone cutting, breaking or removal means other than saws, e.g. Osteoclasts; Drills or chisels for bones; Trepans for particular parts of the body
- A61B17/1671—Bone cutting, breaking or removal means other than saws, e.g. Osteoclasts; Drills or chisels for bones; Trepans for particular parts of the body for the spine
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- A61B17/88—Osteosynthesis instruments; Methods or means for implanting or extracting internal or external fixation devices
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- A61B17/22031—Gripping instruments, e.g. forceps, for removing or smashing calculi
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- A61B17/221—Gripping devices in the form of loops or baskets for gripping calculi or similar types of obstructions
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- A61B17/221—Gripping devices in the form of loops or baskets for gripping calculi or similar types of obstructions
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- A61B2017/2926—Details of heads or jaws
- A61B2017/2927—Details of heads or jaws the angular position of the head being adjustable with respect to the shaft
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- A61B17/320016—Endoscopic cutting instruments, e.g. arthroscopes, resectoscopes
- A61B17/32002—Endoscopic cutting instruments, e.g. arthroscopes, resectoscopes with continuously rotating, oscillating or reciprocating cutting instruments
- A61B2017/320028—Endoscopic cutting instruments, e.g. arthroscopes, resectoscopes with continuously rotating, oscillating or reciprocating cutting instruments with reciprocating movements
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Abstract
Description
- This application claims the benefit of provisional U.S. Application Ser. No. 60/499,934, filed Sep. 3, 2003, and entitled “Mechanical Devices for Creating Voids in Interior Body Regions and Related Methods.”
- This invention relates generally to tools for creating cavities or voids in interior body regions. In particular, the invention relates to creating voids in bone for diagnostic or therapeutic purposes.
- A minimally invasive method of forming a cavity or void within one of the body's solid organs, for both diagnostic and treatment purposes, is becoming increasingly important as radiological and other types of scanning techniques improve a physician's ability to view inside the body without having to make an incision.
- The most common solid organ currently making use of a minimally invasive technique to form a void is bone. Typically this is any pathological bone in the body with a fracture, osteoporosis, or a tumor. The most commonly used void-forming method for bones is the inflatable bone tamp, as described in U.S. Pat. Nos. 4,969,888 and 5,108,404. Void formation in this case is usually followed by filling with a filling substance like bone cement or a bone substitute.
- Mechanical methods are also available for making voids inside solid organs. Those solid organs include the brain, the kidneys, the spleen, the liver and bone. In the brain, for example, an abscess could be easily debrided and irrigated with a minimally invasive mechanical void technique. A fractured spleen could be approached with a minimally invasive technique, to make a small void to fill with gelfoam or some other coagulant to stop hemorrhage. An osteoporotic, fractured vertebral body or bone tumor could be approached by a minimally invasive mechanical system in order to create a cavity or void and then refill with a bone substitute. A demand exists for systems or methods that are capable of forming voids in bone and other interior body regions in safe and efficacious ways.
- The invention provides systems and methods for creating voids in interior body regions.
- One aspect of the invention provides a cutting tip for cutting or scraping bone. In one embodiment, a curette-type instrument at the end of a shaft can be mechanically angled into different positions to scrape material to form a void. In another embodiment, a mechanical device at the end of a shaft resembles a T-type configuration and allows both translational and rotational cutting to form a void. In a third embodiment, the cutting tip includes a turned and tapered trunk. In a fourth embodiment, the cutting tip includes a conical trunk. In a fifth embodiment, a sharp, stout, metal spring is provided on the end of a shaft. In a sixth embodiment, the distal end of a shaft carries two more fingers to grab tissue for extraction. In a seventh embodiment, a hinged void-forming device is carried by a shaft and allows for formation of a void, which may be of a rectangular or any other pre-determined shape.
- Another aspect of the invention provides an actuator mechanism for deploying a cutting tip. In one embodiment, rotational movement of a thumbwheel is converted to translational movement of a plunger rod. In an alternative embodiment, rotational movement of a control knob is converted to translational movement of a plunger rod through interaction of a series of gears.
- Another aspect of the invention provides a tool for creating voids in interior body regions. The tool comprises a shaft, a tip for contacting bone, and a hinge member coupling the tip to the shaft. The tip becomes uncoupled if the torque applied exceeds a maximum hinge torque. The shaft includes a region of weakness proximal to the tip along which the shaft will break if the torque applied exceeds a maximum shaft torque. The maximum hinge torque is greater than the maximum shaft torque.
- According to another aspect of the invention, a tool for creating voids in interior body regions comprises a shaft assembly including a lumen, a tip for contacting bone coupled to the shaft, and a rod slidable within the lumen. The rod is tethered to the tip.
- According to another aspect of the invention, a tool for creating voids in interior body regions comprises a shaft including a lumen, and a tip for contacting bone coupled to the shaft by a coupling element. The tip is additionally tethered to the shaft such that the tip remains tethered to the shaft if the coupling element becomes inoperable.
- According to another aspect of the invention, a tool for creating voids in interior body regions comprises a cannula and a shaft. The shaft has a handle and is sized and configured for passage through the cannula. A projection extends radially from the shaft to restrict forward advancement of the shaft within the cannula.
- Another aspect of the invention provides methods of creating a void in bone. The methods provide one or more mechanical cutting tools that may be used in combination with one or more expandable void-creating structures to form a void of a desired size and configuration.
-
FIG. 1 is a perspective view of a mechanical tool for creating voids in interior body regions and illustrating pivoting movement of the cutting tip in phantom. -
FIG. 2 is a perspective view of a bone treatment device. -
FIG. 3 is a perspective view illustrating insertion and use of the device ofFIG. 2 in a vertebra. -
FIG. 4 is a perspective view of an alternative embodiment of a cutting tip and illustrating pivoting movement of the tip in phantom. -
FIG. 5 is a front plan view of the tip shown inFIG. 4 and illustrating rotational movement of the cutting tip. -
FIG. 6 illustrates 180° rotational movement of the cutting tip in a vertebra to create a 180° void. -
FIG. 7 illustrates the shaft rotated 180° relative toFIG. 6 and the cutting tip again rotated 180° to form a 360° void. -
FIG. 8 is a side view of the tip shown inFIG. 4 and illustrating translational movement of the cutting tip in a sawing-like motion. -
FIG. 9 illustrates the translational movement of the cutting tip and formation of a void in a vertebra. -
FIG. 10 is a perspective view illustrating the use of a marker band to identify the position of the cutting tip in relation to the distal end of the cannula. -
FIG. 11 is a perspective view illustrating use of a stop to limit translational advancement of the shaft within a cannula. -
FIG. 12A is an enlarged view of a groove located on the shaft of the cutting tool. -
FIG. 12B is a perspective view of an alternative embodiment of a shaft in which a portion of the shaft is formed of a material of reduced strength and/or rigidity relative to the rest of the shaft. -
FIG. 13 is a perspective view of an alternative embodiment of a stop that limits translational and rotational movement of the shaft along and within the cannula. -
FIG. 13A is a perspective view of an alternative embodiment of a T-shaped slot that limits translation and rotational movement of the shaft along and within the cannula. -
FIG. 14 is a schematic view representing the preset size and configuration of a void formed by performing a full sweep motion of a cam follower along a cam surface. -
FIG. 15 is a perspective view of an alternative embodiment of a cutting tip and illustrating pivoting movement of the tip in phantom. -
FIG. 16 is a front plan view of the tip shown inFIG. 15 and illustrating rotational movement of the cutting tip. -
FIG. 17 is a perspective view of an alternative embodiment of a cutting tip and illustrating pivoting movement of the tip in phantom. -
FIG. 18 is a front plan view of the tip shown inFIG. 17 and illustrating rotational movement of the cutting tip. -
FIG. 19 is a sectional view of an actuator mechanism for deploying a cutting tip and showing placement of the tool in the user's hand. -
FIG. 20 is a close-up and partial sectional view of the thumbwheel, threaded cap, flange, and stop ofFIG. 19 . -
FIG. 21 is a cut-away view of the tether and hinge mechanism of the cutting tip. -
FIG. 22 is a side sectional view of an alternative embodiment of an actuator mechanism in which a lever actuates movement of the plunger rod. -
FIG. 23 is a perspective view of a tool incorporating an alternative embodiment of an actuator mechanism. -
FIG. 24 is a top sectional view of an alternative embodiment of an actuator mechanism. -
FIG. 25 is a side sectional view of an alternative embodiment of an actuator mechanism and showing placement of the tool in the user's hand. -
FIG. 26 is a side partial section view illustrating an alternative embodiment of a mechanical bone cutting tool illustrating the cutting tip in a straightened or malleable state and retracted within a cannula. -
FIG. 27 is a view similar toFIG. 26 and illustrating advancement of the cutting tip beyond the distal tip of the cannula and the introduction of fluid to activate the cutting tip. -
FIG. 28 is a view similar toFIG. 27 and illustrating activation of the cutting tip to a predetermined configuration. -
FIG. 29 is a side view of an alternative embodiment of a cutting tip illustrating the cutting tip in a straightened or malleable state. -
FIG. 30 is a view similar toFIG. 29 illustrating the cutting tip in the activated state. -
FIG. 31 is a side view of an alternative embodiment of a cutting tip illustrating the cutting tip in a straightened or malleable state. -
FIG. 32 is a view similar toFIG. 31 illustrating the cutting tip in the activated state. -
FIG. 33 is a side view of an alternative embodiment of a cutting tip carried by a shaft and illustrating a dual lumen extending through the shaft into the cutting tip. -
FIG. 34 is a side view of an alternative embodiment of a cutting tip illustrating a throughbore extending through the cutting tip. -
FIG. 35A is a side view illustrating a pre-bent or formed cutting tip confined by a cannula. -
FIG. 35B is a side view similar toFIG. 35A illustrating the deployment of the pre-bent or formed cutting tip by extension of the tip beyond the cannula. -
FIG. 36 is a side view of an alternative embodiment of a mechanical void-creating device. -
FIG. 37 is a side view of an alternative embodiment of a mechanical void-creating device. -
FIG. 38 is a side view of an alternative embodiment of a mechanical void-creating device. -
FIG. 39 is a top view of the device shown inFIG. 38 . -
FIG. 40 is a side view of an alternative embodiment of the device ofFIGS. 38 and 39 in which spring blades extend from the device. - FIGS. 41A-D illustrate a method of creating and filling a void in bone in which a first mechanical cutting tool is used to create a void in bone and a second mechanical cutting tool is used to expand and/or further define the void.
- FIGS. 42A-E illustrate an alternative method of creating and filling a void in bone in which a first mechanical cutting tool is used to create a void in bone and a second mechanical cutting tool and then an expandable body are used to expand and/or further define the void.
- FIGS. 43A-D illustrate an alternative method of creating and filling a void in bone in which a first expandable body is used to create a void in bone and a second expandable body is used to expand and/or further define the void.
- FIGS. 44A-E illustrate an alternative method of creating and filling a void in bone in which a first expandable body is used to create a void in bone and a second expandable body and then a mechanical cutting tool are used to expand and/or further define the void.
- FIGS. 45A-E illustrate an alternative method of creating and filling a void in bone in which a first expandable body is used to create a void in bone and a mechanical cutting tool and then a second expandable body are used to expand and/or further define the void.
- FIGS. 46A-E illustrate an alternative method of creating and filling a void in bone in which an expandable body is used to create a void in bone and a first mechanical cutting tool and then a second mechanical cutting tool are used to expand and/or further define the void.
- FIGS. 47A-E illustrate an alternative method of creating and filling a void in bone in which a first cutting tool is used to create a void in bone and an expandable body and then a second mechanical cutting tool are used to expand and/or further define the void.
- FIGS. 48A-E illustrate an alternative method of creating and filling a void in bone in which a mechanical cutting tool is used to create a void in bone and a first expandable body and then a second expandable body are used to expand and/or further define the void.
- Although the disclosure hereof is detailed and exact to enable those skilled in the art to practice the invention, the physical embodiments herein disclosed merely exemplify the invention that may be embodied in other specific structure. While the preferred embodiment has been described, the details may be changed without departing from the invention, which is defined by the claims.
- The systems and methods embodying the is invention can be adapted for use virtually in any interior body region, where the formation of a cavity or void within tissue is required for a therapeutic or diagnostic purpose. The preferred embodiments show the invention in association with systems and methods used to treat bones. This is because the systems and methods which embody the invention are well suited for use in this environment. It should be appreciated that the systems and methods which embody features of the invention can be used in other interior body regions, as well.
- Various embodiments of cutting tips are described below in detail. In each case their sizes and shapes could be produced to fit the ideal void to be formed, whether it is a void in a tibia or a vertebral body. In addition, these mechanical tools could be made of any bio-compatible metal (for example, but not limited to stainless steel, titanium, titanium alloys, tantalum, aluminum, aluminum alloys, or other metals) that has adequate shear and tensile strength to perform their void-forming function. Plastic polymers having suitable biomechanical properties may also be used for these tools. Alternatively, the tool may be plated or coated with a biocompatible material.
- I. Mechanical Cutting Tool
- A. Curette
-
FIGS. 1-3 show atool 10 capable of forming a cavity or void in a targeted treatment area. Thetool 10 comprises ashaft 12 having a proximal and a distal end, respectively 14 and 16. Theshaft 12 preferable includes ahandle 18 to aid in gripping and maneuvering theshaft 12 through a pre-formed access path into bone. Thehandle 18 can be made of any suitable material, e.g., any rigid polymer or metal or combination thereof, secured about theshaft 12. Thehandle 18 is desirably sized and configured to be securely and comfortably grasped by the physician. - The
shaft 12 carries a void-formingstructure 20 at itsdistal end 16. In the illustrated embodiment, thestructure 20 takes the form of amulti-faceted cutting tip 20. The cuttingtip 20 may be adapted for use in various body regions, e.g., to create a void in bone. The cuttingtip 20 may also serve to remove hard or soft tumors from tissue. As used in this specification, a cutting tip is a surface adapted to mechanically form a void in bone through contact with the bone, e.g., by cutting, shearing, scooping, shaving, sciving, dissecting, or scoring of the bone. - The cutting
tip 20 is hingedly coupled todistal end 16 of theshaft 12. The cuttingtip 20 is desirably adapted to extend radially from theshaft 12 and radially from the pre-formed access path to a diameter that is greater than a diameter of the access path. The cuttingtip 20 can be made of any suitable biocompatible material, e.g., stainless steel, cobalt chromium, titanium and alloys or mixtures thereof. Theshaft 12 and cuttingtip 20 can alternatively be made of different materials (e.g. alloys of stainless steel with different strengths: 303 stainless steel, 304 stainless steel, 17-4 stainless steel, 17-7 stainless steel) and welded or otherwise bonded together. As will be described in detail later, an actuator, e.g., wheel 22 (see also, e.g.,FIGS. 19 and 23 ), permits selective movement of the cuttingtip 20 from a first, closed or non-deployed position to a second, open or deployed position. - In the closed position (represented by solid lines in
FIG. 1 ), the cuttingtip 20 extends from thedistal end 16 of theshaft 12 along the axis S of theshaft 12. In this position, theshaft 12 can be easily passed through acannula 23 or other instrument. The hinge mechanism permits pivoting of thetip 20 at an angle A transverse to axis S ofshaft 12 to the opened position (represented in phantom inFIG. 1 ). In a preferred embodiment, the cuttingtip 20 is adapted to pivot and be selectively secured in any pivot position from 0-90° relative to the axis S of theshaft 12. - Desirably, the actuating mechanism provides positive, controlled movement in both directions (i.e., from the open, deployed position to the closed, non-deployed position and from the closed, non-deployed position to the open, deployed position) during all degrees of actuation. That is, the secured pivot position and angle A are maintained regardless of the rotational orientation of the
shaft 12. The actuator mechanism provides positive cutting action as the tip is actuated in either direction to provide bi-directional cutting. Actuation may be repeated so as to provide continuous cutting. The speed of actuation may be varied to vary the speed of cutting. The cuttingtip 20 also permits translational (i.e., longitudinal) movement along the axis S of theshaft 12 in a push-pull or sawing motion with the tip in the deployed position. The physician creates a desired void by repeated actuation, translational movement, or by performing a series of combined actuation and translational movements. - In use, the cutting
tip 20 is placed in the closed position extending from thedistal end 16 of theshaft 12, i.e., at a 0° angle A relative to axis S. Thetool 10 may be introduced into a targeted treatment site through an open procedure. Desirably, thetool 10 is introduced in a closed and minimally invasive procedure in which apercutaneous cannula 23 is advanced into a desired treatment region, e.g., avertebral body 37. Theshaft 12 is then passed through thecannula 23 and the cuttingtip 20 is extended beyond the distal end of thecannula 23. Alternatively, thecannula 23 may be removed after introduction of thetool 10. Fluoroscopy or other visualization techniques may be employed to aid in introducing thecannula 23 and tool into the targeted treatment area. The cuttingtip 12 is then pivoted to a desired position, i.e., preferably any position between 0-150°, and most preferably about 90°. Also, conceivably thetip 20 could deploy in either direction without stopping in the non-deployed condition. Actuation may be repeated and theshaft 12 advanced in fore and aft directions by pushing and pulling in a sawing-like motion to thereby create a void. - If rotational cutting is desired, turning of
shaft 12 is required to reposition thetip 20 to continue cutting. In this case, the cuttingtip 20 is returned to the closed position and theshaft 12 turned or rotated to a new position. The cuttingtip 20 is again pivoted to a desired angle A (open position) and theshaft 12 again advanced in fore and aft directions using a push-pull motion. It is apparent that theshaft 12 may be repositioned any number of times to produce a void of a desired configuration. - With reference now to
FIGS. 2 and 3 , thecannula 23 desirably incorporates a distal portion having a reduced profile. Thecannula 23 includes alarge diameter portion 25, a small diameterdistal portion 27, and atransition portion 29. Alternatively, thecannula 23 may provide a taper between the large andsmall diameter portions 25 and 27 (not shown). Theshaft 12 of thetool 10 is desirably sized to fit within alumen 31 extending through thecannula 23, and may be of a constant or varying size. - Desirably, the reduced distal tip diameter of the
cannula 23 will allow the tip of thetool 10 to be inserted into the targeted bone, with a corresponding reduction in the size of the access path created in the bone. Thesmaller diameter section 27 of thecannula 23 will pass through the cortical wall into the bone, while thelarger diameter section 25 can abut against the outside of the bone (sealing the opening, if desired), and will desirably stretch, but not tear, softer tissues. - In a preferred embodiment, the
smaller diameter portion 27 is desirably sized such that, when thelarger diameter portion 25 abuts thecortical bone 33 of thepedicle 35, the distal end of thesmaller diameter portion 27 extends through thepedicle 35 and emerges into thevertebral body 37 and enters intocancellous bone 39. In this embodiment, thetool 10 could be sized such that, when fully inserted into thecannula 23, thedistal cutting tip 20 would be prevented from contacting and/or breaching the anteriorcortical wall 41 of thevertebral body 37 or targeted bone. - Other low profile bone access tools are described in U.S. patent application Ser. No. 09/952,014, filed Sep. 11, 2001, entitled “Systems and Methods for Accessing and Treating Diseased or Fractured Bone Employing a Guide Wire,” which is herein incorporated by reference.
- B. T-Tip Embodiment
- In many cases, it is desirable to cut in both a rotational as well as in a translational direction. In such cases, it is preferable that the rotational cutting motion reflects an ergonomic and natural motion for the physician.
FIGS. 4-9 illustrate an embodiment of acutting tool 100 having a cuttingtip 120 which permits translational, rotational, or simultaneous translational and rotational movement of the cutting tip using an ergonomic and natural motion. The cutting tip is made from any suitable biocompatible material, e.g., stainless steel. - As
FIG. 4 illustrates, the cuttingtip 120 provides apivot region 124 hingedly attached to ashaft 112, e.g.,pivot pin 126 passes throughhole 128 inpivot region 124 and intoshaft 112. This arrangement permits a wide range of pivot motion allowing the cutting tip to pivot at virtually any desired angle. In a preferred embodiment, the cuttingtip 120 is adapted to pivot from 0-90° relative to the axis S of theshaft 112. Similar to the embodiment ofFIG. 1 , the actuating mechanism is positive in both directions. - A
collar 130 divides thepivot region 124 and atrunk region 132 and provides additional strength and support to thecutting tip 120. The maximum width (W) of thetrunk 132 is parallel to the axis S of theshaft 112 when thetip 120 is deployed at 90° (illustrated in phantom inFIG. 4 ). - The
trunk 132 carries acutting disc 134 providing a dual rounded cutting surface extending on either side of thetrunk 132, providing a 360° cutting surface. In a preferred embodiment, the diameter ofdisc 134 is approximately the same as the diameter of theshaft 112 so as to minimize stress on thetip 120 during cutting and to provide ease of passage through a cannula. - The tip includes a flat or
straight cutting surface 136 along the tip of thedisc 134 that provides greater ease in cutting bone on the pullback motion. When pushing, theshaft 112 provides the strength and force for cutting. - The
disc 134 andtrunk 132 together provide a large surface contact area that enables thetip 120 to take an aggressive bite into bone and gouge bone material in large chunks. - The disc configuration allows rotational cutting in both clockwise and counterclockwise directions. With reference to
FIG. 5 , thetip 120 is extended to a desired angle A, e.g., 90° along axis T. Theshaft 112 is then rotated 0-90° in a first direction (represented by arrow 138) relative to axis T. Theshaft 112 can be rotated 0-90° in the opposite direction (represented by arrow 140) relative to axis T to create a void extending 180° by a simple turning of the physician's wrist. -
FIG. 6 illustrates rotation of thecutting tip 120 in bone, e.g., avertebra 142, to create a 180° void. In many cases, it may be desirable to create a void extending 360°. AsFIG. 7 shows, after formation of a 180° void, theshaft 112 may be rotated 180° and again aligned approximately along axis T. Theshaft 112 is then rotated 0-90° in a first direction (represented by arrow 144) relative to axis T. Theshaft 112 can be rotated 0-90° in the opposite direction (represented by arrow 146) relative to axis T to create a void extending 360°. The physician can monitor the position of thetip 120 with use of fluoroscopy. - The disc configuration also allows translational cutting in a push-pull or sawing motion as represented by arrows in
FIGS. 8 and 9 . In use, the physician may deliver translational and rotational forces simultaneously by pushing in and pulling out while simultaneously rotating a handle or alternating rotational and translational motions. In this manner, the physician controls rotational and translational movement of thecutting tip 120 to create a void of desired size and shape, e.g., cylindrical. - Desirably, as seen in
FIG. 10 , theshaft 112 carries a boss or stop 102 designed to limit forward, i.e., translational, motion of theshaft 112 within acannula 104. The diameter of thestop 102 approximates the diameter of thecannula 104 so that thestop 102 rests against the face or top 106 of thecannula 104 to stop forward advancement of theshaft 112 within thecannula 104. - The
stop 102 is positioned on theshaft 112 such that there is sufficient room to accommodate the physician's fingers wrapped around and under thehandle 18. Thestop 102 thus provides clearance between the physician's fingers and thepercutaneous access cannula 104, preventing pinching or catching of the physician's fingers. Thestop 102 stops insertion of theshaft 112 to leave a comfortable working distance for the physician's hand when rotating the shaft 112 (i.e., a sweeping cutting motion) or when using a push-pull cutting motion or a combination of both cutting motions. In a representative embodiment, thestop 102 is positioned approximately 1.75 inches (about 4.5 cm.) from the base of thehandle 18. By restricting or preventing further advancement of theshaft 112, thestop 112 prevents advancement of the shaft 112 (and void-forming structure 20) within the vertebral body. This prevents the possibility of puncturing or breaching the anterior cortical wall of the vertebra 142 (see alsoFIG. 9 ). - Desirably, a
marker band 101 is positioned distal of thestop 102. As seen inFIG. 10 , when theshaft 112 is fully inserted into theaccess cannula 104, themarker band 101 is aligned with theface 106 of thecannula 104 as the cuttingtip 120 is exiting thecannula 104 into a bone, e.g., avertebra 142. As shown inFIG. 11 , when theshaft 112 is fully inserted into thecannula 104, thetip 120 extends beyond the distal end 103 of the cannula 103. - In a representative embodiment, the
marker band 101 is located approximately 3 cm. distal of thestop 102. In this embodiment, when theshaft 112 is fully inserted into the cannula 104 (i.e., resting against the stop 102), thetip 120 extends approximately 3.5 cm. from the distal end 103 of thecannula 104 when thecutting tip 120 is in the non-deployed position (i.e., aligned with the axis S of the shaft 112), and approximately 3 cm. from the distal end 103 of thecannula 104 when thetip 120 is in the deployed position (e.g., at 90°). - In a preferred embodiment, a
groove 105 is positioned proximal thestop 102. As best seen inFIG. 12 , thegroove 105 is a turned angular cut having an angle G with a radius R on theshaft 112 to define a line of weakness on theshaft 112. In a representative embodiment, thegroove 105 is a 60° angular cut (i.e., G=approximately 60°) having a radius R of approximately 0.006 inch. The mean torque required for failure of theshaft 112 at groove 105 (the maximum shaft torque) is less than the torque required for failure of theshaft 112 at pin 126 (the maximum hinge torque) (see alsoFIG. 4 ), or more generally, of the cutting assembly itself. For example, it has been found that the mean torque required to scrape normal bone is approximately 2.0 in.-lb. In a representative embodiment, the mean torque required for failure of theshaft 105 atgroove 105 is approximately 7.3 in.-lb. and the mean torque required for failure atpin 128 is 9.3 in.-lb. In the event that excessive torque is translated through theshaft 112, thegroove 105 results in theshaft 112 breaking or severing at thegroove 112 before thetip 120 breaks or fails at thepivot region 124. This provides an additional safety feature that allows theshaft 112 andundeformed pivot region 124 to be safely removed from thecannula 104 without complications. Failure or deformation of thepivot region 124 is avoided. - It is contemplated that the region of weakness can also be formed by any of a variety of other suitable means that provide that the
shaft 112 will sever or break prior to thetip 120 becoming uncoupled from the shaft 112 (i.e., that provide that the maximum hinge torque is greater than the maximum shaft torque). For example, as shown inFIG. 12B , aportion 111 of theshaft 112 may be formed of a material of reduced strength and/or rigidity relative to the remaining portions 113A and 113B of theshaft 112 to define a region of weakness. In one representative embodiment, shaft portions 113A and 113B are formed of a biocompatible metal andshaft portion 111 is formed of a biocompatible plastic material. - With reference to
FIG. 13 , theshaft 112 may also carry a boss or stop 102 with a tine or lug 108 that selectively mates with a complementary slot or groove 110 in acannula 104 or other access device so as to limit rotational motion to a preset angle. In this arrangement, the slot or groove 110 defines a cam surface. The tine or lug 108 serves as a cam follower. The configuration of the cam surface and cam follower can vary, but preferably define a system in which a sweep of the cam follower across the full range of motion of the cam surface consistently creates a void of a predetermined size and shape. -
FIG. 13 shows an embodiment in which the cam surface takes the form of anelongated slot 110 in the circumferential margin of thecannula 104. The depth of reach is defined by the depth of the slot. That is, the length LS of the slot limits forward advancement of the stop 102 (and therefore the shaft 112) within thecannula 104. The width WS of the slot is greater than the width WC of the lug ortine 102 by a pre-determined amount. The angle of rotation is controlled by the extent of theslot 110, i.e., the difference in width between theslot 110 and the width of tine or lug 108 (i.e., the difference between WS and WC). Because the depth of the reach and the angle of rotation are pre-determined and constant, a sweep of the full range of motion of the cam surface and the cam follower consistently creates a void of a predetermined size and shape. For example,FIG. 14 illustrates the formation of a pre-determined pie-shaped void having an angle A1. The pre-determined void has a length corresponding to the length LS ofslot 110 as shown inFIG. 13 . Theslot 110 can be varied, e.g., by varying the width of theslot 110 along its length, to form voids of a desired, pre-determined shape and size. For example,FIG. 13A illustrates an alternative embodiment of aslot 110A in which theslot 110A is generally T-shaped and adapted to form a pre-determined void biased such that the most forward portion is of greater volume, with each volume also being wedge shaped. - In use, the
tool 100 is introduced into a targeted treatment site. Desirably, thetool 100 is introduced in a closed and minimally invasive procedure in which apercutaneous cannula 104 is advanced into a desired treatment region, e.g., a vertebral body. Introduction of the tool may be assisted by conventional visualization techniques, as previously described. Theshaft 112 is then passed through thecannula 104 and thecutting tip 120 is extended beyond the distal end of thecannula 104. The cuttingtip 112 is then pivoted to the desired position, i.e., any position between 0-90°. - The physician manipulates the
cutting tip 120 by sweeping theshaft 112 along the full range of motion of the cam surface and cam follower. Thestop 102 serves to limit translational movement of theshaft 112 along thecannula 104 and the lug ortine 108 limits rotational movement of theshaft 112 within thecannula 104 to create a void of a pre-determined size and shape. Because the void created is of a consistent and pre-determined size and shape, visualization is not required during cutting and void formation. The need for fluoroscopy or other visualization techniques is thereby reduced, limiting the patient's exposure to radiation or dyes. Upon completion of the procedure, the cuttingtip 112 is returned to the non-deployed position and thecannula 104 andtool 100 are withdrawn. - C. Turned and Tapered Trunk Embodiment
-
FIGS. 15 and 16 illustrate an alternative embodiment of atool 200 for creating voids in interior body regions. In this embodiment, thetrunk 232 is tapered and rotated 90° relative to the embodiment shown inFIGS. 4-9 so that the maximum width W of the trunk is perpendicular to the axis S of theshaft 212 when thetip 220 is deployed at a 90° angle A from the axis S of theshaft 212. - This arrangement minimizes the combined surface area of the
disc 234 andtrunk 232 in contact with the bone during scraping and cutting and thus minimizes transmission of significant force and stress to the hinge mechanism. - The
disc 234 has a convexfront surface 248 providing a dome-shape. Preferably, thedisc 234 has a diameter that is approximately the same as the diameter of theshaft 212, minimizing stress on thetip 220 during cutting and providing ease of passage of thetip 220 through a cannula. The domed configuration facilitates cutting and scraping of bone by producing leverage on the bone that allows thetip 220 to roll out of the bone easily. The domed configuration allows the tip to easily release from bone and to disengage from the bone for easy withdrawal. - The
disc 234 provides a 360° cutting surface and permits both translational and rotational movement of thecutting disc 234 when deployed at the desired angle A, as previously described. - D. Conical Trunk Configuration
-
FIGS. 17 and 18 illustrate another alternative embodiment of atool 300 for creating voids in interior body regions. In this embodiment, thetrunk 332 is tapered similar to the embodiment ofFIGS. 15 and 16 , but is conical. - The
trunk 332 also carries a dome-shapeddisc 334 allowing both translational and rotational cutting, similar to the embodiment ofFIGS. 15 and 16 . - The combined cutting surface of the
disc 334 andtrunk 332 is minimized and is designed to reduce the force and stress on the hinged mechanism by minimizing the contact area in the bone in all directions. The same profile (symmetrical cross-section of the conical trunk 332) is presented to the bone regardless of whether pushing or pulling (translational) force, turning (rotational) force, or a combination of both forces is applied. - II. Actuator Mechanism
- A. Thumbwheel Embodiment
-
FIGS. 19-22 illustrate one embodiment of an actuator mechanism for use with a void-forming tool. The actuator mechanism converts rotational motion into translational movement to control the deployment of a cutting tip. By way of illustration and not limitation, the actuator mechanism is illustrated with the cuttingtip 120 embodiment ofFIGS. 4-9 . - The actuator mechanism provides a
thumbwheel 150, an insert orcap 152,flange 154,plunger rod 156, androtational stop 158. Thethumbwheel 150,cap 152,flange 154,plunger rod 156, and stop 158 may be made of any suitable metal. The thumbwheel is seated in a free-floating manner in aslot 160 withinhandle 18. In a preferred embodiment, thehandle 18 is made of a strong and durable polymer plastic. - The
thumbwheel 150 extends, at least in part, from thehandle 18 for manipulation by the thumb or index finger of the user, as seen inFIG. 19 . Thethumbwheel 150 desirably includes grooves or knurls for easy grasping and manipulation. While thethumbwheel 150 may be configured for manual manipulation, it is contemplated that the actuator may also be power-driven. Thecap 152 is seated within thethumbwheel 150 and is desirably threaded or otherwise adapted to engage thewheel 150 so as to move with thewheel 150. Thecap 152 is connected, e.g., by welding, to theplunger rod 156. The transmission ratio, and therefore the amount of torque delivered, may be controlled by altering the thread pitch of thecap 152. - The
plunger rod 156 is sized and configured to be seated within theshaft 112 and to extend beyond theshaft 112 andthumbwheel 150 through bores in thecap 152 andthumbwheel 150. In the illustrated embodiment, thethumbwheel 150 andshaft 112 are positioned offset on thehandle 18 for placement of theshaft 112 between the index and middle finger, as seen inFIG. 19 . As shown inFIG. 21 , the distal end of theplunger rod 156 is coupled totether wire 166. Thetether 160 is looped to pass throughholes 168 in cuttingtip 120 belowpin 126 and is swaged or welded to theplunger rod 156. Movement ofplunger rod 156 regulates pressure on thetether 160 to actuate thetip 120 between the deployed and non-deployed positions. Thetether 160 will keep thetip 120 attached toshaft 112 in the event of breakage or failure ofpin 126 to permit easy removal. This prevents parts from being left behind during removal, thereby providing an additional safety feature. - While the illustrated embodiment shows the
tip 120 coupled to theshaft 112 and additionally tethered to theshaft 112 by arod 156, it is contemplated that thetip 120 may be additionally tethered to theshaft 112 by any of a variety of ways to provide that thetip 120 remains tethered to theshaft 112 if the coupling element (e.g., pin 126) becomes inoperable. For example, in an alternative embodiment, thetip 120 is additionally tethered toshaft 112 by a cable or pulley (not shown). - The
flange 154 is seated in aslot 170 within thehandle 18 and is coupled to theshaft 112, e.g., by welding or by interference or compression fit. Desirably, theflange 154 includes an offset bore such that there is only one way in which it may be seated withslot 170. Theflange 154 engages theshaft 112 within thehandle 18 and is sized and configured to essentially prevent rotational movement of theshaft 112. - In the illustrated embodiment, the
rod 156 has arectangular end 172 sized and configured to pass through a complementaryrectangular opening 174 in thestop 158. Thestop 158 engages therod 156 to prevent rotation of therod 156 during actuation. Thestop 158 is mounted to theplunger rod 156 and seated exterior to and againstslot 160. The arrangement of themetal stop 158 against theplastic slot 160 creates additional frictional forces to provide additional strength and reinforcement and serves to limit the amount of torque delivered to theplunger rod 156. - Rotation of the
thumbwheel 150 in a first direction advances theplunger rod 156 in a first direction along theshaft 112 to decrease tension onwire 166 and actuate deployment of thecutting tip 120. Rotation of thethumbwheel 150 in the opposite direction advances the plunger rod in the opposite direction within theshaft 112 and increases tension onwire 166 to actuate movement of thecutting tip 120 from the deployed to the non-deployed position. This arrangement converts the rotational movement of thethumbwheel 150 into the translational movement of theplunger rod 156. - In an alternative embodiment, shown in
FIG. 22 , alever 176 is hingedly attached to theplunger rod 156. Movement of thelever 176 in a first direction advances the plunger in a first direction to deploy thecutting tip 120, and movement of thelever 176 in the opposite direction advances theplunger 156 in a second direction to move thecutting tip 120 from the deployed to the non-deployed position. In this manner, thelever 176 permits the physician to continuously and conveniently move thetip 120 itself without moving theshaft 112 to create a reciprocating cutting motion. - B. Gear Embodiment
-
FIGS. 23-25 illustrate an embodiment of an actuator similar to the embodiment ofFIGS. 19-21 . The actuator provides a series of gears that interact to convert rotational motion to translational motion. - A
central gear 178 is similar in configuration and function to thethumbwheel 150 shown inFIGS. 19-21 . Thecentral gear 178 andshaft 112 are centered along the bottom of thehandle 18 for placement of theshaft 112 between the middle and ring fingers. -
Control knobs handle 18 for actuation by the user's thumb. Alternatively, thecontrol knobs control knob intermediate gear control knob central gear 178. Rotation of thecontrol knob intermediate gear central gear 178. Rotational movement of the control knob 180 is thereby converted into translational movement of theplunger rod 156, similar to the previous embodiment. - The symmetric design is designed for easy use by either the right or left hand. Further, the symmetric design allows easy rotation of the
handle 18. - In use, the
shaft 112 is advanced through acannula 104. The cuttingtip 120 is extended beyond the distal end of thecannula 104. Acontrol knob cutting tip 130 to the desired angle. The physician then creates a desired void by performing a series of translational and rotational movements of theshaft 112. The physician then returns the cuttingtip 120 to the non-deployed position. - If desired, the
handle 18 can then be rotated 180°. The opposingcontrol knob cutting tip 120 to a desired angle and another series of translational and rotational movements may be performed. - Once the desired void is created, the physician returns the
tip 120 to the non-deployed position. Thetool 100 is withdrawn from the patient. The physician then completes the procedure by filling the void with a bone cement or bone substitute, removing thecannula 104, and closing the incision. - The rate and/or force of cutting may be controlled by altering the transmission ratio. The force may be varied by varying the screw thread pitch or the transmission gear ratio. The rate of motion (i.e., speed of actuation) may be varied by manually or mechanically varying the speed of actuation.
- III. Alternative Embodiments of Mechanical Void Creators
- A. Shape Memory Alloys
-
FIGS. 26-28 illustrate an embodiment of atool 700 employing acutting tip 720 formed of a shape memory alloy. Use of a shape memory alloy allows for a smaller instrument as the hinge mechanism is no longer needed to activate the tip. Smaller instruments are safer and can access smaller vertebral bodies located higher in the spine. Smaller instruments are also less invasive and are less traumatic to the patient, allowing for a faster recuperation time. - A
malleable rod 701 formed of a shape memory alloy, e.g., Nitinol, is provided. It is contemplated that therod 701 may be of a variety of different diameters, tip configurations, and actuation angles. Therod 701 has a malleable or straightened state (FIGS. 26 and 27 ) and an activated or articulated predetermined, desired state (FIG. 28 ). Therod 701 is sized and configured for passage in a straightened or malleable state through acannula 104 into a vertebra or any bone surface. Once inserted into the bone, therod 701 returns to its predetermined, desired memory shape as a result of either the body temperature of the patient or by means of an electrical impulse (e.g., cooling, heat, voltage, etc.). For example, the distal end of therod 701 is activated to an angle, e.g., 90°, to form an elbow defining a cutting tip, as shown inFIG. 28 . In a representative embodiment, the length from the distal end of the rod to the bend is approximately 0.5 cm. Cutting of the bone is accomplished by a rotating motion or a push-pull motion or a combination of both motions, as previously described. Therod 701 desirably includes alumen 703 that permits introduction of a cooling or heating media (S), e.g., saline, to return therod 701 to a straightened state allowing for easy withdrawal. - In another embodiment, the
rod 701 is formed from a shape memory alloy with an activation temperature that is equal to room temperature, i.e., therod 701 is fully austenitic at room temperature. Therefore, therod 701 is fully articulated to its predetermined shape at room temperature. Therod 701 is chilled to a martensitic condition (malleable state) prior to insertion into bone, allowing for easy insertion. Therod 701 articulates to the predetermined, desired position upon returning to room temperature. This ensures that the proximal end of thecutting tip 720 attains full activation without depending on heat transfer from the distal end of the rod 701 (which is in contact with the patient) or any outside means (e.g., heat, voltage, etc.). Alumen 703 is provided in therod 701 to facilitate the introduction of a cooling media (S), e.g., chilled saline, to deactivate the material and allow for easy withdrawal. In another alternative embodiment, the alloy is super-elastic and thecannula 104 confines the pre-bent or formed cuttingtip 720 until the activation mechanism deploys thecutting tip 720 to extend beyond the cannula 104 (seeFIGS. 35A and 35B ). - In another alternative embodiment, the
rod 701 may be used to straighten thecannula 104 which is formed of a shape memory alloy. In this embodiment, the cuttingtip 720 is disposed on the shape memory cannula 104 (not shown). Thecannula 104 is educated to have a curved tip and therod 701 is moveably disposed within thecannula 104 to straighten thecannula 104 by fully engaging therod 701 within the cannula 104 (i.e. by pushing the rod 701) and to allow thecannula 104 and cuttingtip 720 to curve or articulate by pulling back on therod 701. Desirably, therod 701 is made of a rigid material, such as stainless steel. - In another embodiment, the activation temperature of the alloy is set at a temperature higher than body temperature. In this embodiment, the
rod 701 is malleable for insertion and withdrawal. Therod 701 achieves full activation to its predetermined shape only through the application of heat or voltage. This permits control of the change of the state of therod 701 from malleable to the predetermined shape, or any percentage there between, using a potentiometer or other suitable device. - The
rod 701 may be attached to a handle by a standard square drive or Hudson-style orthopedic fitting on the proximal end (not shown). A torque-regulating handle could be mated to therod 701 to allow for torque-limiting rotational scraping. - In one embodiment, the
rod 701 is fixedly attached or otherwise coupled to ahandle 18 having an actuator mechanism. For example, in the illustrated embodiment, therod 701 is coupled to athumbscrew 152 and is driven by an actuator mechanism similar to the mechanism illustrated inFIGS. 19 and 20 . Therod 701 is actuated (moved in fore and aft directions) within thecannula 104 by the actuator mechanism. This permits thecutting tip 720 to be retracted (FIG. 26 ) in a malleable state within thecannula 104 for easy insertion and withdrawal and then extended (FIG. 27 ) beyond the distal end of thecannula 104 within bone and activated for use (FIG. 28 ). - In a preferred embodiment, the
handle 18 includes aluer fitting 705. The fitting 705 is sized and configured to mate with a complementary luer fitting 707 on a fluid introduction device, e.g., asyringe 709, to establish fluid communication between thelumen 703 and thefluid introduction device 709. Fluid, e.g., chilled or heated saline, may be introduced from thesyringe 709 through therod lumen 703 to control movement of therod 701 between the malleable (deactivated) and activated states. - In an alternative embodiment, shown in
FIGS. 29 and 30 , acutting tip 720A of a desired configuration is formed at the distal end of themalleable rod 701. Thetip 720A may be a separate piece welded to therod 701, or thetip 720A may be carved or otherwise formed in therod 701, e.g., by conventional machining techniques. In the illustrated embodiment, the cuttingtip 720A is of a conical trunk and domed disc configuration similar to the embodiment illustrated inFIGS. 17 and 18 . It is apparent, however, that the configuration of thecutting tip 720A can be varied according to the procedure being performed and/or to accommodate individual anatomy. In one embodiment, theentire rod 701, including thecutting tip 720A, are formed of the shape memory alloy. Therod 701 yields from a malleable state (FIG. 29 ) to the activated state (FIG. 30 ) as previously described. Therod 701 desirably includes alumen 703 to permit introduction of a fluid media to control movement between the deactivated and activated states, as also previously described. - In an alternative embodiment, illustrated in
FIGS. 31 and 32 , thetip 720A and adistal portion 711 of therod 701 are formed of a shape memory alloy. Arod body 713 is formed of any suitable biocompatible, surgical grade material. Thedistal portion 711, carrying thecutting tip 720A, is welded or otherwise fixed to therod body 713. Thedistal portion 711 of therod 701 yields from a malleable state (FIG. 31 ) to the activated state (FIG. 32 ). Therod 701 desirably includes alumen 703 to permit introduction of a fluid media to control movement between the deactivated and activated states. In an alternative embodiment, therod 701 may include adual lumen 714 so that fluid media can circulate through theshaft 112 and desirably through the cutting tip 720 (seeFIG. 33 ) In another alternative embodiment, therod 701 may include athroughbore 703A to accommodate more thermal flow (seeFIG. 34 ). - B. Alternative Mechanical Void Creators
-
FIG. 36 shows an alternative embodiment of amechanical tool 400 for creating a void in an interior body region. Ashaft 412 carries a sharp, stout,metal spring 420 on the end of ashaft 412. Theshaft 412 can be rotated against the direction of thespring 420 causing it to cut bone (or other tissue) in an expanding fashion. Thetool 400 is sized and configured to be introduced through a cannula (not shown) with thespring 420 extending beyond the cannula and theshaft 412 rotated into the tissue a short distance at a time. Theshaft 412 can then be withdrawn to remove any captured tissue. If no tissue is captured, thetool 400 is reintroduced farther into the tissue and tissue removal is again attempted. Thetool 400 may also be used to loosen tissue to allow better cutting and/or removal by other mechanical tools. -
FIG. 37 shows another embodiment of amechanical tool 500 for creating a void in an interior body region. Two ormore fingers 520 are carried on the distal end of ashaft 512. Preferably, theshaft 512 carries fourfingers 520, twofingers 520 facing each other. Thefingers 520 are introduced into the tissue through a cannula (not shown), and then mechanically closed with a pulley-type system or other similar system to grab tissue for extraction. Desirably, thefingers 520 are adapted to further expand as the size of the void increases. It is apparent that the length of thefingers 520 may be chosen to suit the intended use and particular individual anatomy. -
FIGS. 38 and 39 show another embodiment of amechanical tool 600 for creating a void in an interior body region. The tool includes a hinged void-creatingdevice 620 carried on the distal end of theshaft 612. The void-creatingdevice 620 may be used to create a void or to loosen tissue to allow better cutting and removal by other mechanical tools. - The void-creating
device 620 provides for adjusting the height of thedevice 620. Apositioning rod 621 is coupled to thedevice 620 for expanding and contracting thedevice 620. The height may be adjusted by drawing in therod 621 to increase the height H and pushing out on the rod to decrease the height H of thedevice 620. Calibrated markings (not shown) may be provided on the rod handle to indicate the dimension of thedevice 620 as therod 621 is drawn back or advanced. The height H may also be chosen to suit the intended use and particular individual anatomy. -
FIG. 40 shows an embodiment similar toFIGS. 35 and 36 , but additionally providing a spring blade or series ofspring blades 623 for more aggressive cutting. Thespring blades 623 are coupled to the last blades out of the cannula and desirably pre-bent to cut parallel to the end plates. - IV. Creation of Voids in Bone
- Two or more different mechanical cutting tools of the type described may also be used in combination to form a cavity or void of a desired size and configuration in a targeted bone. In addition, one or more mechanical cutting tools may be used in combination with one or more expandable void-creating tools to form the desired void. Expandable structures for creating voids in bones are described in U.S. Pat. Nos. 4,969,888, 5,827,289, 5,972,015, 6,235,043, 6,248,110, and 6,607,544, all of which are herein incorporated by reference.
- Fracture reduction and deformity correction is influenced by a variety of factors, including, but not limited to, acuteness of the fracture, bone quality (e.g. osteoporosis, bone cancers, steroid-induced osteoporosis), and healing. In some fractures, expansion of the expandable structure may be distorted by a region or regions of hard bone. This results in a high pressure within the expandable structure and low volume of expansion media within the expandable structure. The use of a mechanical cutting tool to selectively break up the region of hard bone will allow the expandable structure to achieve a more consistent and reliable fracture reduction. Mechanical cutting or scraping tools will break bone, but an expandable structure is required for the en-masse endplate reduction and deformity correction.
- In use, an access path to bone is made using a conventional access cannula by techniques commonly known in the art. A first void creator, which may be a mechanical cutting tool or an expandable structure, is then introduced into a bone to create a void. The first void creator is then removed. A second void creator, which may be the same as or different from the first void creator, is then inserted into the bone to enlarge or further define the void to form a void of a desired size and configuration. The second void creator is then removed. If desired, a third void creator, which may be the same or different from the first and/or second void creators, may then be introduced to further enlarge and define the void and then removed. Desirably, a filling material, e.g., bone cement or bone substitute, is then injected or otherwise introduced into the void to fill the void.
- In one embodiment, illustrated in
FIGS. 41A-41D , a firstmechanical cutting tool 800A and a secondmechanical cutting tool 800B, which may be different in size and/or configuration from thefirst cutting tool 800A, are used to create avoid 802 of a desired size and configuration. Anaccess cannula 104 is percutaneously introduced to provide an access path into a bone, e.g., a vertebra 142 (FIG. 41A ). The firstmechanical cutting tool 800A is introduced through thecannula 104 into thecancellous bone 39 of thevertebra 142. The cuttingtip 820A is manipulated in a series of longitudinal and/or rotational movements to create a void 802 in the cancellous bone 39 (FIG. 41B ). Thefirst cutting tool 800A is then removed. The secondmechanical cutting tool 800B is then introduced and manipulated in a series of longitudinal and/or rotational movements (FIG. 41C ). Thesecond cutting tool 800B desirably has acutting tip 820B of a different size and/or configuration to enlarge and/or otherwise further define the void 802 created by thefirst tool 800A. For example, in the illustrated embodiment, thesecond cutting tool 800B has acutting tip 820B of a greater height than thefirst cutting tip 820A to enlarge thevoid 802, but is of a similar configuration. Thesecond cutting tool 800B is then removed. Afiller material 804, e.g., bone cement or bone substitute, may then be introduced into the void 802 to fill the void 802 (FIG. 41D ). - Alternatively, as shown in
FIGS. 42A-42E , after removal of thesecond cutting tool 800B, anexpandable structure 900 may be introduced through thecannula 104 and expanded to enlarge and/or further define the void 802 created by the first and second mechanical cutting tools 802A and 802B. While in the illustrated embodiment theexpandable structure 900 takes the form of a balloon adapted to expand or form a void by compression of cancellous bone, theexpandable structure 900 may be any suitable device which can be expanded to enlarge and/or further define the void. For example, theexpandable structure 900 may also be a mechanical jack, retractor, or spring. Desirably, theexpandable structure 900 has a collapsed condition permitting insertion of theexpandable structure 900 through thecannula 104 and an expanded condition in which theexpandable structure 900 compactscancellous bone 39 upon expansion within thecancellous bone 39. Theexpandable structure 900 is then removed. The void 802 may then be filled, as previously described. - In another embodiment, illustrated in
FIGS. 43A-43D , a firstexpandable structure 900A and a secondexpandable structure 900B, which may be different in size and/or configuration from the firstexpandable structure 900A, are used to create avoid 802 of a desired size and configuration. Anaccess cannula 104 is percutaneously introduced to provide an access path into a vertebra 142 (FIG. 43A ). The firstexpandable structure 900A is introduced through thecannula 104 in the collapsed condition into thecancellous bone 39 of thevertebra 142. Theexpandable structure 900A is then expanded to create a void 802 in cancellous bone 39 (FIG. 43B ). The firstexpandable structure 900A is then removed. The secondexpandable structure 900B is then introduced and expanded (FIG. 43C ). The secondexpandable structure 900B is desirably of a different size and/or configuration such that expansion of the secondexpandable structure 900B enlarges and/or otherwise further defines the void 802 created by the firstexpandable structure 900A. For example, in the illustrated embodiment, the secondexpandable structure 900B is of a larger volume, but is of a similar configuration. It is contemplated, however, that the secondexpandable structure 900B may be of a different configuration than the firstexpandable structure 900A. The secondexpandable structure 900B is then removed. Afiller material 804, e.g., bone cement or bone substitute, may then be introduced into the void 802 to fill the void 802 (FIG. 43D ). - Alternatively, as shown in
FIGS. 44A-44E , after removal of the secondexpandable structure 900B, if desired, amechanical cutting tool 800 may be introduced through thecannula 104 to enlarge and/or further define the void 802 created by the first and secondexpandable structures cutting tool 800 is then removed. The void 802 may then be filled, as previously described. -
FIGS. 45A-45E illustrate another method of creating a void 802 in bone of a desired size and configuration. Anaccess cannula 104 is percutaneously introduced to provide an access path into a vertebra 142 (FIG. 45A ). A firstexpandable structure 900A is introduced through thecannula 104 in the collapsed condition into thecancellous bone 39 of thevertebra 142. Theexpandable structure 900A is then expanded to create a void 802 in cancellous bone 39 (FIG. 45B ). Because the reticulum of thecancellous bone 39 may be somewhat dense, it may be difficult for theexpandable structure 900A to sufficiently compact thecancellous bone 39 to permit full expansion of theexpandable body 900A. This may occur with older fractures or in normal bone that has been injured by trauma, but is not necessarily osteoporotic. In this case, theexpandable structure 900A may expand preferentially in a given direction depending on the density of the reticulum, but is not able to expand to its full preformed shape, as seen inFIG. 45B . The firstexpandable structure 900A is then removed. - A
mechanical cutting tool 800 is then introduced (FIG. 45C ). The cuttingtip 820 is manipulated in a series of longitudinal and/or rotational movements to enlarge and/or otherwise further define the void 802 created by theexpandable structure 900A. Thecutting tool 800 is then removed. - If desired, a second
expandable structure 900B, which may be of a different size and/or configuration from the firstexpandable structure 900A, is then introduced prior to filling the void 802 (FIG. 45D ). Use of thecutting tool 800 to break or cut the reticulum and expand thevoid 802 allows the secondexpandable structure 900A to fully expand. The secondexpandable structure 900A is then expanded to enlarge and/or otherwise further define the previously createdvoid 802. The secondexpandable structure 900B is then removed. Alternatively, instead of a secondexpandable structure 900B, the firstexpandable structure 900A may be reintroduced, re-expanded, and then removed. Afiller material 804 may then be introduced into the void 802 to fill the void (FIG. 45E ). - In an alternative method shown in
FIGS. 46A-46E , anaccess cannula 104 is percutaneously introduced to provide an access path into a vertebra 104 (FIG. 46A ). Anexpandable structure 900 is introduced and expanded to create a void 802 in cancellous bone 39 (FIG. 46B ). The firstexpandable structure 900A is then removed. - A first
mechanical cutting tool 800A is then introduced (FIG. 46C ). The cuttingtip 820A is manipulated in a series of longitudinal and/or rotational movements to enlarge and/or otherwise further define the void 802 created by theexpandable structure 900. Thecutting tool 800 is then removed. - If desired, a second
mechanical cutting tool 800B, which may be of a different size and/or configuration from the firstmechanical cutting tool 800A, is then introduced prior to filling the void 802 (FIG. 46D ). The cuttingtip 820B is manipulated in a series of longitudinal and/or rotational movements to enlarge and/or otherwise further define the void 802 created by theexpandable structure 900 andfirst cutting tool 800A. Thesecond cutting tool 800B is then removed. Afiller material 804 may then be introduced into the void 802 to fill the void 802 (FIG. 46E ). - In an alternative method shown in
FIGS. 47A-47E , a firstmechanical cutting tool 800A is introduced and manipulated in a series of longitudinal and/or rotational movements to create avoid 802. Thefirst cutting tool 800A is then removed. Anexpandable structure 900 is then introduced and expanded to enlarge and/or otherwise further define the void 802 created by thefirst cutting tool 800A. Theexpandable structure 900 is then removed. - If desired, a second
mechanical cutting tool 800B, which may be of a different size and/or configuration from the firstmechanical cutting tool 800A, is then introduced prior to filling thevoid 802. The cuttingtip 820B is manipulated in a series of longitudinal and/or rotational movements to enlarge and/or otherwise further define the void 802 created by theexpandable structure 900A and first cutting tool 802A. The second cutting tool 802B is then removed. Afiller material 804 may then be introduced into the void 802 to fill thevoid 802. - Alternatively, as seen in
FIGS. 48A-48E , instead of a second mechanical cutting tool, a secondexpandable structure 900B, is introduced and expanded to enlarge and/or otherwise further define the void created by the firstexpandable structure 900A andfirst cutting tool 800A.
Claims (9)
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US10/893,155 US20050240193A1 (en) | 2003-09-03 | 2004-07-16 | Devices for creating voids in interior body regions and related methods |
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AU2004270128A1 (en) | 2005-03-17 |
EP1663029A4 (en) | 2010-06-09 |
AU2004270128B2 (en) | 2010-12-23 |
KR101132644B1 (en) | 2012-04-02 |
KR20060133952A (en) | 2006-12-27 |
CN1845709B (en) | 2012-06-20 |
EP1663029A2 (en) | 2006-06-07 |
CA2537048C (en) | 2010-01-12 |
CA2537048A1 (en) | 2005-03-17 |
JP4555293B2 (en) | 2010-09-29 |
MXPA06002541A (en) | 2006-06-20 |
WO2005023085A2 (en) | 2005-03-17 |
US20050113838A1 (en) | 2005-05-26 |
US6923813B2 (en) | 2005-08-02 |
JP2007503911A (en) | 2007-03-01 |
CN1845709A (en) | 2006-10-11 |
IL173842A0 (en) | 2006-07-05 |
WO2005023085A3 (en) | 2005-05-12 |
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