Patent Application
20230263600
The present patent applications claims priority to European Patent Application No. EP20184074.1 that was filed on Jul. 3, 2020, the entire contents thereof herewith incorporated by reference in its entirety.
The present application is directed to the field of dental implants, the field of manufacturing dental implants, and field of dental implant systems and methods of implanting a dental implant to a jaw bone, as well as bone anchors and fixtures.
In the field of dental implants, the state of the art has proposed some devices that do not rely on a threading for attachment to a jaw bone. For example, U.S. Pat. No. 8,167,619 is directed to an expandable dental implant having an envelope 1 with narrow longitudinal slits 19 to form deformable clasps 21, and conical expander member 20 arranged inside envelope 1, such that elastically deformable clasps 21 are adapted to expand laterally outwards as an expander 20 is longitudinally displaced by a displacing means along the main longitudinal axis of the implant towards the apical end. As expander member 20 is coronally displaced, clasps 21 are gradually urged apically outwards. Substantially radial forces applied to expander 20 by each leg at corresponding contact points B′ and C′ prevent the expander member from being apically displaced. When the displacing means is detached from the expander 20, the expander 20 is immobilized, and will not be loosened over the course of time.
U.S. Pat. No. 6,273,720 is directed to a dental implant system including an implant 10 having a narrow gauge body 12 which is press fitted into a receptor site formed in the jawbone 14 of a dental patient. Before installation of the implant 10 an incision is made in the gum tissue of the patient and the underlying bone is exposed. A drill having a drill bit of a configuration matching the configuration of the implant is used to bore a hole in the jawbone 14 of a size slightly smaller than the circumference of the implant body 12. This permits the implant 10 to be press fitted into the bored hole. The exterior of the implant body 12 should preferably have a plurality of serrations 24 which are spaced longitudinally apart along the vertical height of the implant 10 to facilitate the seating of a plasma sprayed coating of hydroxyl apatite “HA” before the implant 10 is press fitted into the jawbone 14.
Brazilian Patent Application No. 202012010880 discusses a threadless dental implant having a straight horizontal base 2, from which cylindrical pillars 3 vertically project upwardly parallel to each other, the horizontal base 2 and the cylindrical pillars 3 forming a U-shape, wherein the pillars 3 have central channels 4 with a rectangular upper profile, for receiving a slap implant 5 and abutment elements 6.
U.S. Patent Publication No. 2010/0114314 is directed to a dental implant 10 has a rigid member 12, and an expandable, porous member 14. The porous member 14 engages an apical or distal end portion 18 of the rigid member 12 when it is placed in a bore in bone. With this structure, a longitudinal force may be applied to the rigid member 12 so that the rigid member 12 impacts against the porous member. This driving force causes the porous member 14 to expand radially outward into the surrounding bone of the surgical site.
U.S. Patent Publication No. 2010/0047741 describes a dental implant carrier 6 is made in two parts that includes a base body 7 with its laterally projecting expanding parts 8a and 8b which are made in spring-elastic form and whose spring force acts radially outwardly under load.
European Patent Application No. EP19201095.7, this reference herewith incorporated by reference in its entirety, describes another threadless dental implant bone anchor and corresponding system, that relies on a conically-shaped meshed wall as a bone- facing implant element that can be expanded to engage with the jaw bone, and uses an expansion tool to provide for the radial expansion, for improved fastening and ossointegration with the jaw bone.
U.S. Pat. Pub. No. 2004/0053196 describes a dental implant 1 having surface regions 4 of a first type which have osseo-integrative properties, and surface regions 8 of a second type made of a material that is liquefiable by ultrasonic oscillation. The liquefiable material of surface regions 8 can have thermoplastic properties or a thixotropic cement, so that in can be pressed into unevennesses, pores or suitably produced geometries of the bone tissue. After solidification it forms a positive-fit connection between the implant and the surrounding bone tissue. In a special variant that is used for an existing dental cavity without using a drill hole, surface regions 8 can be formed as longitudinal fingers 6, and axially-extending, self-cutting or grooving elements 9 can be formed form the first type of material, traversing surface regions 8.
U.S. Pat. Pub. No. 2009/0011384 describes a dental implant 120, 130 where protrusions 124, 134 are formed as helical ribs or threads 128, 138 that can extend respectively along stem portions 123, 133. Threads 128, 138 respectively extend through helical openings 125, 135 on the sleeves 126, 136, and can extend past the porous sleeves 126, 136 on the core of implant 120, 130, and may extend only in portions of the openings 125, 135 on the sleeves 126, 136 whether continuously or in separated segments along the helical path formed by the openings.
U.S. Pat. No. 4,011,602 describes an expandable device for attachment to bone tissue, where a porous body member 10 having longitudinal cuts 12, 18 can be radially expanded by an inner tapered cylindrical member 22, to provide a stress between the tissue and the body member in the range of about 150 to 750 psi.
However, despite all the progress made in the field of dental implants, and attempts having been made to find solutions with threadless dental implants, strongly improved dental implants are desired that do not rely on a threading for threadable attachment and also do not rely on bone compression or pressure mechanisms to the native jaw bone, for example mechanical expansion mechanisms, to improve mechanical attachment and its durability, improve bone healing, osso-integration, for simplified and efficient handling of the dental implant, to shorten preparation time, reduce risks of bone fractures during the implanting process, and to provide for a cost-effective solution.
According to an aspect of the present invention, a jaw bone anchor for threadless engagement with a jaw bone is provided, the jaw bone anchor having an apical side, a coronal side, and having a root section. Preferably, the jaw bone anchor includes an inner core having a longitudinal extension along the root section, an outer osso-integrative shell layer that is arranged around the inner core, and a plurality of radially-extending bone engaging elements, the radially-extending bone engaging elements extending from the inner core, traversing and protruding from the outer osso-integrative shell layer.
According to another aspect of the present invention, a dental implant system is provided, preferably including a crown, a dental abutment, a jaw bone anchor for threadless engagement with a jaw bone, and an attachment device for attaching the dental abutment to the jaw bone anchor. Moreover, preferably, the jaw bone anchor has an apical side, a coronal side, and extending along a root section, and the jaw bone anchor preferably includes an inner core having a longitudinal extension along the root section, an outer osso-integrative shell layer that is arranged around the inner core, a plurality of radially-extending bone engaging elements, the radially-extending bone engaging elements extending from the inner core, traversing the outer osso-integrative shell layer, and an attachment mechanism that is accessible via the coronal side for attachment of the dental abutment with the attachment device.
According to another aspect of the present invention, a jaw bone anchor for a dental implant is provided. Preferably, the jaw bone anchor includes an apical side, a coronal side, and a root section, the jaw bone anchor includes an inner stabilizing means extending along the root section, an outer osso-integrative means surrounding the inner stabilizing means, and a plurality of radially-extending bone engaging means, the radially-extending bone engaging means extending from the inner stabilizing means and traversing and protruding from the outer osso-integrative means, wherein the inner stabilizing means and the plurality of radially-extending bone engaging means are configured to provide for a primary stability of the jaw bone anchor before ossointergration.
According to still another aspect of the present invention, a method for anchoring a threadless dental implant to a jaw bone drill hole is provided. Preferably, the method includes a step of drilling a jaw bone drill hole to a target dental implant location, the jaw bone drill hole having a complementary shape to a shape of the root section of a jaw bone anchor, the jaw bone drill hole having a diameter that is wider than corresponding portions of the jaw bone anchor, inserting the jaw bone anchor into the jaw bone drill hole, such that radially-extending or protruding bone engaging elements engage with native bone structure of the jaw bone inside the jaw bone drill hole, while preserving a gap between a cylindrical, conical, or combined cylindrical-conical outer osso-integrative shell layer and a bone surface of the jaw bone drill hole, to provide for a primary stability of jaw bone anchor relative to the jaw bone before the osso-integration phase of the jaw bone anchor.
According to another aspect of the present invention, a method for manufacturing a jaw bone anchor or fixture is provided. Preferably, the method includes a step of machining a core and protruding elements from one solid piece of material or by an additive manufacturing step, and a step of depositing a porous, osso-integrative shell layer having a substantially cylindrical shape around the core by a three-dimensional printing method or additive manufacturing step onto an outer surface of the core, such that the protruding elements still traverse the osso-integrative shell layer.
The above and other objects, features and advantages of the present invention and the manner of realizing them will become more apparent, and the invention itself will best be understood from a study of the following description with reference to the attached drawings showing some preferred embodiments of the invention.
The accompanying drawings, which are incorporated herein and constitute part of this specification, illustrate the presently preferred embodiments of the invention, and together with the general description given above and the detailed description given below, serve to explain features of the invention.
Herein, identical reference numerals are used, where possible, to designate identical elements that are common to the figures. Also, the images are simplified for illustration purposes and may not be depicted to scale.
According to some aspects of the present invention, as shown in
The crown-facing or coronal side of jaw bone anchor or fixture 100 includes a neck 70 having an opening 40, for example an opening having an upper conically-shaped recess for engaging with a dental abutment 80, and an attachment element or mechanism 45, preferably a threading for engagement with a corresponding threading of an attachment device 60, preferably a screw with a head and complementary threading. Jaw bone anchor or fixture 100 further includes an inner core 10 having an outer surface 12, core 10 preferably made of a solid material, for example such that no voids or cavities are formed in the material of core 10, and an outer osso-integrative shell layer 20, preferably made of a material that can provide for ossointegration, for example a titanium-based material, for example but not limited to a commercially pure titanium, titanium alloys, titanium nitride (TiN). Moreover, at least the bone-facing outer surface 22 of the osso-integrative shell layer 20 is porous, for example by having a trabecular structuration. In terms of porosity, the osso-integrative shell layer can have a porosity of about 40% to 60% in terms of a fraction of the volume of voids over the total volume, and can have an average pore size in a range between 100 μm and 500 μm, more preferably between 300 μm and 400 μm. A thickness H3 of a wall formed by the osso-integrative shell layer 20 can have a thickness between 0.1 mm and 1 mm, more preferably about 0.2 mm to 0.6 mm.
Jaw bone anchor or fixture 100 further includes radially-protruding bone-engaging elements 30 along the root section RS or the jaw-bone facing section, bone engaging elements 30 that protrude in a direction that is radially away from central axis CA from inner core 10 and are traversing the outer osso-integrative shell layer 20, such that an apex, tip, or summit 31 of bone-engaging elements 30 protrude away from bone-facing outer surface 22 of the osso-integrative shell layer 20, for example by a height H1 of about 0.1 mm to 1 mm, while having an entire height H2 that is measured from outer surface 12 of inner core 10 that is preferably about in a range between 0.2 mm to 2 mm. Once jaw bone anchor 100 is placed into drilling hole DH of jaw bone JB at its final position for ossointegration purposes, apexes or summits 31 of bone-engaging elements 30 will penetrate into the bone structure of jaw bone JB, for example preferably by about 50% to 99% of its height H as shown on the right hand side of
Bone-engaging elements 30 are preferably made from a solid material, and can form an integral part together with inner core 10. For example, preferably, bone-engaging elements are made of a non-porous or other type of non-pervious material, for example from solid metal or metal alloy, for example the typical material used for dental abutments and fixtures, such as titanium or different titanium-based materials and alloys. Also, given the primary stability purpose of bone-engaging elements 30, these elements 30 are not liquifiable or otherwise capable of dissolving by applying mechanical oscillation, as they have provide for the first anchoring of jaw bone anchor or fixture 100 during the osseo-integration stage. In other words, once bone anchor or fixture 100 is inserted into drilling hole DH, and upon initiation and performance of the osseo-integration stage, where osso-integrative shell layer 20 integrates with the surrounding bone, bone-engaging elements 30 remain solid and intact, firmly holding jaw bone anchor or fixture 100 or fixture in place. Also, osso-integrative shell layer 20 is made of porous material, or other type of pervious material, but is also not made of a liquifiable or otherwise capable of dissolving by applying mechanical oscillation.
The relative and absolute dimensions of inner core 10 and the bone engaging elements 30 as well as osso-integrative shell layer 20 are designed such that, during a placement of jaw bone anchor 100 into hole drill hole DH, tips 31 of bone engaging elements 30 will engage into bone structures of bone surfaces BS inside drill hole DH with a certain height or depth, and tips 31 of bone engaging elements 30 will move downwards and slide within bone structure. Once placed at a position of ossointegration of jaw bone anchor 100, tips 31 of bone engaging elements 30 will remain in bone structures of bone surfaces BS with a certain height or depth H1, and simultaneously, outer surface 22 of osso-integrative shell layer 20 will not exert any or only very little pressure to surrounding bone surfaces BS of bone structures of jaw bone JB of drill hole DH. In this respect, tips 31 of bone-engaging elements 30 are such that they fully protrude radially away from outer surface 12 of inner core 10 through osso-integrative shell layer 20 from inner core 10 with height H2 that is larger than height H3.
Specifically, dimensions of outer surface 22 of osso-integrative shell layer 20 and dimensions of drill hole DH are designed remain at a distance or gap GP between outer surface 22 and bone surface BS, to thereby prevent generating any or only little bone compression during the osso-integration phase and healing, which can in turn avoid a bone resorption phase at the beginning of the healing for implantation. In this respect, a drill hole DH is drilled into the jaw bone JB in preparation of the jaw bone anchoring that has a diameter that is slightly larger than a diameter of the jaw bone anchor 100 at a corresponding depth into the drill hole DH, when jaw bone anchor 100 is placed at the final, osso-integration position, the diameter being two times a distance or gap GP. Moreover, it is possible that tip 35 of jaw bone anchor 100 can be contact with a bone floor BF of drill hole DH, but without exerting pressure on to the bone floor BF. This allows to limit a penetration depth of jaw bone anchor 100 along axis CA into drill hole DH. Gap GP that will form a cylindrical, conical, or combined cylindrical-conical wall shape, can be filled with an ossointegration paste, with blood, or ossointegration-enhancing active agents, or combination thereof, for aiding the osso-integration of osso-integrative shell layer 20 to the surrounding bone structures BS.
The radially-extending bone engaging elements 30 are configured and designed to allow for a secure insertion of jaw bone anchor 100 into drill hole DH and for engagement and partial penetration of tips 31 with jaw bone JB when jaw bone anchor 100 is pressed into DH along axis CA. In addition, by virtue of the mechanical interconnection between bone engaging elements 30 with inner core 10, both preferably made of solid material, upon insertion of jaw bone anchor 100 to a desired target position of the dental implant, elements 30 and core 10 are configured to give jaw bone anchor 100 the necessary primary stability to with localized bone compression by tips 31 at least partially engaging into jaw bone JB, to enable ossointegration between shell layer 20 and bone surface BS of jaw bone JB. At the same time, bone engaging elements 30 prevent rotation or turning of jaw bone anchor 100 relative to jaw bone JB around center axis CA. In this respect, with a substantial equal distribution of bone engaging elements 30 around outer surface of bone anchor 100 together with a protruding height H1 of tips 31 of bone engagement elements 30 in a radial direction away from outer surface 22 of osso-integrative shell layer 20, at time of placing jaw bone anchor 100 to drill hole DH by pressing anchor 100 along axis CA into drill hole DH, tips 31 of bone engaging elements 30 will permit a centering of jaw bone anchor 100 with respect to the rotational center axis CA of drill hole DH.
With respect to the mechanical separation of inner core 10 and bone engaging elements 30 made of solid material, and osso-integrative shell layer 20 having at least its outer surface 22 being porous, for example a trabecular structure, it is possible to mechanically separate two functions of the jaw bone anchor 100, providing for substantial advantages over the state of the art. First, with the solid inner core 10 and bone engaging elements 30, primary stability to jaw bone anchor 100 is provided for the time after insertion of jaw bone anchor 100 to drill hole DH, but before the ossointegration of jaw bone anchor 100 has taken place. Structure and arrangement of bone engaging elements 30 also allow to provide for substantial resistance against rotation or turning of jaw bone anchor 100 relative to jaw bone JB even before ossointegration, as further discussed below. Second, virtue of the gap GP that minimizes or even disallows contact between outer surface 22 of osso-integrative shell layer 20 and bone surface BS of drill hole DH, no compressive force is exerted on bone surface BS of drill hole DH, and thereby does not cause any native bone compression. This feature in turn allows to minimize pressure necrosis and bone resorption of the jaw bone structures to a maximum, and can entirely avoid it. See for example, Bashutski, Jill D., Nisha J. D'Silva, and Hom-Lay Wang., “Implant Compression Necrosis: Current Understanding and Case Report,” Journal of Periodontology, Vol. 80, No. 4, 2009, pp. 700-704, see also Nevins, Myron, Marc L. Nevins, Peter Schupbach, Joseph Fiorellini, Zhao Lin, and David M. Kim, “The Impact of Bone Compression on Bone-to-Implant Contact of an Osseointegrated Implant: a Canine Study,” International Journal of Periodontics & Restorative Dentistry, Vol. 32, No. 6, 2012.
This feature in turn will allows for a shorter period of ossointegration of the jaw bone anchor 100 inside a drill hole DH. In other words, despite avoiding nearly all bone compression on a surface level of bone surface BS of a drill hole DH, a very strong primary stability is achieved by a few bone engaging elements 30 having a limited surface or volume of impact to the native jaw bone, only establishing a very limited local compression to native jaw bone JB, and at the same time, a fast and strongly improved ossointegration is possible. To achieve this, dimensions of the drill hole DH and dimensions of jaw bone anchor 100 are matched such that a gap GP between outer surface 22 of shell layer 20 and inner surface of drill hole DH is formed when jaw bone anchor 100 is inserted into drill hole DH, as explained above, and thereby, the existing native bone cavity from the native tooth root is not used. In addition, no elements are used with jaw bone anchor 100 that will expand to cause a critical compression to bone structures, to provide for a solid, non-expanding anchor 100. This is a substantial improvement over existing jaw bone anchors that use a bone threading creating a highly compressive force with the threads to the bone, for example tapped, self-tapping or self-cutting types, or other type of jaw bone anchors using expanding hooks or jaws for primary, pre-ossointegration bone anchoring.
For example, in the example shown in
Moreover, the long sides of the rectangular base of pyramid is arranged to be parallel to center axis CA, and the short sides is arranged tangential to the outer surface 12 of inner core 10, perpendicular to center axis CA. With the reduced width of pyramids that form bone engaging elements 30 facing the bone structure of bone surface BS, such that a front apically-facing sloped surface 32 of pyramid engages with bone structures, jaw bone anchor 100 can be pushed into drill hole DH with jaw bone anchor 100 engaging to bone, by cutting, scratching, or grating against bone structures with less resistance, and at the same time the two long side sloped surfaces of the pyramids face the bone structures to prevent rotation of jaw bone anchor 100 around center axis CA. It is also possible that the pyramids that form bone engaging elements 30 are slanted, so that front apically-facing sloped surface 32 of pyramid that faces downwards towards jaw bone JB during insertion has a smaller slant angle relative to center axis CA, as compared to a slant angle of rear coronal-side sloped surface 34 relative to center axis, as further explained with respect to
In a variant, it is possible that bone engaging elements or teeth 30, also referred to as plurality of radially-extending bone engaging means, have a shape that is different from a pyramidal shape, but permitting to cut or otherwise mechanically engage with bone structures at bone surface BS when jaw bone anchor 100 is pushed into drill hole DH, and at the same time, once engaged with native bone, resisting rotational movements of jaw bone anchor 100. Generally speaking, bone engaging elements 30 can be chosen to have a radially-protruding structure that is narrower in width in a tangential directions relative to surface 22, and is comparatively longer in the axial direction with respect to center axis CA. Thereby, relatively speaking, an area of a side surface that resist a rotation of jaw bone anchor 100 is larger than an area front, apically facing surface or a rear, crown-facing surface of the structure, for easier engagement to bone structures. These shapes can include but are not limited to a blade or cutter-like shape with its longitudinal axis substantially parallel to a center axis CA, ramp-shaped bone engaging elements 30 with a surface of ramp arranged towards the apical side of jaw bone anchor 100, circularly-, ovally-, elliptically-, or other round-shaped partial disks having a plane that is arranged radially relative to center axis, tetrahedron-shaped having two longer sides, tabs that are obliquely arranged to a center axis CA, ridge-like shapes.
As another example,
Moreover,
It is also possible that rear slope angle is 90° or more, such that rear crown-facing sloped surface 134 is arranged perpendicular to center axis CA, or such that surface 134 forms a hook-like, ramp-like, claw-like, clip-like, or grapnel structure, for the primary stability and fastening with the bone, as depicted on the
Following the conically-shaped section COS, a cylindrically-shaped section CYS is arranged, having a diameter that is equal to a largest diameter of conically-shaped section COS, the outer surface 126 of the COS and outer surface 122 of osso-integrative wall 120 of CYS continuously arranged with no edge, recess, or other discontinuity between the outer surfaces 122, 126 of COS and CYS, respectively. Towards an upper edge of cylindrically-shaped section CYS, radially and angularly spaced apart by an angle of 120°, three (3) bone engaging elements 130 are shown, having an axially-extending longitudinal ridge-like shape, in the variant shown having the same shape as the ones located on the conically-shaped section COS, but being oriented to be parallel with the central axis CA, and outer surface 122 of cylindrically-shaped section CYS. Both osso-integrative wall 120 that is cylindrically shaped, and osso-integrative wall 124 that is conically shaped are both made to have a porous structure, for example a trabecular structure. In the variant shown, a thickness of the layers 120, 124 is about 0.4 mm, having a trabecular porous structure with a porosity of 50% per volume, and an average pore size between 300 μm and 400 μm. In contrast thereto, core 110 and bone engaging elements 130 are made of solid material.
Bone engaging elements 130, with their longitudinal ridge-like shape, can form a sharp edge at the ridge, to provide for a cutting edge that allows to cut into the bone, with the lateral side walls allowing to engage with bone, preventing rotation and providing for the primary stability of jaw bone anchor 300 to drill hole DH. In a variant, front apically-facing sloped surface 132 can be made of two surfaces arranged at a relatively acute angle towards each other, for example 45°or less, to provide for a cutting edge facing the bone structure to facilitate engagement and anchoring with bone structure of jaw bone JB.
Next, the dimensions and their function for the placement and ossointegration of jaw bone anchor 300 into a drill hole DH is explained, as exemplarily illustrated in
However, in a variant, the diameter of the upper cylindrically-shaped bore hole is chosen to be larger than 3.5 mm, in other words larger than a diameter formed by a circle that coincides with a radially outermost point of the three (3) bone engaging elements 130 of conically-shaped section COS, but still less than a diameter formed by a circle that coincides with a radially outermost point of the three (3) bone engaging elements 130 of cylindrically-shaped section CYS, being less than the exemplary 3.9 mm, for example between 3.6 mm and 3.7 mm, so that bone engaging elements 130 of conically-shaped section COS may only or do not touch bone surface BS of the cylindrical part of drill hole DH upon insertion of jaw bone anchor 300, but will only engage with bone surface BS of the middle conical part of drill hole DH. This configuration is preferably used when anchor 300 crosses two different bone densities along the central axis towards the jaw bone JB, for example where the crestal cortical bone is traversed first, having a high bone density, and thereafter the spongious cancellous bone is accessed for anchoring, having a low bone density as compared to the crestal cortical bone. In this respect, at the final placement position, anchor 300 can be configured such that CYS lies substantially within the crestal cortical section, while COS lies substantially within the cancellous bone. In this respect, different anchors 300 can be manufactured for different placements and patients, depending of the depth of crestal cortical section of jaw bone JB. However, bone engaging elements 130 of cylindrically-shaped section CYS will engage and cut into the bone structure at bone surface BS of cylindrically-shaped bore hole only once these bone engaging elements 130 reach the upper edge of drill hole DH.
In either variant, as only bone engaging elements 130 of cylindrically-shaped section CYS will more profoundly engage with cylindrically-shaped bore hole, and only bone engaging elements 130 of conically-shaped section CYS will more profoundly engage with conically-shaped bore hole, it is possible to first insert jaw bone anchor 300 with a first pressure partially into drill hole DH, until at least one of upper bone engaging elements 130 of cylindrically-shaped section CYS abut against upper edge of drill hole DH, or lower bone engaging elements 130 of conically-shaped section COS engage with a bone surface BS of the conical section of drill hole, or both. Next, with a second pressure that is higher than the first pressure, jaw bone anchor 300 can be pressed into its final position for ossointegration, such that a surface of tip 135 abuts against bone floor BF of drill, hole DH, and bone engaging elements 130 will be pressed and cut into bone structure at bone surface BS. This two steps can be done manually by an operator or dental surgeon.
According to another aspect of the present invention, a method for manufacturing a jaw bone anchor or fixture 100 as described herein is provided. With respect to the manufacturing of the jaw bone anchor 100, 300, it is possible that core 10 and protruding elements 30 are machined from one solid piece of material with a first step, for example titanium or titanium-based block of raw material, or made by an additive manufacturing process such as a three-dimensional printing, and thereafter, a porous, osso-integrative shell layer 20 is deposited by a three-dimensional printing method or additive manufacturing process to an outer surface 12 of core 10 in a second step, for example as described in U.S. Patent Publication No. 2020/0100874, where an osso-integrative layer is deposited by a three-dimensional printing method to an interface layer, this reference herewith incorporated by reference in its entirety. As a variant, it is possible that a core 10 is provided by machining with a lathe, and thereafter both protruding elements 30 as solid material and osso-integrative shell layer 20 as an at least partially porous layer are deposited by three-dimensional printing, or another additive process. Moreover, it is also possible that an manufacturing element is formed by machining, include neck 70, opening 40, and an attachment element or mechanism 45, and including a longitudinal cylinder or tapered section that has similar dimensions and length of the final dimensions of anchor 100 is formed. Subsequently, core 10, protruding elements 30, and osso-integrative shell layer 20 are three-dimensional printed in this order by rotating neck 70 and pre-formed cylinder or tapered section. In this respect, core 10 forms a cylindrical or tapered lumen around the pre-formed cylinder or tapered section. In another variant, neck 70, core 10, protruding elements 30, and osso-integrative shell layer 20 are all three-dimensional printed, and thereafter opening 40, and an attachment element or mechanism 45 are machined into neck 70. In another variant, neck 70 and opening 40 are machined from a solid piece, core 10 and structure 20 are then three-dimensionally printed on neck 70. Thereafter, attachment mechanism 45 is machined and placed into neck 70 during or after the step of three-dimensional printing.
Jaw bone anchor or fixture 100 has been described herein in the context of a dental application and surgery for a dental implant or prosthesis, but the same type of jaw bone anchor or fixture can be used for other types implants and surgeries, serving different applications and purposes, where a non-threaded anchoring element is desired and provides for some benefits. For example. it could be used for different types of orthopedic surgeries, where a bone anchoring element can be required to he placed inside a bone, for attaching other devices thereto, for example a pedicle screw, rod holder, or other type of implant element, for example for improved adjustability.
While the invention has been disclosed with reference to certain preferred embodiments, numerous modifications, alterations, and changes to the described embodiments, and equivalents thereof, are possible without departing from the sphere and scope of the invention. Accordingly, it is intended that the invention not be limited to the described embodiments, and be given the broadest reasonable interpretation in accordance with the language of the appended claims.
| Number | Date | Country | Kind |
|---|---|---|---|
| 20184074.1 | Jul 2020 | EP | regional |
| Filing Document | Filing Date | Country | Kind |
|---|---|---|---|
| PCT/IB2021/055792 | 6/29/2021 | WO |
