Patent Application
20050234493
This disclosure relates to methods and devices for cavity creation in mammalian bone tissue.
Vertebral compression fractures and other bone damage may result from degenerative bone disease. When cancellous bone is diseased, the surrounding cortical bone may be more prone to compression fracture or collapse, because the cancellous bone no longer provides interior support for the surrounding bone.
A common bone disease that may lead to vertebral compression fractures and other bone damage is osteoporosis. Osteoporotic loss of calcium and phosphate salts in the bone may result in decreased bone mass and a loss of bone-structure strength.
Bone mass loss, decreased bone-structure strength, vertebral compression fractures and other bone damage also may be caused by a number of other diseases or conditions. For example, osteolysis, avascular necrosis, and bone cancer (e.g., osteolytic metastasis, myeloma, and malignant tumors of the bone marrow) predispose the bone to fracture or collapse. Other pathologies that may be related to such progressive bone diseases and vertebral compression fractures include posture change (slumping), decubitus ulcers (bed sores), hemangiomas, and neoplasms.
Vertebral compression fractures may cause the spine to compress resulting in kyphosis (round back) or scoliosis (spinal curvature). As the kyphosis increases, a person's head may migrate forward, causing chronic neck tension. Increased kyphosis also may limit one's ability to breathe freely. Vertebral compression fractures may impair a person's ability to walk unassisted; it may lead to a loss of height, severe back pain and deformity and cause prolonged or permanent disability or even death. Further, degenerative vertebral bone diseases may lead to the collapsing of the vertebra and the onset of painful bone-on-bone rubbing. Other types of bone damage may affect a patient in numerous ways.
Vertebroplasty is a conventional procedure that may be used to treat vertebral compression fractures. U.S. Pat. No. 6,273,916 (issued Aug. 14, 2001) and U.S. Pat. No. 6,048,346 (issued Apr. 11, 2000) relate to vertebroplasty. In vertebroplasty, bone cement may be used to reinforce a collapsed vertebra to provide increased structural support thereby relieving pain associated with undue pressure on the nerves.
A second conventional procedure is kyphoplasty, which is a technique that combines vertebroplasty with balloon catheter technology. U.S. Pat. No. 4,969,888 (issued Nov. 11, 1990); U.S. Pat. No. 5,108,404 (issued Apr. 28, 1992); U.S. Pat. No. 5,972,015 (issued Oct. 26, 1999); U.S. Pat. No. 6,066,154 (issued May 23, 2000); U.S. Pat. No. 6,235,043 (issued May 22, 2001); U.S. Pat. No. 6,423,083 (issued Jul. 23, 2002); U.S. Pat. No. 6,607,544 (issued Aug. 19, 2003); U.S. Pat. No. 6,623,505 (issued Sep. 23, 2003) and U.S. Pat. No. 6,663,647 (issued Dec. 16, 2003), relate to kyphoplasty.
Methods and devices for cavity creation in mammalian bone tissue are disclosed. In one embodiment, methods and devices are disclosed for cavity creation in weak, damaged, or diseased mammalian bone tissue, such as the cancellous bone tissue of mammalian vertebrae.
In another embodiment, methods and devices are disclosed for introducing an elastomeric material into bone tissue and applying a deforming force to the elastomeric material, whereupon the elastomeric material expands within the bone tissue to create a cavity. The deforming force applied to the elastomeric material is then removed thereby allowing the elastomeric material to resume its original shape. The elastomeric material is then withdrawn from the newly formed cavity.
The cavity so created can then be filled with a biocompatible filler, such as bone cement, using standard methods in the art. Preferably, the cavity is filled with bone cement using a Plexis™ or twistOR PrePack™ system, which are described in more detail below.
In some implementations, one or more of the following advantages may be present. The methods and devices disclosed may be useful to repair, stabilize, and reinforce weak, damaged, or diseased mammalian bone tissue and, therefore, may be useful to treat bone weakening and loss of bone mass, bone fracture, bone defects, and bone disease (such as, vertebral weakening and vertebral fractures, other bone damage and particularly vertebral compression fractures). Such conditions may have resulted from degenerative bone diseases, such as osteoporosis, osteolysis, avascular necrosis, bone cancer (e.g., osteolytic metastasis, myeloma, and malignant tumors of the bone marrow), and other diseases of bone that induce loss of bone mass or otherwise predispose the bone to weakening, fracture, or collapse.
These and other features, aspects, and advantages will become better understood with regard to the following description, examples, appended claims, and accompanying drawings where:
1.0 Devices
According to one implementation, a cavity creation device introduces an elastomer into bone tissue, such as a vertebral body, applies deforming forces to the elastomer to cause the elastomer to expand in the tissue to create a cavity. Upon removal of the deforming force, the elastomer withdraws back into the device leaving an empty cavity for subsequent filling with bone cement.
Referring to
The illustrated cavity creation device 1000 is adapted to be inserted into delivery tube device 1050, wherein delivery tube device 1050 is first introduced into the vertebral body by any method well-known by those having ordinary skill in the art. Once delivery tube device 1050 is appropriately positioned within the vertebral body, cavity creation device 1000 is slid into delivery tube device 1050 such that the portion of elastomer holding sleeve 1080 having guide rod 1090 extending from sleeve 1080 is exposed from the end of delivery tube device 1050, as shown in
As shown in
When elastomer holding sleeve 1080 and plunger 1010 are completely engaged through delivery tube device 1050, as in
To initiate elastomer expansion and cavity creation, plunger 1010 must be compressed and driven through elastomer holding sleeve 1080 to apply a deforming force to elastomer 1070. One embodiment of plunger 1010 includes a simple manual pushing mechanism to compress plunger 1010 through elastomer holding sleeve 1080 and deliver the force upon elastomer 1070. In this embodiment, as shown in
Alternatively, the head of threaded plunger 1150 may be driven into an air baffle thereby creating an increased pressure acting on elastomer 1070. The ratcheted crank handle 1130 provides a precise and quantified delivery of plunger force onto elastomer 1070. Removal of the plunger force is achieved by applying a reverse action to ratcheted crank handle 1130.
When the force is applied to elastomer 1070 by plunger 1010 (or threaded plunger 1150), elastomer 1070 will begin to expand in the path of least resistance, or toward bumper 1100. Bumper 1100, which maintains a fixed position at the end of guide rod 1090, provides a resistive force to elastomer 1070 when sufficient plunger force is applied to elastomer 1070 to cause elastomer 1070 to make contact with bumper 1100. As depicted in
When the physician reaches the desired cavity size by means of mechanical (number of revolutions or distance compressed) and visual (CT scan) determinations, he or she can cease plunger movement and begin to back the plunger off elastomer 1070. Withdrawal of the plunger force will allow elastomer 1070 to move toward the area of least pressure or resistance, which will draw elastomer 1070 back into elastomer holding sleeve 1080. Once elastomer 1070 is completely retracted back into elastomer holding sleeve 1080, cavity creation device 1000 may be removed from delivery tube device 1050 allowing for introduction of a cement mixture into the created cavity via delivery tube device 1050.
1.1 Substitution Of Elastomer with a Collapsible Segmented Elastomeric Tube
One to many elastomer segments 1200 of the collapsible segmented elastomeric tube 1180 are exposed at the end of the elastomer holding sleeve 1080 of cavity creation device 1000, as shown in
To create the cavity in the vertebral body, cavity creation device 1000 according to this embodiment is inserted through delivery tube device 1050, previously introduced into the vertebral body. The bottom end of cavity creation device 1000 protrudes past the bottom of delivery tube device 1050. Once cavity creation device 1000 is fully inserted into delivery tube device 1050, plunger 1010 is driven through elastomer holding sleeve 1080 by pushed manual force or by force generated by ratcheted crank handle 1130, as described in detail above. As plunger 1010 is driven through elastomer holding sleeve 1080, the elastomer segment 1200 located at the bottom of elastomer holding sleeve 1080 will collapse upon itself and spread outward in a radial direction. This may occur as the result of the elastomer segment 1200 being forced against a counterforce being applied by the bumper. As continued pressure is applied to plunger 1010, the other elastomer segments 1200 of collapsible segmented elastomeric tube 1180 will collapse on to one another in sequential order until all of the elastomer segments 1200 have collapsed. The elastomer segments 1200 spread within the vertebral body and push against the cancellous bone within the vertebral body thereby creating a cavity therein.
Once the desired cavity is created in the vertebral body, collapsible segmented elastomeric tube 1180 is removed from the newly formed cavity by retracting plunger 1010 out of elastomer holding sleeve 1080. Upon removal of the force applied by plunger 1010, the elastomer segments 1200 will retract to their original size and shape and slide back into their original alignment. When plunger 1010 is fully retracted within elastomer holding sleeve 1080, the entire cavity creation device 1000 is removed from delivery tube device 1050.
1.2 Bone Cavity Formation by Substituting Elastomer with a Primary Elastomer Encapsulated within a Secondary Casing
In another embodiment, elastomer 1070 (see
Plunger 1010 is inserted into elastomer holding sleeve 1080, whereupon primary elastomer 1070 is adjacent to plunger head 1030 or separated from the plunger head by an air baffle. When elastomer holding sleeve 1080 and plunger 1010 are completely engaged through delivery tube device 1050, the secondary casing region (which defines the enclosed cylindrical space that is located between elastomer holding sleeve 1080 and bumper 1100) is exposed, and the device is ready for use.
When used to treat a vertebral fracture, delivery tube device 1050 is inserted in the patient's vertebrae and the cavity creation device is pushed into the cancellous bone inside the patient's vertebral body. The secondary casing region extends within the bone tissue. Bumper 1100 is pointed to allow for easier movement through the spongy bone.
In operation, plunger 1010 forces primary elastomer 1070 toward bumper 1100 into the cylindrical space defined by the secondary casing. Plunger 1010 can be operated in one of two ways; a simple manual pushing or through ratcheted crank handle 1130 that utilizes a threaded plunger to deliver a more precise and quantified pressure. As plunger 1010 compresses elastomer 1070 against bumper 1100, elastomer 1070 expands in the path of least resistance, which is the region of the secondary casing. Bumper 1100, at the end of elastomer holding sleeve 1080, is immovable and acts to force elastomer 1070 to expand outward, in a direction perpendicular to guide rod 1090 within the secondary casing, causing the secondary casing to expand which forces bone tissue outward thereby forming a cavity within the vertebral body.
When the surgeon reaches the desired cavity size by means of mechanical (for example, the number of revolutions of delivery tube device handle 1060 or distance compressed) and/or visual (CT scan) determinations, he or she withdraws plunger 1010 through elastomer holding sleeve 1080. Upon withdrawal of plunger 1010, elastomer 1070 completely retracts within elastomer holding sleeve 1080. Cavity creation device 1000 can then be removed and bone cement can be introduced into the created cavity.
1.3 Bone Cavity Formation by Way of an Implantable Elastomeric Casing Expanded with Bone Cement or other Biocompatible Filler
In another embodiment, bone fractures, such as vertebral fractures can be treated by inserting a biocompatible, elastomeric casing into bone tissue and forcing a biocompatible filler, such as polymethylmethacrylate (PMMA) bone cement, into the casing whereby the casing expands within the bone tissue to correct and reinforce the bone structure. The expanded casing and biocompatible filler are left within the vertebral body as an implant. Preferably, the elastomer casing is chemically resistant to the biocompatible filler. It also may be preferable that the elastomer casing is approved by the Food and Drug Administration (FDA) for implantation within the human body.
Referring to
The cavity is created by forcing biocompatible filler, such as prepared bone cement, from an approved mixing device through elastomer holding sleeve 1080 and into the elastomeric casing. The biocompatible filler may be forced against a bumper at an end of the elastomeric casing. The casing expands thereby pushing bone tissue outward to create a bone cavity completely filled by the elastomer-encased biocompatible filler implant. Once the elastomer-encased biocompatible filler implant has reached the desired size, the surgeon disengages elastomer holding sleeve 1080. The elastomer-encased biocompatible filler implant remains in the human body as an FDA approved implantable device.
2.0 Elastomers
Elastomeric materials (generally polymers) generally deform upon application of a deforming force and substantially resume their original dimensions after the deforming force is removed. In a preferred embodiment, the elastomeric materials may be elastomers. Elastomers are rubbery polymers that can be expanded upon application of a compressive force or stretched easily to high extensions and rapidly recover their original dimensions when the applied stress is released. Preferably, elastomers are semi-crystalline. For a general discussion of elastomers, see R. J. YOUNG & P. A. LOVELL, INTRODUCTION To POLYMERS 11 (2d ed., Nelson Thomes Ltd 2002), hereby incorporated herein by reference. In general, except in the case of thermoplastic elastomers, the polymeric backbone is crosslinked. Exemplary functional, physical, and mechanical characteristics of suitable elastomeric materials are described in more detail below.
2.1 Functional Characteristics of Elastomers
One of skill in the art can readily identify elastomers according to desired functional, physical, and mechanical characteristics. Elastomers are preferably biocompatible and have suitable expansion and elongation properties, glass transition temperatures, crystallinity, and crosslinking.
2.1.1 Biocompatibility
Preferably, elastomeric materials are compatible with mammalian tissue, suitable for implantation in mammals, interact with mammalian tissue in a nontoxic manner, and do not destroy the cellular constituents of the body fluid with which they interface. M. Szycher, et al., POLYURETHANE ELASTOMERS IN MEDICINE 234-244 (1990); S. Dumitriu & D. Dumitriu, BIOCOMPATIBILITY OF POLYMERS 100-158 (1990), both of which citations are hereby incorporated herein by reference.
Methods for testing biocompatibility are well known in the art, see e.g., the Food and Drug Administration's (FDA) guidance and International Organization for Standardization (ISO) 10993 standards, hereby incorporated herein by reference, which provides a set of criteria for testing biocompatibility of elastomers based on the duration of the implantation and the nature of the contact with the biomaterial. Other methods for testing biocompatibility are described in the literature. For cytotoxicity tests, see e.g., M. J. Menconi, et al., Molecular Approaches to the Characterization of Cell and Blood/Biomaterial Interactions, 7 J. CARDIAC SURG. 177-187 (1992); B. Sadd, et al., Interactions of Osteoblasts and Macrophages with Biodegradable and Highly Porous Polyesterurethane Foam and Its Degradation Products, 32 J. BIOMED. MATER. RES. 355-366 (1996); H. Oshima & M. Nakamura, A Study On Reference Standard for Cytotoxicity Assay of Biomaterials, 4 BIOMED. MATER. ENG. 327-332 (1992), each of which references is hereby incorporated herein by reference. The crystal violet, neutral red, or tryptan blue cell viability screening tool is a commonly used tests to determine toxicity, see e.g., S. A. Rosenbluth, et al., Tissue Culture Method for Screening Toxicity of Plastic Materials to be Used in Medical Practice, 54 J. PHARMACEUT. SCI. 156-159 (1965), hereby incorporated herein by reference. For examples of sensitization assays of irritation, see e.g., B. Huang, et al., Cellular Reaction to Vascugraft Polyesterurethane Vascular Prosthesis: In Vivo Study In Rats, 13 BIOMATERIALS 209-216 (1992); for examples of hemocompatibility and blood interaction assays, see e.g., AFNOR. Nor. Biological Evaluation of Medical Devices, Part 4: Selection of Tests for Interactions with Blood, AFNOR, Paris, 1994, hereby incorporated herein by reference.
Most preferably, the elastomers are manufactured using appropriate principles of current Good Manufacturing Practice (cGMP) regulations and meet the Food and Drug Administration's (FDA) guidance and International Organization for Standardization (ISO) 10993 standards or devices for implantation into tissue or bone for a limited duration of less than 24 hours.
2.1.2 Expansion/Elongation
Preferably, elastomers expand in volume upon application of a compressive force and elongate upon application of a stretching force. In general elastomer expansion is directly related to elastomer elongation.
Elastomer expansion and elongation can be measured according to the procedure set forth in American Society for Testing and Materials (“ASTM”) D412 “Standard Test Methods for Vulcanized Rubber and Thermoplastic Elastomers-Tension” or the corresponding Dow Corning Corporate Test Method (“CTM”) 0137 Å, both of which citations are hereby incorporated herein by reference. ASTM test procedures are compiled, reviewed, and published by the American Society for Testing and Materials, an independent and voluntary standards development organization.
Expansion of an elastomer is generally defined as the percentage of volume increase per unit of compressive pressure. Preferably elastomers exhibit an expansion percentage of from about 100 percent to about 1000 percent of their original volume upon application of a compressive pressure of from about 25 psi to about 500 psi to an elastomer of dimensions suitable for use in a cavity creation device.
Elongation is generally defined as the increase in extension produced by a tensile stress, expressed numerically as a fraction or percentage of the elastomer's initial length. Preferably elastomers exhibit an elongation percentage of from about 100 percent to about 1000 percent of their original length upon application of a retraction force of from about 25 psi to about 500 psi to an elastomer of dimensions suitable for use in a cavity creation device.
Preferably, upon removal of the stress that caused the expansion or elongation, elastomers used revert to dimensions of from about 100 percent to about 110 percent of their original volume or length, more preferably, of from about 100 percent to about 103 percent of their original volume or length.
2.1.3 Glass Transition Temperature
As an elastomer is cooled, it becomes more viscous and flows less readily. As the temperature is reduced further, the elastomer transitions from a rubbery consistency to a relatively hard polymer glass. The temperature range at which the elastomer undergoes the transformation from a rubbery consistency to a relatively hard polymer glass is known as the glass transition temperature. For a general discussion, see R. J. YOUNG & P. A. LOVELL, INTRODUCTION To POLYMERS 292-300 (2d ed., Nelson Thomes Ltd 2002), hereby incorporated herein by reference.
Preferably, the elastomer has a glass transition temperature higher than the temperature at which it will be used. ID. at 300. Thus, preferably, the glass transition temperature of the elastomer is lower than the body temperature of the mammal to be treated, preferably, below about 15° C., more preferably, below about 10° C.
The glass transition temperature of elastomers is determined by well-known procedures such as those described in R. J. YOUNG & P. A. LOVELL, INTRODUCTION To POLYMERS 292-298 (2d ed., Nelson Thornes Ltd 2002), hereby incorporated herein by reference. For example, the glass transition temperature can be determined by measuring the specific volume of a polymer sample as a function of the temperature. Kovacs, 30 J. POLY. SCI. 131 (1958), hereby incorporated herein by reference.
2.1.4 Crystallinity
In another preferred embodiment, elastomers are semi-crystalline (i.e., have a relatively low degree of crystallinity). R. J. YOUNG & P. A. LOVELL, INTRODUCTION To POLYMERS 300 (2d ed., Nelson Thornes Ltd 2002). The degree of crystallinity can be measured by well-known procedures, such as those described in ID. at 241-285, hereby incorporated herein by reference. The preferred degree of crystallization of elastomers will generally depend on the identity and desired properties of the elastomer. One of skill in the art might readily determine the degree of crystallization needed for a particular elastomer by measuring the physical properties of the elastomer as a function of crystallinity.
2.1.5 Crosslinking
In still another preferred embodiment, elastomers are lightly crosslinked. R. J. YOUNG & P. A. LOVELL, INTRODUCTION To POLYMERS 300 (2d ed., Nelson Thornes Ltd 2002). However, chemical crosslinks are less important when a thermoplastic is used as the elastomeric material because thermoplastic elastomers display advantageous elastomeric properties with little or no crosslinking. ID. at 303-306.
The degree of crosslinking can be determined by well-known methods, such as those described in ID. at 300-305 and references cited therein, hereby incorporated herein by reference. The preferred degree of crosslinking of elastomers will generally depend on the identity and desired properties of the elastomer. One of skill in the art might readily determine the degree of crosslinking needed for a particular elastomer by measuring the physical properties of the elastomer as a function of crosslinking.
2.2 Examples of Elastomers
Suitable elastomers include, but are not limited to, (1) general use elastomers, such as natural rubber, synthetic polyisoprene, styrene butadiene copolymers, and polybutadienes; (2) special elastomers, such as ethylene propylene and diene copolymers, isobutylene isoprene copolymers, haloisobutylene isoprene copolymers, nitrile butadiene copolymers, and polychloroprenes; (3) very special elastomers, such as high thermal and/or chemical resistance elastomers, such as polysiloxane or silicone elastomers, fluorocarbon elastomers (e.g., Viton® A, Viton B, Viton GF, and Viton GFLT, all commercially available from DuPont Dow Elastomers LLC), chloropolyethylene and chlorosulfonyl polyethylenes, polyacrylates, ethylene vinyl acetate elastomers, ethylene methyl acrylate, hydrogenated nitrile elastomers, and epichlorhydrin elastomers; and (4) thermoplastic elastomers, such as Surlyn® (made by DuPont), styrene-butadiene-styrene polymer (which comprises short block of polystyrene followed by a longer block of polybutadiene, followed by another short block of polystyrene), and segmented copolymers prepared by the reaction of diisocyanate with a prepolymer polyol and a short chain diol. An example of this preparation procedure is described in R. J. YOUNG & P. A. LOVELL, INTRODUCTION To POLYMERS 117-118 (2d ed., Nelson Thomes Ltd 2002), hereby incorporated herein by reference.
Useful chemical families of elastomers include, but are not limited to, silicon elastomers, polyurethane elastomers, saturated polyesters and co-polyesters, natural rubbers, polyvinyl chlorides, polyolefins, styrene copolymers, natural rubbers, hydrogels, polypeptide and collagen elastomers, polyphosphazenes, polyamides, polyacrylics, and fluorinated elastomers.
In one preferred embodiment, elastomers are high-consistency rubber silicone elastomers. Suitable high-consistency rubber silicone elastomers include, but are not limited to, crosslinked dimethyl and methyl-vinyl siloxane copolymers and Dow Corning Class VI Elastomers.
2.3 Sources of Elastomers
Elastomers may be readily available commercially. Elastomers also may be synthesized and characterized using well-known methods, for example see, R. J. YOUNG & P. A. LOVELL, INTRODUCTION To POLYMERS 15-240 (2d ed., Nelson Thomes Ltd 2002), hereby incorporated herein by reference. Commercial sources and methods to manufacture various elastomers are disclosed in D. J. CHAUVEL-LEBRET ET AL., Biocompatibility Of Elastomers, in POLYMERIC BIOMATERIALS 311-360 (Severian Dumitriu ed., 2nd ed. 2002), hereby incorporated herein by reference.
Dow Corning Class VI elastomers are commercially available from Dow Corning Corporation Corporate Center, PO Box 994, Midland, Mich. 48686-0994, United States.
2.4 Additives
Elastomers may contain various additives, for example, fillers, such as precipitated silica, chalks, and kaolins; opacifiers, such as barium sulfate; protective agents, such as amines and phenols; and crosslinking agents. D. J. CHAUVEL-LEBRET ET AL., Biocompatibility Of Elastomers, in POLYMERIC BIOMATERIALS 311-360 (Severian Dumitriu ed., 2nd ed. 2002), hereby incorporated herein by reference.
2.5 Sterilization of Elastomers
Preferably, before use, the elastomers will be sterilized. Sterilization techniques will vary depending on the identity of the elastomer and the preference of the surgeon or manufacturer. Methods for sterilization are well known in the art. For general discussions with references see, Barry Garfinkle & Martin Henley, Sterilization, in 2 REMINGTON: THE SCIENCE AND PRACTICE OF PHARMACY 1463-1486 (Alfonso R. Gennaro ed., 19th ed., 1995); D. J. CHAUVEL-LEBRET ET AL., Biocompatibility Of Elastomers, in POLYMERIC BIOMATERIALS 334-335 (Severian Dumitriu ed., 2nd ed. 2002), both of which citations are hereby incorporated herein by reference.
Suitable methods for sterilization of elastomers include, but are not limited to, exposure to ethylene oxide (500-540 mg/L) in 80 percent carbon dioxide at a relative humidity of over 35% for 3 hours at 35-41° C.; exposure to gamma radiation (e.g., 2.5 Mrad for 5 hours), see e.g., A. Pizzoferrato et al., In Vitro Biocompatibility of a Polyurethane Catheter After Deposition of Fluorinated Film, 16 BIOMATERIALS 361-367 (1995); B. Sadd, et al., Interactions of Osteoblasts and Macrophages with Biodegradable and Highly Porous Polyesterurethan Foam and Its Degradation Products, 32 J. BIOMED. MATER. RES. 355-366 (1996), both of which citations are hereby incorporated herein by reference; dry heat or autoclaving, see e.g., K. M. Miller & J. M. Anderson, In Vitro Stimulation of Fibroblast Activity by Factors Generated from Human Monocytes Activated by Biomedical Polymers, J. BIOMED. MATER. RES. 911-930 (1989); and use of antiseptic solutions, see e.g., M. J. Menconi, et al., Molecular Approaches to the Characterization of Cell and Blood/Biomaterial Interactions, 7 J. CARDIAC SURG. 177-187 (1992); J. A. Hunt et al., Effect of Biomaterial Surface Charge on the Inflammatory Response: Evaluation of Cellular Infiltration and TNF alpha Production, J. BIOMED. MATER. RES. 139-144 (1996), both of which citations are hereby incorporated herein by reference.
3.0 Introduction of a Biocompatible Filler into the Bone Cavity
According to one embodiment, once the appropriate cavity is created in bone tissue, cavity creation device 1000 is removed from the delivery tube device 1050 and delivery tube device 1050 remains implanted in the bone tissue. A biocompatible filler, such as bone cement, can then be introduced into the cavity through the delivery tube device 1050 to treat weak, damaged, or diseased bone tissue. In one embodiment, a delivery device is connected directly to delivery tube device 1050 to deliver the biocompatible filler into the cavity. In a preferred embodiment, either the twistOR PrePack (illustrated by
3.1 twistOR PrePack™: An Exemplary Device for Introduction of Bone Cement Into a Bone Cavity
By referring to
In
In the preferred construction, the second component of the bone cement, which comprises dry powder 26, is stored in vessel 25 of bone cement handling and delivery system 22, as clearly shown in
In addition to preferably shipping dry powder 26 in vessel 25 of bone cement handling and delivery system 22, the first component, which comprises liquid monomer 27, is contained in sealed container 21. Sealed container 21 can be any suitable container adaptable to create a flow path to the vessel by way of transfer assembly 23. For example, sealed container 21 can be flexible or non-flexible plastic or polymer, preferably, glass or other chemically resistant material. In one preferred embodiment, sealed container 21 comprises glass vial or tube 30 having a single opening or portal on which cap or closure 31 is mounted.
As detailed above, cap or closure 31 of sealed container 21 comprises an integrally formed sealing membrane, preferably, a septum to provide access to the interior of glass vial/tube 30. Sealing membrane 32 comprises a generally conventional construction, formed of elastomeric material, which typically comprises elastomeric plastics, rubbers, silicones, and the like. In this way, liquid monomer 27 is sealed within glass tube/vial 30, while providing access to the interior of tube/vial 30 only upon creating a flow path, for example, by using a transfer conduit, such as a suitable syringe needle.
In certain embodiments, vacuum is used to cause the sealed-container contents to transfer into the vessel (the means for transfer). In these embodiments, the vessel will comprise vacuum portal 35 for attachment to a vacuum supply. In other embodiments, sealed container 21 can be constructed such that the twistOR PrePack™ can operate without vacuum. Sealed container 21 will comprise the means to transfer the container contents into vessel 25. In these embodiments, vacuum portal 35 is not required. In one such embodiment, sealed container 21 is a chemically resistant squeeze bottle or flexible bag so that container 21's contents can be squeezed into the vessel 25. In another such embodiment, sealed container 21 is preloaded with a pressurized gas that functions to push the monomer out of container 21 upon creating a flow path by connection to transfer assembly 23. Preferably, container 21's contents (e.g., monomer) is preloaded along with the pressurized gas.
In addition, cover 24 of bone cement handling and delivery system 22 comprises an access portal 34 and vacuum portal 35 that are mounted thereto and provide access to the interior of vessel 24. Vacuum portal 35 comprises a generally conventional construction that enables a vacuum source to be connected thereto, using any suitable vacuum connection. In addition, access portal 34 comprises a sealing membrane 36, preferably, a septa-like disk mounted in access portal 34 for sealing the interior of vessel 25 from the ambient air, while also enabling access to the interior of vessel 25 to be achieved by creating a flow path, for example by employing a transfer conduit, such as a suitable needle or syringe.
Finally, holder 37 is employed for maintaining sealing membrane 36 in the precisely desired position within access portal 34. By forming holder 37 with two separate and distinct diameters, one portion of holder 37 is inserted into access portal 34, while the second, larger diameter portion thereof engages the outer terminating edge of access portal 34. In this way, sealing membrane 36 is securely maintained in the desired position within access portal 34.
The construction of transfer assembly 23 of twistOR PrePack™ is completed by providing for mating engagement thereof with cap 31 of sealed container 21 and access portal 34 of cover 24 of handling and delivery system 22. As fully depicted in
In addition, collar portion 40 is constructed with an inside diameter dimensioned for co-operative, frictional engagement with cap 31 of sealed container 21. In this way, when transfer assembly 23 is mounted to sealed container 21, transfer assembly 23 is frictionally engaged securely with sealed container 21, preventing any unwanted, easy dislodgment of sealed container 21 from assembly 23.
Similarly, collar 41 comprises an inside dimension constructed for mating, co-operative, sliding engagement with access portal 34 of cover 24. In addition, by designing collar 41 with an inside dimension that is slightly greater than the outside dimension of access portal 34, secure holding engagement of transfer assembly 23 with access portal 34 is achieved whenever assembly 23 is telescopically mounted into overlying engagement with access portal 34.
In order to complete the construction of transfer assembly 23, a mechanism for providing a flow path between the vessel and the sealed container, is provided. The preferred flow path is created by a transfer conduit, such as dual ended piercing conduit 44 (double-tipped syringe needle). As depicted, transfer conduit 44 comprises a support base 45, a syringe needle forming member 46 mounted to one surface of support base 45 and a syringe needle forming member 47 mounted to the opposed surface of support base 45.
In the preferred construction, syringe needle forming members 46 and 47 comprise elongated, hollow tubes mounted to support base 45 in coaxial alignment with each other, forming a continuous, elongated flow path therebetween. In addition, each syringe needle forming member 46 and 47 comprises sharp, pointed, distal ends constructed for piercing the sealing membrane 36 (any septa-like material) for gaining access to the interior associated with the sealing membrane.
In addition, base 45 of piercing element 44 is securely mounted in transfer assembly 23, preferably affixed in support plate 42. When mounted in its secure position, syringe needle forming member 46 extends into collar portion 40, substantially centrally disposed therein. In this position, syringe needle forming member 46 is peripherally surrounded by the wall forming collar portion 40 with its sharp, distal end extending toward the opening of collar 40.
Similarly, syringe needle forming member 47 is securely positioned to be centrally disposed within collar portion 40, peripherally surrounded by the wall forming collar 41. In addition, the sharp distal end of syringe needle forming portion 47 extends towards the open end of collar 41.
By employing this construction, the telescopic axial advance of transfer assembly 23 into engagement with sealed container 21 and access portal 34 of cover 24, causes syringe needle forming portions 46 and 47 to pierce the sealing membranes 32 and 36 and establish a direct fluid transfer flow path between sealed container 21 and vessel 25. In the preferred construction, in order to eliminate any unwanted injuries, tip cover 48 is preferably mounted to syringe needle forming member 46. Since the diameter of collar portion 40 is large enough to enable a finger tip to enter its open end, the use of cover 48 prior to engagement of cover 40 onto cap 31 provides the desired protection.
In addition, in the preferred construction, collar 40 comprises radially extending flange 49 formed on its terminating end. By employing flange 49, ease of use and control of collar 40 is provided.
By referring to
As with the embodiment detailed above, collar portion 56 comprises an inside diameter constructed for mating, co-operative, sliding engagement with access portal 34 of cover 24. In addition, by designing collar portion 56 with an inside diameter that is slightly greater than the outside diameter of access portal 34, secure holding engagement of transfer assembly 23 with access portal 34 is achieved whenever assembly 23 is telescopically mounted into overlying engagement with access portal 34.
In addition, collar portion 55 comprises an inside diameter dimensioned for co-operative, frictional engagement with cap 31 of sealed container 21. In addition, in this embodiment, collar portion 55 comprises a plurality of tabs 58 mounted to the inside wall of collar portion 55 that extend radially inwardly therefrom. In addition, tabs 58 are formed on the inside wall of collar portion 55 in a vertical position that is slightly greater than the vertical height of cap 31 of sealed container 21. Finally, in the preferred construction, tabs 58 are formed about the inside wall of collar portion 55 substantially equidistant from each other, thereby being spaced apart a distance of about 120°.
By employing this construction, whenever sealed container 21 is telescopically inserted into collar portion 55 of transfer assembly 23, cap 31 of sealed container 21 is frictionally engaged with collar portion 55, securely locked in position by tabs 58 engaging the edge of cap 31 and preventing telescopic removal of sealed container 21 from collar portion 55. In this way, once sealed container 21 has been mounted in secure, locked engagement with transfer assembly 23, dislodgment or removal of sealed container 21 from collar 55 is prevented.
Furthermore, in this embodiment of twistOR PrePack™, transfer assembly 23 comprises gas-flow aperture 74 comprising gas-flow conduit 61 mounted in support wall 57 and transfer conduit 60 also mounted in support wall 57. Preferably, transfer conduit 60 and gas-flow conduit 61 are independent syringe needles. As shown in
With support base 65 of transfer conduit 60 mounted in receiving hole 69 of support wall 57 of transfer assembly 23, piercing end 63 extends from support wall 57 into the interior of collar portion 55, while piercing end 64 extends from support wall 57 into collar portion 56. In this way, as detailed above, whenever transfer assembly 23 is mounted to access portal 34 of cover 24, and sealed container 21 is mounted to transfer assembly 23, the monomer contained in sealed container 21 is able to be transferred through transfer conduit 60 into vessel 25.
In this embodiment of twistOR PrePack™, transfer assembly 23 also comprises a gas-flow conduit 61 that incorporates an elongated, cylindrically shaped, hollow piercing element 66 mounted to support base 67. In the preferred construction, support base 67 is mounted in receiving hole 68 formed in support wall 57 of transfer assembly 23, with hollow piercing element 66 extending therefrom into the interior of collar portion 55. In addition, base 67 of gas-flow conduit 61 cooperates with gas-flow aperture 74 formed in support wall 57, thereby providing an air flow path from the ambient surroundings through hollow gas-flow conduit 61 into the interior of sealed container 21 whenever sealed container 21 is mounted in collar 55.
By employing this embodiment of twistOR PrePack™ 23, it is ensured that monomer stored in sealed container 21 is capable of flowing freely through transfer conduit 60 into vessel 25 whenever the monomer is desired for being added into vessel 25. By providing a separate gas flow pathway (preferably ambient air) through gas-flow aperture 74 and gas-flow conduit 61, gas, such as nitrogen, argon, or other inert gas or air is constantly replaced in sealed container 21 as the monomer is withdrawn therefrom. In this way, the creation of a partial vacuum is avoided and free flow of the monomer is provided.
In the preferred construction, this embodiment of twistOR PrePack™ is completed by incorporating cover 70 that is constructed for being mounted in collar portion 55 for preventing and blocking any unwanted entry into collar portion 55, prior to the insertion of sealed container 21. In this way, contact with the terminating ends of piercing elements 63 and 66 is prevented and any unwanted or accidental injury is avoided.
In the preferred construction, cover 70 comprises an outwardly extending rim 71 formed on the base thereof, which cooperates with inwardly extending tabs 58, in order to secure cover 70 in the desired position. In addition, whenever monomer bearing sealed container 21 is ready for insertion in collar portion 55, cover 70 is easily removed from its secured position, thereby enabling sealed container 21 to be telescopically inserted and locked in position in collar portion 55.
3.2 The Plexis™ System: An Exemplary Device for Introduction of Bone Cement into a Bone Cavity
In operation, Plexis™ system 200 corresponds to bone cement handling and delivery system 22 of
As discussed above, in a preferred construction, mixing chamber 295 comprises cover assembly 290 (see
In a preferred embodiment of cover assembly 290, mixing chamber cover 320 attaches to mixing chamber 295 by threaded engagement. Mixing chamber 295 houses mixing-unit 385. Mixing unit 385 can be any assembly well known in the art to mix components, for example, but not limited to, mixers comprising mixing vanes, such as paddles, blades, and propellers. Preferably, mixing unit 385 comprises cylindrical, hollow mixing shaft 390 and helical mixing vanes 395. In a more preferred embodiment, hollow mixing shaft 390 comprises a large-diameter end 400 and mixing head 405.
The Plexis™ system further comprises a drive mechanism to drive the mixed components from dispensing chamber 305 into the desired location. The drive mechanism can be any device well known in the art to drive contents from a chamber. Preferably, the drive mechanism comprises a plunger that can be driven by a rotational drive or simply by pushing the plunger down by hand.
The preferred drive mechanism 410 is shown in
Rotational drive 112 (shown in
During the mixing stage, drop shaft 340 is in the up position such that drive-head engagement 351 is held above and is therefore not engaged with drive head 430. This is illustrated by
As mentioned above, controllable portal assembly 300 comprises a mechanism for opening a flow path between mixing chamber 295 and dispensing chamber 305 after mixing of the components contained in mixing chamber 295 is complete. Such a mechanism is herein termed a controllable portal.
Controllable portal 467 comprises sliding tube 470 securely fixed to dispensing chamber 305. Preferably, sliding tube 470 forms a tight seal with both the mixing chamber 295 and dispensing chamber 305, for example, by use of o-rings 475. In
3.2.1 The Mixing Phase of the Plexis™ System
The components to be mixed are contained within mixing chamber 295. One or more of the components can be prepackaged in the mixing and dispensing unit and/or additional components can be added directly before mixing.
As shown in
Further, in this mixing phase, drop shaft 340 is engaged by engagement pin 355 and therefore locked in the up position such that drive head 430 is not engaged with rotating drive-head engagement 351. And in the up position, as discussed above, drop shaft 340 is rotationally engaged with mixing head 405. Also, advancing member 425 is fully inserted into bore 420. Tooth 500 of guide washer 495 is engaged with locking-slot 490 so that plunger shaft 415 is prevented from rotating.
In the above configuration, upon connection and operation of a rotational drive 112 to rotating-means connection 350, mixing unit 385 is rotated along its axis thereby mixing the components within mixing chamber 295.
3.2.2 Transfer of Mixed Components from Mixing Chamber to Dispensing Chamber Of the Plexis™ System
When the mixing phase is complete, the contents of mixing chamber 295 are ready for transfer to dispensing chamber 305. This is accomplished by opening controllable portal 467 to create a flow path. In a preferred embodiment, rotation of helical shaped mixing vanes 395 is used force the contents of mixing chamber 295 into dispensing chamber 305 by action of mixing unit 385.
Rotating of locking collar 450 is complete when locking rods 485 are locked within complementary locking slots 465 of end cap 460. The construction of locking rods 485 and locking collar 450 effectively provide a turnbuckle construction that causes dispensing chamber 305 to move downward.
Once dispensing chamber 305 is in the position depicted in
3.2.3 The Dispensing Phase of the Plexis™ System
Once the contents are loaded into dispensing chamber 305, drop shaft 340 can be dropped by releasing engagement pin 355. This causes drive-head engagement 351 of drop shaft 340 to rotationally engage with drive head 430 of plunger advancing member 425. At the same time the upper portion 349 (
Upon activating rotational drive 112, rotating means connection 350 is controllably rotated. The rotational movement causes plunger advancing member 425 to rotate. Since plunger advancing member 425 is axially fixed (cannot move up and down but can only rotate), plunger shaft 415 and plunger-sealing-end 435 are controllably axially advanced longitudinally through dispensing chamber 305. The longitudinal movement of plunger sealing-end 435 in dispensing chamber 305 forces the mixed components contained therein to be delivered through outlet portal 310 of dispensing chamber 305. Preferably, dispensing portal 310 is adapted to connect to the standard needle or cannula (not shown) used in vertebroplasty procedures.
In addition, by controlling the rotational movement or speed of rotating-means connection 350, the precisely desired pressure for advancing the mixed components through dispensing chamber 305 is achieved. Furthermore, by stopping the rotational movement of rotating-means connection 350 or reversing the direction rotating-means connection 350, complete control over the delivery of the mixed components to the precisely desired site is achieved. In fact, by reversing the rotation of rotating-means connection 350, the plunger direction is reversed and the contents can actually be pulled back into dispensing chamber 305. This provides much greater control than previously available. In addition, in the preferred embodiment, reference indicia are marked or etched on the outer surface of dispensing chamber 305, thereby enabling the operator to precisely measure the quantity of material being delivered.
In another convenient embodiment, the Plexis™ system can be calibrated such that the number of revolutions of drop shaft 340 and/or the rotational drive 112 corresponds to an amount (e.g., a weight or volume) of bone cement dispensed. In this embodiment, a clinician dispensing a biocompatible filler using the Plexis™ system can dispense a predetermined amount by completing a pre-determined number of rotations of drop shaft 340 and/or rotational drive 112.
3.3 Illustrative Embodiment—Manually Actuable Plexis™ System
Certain aspects may now be more clearly understood by consideration of the following specific embodiment in the form of a manually actuable Plexis™ system. By manually actuable is meant that both mixing of the components and dispensing of the mixed components can be manually effected and controlled without the use of power tools. One advantage of manual actuation is that operation is not dependent on the presence of power tools or electrical outlets in a sterile environment. Another is the finer level of control provided by direct hand control.
The exemplary apparatus is similar in structure and function to the apparatus previously illustrated and described except that it provides adaptations to facilitate manual mixing and manual dispensing of the mixed components.
It is contemplated that the apparatus 500 will be delivered with the crank handle 543 in the open radially extended position (
The monomer is further drawn into the mixing housing 502 which can contain the powder polymer. The vial and the transfer housing 531 are then removed together, the simultaneous removal assured by locking fingers of the transfer housing locking onto the cap of the vial.
The user then mixes the monomer and powder to form bone cement by rotating the radially extended handle 543 or by rotating the handle cap 547 (which acts as a knob). With the handle 543 in open position, a cam surface 543A pushes downward on a crank handle gear 548 causing the gear configuration to interface with a corresponding gear configuration 503A on the end of mixing paddle 503. The manual rotational movement of the handle or knob is thus transmitted to actuate the mixing paddle 503.
When the cement is mixed, the user rotates the controllable portal assembly 507 to open the controllable port between the mixing chamber 502 and the dispensing syringe tube 535. The handle 543 is then turned to move the mixed material through the now open port into the syringe tube 535.
After the syringe tube 535 is filled, the user flips the hinged handle 543 across the center of the cap 547 to lock the handle in the second position (
The user then rotates handle 543 or the knobbed crank handle cap 547 to actuate the plunger mechanism (511, 518, 533) pushing the mixed material out the end of the syringe tube 535 and typically into a needle or cannula (not shown).
3.4 Component Structure
The needle housing 531 and needle housing cap 532 are preferably of the design shown and described in connection with
The crank handle is held in place by a crank handle cup comprising a pivot half 541 and a clamp half 542, each secured to the crank handle cap 547. The cup (541,542) also houses the crank handle gear 548, permitting it to slide longitudinally. The longitudinal position of the gear 548 is controlled by the cam surface 543A of the handle. The gear is loaded by spring 549 in the disengaged condition with respect to the mixing paddle 503. Thus when the handle is in the first position (
The crank handle cup assembly (541, 542) also locks onto the top end of the paddle 503 to provide alignment between the paddle and the gear 548. The two halves 541, 542 are secured together as by screws 539 or snap-fit connections (not shown). The cup could also be molded as a one piece part.
The end cap 501 is advantageously similar to top cap 315 of
The mixing paddle 503 is advantageously similar to paddle 390 of
In other regards, the drive mechanisms for mixing and dispensing and the mechanisms for operating the controllable port between the mixing chamber and the dispensing chamber are the same as those described for other embodiments herein.
It can now be seen that the exemplary apparatus for manually mixing and dispensing components comprises a sealed mixing chamber having an access portal and a vacuum portal, a mixing unit in the mixing chamber to mix the components, and a first manually actuable drive mechanism associated with the mixing unit to actuate mixing.
The apparatus further includes a dispensing chamber connected to the sealed mixing chamber but which is isolated from the mixing chamber. A controllable portal is provided for opening a flow path between the sealed mixing chamber and the dispensing chamber after the components are mixed. A second manually actuable drive mechanism associated with the dispensing chamber is provided to drive the mixture from the dispensing chamber.
In advantageous forms, the mixing chamber is preloaded with bone cement powder. The first and second drive mechanisms comprise rotationally movable handles or knobs and preferably a common handle or knob. A mechanical switching arrangement can be provided to disengage the common handle or knob from the first drive mechanism. The preferred mixing unit comprises a mixing paddle, and the preferred second drive mechanism comprises a plunger shaft.
3.5 Biocompatible Fillers and Bone Cements for Filling Cavities
Suitable biocompatible bone void fillers are well known by those in the art and include, but are not limited to, bone cements, calcium phosphates, and bioresorbable polymers. Preferably, such fillers conform with the Food and Drug Administration's Class II Special Controls Guidance Document: Polymethylmethacrylate (PMMA) Bone Cement; Guidance for Industry and FDA.
In a preferred embodiment, the biocompatible filler is bone cement, more preferably, bone cement formed from a mixture of polymethylmethacrylate (PMMA), methyl methacrylate monomer, and a substance to radiopacify the cement mixture. The radiopacifier enables monitoring of the cement mixture using x-ray radiographs. Examples of radiopacifiers include barium salts, ceramic particles, or tantalum materials.
In an additional embodiment, the bone cement mixture can include one or more additional pharmaceutical agents, such as an antibiotic to reduce the risk of infection. One example of a suitable antibiotic for use in the bone cement mixture is tobramycin.
Suitable commercially available bone cement mixtures include, but are not limited to, Concert®, Concert® Cranioplast, Palacos, Palacos G, DePuy 1, 2, and 3, DePuy 1 with Gentamycin, Osteobond, Simplex-P, Simplex-P with Tobramycin, Versabond, Endurance, all commercially available, for example, commercially available from Advanced Biomaterial Systems, Inc., Chatham, N.J.
In an exemplary procedure, to correct a fractured vertebrae, the patient lies on an operating table, while the physician introduces a conventional spinal needle assembly into the soft tissue in the patient's back. The patient can lie facedown on the table, or on either side, or at an oblique angle, depending upon the physician's preference. Alternatively, the procedure can be performed through an open anterior procedure or an endoscopic anterior procedure.
The spinal needle assembly typically comprises a stylet slidably housed within a stylus. The assembly typically has, for example, about an 18 gauge diameter. Other gauge diameters can and will be used to accommodate appropriate guide pins, as will be described in greater detail below. For example, in certain instances, 13 gauge to 8 gauge needles may be suitable. In yet other applications, use of even larger needles than that may be desirable.
Under radiological, CT, or MRI monitoring, the physician advances the assembly through the soft tissue and into the targeted vertebra. The physician will typically administer a local anesthetic, for example, lidocaine, through the assembly. Other forms of anesthesia may be used.
The physician causes the spinal needle assembly to penetrate the cancellous bone of the targeted vertebrae. Access to the cancellous bone may be through the pedicle, known as transpedicular access. It is contemplated that posterolateral access, through the side of the vertebral body, may be preferred, if a compression fracture has collapsed the vertebral body below the plane of the pedicle, or for other reasons based upon the discretion and preference of the physician.
After positioning the spinal needle assembly in the cancellous bone, the physician holds the stylus and withdraws the stylet. Still holding the stylus, the physician slides a guide pin through the stylus and into the cancellous bone. The physician now removes the stylus, leaving the guide pin deployed within the cancellous bone.
Next, the physician makes a small incision in the patient's back sufficiently sized to accommodate a delivery tube device, such as a trocar or a cannula. The delivery tube device is inserted into the patient's vertebral body using a transpedicular or extrapedicular approach. A drill is inserted into the delivery tube device to create a channel in the vertebral body stopping just behind the anterior wall. The drill device is then removed from the delivery tube device.
The elastomer delivery device is inserted into the canal or tube of the delivery tube device. The elastomer delivery device is packed with the elastomer. A plunger is then made to apply a deforming force to the, elastomer thereby pushing the elastomer out of the end of the elastomer delivery device and into the vertebral body. The elastomer maintains its linear backbone structure until coming into contact with the bumper located on the guide rod. The deforming force created by the bumper causes the elastomer to expand outwardly. The combination of the deforming forces created by the plunger action and the bumper cause the elastomer to expand throughout the cancellous bone and create a cavity therein. Due to the application of stress or pressure, the elastomer material expands approximately 3 to 10 times its normal size.
Advantageously, the expanded elastomer material acts on the collapsed vertebral body to restore height in the collapsed vertebral body. Once the desired cavity is created, the action applied to the ratcheting device is reversed and the deforming force acting on the elastomer is removed. The removal of the deforming forces and the space created in the elastomer delivery device by the reversal of the plunger allows the elastomer to retract back into its linear backbone structure within the elastomer delivery device. Upon withdrawal of the elastomer from the cavity, the cavity creation device is removed from the delivery tube device. Next, the physician may introduce a bone cement mixture (described in detail in section above) or biomaterials into the newly formed cavity in the vertebral body. Preferably, delivery of the bone cement mixture is accomplished by way of a tube, hose, cannula, or needle. For example, by use of the Plexis™ system described above.
The above example is for explanatory purposes only and is not intended to limit the use of the device to the specific manner described.
From the above Summary, Description, Figures, and Example, it is clear that in one embodiment, a device for creating a cavity in mammalian tissue includes
In another embodiment, a device for creating a cavity in mammalian tissue includes:
In still another embodiment, a kit for assembly into a device for creating a cavity in mammalian tissue includes the following components:
In still another embodiment, the a method of creating a cavity in mammalian tissue includes:
In still yet another embodiment, a method of repairing, stabilizing, or reinforcing weak, damaged or diseased mammalian bone tissue with a device includes:
Although various aspects have been described in considerable detail with reference to certain preferred embodiments and versions, other versions and embodiments are possible. Therefore, the spirit and scope of the appended claims should not be limited to the description of the versions and embodiments expressly disclosed herein.
This application claims the benefit of U.S. Provisional Application No. 60/558,330, filed Mar. 31, 2004 and U.S. Provisional Application No. 60/558,860, filed Apr. 2, 2004.
| Number | Date | Country | |
|---|---|---|---|
| 60558330 | Mar 2004 | US | |
| 60558860 | Apr 2004 | US |
