CA2540211A1 - Apparatus for reducing compression bone fractures using high strength ribbed members - Google Patents
Apparatus for reducing compression bone fractures using high strength ribbed members Download PDFInfo
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- CA2540211A1 CA2540211A1 CA002540211A CA2540211A CA2540211A1 CA 2540211 A1 CA2540211 A1 CA 2540211A1 CA 002540211 A CA002540211 A CA 002540211A CA 2540211 A CA2540211 A CA 2540211A CA 2540211 A1 CA2540211 A1 CA 2540211A1
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- proximal
- distal
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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
-
- 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
- A61B17/8858—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 laterally or radially expansible
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
- A61B17/00—Surgical instruments, devices or methods, e.g. tourniquets
- A61B17/56—Surgical instruments or methods for treatment of bones or joints; Devices specially adapted therefor
- A61B17/58—Surgical instruments or methods for treatment of bones or joints; Devices specially adapted therefor for osteosynthesis, e.g. bone plates, screws, setting implements or the like
- A61B17/68—Internal fixation devices, including fasteners and spinal fixators, even if a part thereof projects from the skin
- A61B17/70—Spinal positioners or stabilisers ; Bone stabilisers comprising fluid filler in an implant
- A61B17/7097—Stabilisers comprising fluid filler in an implant, e.g. balloon; devices for inserting or filling such implants
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
- A61B90/00—Instruments, implements or accessories specially adapted for surgery or diagnosis and not covered by any of the groups A61B1/00 - A61B50/00, e.g. for luxation treatment or for protecting wound edges
- A61B90/03—Automatic limiting or abutting means, e.g. for safety
- A61B2090/037—Automatic limiting or abutting means, e.g. for safety with a frangible part, e.g. by reduced diameter
Abstract
A device (100) for treating a bone structure (such as, e.g., reducing a bone fracture, e.g., a vertebral compression fracture, or stabilizing adjacent bone structure, e.g., vertebrae) comprises rigid or semi-rigid members (102), each of which comprises a common base (110) and a plurality of ribs (112) that extent along the a longitudinal portion of the common base. The device is configured to be placed in a collapsed state by engaging the pluralities of ribs of the members in an interposed arrangement, and configured to be placed in a deployed state by disengaging the pluralities of ribs.
Description
APPARATUS FOR REDUCING COMPRESSION BONE FRACTURES USING HIGH
STRENGTH RIBBED MEMBERS
FIELD OF THE INVENTION
This invention relates to the treatment of bone structures, such as vertebrae, and in particular, to the reduction and stabilization of compression bone fractures.
BACKGROUND OF THE INVENTION
Spinal injuries, bone diseases, such as osteoporosis, vertebral hemangiomas, multiple myeloma, necrotic lesions (Kummel's Disease, Avascular Necrosis), and metastatic disease, or other conditions can cause painful collapse of vertebral bodies. Osteoporosis is a systemic, progressive and chronic disease that is usually characterized by low bone mineral density, deterioration of bony architecture, and reduced overall bone strength. Vertebral compression fractures (VCF) are common in patients who suffer from these medical conditions, often resulting in pain, and compromises to activities of daily living.
Fig. 1 illustrates three vertebrae 10, 12, and 14, each with an anterior side 16, a posterior side 18, and lateral sides 20 (only one shown). Vertebrae 10 and 14 are fully intact, while vertebra 12 has a VCF 22 (i.e., the top 24 and bottom 26 of the vertebra 12 have been displaced towards each other). The force required to reduce the VCF 22 (i.e., to displace the top 24 and bottom 26 of the vertebra 12 back to their original positions) can often be rather high. Present needles for use within vertebrae bend or deform in the presence of lateral force, and thus, are not rigid enough to reduce VCF's. Balloons can be placed in the fractured vertebra and expanded to reduce the VCF. Such balloons, however, will expand equally in all radial directions, which can cause the vertebra to shatter on the anterior, posterior, and lateral sides.
SUMMARY OF THE INVENTION
In accordance with a first embodiment of the invention, a device for reducing a bone fracture, e.g., a vertebral compression fracture, is provided. The device comprises a first rigid member having a first common base and a first plurality of ribs extending along at least a longitudinal portion of the first common base, and second rigid member having a common base and a second plurality of ribs extending along at least a longitudinal portion of the second common base. The device is configured to be placed in a collapsed state by engaging the first and second pluralities of ribs in an interposed arrangement, and configured to be placed in a deployed state by disengaging the first and second pluralities of ribs. The ribs can be any shape, e.g., flutes, that allows opposing ribs to intermesh with one another. A coupling mechanism such as, e.g., a hinge, may be used to couple the first and second rigid members together.
The first and second rigid members, when the device is in the collapsed state, can have a combined cross-sectional profile that is substantially the same as each of the individual cross-sectional profiles of the first and second rigid members, when the device is in the deployed state. For example, the combined cross-sectional profile can be circular, and the individual cross-sectional profiles can have an arcuate shape, in which case, the radius of the circular profile can be substantially equal to the radius of curvature of each of the individual cross-sectional profiles.
Thus, it can be appreciated that the interposition of the ribs provides a smaller combined profile for the members, while not substantially reducing the shear strength of the individual members during deployment of the device.
In accordance with another embodiment of the invention, a device for reducing a bone fracture, e.g., vertebral compression fracture, is provided.
The device comprises first and second proximal member portions, and first and second distal member portions. The first proximal and distal member portions can either form a single member or multiple members, and the second proximal and distal member portions can likewise either form a single member or multiple members.
The device further comprises a first intermediate hinge located between the respective proximal and distal member portions, wherein a first hinge point is formed, and a second intermediate hinge located between the respective proximal and distal member portions, wherein a second hinge point is formed. If the member portions are formed of single members, the intermediate hinges can be living hinges (i.e., points where the members bend or deform).
The device further comprises an actuating coupling assembly configured for displacing the proximal ends of the first and second proximal member portions and distal ends of the first and second distal member portions towards each other, whereby the first and second hinge points are respectively displaced outward away from each other to deploy the device. In this manner, the device can be used to apply opposing forces on the bone structure in order to reduce the fracture.
In an alternative embodiment, the coupling assembly is configured for displacing the proximal ends of the first and second proximal member portions and the distal ends of the first and second distal member portions away from each other, whereby the first and second hinge points are respectively displaced inward towards each other to collapse the device.
In one embodiment, the coupling assembly comprises a drive shaft, a proximal coupling mechanism rotatably coupled to the drive shaft, and a distal coupling mechanism coupled to the drive shaft. In this case, the device further comprises proximal hinges between the respective proximal member portions and the proximal coupling mechanism, and distal hinges between the respective distal members portions and the distal coupling mechanism. The drive shaft can be variously configured. For example, the drive shaft can be a drive screw, in which the proximal coupling mechanism may comprise a nut in which the drive screw is threadedly engaged. Or the drive shaft may be a shear wire, in which case, the proximal coupling mechanism is an annular ring through which the shear wire is slidably engaged. In the case of a shear wire, a weakened region can be provide that causes the shear wire to break off after deployment of the device. The distal coupling mechanism can be, e.g., a spherical cap that houses the distal end of the drive shaft.
The device may optionally include more intermediate hinges to provide a larger surface that contacts the bone structure. For example, the device may comprise a first central member portion located between the first proximal and distal member portions, and a second central member portion located between the second proximal and distal member portions. In this case, the first intermediate hinge will be located between the first proximal member portion and the first central member portion, and the second intermediate hinge will be located between the second proximal member portion and the second central member portion. A third intermediate hinge will be located between the first distal member portion and the first central member portion, and a fourth intermediate hinge will be located between the second distal member portion and the second central member portion. Thus, the first and second central member portions will be respectively displaced outward away from each to deploy the device, thereby providing a greater surface area in contact with the bone structure.
STRENGTH RIBBED MEMBERS
FIELD OF THE INVENTION
This invention relates to the treatment of bone structures, such as vertebrae, and in particular, to the reduction and stabilization of compression bone fractures.
BACKGROUND OF THE INVENTION
Spinal injuries, bone diseases, such as osteoporosis, vertebral hemangiomas, multiple myeloma, necrotic lesions (Kummel's Disease, Avascular Necrosis), and metastatic disease, or other conditions can cause painful collapse of vertebral bodies. Osteoporosis is a systemic, progressive and chronic disease that is usually characterized by low bone mineral density, deterioration of bony architecture, and reduced overall bone strength. Vertebral compression fractures (VCF) are common in patients who suffer from these medical conditions, often resulting in pain, and compromises to activities of daily living.
Fig. 1 illustrates three vertebrae 10, 12, and 14, each with an anterior side 16, a posterior side 18, and lateral sides 20 (only one shown). Vertebrae 10 and 14 are fully intact, while vertebra 12 has a VCF 22 (i.e., the top 24 and bottom 26 of the vertebra 12 have been displaced towards each other). The force required to reduce the VCF 22 (i.e., to displace the top 24 and bottom 26 of the vertebra 12 back to their original positions) can often be rather high. Present needles for use within vertebrae bend or deform in the presence of lateral force, and thus, are not rigid enough to reduce VCF's. Balloons can be placed in the fractured vertebra and expanded to reduce the VCF. Such balloons, however, will expand equally in all radial directions, which can cause the vertebra to shatter on the anterior, posterior, and lateral sides.
SUMMARY OF THE INVENTION
In accordance with a first embodiment of the invention, a device for reducing a bone fracture, e.g., a vertebral compression fracture, is provided. The device comprises a first rigid member having a first common base and a first plurality of ribs extending along at least a longitudinal portion of the first common base, and second rigid member having a common base and a second plurality of ribs extending along at least a longitudinal portion of the second common base. The device is configured to be placed in a collapsed state by engaging the first and second pluralities of ribs in an interposed arrangement, and configured to be placed in a deployed state by disengaging the first and second pluralities of ribs. The ribs can be any shape, e.g., flutes, that allows opposing ribs to intermesh with one another. A coupling mechanism such as, e.g., a hinge, may be used to couple the first and second rigid members together.
The first and second rigid members, when the device is in the collapsed state, can have a combined cross-sectional profile that is substantially the same as each of the individual cross-sectional profiles of the first and second rigid members, when the device is in the deployed state. For example, the combined cross-sectional profile can be circular, and the individual cross-sectional profiles can have an arcuate shape, in which case, the radius of the circular profile can be substantially equal to the radius of curvature of each of the individual cross-sectional profiles.
Thus, it can be appreciated that the interposition of the ribs provides a smaller combined profile for the members, while not substantially reducing the shear strength of the individual members during deployment of the device.
In accordance with another embodiment of the invention, a device for reducing a bone fracture, e.g., vertebral compression fracture, is provided.
The device comprises first and second proximal member portions, and first and second distal member portions. The first proximal and distal member portions can either form a single member or multiple members, and the second proximal and distal member portions can likewise either form a single member or multiple members.
The device further comprises a first intermediate hinge located between the respective proximal and distal member portions, wherein a first hinge point is formed, and a second intermediate hinge located between the respective proximal and distal member portions, wherein a second hinge point is formed. If the member portions are formed of single members, the intermediate hinges can be living hinges (i.e., points where the members bend or deform).
The device further comprises an actuating coupling assembly configured for displacing the proximal ends of the first and second proximal member portions and distal ends of the first and second distal member portions towards each other, whereby the first and second hinge points are respectively displaced outward away from each other to deploy the device. In this manner, the device can be used to apply opposing forces on the bone structure in order to reduce the fracture.
In an alternative embodiment, the coupling assembly is configured for displacing the proximal ends of the first and second proximal member portions and the distal ends of the first and second distal member portions away from each other, whereby the first and second hinge points are respectively displaced inward towards each other to collapse the device.
In one embodiment, the coupling assembly comprises a drive shaft, a proximal coupling mechanism rotatably coupled to the drive shaft, and a distal coupling mechanism coupled to the drive shaft. In this case, the device further comprises proximal hinges between the respective proximal member portions and the proximal coupling mechanism, and distal hinges between the respective distal members portions and the distal coupling mechanism. The drive shaft can be variously configured. For example, the drive shaft can be a drive screw, in which the proximal coupling mechanism may comprise a nut in which the drive screw is threadedly engaged. Or the drive shaft may be a shear wire, in which case, the proximal coupling mechanism is an annular ring through which the shear wire is slidably engaged. In the case of a shear wire, a weakened region can be provide that causes the shear wire to break off after deployment of the device. The distal coupling mechanism can be, e.g., a spherical cap that houses the distal end of the drive shaft.
The device may optionally include more intermediate hinges to provide a larger surface that contacts the bone structure. For example, the device may comprise a first central member portion located between the first proximal and distal member portions, and a second central member portion located between the second proximal and distal member portions. In this case, the first intermediate hinge will be located between the first proximal member portion and the first central member portion, and the second intermediate hinge will be located between the second proximal member portion and the second central member portion. A third intermediate hinge will be located between the first distal member portion and the first central member portion, and a fourth intermediate hinge will be located between the second distal member portion and the second central member portion. Thus, the first and second central member portions will be respectively displaced outward away from each to deploy the device, thereby providing a greater surface area in contact with the bone structure.
To ensure proper placement and orientation of the member portions, a cannula that is capable of engaging the actuating coupling assembly can be provided. In addition, a driver can be provided in order to operate the actuating coupling assembly. The members can optionally comprise ribs, as previously discussed above, in order to provide a smaller combined profile, while preserving shear strength.
BRIEF DESCRIPTION OF THE DRAWINGS
The drawings illustrate the design and utility of embodiments) of the invention, in which similar elements are referred to by common reference numerals, and in which:
Fig. 1 is a lateral view of three vertebra, two of which are normal, and one of which has a compression fracture;
Fig. 2 is a plan view of a vertebral compression fracture reduction device constructed in accordance with a embodiment of the invention, wherein the device is particularly shown in a collapsed state;
Fig. 3 is a plan view of the device of Fig. 2, wherein the device is particularly shown in a deployed state;
Fig. 4 is a cross-sectional view of the device of Fig. 2, taken along the lines 4-4;
Fig. 5 is a cross-sectional view of the device of Fig. 3, taken along the lines 5-5;
Fig. 6 is a plan view of a vertebral compression fracture reduction device constructed in accordance with another embodiment of the invention, wherein the device is particularly shown in a collapsed state;
Fig. 7 is a plan view of the device of Fig. 6, wherein the device is particularly shown in a deployed state;
Fig. 8 is a cross-sectional view of the device of Fig. 6, taken along the lines 10-10;
Fig. 9 is a cross-sectional view of the device of Fig. 7, taken along the lines 11-11;
Fig. 10 is a plan view of a vertebral compression fracture reduction device constructed in accordance with still another embodiment of the invention, wherein the device is particularly shown in a collapsed state;
Fig. 11 is a plan view of the device of Fig. 10, wherein the device is particularly shown in a deployed state;
Fig. 12 is a plan view of a vertebral compression fracture reduction device constructed in accordance with yet another embodiment of the invention, wherein the device is particularly shown in a collapsed state;
Fig. 13 is a plan view of the device of Fig. 12, wherein the device is particularly shown in a deployed state;
Fig. 14 is a plan view of a vertebral compression fracture reduction device constructed in accordance with yet another embodiment of the invention, wherein the device is particularly shown in a collapsed state;
Fig. 15 is a plan view of the device of Fig. 14, wherein the device is particularly shown in a deployed state;
BRIEF DESCRIPTION OF THE DRAWINGS
The drawings illustrate the design and utility of embodiments) of the invention, in which similar elements are referred to by common reference numerals, and in which:
Fig. 1 is a lateral view of three vertebra, two of which are normal, and one of which has a compression fracture;
Fig. 2 is a plan view of a vertebral compression fracture reduction device constructed in accordance with a embodiment of the invention, wherein the device is particularly shown in a collapsed state;
Fig. 3 is a plan view of the device of Fig. 2, wherein the device is particularly shown in a deployed state;
Fig. 4 is a cross-sectional view of the device of Fig. 2, taken along the lines 4-4;
Fig. 5 is a cross-sectional view of the device of Fig. 3, taken along the lines 5-5;
Fig. 6 is a plan view of a vertebral compression fracture reduction device constructed in accordance with another embodiment of the invention, wherein the device is particularly shown in a collapsed state;
Fig. 7 is a plan view of the device of Fig. 6, wherein the device is particularly shown in a deployed state;
Fig. 8 is a cross-sectional view of the device of Fig. 6, taken along the lines 10-10;
Fig. 9 is a cross-sectional view of the device of Fig. 7, taken along the lines 11-11;
Fig. 10 is a plan view of a vertebral compression fracture reduction device constructed in accordance with still another embodiment of the invention, wherein the device is particularly shown in a collapsed state;
Fig. 11 is a plan view of the device of Fig. 10, wherein the device is particularly shown in a deployed state;
Fig. 12 is a plan view of a vertebral compression fracture reduction device constructed in accordance with yet another embodiment of the invention, wherein the device is particularly shown in a collapsed state;
Fig. 13 is a plan view of the device of Fig. 12, wherein the device is particularly shown in a deployed state;
Fig. 14 is a plan view of a vertebral compression fracture reduction device constructed in accordance with yet another embodiment of the invention, wherein the device is particularly shown in a collapsed state;
Fig. 15 is a plan view of the device of Fig. 14, wherein the device is particularly shown in a deployed state;
Fig. 16 is a plan view of a vertebral compression fracture reduction assembly constructed in accordance with yet another embodiment of the invention;
Fig. 17 is a perspective view of a nut used in the assembly of Fig. 16; and DETAILED DESCRIPTION OF THE ILLUSTRATED EMBODIMENTS
Referring to Figs. 2 and 3, a bone fracture reduction device 100 constructed in accordance with one embodiment of the invention is illustrated. The device can be used for treating a compression bone fracture, and specifically, a compression fracture within a vertebra. The device 100 generally comprises a pair of rigid members 102, and a coupling mechanism, and specifically a hinge 104, for coupling the members 102 together.
The materials used in constructing the members 102 may comprise any of a wide variety of biocompatible materials. In one embodiment, a radiopaque material, such as metal (e.g., stainless steel, titanium alloys, or cobalt alloys) or a polymer (e.g., ultra high molecular weight polyethylene) may be used.
Polymethylmethacrylate (PMMA) can also be used if, e.g., the device 100 or portion thereof is to be implanted within the vertebra 200.
Each member 102 has a portion 106 that is proximal to the hinge 104, and a portion 108 that is distal to the hinge 104. As illustrated in Fig. 2, the device 100 can be placed in a collapsed state by displacing the respective proximal member portions 106 away from each other, thereby displacing the respective distal member portions 108 toward each other. As will be described in further detail below, placing the device 100 in a collapsed state facilitates introduction of the distal member portions 108 into the vertebra 200.
Fig. 17 is a perspective view of a nut used in the assembly of Fig. 16; and DETAILED DESCRIPTION OF THE ILLUSTRATED EMBODIMENTS
Referring to Figs. 2 and 3, a bone fracture reduction device 100 constructed in accordance with one embodiment of the invention is illustrated. The device can be used for treating a compression bone fracture, and specifically, a compression fracture within a vertebra. The device 100 generally comprises a pair of rigid members 102, and a coupling mechanism, and specifically a hinge 104, for coupling the members 102 together.
The materials used in constructing the members 102 may comprise any of a wide variety of biocompatible materials. In one embodiment, a radiopaque material, such as metal (e.g., stainless steel, titanium alloys, or cobalt alloys) or a polymer (e.g., ultra high molecular weight polyethylene) may be used.
Polymethylmethacrylate (PMMA) can also be used if, e.g., the device 100 or portion thereof is to be implanted within the vertebra 200.
Each member 102 has a portion 106 that is proximal to the hinge 104, and a portion 108 that is distal to the hinge 104. As illustrated in Fig. 2, the device 100 can be placed in a collapsed state by displacing the respective proximal member portions 106 away from each other, thereby displacing the respective distal member portions 108 toward each other. As will be described in further detail below, placing the device 100 in a collapsed state facilitates introduction of the distal member portions 108 into the vertebra 200.
In contrast, as illustrated in Fig. 3, the device 100 can be placed in a deployed state by displacing the respective proximal member portions 106 toward each other, thereby displacing the respective distal member portions 108 away from each other. As will be described in further detail below, placing the device 100 in an expanded state causes the distal member portions 108 to create a vertical force that reduces the compression fracture 202 within the vertebra 200. As illustrated, the members 102 are angled, such that the device 100 can be fully deployed without interference between the proximal member portions 106.
The distal member portions 108 are specially designed, such that they can be introduced through smaller channels within the vertebra 200 (e.g., through an gauge channel drilled into the bone), without significant loss of shear strength in the direction of their movement. Notably, the smaller the hole through which the device 100 is introduced, the less trauma is caused to the region.
To this end, each member 102 comprises a common base 110 and a plurality of ribs 112 (specifically, flutes) extending along the length of the common base 110, as best shown in Figs. 4 and 5. As illustrated, the ribs 112 of the respective members 102 are configured to engage each other in an interposed arrangement when the device 100 is placed into the collapsed configuration (Fig. 4), and are configured to disengage each other when the device 100 is placed into the deployed state (Fig. 5). In this manner, the combined cross-sectional profile of the members 102 can be reduced when the device 100 is placed in the collapsed state, thereby minimizing the size of the channel needed to introduce the device 100 within the vertebra 200.
Specifically, the combined cross-sectional profile of the members 102 is about the same as the individual cross-sectional profiles of the members 102 when the device 100 is placed in the deployed state. As can be seen, the combined cross-sectional profile is a circle having a radius r, and the individual cross-sectional profiles are circles having radii r~, r2, wherein the radius r is approximately equal to the radii r~, r2.
Although the combined cross-sectional profile of the members 102 is reduced when the device 100 is placed in the collapsed state, the shear strength of each member 102 is not substantially reduced when the device 100 is placed in the deployed state. Specifically, the ribs 112 support the members 102 along the direction in which shear forces will be applied during deployment of the device 100.
In essence, the members 102 have almost the same amount of shear strength as if they were composed of a solid piece of material.
It can be appreciated that the provision of ribs 112 on the distal member portions 108 allows the device 100 to be collapsed enough to be introduced through a small passage into a vertebra, yet maintain the shear strength necessary to reduce a compression fracture therein.
Referring to Figs. 6 and 7, another bone fracture reduction device 150 constructed in accordance with one embodiment of the invention is illustrated.
The device 150 can be used for treating a compression bone fracture, and specifically, a compression fracture within a vertebra. The device 150 can be especially used on patients with a relatively large amount of tissue between the skin and the vertebra, because all actuation is accomplished within the vertebra itself. The device generally comprises a pair of proximal rigid members 152, a pair of distal rigid members 154, a pair of intermediate coupling mechanisms (specifically, hinges 156) coupling the proximal members 152 to the distal members 154, and an actuating coupling assembly 158 for alternatively placing the device 150 in a collapsed state and a deployed state, as will be described in further detail below.
The materials used in constructing the proximal and distal members 152/154 may comprise any of a wide variety of rigid biocompatible materials. In one embodiment, a radiopaque material, such as metal (e.g., stainless steel, titanium alloys, or cobalt alloys) or a polymer (e.g., ultra high molecular weight polyethylene) may be used. PMMA can also be used if, e.g., the device 150 or portion thereof is to be implanted within the vertebra 200.
The actuating coupling assembly 158 generally comprises a distal coupling assembly 160, a proximal coupling assembly 162, and a drive 164 that interacts with the coupling assemblies 160 and 162. Specifically, the drive 164 comprises a threaded drive shaft or drive screw 166 having a proximal end 168 and a distal end 170, and a drive coupling 172 mounted to the proximal end 168 of the drive screw 166. The distal coupling assembly 160 comprises a hollow spherical cap 174 in which the distal end 170 of the drive screw 166 freely rotates, and a pair of hinges 176 that are coupled to the respective distal ends of the distal members 154.
The proximal distal coupling assembly 162 comprises a nut 178 through which the drive screw 166 extends, and a pair of hinges 180 that are coupled to the respective proximal ends of the proximal members 152. Because the drive screw 166 is threaded, the nut 178 (which is also threaded) will be longitudinally displaced in the distal direction towards the spherical cap 174 when the drive screw 166 is rotated in one direction, and will be longitudinally displaced in the proximal direction away from the spherical cap 174 when the drive screw 166 is rotated in the other direction.
In response to distal displacement of the nut 178 relative to the spherical cap 174, the hinging action of the intermediate hinges 156, distal hinges 176, and proximal hinges 180 will cause the pair of proximal members 152 and the pair of distal members 154 to move towards each other-in effect collapsing upon each other, which will then cause the distal ends of the proximal members 152 and the proximal ends of the distal members 154 to move outward (i.e., away from the drive screw 166) at central hinge points 182, thereby placing the device 150 in its deployed state (Fig. 7). In contrast, in response to proximal displacement of the nut 178 relative to the spherical cap 174, the hinging action of the intermediate hinges 156, distal hinges 176, and proximal hinges 180 will cause the pair of proximal members 152 and the pair of distal members 154 to move away from each other at the central hinge points 182, which will then cause the distal ends of the proximal members 152 and the proximal ends of the distal members 154 to move inward (i.e., towards the drive screw 166), thereby placing the device 150 in its collapsed state (Fig. 6).
Like with the previously described members of the device 100, the proximal and distal members 154 of the device 150 are specially designed, such that they can be introduced through smaller channels within the vertebra 200 without significant loss of shear strength in the direction of their movement. To this end, each proximal member 152 comprises a common base 184 and a plurality of ribs 186 (specifically, flutes) extending along the length of the common base 184, as best shown in Figs. 8 and 9. As illustrated, the ribs 186 of the proximal members 152 are configured to engage each other in an interposed arrangement when the device 150 is placed into the collapsed configuration (Fig. 8), and are configured to disengage each other when the device 150 is placed into the deployed state (Fig. 9). As illustrated, the distal ends of some of the ribs 186 have been removed to provide a channel 188 that accommodates the drive screw 166 when the device 150 is in the collapsed state.
Although not shown, the distal members 154 are similarly constructed and interact with each other in the same manner.
It can be appreciated that, in the same manner as that described above with respect to the device 100, the combined cross-sectional profile of the proximal members 152, and the combined cross-sectional profile of the distal members 154, are reduced when the device 150 is placed in the collapsed state, yet the shear strength of each member 152/154 is not substantially reduced when the device is placed in the deployed state.
Again, it can be appreciated that the provision of ribs 186 on the members 152/154 allows the device 150 to be collapsed enough to be introduced through a small passage into a vertebra, yet maintain the shear strength necessary to reduce a compression fracture therein.
It should be noted that any number of the hinges 156, 176, and 180 of the device 150 can be replaced with "living" hinges, it which case, a corresponding proximal member 152 and distal member 154 would be replaced with a single member that is directly coupled between the spherical cap 174 and nut 178. For example, Figs. 10 and 11 illustrate a bone fracture reduction device 300 that is similar to the device 150 with the exception that it uses living hinges (i.e., portions where the members are bent or deformed). In particular, the device 300 comprises a pair of rigid members 302 that are formed between the distal spherical cap 174 and the nut 178. Each rigid member 302 comprises a proximal portion 304, a distal portion 306, an intermediate living hinge 308 formed between the proximal and distal portions 304 and 306, a proximal living hinge 31 0 formed between the proximal portion 304 and the nut 178, and a distal living hinge 312 formed between the distal portion 306 and the spherical cap 174.
In response to distal displacement of the nut 178 relative to the spherical cap 174, the hinging action of the intermediate hinge 308, proximal hinge 310, and distal hinge 312 (i.e., bending or deformation of the members 302) will cause the proximal and distal portions 304 and 306 of each member 302 to move towards each other-s in effect collapsing upon each other, which will then cause the distal ends of the proximal portions 304 and the proximal ends of the distal portions 306 fio move outward (i.e., away from the drive screw 166) at central hinge points 314, thereby placing the device 300 in its deployed state (Fig. 11 ). In contrast, in response to proximal displacement of the nut 178 relative to the spherical cap 174, the hinging action of the intermediate hinge 308, proximal hinge 310, and distal hinge 312 will cause the proximal portions 304 and the distal portions 306 to move away from each other at the central hinge points 314, which will then cause the distal ends of the proximal portions 304 and the proximal ends of the distal portions 306 to move inward (i.e., towards the drive screw 166), thereby placing the device 300 in its collapsed state (Fig.10).
Like with the previously described members of the device 150, the members 302 of the device 300~are specially designed, such that they can be introduced through smaller channels within the vertebra 200 without significant loss of shear strength in the direction of their movement. That is, the members 302 have ribs similar to the ribs 186 illustrated in Figs. 8 and 9. The device 300 can be used to reduce a vertebral compression fracture.
Referring now to Figs, 12 and 13, another bone fracture reduction device 350 is illustrated. The device 350 is similar to the previously described device 300 with the exception that it includes a pair of central supports as opposed to central hinge points. The device 350 comprises a pair of rigid members 352 formed between the distal spherical cap 174 and the nut 178. Each member 352 comprises a proximal portion 354, a distal portion 356, and a central portion 358. Each member 352 also comprises two intermediate living hinges 360 between central portion 358 and the respective proximal and distal portions 354 and 356, a proximal living hinge formed between the proximal portion 354 and the nut 178, and a distal living hinge 364 formed between the distal portion 356 and the spherical cap 174.
In response to distal displacement of the nut 178 relative to the spherical cap 174, the hinging action of the intermediate hinges 360, proximal hinge 362, and distal hinges 364 will cause the proximal and distal portions 354 and 356 of each member 302 to move towards each other-in effect collapsing upon each other, which will then cause the central portions 358 to move outward (i.e., away from the drive screw 166), thereby placing the device 350 in its deployed state (Fig.
13). In contrast, in response to proximal displacement of the nut 178 relative to the spherical cap 174, the hinging action of the intermediate hinges 360, proximal hinges 362, and distal hinges 364 will cause the proximal portions 354 and the distal portions 356 to move away from each other, which will then cause the central portions 358 to move inward (i.e., towards the drive screw 166), thereby placing the device 350 in its collapsed state (Fig. 12).
Like with the previously described members of the device 150, the members 352 of the device 350 are specially designed, such that they can be introduced through smaller channels within a vertebra without significant loss of shear strength in the direction of their movement. That is, the members 352 have ribs similar to the ribs 186 illustrated in Figs. 8 and 9. The device 350 can be used to reduce a vertebral compression fracture in the same manner as the above-described devices, with the exception that the central portions 358 engages a greater area of the bone structure than does the central hinge points 182, thereby providing a greater control in reducing the fracture, as well as minimizing damage to the inferior and superior sides of the vertebra.
Referring now to Figs. 14 and 15, another bone fracture reduction device 400 is illustrated. The device 400 is similar to the previously described device 300 with the exception that it includes a shear rod or wire, rather than a drive screw.
In particular, the device 400 comprises an annular ring 402, and a shear wire 404 that has a distal end 406 that is mounted within the spherical cap 174 (e.g., by soldering, glue, welding, or other suitable junction method), and a proximal end 408 that extends through the aperture (not sho~nrn) of the annular ring 402.
Proximal movement of the shear wire 404 relative to the annular ring 402 (e.g., by pulling the shear wire 404) will longitudinally displace the spherical cap 174 in the proximal direction. In response to proximal displacement of the spherical cap 174 relative to the annular ring 402, the hinging action of the intermediate hinge 308, proximal hinge 310, and distal hinge 312 will cause the proximal and distal portions 304 and 306 of each member 302 to bend or deform towards each other-in effect collapsing upon each other, which will then cause the distal ends of the proximal portions 304 and the proximal ends of the distal portions 306 to move outward (i.e., away from the shear wire 404) at central hinge points 314, thereby placing the device 400 in its deployed state (Fig. 15). The shear wire 404 has a weakened region 410 near it distal end 406 that breaks once a predetermined tensile force has been exerted on the shear wire 404. In this manner, once the device has been fully deployed, the tensile force on the shear wire 404 will increase causing the shear wire 404 to break. The device 400 will remain in its deployed state by virtue of the natural resistance of the members 304 to return to their undeformed state. Alternatively, the shear wire 404 can be designed, such that the weakened region 410 is inside or just proximal to the annular ring 402 when the device 400 is fully deployed. In this case, the portion of the shear wire 404 just distal to the weakened region 410 can be designed, such that it wedges into the annular ring when the shear wire 404 breaks.
Once the device 400 has been placed in the deployed state, it cannot be normally placed back into the collapsed state. If the shear wire 404 is replaced with a shear rod that exhibits the necessary column strength, however, the device can be placed back into the collapsed state if the shear rod has not yet broken. In this case, the shear rod may be distally displaced to cause the distal ends of the proximal portions 304 of the members 302 and the proximal ends of the distal portions 306 of the members 304 to move inward (i.e., toward the shear rod) at central hinge points 314, thereby placing the device 400 in the collapsed state (Fig.
14).
The device 400 can be used to reduce a vertebral compression fracture in the same manner as the above-described devices, with the exception that the shear wire 404 is pulled in order to deploy the device 400. In addition, the shear wire automatically breaks off after deployment of the device 400, whereas in the former case, an affirmative step must be taken in order to break the drive screw 166 off.
It should be noted that during deployment, the previously described devices can be positioned and stabilized using any of a variety of mechanisms. For example, Fig. 'i6 illustrates a bone fracture treatment assembly 450 that generally comprises a bone fracture reduction device 452, a cannula 454 that is configured to stabilize and control the position of the device 452, and a screw driver 456 for actuating deployment of the device 452.
The cannula 454 comprises a shaft 458 with a distal tip 462, and a lumen 460 extending through the cannufa shaft 458. To facilitate control of the device 452, the cannula shaft 458 is preferably stiff (e.g., it can be composed of a stiff material, or reinforced with a coating or a coil to control the amount of flexing). The materials used in constructing the cannula shaft 458 may comprise any of a wide variety of biocompatible materials. In one embodiment, a radiopaque material, such as metal (e.g., stainless steel, titanium alloys, or cobalt alloys) or a polymer (e.g., ultra high molecular weight polyethylene) may be used.
The outer diameter of the cannula shaft 458 is preferably less than %2 inch, although other dimensions for the outer diameter may also be appropriate, depending on the particular application or clinical procedure. The cannula lumen 460 should have a d iameter so as to allow movement of the screw driver 456 therein. In the illustrated embodiment, the profile of the cannula lumen 460 is circular, but can be other shapes as well.
The device 452 is similar to the previously described device 150 with the exception that it com prises a nut 464 that is specifically configured for engaging the cannula 454. In particular, the nut 464 comprises clasps 466 (shown in Fig.
17) for grasping the distal tip 462 of the cannula 454. For example, four clasps 464 can be provided for respectively grasping the top, bottom, left side, and right side of the cannula tip. The screw driver 456 comprises a shaft 468 and a distal tip 470 that is configured for engaging the drive coupling 172 of the drive 164. For example, if the drive coupling 172 is a hex head, the distal tip 470 of the screw driver 456 can be a hex socket. If the drive coupling 172 has a slot, the distal tip 470 of the screw driver 456 can be a flat flange.
It should be noted that all of the biocompatible members described herein can be composed of a semi-rigid, rather than a rigid, material. For the purposes of this specification, a semi-rigid member is one that laterally flexes in the presence of the force required to reduce the compression fracture of the bone structure in which the member is intended to be introduced. Providing semi-rigid members has the advantage of distributing the stress along the bone surface that the members contact, thereby minimizing the risk that a member will puncture or fracture the wall of the bone structure at areas other than the original fracture site.
It should also be noted that the use of the devices described herein are not limited to the reduction of a bone fracture, but can also be used for stabilizing adjacent bone structures, e.g., vertebrae, with or without additional material to further stabilize the bone structures.
The distal member portions 108 are specially designed, such that they can be introduced through smaller channels within the vertebra 200 (e.g., through an gauge channel drilled into the bone), without significant loss of shear strength in the direction of their movement. Notably, the smaller the hole through which the device 100 is introduced, the less trauma is caused to the region.
To this end, each member 102 comprises a common base 110 and a plurality of ribs 112 (specifically, flutes) extending along the length of the common base 110, as best shown in Figs. 4 and 5. As illustrated, the ribs 112 of the respective members 102 are configured to engage each other in an interposed arrangement when the device 100 is placed into the collapsed configuration (Fig. 4), and are configured to disengage each other when the device 100 is placed into the deployed state (Fig. 5). In this manner, the combined cross-sectional profile of the members 102 can be reduced when the device 100 is placed in the collapsed state, thereby minimizing the size of the channel needed to introduce the device 100 within the vertebra 200.
Specifically, the combined cross-sectional profile of the members 102 is about the same as the individual cross-sectional profiles of the members 102 when the device 100 is placed in the deployed state. As can be seen, the combined cross-sectional profile is a circle having a radius r, and the individual cross-sectional profiles are circles having radii r~, r2, wherein the radius r is approximately equal to the radii r~, r2.
Although the combined cross-sectional profile of the members 102 is reduced when the device 100 is placed in the collapsed state, the shear strength of each member 102 is not substantially reduced when the device 100 is placed in the deployed state. Specifically, the ribs 112 support the members 102 along the direction in which shear forces will be applied during deployment of the device 100.
In essence, the members 102 have almost the same amount of shear strength as if they were composed of a solid piece of material.
It can be appreciated that the provision of ribs 112 on the distal member portions 108 allows the device 100 to be collapsed enough to be introduced through a small passage into a vertebra, yet maintain the shear strength necessary to reduce a compression fracture therein.
Referring to Figs. 6 and 7, another bone fracture reduction device 150 constructed in accordance with one embodiment of the invention is illustrated.
The device 150 can be used for treating a compression bone fracture, and specifically, a compression fracture within a vertebra. The device 150 can be especially used on patients with a relatively large amount of tissue between the skin and the vertebra, because all actuation is accomplished within the vertebra itself. The device generally comprises a pair of proximal rigid members 152, a pair of distal rigid members 154, a pair of intermediate coupling mechanisms (specifically, hinges 156) coupling the proximal members 152 to the distal members 154, and an actuating coupling assembly 158 for alternatively placing the device 150 in a collapsed state and a deployed state, as will be described in further detail below.
The materials used in constructing the proximal and distal members 152/154 may comprise any of a wide variety of rigid biocompatible materials. In one embodiment, a radiopaque material, such as metal (e.g., stainless steel, titanium alloys, or cobalt alloys) or a polymer (e.g., ultra high molecular weight polyethylene) may be used. PMMA can also be used if, e.g., the device 150 or portion thereof is to be implanted within the vertebra 200.
The actuating coupling assembly 158 generally comprises a distal coupling assembly 160, a proximal coupling assembly 162, and a drive 164 that interacts with the coupling assemblies 160 and 162. Specifically, the drive 164 comprises a threaded drive shaft or drive screw 166 having a proximal end 168 and a distal end 170, and a drive coupling 172 mounted to the proximal end 168 of the drive screw 166. The distal coupling assembly 160 comprises a hollow spherical cap 174 in which the distal end 170 of the drive screw 166 freely rotates, and a pair of hinges 176 that are coupled to the respective distal ends of the distal members 154.
The proximal distal coupling assembly 162 comprises a nut 178 through which the drive screw 166 extends, and a pair of hinges 180 that are coupled to the respective proximal ends of the proximal members 152. Because the drive screw 166 is threaded, the nut 178 (which is also threaded) will be longitudinally displaced in the distal direction towards the spherical cap 174 when the drive screw 166 is rotated in one direction, and will be longitudinally displaced in the proximal direction away from the spherical cap 174 when the drive screw 166 is rotated in the other direction.
In response to distal displacement of the nut 178 relative to the spherical cap 174, the hinging action of the intermediate hinges 156, distal hinges 176, and proximal hinges 180 will cause the pair of proximal members 152 and the pair of distal members 154 to move towards each other-in effect collapsing upon each other, which will then cause the distal ends of the proximal members 152 and the proximal ends of the distal members 154 to move outward (i.e., away from the drive screw 166) at central hinge points 182, thereby placing the device 150 in its deployed state (Fig. 7). In contrast, in response to proximal displacement of the nut 178 relative to the spherical cap 174, the hinging action of the intermediate hinges 156, distal hinges 176, and proximal hinges 180 will cause the pair of proximal members 152 and the pair of distal members 154 to move away from each other at the central hinge points 182, which will then cause the distal ends of the proximal members 152 and the proximal ends of the distal members 154 to move inward (i.e., towards the drive screw 166), thereby placing the device 150 in its collapsed state (Fig. 6).
Like with the previously described members of the device 100, the proximal and distal members 154 of the device 150 are specially designed, such that they can be introduced through smaller channels within the vertebra 200 without significant loss of shear strength in the direction of their movement. To this end, each proximal member 152 comprises a common base 184 and a plurality of ribs 186 (specifically, flutes) extending along the length of the common base 184, as best shown in Figs. 8 and 9. As illustrated, the ribs 186 of the proximal members 152 are configured to engage each other in an interposed arrangement when the device 150 is placed into the collapsed configuration (Fig. 8), and are configured to disengage each other when the device 150 is placed into the deployed state (Fig. 9). As illustrated, the distal ends of some of the ribs 186 have been removed to provide a channel 188 that accommodates the drive screw 166 when the device 150 is in the collapsed state.
Although not shown, the distal members 154 are similarly constructed and interact with each other in the same manner.
It can be appreciated that, in the same manner as that described above with respect to the device 100, the combined cross-sectional profile of the proximal members 152, and the combined cross-sectional profile of the distal members 154, are reduced when the device 150 is placed in the collapsed state, yet the shear strength of each member 152/154 is not substantially reduced when the device is placed in the deployed state.
Again, it can be appreciated that the provision of ribs 186 on the members 152/154 allows the device 150 to be collapsed enough to be introduced through a small passage into a vertebra, yet maintain the shear strength necessary to reduce a compression fracture therein.
It should be noted that any number of the hinges 156, 176, and 180 of the device 150 can be replaced with "living" hinges, it which case, a corresponding proximal member 152 and distal member 154 would be replaced with a single member that is directly coupled between the spherical cap 174 and nut 178. For example, Figs. 10 and 11 illustrate a bone fracture reduction device 300 that is similar to the device 150 with the exception that it uses living hinges (i.e., portions where the members are bent or deformed). In particular, the device 300 comprises a pair of rigid members 302 that are formed between the distal spherical cap 174 and the nut 178. Each rigid member 302 comprises a proximal portion 304, a distal portion 306, an intermediate living hinge 308 formed between the proximal and distal portions 304 and 306, a proximal living hinge 31 0 formed between the proximal portion 304 and the nut 178, and a distal living hinge 312 formed between the distal portion 306 and the spherical cap 174.
In response to distal displacement of the nut 178 relative to the spherical cap 174, the hinging action of the intermediate hinge 308, proximal hinge 310, and distal hinge 312 (i.e., bending or deformation of the members 302) will cause the proximal and distal portions 304 and 306 of each member 302 to move towards each other-s in effect collapsing upon each other, which will then cause the distal ends of the proximal portions 304 and the proximal ends of the distal portions 306 fio move outward (i.e., away from the drive screw 166) at central hinge points 314, thereby placing the device 300 in its deployed state (Fig. 11 ). In contrast, in response to proximal displacement of the nut 178 relative to the spherical cap 174, the hinging action of the intermediate hinge 308, proximal hinge 310, and distal hinge 312 will cause the proximal portions 304 and the distal portions 306 to move away from each other at the central hinge points 314, which will then cause the distal ends of the proximal portions 304 and the proximal ends of the distal portions 306 to move inward (i.e., towards the drive screw 166), thereby placing the device 300 in its collapsed state (Fig.10).
Like with the previously described members of the device 150, the members 302 of the device 300~are specially designed, such that they can be introduced through smaller channels within the vertebra 200 without significant loss of shear strength in the direction of their movement. That is, the members 302 have ribs similar to the ribs 186 illustrated in Figs. 8 and 9. The device 300 can be used to reduce a vertebral compression fracture.
Referring now to Figs, 12 and 13, another bone fracture reduction device 350 is illustrated. The device 350 is similar to the previously described device 300 with the exception that it includes a pair of central supports as opposed to central hinge points. The device 350 comprises a pair of rigid members 352 formed between the distal spherical cap 174 and the nut 178. Each member 352 comprises a proximal portion 354, a distal portion 356, and a central portion 358. Each member 352 also comprises two intermediate living hinges 360 between central portion 358 and the respective proximal and distal portions 354 and 356, a proximal living hinge formed between the proximal portion 354 and the nut 178, and a distal living hinge 364 formed between the distal portion 356 and the spherical cap 174.
In response to distal displacement of the nut 178 relative to the spherical cap 174, the hinging action of the intermediate hinges 360, proximal hinge 362, and distal hinges 364 will cause the proximal and distal portions 354 and 356 of each member 302 to move towards each other-in effect collapsing upon each other, which will then cause the central portions 358 to move outward (i.e., away from the drive screw 166), thereby placing the device 350 in its deployed state (Fig.
13). In contrast, in response to proximal displacement of the nut 178 relative to the spherical cap 174, the hinging action of the intermediate hinges 360, proximal hinges 362, and distal hinges 364 will cause the proximal portions 354 and the distal portions 356 to move away from each other, which will then cause the central portions 358 to move inward (i.e., towards the drive screw 166), thereby placing the device 350 in its collapsed state (Fig. 12).
Like with the previously described members of the device 150, the members 352 of the device 350 are specially designed, such that they can be introduced through smaller channels within a vertebra without significant loss of shear strength in the direction of their movement. That is, the members 352 have ribs similar to the ribs 186 illustrated in Figs. 8 and 9. The device 350 can be used to reduce a vertebral compression fracture in the same manner as the above-described devices, with the exception that the central portions 358 engages a greater area of the bone structure than does the central hinge points 182, thereby providing a greater control in reducing the fracture, as well as minimizing damage to the inferior and superior sides of the vertebra.
Referring now to Figs. 14 and 15, another bone fracture reduction device 400 is illustrated. The device 400 is similar to the previously described device 300 with the exception that it includes a shear rod or wire, rather than a drive screw.
In particular, the device 400 comprises an annular ring 402, and a shear wire 404 that has a distal end 406 that is mounted within the spherical cap 174 (e.g., by soldering, glue, welding, or other suitable junction method), and a proximal end 408 that extends through the aperture (not sho~nrn) of the annular ring 402.
Proximal movement of the shear wire 404 relative to the annular ring 402 (e.g., by pulling the shear wire 404) will longitudinally displace the spherical cap 174 in the proximal direction. In response to proximal displacement of the spherical cap 174 relative to the annular ring 402, the hinging action of the intermediate hinge 308, proximal hinge 310, and distal hinge 312 will cause the proximal and distal portions 304 and 306 of each member 302 to bend or deform towards each other-in effect collapsing upon each other, which will then cause the distal ends of the proximal portions 304 and the proximal ends of the distal portions 306 to move outward (i.e., away from the shear wire 404) at central hinge points 314, thereby placing the device 400 in its deployed state (Fig. 15). The shear wire 404 has a weakened region 410 near it distal end 406 that breaks once a predetermined tensile force has been exerted on the shear wire 404. In this manner, once the device has been fully deployed, the tensile force on the shear wire 404 will increase causing the shear wire 404 to break. The device 400 will remain in its deployed state by virtue of the natural resistance of the members 304 to return to their undeformed state. Alternatively, the shear wire 404 can be designed, such that the weakened region 410 is inside or just proximal to the annular ring 402 when the device 400 is fully deployed. In this case, the portion of the shear wire 404 just distal to the weakened region 410 can be designed, such that it wedges into the annular ring when the shear wire 404 breaks.
Once the device 400 has been placed in the deployed state, it cannot be normally placed back into the collapsed state. If the shear wire 404 is replaced with a shear rod that exhibits the necessary column strength, however, the device can be placed back into the collapsed state if the shear rod has not yet broken. In this case, the shear rod may be distally displaced to cause the distal ends of the proximal portions 304 of the members 302 and the proximal ends of the distal portions 306 of the members 304 to move inward (i.e., toward the shear rod) at central hinge points 314, thereby placing the device 400 in the collapsed state (Fig.
14).
The device 400 can be used to reduce a vertebral compression fracture in the same manner as the above-described devices, with the exception that the shear wire 404 is pulled in order to deploy the device 400. In addition, the shear wire automatically breaks off after deployment of the device 400, whereas in the former case, an affirmative step must be taken in order to break the drive screw 166 off.
It should be noted that during deployment, the previously described devices can be positioned and stabilized using any of a variety of mechanisms. For example, Fig. 'i6 illustrates a bone fracture treatment assembly 450 that generally comprises a bone fracture reduction device 452, a cannula 454 that is configured to stabilize and control the position of the device 452, and a screw driver 456 for actuating deployment of the device 452.
The cannula 454 comprises a shaft 458 with a distal tip 462, and a lumen 460 extending through the cannufa shaft 458. To facilitate control of the device 452, the cannula shaft 458 is preferably stiff (e.g., it can be composed of a stiff material, or reinforced with a coating or a coil to control the amount of flexing). The materials used in constructing the cannula shaft 458 may comprise any of a wide variety of biocompatible materials. In one embodiment, a radiopaque material, such as metal (e.g., stainless steel, titanium alloys, or cobalt alloys) or a polymer (e.g., ultra high molecular weight polyethylene) may be used.
The outer diameter of the cannula shaft 458 is preferably less than %2 inch, although other dimensions for the outer diameter may also be appropriate, depending on the particular application or clinical procedure. The cannula lumen 460 should have a d iameter so as to allow movement of the screw driver 456 therein. In the illustrated embodiment, the profile of the cannula lumen 460 is circular, but can be other shapes as well.
The device 452 is similar to the previously described device 150 with the exception that it com prises a nut 464 that is specifically configured for engaging the cannula 454. In particular, the nut 464 comprises clasps 466 (shown in Fig.
17) for grasping the distal tip 462 of the cannula 454. For example, four clasps 464 can be provided for respectively grasping the top, bottom, left side, and right side of the cannula tip. The screw driver 456 comprises a shaft 468 and a distal tip 470 that is configured for engaging the drive coupling 172 of the drive 164. For example, if the drive coupling 172 is a hex head, the distal tip 470 of the screw driver 456 can be a hex socket. If the drive coupling 172 has a slot, the distal tip 470 of the screw driver 456 can be a flat flange.
It should be noted that all of the biocompatible members described herein can be composed of a semi-rigid, rather than a rigid, material. For the purposes of this specification, a semi-rigid member is one that laterally flexes in the presence of the force required to reduce the compression fracture of the bone structure in which the member is intended to be introduced. Providing semi-rigid members has the advantage of distributing the stress along the bone surface that the members contact, thereby minimizing the risk that a member will puncture or fracture the wall of the bone structure at areas other than the original fracture site.
It should also be noted that the use of the devices described herein are not limited to the reduction of a bone fracture, but can also be used for stabilizing adjacent bone structures, e.g., vertebrae, with or without additional material to further stabilize the bone structures.
Claims (22)
1. A device for treating a bone structure, comprising:
a first biocompatible rigid or semi-rigid member having a first common base and a first plurality of ribs extending along at least a longitudinal portion of the first common base; and a second biocompatible rigid or semi-rigid member having a common base and a second plurality of ribs extending along at least a longitudinal portion of the second common base;
characterized in that the device is configured to be placed in a collapsed state by engaging the first and second pluralities of ribs in an interposed arrangement, and in a deployed state by disengaging the first and second pluralities of ribs.
a first biocompatible rigid or semi-rigid member having a first common base and a first plurality of ribs extending along at least a longitudinal portion of the first common base; and a second biocompatible rigid or semi-rigid member having a common base and a second plurality of ribs extending along at least a longitudinal portion of the second common base;
characterized in that the device is configured to be placed in a collapsed state by engaging the first and second pluralities of ribs in an interposed arrangement, and in a deployed state by disengaging the first and second pluralities of ribs.
2. The device of claim 1, further comprising a coupling mechanism that couples the first and second members together.
3. The device of claim 2, wherein the coupling mechanism is a hinge.
4. The device of any of claims 1 - 3, wherein the first and second pluralities of ribs are flutes.
5. The device of any of claims 1 - 4, wherein the first and second members have a combined cross-sectional profile, and each of the first and second members has an individual cross-sectional profile, the combined cross-sectional profile being substantially the same as the individual cross-sectional profile.
6. The device of any of claims 1 - 4, wherein the first and second members have a combined cross-sectional circular profile, and each of the first and second members has a respective individual cross-sectional arcuate profile, the combined cross-sectional profile having a radius that is substantially equal to a radius of curvature of the individual cross-sectional profile.
7. The device of any of claims 1 - 6, wherein the first and second members are sized to fit within a vertebra.
8. A device for treating a bone structure, comprising:
first and second proximal biocompatible member portions;
first and second distal biocompatible member portions;
a first intermediate hinge located between the respective proximal and distal member portions, wherein a first hinge point is formed;
a second intermediate hinge located between the respective proximal and distal member portions, wherein a second hinge point is formed; and an actuating coupling assembly configured for displacing proximal ends of the first and second proximal member portions and distal ends of the first and second distal member portions towards each other, whereby the first and second hinge points are respectively displaced outward away from each other to deploy the device.
first and second proximal biocompatible member portions;
first and second distal biocompatible member portions;
a first intermediate hinge located between the respective proximal and distal member portions, wherein a first hinge point is formed;
a second intermediate hinge located between the respective proximal and distal member portions, wherein a second hinge point is formed; and an actuating coupling assembly configured for displacing proximal ends of the first and second proximal member portions and distal ends of the first and second distal member portions towards each other, whereby the first and second hinge points are respectively displaced outward away from each other to deploy the device.
9. The device of claim 8, wherein the coupling assembly is configured for displacing the proximal ends of the first and second proximal member portions and the distal ends of the first and second distal member portions away from each other, whereby the first and second hinge points are respectively displaced inward towards each other to collapse the device.
10. The device of claim 8, wherein the coupling assembly comprises a drive shaft, a proximal coupling mechanism coupled to the drive shaft, and a distal coupling mechanism coupled to the drive shaft, the device further comprising proximal hinges between the respective proximal member portions and the proximal coupling mechanism, and distal hinges between the respective distal members portions and the distal coupling mechanism.
11. The device of claim 10, wherein the drive shaft is a drive screw, and the proximal coupling mechanism comprises a nut in which the drive screw is threadedly engaged.
12. The device of claim 10, wherein the drive shaft is a shear wire and the proximal coupling mechanism is an annular ring through which the shear wire is slidably engaged.
13. The device of claim 12, wherein the shear wire comprises a weakened region that causes the shear wire to break after the device has been fully deployed.
14. The device of claim 10, wherein the distal coupling mechanism is a spherical cap that houses a distal end of the drive shaft.
15. The device of claim 8, wherein the first proximal and distal member portions form separate members, and the second proximal and distal member portions form separate members.
16. The device of claim 8, wherein the first proximal and distal member portions form a single member, the second proximal and distal member portions form a single member, and the first and second intermediate hinges are living hinges.
17. The device of claim 8, further comprising:
a first central biocompatible member portion located between the first proximal and distal member portions, wherein the first intermediate hinge is located between the first proximal member portion and the first central member portion;
a second central biocompatible member portion located between the second proximal and distal member portions, wherein the second intermediate hinge is located between the second proximal member portion and the second central member portion;
a third intermediate hinge located between the first distal member portion and the first central member portion; and a fourth intermediate hinge located between the second distal member portion and the second central member portion;
whereby the first and second central member portions are respectively displaced outward away from each to deploy the device when the actuating coupling assembly displaces the proximal ends of the first and second proximal member portions and the distal ends of the first and second distal member portions towards each other.
a first central biocompatible member portion located between the first proximal and distal member portions, wherein the first intermediate hinge is located between the first proximal member portion and the first central member portion;
a second central biocompatible member portion located between the second proximal and distal member portions, wherein the second intermediate hinge is located between the second proximal member portion and the second central member portion;
a third intermediate hinge located between the first distal member portion and the first central member portion; and a fourth intermediate hinge located between the second distal member portion and the second central member portion;
whereby the first and second central member portions are respectively displaced outward away from each to deploy the device when the actuating coupling assembly displaces the proximal ends of the first and second proximal member portions and the distal ends of the first and second distal member portions towards each other.
18. The device of claim 8, wherein each of the member portions comprises a common base and a plurality of ribs extending along at least a longitudinal portion of the common base, wherein the device is configured to be placed in a collapsed state by engaging the respective pluralities of ribs of the first proximal and distal member portions in an interposed arrangement and engaging the respective pluralities of ribs of the second proximal and distal member portions in an interposed arrangement, and wherein the device is configured to be placed in a deployed state by disengaging the respective pluralities of ribs of the first proximal and distal member portions and disengaging the respective pluralities of ribs of the second proximal and distal member portions.
19. The device of any of claims 8 - 18, wherein the member portions are sized to fit within a vertebra.
20. The device of any of claims 8 - 19, further comprising a cannula configured for controllably engaging the actuating coupling assembly.
21. The device of any of claims 8 - 20, further comprising a driver configured for operating the actuating coupling assembly.
22
Applications Claiming Priority (3)
| Application Number | Priority Date | Filing Date | Title |
|---|---|---|---|
| US10/674,723 US7513900B2 (en) | 2003-09-29 | 2003-09-29 | Apparatus and methods for reducing compression bone fractures using high strength ribbed members |
| US10/674,723 | 2003-09-29 | ||
| PCT/US2004/031379 WO2005032433A2 (en) | 2003-09-29 | 2004-09-24 | Apparatus for reducing compression bone fractures using high strength ribbed members |
Publications (1)
| Publication Number | Publication Date |
|---|---|
| CA2540211A1 true CA2540211A1 (en) | 2005-04-14 |
Family
ID=34376928
Family Applications (1)
| Application Number | Title | Priority Date | Filing Date |
|---|---|---|---|
| CA002540211A Abandoned CA2540211A1 (en) | 2003-09-29 | 2004-09-24 | Apparatus for reducing compression bone fractures using high strength ribbed members |
Country Status (5)
| Country | Link |
|---|---|
| US (1) | US7513900B2 (en) |
| EP (1) | EP1673046A2 (en) |
| JP (1) | JP2007515197A (en) |
| CA (1) | CA2540211A1 (en) |
| WO (1) | WO2005032433A2 (en) |
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2003
- 2003-09-29 US US10/674,723 patent/US7513900B2/en not_active Expired - Fee Related
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- 2004-09-24 WO PCT/US2004/031379 patent/WO2005032433A2/en active Application Filing
- 2004-09-24 EP EP04784978A patent/EP1673046A2/en not_active Withdrawn
- 2004-09-24 CA CA002540211A patent/CA2540211A1/en not_active Abandoned
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| JP2007515197A (en) | 2007-06-14 |
| EP1673046A2 (en) | 2006-06-28 |
| US20050070911A1 (en) | 2005-03-31 |
| WO2005032433A3 (en) | 2005-07-21 |
| WO2005032433A2 (en) | 2005-04-14 |
| US7513900B2 (en) | 2009-04-07 |
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| Date | Code | Title | Description |
|---|---|---|---|
| FZDE | Discontinued |