Dental provisional superstructures and materials for producing same and corresponding method

0001The present invention relates to a dental substance, a dental mixture and a dental multi-component system for producing the material of a provisional superstructure for a dental implant or a core for a provisional superstructure for a dental implant by polymerization hardening.

0002The invention also relates to the corresponding provisional superstructures and cores themselves, which can be produced by polymerisation hardening from the dental mixtures according to the invention or from the dental multi-component systems according to the invention. The present invention also relates to a corresponding provisional denture which, in addition to a provisional superstructure according to the invention, also comprises a dental implant and a preferably metallic abutment. The present invention also relates to a kit for producing a plurality of provisional superstructures according to the invention for a dental implant or a plurality of cores according to the invention for provisional superstructures for a dental implant. A corresponding method for producing a temporary superstructure or a core is also the subject of the present invention. The invention also relates to a method for provisional care of a dental implant for therapeutic and / or cosmetic purposes, provisional superstructures according to the invention being used. Finally, the invention also relates to the use of a dental substance according to the invention, a dental mixture or a dental multicomponent system for producing a provisional superstructure or a core for such a provisional superstructure.

0003All aspects of the present invention are related to the use of dental implants and in particular the progressive bone loading method.

0004In modern dentistry, the use of dental implants is a complex, otherwise reliable and also aesthetically pleasing treatment method for the care of tooth gaps.

0005Compared to the alternative options for dentures such as fixed non-implant-supported bridges or removable prostheses, implants have clear advantages; in particular, they stress the jawbone in almost the same way as the original tooth. A dental implant (dental implant) is an artificial tooth root, usually in the technical form of a screw, which is implanted in the jaw bone when the tooth and its roots have been lost. As the implant grows together with the bone, the implant takes on almost the same functions as the original tooth root and also introduces forces into the bone, which puts the bone under tension. This stress on the jaw bone actively stimulates and supports the bone metabolism, so that the jaw bone is preserved. The edentulous jawbone, which is only covered by gums, under full dentures, however, is incorrectly stressed by the lack of tensile force in the bones and additionally superficial pressure, and it gradually degrades over the years, sometimes slowly and sometimes rapidly. As bone degradation progresses, the entire bone bed changes, which leads to major problems after years.

0006Dental implants are therefore inserted into the jaw bones in order to enable better prosthetic care for the patient after healing and to maintain the local bone compared to restoration without implants. In this way, total dentures are often avoided in edentulous patients, since the patient can be supplied with either fixed dentures or combined removable dentures. In the case of gaps in the teeth, grinding of healthy teeth to produce conventional (non-implant-supported) bridges can be avoided.

0007The implantological intervention is quite extensive and essentially comprises the following steps:<ul id="ul0001" list-style="dash"><li>Insert the implant into the jawbone</li><li>Healing of the implant in the bones</li><li>Exposing the implant</li><li>Taking impressions with special impression aids</li><li>Manufacture of dentures (superstructure)</li><li>Try in the dental prosthesis made by the dental technician</li><li>Insertion of the final denture (final restoration of the implant).</li></ul>

0008In the context of the present text, “superstructure” is understood to mean an element that is or is to be connected directly or indirectly to a dental implant and is intended to protrude completely or almost completely into the oral cavity. As a rule, the superstructure is a denture. A superstructure can be, for example, a crown, a bridge (or part of a bridge) or a removable prosthesis (or part of a removable prosthesis). In the context of the present text, the term "final", such as in the context of "final superstructure" or "final dentures", refers to an element that is not intended from the start to be replaced by another element after a certain period of time. In contrast to this, "provisional" in the context of the present text is understood to mean an element which is intended from the start to be replaced by another element at a later point in time. The adjective "provisional" should be understood accordingly. As a rule, a connection element between the implant and the superstructure is provided, a so-called abutment. Any abutment that may be present is not included in the superstructure in the context of the present text. "Connecting" a provisional superstructure to a dental implant means both positioning the superstructure directly on the implant (without using an abutment) and positioning the superstructure on an abutment that is positioned on the implant (indirect connection).

0009The healing phase in the treatment procedure given above is usually between 2 and 6 months. This leads to so-called osseointegration of the implant. This means that bone grows on the implant surface and the implant is firmly anchored in the bone. However, there is still no optimal architectural alignment of the bone structure, which can absorb and transmit forces. In the treatment procedure specified above, with the subsequent exposure of the implant and the subsequent supply of the implants with the prosthetic work (the superstructure), there is a sudden one-hundred percent transfer of forces, i.e. a complete transfer of the forces generated during chewing to the previously caused by forces unloaded implant and the unloaded surrounding bone structure. The disadvantage of the above-mentioned course of treatment is the spontaneous, one-hundred percent load on the implants and the surrounding bone structure, which may not correspond to the bone situation around the implant and in some situations overload the bone.

0010In order to achieve good osseointegration, the bone and the cells in it take time to grow on the surface of the implant and to remodel the surrounding bones. Until now, it was assumed that the time and quality of the bone were responsible for the healing rate and also for the success of osseointegration. It is discussed whether physiological forces acting on the implant promote osseointegration. Physiological forces would only burden the emerging bone structure to the extent that the healing process that had occurred up to that point allowed. Such a physiological application of force and a resulting improvement in the healing process can presumably shorten the healing time.

0011How long the healing time should be without using such a technique of physiological force application depends on recognized classifications of the density and structure of the bone, which provide recommendations for certain healing times. In general, this is 6 months for the upper jaw and 3 months for the lower jaw, since different bone structures and qualities can be found here.

0012Another important prerequisite for successful implantation is that the implant has so-called primary stability after it has been introduced into the bone. This means that it must not sit loosely immediately after insertion, but is anchored absolutely, that is to the maximum possible extent, firmly in the bone, which can also be done with the help of devices such as the Periotest^® displaced, can measure. Interestingly, after initial primary stability, the implant often loosens somewhat after about 14 days before becoming firmer again. This is explained by bone removal and remodeling processes. The implant is probably very sensitive to external forces within this time.

0013In recent years, new considerations have been made regarding the healing times required after the insertion of an implant. Above all, following the patient's wish not to have to wait as long until the final restoration was started, with shortened healing times or without healing times at all and, according to the alternative just mentioned, with immediate (directly after the implantation or within 24 to 36 hours afterwards) to work on provisional or final restoration of the implant and load.

0014Studies on the immediate loading of implants compared to the conventional method are contradictory. There are studies showing that the healing achieved was worse with immediate implant placement (<nplcit id="ncit0001" npl-type="s"><text>M. Lorenzoni, C. Pertl, K. Zhang, W. Wegschneider, Clin. Oral Implants Res., 2003, 14 (3) 273-279</text></nplcit>); other studies found no difference (<nplcit id="ncit0002" npl-type="s"><text>P. Quinlan et al., Int. J. Oral Maxillofac Implants 2005, 20 (3), 360-370</text></nplcit>) or came to the restriction that the patients should be selected carefully and the loading forces on the implants should be kept as low as possible (<nplcit id="ncit0003" npl-type="s"><text>G. Romanos, J. Oral Implantol. 2004, 30 (3), 189-197</text></nplcit>).

0015The failures in immediate loading seem to be due to too early and too strong transmission of force to the implant bone structure, which in these cases is currently being built up and rebuilt. This system can probably tolerate certain physiological forces; they may even have a stimulating effect; however, if they become too large, the tolerance tears off and there is no osseointegration, but a connective tissue separation of the implant.

0016The conventional method with the comparatively long healing times has the disadvantage that these remodeling processes do not occur slowly and continuously, since the jawbone is initially not stressed over a longer period of time (no occlusion with the opposing jaw) and later a sudden full load due to the temporary or the final restoration (superstructure), which can also lead to implant loss.

0017The method of immediate loading is disadvantageous because, according to previous knowledge, there is a risk that the surrounding bone-implant boundary will be overloaded, which in this early phase of healing can then mean the loss of the implant.

0018Based on these findings, the so-called (also referred to as "classic") method of progressive force loading (progressive bone loading) was described (<nplcit id="ncit0004" npl-type="s"><text>R. Appleton et al., Clin. Oral Implants Res. 2005, 16 (2), 161-167</text></nplcit>). The forces have to be slowly transferred to the bones. This increasing power transmission is called "progressive loading". First, a temporary (a temporary superstructure) based on plastic is used, which first ensures that the temporary denture (the temporary) does not occlude with its antagonist. During this time, the patient is required to eat only liquid or mushy food. Finally, the temporary restoration is modified so that it is brought closer and closer to the antagonistic tooth in several steps until it is finally in occlusion with the opposing jaw. The jawbone should adapt to the increasing load during this period until the final restoration finally takes place.

0019The resulting bone training is intended to bring about slow reconstruction of the bone architecture induced by physiological and reduced forces. This bone architecture is particularly important in order to physiologically distribute forces in the bone, since this is a basic principle of nature and bone.

0020The provisional dentures are made in the prior art from conventional dental prosthetic plastics of considerable hardness. Radically polymerizable acrylates are preferably used for this purpose. These systems are described exhaustively in the literature, for example in<patcit id="pcit0001" dnum="EP270915A"><text>EP 270915</text></patcit>, in the <patcit id="pcit0002" dnum="EP630640A"><text>EP 630640</text></patcit>, in the <patcit id="pcit0003" dnum="US6063830A"><text>US 6063830</text></patcit>, in the <patcit id="pcit0004" dnum="US5548001A"><text>US 5548001</text></patcit>, in the <patcit id="pcit0005" dnum="US4617327A"><text>US 4617327</text></patcit>, as well as in the <patcit id="pcit0006" dnum="EP0677286A"><text>EP 0677286</text></patcit>.

0021In addition to the systems based on acrylate chemistry, spiro orthoesters and polycyclic ketallactones have been proposed for the production of dental materials (<patcit id="pcit0007" dnum="US4387215A"><text>US 4387215</text></patcit>). The<patcit id="pcit0008" dnum="DE19506222"><text>DE 19506222</text></patcit> describes cationically polymerizable materials based on oxetane and oxacyclobutane derivatives. Furthermore, bicycloaliphatic 2-methylene-1,3-dioxepanes are from the<patcit id="pcit0009" dnum="DE4439485"><text>DE 4439485</text></patcit> known. The<patcit id="pcit0010" dnum="US5665839A"><text>US 5665839</text></patcit> discloses radically polymerizable oxathiepane that <patcit id="pcit0011" dnum="DE19612004"><text>DE 19612004</text></patcit> describes radically polymerizable multifunctional vinylcyclopropane derivatives, while the <patcit id="pcit0012" dnum="DE102004002178"><text>DE 102004002178</text></patcit> Proposes monomers that can cross-link through ring-opening metathesis.

0022Disadvantages of the "classic" progressive bone loading method described above are the fact that patients are only allowed to eat porridge and that due to the fact that there are no functional chewing forces, there is no controllable, reduced force introduction compared to a situation with functional full load . However, if the patient should eat food that requires chewing, the chewing forces on the implant should not be controlled.

0023There are already efforts in the prior art to specify provisional superstructures for dental implants, with the aid of which the disadvantages associated with the use of conventional provisional superstructures can be minimized, in particular also the disadvantages associated with the "classic" progressive bone loading method . For example, the<patcit id="pcit0013" dnum="WO2008037753A2"><text>WO 2008/037753 A2</text></patcit> elastic temporary superstructures for dental implants made of materials with a modulus of elasticity of less than 300 MPa. The in the<patcit id="pcit0014" dnum="WO2008037753A2"><text>WO 2008/037753 A2</text></patcit> The provisional superstructures disclosed are based on special curable starting materials, in particular silicones comprising polyatomic crosslinkable groups or optionally substituted crosslinkable polyethers. The in the<patcit id="pcit0015" dnum="WO2008037753A2"><text>WO 2008/037753 A2</text></patcit> proposed curable starting materials have proven their worth in practice; however, in practice it is difficult and in some cases not at all possible to achieve sufficient adhesion of the superstructures made from the special curable starting materials to conventional dental abutments, such as are used in connection with dental implants. According to the<patcit id="pcit0016" dnum="WO2008037753A2"><text>WO 2008/037753 A2</text></patcit> Therefore, specially designed abutments with undercuts and a form fit with complementary temporary superstructures are also used. In practice, however, the use of abutments without undercuts is preferred, since corresponding undercuts cannot be filled in with inelastic materials (such as those used after osseointegration when using permanent superstructures). In addition, in practice a connection between such a specific abutment with undercuts and a provisional superstructure is in some cases not sufficiently firm (if the provisional superstructure does not completely fill the undercut) or is almost irreversible (if the provisional superstructure snaps firmly into the undercut) ). Therefore, abutments are still typically designed in dental practice so that they taper towards the occlusal surface (occlusal surface), e.g. B. have a conical cross section. Deviating from this typical abutment shape is not considered desirable in dental practice.

0024The document <patcit id="pcit0017" dnum="US7798812A1"><text>US 7,798,812 A1</text></patcit> bears the title "Temporary dental prosthesis" and discloses provisional (temporary) dental prostheses that are resilient to stress and essentially absorb external stresses. Silicones are again mentioned as suitable materials for such temporary restorations, but also: rubber, nylon, polyethylene, copolymers, compomers, elastomers, plastics, Teflon and other biocompatible materials. In the<patcit id="pcit0018" dnum="US7798812A1"><text>US 7,798,812 A1</text></patcit> In addition to a prosthesis body, the disclosed superstructures include an interface structure which corresponds in function to a conventional abutment. The prosthesis body and interface structure are either integrally linked to one another or reversibly mounted to one another, in particular using screw connections. The teaching of<patcit id="pcit0019" dnum="US7798812A1"><text>US 7,798,812 A1</text></patcit> does not provide for the attachment of a prosthetic body to a typical commercial abutment (as explained above). Because the systems according to<patcit id="pcit0020" dnum="US7798812A1"><text>US 7,798,812 A1</text></patcit> require the use of specifically adapted interface structures instead of commercially available abutments, their use is perceived as disadvantageous in some cases.

0025It was therefore a primary object of the present invention to provide a provisional superstructure for a dental implant, with the aid of which the disadvantages associated with the use of conventional provisional superstructures can be minimized, in particular the disadvantages associated with carrying out the technical teachings <patcit id="pcit0021" dnum="WO2008037753A2"><text>WO 2008/037753 A2</text></patcit> and <patcit id="pcit0022" dnum="US7798812A1"><text>US 7,798,812 A1</text></patcit> occur. Linked to this primary task were the further tasks of specifying dental substances, dental mixtures or dental multicomponent systems for producing the material of a provisional superstructure for a dental implant or a core for a provisional superstructure for a dental implant, to specify a corresponding provisional denture, specify a kit for producing a plurality of provisional superstructures or cores for provisional superstructures that can be used in methods for accelerating the osseointegration of dental implants, preferably according to the principle of progressive bone loading, and specify corresponding methods for provisional care of a dental implant.

0026With regard to the dental substance, dental mixture or dental multi-component system to be specified for producing the material of a temporary superstructure for a dental implant or a core for a temporary superstructure for a dental implant, this task is surprisingly achieved by a dental substance, a dental mixture or a dental Multi-component system consisting of (a) one, two or more polymerizable (meth) acrylates, and optionally further constituents, the dental substance, the dental mixture or the dental multicomponent system being curable to form a product, the maximum pressure module achievable by (polymerization) curing preferably being at least 420 MPa or less. For further optional components (b), (c) etc. see below. The "maximum pressure module achievable by polymerization / hardening" is a material property. The method to be used in the context of the present text to determine this property is defined below. The production of a suitable test specimen is also explained below.

0027The dental substances, mixtures and multicomponent systems are used for therapeutic treatment to accelerate the osseointegration of dental implants, in particular according to the progressive bone loading method.

0028The term "polymerization hardening" in the present text means the solidification or hardening of a substance, a mixture or a multicomponent system by forming covalent bonds through radical and / or ionic polymerization or crosslinking, in particular through radical polymerization. Not meant are other, in particular physical, processes that lead to the hardening of a mixture, such as sintering, tempering or freezing.

0029The term "(meth) acrylates" in the present text encompasses acrylates and methacrylates.

0030It was surprising that dental substances, dental mixtures or dental multicomponent systems, which consist of one, two or more polymerizable (meth) acrylates and optionally further constituents, meet all requirements for a starting material, as should be specified in the context of the present invention. In particular, the materials and products that can be produced from the dental substances, dental mixtures or dental multi-component systems mentioned are outstandingly suitable for use as a temporary superstructure for a dental implant or suitable as a core for such a provisional superstructure if it is to be used in a therapeutic treatment to accelerate the osseointegration of dental implants, in particular in a method using the progressive bone loading method. The materials that can be produced from the dental substances according to the invention, dental mixtures or dental multicomponent systems by polymerization curing combine both the z. B. Desired property of a low pressure module with the excellent adhesion to commercially available, typical, metallic abutments for the process of progressive bone loading. Starting from the dental substances, dental mixtures and dental multi-component systems according to the invention, provisional superstructures can thus be produced which adhere excellently to typical abutments and which are at the same time so soft that they can be used as part of a progressive bone loading therapy in which successive provisional ones Superstructures of increasing hardness can be used. In this respect it should be referred to the explanations below and to the basic explanations in the <patcit id="pcit0023" dnum="WO2008037753A2"><text>WO 2008/037753 A2</text></patcit> referred to such a type of therapy.

0031The dental substance according to the invention, the dental mixture according to the invention or the dental multi-component system according to the invention is used in a therapeutic treatment to accelerate the osseointegration of dental implants, preferably according to the progressive bone loading method, with the dental substance or the dental mixture or a temporary superstructure for a dental implant or a core for a temporary superstructure for a dental implant is produced by polymerization hardening in the multi-component system.

0032A substance according to the invention, a dental mixture according to the invention or a dental multi-component system according to the invention is very particularly preferably used in a therapeutic treatment for accelerating the osseointegration of dental implants according to the progressive bone loading method, with several provisional superstructures consisting of or as a core material comprising materials with different pressure modules are produced and connected to the dental implant one after the other in the order of increasing pressure modules.

0033As already explained above, "classic" methods of progressive bone loading (in which provisional superstructures are used, which are reduced in height in comparison with the dental situation to be restored, so that it does not normally occur in the patient's oral cavity an occlusion with the antagonists) from the more recent progressive bone loading procedures, in which successive superstructures of increasing hardness are used, whereby these regularly have dimensions that correspond to those of the situation to be restored. An occlusion with the antagonist in the patient's oral cavity is therefore possible and even desirable. The dental substances, dental mixtures or dental multi-component systems according to the invention are thus intended in particular for use in the latter-mentioned methods of progressive bone loading.

0034A preferred dental mixture or dental multi-component system according to the invention consists of:<ol id="ol0001"><li>(a) one, two or more polymerizable (meth) acrylates,</li><li>(b) one or more catalysts and / or initiators for the polymerization,</li><li>(c) optionally one or more inorganic and / or organic fillers,</li><li>(d) optionally one or more stabilizers, for which the following applies: the stabilizer or stabilizers are not polymerizable (meth) acrylates, and</li><li>(e) optionally one or more other additives.</li></ol>

0035The following polymerizable (meth) acrylates are preferred dental substances according to the invention or preferred constituents of component (a) of a dental mixture or dental multicomponent system according to the invention, the dental substance or the dental mixture or the dental multicomponent system being curable to form a product, the The maximum achievable pressure module by hardening is 420 MPa or less:<ol id="ol0002"><li>1. Alkyl (meth) acrylates whose alkyl group has at least 6 carbon atoms.</li><li>2nd Di (meth) acrylates of polybutadiene, which can preferably be prepared by the esterification of a hydroxy-functional polybutadiene with (meth) acrylic acid (as hydroxy-functional polybutadienes, for example, types of "Poly BD" from Cray Valley are suitable, for example Poly BD R- 45 HTLO Resin).</li><li>3rd Alkyl ether di (meth) acrylates, the alkyl groups of which independently of one another each have at least 6 carbon atoms.</li><li>4th Polyalkyl ether (mono / di / poly) (meth) acrylates, the alkyl groups of which each independently have at least 2 carbon atoms and the number of ether functions is at least 8.</li><li>5. Aliphatic or aromatic urethane di (meth) acrylates, in particular:<ul id="ul0002" list-style="none"><li>5a. Aliphatic urethane di (meth) acrylates which can be prepared by reacting a diisocyanate component, preferably from the group of isophorone diisocyanate (IPDI), hexamethylene diisocyanate (HDI), cyclohexane diisocyanate, dicyclopentadiene diisocyanate, hydrogenated methylene diphenyl diisocyanate (hydrogenated MDI), with one being particularly preferred (IPDI) Meth) acrylate-functional hydroxyl component, preferably with a hydroxyalkyl (meth) acrylate (for example hydroxyethyl methacrylate (HEMA)) and / or an alkoxylated hydroxyalkyl (meth) acrylate, the latter can be prepared from a molar excess of ethylene oxide and / or propylene oxide and / or butylene oxide and / or tetrahydrofuran, etc. and (Meth) acrylic acid, can form polymers with excellent flexible properties. The reaction of the diisocyanate with ethoxylated and / or propoxylated hydroxyethyl acrylate (HEA), hydroxyethyl methacrylate (HEMA), hydroxypropyl acrylate (HPA), hydroxypropyl methacrylate (HPMA) is particularly preferred; the reaction with ethoxylated and / or propoxylated hydroxyethyl methacrylate (HEMA) is very particularly preferred. The degree of flexibility of the cured molding material can be tailored as a starting material for the isocyanate reaction with a diisocyanate by the stoichiometry of the reaction between the cyclic ether and the (meth) acrylic acid to the alkoxylated hydroxyalkyl (meth) acrylate. Aliphatic urethane di (meth) acrylates are commercially available products or can be synthesized according to known methods which a person skilled in the art can master.</li><li>5b. Aliphatic or aromatic urethane di (meth) acrylates which can be prepared by reacting a diisocyanate component from the group of aromatic and aliphatic diisocyanates with a (meth) acrylate-functional hydroxyl component based on polybutadiene diols. Aliphatic or aromatic urethane di (meth) acrylates, which can be prepared by reacting a diisocyanate component from the group of aromatic and aliphatic diisocyanates with α- (hydroxy) -ω - [(meth) acrylic] polybutadiene, are particularly suitable by esterifying a hydroxy-functional polybutadiene (eg "Poly BD R-45HTLO Resin" from Cray Valley) with an equivalent of (meth) acrylic acid.</li></ul></li><li>6. Alkoxylated bisphenol di (meth) acrylates, the alkyl groups of which each independently have at least 2 carbon atoms and the total number of ether functions is at least 10.</li></ol>

0036Combinations (mixtures) of (meth) acrylates as defined in items 1 to 6 above with one another and / or with further (meth) acrylates are advantageous in some cases, in particular combinations of the aforementioned (meth) acrylates from groups 1-6 with polyethylene glycol dimethacrylate , e.g. B. of aliphatic urethane di (meth) acrylate (see groups 5a and 5b above) with polyethylene glycol dimethacrylate (n = 9) (see group 3 above). The person skilled in the art will determine on the basis of simple preliminary tests whether a corresponding mixture after polymerization hardening has the pressure modulus of less than 420 MPa relevant according to the invention and is suitable for use in a therapeutic treatment for accelerating the osseointegration of dental implants, in particular according to the progressive bone loading method ( for this it must be in a solid phase). If necessary, the person skilled in the art will set the desired properties by varying further constituents.

0037Preferred dental mixtures according to the invention preferably comprise in component (a) a (meth) acrylate as defined above in items 1 to 6. (Meth) acrylates to be used with preference or in combination with preference are given below:<ul id="ul0003" list-style="none" compact="compact"><li>Poly-alkyl ether tri (meth) acrylates, poly alkyl ether poly (meth) acrylates, poly alkyl ether alkoxy di (meth) acrylates, poly alkyl ether alkoxy tri (meth) acrylates, poly alkyl ether Alkoxy-poly (meth) acrylates, poly-aliphatic-urethane di (metha) crylates, poly-aliphatic-urethane (metha) crylates, polyethylene glycol di (meth) acrylates, polypropylene glycol di (meth) acrylates, polyisopropylene glycol di (meth) acrylates, polyisobutylene glycol di (meth) acrylates, bisphenol A alkoxylate di (meth) acrylic latex, Bisphenol F alkoxylate di (meth) acrylates, bisphenol B alkoxylate di (meth) acrylates, ethoxylated bisphenol A di (meth) acrylates, ethoxylated bisphenol F di (meth) acrylates, ethoxylated bisphenol B -Di (meth) acrylates, propoxylated bisphenol A di (meth) acrylates, propoxylated bisphenol F di (meth) acrylates, propoxylated bisphenol B di (meth) acrylates and other alkoxylated bisphenol derivatives di (meth) acrylates .</li></ul>

0038Preferred (meth) acrylates for use in component (a) of a dental mixture or dental multicomponent system to be used according to the invention are listed, inter alia, in I.) <nplcit id="ncit0005" npl-type="b"><text>Paint raw material tables; Erich Karsten; 10th edition; Vincentz Verlag Hannover; 2000; II</text></nplcit>.) <nplcit id="ncit0006" npl-type="b"><text>Polymer handbook; 4th edition; Editors: J.Brandrup, EH Immergut &amp; EA Grulke; Wiley Verlag; 1999 and III</text></nplcit>.) <nplcit id="ncit0007" npl-type="b"><text>Chemistry &amp; Technology of UV&amp;EB Formulation for Coatings, Inks &amp; Paints: Volume III -Prepolymers &amp; Reactive Dilutents; Editor: G. Webster; SITA Technology Ltd. London; published by John Wiley &amp; Sons Ltd., London, 1997</text></nplcit>. The teaching regarding preferred (meth) acrylates disclosed in said documents is part of the present application by reference. Commercially available compounds are available from Atofina and its subsidiary companies Sartomer and Cray Valley, among others. Examples are listed below:<ul id="ul0004" list-style="none" compact="compact"><li>2- (2-ethoxyethoxy) ethyl acrylate ((EOEOEA) SR256), 2-phenoxyethyl acrylate ((PEA) SR339C), caprolactone acrylate (SR495), cyclic trimethylopropane formal acrylate ((CTFA) SR531), ethoxylated₄ Nonyl phenol acrylate (SR504), isobornyl acrylate ((IBOA) SR506D), isodecyl acrylate ((IDA) SR395), lauryl acrylate (SR335), octyl decyl acrylate ((ODA) SR484), stearyl acrylate (SR257C), tetrahydrofurfuryl acrylate ( (THFA) SR285), tridecyl acrylate (SR489), alkoxylated diacrylate (SR802), alkoxylated hexanediol diacrylate (CD561), ester diol diacrylate (SR606A), ethoxylated₁₀ Bisphenol A Diacrylate (SR602), Polyethylene Glycol 400 Diacrylate ((PEG400DA) SR344), Polyethylene Glycol 600 Diacrylate ((PEG600DA) SR610), Ethoxylated₁₅ Trimethylolpropane triacrylate (CN435), ethoxylated₂₀ Trimethylolpropane triacrylate (SR415), ethoxylated₉ Trimethylolpropane triacrylate (SR502), Highly propoxylated glycerol triacrylate (SR9021), Modified pentaerythritol triacrylate (SR444), 2-phenoxyethyl methacrylate (SR340), Ethoxylated₁₀ Hydroxyethyl methacrylate (CD572), isobornyl methacrylate (SR423A), lauryl methacrylate (SR313E), methoxy polyethylene glycol 350 monomethacrylate (CD550), methoxy polyethylene glycol 550 monomethacrylate (CD552), polypropylene glycol monomethacrylate (SR604), stearyl methacrylate (SR324) methacrylate (SR324), stearyl methacrylate (SR324) Methacrylate ((THFMA) SR203), ethoxy-lated₁₀ Bisphenol A Dimethacrylate (SR480), Polyethylene Glycol 600 Dimethacrylate ((PEG600DMA) SR252), Polybutadiene, dimethacrylate (CN301), Difunctional Polyester Acrylate (CN UVP210), Hexafunctional Polyester Acrylate (CN293), Polyester Acrylate (CN203), Polyester Acrylate (SYNOCURE AC1007), etc.</li></ul>

0039Preferred mixtures or multicomponent systems to be used according to the invention as specified above or below include in or as component (a) one or more (meth) acrylates selected from the group consisting of:<ol id="ol0003"><li>1. Alkyl (meth) acrylates whose alkyl group has at least 6 carbon atoms;</li><li>2nd Di (meth) acrylates of polybutadiene;</li><li>3rd Alkyl ether di (meth) acrylates, the alkyl groups of which independently of one another each have at least 6 carbon atoms;</li><li>4th Polyalkyl ether (mono / di / poly) (meth) acrylates, the alkyl groups of which each independently have at least 2 carbon atoms and the number of ether functions is at least 8;</li><li>5. Aliphatic or aromatic urethane di (meth) acrylates;</li><li>6. Alkoxylated bisphenol di (meth) acrylates, the alkyl groups of which each independently have at least 2 carbon atoms and the total number of ether functions is at least 10.</li></ol>

0040A mixture or multicomponent system to be used according to the invention preferably comprises in or as component (c) one or more particulate inorganic and / or organic fillers, which are preferably selected from the group consisting of silicon dioxide, metal oxides and poly (meth) acrylates.

0041The use of surface-modified or non-surface-modified SiO is very particularly preferred₂-Particles with an average particle diameter of less than 200 nm in or as component (c). In addition to these SiO₂-Particles may optionally have additional particulate inorganic or organic fillers.

0042The surface-modified or non-surface-modified SiO₂Particles with an average particle diameter of less than 200 nm of component (c) are preferably pyrogenic SiO₂ like it is under the name AEROSIL^® (Evonik) is offered. These particles influence both the hardness of the polymerization-hardened dental mixture or multicomponent system and the consistency of the dental mixture or multicomponent system itself and are preferably modified on the surface. The particulate inorganic or organic fillers optionally contained in component (c) are preferably silicon-containing and include, for example ground quartz, for example an average particle diameter of approx. 10 µm.

0043In principle, all inert materials are suitable as particulate inorganic and / or organic fillers. The particulate fillers have an influence on the pressure module of the dental mixture or multicomponent system according to the invention, which serves as the starting material for the production of superstructures or cores. Examples of inorganic fillers are glasses, in particular dental glasses, silicon dioxide (for example as quartz, cristobalite, pyrogenic SiO₂ like that under the name AEROSIL^® (Evonik) offered and / or manufactured using a sol-gel process₂), Examples of organic fillers are poly (meth) acrylates. The fillers are incorporated into the matrix during the polymerization hardening of the reactive constituents, in particular component (a) of the dental mixture or multicomponent system according to the invention and impart strength to the hardened product (for example the immediately usable dental superstructure or the core).

0044The dental mixture to be used according to the invention or the dental multi-component system to be used according to the invention is preferably colored, as is the product resulting therefrom (in particular a dental superstructure or a core according to the invention), in particular in order to adapt its color to a color of natural teeth. Examples of coloring constituents are, for example, one or more inorganic or organic fillers of constituent (c) (eg tooth-colored poly (meth) acrylate particles, metal oxides and / or ground quartz). However, additional coloring constituents can also be provided as or in the optional component (s), for example natural dyes or synthetic dyes such as azo, triarylmethane, quinophthalone, xanthene and indigo dyes and anthraquinone, nitroso and phthalocyanine dyes.

0045Additional polymerizable compounds can be provided as or in the optional component (e).

0046Particulate fillers, which have a solid inorganic or organic core and have polymerizable (meth) acrylate groups on their surface, are not counted among the polymerizable (meth) acrylates of component (a), but rather as component (c), especially in quantitative quantities. . In all other cases, components that can be technically and conceptually assigned to two or more components are assigned to the previously mentioned component for the purposes of quantitative information (i.e. (a) before (b) before (c) before (d) before (e) etc.).

0047Particularly preferred dental mixtures according to the invention or dental multicomponent systems according to the invention, such as are provided for use in the above-mentioned therapeutic methods, are mixtures which are chemically curable and / or light-curable. Dental mixtures or dental multi-component systems according to the invention are preferably both chemically curable and light-curable. They thus enable curing using the dual-cure process. For example, the dental mixtures can initially be pre-hardened with light to obtain a certain basic strength, and then chemically hardened. Multicomponent systems with two or more components (comprising different dental mixtures), which are mixed with one another to form a dental mixture at the start of curing, are preferred for the dual-cure method.

0048Dental two-component systems to be used according to the invention have a first and a second component, which preferably have a volume ratio of 10: 1 to 1:10, preferably 4: 1 to 1: 4, particularly preferably 2: 1 to 1: 2 and in particular 1: 1 are mixed in a dental mixture. The mixing preferably takes place in a static mixing device. The first and second components are particularly preferably matched to one another in such a way that, after mixing, the crosslinking takes place within a period of 30 s to 10 min. is completed.

0049In light-curing systems, component (b) of a dental mixture to be used according to the invention comprises a light-curing initiator. Examples of a light curing initiator include catalysts that only have a photosensitizing effect and combinations of a sensitizer and an accelerator.

0050Examples of photosensitizers are alpha-diketones, benzoin alkyl ethers, thioxanthones, benzophenones, acylphosphine oxides, acetophenones, ketals, titanocenes, sensitizing dyes, etc. The sensitizers can be used alone or in combination. Specific substance examples of the different classes can be found, for example, in the<patcit id="pcit0024" dnum="DE102006019092A1"><text>DE 10 2006 019 092 A1</text></patcit> or in the <patcit id="pcit0025" dnum="DE3941629C2"><text>DE 39 41 629 C2</text></patcit>which are part of the present application by reference.

0051Examples of accelerators which are used together with the sensitizers are tertiary amines, secondary amines, barbituric acids, tin compounds, aldehydes and sulfur compounds. Specific substance examples of the different classes can be found in the<patcit id="pcit0026" dnum="DE102006019092"><text>DE 10 2006 019 092</text></patcit> or in the <patcit id="pcit0027" dnum="DE3941629C2"><text>DE 39 41 629 C2</text></patcit>which are part of the present application by reference. Other suitable initiators and combinations of initiators are in the<patcit id="pcit0028" dnum="DE60116142"><text>DE 601 16 142</text></patcit> described, which are part of the present application by reference.

0052The photoinitiators which can be used in the context of the present invention are characterized in that they are absorbed by light in the wavelength range from 300 nm to 700 nm, preferably from 350 nm to 600 nm and particularly preferably from 380 nm to 500 nm, if appropriate in combination with an or several coinitiators which can cause curing of a curable mixture or multicomponent system according to the invention.

0053The maximum absorption of camphorquinone (CC) is around 470 nm and thus in the range of blue light. Camphorquinone (CC) is one of the PI₂Initiators and is used regularly together with a coinitiator. A curable mixture or multicomponent system according to the invention preferably contains the combination of an alpha-diketone and an aromatic tertiary amine; preference is given to the combination of camphorquinone (CC) and ethyl<i>p</i>-<i>N, N</i>-dimethylaminobenzoate (DABE).

0054Also preferred is the further combination of the "alpha-diketone / aromatic tertiary amine" system with a phosphine oxide, in particular with the phenyl-bis (2,4,6-trimethylbenzoyl) phosphine oxide and / or the 2,4,6-trimethylbenzoyldiphenylphosphine oxide. With regard to the structures of suitable phosphine oxides for use in curable mixtures according to the invention, reference is made to the documents<patcit id="pcit0029" dnum="DE3801511C2"><text>DE 38 01 511 C2</text></patcit>, <patcit id="pcit0030" dnum="DE102006050153A1"><text>DE 10 2006 050 153 A1</text></patcit>, <patcit id="pcit0031" dnum="EP0184095B1"><text>EP 0 184 095 B1</text></patcit>, <patcit id="pcit0032" dnum="DE4231579C2"><text>DE 42 31 579 C2</text></patcit>, <patcit id="pcit0033" dnum="EP0366977B1"><text>EP 0 366 977 B1</text></patcit>, <patcit id="pcit0034" dnum="US7081485B2"><text>US 7,081,485 B2</text></patcit>, <patcit id="pcit0035" dnum="DE3236026A1"><text>DE 32 36 026 A1</text></patcit>, <patcit id="pcit0036" dnum="US20070027229A1"><text>US 2007/0027229 A1</text></patcit>, <patcit id="pcit0037" dnum="EP0262629B1"><text>EP 0 262 629 B1</text></patcit>, <patcit id="pcit0038" dnum="EP0073413A"><text>EP 0 073 413</text></patcit>, <patcit id="pcit0039" dnum="US7148382B2"><text>US 7,148,382 B2</text></patcit>, <patcit id="pcit0040" dnum="US5761169A"><text>US 5,761,169</text></patcit>, <patcit id="pcit0041" dnum="DE19708294A1"><text>DE 197 08 294 A1</text></patcit>, <patcit id="pcit0042" dnum="EP0057474A"><text>EP 0 057 474</text></patcit>, <patcit id="pcit0043" dnum="EP0047902A"><text>EP 0 047 902 A</text></patcit>, <patcit id="pcit0044" dnum="EP0007508A"><text>EP 0 007 508</text></patcit>, <patcit id="pcit0045" dnum="DE60029481T2"><text>DE 600 29 481 T2</text></patcit>, <patcit id="pcit0046" dnum="EP0980682B1"><text>EP 0 980 682 B1</text></patcit>, <patcit id="pcit0047" dnum="EP0948955B1"><text>EP 0 948 955 B1</text></patcit>, <patcit id="pcit0048" dnum="EP1236459B1"><text>EP 1 236 459 B1</text></patcit> and <patcit id="pcit0049" dnum="EP0173567A2"><text>EP 0 173 567 A2</text></patcit> referenced, which are part of the present application by reference. The phosphine oxides specified in these documents are particularly suitable alone or in combination with the "alpha-diketone / amine" system as a photopolymerization initiator system in the mixtures or multicomponent systems according to the invention.

0055Alternatively, borate salts, as described, for example, in <patcit id="pcit0050" dnum="US4772530A"><text>US 4,772,530</text></patcit>, <patcit id="pcit0051" dnum="US4954414A"><text>US 4,954,414</text></patcit>, <patcit id="pcit0052" dnum="US4874450A"><text>US 4,874,450</text></patcit>, <patcit id="pcit0053" dnum="US5055372A"><text>US 5,055,372</text></patcit> and <patcit id="pcit0054" dnum="US5057393A"><text>US 5,057,393</text></patcit> are used as photoinitiators, which are part of the present application by reference.

0056Other suitable photoinitiators (light curing initiators) are in <nplcit id="ncit0008" npl-type="b"><text>J.-P. Fouassier, Photoinitiation, Photopolymerization and Photocuring, Hanser Publishers, Munich, Vienna, New York 1995</text></nplcit> as in <nplcit id="ncit0009" npl-type="b"><text>JF Rabek (ed.), Radiation Curing in Polymer Science and Technology, Vol. II, Elsevier Applied Science, London, New York 1993</text></nplcit> described, which are part of the present application by reference.

0057In the case of chemically curing systems, component (b) of a mixture to be used according to the invention comprises an initiator for chemical curing. Various initiators for chemical curing are known to the person skilled in the art. In this respect it is exemplary of the<patcit id="pcit0055" dnum="EP1720506A"><text>EP 1 720 506</text></patcit> referred. Preferred initiators for chemical hardening are benzoyl peroxide, lauroyl peroxide, especially dibenzoyl peroxide in combination with amines such as N, N-dimethyl-p-toluidine, N, N-dihydroxyethyl-p-toluidine and structurally related amines.

0058The peroxides and the amines are divided into two different components of a dental material, each of which already represents a dental mixture. When the amine-containing component (so-called base paste) is mixed with the peroxide-containing component (so-called initiator or catalyst paste) to form a dental (secondary) mixture, the reaction of amine and peroxide (redox reaction) initiates the radical reaction.

0059Dual curing systems include a combination of photoinitiators and chemical curing initiators. For example, a base paste (used as the first component) can additionally contain a photoinitiator, so that the base paste can either be used alone as a light-curing (to be used as second component) or together with an initiator paste as a light- and self-curing dental material (dental mixture). In addition to the oxidatively active organic peroxide compounds, barbituric acids or barbituric acid derivatives and malonyl sulfamides can also be used as redox systems. Of the barbituric acid systems, the so-called "Bredereck systems" are of great importance. Examples of suitable "Bredereck systems" as well as references to the corresponding patent literature can be found in the<patcit id="pcit0056" dnum="EP1839640A"><text>EP 1 839 640</text></patcit> as in <patcit id="pcit0057" dnum="DE1495520"><text>DE 1495520</text></patcit>, <patcit id="pcit0058" dnum="WO02092021A"><text>WO 02/092021</text></patcit> or in <patcit id="pcit0059" dnum="WO02092023A"><text>WO 02/092023</text></patcit>which are part of the present application by reference.

0060Suitable malonyl sulfamides are in the <patcit id="pcit0060" dnum="EP0059451A"><text>EP 0 059 451</text></patcit> described which is part of the present application by reference. Preferred compounds are 2,6-dimethyl-4-isobutylmalonylsulfamide, 2,6-diisobutyl-4-propylmalonylsulfamide, 2,6-dibutyl-4-propylmalonylsulfamide, 2,6-dimethyl-4-ethylmalonylsulfamide and 2,6-diocytyl- 4-isobutylmalonylsulfamide.

0061Sulfur compounds in the oxidation state +2 or +4 such as sodium benzene sulfinate or sodium paratoluenesulfinate can also be used.

0062To accelerate curing, the polymerization can be carried out in the presence of heavy metal compounds such as Ce, Fe, Cu, Mn, Co, Sn or Zn, copper compounds being particularly preferred. The heavy metal compounds are preferably used in the form of soluble organic compounds. Preferred copper compounds are copper benzoate, copper acetate, copper ethyl hexanoate, copper di (methacrylate), copper acetylacetonate and copper naphthenate.

0063Instead of the barbituric acid / derivatives, salts of CH active compounds can also be used. <patcit id="pcit0061" dnum="EP1872767A"><text>EP 1 872 767</text></patcit>, <patcit id="pcit0062" dnum="EP2070506A"><text>EP 2 070 506</text></patcit>, <patcit id="pcit0063" dnum="DE112006001049"><text>DE 11 2006 001 049</text></patcit>, <patcit id="pcit0064" dnum="US7214726B"><text>US 7,214,726</text></patcit>, <patcit id="pcit0065" dnum="EP2070935A"><text>EP 2 070 935</text></patcit> such as <patcit id="pcit0066" dnum="WO2007131725A"><text>WO 2007/131725</text></patcit> describe suitable systems.

0064Preferred dental mixtures according to the invention or dental multicomponent systems according to the invention, as they are intended for use in the above-mentioned therapeutic methods, comprise<ol id="ol0004"><li>(a) a total of 20.0 to 99.9 percent by weight of polymerizable (meth) acrylates,</li><li>(b) a total of 0.1 to 10.0 percent by weight of catalysts and initiators for the polymerization,</li><li>(c) a total of 0.0 to 60.0 percent by weight of inorganic and organic fillers,</li><li>(d) a total of 0.0 to 5.0 percent by weight of stabilizers, for which the following applies: the stabilizer or stabilizers are not polymerizable (meth) acrylates, and</li><li>(e) a total of 0.0 to 50.0 percent by weight of other additives.</li></ol>

0065Particularly preferred dental mixtures to be used according to the invention or dental multicomponent systems according to the invention, as are intended for use in the above-mentioned therapeutic methods<ol id="ol0005"><li>(a) a total of 44.9 to 99.9 percent by weight of polymerizable (meth) acrylates,</li><li>(b) a total of 0.1 to 5.0 percent by weight of catalysts and initiators for the polymerization,</li><li>(c) a total of 0.0 to 55.0 percent by weight of inorganic and organic fillers,</li><li>(d) a total of 0.0 to 2.0 percent by weight of stabilizers, for which the following applies: the stabilizer or stabilizers are not polymerizable (meth) acrylates, and</li><li>(e) a total of 0.0 to 5.0 percent by weight of other additives.</li></ol>

0066The present invention also relates to a provisional superstructure for a dental implant and a core for a provisional superstructure for a dental implant, which can be produced by polymerization curing a dental mixture to be used according to the invention or a dental multicomponent system to be used according to the invention.

0067According to the material properties of the dental substances, mixtures or multicomponent systems to be used according to the invention, which have already been explained above, the material of the provisional superstructure or the material of the core for a provisional superstructure at least preferably has a pressure module of less than 420 MPa according to the invention, and is therefore special when subjected to pressure soft. On account of this low pressure module, a provisional superstructure according to the invention or a corresponding core is particularly well suited for use in the preferred progressive bone loading processes in which materials with increasing hardness are successively used. When using provisional superstructures or In contrast to the "classic" progressive bone loading procedures, it is no longer necessary to reduce the dimensions of the temporary superstructures compared to the dimensions of the tooth to be restored. Because of the choice according to the invention of the suitable material (superstructure or core based on (meth) acrylates), excellent adhesion to a conventional metallic abutment is also ensured, which was not achieved according to the methods of the prior art.

0068According to a first alternative embodiment of a superstructure according to the invention, this consists of a core and a cap for the core, the outer surface of the core being partially exposed, so that the core can be deformed at least in sections independently of the cap under pressure, the material of the cap preferably being used has a higher pressure modulus than the material of the core.

0069The cap preferably serves to provide a surface with chewing properties that are improved compared to the surface (outer surface) of the core (in particular increased abrasion resistance). The material, thickness and shape of the cap are selected and adapted to the core in such a way that the core's ability to absorb chewing forces and reduce their transfer to the implant is retained. The cap is preferably designed to cover only part of the outer surface (outer surface) of the core, this part encompassing the occlusal surface. The cap is preferably made of ceramic or a conventional provisional crown material of comparatively high hardness (e.g. Plastics or composites based on plastics, for example based on (meth) acrylate-containing compounds such as polymethyl methacrylate (PMMA), bisphenol-A-glycidyl methacrylate (bis-GMA), urethane dimethacrylate (UDMA) or triethylene glycol dimethacrylate (TEGDMA); see also the above statements on conventional dental prosthetic plastics. The cap is glued to an assigned core, for example, or is arranged on it with the formation of a clamp seat (possibly with a positive fit) in order to produce the provisional superstructure.

0070According to a second alternative embodiment of a provisional superstructure according to the invention, this does not have a cap of the type described above. A provisional superstructure according to the invention can then preferably be produced by a single polymerization hardening of a single dental mixture to be used according to the invention.

0071As already explained, the term “provisional superstructure” denotes a superstructure that is intended from the start to be replaced by another superstructure at a later point in time. As a rule, such a temporary superstructure is intended to remain in the mouth for a few days, weeks or months until the final superstructure is supplied. The provisional superstructure according to the invention can be connected directly to the dental implant directly after the implantation (immediate loading) or after a shortened or conventional healing time (e.g. 3 to 6 months), or preferably in such a way that the provisional superstructure is in occlusion with the opposite jaw. The provisional superstructure thus ensures that chewing forces are absorbed and, due to the elasticity and flexion of the provisional superstructure, passed on to the implant. During the healing phase, coordinated provisional superstructures of increasing hardness preferably ensure that the contact surface between the implant and jawbone is subjected to increasing loads. The patients do not have to limit themselves to porridge, but can determine their own nutrition depending on the functional eating and chewing function of their provisional superstructure. The use of a provisional superstructure according to the invention is also advantageous for aesthetic reasons, since there is no tooth gap. For the superstructures and cores according to the invention, their pressure module is of crucial importance, as has already been explained above.

0072A provisional superstructure according to the invention or a core according to the invention for a provisional superstructure is preferred, the provisional superstructure being a provisional crown. In the context of the present text, "crown" is understood to mean an element which is intended to replace a single tooth and whose retention on another element is essentially based on a positive or non-positive connection between (at least a part) of its inner surface and an outer surface of the other element. A crown is preferably approximated to the natural tooth geometry. In this way, a controlled application of force is particularly possible. However, a provisional superstructure according to the invention can also be a provisional bridge pillar.

0073The invention also relates to a provisional tooth replacement<ul id="ul0005" list-style="dash"><li>a provisional superstructure according to the invention (which or its material can therefore be produced by polymerization hardening of a dental mixture to be used according to the invention),</li><li>a dental implant and</li><li>a preferably metallic abutment, which is arranged between the temporary superstructure and the dental implant and ensures their connection as well as optional</li><li>an adhesion promoter, which is arranged between the temporary superstructure and the abutment.</li></ul>

0074A dental implant is preferably made of titanium and a preferred abutment is made of metal, with titanium being used particularly frequently.

0075In preferred provisional dentures according to the invention (dental provisionals), the provisional superstructure and the abutment are connected without positive locking in the direction of force along the longitudinal axis of the dental implant away from the jawbone into which the implant is inserted or to be inserted.

0076A connection without such a form fit is achieved, for example, with the abutments already explained above, which are designed in such a way that they taper towards the occlusal surface (occlusal surface), e.g. B. have a conical cross-section. Particularly preferred provisional dentures according to the invention comprise a metallic abutment which has a cross section tapering towards the occlusal surface (occlusal surface), so that the provisional superstructure and the abutment are connected without positive locking in the direction of force along the longitudinal axis of the dental implant away from the jawbone into which the Implant or is to be used. It is particularly preferred if the metallic abutment used has a conical cross section. Provisional dentures according to the invention do not always include an adhesion promoter between the temporary superstructure and the abutment. Rather, an adhesion promoter is generally unnecessary due to the excellent self-adhesion of the provisional superstructure on the abutment.

0077If an adhesion promoter is used to improve the adhesion of the temporary superstructure to the abutment, this is preferably selected from the group of eugenol-free cements based on zinc oxide (e.g. Provicol (VOCO), RelyX Temp E (3M Espe)) or (meth) acrylic-based temporary fastening composites (e.g. Telio CS Link (Ivoclar Vivadent) and implantlink^® semi (Detax)).

0078Preferred stabilizers (inhibitors) for use in dental mixtures or multicomponent systems according to the invention are usually added in order to avoid spontaneous polymerization. They react with premature radicals that are trapped, prevent premature polymerization and increase the storage stability of the light-curable dental mixture or the multi-component system. Common stabilizers (inhibitors) are phenol derivatives such as hydroquinone monomethyl ether (HQME) or 2,6-di-tert-butyl-4-methylphenol (BHT). Other stabilizers (inhibitors) such as tert-butylhydroxyanisole (BHA), 2,2 diphenyl-1-picryl-hydrazyl, galvinoxyl, triphenylmethyl radicals, 2,3,6,6, -tetramethylpiperidinyl-1-oxyl radicals (TEMPO) and derivatives of TEMPO or phenothiazine and derivatives of this compound are in the<patcit id="pcit0067" dnum="EP0783880B1"><text>EP 0 783 880 B1</text></patcit> described; the derivatives disclosed therein are part of the present application by reference. Alternative stabilizers (inhibitors) are in the<patcit id="pcit0068" dnum="DE10119831A1"><text>DE 101 19 831 A1</text></patcit> and in the <patcit id="pcit0069" dnum="EP1563821A1"><text>EP 1 563 821 A1</text></patcit> indicated and are part of the present application by reference.

0079Preferred additives for use in dental mixtures or multicomponent systems according to the invention are, for example, UV absorbers which, for example, are able to absorb UV radiation due to their conjugated double bond systems and aromatic rings. Examples of preferred UV absorbers are 2-hydroxy-4-methoxybenzophenone, phenyl salicylic acid, 3- (2'-hydroxy-5'-methylphenyl) benzotriazole and diethyl 2,5-dihydroxy-terephthalate.

0080The present invention also relates to a kit for producing a plurality of provisional superstructures for a dental implant or a plurality of cores for provisional superstructures for a dental implant, comprising<ul id="ul0006" list-style="dash"><li>a corresponding number of dental substances, dental mixtures or dental multicomponent systems to be used according to the invention, as defined above, each of the dental substances, mixtures or multicomponent systems being curable to form a product, the pressure module which can be maximally achieved by (polymerization) curing thus preferably each is 420 MPa or less and the pressure modulus of the products is different under the same curing conditions or</li><li>a corresponding number of blanks from a hardened or producible by hardening from a dental substance or mixture to be used according to the invention as defined above, the pressure modulus of the material of each of the blanks being different and being at least preferably 420 MPa or less, such as</li><li>optionally one or more additional components selected from the group consisting of bonding agents, abutments, implants, molding tools (molds), impression materials.</li></ul>

0081A "blank" is to be understood here as a precursor of a provisional superstructure or a core according to the invention, which generally cannot be connected in unchanged form to an implant or an abutment, but is intended in terms of its shape to a specific patient situation to be adapted, for example by removing (e.g. Cutting, grinding or any other ablative shaping process) of excess.

0082In some preferred configurations, a kit according to the invention also comprises materials for producing a mold by molding and / or means for producing an insulating layer on an abutment to prevent or reduce the adhesion of a pressed-on, hardened product and / or scaffold building blocks for building a removable dental modulation and / or a temporary superstructure and / or one or more materials for producing a removable dental modulation.

0083A kit according to the invention is preferred for producing several (for example 2, 3 or more) provisional superstructures or cores according to the invention, the materials of which differ in terms of their pressure modules. The provisional superstructures or cores to be produced are regularly intended to be connected to the dental implant one after the other in the order of increasing pressure modules. A kit according to the invention is particularly preferred for producing 3 or more provisional superstructures or cores, one or more provisional superstructures or cores made of materials with pressure modules in the ranges (i) &lt;25 MPa, (ii) 25 MPa to &lt;100 MPa and (iii) 100 MPa to 420 MPa.

0084A particularly preferred kit according to the invention comprises<ul id="ul0007" list-style="dash"><li>a first dental substance to be used according to the invention, a first dental mixture to be used according to the invention or a first dental multicomponent system to be used according to the invention as defined above, the first dental substance or the first dental mixture or the first dental multicomponent system being curable to form a product, the by Hardening (polymerization hardening) maximum achievable pressure modulus is in the range from 25 MPa to less than 100 MPa,</li><li>a second dental substance to be used according to the invention, a second dental mixture to be used according to the invention or a second dental multicomponent system to be used according to the invention as defined above, the second dental substance or the second dental mixture or the second dental multicomponent system being curable to form a product, the Curing (polymerization curing) maximum achievable pressure modulus is in the range of 100 MPa to 420 MPa,</li><li>optionally a third dental substance, a third dental mixture or a third dental multicomponent system, preferably a third dental substance to be used according to the invention, a third dental mixture to be used according to the invention or a third dental multicomponent system to be used according to the invention, as defined above, the third dental substance or the third dental mixture or the third dental multicomponent system can be hardened to form a product, the maximum pressure module that can be achieved by hardening (polymerization hardening) being less than 25 MPa,</li><li>optionally a further dental substance, a further dental mixture or a further dental multicomponent system, the further dental substance or the further dental mixture or the further dental multicomponent system being curable to form a product, the maximum pressure module achievable by hardening (polymerization hardening) being greater is as 420 MPa.</li></ul>

0085A very particularly preferred kit according to the invention comprises<ul id="ul0008" list-style="dash"><li>a first dental substance, a first dental mixture or a first dental multicomponent system as defined above, the first dental substance or the first dental mixture or the first dental multicomponent system being curable to form a product, the maximum pressure module achievable by curing in the range from 25 MPa to less than 100 MPa,</li><li>a second dental substance, a second dental mixture or a second dental multicomponent system as defined above, the second dental substance or the second dental mixture or the second dental multicomponent system being curable to form a product, the maximum pressure module achievable by curing in the range from 100 MPa to 420 MPa, further comprehensive</li><li>a third dental substance, a third dental mixture or a third dental multicomponent system preferably as defined above, the third dental substance or the third dental mixture or the third dental multicomponent system being curable to form a product, the maximum pressure module achievable by curing being smaller is as 25 MPa, and or</li><li>a further dental substance, a further dental mixture or a further dental multicomponent system, preferably consisting of one, two or more polymerizable (meth) acrylates and optionally further components, the further dental substance or the further dental mixture or the further dental Multi-component system can be hardened to a product, the maximum pressure module achievable by hardening being greater than 420 MPa.</li></ul>

0086The invention also relates to a method for producing a provisional superstructure according to the invention for a dental implant or a core according to the invention for a provisional superstructure for a dental implant as explained above or a provisional denture according to the invention as explained above, with the following steps:<ul id="ul0009" list-style="dash"><li>Providing or producing a dental substance to be used according to the invention, a dental mixture according to the invention or a dental multicomponent system according to the invention,</li><li>Hardening the dental substance, the dental mixture or the dental multi-component system, preferably in a mold,</li><li>optional further steps or</li><li>Provision of a kit according to the invention, as explained above, comprising blanks,</li><li>Adjusting the shape of one of the blanks, so that the provisional superstructure according to the invention, the core according to the invention or the provisional dentures according to the invention result.</li></ul>

0087A preferred method according to the invention for producing a provisional superstructure or a corresponding core comprises the following steps:<ul id="ul0010" list-style="dash"><li>Providing or producing a dental substance to be used according to the invention, a dental mixture to be used according to the invention or a dental multi-component system to be used according to the invention, as explained above,</li><li>Providing a suitable form,</li><li>Filling the mold with the dental substance, the dental mixture or the dental multi-component system, and afterwards</li><li>Hardening (polymerization hardening) of the dental substance, the dental mixture or the dental multi-component system in the mold</li><li>Removal of the hardened product (ie the blank, superstructure or core) from the mold and afterwards</li><li>optionally adapt the shape of the hardened product (ie the blank thus formed), and</li><li>optional further steps or</li><li>Providing a kit according to the invention comprising blanks,</li><li>Adapting the shape of one of the blanks (e.g. by grinding an oversize blank), so that a superstructure according to the invention or a core according to the invention results.</li></ul>

0088It goes without saying that the statements made above regarding preferred configurations of the dental substances to be used according to the invention, dental mixtures and dental multi-component systems, the provisional superstructure according to the invention, the core according to the invention and the kit according to the invention also apply accordingly to the methods according to the invention.

0089A particularly preferred method for producing a provisional superstructure for a dental implant or a core for a provisional superstructure for a dental implant or a denture according to the invention comprises the following steps:<ul id="ul0011" list-style="dash"><li>Producing a model of the dental situation from a model mass, the teeth or the teeth to be replaced by the provisional dental superstructure being left out in the model,</li><li>Arranging a manipulation implant in each case on the position or positions of the model which correspond to the position or positions of the dental implant or implants in the dental situation,</li><li>Arranging one abutment (which serves as a model or can be used directly in the oral cavity) on the or each of the manipulation implants, the or each abutment being identical or having the same dimensions as the respective, preferably prefabricated, commercially available one Abutments of the inserted or to be inserted dental implant,</li><li>Applying an insulating layer on the abutment (s) which are arranged on the manipulation implant (s),</li><li>Producing or arranging a removable dental model of the tooth or teeth to be replaced by the provisional dental superstructure on the abutment (s) provided with an insulating layer,</li><li>Creation of a mold by molding the model including the removable dental model,</li><li>Removing the dental model from the abutments provided with an insulating layer and arranged on the manipulation implants,</li><li>renewed application of an insulating layer on the abutments arranged on the manipulation implants,</li><li>Providing or producing a dental substance to be used according to the invention, a dental mixture to be used according to the invention or a dental multicomponent system to be used according to the invention as defined above,</li><li>Filling the mold produced by molding with the dental substance or the dental mixture or the dental mixture or the dental multicomponent system provided or manufactured,</li><li>Placing the filled mold on the abutments provided with an insulating layer on the manipulation implants on the model and then allowing the dental material or the dental mixture or the dental multi-component system to harden,</li><li>preferably removing the mold with the hardened, now molded product (resulting from the dental substance or the dental mixture or the dental multi-component system by means of polymerization curing) from the model,</li><li>Separate the temporary dental superstructure or core formed from the hardened molded product from the mold.</li></ul>

0090It goes without saying that dental implants can preferably be used in the methods according to the invention in combination with commercially available abutments prefabricated by the implant manufacturer for the corresponding implant. For preferred configurations of abutments, we refer to our explanations above, which also apply to the method according to the invention and its preferred configurations.

0091The term "dental situation" denotes the situation in the oral cavity of a patient, in particular a patient who is to be provided with a dental restoration based on an implant.

0092The term “manipulation implants” denotes true-to-shape replicas of the dental implant inserted or to be used at the corresponding position in the oral cavity.

0093The insulating layer used in the preferred method according to the invention described above on the abutment or the abutments arranged on the manipulation implants has the effect, in particular, that a precisely fitting but non-adherent superstructure can be produced on the abutment which serves as a model or can be used directly in the oral cavity. The superstructure must not yet adhere firmly to the abutment in the corresponding process stage, because with a firm bond of abutment and superstructure it would of course no longer be possible to screw the abutment into the implant inserted in the patient's oral cavity in the usual way.

0094The method according to the invention for producing a provisional superstructure, a core for a provisional superstructure or a provisional tooth replacement can preferably be designed as a so-called chair-side method. A (chair-side) method according to the invention for producing a provisional superstructure for a dental implant or a core for a provisional superstructure for a dental implant as defined above or a provisional denture as defined above, with an abutment for the or each dental implant for connecting the temporary superstructure to the dental implant comprises the following steps:<ul id="ul0012" list-style="dash"><li>Creating a model of the dental situation in which the tooth (s) to be replaced by the provisional dental superstructure is still in the patient's mouth, from a model mass, so that the model simulates the tooth (s) to be replaced by the provisional dental superstructure ,</li><li>Insertion of the dental implant (s) with the corresponding abutment in the patient's mouth,</li><li>optionally applying an insulating layer on one or more (model) abutments of the dental implant (s) used in the patient's mouth,</li><li>Creating a shape by molding the model,</li><li>Providing or producing a dental substance to be used according to the invention, a dental mixture to be used according to the invention or a dental multicomponent system to be used according to the invention,</li><li>Filling the mold produced by molding with the dental substance, the dental mixture or the dental multi-component system,</li><li>Placing the filled form on the (model) abutments of the dental implants used in the patient's mouth and then optionally provided with an insulating layer and then allowing the dental material, the dental mixture or the dental multi-component system (which is used as the starting material for Fabrication of the temporary superstructure or the core),</li><li>in some cases, in particular for the purpose of post-processing, removing the mold with the hardened, now molded product from the (model) abutments provided with an insulating layer,</li><li>Separate the temporary superstructure formed from the hardened molded product from the mold.</li></ul>

0095It goes without saying that the method according to the invention can be designed as a chair-side method, but does not have to be designed as a chair-side method. In a large number of cases, it is advantageous to choose a process design instead of a chair-side process in which no single process step takes place in the mouth of or on the patient. Process designs of this type are also referred to as lab-side processes.

0096If pre-fabricated abutments are used in the method according to the invention for producing a provisional superstructure or a core for a provisional superstructure, it is advantageous if the method according to the invention comprises the following further step:<ul id="ul0013" list-style="dash" compact="compact"><li>Provision of a prefabricated abutment for the dental implant to be inserted or inserted, or one prefabricated abutment for each dental implant to be inserted or inserted, and optionally a second prefabricated abutment for the dental implant to be inserted or inserted, or a second prefabricated abutment for each dental implant to be used or inserted Implant, whereby the or the dimensions of the respective second abutment are identical to the respective prefabricated abutment of the dental implant used or to be used.</li></ul>

0097The insulating layer to be applied to (model) abutments in preferred methods according to the invention preferably comprises petroleum jelly or glycerin or consists of these substances.

0098The removable dental model to be used in preferred methods according to the invention is preferably produced in the form of a wax-up model or from light-curing plastic.

0099The form to be used in preferred methods according to the invention is according to a first alternative<ol id="ol0006"><li>(a) a model rail produced by thermoforming a thermoforming film over the model or according to a second alternative</li><li>(b) produced from the model by molding using an impressionable plastic (for example made of silicone material).</li></ol>

0100The mold is preferably transparent, so that irradiation of the dental substance, dental mixture or dental multi-component system filled into the mold with light is possible through the molding material. A dental mixture or multicomponent system to be used according to the invention is preferably light-curing or dual-curing and is hardened in the mold by irradiation through the molding material (polymerization hardening).

0101It goes without saying that the hardened products produced in preferred methods according to the invention can still be reworked to produce a dental superstructure or a corresponding core suitable for immediate use. In some cases, the methods according to the invention therefore include, as a further step, the reworking of the hardened, molded products or the provisional superstructure or of the core, the post-processing preferably being carried out using one or more techniques selected from the group consisting of trimming, milling and polishing.

0102It follows from the explanations above that, in the method according to the invention, the abutments used preferably have no undercuts or undercuts.

0103Provisional superstructures for a dental implant according to the invention are preferably selected from the group consisting of crowns and bridges. Accordingly, cores according to the invention are preferably cores for a temporary crown or bridge.

0104In preferred methods according to the invention for producing a provisional superstructure or a corresponding core, several individual shapes are produced. Each of these individual shapes then serves to produce individual ones of the provisional dental superstructures to be used one after the other, which are said to have increasing hardness (increasing pressure modules, see above).

0105In preferred methods according to the invention, as mentioned, a mold is used for the production of the provisional dental superstructure according to the invention. In a preferred embodiment, a (partial) process for producing this mold comprises the following steps:<ul id="ul0014" list-style="dash"><li>Producing a model of a dental situation from a model mass, the teeth or teeth to be replaced by the provisional superstructure being left out in the model,</li><li>Arranging a manipulation implant in each case on the position or positions of the model which correspond to the position or positions of the dental implant or implants in the dental situation,</li><li>Arranging one (model) abutment on the or each of said manipulation implants, the or each abutment being identical or having the same dimensions as the respective prefabricated abutment of the dental implant used or to be used,</li><li>Applying an insulating layer to the (model) abutments arranged on the manipulation implants,</li><li>Producing or arranging a removable dental model of the tooth or teeth to be replaced by the provisional superstructure on the (model) abutments provided with an insulating layer,</li><li>Creation of a shape by molding the model including the removable dental model.</li></ul>

0106The invention also relates to a method for the provisional care of a dental implant for therapeutic or cosmetic purposes, comprising the steps<ol id="ol0007"><li>(a) provision of a provisional superstructure according to the invention as defined above or provision of a plurality of provisional superstructures according to the invention as defined above and selection of a provisional superstructure, or Provision of several provisional superstructures as defined above and selection of a provisional superstructure,</li><li>(b) connecting the temporary superstructure to the dental implant (preferably by means of an abutment) and then</li><li>(c) allowing a period of time to elapse and thereafter</li><li>(d) loosening the connection (preferably made by means of an abutment) between the provisional superstructure and the dental implant (the preferably used abutment advantageously remaining connected to the implant) and if necessary afterwards the following steps:</li><li>(e) selecting a further provisional superstructure provided in step (a),</li><li>(f) connecting the provisional superstructure selected in step (e) to the dental implant and thereafter</li><li>(g) allowing a period of time to elapse and thereafter</li><li>(h) loosening the connection (preferably made by means of an abutment) between the provisional superstructure and the dental implant (the preferably used abutment advantageously remaining connected to the implant),</li><li>(i) repeating steps (e) to (h) until several or all of the provisional superstructures provided in step (a) have been connected to the implant and the respective connection has been released again.</li></ol>

0107The method according to the invention for the provisional care of a dental implant for cosmetic purposes is preferably carried out with only one provisional superstructure according to the invention as defined above.

0108In a preferred method according to the invention for provisional therapeutic treatment of a dental implant, a plurality of provisional superstructures consisting of or made of core material comprising materials with different pressure modules are provided or produced and connected to the dental implant one after the other in the order of increasing pressure modules.

0109In a particularly preferred method according to the invention for provisional care of a dental implant for therapeutic and / or cosmetic purposes, the, several or all of the provisional superstructures are connected to the dental implant in such a way that the respective provisional superstructure is occluded with the antagonist teeth when the jaw is closed.

0110Finally, the present invention also relates to the use of a dental substance to be used according to the invention, a dental mixture to be used according to the invention or a dental multi-component system to be used according to the invention as defined above for producing a provisional superstructure for a dental implant or a core for a provisional superstructure for a dental implant, preferably a provisional superstructure according to the invention or a core according to the invention as defined above.

0111Further aspects of the present invention result from the following regulations, examples and patent claims.

Specification for determining the maximum pressure module of a dental substance, dental mixture or dental multi-component system that can be achieved by hardening:

1. Manufacture a test specimen:

0112The dental substance, the dental mixture or the dental multicomponent system, the maximum pressure module of which can be determined by hardening, is provided. In the case of a multi-component system, the components are completely mixed so that a dental mixture is formed.

0113It is now cured, the curing conditions depending on the properties of the substance to be examined:<ul id="ul0015" list-style="dash"><li>If the provided dental substance or the provided or manufactured dental mixture can be hardened by irradiation with light up to the maximum achievable pressure module, it is irradiated with light in such a way that its maximum achievable pressure module is reached.</li><li>If the dental substance or dental mixture provided cannot be hardened by irradiation with light, but by chemical hardening up to the maximum achievable pressure module, chemical hardening is initiated if necessary after the addition of initiators, so that the maximum achievable pressure module is achieved .</li><li>If the provided dental material or the dental mixture is not curable by irradiation with light and also not by chemical hardening up to the maximum achievable pressure module, but only by a combination of irradiation with light and chemical hardening, the provided dental material or . the dental mixture provided is both irradiated with light and chemical curing is initiated, so that the maximum achievable pressure module is reached.</li></ul>

0114It is to be determined on the basis of preliminary tests which curing conditions are to be selected in order to reliably achieve the maximum achievable pressure module.

0115The hardening of the provided dental material or the provided dental mixture to a cylindrical test specimen is carried out in a Teflon mold with a cylindrical through hole and an inner diameter of 4.0 mm and a height of 6.0 mm. The dental material or dental mixture provided is filled into the mold and covered on both free sides with a transparent acetate film. The dental substance or dental mixture provided is then cured in the mold under the curing conditions specified above, so that a cylindrical test specimen with a diameter of 4 mm and a height of 6 mm results. The exact dimensions (height = L₀ and diameter = d₀) of the test specimen are determined with a micrometer or a corresponding measuring instrument with a scale of 2 µm or less.

2nd Determination of the pressure modulus of the test specimen produced:

0116To determine the pressure module, the compressive strength is first determined. The pressure module is calculated from the determined measurement data.

0117The determination of the compressive strength is based on EN ISO 9917 part 1.

0118To prepare for the measurement, the cylindrical test specimen produced according to point 1 is placed with the flat surfaces between the pressure stamps of a universal testing machine and loaded at a feed rate of 3 mm / min up to a preload of 5 Newtons. The feed path covered up to the said pre-force is not considered below.

0119To determine the compressive strength (see below (a)) and to determine the pressure module (see below (b)), the test specimen is then subjected to a test speed of 0.5 mm / min until it breaks; the force (F) is recorded as a function of the feed path (L), in mm (starting from L = 0 mm at F = 5 N, see above). A total of at least five test specimens are produced, each of which is used for a measurement:<ol id="ol0008"><li>(a) The maximum force exerted when the test specimen breaks (F_Max) is noted and the <u>Compressive strength</u> (σ) is calculated in megapascals (MPa) using the following equation: <maths id="math0001"><math display="block"><mi>σ</mi><mo>=</mo><mfrac><mrow><mn>4</mn><mo>*</mo><msub><mi>F</mi><mi mathvariant="italic">Max</mi></msub></mrow><mrow><mi>π</mi><mo>*</mo><msubsup><mi>d</mi><mn>0</mn><mn>2</mn></msubsup></mrow></mfrac></math><img file="EP2481391A2_D0001.tif" /></maths>It is F_Max: the maximum force measured at break, in Newtons (N); d₀: the measured diameter of the test specimen, in mm.</li><li>(b) The force (F) determined in the measurement of the compressive strength in Newton is plotted as a function of the feed path (L) in mm. The linear curve range is determined in the range of a feed path between 0.2 mm and 0.5 mm. Then the initial coordinates (L_A and F_A) and the final coordinates (F_E and L_E) of the linear curve area. With the values ​​determined in this way, the<u>Printing module</u> (E), in megapascals (MPa), calculated using the following equation: <maths id="math0002"><math display="block"><mi>E</mi><mo>=</mo><mfrac><mfenced open="[" close="]"><mn>4</mn><mo>*</mo><msub><mi>L</mi><mn>0</mn></msub><mo>*</mo><mfenced><msub><mi>F</mi><mi>E</mi></msub><mo>-</mo><msub><mi>F</mi><mi>A</mi></msub></mfenced></mfenced><mfenced open="[" close="]"><mi>π</mi><mo>*</mo><msubsup><mi>d</mi><mn>0</mn><mn>2</mn></msubsup><mo>*</mo><mfenced><msub><mi>L</mi><mi>> E</mi></msub><mo>-</mo><msub><mi>L</mi><mi>A</mi></msub></mfenced></mfenced></mfrac></math><img file="EP2481391A2_D0002.tif" /></maths>It is L₀: the measured height of the test specimen, in mm; d₀: the measured diameter of the test specimen, in mm; F_A: Force at the beginning of the linear range, in Newtons (N); F_E: Force at the end of the linear range, in Newtons (N); L_A: Feed path at the beginning of the linear range, in mm; L_E: Feed path at the end of the linear range, in mm.</li></ol>

0120The mean value is formed from the at least five determinations carried out in the print module. This mean value for the pressure module is the value for the maximum pressure module that can be achieved by hardening.

0121In the context of the present text it is assumed that the printing module of a provisional superstructure, a core for a provisional superstructure or a corresponding blank corresponds to the printing module of the material from which it was manufactured.

0122It should be noted that the pressure module of a provisional superstructure, a core for a provisional superstructure or the material of a corresponding blank, will generally change in the patient's oral cavity. As a rule, the pressure module of the resulting "wet" products is smaller than that of the "dry" products.

Examples:

0123<ul id="ul0016" list-style="none"><li>The invention is further illustrated by the following examples. Unless otherwise stated, all information is based on weight. The following abbreviations are used:</li><li>UDMA = urethane dimethacrylate (CAS Number 72869-86-4)</li><li>aliphatic urethane dimethacrylate = genomer 4256 from Rahn AG</li><li>Polyethylene glycol dimethacrylate = polyethylene glycol 400 dimethacrylate (n = 9)</li><li>Coinitiator = ethyl<i>pN, N</i>-dimethylaminobenzoate</li><li>Stabilizer = 2,6-Di-<i>tert</i>-butyl-4-methylphenol</li><li>Prepolymer = polymerized alkyl dimethacrylates</li><li>GK = silanized barium aluminosilicate glass (i.e.₅₀= 1.0 µm)</li><li>UV stabilizer = 2- (2H-benzotriazol-2-yl) -<i>p</i>-cresol</li><li>Fumed silica = fumed silica with a BET surface area in the range: 170-230 m²/G</li></ul>

Examples A to F: Manufacture of dental mixtures and multicomponent systems according to the invention

Example A: Preparation of a dental mixture according to the invention

0124The following components were weighed into a beaker:<tables id="tabl0001" num="0001"><table frame="none"><tgroup cols="3" colsep="0" rowsep="0"><colspec colnum="1" colname="col1" colwidth="54mm" /><colspec colnum="2" colname="col2" colwidth="15mm" align="right" /><colspec colnum="3" colname="col3" colwidth="27mm" /><tbody><row><entry>aliphatic urethane dimethacrylate</entry><entry>50.00 g</entry><entry>Component a)</entry></row><row><entry>Polyethylene glycol dimethacrylate</entry><entry>49.65 g</entry><entry>Component a)</entry></row><row><entry>Camphorquinone</entry><entry>0.10 g</entry><entry>Component b)</entry></row><row><entry>Coinitiator</entry><entry>0.15 g</entry><entry>Component b)</entry></row><row><entry>stabilizer</entry><entry>0.10 g</entry><entry>Component d)</entry></row></tbody></tgroup></table></tables>

0125The mixture was then homogenized with a KPG stirrer for 12 hours and then deaerated in the desiccator for two hours.

Example B: Preparation of a dental mixture according to the invention

0126The following components were weighed into a beaker:<tables id="tabl0002" num="0002"><table frame="none"><tgroup cols="3" colsep="0" rowsep="0"><colspec colnum="1" colname="col1" colwidth="54mm" /><colspec colnum="2" colname="col2" colwidth="15mm" /><colspec colnum="3" colname="col3" colwidth="27mm" /><tbody><row><entry>aliphatic urethane dimethacrylate</entry><entry>79.83 g</entry><entry>Component a)</entry></row><row><entry>UDMA</entry><entry>8.65 g</entry><entry>Component a)</entry></row><row><entry>Hexanediol dimethacrylate</entry><entry>11.20 g</entry><entry>Component a)</entry></row><row><entry>Camphorquinone</entry><entry>0.12 g</entry><entry>Component b)</entry></row><row><entry>Coinitiator</entry><entry>0.19 g</entry><entry>Component b)</entry></row><row><entry>stabilizer</entry><entry>0.10 g</entry><entry>Component d)</entry></row></tbody></tgroup></table></tables>

0127The mixture was then homogenized with a KPG stirrer for 12 hours and then deaerated in the desiccator for two hours.

Example C: Preparation of a dental mixture according to the invention in paste form:

0128The following components were weighed into a beaker:<tables id="tabl0003" num="0003"><table frame="none"><tgroup cols="3" colsep="0" rowsep="0"><colspec colnum="1" colname="col1" colwidth="54mm" /><colspec colnum="2" colname="col2" colwidth="15mm" align="right" /><colspec colnum="3" colname="col3" colwidth="27mm" /><tbody><row><entry>aliphatic urethane dimethacrylate</entry><entry>45.56 g</entry><entry>Component a)</entry></row><row><entry>UDMA</entry><entry>4.92 g</entry><entry>Component a)</entry></row><row><entry>Hexanediol dimethacrylate</entry><entry>6.36 g</entry><entry>Component a)</entry></row><row><entry>Camphorquinone</entry><entry>0.07 g</entry><entry>Component b)</entry></row><row><entry>Coinitiator</entry><entry>0.1 g</entry><entry>Component b)</entry></row><row><entry>stabilizer</entry><entry>0.06 g</entry><entry>Component d)</entry></row><row><entry>Pigments</entry><entry>0.04 g</entry><entry>Component e)</entry></row></tbody></tgroup></table></tables>

0129The mixture was then homogenized with a KPG stirrer for 12 hours and deaerated in the desiccator for a further two hours. The fillers for this mixture were:<tables id="tabl0004" num="0004"><table frame="none"><tgroup cols="3" colsep="0" rowsep="0"><colspec colnum="1" colname="col1" colwidth="35mm" /><colspec colnum="2" colname="col2" colwidth="15mm" /><colspec colnum="3" colname="col3" colwidth="27mm" /><tbody><row><entry>Prepolymer</entry><entry>27.06 g</entry><entry>Component c)</entry></row><row><entry>Fumed silica</entry><entry>15.83 g</entry><entry>Component c)</entry></row></tbody></tgroup></table></tables>added and by intimately mixing with a double planetary mixer, a homogeneous paste was prepared.

Example D: Preparation of a dental mixture according to the invention

0130The following components were weighed into a beaker:<tables id="tabl0005" num="0005"><table frame="none"><tgroup cols="3" colsep="0" rowsep="0"><colspec colnum="1" colname="col1" colwidth="55mm" /><colspec colnum="2" colname="col2" colwidth="15mm" /><colspec colnum="3" colname="col3" colwidth="27mm" /><tbody><row><entry>aliphatic urethane dimethacrylate</entry><entry align="right">30.34 g</entry><entry>Component a)</entry></row><row><entry>UDMA</entry><entry align="right">7.45 g</entry><entry>Component a)</entry></row><row><entry>Hexanediol dimethacrylate</entry><entry align="right">3.76 g</entry><entry>Component a)</entry></row><row><entry>Bis-GMA</entry><entry align="right">3.69 g</entry><entry>Component a)</entry></row><row><entry>Triethylene glycol dimethacrylate</entry><entry align="right">1.27 g</entry><entry>Component a)</entry></row><row><entry>Camphorquinone</entry><entry align="right">0.07 g</entry><entry>Component b)</entry></row><row><entry>Coinitiator</entry><entry align="right">0.10 g</entry><entry>Component b)</entry></row><row><entry>stabilizer</entry><entry align="right">0.05 g</entry><entry>Component d)</entry></row><row><entry>GK</entry><entry align="right">22.81 g 0.04 g</entry><entry>Component c) Component d)</entry></row><row><entry>UV stabilizer</entry><entry align="right" /><entry /></row><row><entry>Pigments</entry><entry align="right">0.03 g</entry><entry>Component e)</entry></row></tbody></tgroup></table></tables>

0131The mixture was then homogenized with a KPG stirrer for 12 hours and deaerated in the desiccator for a further two hours. The fillers for this mixture were:<tables id="tabl0006" num="0006"><table frame="none"><tgroup cols="3" colsep="0" rowsep="0"><colspec colnum="1" colname="col1" colwidth="35mm" /><colspec colnum="2" colname="col2" colwidth="15mm" /><colspec colnum="3" colname="col3" colwidth="27mm" /><tbody><row><entry>Fumed silica</entry><entry align="right">12.36 g</entry><entry>Component c)</entry></row><row><entry>Prepolymers</entry><entry align="right">18.04 g</entry><entry>Component c)</entry></row></tbody></tgroup></table></tables>added and by intimately mixing with a double planetary mixer, a homogeneous paste was prepared.

Example E: Production of a dental mixture according to the invention

0132The following components were weighed into a beaker for the preparation of the dental mixtures according to the invention:<tables id="tabl0007" num="0007"><table frame="none"><tgroup cols="3" colsep="0" rowsep="0"><colspec colnum="1" colname="col1" colwidth="54mm" /><colspec colnum="2" colname="col2" colwidth="15mm" /><colspec colnum="3" colname="col3" colwidth="27mm" /><tbody><row><entry>aliphatic urethane dimethacrylate</entry><entry align="right">75.45 g</entry><entry>Component a)</entry></row><row><entry>Polyethylene glycol dimethacrylate</entry><entry align="right">24.20 g</entry><entry>Component a)</entry></row><row><entry>Camphorquinone</entry><entry align="right">0.10 g</entry><entry>Component a)</entry></row><row><entry>Coinitiator</entry><entry align="right">0.15 g</entry><entry>Component d)</entry></row><row><entry>stabilizer</entry><entry align="right">0.11 g</entry><entry>Component b)</entry></row></tbody></tgroup></table></tables>

0133The mixture was then homogenized with a KPG stirrer for 12 hours and deaerated in the desiccator for a further two hours.

Example F: Production of a dental multicomponent system according to the invention

Example F1: Preparation of the catalyst mixture

0134The following components were weighed into a beaker for the preparation of the catalyst mixture:<tables id="tabl0008" num="0008"><table frame="none"><tgroup cols="3" colsep="0" rowsep="0"><colspec colnum="1" colname="col1" colwidth="54mm" /><colspec colnum="2" colname="col2" colwidth="15mm" /><colspec colnum="3" colname="col3" colwidth="27mm" /><tbody><row><entry>aliphatic urethane dimethacrylate</entry><entry align="right">48.78 g</entry><entry>Component a)</entry></row><row><entry>Polyethylene glycol dimethacrylate</entry><entry align="right">48.96 g</entry><entry>Component a)</entry></row><row><entry>stabilizer</entry><entry align="right">0.12 g</entry><entry>Component b)</entry></row><row><entry>Benzoyl peroxide</entry><entry align="right">2.14 g</entry><entry>Component b)</entry></row></tbody></tgroup></table></tables>

0135The mixture was then homogenized with a KPG stirrer for 12 hours and deaerated in the desiccator for a further 2 hours.

Example F2: Preparation of the base mixture

0136The following components were weighed into a beaker for the preparation of the basic mixture:<tables id="tabl0009" num="0009"><table frame="none"><tgroup cols="3" colsep="0" rowsep="0"><colspec colnum="1" colname="col1" colwidth="54mm" /><colspec colnum="2" colname="col2" colwidth="15mm" /><colspec colnum="3" colname="col3" colwidth="27mm" /><tbody><row><entry>aliphatic urethane dimethacrylate</entry><entry align="right">48.84 g</entry><entry>Component a)</entry></row><row><entry>Polyethylene glycol dimethacrylate</entry><entry align="right">48.84 g</entry><entry>Component a)</entry></row><row><entry><i>N, N</i>-Bis (2-hydroxyethyl) -<i>p</i>-toluidine</entry><entry align="right">1.53 g</entry><entry>Component b)</entry></row><row><entry>Camphorquinone</entry><entry align="right">0.31 g</entry><entry>Component b)</entry></row><row><entry>Coinitiator</entry><entry align="right">0.45 g</entry><entry>Component b)</entry></row></tbody></tgroup></table></tables>

0137The mixture was homogenized with a KPG stirrer for 12 hours and deaerated in the desiccator for a further 2 hours.

Example G: Determination of Material Properties of the Dental Mixtures and Dental Multi-Component Systems Produced in Examples A to F:

0138The dental mixtures according to the invention or the dental multicomponent system according to Example F produced in Examples A to E (after mixing the components in a volume ratio of 1: 1) were used according to the above "specification for determining the maximum pressure module of a dental substance, dental mixture, which can be achieved by curing or dental multi-component system "for their pressure module. Portions of the dental multi-component system according to Example F were cured for test purposes both with light irradiation (dual-cure) and without light irradiation (chemical curing). After removal from the mold, the test specimens were stored dry at 37 ° C. and then measured. For comparison, the self-hardening temporary crown material Structur 2 SC from VOCO GmbH was examined. The measured values ​​are summarized in the following table:<tables id="tabl0010" num="0010"><table frame="all"><tgroup cols="6"><colspec colnum="1" colname="col1" colwidth="24mm" /><colspec colnum="2" colname="col2" colwidth="30mm" /><colspec colnum="3" colname="col3" colwidth="31mm" /><colspec colnum="4" colname="col4" colwidth="30mm" /><colspec colnum="5" colname="col5" colwidth="25mm" /><colspec colnum="6" colname="col6" colwidth="30mm" /><thead><row><entry valign="middle">example</entry><entry valign="top">Compressive strength [MPa]</entry><entry valign="top">Pressure module [MPa]</entry><entry valign="top">Extensibility [mm]</entry><entry valign="top">Max. Force [N]</entry><entry valign="top">Force at 1 mm [N]</entry></row></thead><tbody><row><entry>A dry</entry><entry align="center" valign="bottom">58</entry><entry align="center" valign="bottom">21</entry><entry align="center" valign="bottom">3,0</entry><entry align="center" valign="bottom">308</entry><entry align="center" valign="bottom">53</entry></row><row><entry>B dry</entry><entry align="center" valign="bottom">112</entry><entry align="center" valign="bottom">16</entry><entry align="center" valign="bottom">2,4</entry><entry align="center" valign="bottom">60</entry><entry align="center" valign="bottom">53</entry></row><row><entry>C dry</entry><entry align="center" valign="bottom">45</entry><entry align="center" valign="bottom">92</entry><entry align="center" valign="bottom">3,0</entry><entry align="center" valign="bottom">370</entry><entry align="center" valign="bottom">108</entry></row><row><entry>D dry</entry><entry align="center" valign="bottom">96</entry><entry align="center" valign="bottom">400</entry><entry align="center" valign="bottom">1,6</entry><entry align="center" valign="bottom">920</entry><entry align="center" valign="bottom">619</entry></row><row><entry>E dry</entry><entry align="center" valign="bottom">44</entry><entry align="center" valign="bottom">4</entry><entry align="center" valign="bottom">3,0</entry><entry align="center" valign="bottom">105</entry><entry align="center" valign="bottom">29</entry></row><row rowsep="0"><entry>F</entry><entry align="center" valign="bottom" /><entry align="center" valign="bottom" /><entry align="center" valign="bottom" /><entry align="center" valign="bottom" /><entry align="center" valign="bottom" /></row><row rowsep="0"><entry>dry DC *</entry><entry align="center" valign="bottom">226</entry><entry align="center" valign="bottom">11</entry><entry align="center" valign="bottom">2,82</entry><entry align="center" valign="bottom">323</entry><entry align="center" valign="bottom">60</entry></row><row><entry>dry CC^#</entry><entry align="center" valign="bottom">221</entry><entry align="center" valign="bottom">14</entry><entry align="center" valign="bottom">2,75</entry><entry align="center" valign="bottom">253</entry><entry align="center" valign="bottom">59</entry></row><row><entry><i>Structure 2</i> SC</entry><entry align="center" valign="bottom">277</entry><entry align="center" valign="bottom">1170</entry><entry align="center" valign="bottom">nb<img file="EP2481391A2_D0003.tif" /></entry><entry align="center" valign="bottom">nb</entry><entry align="center" valign="bottom">nb</entry></row></tbody></tgroup><tgroup cols="6" rowsep="0"><colspec colnum="1" colname="col1" colwidth="24mm" /><colspec colnum="2" colname="col2" colwidth="30mm" /><colspec colnum="3" colname="col3" colwidth="31mm" /><colspec colnum="4" colname="col4" colwidth="30mm" /><colspec colnum="5" colname="col5" colwidth="25mm" /><colspec colnum="6" colname="col6" colwidth="30mm" /><tbody><row><entry namest="col1" nameend="col6" align="justify">* DC: dual hardened (light + chemical); ^#CC: chemically hardened;<img file="EP2481391A2_D0004.tif" />The extensibility could not be determined due to the hardness of the material; nb: not determined</entry></row></tbody></tgroup></table></tables>

0139The results of the investigations show that the examples AF according to the invention have led to products / materials which can be used excellently in progressive bone loading therapy as the material of superstructures.

Example H: Investigation of the adhesion of hardened dental mixtures according to the invention and dental multicomponent systems to metallic substrates (tensile test):

0140In order to compare the adhesion of the dental superstructures according to the invention, to metallic abutments, with the adhesion of superstructures made from known materials to metallic abutments, superstructure test bodies were produced on an abutment test body made of stainless steel.

0141The superstructure test bodies consisted of:<ol id="ol0009"><li>a) a commercially available silicone material (addition-crosslinking silicone; Fit Test (VOCO), pressure module &lt;420 MPa),</li><li>b) a commercially available methacrylate material (cold-polymerizing paste-paste system; Structure 2 SC (VOCO)),</li><li>c) a dental multi-component system according to the invention according to Example F and</li><li>d) a dental mixture according to the invention according to Example D.</li></ol>

0142The pull-off force was then measured using a universal testing machine by pulling the model abutment out of the superstructure. The following values ​​for the pull-off force could be determined:<tables id="tabl0011" num="0011"><table frame="all"><tgroup cols="2"><colspec colnum="1" colname="col1" colwidth="18mm" /><colspec colnum="2" colname="col2" colwidth="31mm" /><thead><row><entry valign="top">sample</entry><entry valign="top">Peel force [MPa]</entry></row></thead><tbody><row><entry>a)</entry><entry>0,33</entry></row><row><entry>b)</entry><entry>2,95</entry></row><row><entry>c)</entry><entry>0,68 *</entry></row><row><entry>d)</entry><entry>2,34</entry></row></tbody></tgroup><tgroup cols="2" rowsep="0"><colspec colnum="1" colname="col1" colwidth="18mm" /><colspec colnum="2" colname="col2" colwidth="31mm" /><tbody><row><entry namest="col1" nameend="col2" align="justify">* In sample c) the metal abutment was not pulled out of the superstructure, but the material of the superstructure tore.</entry></row></tbody></tgroup></table></tables>