Source: https://patents.google.com/patent/EP2401975B1/en
Timestamp: 2019-07-23 09:18:38
Document Index: 192061175

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EP2401975B1 - Device to be implanted in human or animal tissue and method for implanting and assembling the device - Google Patents
Device to be implanted in human or animal tissue and method for implanting and assembling the device Download PDF
EP2401975B1
EP2401975B1 EP11175622.7A EP11175622A EP2401975B1 EP 2401975 B1 EP2401975 B1 EP 2401975B1 EP 11175622 A EP11175622 A EP 11175622A EP 2401975 B1 EP2401975 B1 EP 2401975B1
EP11175622.7A
EP2401975A1 (en
2006-09-20 Priority to US82629606P priority Critical
2007-09-19 Priority to EP07800649A priority patent/EP2063793B1/en
2007-09-19 Priority to EP11000134.4A priority patent/EP2314239B1/en
2012-01-04 Publication of EP2401975A1 publication Critical patent/EP2401975A1/en
2016-05-25 Publication of EP2401975B1 publication Critical patent/EP2401975B1/en
The invention is in the field of medical technology and concerns a device to be implanted in human or animal tissue, i.e. an implant or endoprosthesis. The device comprises two or more than two device parts which are equipped for in situ assembly, i.e. to be joined during the implantation operation and in the implantation site. The invention further concerns a method for implanting and assembling the device in a human or animal patient, in particular implanting it in bone tissue of the patient.
According to the state of the art, implants or endoprostheses consist of metallic, ceramic or polymer materials. Some known implants or endoprotheses comprise a plurality of parts which are assembled either when being manufactured or immediately before implantation and before being positioned in the implantation site (ex situ assembly). The parts e.g. consist of different materials and form implant regions having different functions, as e.g. described in the publications WO 2004/017857 or WO 2005/079696 . The parts may also come in sets comprising a selection of part shapes or part sizes, wherein parts are chosen and assembled immediately before implantation (ex situ) to fit the individual implantation site (described e.g. in US-5593425 , Bonutti). Furthermore, it is known to fix a further part to the proximal end of an implanted implant or endoprosthesis (in situ assembly) which further part then protrudes from the tissue in which the implant or endoposthesis is implanted (e.g. crown mounted on a dental implant or ball mounted on the shaft of a hip joint prosthesis). It is further known to secure implants or endoprostheses which are implanted in the tissue by further implants (e.g. cross pins for securing the shaft of an endoprosthesis shaft). The known in situ assemblies are usually based on a bore in one of the parts and a corresponding bolt, cone or screw on the other part. Due to the named assembly means the freedom which these assemblies can offer regarding selectable relative positions for the assembled parts and therefore their applications are very limited. In the above mentioned publication US-5593425 it is suggested to assemble endoprosthesis parts, of which one comprises a thermoplastic material, by heating this thermoplastic material and therewith make its surface tacky and to bring the heated and therewith tacky surface in contact with a non-thermoplastic surface of an other endoprosthesis part in order to adhere it there. This method allows more freedom of relative placement of the endoprosthesis parts relative to each other, but the strength of the resulting connection is limited.
WO 02/069817 discloses an implant comprising liquefiable material which is anchored into bone tissue by a form fit connection between the liquefied material and the bone tissue upon liquefaction of the liquefied material, its interpenetration into the porous bone tissue and creation of a form fit connection upon resoliditication of the interpenetrated liquefied material.
It is the object of the invention to create a device to be implanted in a human or animal patient, the device being an implant or endoprosthesis and comprising at least two parts to be assembled in situ. It is a further object to create a method for implanting and assembling the device. The device and the method are to be more universally applicable than known multi-part implants or prostheses for in situ assembly and are to allow more flexibility regarding the relative position of the assembled parts relative to each other, but still resulting in a strong connection between the implant or prosthesis parts.
This object is achieve by the device according to the invention as claimed.
The device according to the invention comprises two (or more than two) parts which parts are equipped for being assembled, i.e. joined together, using mechanical oscillation, in particular ultrasonic vibration, which is applied to one of the parts by contacting this part with a mechanically vibrating tool. The device parts usually consist of an artificial material but some of the parts may also consist of bone tissue. Each one of the two parts of the device comprises a joining location, the two joining locations being matched to each other for being in contact with each other when the parts are positioned to be joined and for being connected to each other after the joining process, wherein the resulting joint is a positive fit connection.
For achieving a positive fit connection, a first one of each matched pair of joining locations comprises a material having thermoplastic properties and being liquefiable by mechanical vibration, which material forms the surface of the joining location or can be pressed to this surface from the inside of the part by application of the mechanical vibration. A second one of each pair of matched joining locations comprises a material which is not liquefiable by the mechanical vibration to be used for joining the two device parts (e.g. metal, ceramic material or polymer with duroplastic properties or with thermoplastic properties but with a melting temperature which is relevantly higher than the melting temperature of the liquefiable material) and it further comprises a structure being suitable for a positive fit connection with the material of the first joining location when this material is liquefied, made to penetrate into the structure and to re-solidify within this structure. The structure of the second joining location comprises an undercut cavity or protrusion or a plurality of undercut cavities or protrusions, wherein one or a relatively small number of cavities (e.g. bores or grooves) or protrusions having a defined form and a size of preferably a few mm is provided and/or a large number of cavities and protrusions having random forms, i.e. being formed by e.g. an open-porous surface material or a surface coating consisting of assembled particles (e.g. sintered material). For enabling penetration of the surface structures by the liquefied material of the first joining location and for realizing a stable joint, the cavities of the porous or particulate surface material need to have a size of at least about 0.3 mm and the surface structure needs to have a depth which is at least twice as large as the fineness of the structure (pore size of the porous material, particle size of the particulate coating).
At least one of the device parts to be joined together further comprises a contact location in which it is able to be contacted with a vibrating tool (e.g. sonotrode of an ultrasonic device) for the joining process. The part comprising the contact location may comprise the first or the second joining location.
At least the device part comprising the contact location and preferably both device parts are designed as mechanically stable oscillators such that mechanical vibration applied to the contact location is transmitted by the oscillator to the joining location with as little damping loss as possible and in particular without reduction of the mechanical stability of the oscillator during the application such that it becomes possible to liquefy enough (but not more) material in the region of the joining locations for achieving the desired positive fit connection but without further changing form or material of the device part. For achieving good oscillator properties the device parts are made of materials having an elasticity module of at least about 0.5 GPa for low damping losses. The surface of either joining location is preferably equipped with protruding energy directors (protruding pyramids, cones, combs etc. having a height of at least 10 µm) which, on application of the vibration, locally concentrate the vibrational energy such causing high local shearing stresses and therefore local and fast liquefaction of the surface material even if the melting point of this material is as high as 200 to 450°C. By such local liquefaction, the amount of material which is liquefied can be kept small (e.g. just enough for penetrating the structure of the second joining location) and therefore the thermal loading of the tissue remains within physiologic limits (allowing for functional regeneration of the tissue) even when macroscopic cavities of the second joining location need to be filled with the liquefied material.
Depending on the form of the two joining locations, the liquefied material may allow adjustments of the relative position of the two device parts during the joining process, which makes it possible to in situ adapt the relative position of the two device parts to the implant site. Larger such in situ adaptation is made possible, if at least one of the joining locations is designed such that it allows joining of the two parts in a selected one of a plurality of different possible relative positions.
According to some aspects of the invention, at least one part of the device or both parts of the device are positioned and possibly fixed in the tissue, the two parts are positioned relative to each other such that their joining locations are in contact with each other and then the mechanical vibration is applied to either one of the parts for joining the two parts by liquefying the liquefiable material of the first joining location, by making it to penetrate into the cavity or cavities or between and under the protrusion or protrusions of the second joining location and letting it re-solidify there. The mechanical vibration used for joining the device parts has e.g. a frequency of 2 to 200 kHz and is preferably ultrasonic vibration.
For fixing the device parts to the tissue per se known methods, such as e.g. screwing, clamping, pinning, cementing, suturing or press-fitting are applicable. According to preferred embodiments of the method, the application of mechanical vibration is used not only for joining the two device parts together but also for fixing one or both of the device parts in the tissue by anchoring it in the tissue (in particular in bone tissue) with the aid of a liquefiable material. The two applications of mechanical vibration may be carried out simultaneously and using the same contact location and the same vibrating tool and/or in succession and using different contact locations and the same tool or different tools.
Devices to be anchored in tissue, in particular in bone tissue, with the aid of a liquefiable material and mechanical vibration and methods for implanting such devices are described in the publications WO 2002/069817 , WO 2004/017857 or WO 2005/079696 .
Experiments show that successful anchorage effected simultaneously with the joining is easily effected for the device part to which the vibration is applied, and anchorage effected before the joining is easier conserved when the subsequent vibration for the joining process is not applied to the anchored device part. These findings are due to the fact that transmission of the vibration through the joining locations being in contact with each other is hardly possible as the liquefiable material being present where the two joining locations are in contact is liquefied substantially immediately on application of the vibration such that hardly any vibrational energy can be transmitted through the joining locations. This means that beyond the joining locations hardly any liquefaction by mechanical vibration occurs and therefore neither anchorage in tissue with the aid of liquefiable material and mechanical vibration nor damaging such anchorage can be effected.
In the present text the term "liquefiable material" is used for a material comprised by the device which material can be liquefied by mechanical vibration, e.g. by ultrasonic vibration. If the liquefiable material is to take over load-bearing functions and/or if only a very limited amount thereof at predetermined locations is to be liquefied, the liquefiable material is a material in which the mechanical vibration causes no internal stress strong enough for plastifying or liquefying the material but on whose surface such liquefaction can be effected by contact with a non-vibrating element, wherein such contact is limited to points or lines (energy directors). Such materials are materials having thermoplastic properties and an elasticity module of at least 0.5 GPa. If the liquefiable material is not to have a load-bearing function and/or if more of the material is to be liquefied by the mechanical vibration, the liquefiable material may be a material as above described but may also be a material with thermoplastic properties and with a smaller elasticity module.
In the present text the term "non-liquefiable material" is used for an additional material comprised by the device. In the non-liquefiable material mechanical vibration, e.g. ultrasonic vibration, as used for liquefaction of the liquefiable material, causes no internal stress which is strong enough for liquefying the material nor is such vibration able to liquefy the non-liquefiable material in surface areas being in contact with a non-vibrating element even if such contact is limited to single points or lines (energy directors).
From the above follows that the properties of the non-liquefiable material of a specific device depend on the properties of the liquefiable material of the same device. Generally speaking: the less vibrational energy is used for liquefaction of enough of the liquefiable material, the easier liquefiable the non-liquefiable material may be. Therefore a thermoplastic material with a high melting temperature (e.g. PEEK) is suitable to be used as non-liquefiable material if the liquefiable material is e.g. PLLA. On the other hand the same thermoplastiv material (e.g. PEEK) is suitable as liquefiable material if the non-liquefiable material is e.g. titanium or a ceramic material.
In the present text the term "mechanically stable oscillator" is used for a body which is able to be vibrated by e.g. ultrasonic vibration without being internally affected by the vibration. A mechanically stable oscillator comprises no form element which is deformed by the vibration, it comprises no material with a high damping loss (e.g. elasticity module considerably less than 0.5 GPa) and, if it comprises more than one part, the parts are joined such that vibration passes through the joint substantially without loss or reflection.
In the present text the terms "bone tissue" or "bone" are used to encompass not only viable bone tissue but also bone replacement material.
According to the invention a plurality of device parts is pre-assembled such that the device parts are movable relative to each other in a limited way. Selected ones of the device parts may be equipped for being anchored in bone tissue with the aid of a liquefiable material and mechanical vibration. The device parts are brought to the implantation site in a pre-assembled configuration or are pre-assembled in the implantation site. In the pre-assembly specific ones of the device parts are still moveable relative to each other in a limited manner. The pre-assembled device parts are positioned relative to each other in a site-specific arrangement by moving the specific device parts relative to each other. The device parts are then locked in this site-specific configuration by being joined to each other with the aid of mechanical vibration. For this joining, adjacent and relative to each other moveable device parts are equipped with second joining locations which face each other and the device comprises in addition a locking part comprising the liquefiable material and being designed to be introduced between the second joining locations facing each other in the pre-assembly of the device parts. For effecting the lock, the liquefiable material of the locking part representing two opposite first joining locations is forced between the second joining locations of the pre-assembled device parts. Anchorage of the correspondingly equipped device parts takes place simultaneously with the joining or in a preliminary step. There may not be any anchorage of device parts in the bone tissue.
Suitable liquefiable materials for joining the parts of the device according to the invention are not biologically resorbable, whereas liquefiable materials for anchoring a part of the device in bone tissue may either be resorbable or non-resorbable.
Suitable non-resorbable liquefiable materials for first joining locations and possibly also for the anchorage of a device part are e.g.: polyolefines (e.g. polyethylene), polyacrylates, polymethacrylates, polycarbonates, polyamides, polyesters, polyurethanes, polysulfones, liquid-crystal-polymers (LCPs), polyacetals, halogenated polymers, in particular halogenated polyolefines, polyphenylene sulphones, polysulfones, Polyaryletherketones (E.g. polyetheretherketone PEEK, available under the trade name Victrex 450G or Peek Optima from Invibo) polyethers, or corresponding copolymers and mixed polymers or composites containing said polymers and fillers or reinforcing agents such as e.g. fibers, whiskers, nanoplatelets, or nanotubes. Particularly suitable are polyamide 11 or polyamide 12.
Suitable resorbable liquefiable materials for anchorage of a device part in bone tissue are e.g.: thermoplastic polymers based on lactic and/or gluconic acid (PLA, PLLA, PGA, PLGA etc) or polyhydroxy alkaneates (PHA), polycaprolactones (PCL), polysaccharides, polydioxanones (PD), polyanhydrides, polypeptides, trimethylcarbonates (TMC), or corresponding copolymers, or mixed polymers, or composites containing said polymers. Particularly suitable as resorbable liquefiable materials are: poly-LDL-lactide (e.g. available from Böhringer under the trade name Resomer LR708) or poly-DL-lactide (e.g. available from Böhringer under the trade name Resomer R208), as well as corresponding copolymers and mixed polymers or composites containing said polymers and fillers or reinforcing agents such as e.g. fibers, whiskers, nanoplatelets, or nanotubes.
The device according to the invention serves the same purposes as known implants and endoprostheses. The device serves in particular for fixing one viable tissue part to another viable tissue part, wherein the device according to the invention constitutes a fixing element, in particular a load bearing fixing element between the two tissue parts. The device may also serve for fixing an artificial element replacing a natural tissue part or an auxiliary element (e.g. auxiliary support part), wherein the device according to the invention constitutes the replacement part or auxiliary part as well as the fixing means.
The advantage of the device according to the invention is the ease of the in situ assembly, the robustness of the assembly, the character of the assembly which makes it non-reversible under physiologic conditions and the easy and little limited in situ adaptability of the assembly.
For carrying out the method a vibration device is used, e.g. an ultrasonic device comprising an ultrasonic transducer, a booster and a sonotrode or a sonotrode (vibrating tool) and an acoustic coupling piece (vibrating tool), wherein the sonotrode or the coupling piece is advantageously exchangeable. Preferably a set is provided which set comprises, in addition to device parts, vibrating tools with distal ends adapted to the contact locations of the device parts and proximal ends adapted to a fixation point of the vibration device or sonotrode respectively. The sets may further comprise printed or otherwise recorded instructions regarding implantation parameters such as e.g. vibration frequencies and application times suitable for the joining and possibly anchoring processes for implantation and assembly of the device parts of the set.
Exemplary embodiments of the method and the device are described in further detail in connection with the following Figures, wherein:
Figs. 1 to 7 illustrate structures of second joining locations and joints achieved by joining matched pairs of joining locations;
illustrates a first group of embodiments of the invention, wherein a pre-assembled plurality of device parts is arranged in a site-specific configuration and the device parts are then joined to each other with a further device part (pin part);
Figs. 9 to 15
show a second group of embodiments of the invention, wherein the device comprises, in addition to the plurality of pre-assembled or pre-assemblable device parts, a locking part for locking the pre-assembled device parts in the site-specific configuration;
Figures 1 to 7 illustrate exemplary embodiments of matched pairs of first and second joining locations suitable for the devices according to the invention and connections between such joining locations. The first joining location F comprises a liquefiable material and possibly energy directors E, the second joining location S comprises an undercut structure of a non-liquefiable material and possibly energy directors E. For joining the two matched joining locations, these are pressed against each other and mechanical vibration is coupled into one of the parts comprising either the first or second joining location from a side opposite the joining location. Pressure and vibration cause the liquefiable material in the region of the energy directors to liquefy and to penetrate in a liquid state into the structure of the second joining location and, on re-solidification, to form therewith a positive fit connection.
The main feature of joining two device parts comprising a matched pair of first and second joining locations using mechanical vibration is the fact that the liquefiable material of the first joining location is liquefied and penetrates in a liquid state into the structure of the second joining location which is usually undercut in the direction of the liquid flow. The resulting positive fit structures of the liquefiable material are characterized by forms which are dependent on the surface tension of the liquid state. The liquefiable material of these structures may adhere to the material of the second joining location but there is no necessity that it does.
Figures 1 to 3 show as a first example of a second joining location S a foam structure e.g. consisting of a metal, e.g. titanium. Fig. 1 shows the foam structure before being penetrated by the liquefiable material, Fig. 3 shows a pin of the liquefiable material being anchored in the foam structure and Fig. 2 shows in a larger scale the interpenetration of the foam structure by the liquefiable material after re-solidification, i.e. the positive fit connection between the two. This positive fit connection which is visible in Figs 2 and 3 comprises in this first example structure elements of a size in the region of about 1mm or less. A first joining location matched to the joining location as shown in Figs. 1 to 3 comprises a liquefiable material, is adapted to the outer surface of the foam material (e.g. even) and is large enough to cover a plurality of the structure elements. The structure elements of the foam structure are able to act as a plurality of energy directors such that the first joining location does not need to be equipped with energy directors. However, the first joining location may also be constituted by a more or less pointed distal end of a pin-shaped device part, which pointed end acts as energy director.
Figure 4 shows in a cascade of three scales a second example of the second joining location and a positive fit connection between this second joining location and a first joining location. The illustrated second joining location is constituted by the surface of a hip joint prosthesis by S+G Implants GmbH, Lübeck, Germany. The surface structure of such implants consists of a metal (preferably titanium or a titanium alloy) and is e.g. produced by sintering a particulate material or by lost form molding. The structure elements have an average size from about 1 mm to about 2 mm. A first joining location matched to the second joining location according to Fig. 4 comprises a liquefiable material and is adapted to cover a plurality of the structure elements as discussed for the joining elements according to Figs 1 to 3. If the structure elements of the second joining location are more rounded than edgy, it is advantageous to equip the matched first joining location with energy directors.
Similar structures as shown in Fig. 4 being suitable for second joining locations may be made of trabecular metal by Zimmer, or of wire mesh as known from implants by Johnson & Johnson. Implants by Eska also have suitable surfaces.
Figure 5 illustrates second joining locations S comprising a more or less regular pattern of undercut openings (e.g. bores or grooves), which are manufactured or molded. In the second joining location S on the left, the mouths of the undercut openings protrude slightly from the overall surface and therewith are capable of acting as energy directors. A matched first joining location F may be completely even. The structure of the second joining location S on the left of Fig. 5 does not comprise energy directors and therefore energy directors E are advantageously provided on the first joining location. The second joining location structures according to Fig. 5 advantageously have a size of about I to several mm and the first joining location covers a plurality thereof.
Figure 6 shows a matched pair of joining locations F and S similar to the joining locations according to Fig. 5 wherein the second joining location structure comprises undercut protrusions (e.g. heads or combs with a narrower neck region) instead of openings. These protrusions, if equipped with more or less sharp edges or points act as energy directors also.
Figure 7 shows a last example of a matched pair of joining locations, wherein the structure of the second joining location S, which is again an undercut opening, is larger than the first joining location F. The first joining location is situated at a distal end of a pin-shaped part, which pin-shaped part is introduced into the opening, when the parts to be joined are pressed against each other. The distal end of the pin is e.g. pointed for being capable of acting as energy director and the pin comprises enough of the liquefiable material for filling the undercut opening constituting the second joining location.
Figures 8 shows an exemplary embodiment of the invention. The three-part devices comprise a plate 20, applicable in osteo-synthesis e.g. for stabilizing a bone fracture, and an insert 92 comprising a through bore and being mounted in a through opening of the plate 20 to be capable to be oriented in different directions relative to the plate. The device further comprises a pin part 93 adapted in cross section to the opening in the insert 92. For implantation the plate 20 is positioned relative to a bone surface, the bone surface is provided with openings for the pin part by introducing a drill through the insert opening thereby orienting the insert 92 in a site-specific way and then introducing the pin part 93 through the opening in the insert 92 into the opening in the bone surface and applying pressure and vibration to its proximal face to firstly anchor the pin part 93 in the bone tissue and to secondly join the insert 92 to the plate 20 to fix it in the site-specific orientation.
The bowl-shaped opening reaching through the plate 20 (bearing part) and the insert 92 (movable part) formed as a half sphere comprise second joining locations each and the pin part 93 comprises a head region 94 (locking part consisting of a liquefiable material which material on pressing the pin part 93 into the openings is pushed between plate 20 and insert 92 to constitute first joining locations on either side and to fix the insert 92 relative to the plate 20.
Figures 9 to 15 illustrate further embodiments of the invention, in which the device, apart from the pre-assembly of device parts or the plurality of device parts designed for being pre-assembled, comprises at least one additional device part (locking part 100) which comprises a liquefiable material and is designed for being introduced between second joining locations facing each other in the pre-assembly of device parts. The site-specific configuration of the pre-assembled device parts is fixed by forcing the liquefiable material of the locking part (100) between the second joining locations of the pre-assembled device parts, wherein this material constitutes two opposite first joining locations matched to the second joining locations of the pre-assembled device parts.
The movement of the pre-assembled device parts relative to each other, which movement is to be blocked by the locking part 100 is in particular a rotation and/or an axial displacement of a rod or bar (moveable part 101) in a bearing opening in a bearing part 102 or formed by a plurality of bearing parts 102. Therein the bearing part 102 and/or the moveable part 102 comprise second joining locations facing each other when the movable part 101 is positioned in the bearing of the bearing part 102. The locking part 100 comprises the liquefiable material at a distal end. It is introduced through the bearing part 102 to contact the moveable part 101 and on application of pressure and mechanical vibration to its proximal face, the liquefiable material of its distal end is liquefied and pressed between the bearing part 102 and the moveable part 101 constituting on two opposite sides a first joining location matched to the two second joining location. On re-solidification the liquefiable material locks the moveable part 101 relative to the bearing part or parts 102.
Figures 9 and 11 show the principle of the above referred locking of a rotation and/or axial displacement of a rod (moveable part 101). The Figures are sections through bearing parts 102 and movable part 101 in a direction perpendicular to the rotation axis. Both bearing and movable part comprise in the sense of second joining locations depressions (as e.g. illustrated in Figs. 1-3, 4, 5 or 6). The space between bearing part 102 and moveable part 101 is accessible for the locking part 100, e.g. by the bearing part 102 comprising a corresponding opening leading from its outer surface to its bearing surface.
Figure 9 shows two bearing parts 102 being connected in any suitable manner to close the bearing surface around the moveable part 101. For locking the moveable part 101 in a desired rotation and axial position relative to the bearing parts, the locking part 100 is introduced into the opening of the bearing part (left hand side of Fig. 9) and, by applying a vibrating tool to its proximal face, the locking part is vibrated and pressed against the surface of the movable part for the liquefiable material to be liquefied in the region of the distal end of the locking part and to be pressed between bearing parts and moveable part and into the structures serving as second joining locations (depressions). On re-solidification of the liquefiable material, rotation and/or axial displacement of the movable part 101 are prevented by the positive fit connection between the movable part 101 and the bearing parts 102 which positive fit connection is realized on opposite sides of the correspondingly shaped liquefiable material of the locking part (locked configuration: right hand side of Fig. 9).
Depending on the surface structures serving as second joining locations, the movable part 101 is locked regarding rotary and/or axial loads. Experiments using a bearing opening of 5.9 mm inner diameter and a rod 5.8 mm diameter being locked using a PLDLLA pin show good locking characteristics against axial displacement with annular grooves and against rotation with axial grooves. Good locking is achieved in both directions if the surface structure on the movable part 101 and the bearing parts 102 comprise a pattern of depressions or a combination of axial grooves or blind bores and ring-shaped grooves.
The locking principle as detailed above is achievable for axial loads only in the same manner for movable parts with other then round cross sections.
Figure 10 shows a further embodiment of the locking according to the invention, which locking in this case is reversible, if the connection between the bearing parts (e.g. threaded bolts in threaded bores 103) is reversible and if the liquefiable material of the locking part 100 does not wet the bearing surfaces and therefore does not adhere to these on re-solidification. For achieving reversibility of the locking, the structures of the second joining locations do not constitute undercuts in the direction, in which the bearing parts are to be separated from each other or constitute only small undercuts in this direction. Such structures are e.g. axial extending grooves whose cross section extends parallel to the bolts and bores 103 into the bearing surfaces of the bearing parts (as shown in Fig. 10) and relatively small structures (e.g. surface roughness) on the movable part 101. Obviously circular grooves as mentioned above are suitable for a reversible locking as illustrated in Fig. 10.
For loosening the connection between bearing parts 102 and movable part 101, the bolts 103 are loosened and the liquefiable material is removed to release the moveable part 101.
Figures 11 to 15 show exemplary applications of the locking principle according to the invention.
Figures 11 and 12 show a rod lock application for fixing a rod (moveable part 101) to neighboring vertebral bodies 51 in order to support the vertebral column and maintain desired distances between the vertebral bodies. The rod locking device is substantially the device according to Fig. 10, wherein the non removable bearing part is equipped with a protrusion 105 which is e.g. equipped for the locking device to be anchored in a corresponding bore provided in the vertebral body. Fig. 11 shows the locking device closed around the rod in a larger scale and Fig. 12 shows the locking device mounted to a vertebral body.
Figure 13 shows an external fixation device for stabilizing the fragments of a tubular bone 45 on both sides of a bone fracture 65. The device comprises supports 110 anchored with suitable means in the bone fragments and a rod 111 which connects the supports 111 to form together with them the exterior device. Between supports 110 and rod 111 double locking devices 112 are provided. A first bearing part 102.1 bears the support 110 and defines the axial and rotary position of the locking device relative to the support. A second bearing part 102.2 bears the rod 111 and defines the axial and rotary position of the rod relative to the support. A third bearing part 102.3 bears an axel of the first bearing part 102.1 and defines an angle between the support and the rod. The whole external fixation device is pre-assembled in situ. When all parts are assembled their relative positions and orientations are locked by introducing locking parts at all locations indicated with an arrow.
Figure 14 shows a further application of a device which is similar to the device shown in Fig. 13 and serves for stabilizing a vertebral column and maintaining defined distanced between vertebral bodies 51. The supports in this case are pedicle screws.
Figure 15 shows in more detail a strikingly simple embodiment of a locking device according to the invention. The device comprises a locking part 100, which preferably consists of the liquefiable material or is coated therewith, and which is anchored in bone tissue 11 with the aid of mechanical vibration. The locking part 100 comprises a shoulder on which a vibrating tool for its anchorage is applied and a protruding section of a smaller cross section. The bearing part 102 which is preferably made of a non-liquefiable material comprises an inner bearing surface and an opening leading to this bearing surface which opening is adapted to the protruding section of the locking part 100. The outer surface of the bearing part 102 around the opening is equipped for constituting a second joining location 6 (e.g. as illustrated in Fig. 6. The bearing part 102 is preliminarily positioned on the protruding section of the locking part 100 and the movable part 101 is introduced in the bearing part 102. The site-specific rotary and/or axial position of the movable part is established and then the bearing part is pushed towards the bone surface and simultaneously vibrated, whereby the protruding section of the locking part 100 is pushed against the moveable part 101, its liquefiable material is liquefied and penetrates between the moveable part 101 and the bearing part 102 to lock these two on re-solidification. At the same time, the end of the bearing part 102 which faces the bone surface is pressed into the shoulder of the locking part 100 and is joined to the latter in the sense of a further pair of matched first and second joining locations.
Instead of or in addition to the above described joining of the bearing part 102 to the locking part 100 via the shoulder of the locking part, it is possible also to equip the inside of the bearing part opening for the protruding section of the locking part 100 as second joining location and effect there a joint between the two parts.
It is obvious for one skilled in the art to combine features of the above described and illustrated embodiments of the invention in different ways and therewith to create further embodiments which are still encompassed by the invention.
A device to be implanted and assembled in a patient, the device comprising:
at least one locking part (100) comprising in a distal region a liquefiable material capable of being liquefied by mechanical vibration, and
a pre-assembly of a plurality of device parts in which pre-assembly the device parts are connected to each other but pairs of selected ones of the device parts are still moveable relative to each other,
or providing a plurality of device parts equipped for such pre-assembly,
wherein of pairs of device parts being moveable relative to each other in the pre-assembly each device part comprises a second joining location (S) comprising a non-liquefiable material and a structure which is suitable to form a positive fit connection with the liquefiable material of the locking part (100), the two second joining locations (S) being arranged on the device parts of the pair to face each other and a space between the two second joining locations (S) being accessible for the locking part (100), the device to be assembled and implanted using a method.
providing the at least one locking part (100),
providing the pre-assembly or providing the plurality of device parts equipped for such pre-assembly, the space between the two second joining locations (S) being accessible for the locking part (100) to be brought in contact with one of the pair of device parts,
positioning the pre-assembly in an implantation site or pre-assemble the device parts in the implantation site to form the pre-assembly,
bringing the pre-assembly into a site-specific configuration by moving the selected ones of the device parts relative to each other, and
bringing the distal end of the locking part (100) into the space between the two second joining locations (S)
pressing the distal end of the locking art (100) against one of the pair of device parts and applying mechanical vibration to the locking part or one of the device parts for a time sufficient for liquefying enough of liquefiable material and press it between the two second joining locations (S) to lock the site-specific configuration of the two device parts.
Device according to claim 1, wherein in the pair of device parts moveable against each other and comprising the two second joining locations (S) one is a plate (20) comprising a bowl-shaped through opening and the other one is an insert (92) comprising a through opening and being mounted in the bowl-shaped through opening of the plate and wherein the locking part is constituted by a head region (94) of a pin part (93) which is adapted to the through opening of the insert (92).
Device according to claim 1, wherein in the pair of device parts moveable against each other and comprising the two second joining locations (S) one is a bearing part (102) or an assembly of bearing parts (102) and the other one is a moveable part (101) extending through the bearing part (102) or bearing part assembly and being axially displaceable and/or rotatable relative to the bearing part or bearing part assembly, wherein the bearing part or bearing part assembly comprises an opening extending from an outer surface thereof to a bearing surface thereof and wherein the locking part (100) is pin-shaped and adapted for being introduced through the opening in the bearing part or bearing part assembly.
Device according to claim 3, wherein the bearing parts (102) of the bearing-part assembly are connected to each other in a reversible manner.
Device according to any one of claims 3 or 4, wherein one of the bearing parts comprises a protrusion (105) equipped for being anchored in bone tissue with the aid of a further liquefiable material and mechanical vibration.
Device according to claim 5 and being a rod clamp to be anchored in a vertebral body (51).
Device according to any one of claims 3 or 4 and being an external fixation device comprising a plurality of supports (110), a rod (111) and a plurality of double bearing parts (112).
Device according to claim 2, wherein a distal end of the pin part (93) is equipped for being anchored in bone tissue with the aid of a further liquefiable material.
Device according to any one of claims 3 or 4, wherein the locking part (100) is equipped for being anchored in bone tissue with the aid of a further liquefiable material and mechanical vibration and wherein one end of the locking part (100) protruding from the bone tissue when the locking part (100) is anchored in bone tissue constitutes the distal end to be positioned in the space between the two second joining locations (S).
Device according to claim 3, wherein the locking part (100) is equipped to be first anchored in the bone tissue such that the distal end thereof protrudes from the bone tissue and wherein the bearing part (102) or bearing part assembly is shaped to be positioned on the protruding distal end of the locking part (100) and pressed against it and vibrated.
EP11175622.7A 2006-09-20 2007-09-19 Device to be implanted in human or animal tissue and method for implanting and assembling the device Active EP2401975B1 (en)
US82629606P true 2006-09-20 2006-09-20
EP07800649A EP2063793B1 (en) 2006-09-20 2007-09-19 Device to be implanted in human or animal tissue
EP11000134.4A EP2314239B1 (en) 2006-09-20 2007-09-19 Device to be implanted in human or animal tissue
EP07800649A Division EP2063793B1 (en) 2006-09-20 2007-09-19 Device to be implanted in human or animal tissue
EP11000134.4A Division EP2314239B1 (en) 2006-09-20 2007-09-19 Device to be implanted in human or animal tissue
EP11000134.4A Division-Into EP2314239B1 (en) 2006-09-20 2007-09-19 Device to be implanted in human or animal tissue
EP07800649.1 Division 2007-09-19
EP11000134.4 Division 2011-01-11
EP2401975A1 EP2401975A1 (en) 2012-01-04
EP2401975B1 true EP2401975B1 (en) 2016-05-25
ID=39200866
EP11175622.7A Active EP2401975B1 (en) 2006-09-20 2007-09-19 Device to be implanted in human or animal tissue and method for implanting and assembling the device
EP11000134.4A Active EP2314239B1 (en) 2006-09-20 2007-09-19 Device to be implanted in human or animal tissue
EP07800649A Active EP2063793B1 (en) 2006-09-20 2007-09-19 Device to be implanted in human or animal tissue
EP11175620.1A Active EP2389883B1 (en) 2006-09-20 2007-09-19 Device to be implanted in human or animal tissue and method for implanting and assembling the device
EP16155742.6A Pending EP3045127A1 (en) 2006-09-20 2007-09-19 Device to be implanted in human or animal tissue and method for implanting and assembling the device
US (4) US9724206B2 (en)
EP (5) EP2401975B1 (en)
JP (5) JP5268113B2 (en)
AT (1) AT505144T (en)
DE (1) DE602007013917D1 (en)
ES (3) ES2364681T3 (en)
PL (2) PL2314239T3 (en)
WO (1) WO2008034276A2 (en)
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2007-09-19 EP EP11175622.7A patent/EP2401975B1/en active Active
2007-09-19 DE DE602007013917T patent/DE602007013917D1/en active Active
2007-09-19 JP JP2009528571A patent/JP5268113B2/en active Active
2007-09-19 ES ES07800649T patent/ES2364681T3/en active Active
2007-09-19 PL PL11000134.4T patent/PL2314239T3/en unknown
2007-09-19 EP EP11000134.4A patent/EP2314239B1/en active Active
2007-09-19 EP EP07800649A patent/EP2063793B1/en active Active
2007-09-19 EP EP11175620.1A patent/EP2389883B1/en active Active
2007-09-19 US US12/442,328 patent/US9724206B2/en active Active
2007-09-19 WO PCT/CH2007/000458 patent/WO2008034276A2/en active Application Filing
2007-09-19 EP EP16155742.6A patent/EP3045127A1/en active Pending
2007-09-19 PL PL11175620T patent/PL2389883T3/en unknown
2007-09-19 ES ES11175620.1T patent/ES2607224T3/en active Active
2007-09-19 AT AT07800649T patent/AT505144T/en not_active IP Right Cessation
2007-09-19 ES ES11000134.4T patent/ES2574664T3/en active Active
2013-04-26 JP JP2013093462A patent/JP5737791B2/en active Active
2013-04-26 JP JP2013093467A patent/JP5853339B2/en active Active
2013-04-26 JP JP2013093472A patent/JP5840645B2/en active Active
2015-11-11 US US14/938,290 patent/US9782268B2/en active Active
2015-11-19 JP JP2015226388A patent/JP2016055184A/en active Pending
2016-01-22 US US15/004,181 patent/US20160135961A1/en not_active Abandoned
2017-06-07 US US15/616,177 patent/US20170266018A1/en active Pending
US20100023057A1 (en) 2010-01-28
EP2063793B1 (en) 2011-04-13
JP2013172996A (en) 2013-09-05
EP3045127A1 (en) 2016-07-20
JP5840645B2 (en) 2016-01-06
PL2389883T3 (en) 2017-03-31
US9724206B2 (en) 2017-08-08
US9782268B2 (en) 2017-10-10
WO2008034276A3 (en) 2008-10-30
EP2389883B1 (en) 2016-09-14
JP5853339B2 (en) 2016-02-09
JP2016055184A (en) 2016-04-21
JP2010504118A (en) 2010-02-12
ES2574664T3 (en) 2016-06-21
US20160058579A1 (en) 2016-03-03
ES2607224T3 (en) 2017-03-29
JP2013172998A (en) 2013-09-05
EP2389883A1 (en) 2011-11-30
JP2013172997A (en) 2013-09-05
DE602007013917D1 (en) 2011-05-26
US20160135961A1 (en) 2016-05-19
EP2401975A1 (en) 2012-01-04
JP5268113B2 (en) 2013-08-21
JP5737791B2 (en) 2015-06-17
WO2008034276A2 (en) 2008-03-27
US20170266018A1 (en) 2017-09-21
EP2314239B1 (en) 2016-03-30
ES2364681T3 (en) 2011-09-12
EP2314239A1 (en) 2011-04-27
EP2063793A2 (en) 2009-06-03
AT505144T (en) 2011-04-15
PL2314239T3 (en) 2016-09-30
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CN105034360B (en) 2018-06-05 Integrated multi-material and a manufacturing method implant
CN104887360B (en) 2018-04-10 Apparatus and method for stabilizing the spine and implant kit
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