WO2009004069A1 - Implant dentaire poreux - Google Patents

Implant dentaire poreux Download PDF

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Publication number
WO2009004069A1
WO2009004069A1 PCT/EP2008/058623 EP2008058623W WO2009004069A1 WO 2009004069 A1 WO2009004069 A1 WO 2009004069A1 EP 2008058623 W EP2008058623 W EP 2008058623W WO 2009004069 A1 WO2009004069 A1 WO 2009004069A1
Authority
WO
WIPO (PCT)
Prior art keywords
porous body
dense member
porous
dental implant
dense
Prior art date
Application number
PCT/EP2008/058623
Other languages
English (en)
Inventor
Ivo Thijs
Wim Bouwen
Steven Mullens
Jan Luyten
Norbert Dejonghe
Original Assignee
Vlaamse Instelling Voor Technologisch Onderzoek (Vito)
Priority date (The priority date is an assumption and is not a legal conclusion. Google has not performed a legal analysis and makes no representation as to the accuracy of the date listed.)
Filing date
Publication date
Application filed by Vlaamse Instelling Voor Technologisch Onderzoek (Vito) filed Critical Vlaamse Instelling Voor Technologisch Onderzoek (Vito)
Publication of WO2009004069A1 publication Critical patent/WO2009004069A1/fr

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Classifications

    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61C—DENTISTRY; APPARATUS OR METHODS FOR ORAL OR DENTAL HYGIENE
    • A61C8/00—Means to be fixed to the jaw-bone for consolidating natural teeth or for fixing dental prostheses thereon; Dental implants; Implanting tools
    • A61C8/0012—Means to be fixed to the jaw-bone for consolidating natural teeth or for fixing dental prostheses thereon; Dental implants; Implanting tools characterised by the material or composition, e.g. ceramics, surface layer, metal alloy
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61C—DENTISTRY; APPARATUS OR METHODS FOR ORAL OR DENTAL HYGIENE
    • A61C8/00—Means to be fixed to the jaw-bone for consolidating natural teeth or for fixing dental prostheses thereon; Dental implants; Implanting tools
    • A61C8/0003—Not used, see subgroups
    • A61C8/0004—Consolidating natural teeth
    • A61C8/0006—Periodontal tissue or bone regeneration
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61C—DENTISTRY; APPARATUS OR METHODS FOR ORAL OR DENTAL HYGIENE
    • A61C8/00—Means to be fixed to the jaw-bone for consolidating natural teeth or for fixing dental prostheses thereon; Dental implants; Implanting tools
    • A61C8/0018—Means to be fixed to the jaw-bone for consolidating natural teeth or for fixing dental prostheses thereon; Dental implants; Implanting tools characterised by the shape
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61C—DENTISTRY; APPARATUS OR METHODS FOR ORAL OR DENTAL HYGIENE
    • A61C8/00—Means to be fixed to the jaw-bone for consolidating natural teeth or for fixing dental prostheses thereon; Dental implants; Implanting tools
    • A61C8/0018—Means to be fixed to the jaw-bone for consolidating natural teeth or for fixing dental prostheses thereon; Dental implants; Implanting tools characterised by the shape
    • A61C8/0037—Details of the shape
    • A61C2008/0046—Textured surface, e.g. roughness, microstructure
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61F—FILTERS IMPLANTABLE INTO BLOOD VESSELS; PROSTHESES; DEVICES PROVIDING PATENCY TO, OR PREVENTING COLLAPSING OF, TUBULAR STRUCTURES OF THE BODY, e.g. STENTS; ORTHOPAEDIC, NURSING OR CONTRACEPTIVE DEVICES; FOMENTATION; TREATMENT OR PROTECTION OF EYES OR EARS; BANDAGES, DRESSINGS OR ABSORBENT PADS; FIRST-AID KITS
    • A61F2/00—Filters implantable into blood vessels; Prostheses, i.e. artificial substitutes or replacements for parts of the body; Appliances for connecting them with the body; Devices providing patency to, or preventing collapsing of, tubular structures of the body, e.g. stents
    • A61F2/02—Prostheses implantable into the body
    • A61F2/30—Joints
    • A61F2002/30001—Additional features of subject-matter classified in A61F2/28, A61F2/30 and subgroups thereof
    • A61F2002/30003—Material related properties of the prosthesis or of a coating on the prosthesis
    • A61F2002/30004—Material related properties of the prosthesis or of a coating on the prosthesis the prosthesis being made from materials having different values of a given property at different locations within the same prosthesis
    • A61F2002/30011—Material related properties of the prosthesis or of a coating on the prosthesis the prosthesis being made from materials having different values of a given property at different locations within the same prosthesis differing in porosity
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61F—FILTERS IMPLANTABLE INTO BLOOD VESSELS; PROSTHESES; DEVICES PROVIDING PATENCY TO, OR PREVENTING COLLAPSING OF, TUBULAR STRUCTURES OF THE BODY, e.g. STENTS; ORTHOPAEDIC, NURSING OR CONTRACEPTIVE DEVICES; FOMENTATION; TREATMENT OR PROTECTION OF EYES OR EARS; BANDAGES, DRESSINGS OR ABSORBENT PADS; FIRST-AID KITS
    • A61F2/00—Filters implantable into blood vessels; Prostheses, i.e. artificial substitutes or replacements for parts of the body; Appliances for connecting them with the body; Devices providing patency to, or preventing collapsing of, tubular structures of the body, e.g. stents
    • A61F2/02—Prostheses implantable into the body
    • A61F2/30—Joints
    • A61F2/30767—Special external or bone-contacting surface, e.g. coating for improving bone ingrowth
    • A61F2002/3092—Special external or bone-contacting surface, e.g. coating for improving bone ingrowth having an open-celled or open-pored structure
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61F—FILTERS IMPLANTABLE INTO BLOOD VESSELS; PROSTHESES; DEVICES PROVIDING PATENCY TO, OR PREVENTING COLLAPSING OF, TUBULAR STRUCTURES OF THE BODY, e.g. STENTS; ORTHOPAEDIC, NURSING OR CONTRACEPTIVE DEVICES; FOMENTATION; TREATMENT OR PROTECTION OF EYES OR EARS; BANDAGES, DRESSINGS OR ABSORBENT PADS; FIRST-AID KITS
    • A61F2/00—Filters implantable into blood vessels; Prostheses, i.e. artificial substitutes or replacements for parts of the body; Appliances for connecting them with the body; Devices providing patency to, or preventing collapsing of, tubular structures of the body, e.g. stents
    • A61F2/02—Prostheses implantable into the body
    • A61F2/30—Joints
    • A61F2/3094—Designing or manufacturing processes
    • A61F2002/30968—Sintering
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61F—FILTERS IMPLANTABLE INTO BLOOD VESSELS; PROSTHESES; DEVICES PROVIDING PATENCY TO, OR PREVENTING COLLAPSING OF, TUBULAR STRUCTURES OF THE BODY, e.g. STENTS; ORTHOPAEDIC, NURSING OR CONTRACEPTIVE DEVICES; FOMENTATION; TREATMENT OR PROTECTION OF EYES OR EARS; BANDAGES, DRESSINGS OR ABSORBENT PADS; FIRST-AID KITS
    • A61F2250/00—Special features of prostheses classified in groups A61F2/00 - A61F2/26 or A61F2/82 or A61F9/00 or A61F11/00 or subgroups thereof
    • A61F2250/0014—Special features of prostheses classified in groups A61F2/00 - A61F2/26 or A61F2/82 or A61F9/00 or A61F11/00 or subgroups thereof having different values of a given property or geometrical feature, e.g. mechanical property or material property, at different locations within the same prosthesis
    • A61F2250/0023—Special features of prostheses classified in groups A61F2/00 - A61F2/26 or A61F2/82 or A61F9/00 or A61F11/00 or subgroups thereof having different values of a given property or geometrical feature, e.g. mechanical property or material property, at different locations within the same prosthesis differing in porosity
    • A61F2250/0024—Special features of prostheses classified in groups A61F2/00 - A61F2/26 or A61F2/82 or A61F9/00 or A61F11/00 or subgroups thereof having different values of a given property or geometrical feature, e.g. mechanical property or material property, at different locations within the same prosthesis differing in porosity made from both porous and non-porous parts, e.g. adjacent parts
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61F—FILTERS IMPLANTABLE INTO BLOOD VESSELS; PROSTHESES; DEVICES PROVIDING PATENCY TO, OR PREVENTING COLLAPSING OF, TUBULAR STRUCTURES OF THE BODY, e.g. STENTS; ORTHOPAEDIC, NURSING OR CONTRACEPTIVE DEVICES; FOMENTATION; TREATMENT OR PROTECTION OF EYES OR EARS; BANDAGES, DRESSINGS OR ABSORBENT PADS; FIRST-AID KITS
    • A61F2310/00—Prostheses classified in A61F2/28 or A61F2/30 - A61F2/44 being constructed from or coated with a particular material
    • A61F2310/00005—The prosthesis being constructed from a particular material
    • A61F2310/00011—Metals or alloys
    • A61F2310/00023—Titanium or titanium-based alloys, e.g. Ti-Ni alloys

Definitions

  • the present invention is related to a dental implant and a method of manufacturing the implant.
  • Titanium and Ti-alloys are commonly used for the production of surgical implants, because of their strength/weight ratio, their high resistance to corrosion and relatively low elasticity modulus, and their biocompatibility . Therefore, Ti and Ti-alloys are already used in a large number of implant materials in a dense form, e.g. for dental implants, shoulder-, hip-, finger- implants, etc.
  • Dense titanium implant materials have the disadvantage to loose their fixation after some time due to their higher strength and higher E-modulus compared to trabecular bone. This phenomenon is known as "stress shielding" [1,2] .
  • Stress shielding [1,2] .
  • a conventional way of improving the fixation is to increase the roughness of the surface or to coat it with a calcium phosphate layer.
  • Patent application WO 02/34155 discloses a porous TiNi dental implant of cylindrical shape.
  • the pores are permeable so as to allow osseointegration of the implant into the bone.
  • the implant is reinforced by at least one wire of dense TiNi running along the entire length of the implant.
  • the porous body and the reinforcing wires are manufactured simultaneously, in the same process by an agglomeration technique.
  • a polymer coating has to be provided on the neck and the supporting head.
  • Another disadvantage of this implant is that the dental crown is fastened onto the polymer coating with no contact with the metal parts of the implant.
  • US patent 5344457 discloses an implant to which a dental bridge may be connected.
  • the implant comprises a lower bone-engaging region and an upper bone attachment region.
  • the lower region is provided with a porous surface into which bone may grow.
  • the porous surface is comprised of a network of discrete particles.
  • the upper region has a surface suitable for bone attachment which is different from the surface of the lower region.
  • the present invention aims to provide a dental implant which overcomes the drawbacks of prior art implants. It is an aim of the invention to provide at least an alternative dental implant having at least a same and preferably an improved functionality compared with dental implants of the prior art. The present invention equally aims to provide a method of manufacturing the implant. Summary of the Invention
  • a dental implant comprising (or consisting of) a porous body made of a porous biocompatible material and a dense member made of
  • the dense member is arranged for accepting a dental crown.
  • the dense member is preferably arranged for removable connection of a dental crown.
  • a first portion of the dense member is surrounded by the porous body and a second, remaining portion of said dense member projects out of the porous body.
  • the first portion and the second portion of the dense member together constitute the dense member.
  • dense bears the meaning of air-tight.
  • the porous body is made of a porous biocompatible material having a compressive strength higher than 40 MPa, preferably falling in the range between 50 MPa and 75 MPa, more preferably, between 55 MPa and 75 MPa.
  • the dense member is preferably a unitary piece. It is made of one material.
  • the dense member can be made from a powder material.
  • Said first portion of the dense member can extend along the entire length of the porous body. Said first portion can also project out of the porous body, at an end remote from said second portion.
  • the porous body comprises open interconnected pores. More preferably, the pores have a mean size in the range between 100 ⁇ m and 500 ⁇ m.
  • the porous body is made of porous titanium or a porous Ti-alloy.
  • the dense member is made of titanium or a Ti-alloy.
  • the porous body surrounding said first portion of the dense member has a thickness larger than or equal to 0.5 mm.
  • the outer size of the second, remaining portion of the dense member is larger than the outer size of said first portion of the dense member, the outer sizes measured in planes perpendicular to the longitudinal axis of the dental implant.
  • said outer size of the second portion is equal to or larger than the outer size of the porous body, the outer sizes measured in planes perpendicular to the longitudinal axis of the dental implant.
  • the dense member comprises a blind hole.
  • the blind hole preferably extends into said first portion of the dense member.
  • the blind hole can comprise thread.
  • the thread is preferably smaller than M2.
  • the blind hole can comprise a portion having a hexagonal form, which is preferably comprised in the second portion.
  • the second portion of the dense member can have a conical shape.
  • dental implants of the invention comprise at least one additional dense member.
  • the dense member is bonded to the porous body.
  • a method of manufacturing a dental implant comprising the steps of: producing a dense member from a biocompatible material, preferably a metal, producing a porous body of a porous biocompatible material, preferably a metal and bonding the porous body and the dense member.
  • the step of producing a porous body comprises using a gelcasting technique.
  • the step of producing a porous body comprises using a 3D fibre deposition technique. A rapid prototyping technique can be used as well for producing the porous body.
  • the bonding step can comprise the step of partially introducing the dense member into the porous body.
  • the bonding step comprises bringing the porous body and the dense member in intimate contact followed by a sintering step. More preferably, the bonding step comprises applying sinter-active powder to the dense member, the porous body, or both.
  • one or more of the steps of: producing a dense member, producing a porous body and the bonding step comprise applying a thermal treatment.
  • the thermal treatment can comprise a sintering step.
  • the thermal treatment preferably comprises a pre-sintering step.
  • the thermal treatment more preferably comprises a calcining step.
  • Figure 1 represents a cross-section of a dental implant of the invention, comprising a dense member acting as an implant base and a porous body.
  • Figure 2 represents different views of the implant of figure 1.
  • Figure 3 represents a block of porous titanium with dental roots fixed to it.
  • the dental implant of the invention comprises a porous body and a dense member.
  • the dense member is arranged for accommodating a dental crown.
  • the porous body ensures a strong fixation of the dental implant to the surrounding bone.
  • the dense member and the porous body are bonded to each other.
  • the porous body is made of a porous biocompatible material, preferably a metal.
  • the dense member is made of a dense biocompatible material, preferably a metal. More preferably, the porous body is made of a porous titanium or Ti-alloy, and the dense member is made of titanium or Ti-alloy.
  • the dense member is preferably made of a biocompatible metal, preferably titanium or a Ti-alloy, in particular an alloy with aluminium and vanadium (e.g. Ti- 6A1-4V) .
  • Other metals that can alternatively be used are stainless steel and alloys of cobalt, chromium and molybdenum (Co-Cr-Mo alloys) .
  • the porous body can be made of a (porous) biocompatible material as indicated hereinabove (for the dense member) .
  • the porous body can be made of a material different from the material of the dense member.
  • the dense member and the porous body are made of a same material. This is advantageous for preventing disparate thermal expansion coefficients.
  • an implant 10 is shown cross-sectionally in figure 1.
  • Dental implant 10 is a tooth root implant.
  • the implant's shape is essentially cylindrical, but other shapes for the implant are equally envisaged by the present invention and the shape of the implant of figure 1 is merely used for illustrative purposes .
  • Dental implant 10 comprises a member 11 of a dense biocompatible material (e.g. titanium or a Ti-alloy) .
  • Dental implant 10 also comprises a porous body 12 of a porous biocompatible material (e.g. porous titanium or a porous Ti-alloy) .
  • the dense member 11 and the porous body 12 are preferably manufactured separately and are bonded to each other afterwards .
  • the dense member 11 is a unitary piece and is made of one (kind of) material.
  • a first portion 112 is immersed into the porous body so as to be surrounded by the porous body 12.
  • a second portion 111 i.e. the remaining portion of the dense member 11 projects out of the porous body, at an end of the implant.
  • the second portion acts as an implant base 111, being a seat for a dental crown.
  • the first portion has the shape of a pin 112 and projects from the base 111 into the porous body. Both the base and the pin have preferably an essentially cylindrical outer shape. Other geometries are however possible.
  • the outer size (diameter) of the base 111 is larger than the outer size (diameter) of the pin 112.
  • the base 111 and the porous body 12 hence can have the same outer diameters.
  • the base 111 of the dense member has a size larger than or equal to the size of the porous body 12.
  • the implant base (111) has a conical shape .
  • the particular design of the dental implant 10 of the invention allows to prevent infections of the bone tissue without the need to provide the implant with special air-tight coatings. It is important for dental implants that the bone tissue is shielded from contact with the oral ambient (air) , as this can transmit infections to the bone.
  • the dental implant 10 is envisaged to be completely immersed in bone.
  • an upper part of the second portion (base) 111 of the dense member is envisaged to project out of the bone and to be surrounded by gingival tissue.
  • An air path towards the bone in which the implant is fixed is avoided because the porous body 12 is shielded from contact with air by the dense member 11.
  • the porous body At an end, distal from the bone, the porous body abuts against the dense member.
  • the porous body 12 is arranged to be completely immersed in the bone tissue.
  • the implant 10 may not provide any air path through the dense member 11 communicating between the oral ambient and the porous body 12. Therefore, the term dense is used here to mean air-tight.
  • the dense member does not comprise open porosity (no connected or "through” pores) .
  • Base 111 acts as a seat for a dental crown.
  • the dental crown can be fastened to the tooth root 10 according to various ways known in the art.
  • the dense member 11 comprises a blind hole
  • the fastening element can be a bolt, in which case hole 113 is provided with internal thread.
  • the thread can be e.g. M 1.6 or M 1.8.
  • Hole 113 extends from the base 111 into the pin 112.
  • An upper portion 115 of the blind hole 113 i.e. a portion of the hole 113 comprised in the second portion or implant base
  • Porous body 12 is permeable for bone cells.
  • the pores of porous body 12 should have a size so as to allow bone cell growth within the porous structure of porous body 12.
  • the growth of bone cells within a porous structure of a biocompatible material has been found to occur for pores having a size of 50 ⁇ m and more.
  • the pores of the porous body 12 are tortuous and are open interconnected pores.
  • the pore size distribution of the porous body 12 can be customized with a pore size lying in the range between 50 ⁇ m and 1500 ⁇ m, more preferably in the range between 50 ⁇ m and 1000 ⁇ m and most preferably in the range between 50 ⁇ m and 500 ⁇ m. Pore size can be measured by image analysis.
  • the mean pore size of the porous body preferably falls in the range between 100 ⁇ m and 500 ⁇ m, which is generally recognized as ideal for allowing bone in-growth. More preferably, the mean pore size of the porous core part falls in the range between 200 ⁇ m and 400 ⁇ m, most preferably in the range between 200 ⁇ m and 300 ⁇ m.
  • the porosity of the porous body 12 preferably falls in the range between 25 % and 95 % of the theoretical density (TD) , with the range between 60% and 90% TD being preferred and the range between 70% and 80% TD being more preferred. Porosity ranges as indicated constitute an optimal compromise between open structure and mechanical strength of the porous body.
  • the portion of porous body 12 which surrounds pin 112 has preferably a thickness equal to or larger than 0.5 mm for mechanical strength.
  • the diameter of the dental implant 10 can be on the order of 4 mm. It is important to note that the porous body 12 is not a coating that is applied onto the dense member 11, as is known in the prior art.
  • the porous body 12 is a bulk porous part to which a dense member is bonded.
  • the compressive strength of the porous material used for the porous body 12 is higher than 40 MPa.
  • the compressive strength is on the order of 50-60 MPa.
  • Most ideal for the porous body is to have a compressive strength between 55 MPa and 75 MPa.
  • the compressive strength is dependent on the amount of porosity. The higher the porosity, the lower the compressive strength will be.
  • a high strength of the porous body obviates the need of reinforcing the porous body with dense material, such as rods or wires. An optimal implant hence results from a trade-off between porosity and strength of the porous body.
  • the bond strength between dense member and porous body is of primary importance for a good and long- lasting implant.
  • the bond strength between dense member and porous body is higher than the strength of the material of the porous body.
  • Figure 2 shows a few views of the dental implant of figure 1.
  • a tooth root implant is of a cylindrical shape with a spherical ending 20 at the bottom.
  • Blind hole 113 is arranged for accepting a dental crown and corresponding fixation element.
  • the upper surface of the dense member forms a seat (base) for a dental crown.
  • Said upper surface preferably does not comprise projections extending above said upper surface.
  • the upper surface is preferably formed of a flat plane.
  • a second aspect of the invention is related to a method of manufacturing the dental implant of the invention.
  • porous bodies are preferably produced by a foam technique (e.g. by gel-casting or tape- casting foamed suspensions) . They can be produced by a 3D fibre deposition technique. They can be produced by a other rapid prototyping technique. These techniques allow to manufacture porous titanium or Ti-alloy.
  • a foam technique e.g. by gel-casting or tape- casting foamed suspensions
  • 3D fibre deposition technique e.g., 3D fibre deposition technique.
  • They can be produced by a other rapid prototyping technique. These techniques allow to manufacture porous titanium or Ti-alloy.
  • the porous body is preferably produced by gel-casting.
  • the mechanical properties and the porosity of the porous body can be tuned within a wide range, avoiding a large discrepancy in mechanical properties of the porous body with these of the surrounding bone .
  • the dense member 11 is produced.
  • the dense member 11 can be machined into a desired form starting from a bulk part, or can be manufactured based on a powder material which is then brought into a desired form and sintered. In the latter case, the green (not sintered) or sintered part can be machined to the required tolerances.
  • the final (sintered) dense member has preferably a density of at least 95% TD.
  • the surface pores of the dense member are smaller than 1 ⁇ m. Those pores are not open pores .
  • the porous body 12 can be in green (not sintered) , pre- sintered (having undergone a thermal treatment at e.g. 1000 0 C, but not sintered), or sintered state.
  • the dense member 11 can be in a green, a pre-sintered or a dense (in case of machining from bulk material) state.
  • the porous body 12 is prepared (machined) for accepting the dense member 11.
  • the dense member 11 is (partially) introduced into the porous body 12. Dense member 11 and porous body 12 are brought into contact and are sintered together, preferably under high vacuum
  • the sintering step is preceded by a calcination step, preferably at temperatures between 400 0 C and 600 0 C.
  • a slow heating until temperatures as indicated is preferred, such as with a heating rate smaller than or equal to 25°C per hour, more preferably smaller than or equal to 20 0 C per hour.
  • Calcination is preferably performed in vacuum (at pressures around 10 ⁇ 3 mbar, preferably between 10 ⁇ 5 mbar and 10 " mbar) and/or in an argon atmosphere.
  • the calcination step is necessary in order to burn out organic components which are still present in the green state. The burning of these organic components during sintering would otherwise produce gasses which would induce cracks and damage the structure .
  • the dense member and the porous body have to be brought in close contact.
  • the bonding between dense member and porous body can be improved by adding fine sinter-active powder (e.g. Ti-powder in case of Ti or Ti-alloys) on one or both surfaces that are brought into contact, or by sandblasting the surfaces in order to remove the Ti ⁇ 2 layer.
  • Ti-powder fine sinter-active powder
  • Ti-powder in case of Ti or Ti-alloys
  • sandblasting the surfaces in order to remove the Ti ⁇ 2 layer.
  • titanium (Ti) or a titanium alloy are used as preferred materials for the porous body and the dense member.
  • Other biocompatible metals as identified above can alternatively be used.
  • An advantage of the design of the dental implant 10 of figure 2 is that the machining to the specified tolerances of the upper surface 114 of base 11 can be deferred until the end of the manufacturing process, i.e. until after the sintering step in which porous body 12 and dense member 11 are bonded.
  • the sintering and the other thermal treatments may induce small deformations to the geometry of the dental implant.
  • final machining of the surface 114 can be accomplished readily by clamping the dental implant at the base 111. Hence there is no problem of damaging the porous body due to clamping.
  • the dense member is manufactured from Ti or Ti-6A1-4V (or another Ti alloy) and is machined following a typical design as shown in figure 1.
  • the porous Ti, Ti-6A1-4V or other Ti-alloy part is manufactured by gelcasting. A suspension is prepared using 30Og Ti (T-1147, Cerac, -325 mesh), 201 H 2 O, 6g Agar (3.18% on H 2 O), 6g Tergitol TMNlO (2% on Ti), 3g Triton (1% on Ti) and 0.36 g Ammonium alginate (0.18% on H 2 O) . It is mixed during 6 minutes at 70 0 C to obtain a fluid foam. The foam is cast into a mould and cooled down until the structure is gellified.
  • the structure is dried at atmospheric pressure and room temperature.
  • the structure is calcined (10 ⁇ 3 mbar, 25°C/hour up to 500 0 C), pre-sintered at 1000 0 C (2 hours isotherm) and sintered at 1350 0 C in a vacuum of 10 ⁇ 5 mbar (heating rate 5°C/min to 1350 0 C).
  • a block of porous Ti or a Ti alloy is obtained.
  • a dental implant can comprise more than one dense members, bonded to one and the same porous body.

Abstract

La présente invention concerne un implant dentaire (10) comprenant un élément dense unitaire (11) fabriqué à partir d'un matériau biocompatible et d'un corps poreux (12) fabriqué à partir d'un matériau biocompatible poreux et ayant une résistance à la compression supérieure à 40 MPa. Une partie (112) de l'élément dense est entourée par le corps poreux. La partie restante (111) se projetant hors du corps poreux. Le corps poreux comprend des pores interconnectés ouverts. Le matériau biocompatible est de préférence du Ti ou un alliage de Ti. L'invention concerne également un procédé de fabrication d'un implant dentaire comprenant les étapes consistant à : produire un élément dense d'un matériau biocompatible, produire un corps poreux d'un matériau biocompatible poreux et lier le corps poreux à l'élément dense. La liaison est effectuée par frittage.
PCT/EP2008/058623 2007-07-03 2008-07-03 Implant dentaire poreux WO2009004069A1 (fr)

Applications Claiming Priority (2)

Application Number Priority Date Filing Date Title
EP07111667 2007-07-03
EP07111667.7 2007-07-03

Publications (1)

Publication Number Publication Date
WO2009004069A1 true WO2009004069A1 (fr) 2009-01-08

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PCT/EP2008/058623 WO2009004069A1 (fr) 2007-07-03 2008-07-03 Implant dentaire poreux

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WO (1) WO2009004069A1 (fr)

Cited By (3)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
GB2477010A (en) * 2010-01-18 2011-07-20 Dental Devices Ltd Ab Dental implant with pores
US9254183B2 (en) 2009-06-17 2016-02-09 The University Of Liverpool Dental implant
EP4279276A1 (fr) * 2022-05-17 2023-11-22 Dentsply Implants Manufacturing GmbH Implants dentaires

Citations (4)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US4259072A (en) * 1977-04-04 1981-03-31 Kyoto Ceramic Co., Ltd. Ceramic endosseous implant
US5344457A (en) * 1986-05-19 1994-09-06 The University Of Toronto Innovations Foundation Porous surfaced implant
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US9254183B2 (en) 2009-06-17 2016-02-09 The University Of Liverpool Dental implant
GB2477010A (en) * 2010-01-18 2011-07-20 Dental Devices Ltd Ab Dental implant with pores
EP4279276A1 (fr) * 2022-05-17 2023-11-22 Dentsply Implants Manufacturing GmbH Implants dentaires
WO2023222431A1 (fr) * 2022-05-17 2023-11-23 Dentsply Sirona Inc. Implants dentaires

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