Source: https://patents.google.com/patent/ES2582460T3/en
Timestamp: 2020-01-26 11:02:33
Document Index: 106759019

Matched Legal Cases: ['art 122', 'arts 124', 'art 122', 'arts 22', 'arts 124', 'art 124', 'art 126', 'arts 24', 'arts 124', 'art.\n9', 'art.\n10']

ES2582460T3 - Surgical stabilization plate - Google Patents
Surgical stabilization plate Download PDF
ES2582460T3
ES2582460T3 ES11767889.6T ES11767889T ES2582460T3 ES 2582460 T3 ES2582460 T3 ES 2582460T3 ES 11767889 T ES11767889 T ES 11767889T ES 2582460 T3 ES2582460 T3 ES 2582460T3
ES11767889.6T
2010-09-30 Priority to US38824310P priority Critical
2010-09-30 Priority to US388243P priority
2010-10-19 Priority to US394580P priority
2011-09-22 Application filed by SPINEWELDING AG filed Critical SPINEWELDING AG
2011-09-22 Priority to PCT/CH2011/000224 priority patent/WO2012040863A1/en
2016-09-13 Publication of ES2582460T3 publication Critical patent/ES2582460T3/en
A surgical stabilization plate (121), comprising a plate part (122) for stabilizing a human or animal spine being placed ventrally relative to the spine and being fixed to two or more different vertebral bodies, and further comprising a plurality of fastening parts (124) adapted to be anchored in the different vertebral bodies, at least one of the fastening parts (124) being rigidly connected to the plate part (122) and comprising a sheath element with a longitudinal opening which is accessible from a proximal side and at least one hole (14) extending from the longitudinal opening to the outside, the stabilization plate (121) comprising a thermoplastic element (21) inserted or insertable in the element further comprising of cover and capable of being liquefied by energy acting on the thermoplastic element (21), in which the hole (14) is positioned so that the ma Liquid thermoplastic terial can be pressed through the hole (14) to the bone tissue of the vertebral body in which the holding part (124) has to be anchored, in which at least one holding part (124) comprises a structure of stabilization capable of absorbing mechanical loads on the stabilization plate (121), in which the plate part (122) is not flat, and in which the stabilization plate (121) comprises at least four fastening parts (124).
Surgical stabilization plate Field of the invention
The invention is in the field of medical technology. In particular, it refers to an anterior cervical plate and an anterior cervical plate system.
If screws have been anchored in living bone tissue, the problem of insufficient bone stability or insufficient bone anchor stability often arises. Especially in the trabecular bone tissue, any load acting on the screw is passed only on a few trabeculae, with adverse consequences both for the ability to withstand load of the screw-bone connection, and for its long-term stability. This is especially severe in osteoporotic or osteopenic bone tissue or otherwise weakened.
A solution to this problem is the use of an alternative anchoring method that is also suitable for fabric in which the screws are not stable. Publications WO 02/069817, WO 2004/017 857, WO 2008/034 277, and WO 2009/055 952 refer to the anchoring of an implant in bone tissue with the help of mechanical vibration and a thermoplastic material that is liquefiable by vibration mechanics, that is, the thermoplastic material is capable of being liquefied when it is vibrated and kept simultaneously in contact with a non-vibrating surface. The thermoplastic material, where it is in contact with the bone tissue, is liquefied and pressed into pores or cavities of the bone tissue to constitute, when it solidifies again, a positive fixation connection with the bone tissue.
A special group of implant embodiments and implant anchoring processes is based on the liquefiable material that is inserted (pre-assembled or inserted in situ) into a longitudinal opening of a sheath element. The sheath element comprises at least one hole in the sheath element wall, through which the liquefied material is pressed from the longitudinal opening to the structures (pores or cavities or other structures) of the bone tissue or other hard tissue or hard tissue replacement material in which anchoring is desired. This principle of pressing liquefied material out of a tube or sleeve element with side openings is described for example in US 7,335,205, US 6,921,264, WO 2009/055 952, WO 2009/010247, WO 2009/010234, and WO 2009/132 472. Other publications refer to the safety of an intercorporeal separator such as WO 2010/096342 or WO 2010/010522 or US 6,558,423.
The present invention relates to a surgical stabilization plate as claimed below. Preferred embodiments of the invention are described in the dependent claims.
The invention relates to a surgical stabilization plate. Such a plate comprises a plate part that is not flat and a plurality of fastening parts, at least one of one of the fastening parts (and for example all of them) being connected neatly to the plate part and comprising a sheath element with a longitudinal opening that is accessible from a proximal side and at least one hole extending from the longitudinal opening to the outside. The stabilization plate also comprises a thermoplastic element inserted or inserted in the sheath element and capable of being liquefied by means of, for example, mechanical energy acting on the thermoplastic element.
In a group of embodiments, at least one hole is a radial hole. The radial hole / holes may be provided at a different location from the distal end of the respective fastening part, but the fastening parts may distally from the radial hole or holes comprise a stabilization part.
An axial extension of the stabilization part can be substantial; it can be for example at least two thirds of a distance between the plate part and the radial holes, or equal to or greater than the distance between the plate part and the radial holes. The stabilization part may have a non-circular cross section. The distance between the plate part and the radial hole is adjusted for example so that the liquid material pressed out through the radial hole to a surrounding bone tissue after a new solidification provides a subcortical anchor of the ACP.
An example of such a stabilization plate is an anterior cervical plate (ACP), in which the plaque part is capable of stabilizing a human or animal spine being placed anteriorly (ventrally) with respect to the spine and being fixed to two or more different vertebral bodies. The fastening parts are thus intended to be anchored in different vertebral bodies.
In accordance with one aspect of the invention, an anterior cervical plate (ACP) is provided, the ACP comprising a plaque portion that is not flat to stabilize a human or animal spine being placed ventrally with respect to the spine and being fixed to two or more different vertebral bodies, and further comprising a plurality of fastening parts adapted to be anchored in the different vertebral bodies. At least one
of the fastening parts is neatly connected to the plate part and comprises a sheath element with a longitudinal opening that is accessible from a proximal side and at least one hole extending from the longitudinal opening to the outside. The anterior cervical plate also comprises a thermoplastic element inserted or inserted into the sheath element by means of a sheath element and capable of being liquefied, for example, by a mechanical energy acting on the thermoplastic element, in which the hole is positioned so that the Liquefied thermoplastic material can be pressed through the hole to the bone tissue of the vertebral body in which the fastener has to be anchored, in which at least one part of the support comprises a stabilization structure capable of absorbing mechanical loads on the Anterior Cervical Plate .
After, for example, a mechanical energy, especially vibration, ceases to affect the thermoplastic element, the liquefied material pressed to the bone tissue solidifies again and thus provides an anchor for the holding part and thus for the ACP.
In a group of embodiments, at least one hole - or at least one of the holes - is a radial hole.
The stabilizing effect of the stabilization structure is an effect in addition to the anchoring effect of the thermoplastic material. To this end, the clamping parts according to a first option comprise structural features that deviate from a purely rational cylinder. For example, the clamping parts may have a greater extension in the transverse direction than in the upper / lower direction. Also as an alternative to the first option, the fastening parts according to a second option may comprise a stabilization part distally of the hole because the radial hole / holes are not provided at the distal end of the respective fastening part. The stabilization part may have a non-circular cross-section and may for example have a greater extension in the lateral (or transverse) direction than in the upper-lower (cranial-caudal) direction.
The radial holes may be positioned to ensure a subcortical anchor. Generally, a more subcortical anchor can be obtained, for example, if a distance between an outer surface of the bone tissue and the proximal limb of an opening through which the anchoring material from the elongated cavity comes out is for example between 2 mm and 7 mm, especially between 3.5 mm and 5.5 mm (these amounts are what keep people from growing). Consequently, a distance between a distal end face of the part plate and the proximal start of the opening can be chosen to be the same order, that is, between 2 mm and 7 mm, especially between 3.5 mm and 5.5 mm
A length (proximal-distal extension) of the opening or openings through which the anchoring material leaves can be between 1 mm and 6 mm, especially between 2.5 mm and 5 mm. Experiments with sub-cortical anchorage (in bone tissue of the vertebral body) have shown that for a plurality (for example four) of holes equally distributed in the circumferential dimension, a ring of anchoring material of a proximal-distal extension corresponding to the chord extension of the openings and of a 10 mm diameter that surrounds a tubular element of 4 mm in diameter.
In embodiments related to spinal stabilization devices that have an intervertebral separator and in relation to a lateral extension of the vertebral body, a subcortical anchorage can be achieved if the depth at which the anchoring material exits is between approximately 5% and 20% of the extension of the vertebral body.
In addition to the fastener parts with a longitudinal opening, the stabilization plate may comprise conventional fasteners.
In a special embodiment, the stabilization plate (for example ACP) comprises four fastening parts of the type described above that are neatly connected to the plate part and comprising a longitudinal opening and at least one hole (for example two, three or four radial openings in approximately equal axial positions) from the longitudinal opening to the outside. If the stabilization plate is an ACP, the clamping parts are then positioned to be propelled to the vertebral bodies of two adjacent vertebrae - two in each.
In another special embodiment, the stabilizer plate comprises four, five or six fastening parts of the type described above that are neatly connected to the plate part and that comprise a longitudinal opening and at least one hole (for example two, three or four openings radial in approximately equal axial positions) from the longitudinal opening to the outside. The ACP in this embodiment reaches three contiguous vertebrae, and the holding parts are then positioned to be propelled to the vertebral bodies of at least the highest and the lowest of the three vertebrae, and possible to the vertebral bodies of the entire of the three vertebrae.
Instruments for implanting the stabilization plate may comprise a template that defines the positions of the notches to be made in the body tissue in positions corresponding to the positions of the fastening parts. According to a first option, the notches can be made previously, in which the template serves to guide the drill that makes the animations. According to a second option, only the cortical bone is previously removed or drilled (or otherwise prepared) in the locations where the holding parts have to penetrate the bone tissue, for example by means of a drill or other instrument guided by Template. According to another option even, the holding parts, which then have a sharp point, can themselves be used to penetrate the cortical bone and advance to the tissue; the template (if any) can be used to directly guide the plate
stabilization during implantation (by hammering).
The fastening parts, if they comprise a plurality of radial holes through which the liquid thermoplastic material can be pressed, can be configured to comprise an angularly structured steering structure with respect to a longitudinal axis of the longitudinal opening to direct different parts of the liquefiable material to different ones of the radial holes. Such address structures may be of the type written in WO 2011/054122.
In embodiments with a plurality of radial holes, these radial holes through which the thermoplastic material flows out during implantation, may be in the same axial position, or may be in different axial positions. The angular positions may be evenly distributed around the circumference. In special embodiments, the angular positions may have a deviation distribution adapted to a particular need. For example, if the implant is intended to be an implant to melt joint parts, and to be inserted into an articulation space, the holes (if there are more than two) may be concentrated on opposite sides to be in contact with the areas of articulation.
The complete shape of the plate part can be thinned in the central part in which the thinning in the central part is formed between the vertebral bodies, and in which the fasteners are located in the corners. In this "thinned in the central part" means that a transverse extension of the plate part in a central region (for example between the vertebrae in which the ACP is anchored) is less than a transverse extension in the upper / lower extremity it is for example less than a transverse distance between the axes of the clamping parts. This may imply that the clamping parts are located in the ACP places that have the greatest distance from the sagittal plane. This serves the purpose of providing a minimum in side plate extension together with a maximum capacity to prevent / absorb lateral bending and twisting.
In a special embodiment, the anterior cervical plate comprises a part of a thinned plate in the central part with exactly four holding parts, one holding part in each corner. In this, the fastening parts are of the type described above and of a piece with the plate part. The anterior cervical plate can also comprise a thermoplastic element - initially separated - by a clamping part, the shape of the thermoplastic element adapted for this purpose must be introduced into the longitudinal opening of the respective clamping part. The plate part may be curved towards the dorsal side at the corners that carry the clamping parts.
The plate part does not need to be flat, nor does it have to have another particular shape, such as for example a translation symmetry. Instead, it is a particular advantage of the construction of a single (integral) part of the plate part with the fastening parts that the plate part can be shaped according to the needs of the user. For example, it can be shaped to absorb mechanical loads in a desired manner. The mechanical reinforcing elements can have, for example, the shape of projections, edges, etc. In addition or as an alternative, the plaque part may be shaped to be adapted to the geometry and dimensions of the bone and have a minimum depth away from the vertebral bodies. As a particular example, the anterior cervical plaque may be curved in the dorsal direction in proximity to the sagittal plane to minimize irritation of the esophagus or sensitive soft tissue structures.
According to another aspect, the invention thus relates to an anterior cervical plate comprising a part of plaque that is not flat to stabilize a human or animal spine being placed ventrally with respect to the spine and being fixed to two or more different vertebral bodies, and also comprising a plurality of fastening parts adapted to be anchored in the different vertebral bodies, the fastening parts being neatly connected to the plate part and comprising a sheath element with a longitudinal opening that is accessible from a proximal side and at least one hole extending from the longitudinal opening to the outside, in which the hole is positioned so that the liquid thermoplastic material can be pressed through the hole to the bone tissue of the vertebral body in which the fastener has if anchored, in which one or both of the following conditions is satisfied.
- the plate part is not flat (it is uneven),
- the outer contour of the clamping parts does not have a rotational cylindrical symmetry.
The feature that the outer contour of "the clamping parts" does not have a rotational cylindrical symmetry in this context implies that the shape of the clamping parts is different from rotationally cylindrical in addition to the holes (for example radial). Especially, the fastening parts may have a non-circular outer contour and / or may have at least one groove or the like.
In particular, at least a plurality of the holes may be radial holes, and the fastening parts may comprise a stabilization part distally of the radial holes, the stabilization part having a greater extension in the transverse direction than in the upper direction. lower. The plate part may be thinned in the central zone according to the definition provided above. The fastening parts can be carried by the edges of the plate part, and the edge parts can optionally be curved to the dorsal side. The plate part may comprise edges or reinforcement projections.
Also in accordance with the other aspect, the anterior cervical plate may also comprise a thermoplastic element inserted or inserted into the sheath element per sleeve element and capable of being liquefied, for example, by means of mechanics acting on the thermoplastic element.
In other embodiments, the stabilizer plate instead of being an ACP may be a fracture stabilization plate or post-osteotoirna. Osteotoirna is a surgical procedure in which an anima is cut for the purpose of being shortened, lengthened or realigned. The osteotoirna is performed on human and animal patients mainly to realign the load bearing surfaces in joints and to realign bone parts in particular in the maxillofacial region but also to realign cured bone parts together with an alignment. relatively unwanted between each other after a fracture. The bone parts separated by the osteotoirna procedure need for the most part to be re-aligned in a desired position relative to each other and to be stabilized in this position to be able to heal together again. According to the state of the art, the osteotoirna zones are usually stabilized with the aid of plates (for example metal plates) that are positioned on the bone surface through the osteotoirna cut and are held in this position with the help of screws or bone nails. Simple bone fractures are stabilized in the same way.
Especially, the stabilizer plate can be used to stabilize fractures or bone cuts near human or animal joints, where conventional plates are sometimes not easy to hold because the anchoring of conventional surgical screws is weak. For example, if the plate is to extend from a part of bone in a joint to a part of our remote part of the joint, the plate anchors that are closest to the joint may be holding parts of the type described above, while that conventional surgical fastening screws may be used to anchor remote bone parts of the joint. Alternatively, all the fastening parts can be of the type described above with longitudinal opening and thermoplastic material elements.
Also, generally the stabilizer plate is advantageous in situations where there is little soft tissue to cover the plate (as a consequence, conventional metal surgical screws tend to cause irritation).
A special application of a stabilizer plate is the stabilization after the osteotoirna of the tibial plateau, especially for human, canine or feline patients.
The mechanical vibration or oscillation suitable for devices and methods according to the embodiments of the invention which includes liquefying a friction heat polymer created through mechanical vibration preferably has a frequency of between 2 and 200 kHz (even more preferably between 10 and 100 kHz, or between 20 and 40 kHz) and a vibration energy of 0.2 to 20 W per square millimeter of active surface. The vibrating element (sonotrode) is for example designed in such a way that its contact face oscillates predominantly in the direction of the axis of the element (longitudinal vibration) and with an amplitude of between 1 and 100 pm, preferably about 10 to 30 pm A rotational or radial oscillation is also possible.
For embodiments of specific devices, it is also possible to use, instead of mechanical vibration, a rotational movement to create the so-called frictional heat necessary for the liquefaction of the anchoring material. Such rotational movement preferably has a speed of the order of 10,000 to 100,000 rpm. Another way of producing the thermal energy for the desired liquefaction comprises coupling electromagnetic radiation to one of the parts of the device to be implanted and designing one of the parts of the device so that it is capable of absorbing electromagnetic radiation, in which such absorption it preferably takes place within the anchoring material to be liquefied or in the immediate vicinity thereof. Electromagnetic radiation is preferably used from the frequency range of the visible or infrared spectrum, in which the preferred radiation source is a corresponding laser. Electric heating of one of the parts of the device may also be possible.
In this text the expression "liquefiable thermoplastic material for example by mechanical vibration" or briefly "thermoplastic material that can be liquefied" or "liquefiable material" is used to describe a material comprising at least one thermoplastic component, the material of which is liquid or flowing when it is heated, in particular when it is heated by friction, that is to say when it is arranged on one of a pair of surfaces (contact faces) that are in contact with each other and moved vibratory or rotationally relative to each other, in which the frequency of the vibration is between 2 kHz and 200 kHz, preferably from 20 to 40 kHz and the amplitude between 1pm and 100 pm, preferably from about 10 to 30 pm. Such vibrations are for example produced by ultrasonic devices such as those known for dental applications. To be able to constitute a connection that supports the tissue load, the material at the time of insertion has an elasticity coefficient of more than 0.5 GPa, preferably more than 1 GPa. The elasticity coefficient of at least 0.5 GPA also ensures that the liquefiable material is capable of transmitting the ultrasonic oscillation with a damping so small that the internal liquefaction and thus the destabilization of the liquefiable element does not occur, that is, the liquefaction occurs only when the liquefiable material is in the liquefaction interface to the stop face. The plasticizing temperature is preferably up to 200 ° C, between 200 ° C and 300 ° C or even more than 300 ° C. Depending on the application, the liquefiable thermoplastic material may or may not be resorbable.
Suitable resorbable polymers are for example based on lactic acid and / or glycolic acid (PLA, PLLA, PGA, PLGA, etc.) or polyhydroxyalkanoates (PHA), polycaprolactones (PCL), polysaccharides, polydioxanones (PD), polyanhydrides,
Corresponding polypeptides or copolymers or mixed polymers or composite materials containing the aforementioned polymers are suitable as resorbable liquefiable materials. Thermoplastics such as, for example, polyolefins, polyacrylates, polymethacrylates, polycarbonates, polyamides, polyesters, polyurethanes, polysulfones, polyaryl ketones, polyimides, polyphenyl sulphides, or polymers of Kqido crystal polymers (LCPS), polyacetals, halogenated polyogenated polymers, halogenated, polyogenated halogenated, polyogenated halogenated, halogenated polymers , polysulfones, polyethers, polypropylene (PP), or corresponding copolymers or mixed polymers or composite materials containing the polymers mentioned as components are suitable as non-absorbable polymers. Examples of suitable thermoplastic material include any of the polylactic products LR708 (amorphous lactic Poly-L-DL 70/30), L209 or L210S by Bohringer Ingelheim.
Specific embodiments of degradable materials are Polylactic such as LR706 PLDLLA 70/30, R208 PLDLA 50/50, L210S, and PLLA 100% L, all from Bohringer. A list of suitable degradable polymeric materials can also be found in Erich Wintermantel und Suk-Won Haa, "Medizinaltechnik mit biokompatiblen Materialien und Verfahren", 3, Auflage, Springer, Berlin 2002 (hereinafter referred to as "Wintermantel"), page 200; for information on PGA and PLA see pages 202 ff, on PCL see page 207, in PHB / PHV copolymers page 206; in polydioxanone PDS page 209. Description of other bio-absorbable material can be found for example in CA Bailey et al., J Hand Surg (Br) April 2006; 31 (2): 208-12.
Specific embodiments of non-degradable materials are: Polyetherketone (PEEK Optima, Grades 450 and 150, Invibio Ltd), Polyetherimide, Polyamide 12, Polyamide 11, Polyamide 6, Polyamide 66, Polycarbonate, Polymethylmethacrylate, Polyoxymethylene, or Polycarbonate methane (in particular Bionate® (in particular Bionateate®) DSM, especially Bionate 75D and Bionate 65D, information according to them is available in the publicly accessible data sheets for example through
www.matweb.com by Automation Creations, Inc.). A summary table of polymers and applications is collected on page 150 of Wintermantel, specific examples can be found on page 161 ff. from Wintermantel (PE, Hostalen Gur 812, Hochst AG), pages 164 ff. (PET) 169 ff. (PA, in particular PA6 and PA 66), 171 ff. (PTFE), 173 ff. (PMMA), 180 (PUR, see table), 186 ff. (PEEK), 189 ff. (PSU), 191 ff. (POM - Polyacetal, registered trademarks Delrin, Tenac, have also been used in endoprotesis by Protec).
The liquefiable material that has thermoplastic properties may contain extraneous phases or compounds that serve other functions. In particular, the thermoplastic material can be reinforced by mixed fillers or fillers, for example particulate fillers that can have a therapeutic or other desired effect. The thermoplastic material may also contain components that expand or dissolve (create pores) in situ (for example polyesters, polysaccharides, hydrogels, sodium phosphates) or compounds that are to be released in situ and that have a therapeutic effect, for example promotion of healing and regeneration (for example growth factors, antibiotics, inflammation inhibitors or buffers such as sodium phosphate or calcium carbonate against adverse effects of acid decomposition). If the thermoplastic material is resorbable, the release of such compounds is delayed.
If the liquefiable material is to be liquefied not with the help of vibratory energy but with the help of electromagnetic radiation, it may contain locally compounds (in particles or molecular) that are capable of absorbing such radiation from a specific frequency range (in particular the range of frequency of the visible or infrared spectrum), for example calcium phosphates, calcium carbonates, sodium phosphates, titanium oxide, mica, saturated fatty acids, polysaccharides, glucose or mixtures thereof.
Loads used may include bone-stimulant, degradable fillers that are to be used in degradable polymers, including: p-Calcium triphosphate (TCP), Hydroxyapatite (HA, of crystallinity <90%; or mixtures of TCP, HA, DHCP, Bio - glass (see Wintermantel) Charges that stimulate bone integration that are only partially or hardly degradable, for non-degradable polymers include: Bio-glasses, Hydroxyapatite (crystallinity> 90%), HAPEX®, see SM Rea et al., Mater Sci Mater Med. September 2004; 15 (9): 997-1005; for hydroxyapatite see also L. Fang et al., Biomaterials July 2006; 27 (20); 3701-7, M Huang et al., J Mater Sci Mater Med July 2003; 14 (7): 655-60, and W. Bonfield and E. Tanner, Materials World January 1997; 5 n ° 1: 18-20. Bioactive load realizations and their description can be found for example in X. Huang and X. Miao, J Biomater App. April 2007; 21 (4): 351-74), JA Juhasz et al., Biomaterials, March 2004; 25 (6): 949-55. Types of particulate charges include; rough type: 5-20 pm (contents preferably 10-25% by volume), less than micron (nano-charges as from precipitation, aspect ratio preferably in the form of a plate> 10, 10-50 nm, content 0.5 to 5% by volume).
A specific example of a material with which experiments were performed was PLDLA 70/30 comprising 30% (weight percent) of biphasic Ca phosphate which showed a particularly advantageous liquefaction behavior.
The ACP material can be any material that does not melt at the melting temperatures of the liquefiable material. Especially, the sheath element may be metal, for example a titanium alloy. A preferred material is grade 5 titanium. This material, in addition to being generally suitable for devices to be implanted, has a relatively low caloric conduction. Due to this poor conduction, the melting zone that appears in the liquefiable material is heated quickly, without the surroundings being heated to too high temperatures. Alternative materials for ACP are other metals such as other titanium alloys, stainless steel, or hard plastics such as PEEK etc.
Next, ways of carrying out the invention and embodiments with reference to the drawings have been described. The drawings are mostly schematic. In the drawings, the same reference numbers refer to the same elements or to analog elements. The drawings show:
Fig. 1 an embodiment of an anterior cervical plaque (ACP);
Fig. 2 a variant of the embodiment of fig. 1, partially in section;
Fig. 3, schematically, the use of an embodiment of an anterior cervical plate;
Fig. 4 a schematic cross section of an anterior cervical plate with an esophagus;
Figs. 5a-5d an embodiment of an anterior cervical plate with reinforcement projections.
Fig. 6 an asymmetric anterior cervical plate in use;
Figs. 7a and 7b the distal and proximal limb, respectively, of an alternative holding part;
Figs. 8 and 9 regions of the distal end of other variants of fastening parts; Y
Fig. 10 an alternative embodiment of an anterior cervical plaque, which is not in accordance with the claimed invention. Description of preferred embodiments
In figs. 1 and 2 an anterior cervical plate (ACP) 121 is depicted 121. The ACP has a plate portion 122 to stabilize a human (or animal) spine being placed anteriorly (ventrally) with respect to the spine and being fixed to two (or more) different vertebral bodies. The plaque part may have a shape of a type known in the art that can be adapted to the particular needs of the patient. For example, in contrast to the embodiment shown, the plate portion may comprise holes formed in accordance with biomechanical considerations to provide some elasticity for certain movements while providing a desired stiffness against other movements.
In the embodiment of fig. 1, the plate part has two holes 123 with an internal thread that can be used to hold the plate during the surgical operation, while the variant of fig. 2 has two holes 123 without any thread. Apart from this difference, the embodiments of figs. 1 and 2 can be identical.
ACP can be used to stabilize a human spine section with or without an intercorporeal fusion implant between two vertebral bodies. Especially, ACP can be used in connection with an intercorporeal fusion implant as described in WO 20101096942.
The thermoplastic elements 21 may initially be separated from the holding parts. In the embodiment shown, they have the shape of a rotational cylinder, but other shapes are possible - adapted to the shape of the longitudinal opening.
In fig. 1, the longitudinal axis 11 (which after the operation, is intended to be parallel to the longitudinal axis (cranial - caudal, superior - inferior) of the vertebrae and thus to the sagittal plane) and the transverse axis 12 (which afterwards are also represented) of the implantation must be parallel to the lateral axis (left-right / lateral middle) of the patient's body) of the ACP. In the present text, generally the "longitudinal", "transverse / lateral", "dorsal" and "central" directions refer to the axes and directions when the ACP is placed in the body in the intended manner.
In addition to the plate part 122, the ACP has a plurality (four in the embodiment shown) of fastening parts 124. Each fastening part is neatly connected to the plate part 122 and for example is of a piece with it (integral ). Each fastening part is in the form of a sheath element (tubular element) with a longitudinal opening that is accessible from the proximal side and at least one radial hole 14 (two holes in the configuration shown) through which, after liquefaction, especially by mechanical energy, the thermoplastic material can be pressed for anchoring.
The radial holes 14 are provided at a distance relative to the plate that ensures the subcortical anchor.
The embodiment shown comprises, in addition to the radial holes 14, an axial, distal hole 19 per tubular element. The purpose of the axial, distal hole 19 is the same as that of the corresponding axial, distal hole of the embodiments described above. In alternative embodiments - described in more detail below - only a distal hole is present in at least one holding portion 124 instead of a radial hole.
In the embodiment shown, the fastener portions 124 comprise, distally of the radial openings 14, a substantial extension that serves as additional stabilizers. Especially, the main load acting on an ACP is initiated by bending along the longitudinal axis of the spine, which will cause forces in the up-down direction (in the orientation of the figure) of the distal extremities of the clamping parts . The
Longer distal extension helps absorb such charges.
In addition or as an alternative, the fastening parts may comprise wings 126 that extend in lateral directions. Such wings or other deviations of a circular shape can be advantageous - especially if they make the transverse extension (extension in a direction perpendicular to the direction that connects with the adjacent vertebra) greater than the upper-lower extension (extension in the direction along of the local axis of the spine / cranial-caudal axis) - so that again the loads that are produced from the flexions of the spine can be ideally absorbed.
Also for applications other than the application such as an ACP, such non-circular cross sections of the additional stabilizers may be advantageous - depending on the limitations on the extensions of the clamping parts and the loads to be supported by the stabilizer plate.
Furthermore, as an alternative to the configuration shown, it may be advantageous to make the clamping parts less sharp and more flexible than the often very sharp tubular shape, for example by making it in the form of a blade. Too high a rigidity can be problematic in situations where it is not desired to transmit completely every moment that acts on the brace on the bone trabeculae but rather to absorb something by a certain elasticity of the bra. A blade shape may be more flexible than a tube shape. Also, a blade form, for which an opening in the bone tissue has not previously been made during surgical insertion, means a lower exposure of the bone tissue than a tube shape that extends more distally.
The fastening parts or at least one of the fastening parts may be shaped in accordance with the first aspect of the invention, that is to say the structural elements or at least one of the structural elements may comprise a steering structure that is angularly structured with respect to to a longitudinal axis of the longitudinal opening to direct different parts of the liquefiable material from a liquefiable element to different holes 14.
Although in the embodiment shown, the ACP comprises four fastening parts, each with a longitudinal opening for a liquefiable element to be inserted, this is not necessary. For example, the ACP may comprise a combination of fastener parts of the described class with conventional fasteners such as surgical screws that are to be inserted through fastener holes. For example, the ACP may comprise conventional fasteners for anchoring in stronger, healthier bone tissue and fastening parts for subcortical anchorage of the type described in locations where the bone tissue is weaker and / or less dense.
In other variants, it is possible to replace at least some of the fastening parts that are neatly fixed to the plate part by tubular elements that can be introduced separately, for example in the manner described in WO 2010/096942.
Also, the total number of fastening parts does not need to be four but may be another suitable number, for example three, five or six. It is also possible that the ACP extends not only through the vertebrae but through the vertebrae, for example three vertebrae, while the ACP can be anchored in all the vertebrae through which it extends (for example by two clamping parts for each one) or, in special situations (for example with a partially removed vertebra) only in some of them, for example in the upper and lower vertebrae of a series of three vertebrae.
In all embodiments, the plate part and the clamping parts may be made of a metal, for example titanium or stainless steel. In alternative embodiments, they can also be made of a non-absorbable plastic, such as PEEK. It is also possible to make them from a resorbable plastic, such as a PLA. If the plate part and the clamping parts are made of a thermoplastic, the softening temperature should preferably be higher than the softening temperature of the thermoplastic elements inserted in the sheath elements of the clamping parts, so that only the thermoplastic elements and not the clamping parts are liquefied. Often, a softening temperature difference of 20 ° C (or more) is sufficient to ensure this.
For implantation, the surgeon may optionally in a first operation locally remove the cortical bone tissue in the areas where the holding parts are to be propelled to the vertebral bodies. After that, the ACP is inserted, if necessary it can be cocked to propel the holding parts completely to the bone tissue until the plate part stops against the cortical bone. Then, if the clamping parts no longer comprise a thermoplastic element, such thermoplastic element is introduced into the longitudinal opening from the proximal side thereof. An insertion tool with a mechanical vibration generator (such as an ultrasonic transducer) and a sonotrode is used to at least partially liquefy the thermoplastic material of the thermoplastic element at the distal end thereof to drive this material through holes 14 to surrounding tissue. The sonotrode, for this purpose, may have a slightly smaller cross-sectional area than the cross-sectional area of the longitudinal opening so as to drive the thermoplastic element deeper into the opening.
While in the embodiment described above, the plate part is represented as essentially flat and the fastening parts are essentially perpendicular to the plate part, this need not be as a main advantage of the approximation according to the invention comprising parts of fastening that must be formed integrally with the plate part is that mechanically stable constructions are possible than when they are
Implants extend only slightly away from the vertebral bodies. Such constructions may comprise non-flat plate parts. A first approximation represented very schematically is shown in fig. 3. The anterior cervical plate is implanted being anchored in two contiguous vertebral bodies 31. An intervertebral disc is shown between the vertebral bodies, as can happen instead of a natural intervertebral disc, an intercorporal spacer (cage) can be placed to replace the intervertebral disc before anchoring this ACP. The parts 22 of thermoplastic material that, during the anchoring process, have exited through the holes 14 to the surrounding tissue are schematically shown in fig. 3. As can happen for any embodiment, the clamping parts are positioned to be anchored centrally with respect to the upper-lower axis in the vertebral bodies. While the anterior cervical plate according to the embodiments of the invention may be designed to stabilize different types of vertebrae, in particular lumbar vertebrae, thoracic vertebrae and cervical vertebrae, the embodiment of fig. 3 belongs to vertebrae of the upper thorax. In fig. 3, esophagus 35 has also been shown schematically. If an anterior cervical plaque is implanted, the configuration and location should ensure that the esophagus is not irritated despite being rather close to the spine. Fig. 4 illustrates, in schematic section through a transverse plane, a possible configuration being the curved plate, in a central region (around the longitudinal axis of the ACP / in proximity to the sagittal plane), towards the dorsal direction to provide more space for the esophagus 35.
The plate part can be relatively thin and yet have sufficient mechanical stability. Figs. 5a-5d show a configuration in which projections 131 extending from the corner regions, in continuity with which the fastening parts are made, are shown towards the center and decrease towards the center. Figs. 5b, 5c and 5d show sections along lines B-B, C-C and D-D in fig. 5th, respectively. The features illustrated in fig. 3 (a concave configuration curved towards the ventral side in a longitudinal section (section along the sagittal plane); a central region curved towards the dorsal side in cross section; the protrusions and / or the inclined corner parts) may be arbitrarily combined, that is, all these characteristics can be combined between sf, or subgroups of two, or three of these characteristics can be combined in any grouping; In addition, the anterior cervical plate does not need to be symmetrical but can also be asymmetric (for example, the protrusions and / or the inclined corners may be present on one side only, etc.).
The shape of the plate part illustrated with respect to figs. 5a-5d is simply an example. The way in which the plate part differs from a flat configuration can be altered in many ways. For example, it would be possible to provide the plate portion with edges instead of the projections illustrated. Also, the projections could be curved to protrude in the opposite direction and / or could be placed elsewhere. Depending on the anatoirna around the AVP, the total 3D structure of the plate can be chosen in many different ways.
Fig. 6 still schematically illustrates a configuration in which the holding parts 124 do not form a right angle with the plate part but form a different angle. Generally, the fastening parts (or at least those fastening parts that are integral with the plate part) are approximately parallel to each other.
Figs. 7a and 7b show a variant of a fastening part 124. In this variant, the fastening part does not comprise any radial hole but only a distal hole 19 through which the liquified material exits to the surrounding tissue. In order to give the configuration stability against ACP movements in ventral directions, the longitudinal opening comprises a step 128 that cooperates with a proximal widening 22 of the thermoplastic element 21.
Figs. 8 and 9 illustrate even the possibility of providing the fastener with a non-widened retention structure in which the bone tissue can grow to ensure long-term stability of the anchor.
Fig. 8 shows a distal region of a wing holding part 126, similar to the embodiment of figs. 1 and 2. The wings are provided with notches 130 (in alternative configurations, the outer contour could comprise a waveform). These notches form a non-widened retaining structure that does not cause substantial additional resistance against the insertion of the fastening part of the anterior cervical plate. In time after implantation, the bone tissue can grow to the retention structures so that the anchorage in the bone tissue gains additional stability. The approach of providing the fastener parts with an outer retention structure can be combined with the use of a resorbable thermoplastic material.
Another example of non-widened retention structure is illustrated in fig. 9. The holding part comprises circumferential edges 129 that serve as retention structures. Combinations of wing retention structures 126 (if present, as illustrated in Fig. 8) and of the body of the fastening part (as shown in Fig. 9) are possible. In addition or as an alternative, micro-retention structures may be used, such as an intended surface roughness of the holding part or a part thereof. A maximum surface roughness of such parts may for example be between 1 pm and 1O0 pm, especially between 1 pm and 50 pm or 20 pm, for example between 2 pm and 10 pm.
The stabilization structure in most of the embodiments described above comprises a stabilization part distally of the radial holes through which the liquid thermoplastic material exits. Alternative configurations are possible, for example clamping parts that have an elliptical cross section or
elongated in another way, especially to have a greater extension in the transverse direction than in the upper / lower direction. An example where this has been taken to one extreme is represented in fig. 10. The embodiment of fig. 10 comprises only two clamping parts 24 that have a substantially transverse extension. In contrast to the embodiments described hereinabove, the thermoplastic elements 21 have no spike shape but 5 have a shape adapted to the shape of the clamping parts 124. In the embodiment shown, the radial holes 14 are arranged in the distal end of the clamping parts. However, the configuration of fig. 10 could also be implemented with more proximal radial holes, for example for subcortical anchoring.
1. A surgical stabilization plate (121), comprising a part of plate (122) to stabilize a human or animal spine being placed ventrally in relation to the spine and being fixed to two or more different vertebral bodies, and comprising also a plurality of fastening parts (124) adapted to be anchored in the different vertebral bodies, at least one of the fastening parts (124) being neatly connected to the plate part (122) and comprising a sheath element with a longitudinal opening that is accessible from a proximal side and at least one hole (14) extending from the longitudinal opening to the outside, furthermore comprising the stabilization plate (121) by sheath element a thermoplastic element (21) inserted or inserted into the sheath element and capable of being liquefied by energy acting on the thermoplastic element (21), in which the hole (14) is positioned so that the thermop material Liquid liquor can be pressed through the hole (14) to the bone tissue of the vertebral body in which the holding part (124) has to be anchored, in which at least one holding part (124) comprises a stabilization structure capable of absorbing mechanical loads on the stabilization plate (121), in which the plate part (122) is not flat, and in which the stabilization plate (121) comprises at least four fastening parts (124).
2. The stabilization plate (121) according to claim 1, wherein at least one hole (14) is a radial hole.
3. The stabilization plate (121) according to claim 2, wherein the stabilization structure comprises a stabilization part distally of the radial hole.
4. The stabilization plate (121) according to claim 3, wherein a distance between the plate part (122) and at least one radial hole (14) is adjusted so that the liquefied material pressed through the radial hole (14) to the surrounding bone tissue after new solidification provides a subcortical anchor.
5. The stabilization plate (121) according to any of claims 3 or 4, wherein an axial extension of the stabilization part is at least two thirds of a distance between the plate part (122) and the radial hole (14).
6. The stabilization plate (121) according to any of the previous claims, wherein at least four clamping parts (124) have a non-circular cross section.
7. The stabilization plate (121) according to claim 6, wherein a transverse extension of at least four fastening parts (124) is greater than an extension in an upper-lower direction.
8. The stabilization plate (121) according to claim 6 or 7, wherein at least one of at least four fastening parts (124) comprises a wing projection from a fastening body part.
9. The stabilization plate (121) according to any of the preceding claims, wherein the plate part (122) has a thinned form in its central part.
10. The stabilization plate (121) according to any of the preceding claims, wherein the plate part (122) comprises at least one edge or one projection.
11. The stabilization plate (121) according to claim 10, wherein the projections (131) extend from the corner regions of the plate part towards the center.
12. The stabilization plate (121) according to claim 11, wherein the projections (131) decrease towards the center.
13. The stabilization plate (121) according to any of the preceding claims, wherein the plate portion is curved.
14. The stabilization plate (121) according to claim 13, in the plate part (122) is curved so that in a cross section a central region extends towards the dorsal region.
15. The stabilization plate (121) according to one of claims 13 to 14, wherein, in a section along the sagittal plane, the plate part (122) is curved towards a ventral side.
ES11767889.6T 2010-09-30 2011-09-22 Surgical stabilization plate Active ES2582460T3 (en)
US388243P 2010-09-30
US394580P 2010-10-19
PCT/CH2011/000224 WO2012040863A1 (en) 2010-09-30 2011-09-22 Anterior cervical plate
ES2582460T3 true ES2582460T3 (en) 2016-09-13
ID=45891771
ES16159688.7T Active ES2690272T3 (en) 2010-09-30 2011-09-22 Surgical stabilization plate
ES11767889.6T Active ES2582460T3 (en) 2010-09-30 2011-09-22 Surgical stabilization plate
US (2) US9241740B2 (en)
EP (2) EP2621384B1 (en)
JP (3) JP6385675B2 (en)
KR (1) KR101872045B1 (en)
CN (2) CN103269650B (en)
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RU (1) RU2599679C2 (en)
WO (1) WO2012040863A1 (en)
BR112013007137A2 (en) * 2010-09-30 2016-06-14 Spinewelding Ag anterior cervical plate
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ES2685438T3 (en) * 2008-05-01 2018-10-09 Woodwelding Ag Device to establish an anchor in the tissue
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EP3045129B1 (en) 2018-03-21
US9241740B2 (en) 2016-01-26
JP2018108379A (en) 2018-07-12
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