Source: http://www.google.com/patents/US7335205?dq=U.S.+Patent+%23+5,723,324
Timestamp: 2016-09-28 20:44:39
Document Index: 424527173

Matched Legal Cases: ['art.\n4', 'art.\n6', 'art.\n7', 'art.\n10', 'art.\n17', 'art.\n21', 'art.\n39', 'art.\n40', 'art.\n42', 'art.\n43', 'art.\n49', 'art.\n61', 'art.\n64', 'art.\n71', 'art.\n82', 'art.\n94', 'art.\n97']

Patent US7335205 - Implants, device and method for joining tissue parts - Google PatentsSearch Images Maps Play YouTube News Gmail Drive More »Sign inPatentsImplants (7) for forming a positive connection with human or animal parts include a material, such as thermoplastics and thixotropic materials, that can be liquefied by means of mechanical energy. The implants (7) are brought into contact with the tissue part, are subjected to the action of ultrasonic...http://www.google.com/patents/US7335205?utm_source=gb-gplus-sharePatent US7335205 - Implants, device and method for joining tissue partsAdvanced Patent SearchTry the new Google Patents, with machine-classified Google Scholar results, and Japanese and South Korean patents.Publication numberUS7335205 B2Publication typeGrantApplication numberUS 10/415,454PCT numberPCT/CH2002/000132Publication dateFeb 26, 2008Filing dateMar 4, 2002Priority dateMar 2, 2001Fee statusPaidAlso published asCA2439533A1, CA2439533C, CN1494398A, CN100337599C, DE50208067D1, EP1363543A1, EP1363543B1, US8114137, US8216286, US8221475, US8221477, US8323323, US8932337, US8945192, US9216083, US20040030341, US20070265622, US20070270974, US20080045961, US20080045962, US20080275500, US20130060265, US20130066384, US20150105862, US20160074083, WO2002069817A1Publication number10415454, 415454, PCT/2002/132, PCT/CH/2/000132, PCT/CH/2/00132, PCT/CH/2002/000132, PCT/CH/2002/00132, PCT/CH2/000132, PCT/CH2/00132, PCT/CH2000132, PCT/CH200132, PCT/CH2002/000132, PCT/CH2002/00132, PCT/CH2002000132, PCT/CH200200132, US 7335205 B2, US 7335205B2, US-B2-7335205, US7335205 B2, US7335205B2InventorsMarcel Aeschlimann, Laurent Torriani, Antonino Lanci, J�rg MayerOriginal AssigneeWoodwelding AgExport CitationBiBTeX, EndNote, RefManPatent Citations (106), Non-Patent Citations (15), Referenced by (155), Classifications (104), Legal Events (4) External Links: USPTO, USPTO Assignment, EspacenetImplants, device and method for joining tissue parts
US 7335205 B2Abstract
Implants (7) for forming a positive connection with human or animal parts include a material, such as thermoplastics and thixotropic materials, that can be liquefied by means of mechanical energy. The implants (7) are brought into contact with the tissue part, are subjected to the action of ultrasonic energy while being pressed against the tissue part. The liquefiable material liquefies and is pressed into openings or surface asperities of the tissue part so that, once solidified, the implant is positively joined thereto. The implantation involves the use of an implantation device that includes a generator (2), an oscillating element, and a resonator (6). The generator (2) causes the oscillating element to mechanically oscillate, and the element transmits the oscillations to the resonator (6). The resonator (6) is used to press the implant (7) against the tissue part to transmit oscillations to the implant (7).
Images(14) Claims(124)
providing an implant comprising a biocompatible material being liquefiable by mechanical oscillation,
positioning the implant on the tissue part in a manner such that an implant region of the liquefiable material is in contact or can be brought into contact with the tissue part,
impinging the positioned implant with mechanical oscillation and simultaneously pressing the implant against the tissue part for a time sufficient for liquefying at least a part of the liquefiable material and for pressing it into surface unevennesses, cavities or pores of the tissue part and
letting the liquefiable material pressed into said surface unevennesses, cavities or pores to re-solidify and, in a re-solidified state to constitute the positive-fit connection.
2. The method according to claim 1, wherein the mechanical oscillation for impinging the implant has a predominantly same direction as the pressing of the implant against the tissue.
3. The method according to claim 1, wherein the step of impinging and simultaneous pressing comprises contacting the implant with a transition element which is actively coupled to a resonator of an implantation device, wherein a distal end of the transition element oscillates predominantly perpendicularly to the direction in which the implant is pressed against the tissue part.
4. The method according to claim 1, wherein the step of impinging and simultaneous pressing comprises creating the surface unevennesses, cavities or pores in the tissue part by hydrostatic pressure.
5. The method according to claim 1, and further comprising a step of mechanically creating the surface unevennesses, cavities or pores in the tissue part.
6. The method according to claim 1, wherein the step of letting the liquefiable material to re-solidify comprises stopping the mechanical oscillation, while still pressing the implant against the tissue part.
7. The method according to claim 1, wherein the mechanical oscillation has a frequency of between 2 and 200 kHz.
8. The method according to claim 1, wherein the step of impinging and simultaneous pressing comprises contacting the implant with a resonator of an implantation device.
the implantation device comprises a generator, an oscillation element and a resonator, the generator being designed for exciting the oscillation element into mechanical oscillation, the resonator and the oscillation element being connected to form an oscillation unit, and a distal end of the resonator being adapted to a proximal face of the implant for transmission of the mechanical oscillations from the resonator to the implant and for pressing the implant against the tissue part.
10. The method according to claim 9, wherein the distal end of the resonator or a distal resonator part is equipped for predominantly oscillating in a longitudinal direction and to press the implant against the tissue part in the same direction.
11. The method according to claim 9, wherein the resonator comprises a transition element which is actively coupled to the resonator, wherein a distal end of the transition element is equipped for predominantly oscillating perpendicularly to a longitudinal direction and to press the implant against the tissue part in the longitudinal direction.
12. The method according to claim 9, wherein the implantation device is designed for mechanical oscillations of the resonator with a frequency between 2 and 200 kHz.
13. The method according to claim 9, wherein the implantation device is designed for a distal end of the resonator to oscillate with an amplitude of between 1 and 100 μm.
14. The method according to claim 9, wherein the oscillation element is a piezoelectric or magnetostrictive oscillator.
15. The method according to claim 9, wherein the implantation device is equipped for setting various frequencies of the mechanical oscillations, various frequency patterns and/or various energy pulsations and wherein the kit further comprises setting instructions for different ones of the implants.
16. The method according to claim 9, wherein the resonator of the implantation device comprises a proximal part and a distal part, the distal part being exchangeably fixed to the proximal part.
17. The method according to claim 1, wherein the step of positioning and the step of impinging and simultaneous pressing comprise minimal invasive surgery.
18. The method according to claim 1, wherein the step of impinging and simultaneous pressing further comprises dissipating heat through a cooling fluid or a heat conducting element.
19. The method according to claim 1, wherein the tissue part comprises living tissue.
20. The method according to claim 1, wherein the tissue part is a human or animal bone part, cartilage part, ligament part or tendon part.
21. The method according to claim 1, and further comprising a step of connecting another tissue part, a suture, a cerclage wire, means for supporting or replacing a tissue part, or a therapeutic auxiliary device to the implant.
22. The method according to claim 1, wherein the tissue part comprises cancellous bone tissue and the liquefiable material is pressed into pores of the cancellous bone tissue.
23. The method according to claim 22, wherein the cancellous bone tissue is osteoporotic bone tissue and is fortified by the liquefiable material pressed into the pores.
24. The method according to claim 1, wherein the implant further comprises a proximal face suitable for transmission of mechanical oscillation into the implant and for simultaneously pressing the implant against the tissue part and a contact surface to be brought into contact with the tissue part, wherein the liquefiable material is arranged to be liquefied by the mechanical oscillation on the contact surface or in a position from which it can be pressed onto the contact surface.
25. The method according to claim 24, wherein the liquefiable material has thermoplastic or thixotropic properties.
26. The method according to claim 1, wherein the liquefiable material is at least partly resorbable.
27. The method according to claim 1, wherein the liquefiable material further comprises foreign phases or substances having further functions.
28. The method according to claim 1, wherein the implant is designed to be suitable as an anchoring means for an artificial support or fixation element, for a prosthesis of a joint ball or socket, for an artificial tooth, bridge or tooth prosthesis, for a suture thread, for a cerclage wire or for a therapeutic auxiliary device.
29. The method according to claim 1, wherein the implant comprises a sleeve (13) of a non-liquefiable material wherein the liquefieable material is arranged in an inside of the sleeve wherein the sleeve comprises opening (58) for exit of the liquefied material and wherein in the step of impinging and simultaneously pressing, a distal end of a resonator is positioned against a proximal face of the liquefiable material.
30. The method according to claim 29, wherein the liquefiable material is resorbable and the sleeve (13) at least partly has a bioactive surface.
31. The method according to claim 29, wherein the implant is a screw and the step of positioning comprises screwing the implant into bone tissue.
32. The method according to claim 31, wherein the implant is a tension screw and is used together with a trochanter plate for fixing a fractured femoral neck bone.
33. The method according to claim 1, wherein the implant is shaped as a plate (35 and 36) or film (35).
34. The method according to claim 33, wherein the plate or film (35) is of one layer.
35. The method according to claim 33, wherein the plate (35 and 36) or film comprises a layer of the liquefiable material and a layer of a non-liquefiable material, and wherein the liquefiable material covers at least a part of one surface of the non-liquefiable material, and wherein the liquefiable material layer and the non-liquefiable material layer are connected to one another by positive fit or material fit.
36. The method according to claim 33, wherein the implant is positioned over a bone fracture or across a gap between two bone plates or between a bone plate and an artificial plate replacing a bone plate and wherein the step of impinging and simultaneously pressing is carried out on both sides of the fracture or gap.
37. A method for creating a positive-fit connection capable of load-bearing to a tissue part in a human or animal body, the method comprising the steps of:
providing a pin- or dowel-shaped implant comprising a proximal face, a contact surface to be brought into contact with the tissue part, and a first material being biocompatible, having thermoplastic properties, and being liquefiable by mechanical oscillation, the first material constituting at least part of the contact surface,
positioning the implant on the tissue part in a manner such that at least part of the contact surface is in contact with the tissue part,
impinging the proximal face of the positioned implant with mechanical oscillation and simultaneously pressing the implant against the tissue part for a time sufficient for liquefying at least part of the liquefiable material in contact with the tissue part and for pressing it into surface unevennesses, cavities or pores of the tissue part, and
letting the liquefiable material pressed into said surface unevennesses, cavities or pores to re-solidify and, in a re-solidified state, to constitute the positive-fit connection.
38. The method according to claim 37, wherein the mechanical oscillation for impinging the implant has a predominantly same direction as the pressing of the implant against the tissue part.
39. The method according to claim 37, wherein the step of impinging and simultaneous pressing comprises contacting the implant with a transition element which is actively coupled to a resonator of an implantation device, wherein a distal end of the transition element oscillates predominantly perpendicularly to the direction in which the implant is pressed against the tissue part.
40. The method according to claim 37, wherein the step of impinging and simultaneous pressing comprises creating the surface unevennesses, cavities or pores in the tissue part by hydrostatic pressure.
41. The method according to claim 37, and further comprising a step of mechanically creating the surface unevennesses, cavities or pores in the tissue part.
42. The method according to claim 37, wherein the step of letting the liquefiable material to re-solidify comprises stopping the mechanical oscillation, while still pressing the implant against the tissue part.
43. The method according to claim 37, wherein the mechanical oscillation has a frequency of between 2 and 200 kHz.
44. The method according to claim 37, wherein the step of impinging and simultaneous pressing comprises pressing with a force of 0.5 to 5 N per mm2 of implant cross section.
45. The method according to claim 37, wherein the step of positioning and simultaneous pressing comprises minimal invasive surgery.
46. The method according to claim 37, wherein the step of impinging and simultaneous pressing comprises dissipating heat from the implantation site through a cooling fluid or a heat conducting element.
47. The method according to claim 37, wherein the tissue part comprises living tissue.
48. The method according to claim 37, wherein said tissue part is a human or animal bone part, cartilage part, ligament part or tendon part.
49. The method according to claim 37, and further comprising a step of connecting another tissue part, a means for supporting or replacing a tissue part, a suture, a cerclage wire, or a therapeutic auxiliary device to the implant.
50. The method according to claim 37, and further comprising a step of providing an opening in the tissue part, wherein the step of positioning comprises positioning the implant in the tissue opening.
51. The method according to claim 50, wherein the step of providing an opening in the tissue part comprises drilling the opening.
52. The method according to claim 50, wherein the tissue part is a bone part with an outer layer of cortical bone and inner cancellous bone and wherein the step of providing an opening in the tissue part comprises opening the cortical layer only.
53. The method according to claim 50, wherein the tissue part is a bone part comprising an outer layer of cortical bone, wherein the step of providing an opening comprises opening the cortical layer and wherein surface unevennesses or a surface roughness are created on the walls of the opening in the cortical layer.
54. The method according to claim 53, wherein a thread is created in the walls of the opening in the cortical layer.
55. The method according to claim 50, wherein a cross section of the opening provided in the tissue part is sufficiently smaller than a corresponding cross section of the implant, for achieving a friction-fit between a wall of the opening and the implant.
56. The method according to claim 37, wherein the step of impinging and simultaneous pressing comprises driving the implant into the tissue part to form an opening therein.
57. The method according to claim 37, wherein the step of impinging and simultaneous pressing comprises guiding the implant with the aid of an implant guide.
58. The method according to claim 57, wherein the implant is guided in a tubular guide or with the aid of a guide wire.
59. The method according to claim 37, wherein, for the step of positioning and for the step of impinging and simultaneous pressing, a proximal implant end is fixed to a distal end of a resonator of an implantation device.
60. The method accordinci to claim 59, wherein:
the implantation device comprises a generator, an oscillation element and a resonator, the generator being designed for exciting the oscillation element into mechanical oscillation, the resonator and the oscillation element being connected to form an oscillation unit, and a distal resonator end being adapted to the proximal face of the implant for transmission of the mechanical oscillations from the resonator into the implant and for pressing the implant against the tissue part.
61. The method according to claim 60, wherein the oscillation element is a piezoelectric or magnetostrictive oscillator.
62. The method according to claim 60, wherein the oscillation unit is driven to oscillate with a frequency between 2 and 200 kHz.
63. The method according to claim 60, wherein the resonator comprises a proximal part and a distal part, the distal part being exchangeably fixed to the proximal part.
64. The method according to claim 60, wherein the generator and the oscillation unit are designed for a distal resonator end to oscillate with an amplitude of between 1 and 100 μm.
65. The method according to claim 60, wherein the implantation device further comprises a housing and an implant guide supported on the housing.
66. The method according to claim 65, wherein the implant is a dental implant.
67. The method according to claim 60, wherein the distal end of the of the resonator is equipped for oscillating in a longitudinal direction and to press the implant against the tissue part in the same longitudinal direction.
68. The method according to claim 60, wherein the resonator comprises a transition element which is actively coupled to the resonator, wherein a distal end of the transition element is equipped for predominantly oscillating perpendicularly to a longitudinal direction and to press the implant against the tissue part in the longidtudinal direction.
69. The method according to claim 60, wherein the implantation device is equipped for setting various frequencies of the mechanical oscillations, various frequency patterns and/or various energy pulsations and wherein the kit further comprises setting instructions for different ones of the implants.
70. The method according to claim 60, wherein the resonator comprises a proximal part and a distal part, the distal part being exchangeably fixed to the proximal part.
71. The method according to claim 60, wherein the resonator or a distal part thereof is adapted for minimal invasive surgery.
72. The method according to claim 60, wherein the resonator of the implantation device or a distal part thereof is exchangeable and sterilizeable.
73. The method according to claim 60, wherein a proximal send of the implant and a distal end of the resonator comprise cooperating holding means for the proximal implant end to be able to be held at the distal resonator end.
74. The method according to claim 73, wherein the cooperating holding means comprise elements of a snap-closure, materials suitable to be bonded together, a securing pin, or a threaded bolt.
75. The method according to claim 73, wherein the proximal end of the implant consists of the first material and wherein a distal face of the resonator carries at least one energy director.
76. The method according to claim 60, wherein a distal face of the resonator or of a distal resonator part corresponds in cross section to the proximal face of the implants.
77. The method according to claim 37, wherein, for the step of impinging and simultaneous pressing, a distal end of a resonator of an implantation device is positioned on the proximal face of the implant and acts like a hammer thereon.
78. The method according to claim 77, wherein the proximal face of the implant comprises a second material which is not liquefiable under implantation conditions.
79. The method according to claim 77, wherein the proximal face of the implant comprises the first material and a distal face of the resonator comprises at least one energy director and wherein the method comprises a step of deform ing the proximal face of the implant with the aid of the distal face of the resonator and mechanical oscillation.
80. The method according to claim 79, wherein the step of deforming is carried out before the step of positioning and further comprises bonding the deformed proximal face of the implant to the distal face of the resonator.
81. The method according to claim 77, wherein the implantation device comprises a generator, an oscillation element and a resonator, the generator being designed for exciting the oscillation element into mechanical oscillation, the resonator and the oscillation element being connected to form an oscillation unit, and a distal resonator end being adapted to the proximal face of the implant for transmission of the mechanical oscillations from the resonator into the implant and for pressing the implant against the tissue part.
82. The method according to claim 37, wherein the implant comprises a core of a second material which is not liquefiable under implantation conditions.
83. The method according to claim 82, wherein the core is removed after implantation.
84. The method according to claim 83, wherein the core is a guide wire.
85. The method according to claim 82, wherein the implant is a part of a prosthesis and the step of positioning comprises positioning said prothesis part in bone tissue.
86. The method according to claim 82, wherein the implant is a dental implant and the step of positioning comprises positioning the implant in an opening in a jaw bone.
87. The method according to claim 37, wherein the step of positioning comprises positioning the implant through a tendon or ligament onto bone tissue situated underneath the tendon or ligament or into an opening provided in the bone tissue underneath the tendon or ligament.
88. The method according to claim 37, wherein a further implant which has the shape of a plate is attached to the tissue part with the aid of the implant or with the aid of a plurality of the implants.
89. The method according to claim 88, wherein the plate is fixed to a proximal end of the implant or implants.
90. The method according to claim 88, wherein the plate is a fixation or stabilization plate.
91. The method according to claim 90, wherein the fixation or stabilization plate is positioned across a bone fracture or laceration.
92. The method according to claim 90, wherein the fixation or stabilization plate is positioned in a head region of a patient for repair or reconstruction purposes.
93. The method according to claim 90, wherein the fixation or stabilization plate is positioned across a gap between two calvaria parts or between a calvaria part and an artificial cover plate replacing a calvaria part.
94. The method according to claim 90, wherein the fixation or stabilization plate is positioned over at least two vertebral bodies.
95. The method according to claim 94, wherein the plate is elastically deformable.
96. The method according to claim 88, wherein the plate comprises at least one through opening and, in the step of positioning, the plate is positioned against the tissue part and the implant is positioned through the through opening in the plate onto the tissue part or into an opening provided in the tissue part.
97. The method according to claim 96, wherein the proximal implant end comprises a head having a larger cross section than a cross section of the through opening.
98. The method according to claim 96, wherein the plate consists of a second material, which is not liquefiable under implantation conditions, and the step of impinging and simultaneous pressing comprises pressing the first material into the through opening, which comprises a wall with unevennesses, cavities or pores.
99. The method according to claim 96, wherein the plate consists of a third material having thermoplastic properties and the step of impinging and simultaneous pressing comprises welding or adhering a region of the implant comprising the first material into the opening of the plate.
100. The method according to claim 96, wherein the step of impinging and simultaneous pressing comprises driving the implant into the bone tissue sufficiently for the proximal implant end to be flush with an outer surface of the plate.
101. The method according to claim 37, wherein the implant has a plurality of different cross sections between a distal and a proximal end thereof.
102. The method according to claim 101, comprising steps between different cross sections.
103. The method method according to claim 37, wherein the first material is a non-resorbable or a resorbable polymer.
104. The method according to claim 103, wherein the first material is a polyethylene (PE), a polymethyl metacrylate (PMME), a polycarbonate (PC), a polyamide, a polyester, a polyacrylate, a polymer based on lactic acid and/or glycolic acid, a polyhydroxyalkanoate (PHA), a polycaprolactone (PCL), a polysaccharide, a polydioxanone (PD), a polyanhydride or a corresponding copolymer.
105. The method according to claim 104, wherein the polymer based on lactic acid and/or glycolic acid is PLA, PLLA, PGA, or PLGA.
106. The method according to 37, wherein the first material further contains foreign phases or additional substances suitable for reinforcing, swelling or rendering porous the material, or for promotion of healing or regeneration, or for furthering x-ray visibility.
107. The method according to claim 106, wherein the additional substance is a growth factor, an antibiotic, an inflammation inhibitor or a buffer.
108. The method according to claim 106, wherein the foreign phases are fibers or whiskers.
109. The method according to claim 37, wherein implant surfaces of the first material are equipped with energy directors in the form of projecting pyramids, cones, hemispheres or ribs.
110. The method according to claim 37, wherein implant surfaces of the first material comprise axially extending ribs which constitute humps or corners of an implant cross section.
111. The method according to claim 37, wherein the distal implant end is pointed or tapers to a plurality of point-like or linear tip regions.
112. The method according to claim 37, wherein the first material constitutes the whole implant.
113. The method according to claim 37, wherein the implant comprises a core with a proximal end, a distal end and a circumferential surface between the proximal end and the distal end and consisting of a second material which is not liquefiable at implantation conditions, and wherein the first material is arranged on the distal end of the core and/or on the circumferential surface of the core.
114. The method according to claim 113, wherein the second material of the core is a metal, a ceramic material, a glass, a polymer or a composite material.
115. The method according to claim 113, wherein the second material comprises titanium, a cobalt-chrome alloy, polyetheraryl ketone, polyfluoro- and/or polychloroethylene, polyetherimide, polyethersulphone, polyvinylchloride, polyurethane, polysulphone, polyester, aluminium oxide, zirconium oxide, a silicate, a calcium phosphate ceramic or glass, or a carbon fiber reinforced high-temperature thermoplastic polymer.
116. The method according to claim 113, wherein the first material is resorbable and the core comprises a bioactive surface.
117. The method according to claim 113, wherein the core is a stem of a joint prosthesis.
118. The method according to claim 113, wherein the implant is a dental implant to be implanted in a jaw bone.
119. The method according to claim 37, wherein a proximal implant end comprises a head.
120. The method according to claim 37, wherein the implant is designed for replacing a further tissue part or for fastening a further tissue part, a therapeutic auxiliary device, a suture, a cerclage wire, an artificial support or fixation element, an artificial joint socket or ball, or an artificial tooth, bridge or tooth prosthesis.
121. The method according to claim 37, wherein, for being held by a distal end of a resonator, a proximal end of the implant is equipped with an inner thread, a resilient head or a through bore.
122. The method according to claim 37, wherein the connection to be created is a pointwise, depth-effective connection.
123. The method according to claim 37, wherein the connection to be created is a large-surfaced, superficial connection.
124. The method according to claim 123, wherein suitable tissue surface regions are roughened before positioning the implant (7).
The invention relates to implants for humans or animals. The implants at least partly create positive-fit connections to human or animal tissue parts, particularly skeletal parts, wherein the implants help connect tissue parts together, or help connect tissue parts to means supporting or replacing tissue parts, or to other therapeutic auxiliary devices. The invention further relates to devices and methods for implanting implants into humans or animals.
The objects are achieved by the implants, the device and the method of the present invention.
The invention is explained in more detail by way of the subsequent Figures, wherein:
Schematically, and in a very simplified manner, FIG. 1 shows an exemplary embodiment of an implantation device 1 applicable for implanting implants according to the invention.
The device 1 comprises a generator 2 and an oscillation unit 3 connected together via a cable 4. The oscillation unit 3, which is partly accommodated in a housing 5, is designed as a hand apparatus to be used like a hand drill, for example. The oscillation unit 3 comprises an oscillation element integrated in the housing 5 (not shown in detail) and actively connected to a resonator (sonotrode) 6. At least a distal resonator part projects out of the housing 5. The generator 2 supplies the oscillation element with energy. Excited by the oscillation element, the resonator oscillates at a predefined frequency or, as the case may be, with a predefined frequency pattern. Frequencies of 2 to 200 Hz and resonator amplitudes of 1 to 100 μm in the direction (z-direction) indicated by the double arrow are particularly suitable. The frequencies may be set depending on the application, the materials to be liquefied and the shape of resonator and implant. It is also conceivable to superimpose additional mechanical oscillations, such as with a lower frequency and larger amplitude on the vibrations in the ultrasound region. In many cases, it is sufficient to design the device for a single oscillation frequency, for example for 20 or 40 kHz and for a resonator amplitude of approximately 20 or 30 μm in the z-direction (direction in which an implant 7 is pressed by the resonator 6 against a tissue part). In order to control the power (supplied energy per unit of time), the excitation may be pulsed, wherein pulse distances and/or pulse lengths are set.
Implants according to the invention to be anchored in the tissue part in a depth-effective manner, as shown in FIGS. 2 to 4, are advantageously pin-like or dowel-like and comprise the liquefiable material for example at their distal end, as well as on further surface regions at which an anchoring is desirable (e.g. in a thread in plate 21 and cortical substance 2 of the bone). In fact, as shown in FIGS. 2 to 4, the implants may completely consist of the liquefiable material, wherein the distal end and the surface regions at which the material is to be liquefied in particular are advantageously provided with energy directors, or energy directors are provided at surfaces coming into contact with these regions. Such energy directors may be distal implant ends that are pointed or taper to one or more essentially point-like or linear tip regions. Further surface regions to be liquefied may include humps, tips or ribs whose height and widths are to be adapted to the anchoring being created. The energy directors project at least 10 μm beyond the surface. They may also be significantly larger and may be designed as axially-running ribs rendering the pin cross section humped or cornered, as is shown in an exemplary way by FIGS. 5 a to 5 e. Pin-like implants have such cross sections over their entire length, or only over a part of their length.
Implant cores as shown in FIGS. 6 and 7 may not only consist of metal (e.g. steels, titanium or cobalt-chrome alloys), but according to their application, may also consist of polymers (e.g. polyetheraryl ketone, polyfluoro—and/or polychloroethylene, polyetherimides, polyethersulphones, polyvinylchlorides, polyurethanes, polysulphones, polyester) or of ceramic or glass-like materials (e.g. aluminium oxide, zirconium oxide, silicates, calcium phosphate ceramics or glass) or of composite materials (e.g. carbon fibre reinforced high-temperature thermoplasts).
FIG. 16 shows a fixation foil 35 which may also have the form of a textile web and which may, for example, be applied for local fixation of the cover plate 30 in the opening of the scull 29. The foil 35 is, for example, tape-like and is advantageously flexible. It consists completely of a liquefiable thermoplast or is, for example, reinforced with a fiber mat, or with a similar structure. It is applied over the gap 33 and is excited on both sides (double arrows) with the help of an implantation device (FIG. 1) in a manner such that it adheres to the surface of the calvaria 29 and the surface of the cover plate 30 (larger-surfaced, less depth-effective connection which may be limited to a multitude or a pattern of individual fixation points). As the case may be, the surface regions, at which the implant is to be connected to the material lying therebelow, may be suitably pre-treated (e.g. roughened) or suitable surface structures (surface unevennesses, recesses, grooves etc.) are provided on the artificial plate 30. In order to conncet the film 35 to a bone surface, a pressure on the order of 0.5 to 3 N per mm2 of resonator end face is sufficient.
For the application shown in FIGS. 19 to 20, it is particularly advantageous to select a resorbable material as the liquefiable material, whilst the bearing part consists of a material that is neither liquefiable nor resorbable and that has a sufficient mechanical strength for the fastening of a tooth, bridge or prosthesis. At the same time, at least the surface of the central part is bioactive (e.g. porous as described for the sleeve 13), that is to say, equipped in a manner such that it promotes an intergrowth with bone tissue. Immediately after implantation, such an implant has a primary stability that is adequate for fastening the tooth, bridge or prosthesis and for normal use thereof. Promoted by the bioactive surface of the central imlant part, regenerated tissue then successively replaces the resorbable material and grows together with the central implant part. The implant according to the invention thus offers an immediate primary stability without the application of cement and, after a resorption and regeneration phase a permanent secondary stability, which is equal to the stability of known implants. In comparison to known implantation methods, however, there is no transition phase in which, according to the state of the art, the opening 41 is closed and one waits for regeneration of bone tissue before the tooth, the bridge or the prosthesis is fastened directly in the regenerated bone.
Pins of PLLA and polycarbonate manufactured by injection molding and having a round cross section of diameters between 3.5 and 4.25 mm, a length of 26 to 40 mm (ideal length at 20 kHz: 35 mm), obtusely tapered, distal ends and four grooves axially extending over 10 mm from the distal end were anchored with an excitation frequency of 20 kHz in cancellous bone (femur head) of freshly slaughtered cattle. For implantation, the thin cortical substance layer lying over the cancellous bone was opened, but the cancellous bone was not pre-drilled. On implantation, the implants were pressed against the tissue with pressures of 60 to 130 N and excited with the excitation frequency (sonotrode amplitude approx. 20 to 25 μm). The advance was limited to 10 mm which was achieved in less than 2 s. The implants were then held without excitation for 5 seconds.
The resulting anchorage depths were in the order of 15 mm and the anchorage on tearing out proved to be stronger than the implants themselves (maximum tear-out forces over 500 N). Sensors being placed at 1 mm from the pre-bore in the cortical bone substance (1.5 mm below the bone surface) recorded temperatures of max. 44� C. (approx. 22� above room temperature) approx. 10 s after implantation. The temperature rise was reduced to half its value in approximately 30 seconds.
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suture relative to hard tissueWO2012037700A1Sep 21, 2011Mar 29, 2012Sportwelding GmbhDevice and method for fixating a suture anchor in hard tissueWO2012040862A1Sep 6, 2011Apr 5, 2012Woodwelding AgMethod and implant for stabilizing two bone portions separated by a cut or fractureWO2012040863A1Sep 22, 2011Apr 5, 2012Spinewelding AgAnterior cervical plateWO2012100358A1Jan 26, 2012Aug 2, 2012Sportwelding GmbhDevice and method for fixating a suture anchor with a suture or a headed anchor in hard tissueWO2012100359A1Jan 26, 2012Aug 2, 2012Sportwelding GmbhMethod and device for floating a suture anchor with a suture in hard tissueWO2013010282A1Jul 10, 2012Jan 24, 2013Woodwelding AgMethod and implant for stabilizing separated bone portions relative to each otherWO2013185250A1Jun 12, 2013Dec 19, 2013Woodwelding AgAssembly for augmenting hard tissue* Cited by examinerClassifications U.S. Classification606/232, 606/331, 606/908, 606/329, 433/173, 606/284, 606/916, 606/70, 606/300, 606/74International ClassificationA61B17/84, B29C65/60, A61C8/00, A61B17/68, A61F2/46, A61L31/00, B29C65/00, A61B17/88, A61F2/00, B29C65/08, A61F2/30, A61F2/36, A61B17/00, A61B17/56, B29C65/54, A61F2/28, A61B17/80Cooperative ClassificationA61F2/28, A61B2017/8655, A61B17/866, A61B17/8625, A61B17/80, B29C66/73791, B29C66/9517, B29C66/9513, B29C66/7392, B29C66/7212, B29C66/71, B29C66/542, B29C66/5346, B29C66/5324, B29C66/30326, A61F2002/30062, A61B17/84, B29C66/81431, B29C65/48, B29C66/81433, B29C65/08, B29C66/8322, A61B17/688, A61F2/30749, A61F2/0077, A61F2002/3611, Y10S606/908, A61F2002/4602, A61F2002/465, A61F2002/4683, A61F2310/00023, A61F2/2875, A61F2/30767, A61B17/842, A61F2002/3625, B29C66/81429, A61F2/36, A61F2002/30064, A61B2017/00955, Y10S606/915, A61B17/8872, A61B17/8085, A61B17/00491, A61F2002/30067, B29C65/562, A61C8/0012, B29C66/81423, A61F2220/0008, A61F2/2846, A61F2/4601, A61B2017/00004, B29C65/601, A61C8/0016, A61B2017/00734, B29C65/54, A61B17/68, A61C8/0018, B29C66/727, A61F2210/0071, B29C65/603, A61F2002/30065, A61F2002/30878, A61F2/3662, B29C66/836, Y10S606/916European ClassificationB29C66/727, B29C65/60B, B29C65/08, B29C65/54, A61C8/00E3, B29C66/836, B29C65/56D, A61B17/68, A61B17/00L, A61F2/30L, A61C8/00F, A61B17/88PLegal EventsDateCodeEventDescriptionSep 15, 2003ASAssignmentOwner name: WOODWELDING AG, SWITZERLANDFree format text: ASSIGNMENT OF ASSIGNORS INTEREST;ASSIGNORS:AESCHLIMANN, MARCEL;TORRIANI, LAURENT;LANCI, ANTONINO;AND OTHERS;REEL/FRAME:014494/0340;SIGNING DATES FROM 20030514 TO 20030525Aug 19, 2008CCCertificate of correctionAug 19, 2011FPAYFee paymentYear of fee payment: 4Aug 11, 2015FPAYFee paymentYear of fee payment: 8RotateOriginal ImageGoogle Home - Sitemap - USPTO Bulk Downloads - Privacy Policy - Terms of Service - About Google Patents - Send FeedbackData provided by IFI CLAIMS Patent Services