US20080261178A1

US20080261178A1 - Process for providing a topography to the surface of a dental implant

Info

Publication number: US20080261178A1
Application number: US12/105,595
Authority: US
Inventors: Frank Homann; Philippe Habersetzer
Original assignee: Straumann Holding AG
Current assignee: Straumann Holding AG
Priority date: 2007-04-19
Filing date: 2008-04-18
Publication date: 2008-10-23
Also published as: EP1982670B1; JP2008264545A; EP1982670A1; KR101539229B1; US10595967B2; US20200246115A1; JP5360642B2; AU2008201488B2; CN101332130A; US20150056574A1; US20130177876A1; KR20080094625A; DE602007002280D1; AU2008201488A1; CA2628911A1; ATE441378T1; ZA200802741B; ES2331663T3; CN101332130B

Abstract

A process for providing a topography to the surface of a dental implant, said surface being made of a ceramic material. At least a part of the surface of the dental implant is etched with an etching solution comprising hydrofluoric acid at a temperature of at least 70° C. Thereby, discrete grains or agglomerates of grains are removed from the ceramic material.

Description

FIELD OF THE INVENTION

The present invention relates to a process for providing a topography to the surface of a dental implant, to a dental implant obtainable by this process, and to the use of a solution comprising hydrofluoric acid for etching the ceramic surface of a dental implant.

BACKGROUND

Dental implants which are inserted into the jawbone, for example for the attachment of artificial teeth, have been successfully used for more than a decade. The major part of the dental implants currently used consist of titanium, since titanium is biocompatible, has a sufficiently low elastic modulus and a relatively high strength.
Apart from its biocompatibility and its mechanical properties, the osteointegrative properties of a dental implant are of major importance. A good osteointegration means that the implant, after reaching a primary stability by screwing it into the bone, safely ossifies within a short healing time so that a permanent bond between implant and bone is guaranteed.
When using titanium as the implant material, osteointegrative properties can be reached by suitable treatment of the implant's surface. To this end, the titanium surface has conventionally been mechanically roughened by a subtractive removing process, e.g. sandblasting, grinding or etching. Alternatively, the surface has been subjected to additive processes, e.g. coating with a textured surface.
U.S. Pat. No. 6,174,167 discloses implants having a surface for bone-tissue apposition, said surface being obtained by machining, application of a textured surface or blasting with particles. It also discloses acid etching, applying growth factor, protein or other materials that promote, enhance and/or maintain bone-tissue growth and/or apposition. The implant is made from a biocompatible material, preferably from titanium or an alloy thereof.
DE-A-4012731 describes a process for producing an implant made of titanium employing spark erosive techniques in order to provide a desired roughness to the implant's surface.
Osteointegration has turned out to be particularly efficient if mechanical roughening of the implant's surface is combined with subsequent etching of the roughened surface, as is for example described in Li et al., J. Biomed. Mater. Res. 2002, 60 (2), pages 325-332.
Similarly, EP-A-0388576 describes the treatment of a titanium implant by a blasting process and subsequent etching with a reducing acid, such as HF, HCl or HCl with H₂SO₄.
Conventional titanium implants which are subjected to such a combined treatment safely ossify within a healing time of about 3 to 4 months after insertion into the bone, thereby providing a permanent bond between the dental implant and the bone.
From an aesthetic point of view, titanium implants have, however, the disadvantage that they are dark in color and therefore mismatch with the natural tooth color.
In contrast, the color of ceramic materials can be closely matched to the natural tooth color. Efforts have thus been made to provide dental implants of which at least the parts that are visible after insertion are made of a ceramic material.
WO-A-0134056 refers to a dental implant consisting of an insertion component which can be fitted in the jawbone and a support component which after implantation protrudes beyond the jawbone. The document discloses that at least the support component is made of zirconia ceramic.
DE-A-19530981 refers to a prefabricated implant supra construction using a tooth-colored zirconia ceramic attached to titanium implants.
Despite their advantageous properties with regard to the color, the use of ceramic materials for dental implants have been limited by their low fatigue stability and thereby by their tendency to crack.
A ceramic material having a high mechanical strength is disclosed in U.S. Pat. No. 6,165,925. U.S. Pat. No. 6,165,925 relates to an yttrium-stabilized zirconium oxide (zirconia) in predominantly tetragonal form for the production of a sintered semi-finished article as a starting material for the manufacture of a prosthesis.
In order to achieve a sufficient mechanical stability, the zirconia ceramic disclosed in U.S. Pat. No. 6,165,925 must be highly dense. The surface of said highly dense zirconia ceramic is clean cut, extremely hard and has essentially no porosity. A dental implant made of such a zirconia ceramic is thus bio-inert and has only weak osteointegrative properties. Conventional techniques for treating the implant's surface in order to achieve a osteointegrative surface have failed, mostly due to the extreme hardness of the material.
Other techniques for providing an osteointegrative ceramic surface have been suggested:
WO-A-2005/027771 relates to a process for preparing a dental installation in which a dispersion is applied on a substrate having a first porosity, said dispersion forming upon sintering a ceramic layer with a second porosity.
EP-A-0870478 relates to a dental retention element having a core of a high-strength material such as zirconia, said core being coated with a ceramic material which can be chemically and/or mechanically processed.
The composite structures disclosed in WO-A-2005/027771 and EP-A-0870478 have the disadvantage that the ceramic coating is easily chipped off.
Alternatively, a treatment comprising abrasive blasting and acid-etching for providing osteointegrative properties to the ceramic implant's surface has been suggested by EP-B-1450722. EP-B-1450722 relates to a dental implant made of zirconia ceramic which after abrasive blasting is subjected to a treatment using phosphoric acid, sulphuric acid, hydrochloric acid or mixtures thereof.
However, the level of osteointegration of such zirconia implants revealed by their removal torque values have been shown to be lower compared to the conventionally used titanium implants. Although after implantation, an initial increase of the removal torque values of the zirconia implants could be measured, a decrease was observed after a certain period. Corresponding studies are discussed in Gudehus, H. T.; Untersuchung des Einwachsverhaltens von Zirkoniumdioxid-Implantaten in die Kieferknochenstruktur—Eine experimentelle Studie am Miniaturschwein, Dissertation Ludwig-Maximilians-Universitat Munchen, 2006.
Lately, Takemoto M. et al. (J. Biomed. Mater. Res., 2006, 78A, pages 693-701) have published a report on the bone-bonding ability of a hydroxyapatite coated zirconia-alumina composite which prior to the coating with the hydroxyapatite is treated at 60° C. in hydrofluoric acid, then washed and heat-treated at 1300° C. The process requires a specific and sophisticated apparatus for the heat-treatment of the implant.

SUMMARY OF THE INVENTION

The present invention provides a simple and straightforward process for providing highly osteointegrative properties to the ceramic surface of a dental implant.
The invention is based on the surprising finding that by etching a dental implant's ceramic surface with an etching solution comprising hydrofluoric acid at a temperature of at least 70° C., discrete grains or agglomerates of grains are removed from the ceramic material. By this removal, a surface having recesses and cavities is formed. As the etching solution penetrates deeper into the ceramic material, further grains or grain agglomerates are removed and, thus, further recesses and cavities are formed.
Thereby, a highly osteointegrative topography is provided to the dental implant's ceramic surface.
Without wanting to be bound by the theory, it is assumed that one reason for the improved osteointegrative properties is the augmentation of the surface area resulting from the removal of discrete grains or agglomerates grains from the ceramic material.
Due to its highly osteointegrative surface topography, the dental implant obtainable by the process of the present invention fastly integrates into the bone. This is further substantiated by studies on the cell response to the dental implant of the present invention, revealing a much higher expression of differentiation factors which are known to play a role in the bone formation process.
As the surface of the dental implant is made of a ceramic material, it allows the color of at least its mounting part to be approximated to the color of a natural tooth. Thus, completely natural looking ceramic reconstructions can be prepared.
The process of the present invention is very simple and allows highly osteointegrative ceramic dental implants to be produced in a fast, efficient and readily industrially applicable manner.

BRIEF DESCRIPTION OF THE DRAWINGS

FIG. 1 is an idealized Abbott curve from which the 2D specific Core Roughness Depth R_k, the reduced Peak Height R_pkand the reduced Groove Depth R_ckare derived;

FIG. 2 is a graphical representation of different profiles defined by different S_kand S_skvalues;

FIG. 3 is an SEM picture of the surface resulting from the treatment according to Example 1 in two different magnification levels, the scale given in the SEM picture corresponding to 20 μm (above) and 5 μm (below), respectively;

FIG. 4 is an SEM picture of the surface resulting from the treatment according to Example 2 in two different magnification levels, the scale given in the SEM picture corresponding to 20 μm (above) and 5 μm (below), respectively;

FIG. 5 is an SEM picture of the surface resulting from the treatment according to Example 3 in two different magnification levels, the scale given in the SEM picture corresponding to 20 μm (above) and 5 μm (below) respectively;

FIG. 6 is an SEM picture of the surface resulting from the treatment according to Example 4 in two different magnification levels, the scale given in the SEM picture corresponding to 20 μm (above) and 5 μm (below), respectively;

FIG. 7 is an SEM picture of the surface resulting from the treatment according to Example 5 in two different magnification levels, the scale given in the SEM picture corresponding to 20 μm (above) and 5 μm (below), respectively;

FIG. 8 is an SEM picture of the surface resulting from the treatment according to Example 6 in two different magnification levels, the scale given in the SEM picture corresponding to 20 μm (above) and 5 μm (below), respectively;

FIG. 9 is an SEM picture of the surface resulting from the treatment according to Example 7 in two different magnification levels, the scale given in the SEM picture corresponding to 20 μm (above) and 5 μm (below), respectively;

FIG. 10 is an SEM picture of the surface according to Example 8 in two different magnification levels, the scale given in the SEM picture corresponding to 50 μm (above) and 20 μm (below), respectively;

FIG. 11 is an SEM picture of the surface according to Example 9 in two different magnification levels, the scale given in the SEM picture corresponding to 50 μm (above) and 20 μm (below), respectively; and

FIG. 12 is an SEM picture of the surface obtained in a is further example, the scale given in the SEM picture corresponding to 5 μm.

DETAILED DESCRIPTION

The process of the present invention allows the surface of any part of the dental implant, such as the bone contacting region, the soft tissue contacting region or both, to be treated independently. Thus, any part of the dental implant's surface can be provided selectively with the osteointegrative topography. Likewise, the whole surface of the dental implant can be treated by the process of the present invention.
The topography obtainable by the process of the present invention can be defined by 3D specific values.
Although there is no standard for the characterization of the topography with 3D specific values, these values can be derived by a simple devolvement from the respective 2D specific values.
For two dimensions, an extra procedure for filtering with suppression of the depth of roughness leads to the roughness profile according to DIN 4776. The definitions therein can directly be transformed into three dimensions.
In particular, the topography can be defined by the 3D specific Kernal Roughness Depth (or Core Roughness Depth) S_k, which, as the 2D specific Core Roughness Depth R_k, can be derived from the so-called Material Ratio Curve (also known as “Abbott curve”).
The Abbott curve represents the height distribution of the surface's material. It is a cumulative function of the material portion of the surface at a particular depth below the highest peak of the surface. In other words, the Abbott curve describes the increase of the material portion of the surface with increasing depth of the roughness profile. At the highest peak, the material portion is 0%, while at the deepest recess (or “valley”) the material portion is 100%. The minimal secant slope, i.e. a defined line of best fit, separates the Abbott curve into the three following ranges:
a) the Core Roughness Depth S_k[μm], i.e. the depth of the roughness core profile,
b) the reduced Peak Height S_pk[μm], i.e. the averaged height of the peaks sticking out of the core range, and
c) the reduced Groove Depth S_vk[μm], i.e. the averaged depth of the grooves sticking out of the core range.
The concept of how these values are derived from the Abbott curve are well known to the person skilled in the art. It is further illustrated in FIG. 1 showing an idealized Abbott curve from which the 2D specific Core Roughness Depth R_k, the reduced Peak Height R_pkand the reduced Groove Depth R_vkare derived. These parameters can directly be transformed to the 3D specific Core Roughness Depth S_k, reduced Peak Height S_pkand reduced Groove Depth S_vk
As shown in FIG. 1, the Core Roughness Depth R_kor, in three dimensions, S_kcorresponds to the vertical distance between the left and right intercepts of the line through the ends of the minimal secant slope window of the Abbott curve. The location of the minimal secant slope window can be determined by shifting it along the Abbott curve until the slope between the two intersection points becomes minimal.
The topography can further be specified by the Skewness S_sk. The Skewness measures the symmetry of the variation of the surface about its mean plane. A Gaussian surface, having a symmetrical shape for the height distribution, has a Skewness of 0. A surface with a predominant plateau and deep recesses will tend to have a negative Skewness, whereas a surface having a number of peaks above average will tend to have a positive Skewness.
For a profile in two dimensions, the 2D specific Skewness R_skis according to DIN EN ISO 4287 defined by the following formula:
$R_{sk} = \frac{1}{R_{q}^{3}} \cdot \frac{1}{N} \cdot \sum_{n = 1}^{N} {(z_{n} - \overline{z})}^{3}$
where z_nis the height or depth of the respective peak or valley, respectively, z is the mean height and R_qis the root-mean-square deviation of the surface.
For determining the Skewness S_skof the topography in three dimensions, the formula is transformed as follows:
$S_{sk} = \frac{1}{S_{q}^{3}} \cdot \frac{1}{M \cdot N} \cdot \sum_{m = 1}^{M} \sum_{n = 1}^{N} {(z_{n} - \overline{z})}^{3}$
where S_qis the root-mean-square deviation of the surface according to the following formula:
$S_{q} = \sqrt{\frac{1}{M \cdot N} \cdot \sum_{m = 1}^{M} \sum_{n = 1}^{N} {(z_{n} - \overline{z})}^{2}}$
A detailed description how the S_kand S_skvalues are determined in practice is given below under item 2 of the Examples.
A graphical representation of different profiles defined by different S_kand S_skvalues is given in the table shown in FIG. 2. In this table, the profiles shown in the first line have a positive Skewness S_sk, the profiles shown in the second line have a Skewness S_skof about 0 and the profiles shown in the third line have a negative Skewness S_sk. The profiles shown in the left column have a (low) Core Roughness Depth S_kof less than 1 μm and the profiles shown in the right column have a (high) Core Roughness Depth S_kof more than 1 μm.
According to one embodiment, the topography obtainable by the process of the present invention has generally a Core Roughness Depth S_kof less than 1 μm. Preferably, the Core Roughness Depth S_kis between 0.3 μm and 1 μm, more preferably between 0.4 μm and 1 μm.
As can be seen from column 1 of FIG. 2, the main portion of such a topography is in the range of the extreme values; either the high peaks or the deep scratches are dominating over the core level. A dental implant having such a surface topography has been found to be highly osteointegrative.
The Skewness S_skof the topography obtained preferably falls within the following equation (I):
S _sk ≦−m*S _k (I)
whereby m is from 0 to 1, preferably about 0.25, more preferably about 0.1.
More preferably, the Skewness S_skis less than 0, meaning that deep grooves in the topography are dominating.
It has been found that asymmetric topographies with deep grooves are highly osteointegrative, and that thereby the absolute roughness values (S_a, R_max, etc.) for example referred to in EP-B-1450722 are irrelevant.
The S_kand S_skvalues of the topography obtainable by one embodiment of the present invention strongly differs from the topographies of commercially available implants, the osteointegrative properties of which have been studied in detail. It is thus highly surprising that the completely different topography obtainable according to the process of the present invention is osteointegrative.
According to a preferred embodiment of the present invention, the ceramic material has an average grain size from about 0.1 μm to about 0.6 μm. Treatment of this material according to the process of the present invention leads to a surface topography with particularly high osteointegrative properties.
The term “ceramic material” encompasses any type of ceramic such as ceramics based on zirconia, alumina, silica or mixtures thereof, optionally comprising further constituents. Preferably, the ceramic material is based on zirconia, more preferably yttria-stabilized zirconia. Apart from the desired osteointegrative properties obtained, this material has the further advantage of a high fracture toughness and bending strength.
An example of an yttria-stabilized zirconia ceramic is described by the international standards ASTM F 1873 and ISO 13356, specifying the characteristics of, and a corresponding test method for, a biocompatible and biostable ceramic bone-substitute material based on yttria-stabilized tetragonal zirconia (yttria tetragonal zirconia polycrystals, Y-TZP) for use as material for surgical implants.
Specific examples of an yttria-stabilized zirconia are ZrO₂-TZP/TZP-A Bio-HIP® (ZrO₂) Bioceramic available from Metoxit AG, Switzerland, and ZIOLOX® available from CeramTec AG, Plochingen, Germany. Both materials offer a particularly high mechanical stability and strength, in particular when prepared by hot isostatic pressing or by sintering with subsequent hot isostatic densification. A detailed description of the ZrO₂-TZP/TZP-A Bio-HIP® (ZrO₂) Bioceramic is given in U.S. Pat. No. 6,165,925, the disclosure of which is incorporated herein by reference.
In particular, the composition of the yttria-stabilized zirconia comprises about 4.5 to about 5.5 weight-% of Y₂O₃and less than about 5 weight-% of HfO₂, the total amount of ZrO₂, Y₂O₃and HfO₂being more than about 99.0 weight-%.
Coprecipitation is the most common method to distribute the yttria homogenously in the zirconia matrix. The stabilizing amount of yttria is added to the purified zirconium salt as an yttrium salt before the precipitation and calcination process is started, as described by Haberko K., Ciesla A., and Pron A., Ceramurgia Int.1 (1975) 111. Alternatively, the zirconia can be stabilized by yttria-coating. This initiates a radial gradient of yttria concentration in the powder, that is distributed in it kinetically during sintering, as described by Burger, W., Richter, H. G., Piconi, C., Vatteroni, R., Cittadini, A., Boccalari, M., New Y-TZP powders for medical grade zirconia. J Mater. Sci. Mater. Med. 1997, 8 (2), 113-118.
It is further preferred that prior to the etching according to the present invention a macroscopic roughness is provided to the ceramic surface of the dental implant by sandblasting, milling and/or injection molding techniques. Thus, a dental implant having especially good osteointegrative properties is obtained.
Sandblasting is generally performed using a pressure of 1 to 12 bar, preferably 4 to 10 bar. A considerably improved macroscopic roughness is achieved when using a hard material such as boron carbide. In a further preferred embodiment, Al₂O₃particles having an average diameter of 250 to 500 μm are used.
As an alternative to sandblasting, the macroscopic roughness can also be provided by injection molding techniques. Injection molding techniques are known to a skilled person and are for example described in US-A-2004/0029075, the content of which is incorporated herein by reference. According to these techniques, casting molds with cavities are used, said cavities corresponding to the peaks of the molded implant's macroscopic roughness. The cavities of the casting mold are slightly greater in proportion than the peaks to be provided, taking into account the shrinking of the ceramic after injection molding. The casting molds themselves may be treated by sand blasting, anodization, laser and/or by erosion techniques in order to produce the cavities or the structured surface on the inner surface of the molds.
Injection molding techniques have the advantage that during this process no phase transformation occurs in the ceramic material which has therefore improved mechanical properties. Furthermore, the manufacture of the dental implant by injection molding circumvents the additional step of providing the macroscopic roughness and is thus quick. In addition, it has an excellent reproducibility and there is no contamination with particles from sandblasting.
It is also envisioned to provide a macroscopic roughness by milling or grinding. For this purpose, milling or grinding devices having a defined grain size are used in order to guarantee a desired macroscopic roughness of the surface.
According to a further preferred embodiment of the present invention, the etching solution comprises at least 50 vol.-%, more preferably at least 80 vol.-% of concentrated hydrofluoric acid. Etching with this etching solution leads after a relatively short etching time to a uniform topography over the whole surface treated.
The etching solution can further comprise at least one compound selected from the group consisting of phosphoric acid, nitric acid, ammonium fluoride, sulfuric acid, hydrogen peroxide and bromic acid. Preferably, the etching solution comprises sulfuric acid in an amount of 50 vol.-% at most.
The etching time depends highly on the etching solution used and typically ranges from about 10 seconds to about 120 minutes. The etching time is preferably about 1 minute to about 60 minutes, more preferably about 20 minutes to about 40 minutes and most preferably about 30 minutes.
Preferably, the etching is followed by washing the dental implant, the washing comprising the subsequent step or the subsequent steps of
c) rinsing the dental implant with a NaCl solution and/or
d) rinsing the dental implant with deionized water.
The performance of the washing step can be improved by using ultrasound. Thereby, grains, grain agglomerates or reaction products which loosely adhere to the surface are effectively removed.
Apart from the process described, the present invention also relates to a dental implant obtainable by this process.
The dental implant may be a one-part or a two-part dental implant comprising an anchoring part for anchoring the implant within the jawbone and a mounting part for receiving a prosthetic build-up construction.
Two-part systems are known in the art. They can either be inserted subgingivally or transgingivally.
According to the (closed) subgingival system, the anchoring part of the dental implant is embedded until the bone ridge so that the mucoperiosteal cover can be seen above the implant. At the end of the primary healing phase, the mounting part and the desired bridge or crown is then applied in a second operation.
According to the (open) transgingival system, the anchoring part of the implant is sunk in up to about 3 mm of the bone ridge at mucosal level, thus avoiding a secondary operation. The wound edges can be directly adapted to the implant neck portion, thereby effecting a primary soft tissue closure to the implant. Then, the desired bridge or crown is screwed or cemented onto the mounting part of the implant, generally using an intermediate abutment.
Transgingivally applied dental implants are often preferred. When implanting such an implant, the soft tissue attachment during the healing process is not disturbed by a secondary operation such as occurring with systems that heal with covered mucous lining.
For example, the dental implant of the present invention can be a two-part, transgingivally applied implant analog to the titanium implant marketed by Institut Straumann AG, Basel/Switzerland, under the tradename “Straumann Dental Implant System”.
The two-part dental implant preferably has an anchoring and a mounting part which are made of the same ceramic material. Thus, the anchoring part and the mounting part have the same thermal coefficient of expansion, allowing them to be closely fitted and avoiding the formation of gaps between them.
Alternatively, the dental implant of the present invention may also be a one-part dental implant. The mechanical stability of a one-part dental implant is generally higher than that of a multi-part system. In combination with the high strength of the ceramic material used, the one-part dental implant of the present invention has thus a particularly high mechanical stability. The one-part dental implant has the additional advantage that there are no interstices and thus no starting points for the formation of bacteria which may cause parodontitis or gingivitis.
The dental implant of the present invention can be directly ground, allowing it to be adapted to further elements to be mounted in a simple way.
The dental implant of the present invention can either be made fully of a ceramic material or can have a core made of another material, such as a metal, for example titanium or an alloy thereof, or another ceramic material.
The present invention encompasses dental implants of which the whole surface is made of a ceramic material and dental implants of which only a part of the surface is made of a ceramic material.
Likewise, the present invention encompasses dental implants of which only a part of the surface, e.g. the bone tissue contacting region of the anchorage part's surface, has the topography obtainable by the process of the invention. Likewise, only the region of the implant's surface contacting the soft tissue may have the topography obtainable by the process of the invention. It has been found that when using a dental implant which in the soft tissue contacting region has the topography obtainable by the process described, the blood coagulum is stabilized which further accelerates the healing process. In a further embodiment of the present invention, both the bone and the soft tissue contacting region may thus have the topography obtainable by to the process described.
It is further preferred that the anchoring part comprises a threaded section. Thereby, the implant can be implanted with the necessary primary stability so that directly subsequent to the implantation a primary treatment is made possible by applying a temporary measure. The surface of the threaded section preferably has the topography obtainable by the process of the invention in order to increase osteointegration.

EXAMPLES

1. Etching of a Surface Made of Yttria-Stabilized Zirconia Ceramic

For Examples 1 to 11, densely sintered bodies made of yttria-stabilized zirconia ceramic as described by Burger, W. et al, New Y-TZP powders for medical grade zirconia. J Mater. Sci. Mater. Med. 1997, 8 (2), 113-118, and having the shape of a disc with a diameter of 15 mm and a thickness of 2 mm are prepared by low pressure injection molding and subsequent hot isostatic pressing. The material falls within the definition of ASTM F 1873 and ISO 13356 and is further specified by an average grain size from about 0.1 μm to about 0.3 μm.
For preparing the bodies, casting molds are used which optionally have been treated by erosion techniques to obtain a macroscopic roughness (or “macroroughness”) on the inner surface of the mold. Depending on the erosion parameters used, a pronounced or a non-pronounced macroroughness is, thus, provided to the surface of the body. Alternatively, a pronounced macroroughness can also be obtained by sandblasting the bodies with Al₂O₃at a pressure of 6 bar and an average working distance of 2 cm. Both the erosion and sandblasting techniques for providing a macroroughness to the surface are known to a person skilled in the art.
The bodies according to Examples 1 to 7 and 10 to 11 are then added to an etching solution in a Teflon container at a defined etching temperature and for a defined etching time. They are then instantly rinsed with deionized water and/or ethanol for five minutes in an ultrasonic device and subsequently dried under nitrogen or hot air.
Comparative Examples 8 and 9 are not added to the etching solution.
The particulars for Examples 1 to 11 are given in Table 1.

TABLE 1

Example	etching solution	etching temperature	etching time	macroroughness

1	Mixture of 80	104°	C.	10 minutes	pronounced
	vol.-% HF and 20				(erosion)
	vol.-% H₂SO₄
2	Concentrated HF	104°	C.	10 minutes	pronounced
					(erosion)
3	Mixture of 85	102-104°	C.	5 minutes	non-pronounced
	vol.-% HF and 15
	vol.-% H₂SO₄
4	Mixture of 50	102-104°	C.	5 minutes	non-pronounced
	vol.-% HF and 50
	vol.-% H₂O
5	Concentrated HF	102-104°	C.	10 minutes	non-pronounced
6	Mixture of 50	102-104°	C.	5 minutes	pronounced
	vol.-% HF and 50				(erosion)
	vol.-% H₂O
7	Mixture of 50	102-104°	C.	10 minutes	non-pronounced
	vol.-% HF and 50
	vol.-% H₂O

8	No etching	—	—	pronounced
(comparative)	(erosion only)			(erosion)
9	No etching	—	—	pronounced
(comparative)	(sandblasted			(sandblasted)
	only)

10	Concentrated HF	102-104°	C.	5 minutes	non-pronounced
11	Concentrated HF	102-104°	C.	5 minutes	pronounced
					(sandblasted)

For Examples 1 to 9, the surface structure obtained by the above treatment is shown in FIGS. 3 to 11 of which
FIG. 3 is an SEM picture of the surface resulting from the treatment according to Example 1 in two different magnification levels, the scale given in the SEM picture corresponding to 20 μm (above) and 5 μm (below), respectively;
FIG. 4 is an SEM picture of the surface resulting from the treatment according to Example 2 in two different magnification levels, the scale given in the SEM picture corresponding to 20 μm (above) and 5 μm (below), respectively;
FIG. 5 is an SEM picture of the surface resulting from the treatment according to Example 3 in two different magnification levels, the scale given in the SEM picture corresponding to 20 μm (above) and 5 μm (below), respectively;
FIG. 6 is an SEM picture of the surface resulting from the treatment according to Example 4 in two different magnification levels, the scale given in the SEM picture corresponding to 20 μm (above) and 5 μm (below), respectively;
FIG. 7 is an SEM picture of the surface resulting from the treatment according to Example 5 in two different magnification levels, the scale given in the SEM picture corresponding to 20 μm (above) and 5 μm (below), respectively;
FIG. 8 is an SEM picture of the surface resulting from the treatment according to Example 6 in two different magnification levels, the scale given in the SEM picture corresponding to 20 μm (above) and 5 μm (below), respectively;
FIG. 9 is an SEM picture of the surface resulting from the treatment according to Example 7 in two different magnification levels, the scale given in the SEM picture corresponding to 20 μm (above) and 5 μm (below), respectively;
FIG. 10 is an SEM picture of the surface according to Example 8 in two different magnification levels, the scale given in the SEM picture corresponding to 50 μm (above) and 20 μm (below), respectively; and
FIG. 11 is an SEM picture of the surface according to
Example 9 in two different magnification levels, the scale given in the SEM picture corresponding to 50 μm (above) and 20 μm (below), respectively.
As can be seen from FIGS. 3 to 9, etching according to the present invention of a surface made of an yttria-stabilized zirconia ceramic leads to a surface having crater-like structures. This surface is highly osteointegrative.
Similar structures are obtained by etching other yttria-stabilized zirconia ceramics. In a further example, a disc made of ZrO₂-TZP/TZP-A Bio-HIP® (ZrO₂) Bioceramic available from Metoxit AG, Switzerland, is etched with a mixture of 50 vol.-% concentrated hydrofluoric acid (HF) and 50 vol.-% of concentrated phosphoric acid as etching solution, the etching time being from about 20 to about 60 seconds and the etching temperature being about 106° C. An SEM picture of the surface obtained is given in FIG. 12, the scale given in the SEM picture corresponding to 5 μm.

2. Parameters Characterizing the Surface Topography

For Examples 1 to 11, the topography of the surface is quantitatively examined using a confocal 3D white light microscope (μSurf, NanoFocus AG, Oberhausen, Germany) over an area of 770 μm×770 μm to calculate the three-dimensional topography parameters S_kand S_sk. The lateral resolution of the microscope is 1.5 μm (512×512 pixels).
The specific measurement parameters are as follows:


	Measuring range:	770 μm × 770 μm
	Aperture:	50%
	Illumination:	Maximal intensity Xe-Lamp
	Objective:	20x
	Drive:	Piezo
	Stepsize:	0.6 μm
	Algorithm:	mean/fast

The ceramic samples are coated with a Au/Pd layer having a thickness of about 20 nm. To this end, a sputter coater (SCD 050; BAL-TEC AG, Liechtenstein) was used. The settings are as follows:
Coating distance: 50 mm
Evacuation: to 4×10⁻¹mbar
Rinsing: with Argon

Current: 65 mA

Time: 55 s

By these settings, an Au/Pd layer having a thickness of about 20 nm is obtained.
The 3D specific Skewness S_skand Core Roughness Depth S_kare calculated using a Gaussian filter with a cut-off wavelength of 10 μm. The Gaussian filter used to analyze the Core Roughness Depth and its associated parameters is a specific filter described in ISO 13 565 Part 1 (DIN 4776). The cut-off wavelength λ_cis defined, according to DIN 4768, as the wavelength of the sinusoidal wave which is separated by the filter into 50% roughness and 50% waviness.
The calculation of the roughness parameter S_kand S_skis carried out by the WinSAM software (University of Erlangen, Germany).
Details to the WinSAM software:
Windows Surface Analysis Module; Version 2.6, University of Erlangen, Germany; “Polynom 3. Grades, MA-Gauss-Filter 7 Punkte=cut-off (10×10 μm²); KFL-Analyse Amplitudendichte 10 nm”.
The filter creates a separation into waviness and roughness. This derivation and therefore also the determined value for the roughness parameter is dependent on the selected cut-off wavelength λ_c. For determining the S_kand S_skvalues, the cut-off wavelength λ_cis set to 10 μm as given above.
The results are given in the diagram of FIG. 13 in which the S_skvalues and the S_kvalues of Examples 1 to 11 are represented pointwise.
Comparatively, the S_kand S_skvalues of the commercially available implants z-Zit® (Example 12) of Ziterion GmbH, Germany, Z-Lock® (Example 13) of Z-Systems AG, Germany, White Sky® (Example 14) of Bredent medical GmbH, Germany, and Ti-SLActive® (Example 15) of Straumann, Switzerland, have also been determined according to the method described above.
As can be seen from FIG. 13, the surface topography of Examples 1 to 7 and 10 to 11 obtained according to one process in accordance with the present invention has a Core Roughness Depth S_kbetween about 0.4 μm and about 1 μm. In these Examples, the Skewness S_skis less than 0. FIG. 13 also clearly illustrates that the surface topography obtained according to the present invention is completely different from the surface topography of commercially available implants, in particular SLActive® (available from Straumann Holding AG, Basel CH), which have a Core Roughness Depth S_ksignificantly higher than 1 μm.

3. In Vitro Cell Tests

In vitro cell tests are carried out using the human osteosarcoma cell line MG-63 because of its ability to differentiate into mature osteoblasts.
The cell line is cultured in a mixture of Dulbecco's modified Eagles's Medium (DMEM; available from Sigma, Switzerland), Penicillin-Streptomycin Solution (100×; available from Sigma, Switzerland) and FBS.
On each of the discs according to Examples 1, 2, 7, 9 and 15, approximately 9000 cells are plated.
After culturing each of the respective discs in a medium containing vitamin D3, they are removed and washed with 1 ml PBS (RT). 350 μl of RLT-buffer (plus β-mercaptoethanol) is added to each disc and incubated for 2 to 3 minutes.
The RLT buffer is removed by simultaneously scratching with a pipette tip over the surface of the discs (to remove all cells) and frozen at −25° C. until RNA extraction.
RNA is isolated using the QIAGEN-Kit RNeasy Micro Kit®. Then, cDNA is produced and the expression of osteocalcin, osteonectin and TGFbeta, which are known to be involved in the bone formation process, is analysed by “Real time PCR”. As reference gene, 18S rRNA is used. Osteocalcin, osteonectin and TGFbeta are known to be suitable biochemical markers for the bone formation process.
For the calculation of the relative fold expression of the respective marker, the Livak method or 2^−ΔΔCtmethod is used. This method is based on the assumption that target and reference genes are amplified with efficiencies close to 100% (corresponding to an amplification rate of 2). The Livak method puts the E_(target)=E_(reference)=2, wherein E is the efficiency of the reaction.
The threshold cycle (Ct) of the target gene is normalized to the reference gene for the test sample and the calibrator sample. As a reference gene, 18S tRNA is used, and as a calibrator sample, cells cultured on the disc of Example 9 is used.
The ΔCt of the test sample is defined as follows:
ΔCt _{(test sample)} =Ct _{(test sample)} −Ct _{(reference gene)}
wherein the ΔCt of the calibrator is defined as follows:
ΔCt _(calibrator) =Ct _{(test calibrator)} −Ct _{(reference calibrator)}
The ΔCt of the test sample is normalized to the ΔCt of the calibrator, resulting in the ΔΔCt:
ΔΔCt=ΔCt _{(test sample)} −ΔCt _(calibrator)
and the normalized expression ratio was calculated by the following formula:
Normalized expression ratio=2^−ΔΔCt
The fold expressions of osteocalcin and TGFbeta on Examples 1, 2, 7 and 15 relative to Example 9 are shown in FIG. 14. As can be seen from FIG. 14, all examples treated according to the present invention exhibit a higher expression of osteocalcin and TGFbeta than comparative Example 9. This substantiates the finding that the examples treated according to the present invention have improved osteointegrative properties. A higher expression of osteocalcin and TGFbeta is also found for Example 15 relating to Ti-SLActive® which is well known for its high osteointegrative properties.
Example 2 has further been analysed for its expression of osteonectin. As shown in FIG. 15, Example 2 shows an expression of osteonectin superior over both comparative Example 9 and Example 15 (Ti-SLActive®).

Claims

1. A process for providing a topography to the surface of a dental implant, said surface being made of a ceramic material, wherein at least a part of the surface of the dental implant is etched with an etching solution comprising hydrofluoric acid at a temperature of at least 70° C., thereby removing discrete grains or agglomerates of grains from the ceramic material.

2. Process according to claim 1, the ceramic material having an average grain size from 0.1 μm to 0.6 μm.

3. Process according to claim 1 or 2, the ceramic material being based on zirconia.

4. Process according to claim 3, the ceramic material being yttria-stabilized zirconia.

5. Process according to claim 4, the composition of the yttria-stabilized zirconia comprising 4.5 to 5.5 weight-% of Y₂O₃and less than 5 weight-% of HfO₂, the total amount of ZrO₂, Y₂O₃and HfO₂being more than 99.0 weight-%.

6. Process according to claim 4, wherein prior to the etching a roughness is provided to the surface of the dental implant by sandblasting, milling and/or injection molding techniques.

7. Process according to claim 4, wherein the etching solution comprises at least 50 vol.-% of concentrated hydrofluoric acid.

8. Process according to claim 1, wherein the etching solution further comprises at least one compound selected from the group consisting of phosphoric acid, nitric acid, ammonium fluoride, sulfuric acid, hydrogen peroxide and bromic acid.

9. Process according to claim 1, wherein the etching solution further comprises sulfuric acid in an amount of 50 vol.-% at most.

10. Process according to claim 4, wherein the etching is performed for 1 minute to 60 minutes.

11. Process according to claim 4, wherein the etching is followed by washing the dental implant, the washing comprising the subsequent step or the subsequent steps of

c) rinsing the dental implant with a NaCl solution and/or

d) rinsing the dental implant with deionized water.

12. Dental implant obtainable by the process of claim 4.

13. Dental implant according to claim 12, the dental implant being a one-part dental implant.