SCREW THREAD IMPLANT

Abstract: The present invention relates to a thread or oriented macroroughness for bone implants, particularly threaded dental implants, a section of said thread or roughness (i.e. the profile) comprising two flanks, a top radius R at the apex formed by the intersection of said two flanks, a bottom radius r formed at the bottom of the groove between two adjacent threads or roughnesses, said flanks forming an angle v with a plane which is perpendicular to a cross section of said thread or roughness and perpendicular to the surface of the implant body, said profile further having a height D. According to the invention the dimensions of the thread or roughness are subject to the following restrictions: for 10 DEG </= v < 35 DEG , R is greater than 0.4 x D and that, for 35 DEG </= v </= 55 DEG , R is greater than 0.2 x D. In a preferred embodiment the restrictions are: for 0.05 mm </= D </= 0.5 mm and 35 DEG </= v </= 55 DEG , the top radius R is larger than 0.2 x D but smaller than D, and in that, for 0.25 mm </= D </= 0.5 mm and 10 DEG </= v < 35 DEG , R is greater than 0.4 x D but smaller than D.

Description: SCREW THREAD IMPLANT The present invention relates to implants for implantation into bone, in particular to dental implants, said implants being provided with threads or an oriented macroroughness. The term "oriented macroroughness" should be understood to comprise elongated beads which may be continuous or not, which may be oriented along the periphery of a cross-section of the implant or not. The oriented macroroughness should have a cross-section or profile specified in the way the thread profile will be defined below and in the appended claims. Background to the invention Bone implants are normally made of rigid material, mostly of titanium, which has been shown to have an affinity for bone tissue and which has an excellent biocompability. Bone implants often have a cylindrical, threaded shape and are screwed into bore-holes in the bone tissue which may be pre-tapped or not. Under certain conditions titanium implants attain a close apposition with the bone tissue which sometimes is called osseointegration. Some factors determining the tissue response to a bone implant have been found to be the following: the biocompatibility of the implant material, the implant design, the implant surface, the status of the host bed, the surgical technique and the loading conditions. As far as the implant design is concerned, a review of the dental implant literature reveals that implants of a large number of different shapes have been used in the past. It appears as if new implant designs to a great extent have been introduced and evaluated on a trial and error basis. As the reason for an implant failure is multi-factorial, a good design may have been discarded due to for example an improper surgical technique or improper loading conditions. Titanium screw-shaped dental implants were used early in the 1960 s, those implants do not appear to have been a success; possibly due to the reasons mentioned above. Overloading has been identified as a main etiologic factor behind loss of dental implants today. If bone is subject to extreme stress it will be resorbed. Assuming that stress induced bone resorbtion is triggered off when the stresses reaches a certain level, an implant should have such a design that the maximum stresses arising in the bone, as a result of a certain load, is minimized. Screw-shaped titanium dental implants dominate the market today. Several studies have adressed the relation between macroscopic design and holding power of screws in bone. By far most of them have been made within the orthopaedic discipline and have had an experimental approach. Pullout tests were carried out in the 1 950 ' s on dog femurs and tibias using vitallium bone screws with different thread profiles. It was observed that when pulling out a freshly inserted screw, the bone threads did not strip but the screw pulled out a small cone-shaped button of compact bone. Clinical experience shows that a bone plate and its screws are sometimes avulsed from bone. This avulsion is preceded by bone resorbtion. The opinion has been expressed that such a loss of holding power is caused by mechanical factors. Continuous compression of cancellous bone by screw threads has been shown to result in hypertrophy and realignment of the trabeculae in parallell with the force. It has also been claimed that cortical bone subjected to compression retains its integrity and is not resorbed. The relevance of pull-out experiments can however be doubted. In a pull-out test acute fracture is provoked. Dental implants seldom fail by acute fracture of the supporting bone. On the contrary the fracture of the implant- bone interface is normally the end of a long process of marginal bone resorbtion. As mentioned above, the assumption that stress induced bone resorbtion is triggered off when the stresses reaches a certain level implies that an implant should be given such a design that the stress peaks arising in the bone are minimized. It has been found that a bone implant being provided with threads or an oriented macro-roughness intended to transfer loads to the bone tissue and designed in accordance with the appended main claim minimizes the stress peaks in the surrounding bone tissue. Preferred embodiments are set forth in the dependent claims. Short description of the appended drawings Fig 1 illustrates a profile of a thread or roughness according to the invention; Fig 2 illustrates the so called contact elements on the profile; Fig 3 illustrates the model used to calculate the stresses; Figs 4 and 5 show the distribution of the elements around the profile of a profile according to the invention respectively a prior art implant Fig 6 illustrates the location of the different maximal stresses. Fig 7 illstrates an alternative embodiment of the apex of the thread Detailed description of a preferred embodiment of the invention Fig 1 illustrates how the parameters describing the profile according to the invention are defined. The implant shown is a screw-shaped dental implant with a diameter of 3.5 mm. The thread profile has two thread flanks and the height of the thread is D. The top radius formed at the apex of the thread profile at the intersection of the two thread flanks is designated R, and the bottom radius between two adjacent thread profiles r. The thread flanks form an angle v with a plane which is perpendicular to a cross-section of the thread and perpendicular to the surface of the implant body. The distance L is defined as the distance between the points of intersection between the two flanks on a thread and the surface of the implant body,, the surface of the implant body being defined as the cylindrical surface touching the deepest parts of the threads. A standard prior art screw-shaped implant with an overall diameter of 3.5 mm would typically be provided with threads having a height D of about 0.35 mm, a flank angle v of 30° , a top radius R of about 0.065 mm corresponding to about 0.2xD and bottom radius of about 0.05 mm corresponding to about 0.1 5xD. As discussed above, the object of the invention is to equalize and mimimize the stress concentrations in the bone tissue which are a result of the loads on the implant in order to obtain an even stress distribution in the bone tissue so as to avoid resorption of the bone tissue because of high stress concentrations whilst avoiding low stresses that also might cause bone tissue resorption. In accordance with the invention it has been found that screw threads (macro-roughness) either having a top radius exceeding 0.4xD or a flank angle exceeding 35 ° substantially equalizes the stress distribution in the bone tissue surrounding the implant. More particularly, the top radius R should be larger than 0.2xD and smaller than D for 35 ° <_ v <_ 55 ° and 0.05 _<. D <_ 0.5 mm and larger than 0.4xD and smaller than D for 1 0° _<_ v < 35 ° and 0.25 <_ D < 0.5 mm An embodiment which at present seems most promising is an embodiment wherein 0.03 _<_ R <_ 0.05 mm, 37 ° _<_ v _<. 43° , 0.01 <, r _<_ 0.025 and 0.08 <_ D <_ 0.1 5 The following calculations illustrate this point. The calculations are performed by means of finite element analysis. The theory of elasticity according to Timoshenko is applied. The program used is Ansys revision 5.0. The object studied is a vertically oriented screw-like implant with a major diameter of 3.5 mm. This implant is built up of identical axisymmetπc elements where each element corresponds to one pitch height of a screw. The thread is modeled as a ring on each element. The profile of the thread as seen in Fig. 1 is characterized by the thread depth (D), the top radius ( ?), the flank angle [ v) , the bottom radius (r) and a straight part of the Iength S at the bottom of the thread. The Iength of the curved part of such an element is, as defined above, designated L. The straight part of the Iength (S) was set as a coefficient c multiplied with this Iength (S = c - L ) . Calculations were made for values of the thread depth of 0. 1 mm, 0.2 mm, 0.3 mm and 0.4 mm while the value of the top radius was set as a coefficient multiplied with the thread depth The value of this coefficient was set at 0 7, 0.2, 0.4, 0.6, 0.8 and 7 The flank angle was varied between 0° and 60° with an increment of 10° The bottom radius was set at 0.1 times the thread depth The coefficient c was set at 0, 0.2, 0.4, 0.8 and 1. 6 This means that a total of 4 x 6 x 7 x 5 x 1 = 840 different thread profiles are used. The implant was assumed to be infinitely long and was assumed to be completely embedded in cortical bone 1 00% bone apposition was assumed. The bone was assumed to be attached to the inner wall of an outer cylinder with a diameter of 70.5 mm, see Fig 1 Rotational symmetry was further assumed The implant and the outer cylinder were assumed to be infinitely stiff while the bone was assumed to be a continuum material, isotropic and linearly elastic with a modulus of elasticity (Young ' s modulus) of 1 50 GPa and a Poisson ' s ratio amounting to 0.3. It was assumed that the bone-implant interface was fπctionless and that only compressive forces could be transmitted between the implant and the bone These interface conditions are modeled by means of contact elements, the lines adjacent to the thread surface in Fig. 2. As is evident from fig. 2 parts of the interface does not have contact elements, the reason being that the interfacial bone at these locations in test runs had turned out to retreated from the implant An infinitely big axial load (a finite load per screw element) was applied on the infinitely long implant. With the assumptions made, the same mechanical events (stresses, strains, displacements) will occur in the bone outside all elements of which the infinitely long implant is composed Consequently it is sufficient to study one single element of the implant, including the surrounding bone, provided that proper boundary conditions can be set up wherein this element with its surrounding bone borders to the overlying and underlying counterparts. The boundary conditions which were used were that, when the load was applied, all nodes in the bone lying in the horisontal plane defined by the upper limiting surface of the element in couples underwent the same displacements as the corresponding nodes in the bone lying in the horisontal plane defined by the lower limiting surface of the same element (Fig.3) . The load, F, which was transmitted from the implant element into the bone tissue was set as a constant (k) multiplied with the Iength {L + S) of the implant element which latter was dependent upon the top radius, the flank angle, the bottom radius, the thread depth and the Iength of the straight part if any The information seeked was the maximum tensile stress, the maximum compressive stress and the maximum von Mieses stress in the bone as a function of the values of the variables used. The implant element was modeled to be completely stiff and fixed, the load F being applied at the further end of the bone as is shown in Fig. 3. The element mesh was built up parametrically. In fig . 4 and 5 the element mesh close to the implant is shown for two calculation examples called Parameter set 1 and Parameter set 2. Parameter set 1 corresponds to a thread profile according to the invention with D = 0.1 mm, v = 40° and R = 0.4xD, r = 0.1 xD whereas parameter set 2 largely corresponds to the prior art implant given above. Each element contained four nodes, the number of degrees of freedom for each node being two. The number of elements used in the mesh varied with the Iength of the straight portion at the bottom of the thread expressed by the coefficient c. With a value of the coefficient c of 0, 0.2-0.4 and 0.8-1 .6 the number of elements were 1 1 29, 1 305 and 1481 respectively. It is assumed that the screw-like structure was embedded in cortical bone. The following mean values for the ultimate stress of human cortical bone have been obtained empirically: σ u0 + = 1 33 MPa, σ u0 - = 1 93 MPa, σ u90 + = 51 MPa and σ u90 ' = 1 33 MPa where the ultimate stress in regard of tension and compression is denoted by σ^ and σ u - respectively. σ u0 and σ u90 signify ultimate stresses in parallell with the long axis of the bone respectively in a transversal plane. It is natural to allow bone stresses of different kinds in proportion to the ultimate stress. The ratios σ u0 -/σ u( and σ u90 -/σ u90 "r are according to the above 1 .45 and 2.61 respectively. In order to simplify comparisons with the maximum tensile stresses obtained the ratios σ max -/1 .45 and cr max -/2.61 are presented in the results (tables 1 -4 and 9-1 2) . However, for the calculations, the ratio σ max -/2 is the value which is of most interest. Disregarding the von Mieses stress, the combination of values of the profile parameters which minimizes the highest of the values, σ + max and σ max - 12 may be regarded as the most favourable thread design. The von Mieses stress can be expressed by the formula σ e = Vσ-r 2 + σ 2 2 + σ 3 2 - σyσ 2 - σ 2 -σ 3 - σyσ 3 where σ , σ 2 and σ 3 are the principal stresses . This formula does not take into consideration a situation where the compressive stress of a material differs from the tensile stress. An analysis of the results showed that the maximum von Mieses stress regularly was composed of one high compressive principal stress, one compressive stress of intermediate magnitude and one insignificant tensile principle stress. In order to be directly comparable with the maximum tensile stress the maximum von Mieses stress should, as the maximum compressive stress, be divided with a certain factor. It is obvious that the value of this factor lies between 1 .45 and 2.61 (it never attains the value 1 .45 nor does it attain the value 2.61 ) . For that reason the ratios o- e max H Λ5 and σ e max /2.61 are presented in the results in tables 1 -4 and 9-1 2 below. The von Miese ' s stresses are given for comparative purposes. Tables 1 - 4 show the results of the calculations. As can be seen in in the tables, the values for σ + max generally are less than 2 and for σ max -/1 .45 generally are less than 2.75 (which corresponds to a value also less than 2 for σ max -/2) within the rectangles which are drawn with dashed lines in table 1 only but are to correspond to the fields 0.05 mm _<_ D <_ 0.5 mm and 35 ° _<. v <i 55 ° , the top radius R being larger than 0.2xD but smaller than D; 0.25 mm _<. D . 0.5 mm and 1 0° _<_ < 35 ° , R being greater than 0.4xD but smaller than D. The calculation results for the parameter fields in which cr+ max < 2 ar, d σ max -/2 < 2 are illustrated with full lines in the tables. As clearly can be seen, the standard screw-shaped implant falls outside these parameter fields. Tables 5 - 8 illustrate the effect obtained by the introduction of a distance S between two adjacent threads. The part of the distance S which is staight is given as a coefficient to be multiplied with the Iength L, i. e. the distance defined above between the points where the flanks intersect the body of the implant. If the coefficient is 0 there is no positive effect of the introduction of a straight part. As can be seen, the positive effects mainly occur for small flank angles and for relatively large top radii, the parameter fields being shifted slighty to lower top radii for small flank angles as for instance can be seen by comparing tables 3 and 1 1 . Tables 9 - 12 show the minimum values for σ + max and the corresponding σ max -/1 .45 corresponding to the values given in tables 5 - 8. Some preferred embodiments are given in the following lists. 20 0.2D-1.0D 35°-55° 0.2D-1.0D 0.25-0.35 0 21 0.2D-1.0D 35°-55° 0.2D-0.8D 0.25-0.35 0-1D 22 0.2D-1.0D 35°-55° 0.2D-0.6D 0.25-0.35 1D-2D 23 0.2D-1.0D 35°-55° 0.2D-1.0D 0.35-0.50 0 24 0.2D-1.0D 35°-55° 0.2D-0.8D 0.35-0.50 0-1D 25 0.2D-1.0D 35°-55° 0.2D-0.6D 0.35-0.50 1D-2D 67 0.6D-1D 10°-35° 0.6D-1D 0.05-0.15 68 0.6D-1D 10°-35° 0.6D-0.8D 0.05-0.15 69 0.6D-1D 10°-35° 0.6D-1D 0.15-0.25 70 0.6D-1D 10°-35° 0.6D-0.8D 0.15-0.25 71 0.6D-1D 10°-35° 0.6D-1D 0.25-0.35 72 0.6D-1D 10°-35° 0.6D-0.8D 0.25-0.35 73 0.6D-1D 10°-35° 0.6D-1D 0.35-0.50 74 0.6D-1D 10°-35° 0.6D-0.8D 0.35-0.50 75 0.4D-0.6D 10°-35° < 0.85R 0.05-0.15 76 0.4D-0.6D 10°-35° < 0.85R 0.05-0.15 77 0.4D-0.6D 10°-35° < 0.85R 0.05-0.15 10°-35° < 0.85R 0.15-0.25 10°-35° < 0.85R 0.15-0.25 10°-35° < 0.85R 0.15-0.25 10°-35° < 0.85R 0.25-0.35 10°-35° < 0.85R 0.25-0.35 10°-35° < 0.85R 0.25-0.35 10°-35° < 0.85R 0.35-0.50 10°-35° < 0.85R 0.35-0.50 10°-35° < 0.85R 0.35-0.50 10°-35° < 0.85R 0.05-0.15 10°-35° < 0.85R 0.05-0.15 10°-35° < 0.85R 0.05-0.15 10°-35° < 0.85R 0.15-0.25 0 10°-35° < 0.85R 0.15-0.25 0-1D 10°-35° < 0.85R 0.15-0.25 1 D-2D 10°-35° < 0.85R 0.25-0.35 0 10°-35° < 0.85R 0.25-0.35 0-1D 10°-35° < 0.85R 0.25-0.35 1 D-2D 10°-35° < 0.85R 0.35-0.50 0 10°-35° < 0.85R 0.35-0.50 0-1D 10°-35° < 0.85R 0.35-0.50 1 D-2D In preferred embodiments the distance between adjacent threads is smaller than 3D, preferably smaller than 2D. In a further preferred embodiment the threads or macroroughness is combined with a microroughness having a pore size of 2 μ to 20 μ, preferably 2 μ to 10 /y. By such a combination of macroscopic and microscopic interlocking also implant surfaces which, if smooth, would not have interacted mechanically with the bone will take part in the transmission of the loads to the bone. This will further tend to smooth away the stress concentrations which inevitably will arise in the bone tissue due to the macroscopic interlocking and which the invention is to alleviate, thus further enhancing the effect the invention is intended to achieve. The microscopic roughness may for instance be made by blasting or chemical etching, but is preferably made by blasting with particles of Ti0 2 . Table 1 : Thread depth = 0. 1 mm. No straight part at the bottom of the thread. The value of σ + max for different combinations of flank angle and top radius as a result of a standard load per unit Iength of the implant segment. In the cases when σ max /1 .45 , σ max /2.61 , σ β max /1 .45 or σ β.max /2.61 exceed σ + max these values are also given. The value of the top radius expressed as a coefficient multiplied with the thread depth (D) . Table 2: Thread depth = 0.2 mm. No straight part at the bottom of the thread. The value of σ + max for different combinations of flank angle and top radius as a result of a standard load per unit Iength of the implant segment. In the cases when σ max /1 .45 , σ max /2.61 , α β . max /1 .45 or σ β max /2.61 exceed σ + max these values are also given. The value of the top radius expressed as a coefficient multiplied with the thread depth (D) . Table 3: Thread depth = 0.3 mm. No straight part at the bottom of the thread. The value of t7 + max for different combinations of flank angle and top radius as a result of a standard load per unit Iength of the implant segment. In the cases when σ max /1 .45 , σ max /2.61 , σ„ .max /1 .45 or σ β max /2.61 exceed σ ax these values are also given. The value of the top radius expressed as a coefficient multiplied with the thread depth (D). Table 4: Thread depth = 0.4 mm. No straight part at the bottom of the thread. The value of tτ + max for different combinations of flank angle and top radius as a result of a standard load per unit Iength of the implant segment. In the cases when t7 max /1 .45 , σ max /2.61 , σ β max /1 .45 or σ β.max /2.61 exceed σ + max these values are also given. The value of the top radius expressed as a coefficient multiplied with the thread depth (D) . T o p r a d i u s 0.2xD mm 0.4xD mm 0.6xD mm 0.8xDmm D mm 2.22 2.26 2.34 2.26 2.06 2.38 2.03 2.95 2.35 238 2.01 1.82 1.70 1.63 3.92 3.53 3.54 3.74 3.93 1.97 2.08 2.18 3.20 2.68 2.70 2.83 2.97 1.65 Table 5: Thread depth = 0.1 mm. The lengths of the straight part of S at the bottom of the thread which minimize the maximum compressive stress, the maximum tensile stress and the maximum von Mieses stress respectively. This Iength is expressed as a coefficient c which is to be multiplied with the Iength of the curved part (1) of the thread (Fig. 1 ) . The table lists the values of this coefficient. Table 6: Thread depth = 0.2 mm. The lengths of the straight part of S at the bottom of the thread which minimize the maximum compressive stress, the maximum tensile stress and the maximum von Mieses stress respectively. This Iength is expressed as a coefficient c which is to be multiplied with the Iength of the curved part (L) of the thread (Fig. 1 ) . The table lists the values of this coefficient. Table 7: Thread depth = 0.3 mm. The lengths of the straight part of S at the bottom of the thread which minimize the maximum compressive stress, the maximum tensile stress and the maximum von Mieses stress respectively. This Iength is expressed as a coefficient c which is to be multiplied with the Iength of the curved part (Z.) of the thread (Fig. 1 ) . The table lists the values of this coefficient. Table 8: Thread depth = 0.4 mm. The lengths of the straight part of S at the bottom of the thread which minimize the maximum compressive stress, the maximum tensile stress and the maximum von Mieses stress respectively. This Iength is expressed as a coefficient c which is to be multiplied with the Iength of the curved part (L) of the thread (Fig. 1 ) . The table lists the values of this coefficient. T o p r a d i u s mm 0.2xD mm 0.4xD mm 0.6xD mm 0.8xDmm lxD mm 8 0.2 0.4 0.8 0.2 0 0.2 0 0 0 0 0.2 0.4 0.8 0.8 0 0.2 0.4 0.2 0 0 0 0 0 0 0 0 0 0 0 0 0 0 0 0 0 0 0 0 0 0 0 0 0 0 0 0 0 0 0 0 0 0 0 0 0 0 0 0 0 0 0 0 0 0 Table 9: Thread depth = 0.1 mm. The lowest of the values of tτ + max for different lengths of the straight part at the bottom of the thread (c = 0, 0.2, 0.4, 0.8, 1 .6) for different combinations of flank angle and top radius as a result of a standard load per unit Iength of the implant segment. In the cases when σ ' max /1 .45 , σ max /2.61 , σ„ .max /1 .45 or σ^/2.61 exceed σ*^ these values are also given (for the combination of parameters which minimized σ*^. The value of the top radius expressed as a coefficient multiplied with the thread depth (D). Table 10: Thread depth = 0.2 mm. The lowest of the values of σ + max for different lengths of the straight part at the bottom of the thread (c = 0, 0.2, 0.4, 0.8, 1 .6) for different combinations of flank angle and top radius as a result of a standard load per unit Iength of the implant segment, in the cases when σ max /1 .45 , σ mβx /2.61 , σ β max /1 .45 or c7.. max /2.61 exceed σ + max these values are also given (for the combination of parameters which minimized σ+ ma χ)- The value of the top radius expressed as a coefficient multiplied with the thread depth (D). Table 11 : Thread depth = 0.3 mm. The lowest of the values of σ + max for different lengths of the straight part at the bottom of the thread (c = 0, 0.2, 0.4, 0.8, 1 .6) for different combinations of flank angle and top radius as a result of a standard load per unit Iength of the implant segment. In the cases when σ max /1 .45 , σ max /2.61 , σ„. max /1 .45 or σ β . max /2.61 exceed σ + max these values are also given (for the combination of parameters which minimized σ + m . The value of the top radius expressed as a coefficient multiplied with the thread depth (D) . Table 12: Thread depth = 0.4 mm. The lowest of the values of σ + max for different lengths of the straight part at the bottom of the thread (c = 0, 0.2, 0.4, 0.8, 1 .6) for different combinations of flank angle and top radius as a result of a standard load per unit Iength of the implant segment. In the cases when σ max /1 .45 , σ max /2.61 , σ β . mϊX /1 .45 or σ β max /2.61 exceed σ + max these values are also given (for the combination of parameters which minimized σ + maκ ). The value of the top radius expressed as a coefficient multiplied with the thread depth (D). The radius R has been constant and has been real in the above examples . In a preferred embodiment, illustrated in Fig 7, the top radius R at the apex is imaginary and defines a the transition point P1 between the straight flank and the curved apex, a first tangent through P1 being directed along said flank, as well as a crest point P2 on the apex in which a second tangent to the curved part is parallel to the longitudinal direction of the implant. In this embodiment the curved apex has the shape of curved part originating in said points P1 and P2 and has tangents in said points coinciding with said first and second tangents, and has a radius of curvature R1 . The radius R1 may for instance increase from a value R mιn to a value R max or may increase from a value R mm to a value R max , then decreasing to a value R min . R mιn should preferably be greater than 0.01 mm and the relationship R m „/R„, n preferably should be greater than 3. One special case of this embodiment is of course that said radius of curvature R1 is constant and equal to said imaginary radius R, the apex thus having a part circular shape with the radius R. The following calculations illustrate the effect of the variable radius of curvature. Uniform top radius = 0.04 mm Flank angle: 40 ° Thread depth: 0.1 mm Bottom radius: 0.01 mm Maximum tensile stress: 1 .784Mpa Variable radius of curvature of the thread top-small continuous variations: Flank angle: 40 ° Thread depth: 0, 1 mm Top radius: R mιn = 0,025mm, R maκ = 0.055mm Bottom radius: 0.01 mm Maximum tensile stress: 1 .750l\Λpa Variable radius of curvature of the thread top - bigger continuous variations: Flank angle: 40 ° Thread depth: 0, 1 mm Top radius: R mm = 0.001 Omm, R max = 0.069mm Bottom radius: 0.01 mm Maximum tensile stress: 1 .721 Mpa As can be seen in the above, there is some improvement with a variable radius of curvature. The invention of course can be varied in many ways within the scope of the appended claims. It should for instance be noted that the two flank angles of the thread or roughness not necessarily have to be identical even if this is a preferred embodiment. In some applications the angles may be different although both are within the ranges specified, in another applications it may be sufficient that the flank being the most heavily loaded has a flank angle within the ranges specified. The same is valid for the top radius which in similarity may have different values on the respective sides of the thread, both values or only one value being within the ranges specified.

Claims: CLAIMS 1 . Thread or oriented macroroughness for bone implants, s particularly threaded dental implants, a section of said thread or roughness (i.e. the profile) comprising two flanks and a curved apex, an imaginary top radius R at the apex formed by the intersection of said two flanks defining the transition point P1 between the straight flank and the curved apex, a first tangent through P1 being directed along said flank, as well as a crest o point P2 on the apex in which a second tangent to the curved part is parallel to the longitudinal direction of the implant, a curved part originating in said points P1 and P2 and having tangents in said points coinciding with said first and second tangents, forming said curved apex, having a radius of curvature R1 , a bottom Iength S, a bottom radius r formed at the bottom s of the groove between two adjacent threads or roughnesses, said flanks forming an angle v with a plane which is perpendicular to the cross-section of said thread or roughness and perpendicular to the surface of the implant body, said profile further having a height D, characterized in that, for 1 0° _<. v < 35 °, R is greater than 0.4xD and that, for 35 ° <_ v _< . 55 °, R is o greater than 0.2xD. 2. Thread or oriented macroroughness according to claim 1 , characterized in that for 0.1 5 <_ D _<. 0.25 mm, 1 0° <_ v < 35 ° and 0.5D <. S <_ 2D, R is greater than 0.5D but smaller than 0.7D. 3. Thread or oriented macroroughness according to claim 1 , characterized in that, for 0.05 mm _<_ D <_ 0.5 mm and 35 ° _<_ v <_ 55 ° , the top radius R is larger than 0.2xD but smaller than D, and in that, for 0.25 mm _<_ D <. 0.5 mm and 1 0° <_ v < 35 ° , R is greater than 0.4xD but smaller than D. 4. Thread or oriented macroroughness according to claim 3, 0 characterized in that, for 0.25 mm _<. D _<_ 0.5 mm and 1 0° _<. v < 35 ° , R is greater than 0.6xD but smaller than D. 5. Thread or oriented macroroughness according to claim 3, characterized in that 0.05 <_ D _< . 0.25 mm for 35 ° _< . v _<_ 55 ° . 6. Thread or oriented macroroughness according to claim 5, characterized in that 0.05 _<_ D _<_ 0.1 5 mm for 35 ° _<_ v j<_ 55 ° . 5 7. Thread or oriented macroroughness according to claim 6, characterized in that 0.05 _<_ D .<_ 0.1 mm for 35 ° v 55 ° . 8. Thread or oriented macroroughness according to claim 1 characterized in that 0.03 _<. R _<. 0.05 mm, 37 ° _< v <_ 43 °, 0.01 <_ r <_ 0.025 and 0.08 _< D <_ 0.1 5. o 9. Thread or oriented macroroughness according to any one of the preceding claims characterized in that the distance between two adjacent threads, crest to crest, is smaller than 3D, preferably smaller than 2D. 1 0. Thread or oriented macroroughness according to any one of the preceding claims characterized in that said radius of curvature R1 is s constant and equal to said imaginary radius R. 1 1 . Thread or oriented macroroughness according to any one of the claims 1 - 9, characterized in that said radius of curvature R1 varies between a minimum value R mιn and a maximum value R max . 1 2. Thread or oriented macroroughness according to claim 1 1 , o characterized in that the relationship R max /R mιn is greater than 3. 1 3. Thread or oriented macroroughness according to claim 1 1 or 1 2, characterized in that R mm is greater than 0.01 mm. 1 4. Thread or oriented macroroughness according to any one of the preceding claims characterized in that said thread profile is symmetric. 5 1 5. Thread or oriented macroroughness according to any one of claims 1 - 1 3 characterized in that said radius R or R1 is located on one first thread flank, the second thread flank being provided with another radius at the apex of the thread which may be different from said said first radius or not and which has one tangent coinciding with said second flank 0 and one tangent through P2 which is parallel with the longitudinal axis of the implant. 1 6. Thread or oriented macroroughness according to any one of the preceding claims, characterized in that said threads or macroroughness is combined with a superimposed microroughness having a pore size of 2 μ to 20 μ, preferably 2 μ to 1 0 μ. 1 7. Implant characterized in that said implant at least partly is provided with threads or oriented macroroughness according to any one of the preceding claims. 1 8. Implant according to claim 1 1 , characterized in that said implant is provided with at least one additional, different thread.

Inventors: HANSSON STIG, HANSSON, STIG
Applicants: ASTRA AB, HANSSON STIG, ASTRA AKTIEBOLAG, HANSSON, STIG
Application year: 1997
Main classification: A61C8
IPC codes: A61B17, A61C8, A61F2