Classifications

• • A—HUMAN NECESSITIES
  • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
  • A61C—DENTISTRY; APPARATUS OR METHODS FOR ORAL OR DENTAL HYGIENE
  • A61C5/00—Filling or capping teeth
  • A61C5/70—Tooth crowns; Making thereof
  • A61C5/73—Composite crowns
• • A—HUMAN NECESSITIES
  • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
  • A61K—PREPARATIONS FOR MEDICAL, DENTAL OR TOILETRY PURPOSES
  • A61K6/00—Preparations for dentistry
  • A61K6/70—Preparations for dentistry comprising inorganic additives
  • A61K6/71—Fillers
  • A61K6/77—Glass
• • A—HUMAN NECESSITIES
  • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
  • A61C—DENTISTRY; APPARATUS OR METHODS FOR ORAL OR DENTAL HYGIENE
  • A61C13/00—Dental prostheses; Making same
  • A61C13/0003—Making bridge-work, inlays, implants or the like
  • A61C13/0022—Blanks or green, unfinished dental restoration parts
• • A—HUMAN NECESSITIES
  • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
  • A61C—DENTISTRY; APPARATUS OR METHODS FOR ORAL OR DENTAL HYGIENE
  • A61C13/00—Dental prostheses; Making same
  • A61C13/225—Fastening prostheses in the mouth
  • A61C13/26—Dentures without palates; Partial dentures, e.g. bridges
• • A—HUMAN NECESSITIES
  • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
  • A61C—DENTISTRY; APPARATUS OR METHODS FOR ORAL OR DENTAL HYGIENE
  • A61C5/00—Filling or capping teeth
  • A61C5/20—Repairing attrition damage, e.g. facets
• • A—HUMAN NECESSITIES
  • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
  • A61C—DENTISTRY; APPARATUS OR METHODS FOR ORAL OR DENTAL HYGIENE
  • A61C5/00—Filling or capping teeth
  • A61C5/70—Tooth crowns; Making thereof
  • A61C5/77—Methods or devices for making crowns
• • A—HUMAN NECESSITIES
  • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
  • A61C—DENTISTRY; APPARATUS OR METHODS FOR ORAL OR DENTAL HYGIENE
  • A61C8/00—Means to be fixed to the jaw-bone for consolidating natural teeth or for fixing dental prostheses thereon; Dental implants; Implanting tools
  • A61C8/0012—Means to be fixed to the jaw-bone for consolidating natural teeth or for fixing dental prostheses thereon; Dental implants; Implanting tools characterised by the material or composition, e.g. ceramics, surface layer, metal alloy
  • A61C8/0016—Means to be fixed to the jaw-bone for consolidating natural teeth or for fixing dental prostheses thereon; Dental implants; Implanting tools characterised by the material or composition, e.g. ceramics, surface layer, metal alloy polymeric material
• • A—HUMAN NECESSITIES
  • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
  • A61K—PREPARATIONS FOR MEDICAL, DENTAL OR TOILETRY PURPOSES
  • A61K6/00—Preparations for dentistry
  • A61K6/15—Compositions characterised by their physical properties
  • A61K6/17—Particle size
• • A—HUMAN NECESSITIES
  • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
  • A61K—PREPARATIONS FOR MEDICAL, DENTAL OR TOILETRY PURPOSES
  • A61K6/00—Preparations for dentistry
  • A61K6/30—Compositions for temporarily or permanently fixing teeth or palates, e.g. primers for dental adhesives
• • A—HUMAN NECESSITIES
  • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
  • A61C—DENTISTRY; APPARATUS OR METHODS FOR ORAL OR DENTAL HYGIENE
  • A61C2201/00—Material properties

Definitions

• the invention relates to a polymerizable, dental composite material comprising
• dental composites There are many dental composites known that are universally applicable for a direct adhesive restoration, as well as for the extraoral production of indirect dentures. From the material class of the dental composite are suitable in principle only the inorganic-organic hybrid materials with larger amounts of inorganic filler such. Dental glass and / or mineral nano-agglomerates. The micro-fiber composites with pre-polymer fillers introduced in the 1980s are not suitable for use in the posterior region (classes I and II) due to the limited wear resistance (abrasion resistance).
• a high filler content is advantageous in order to achieve very good mechanical properties of the cured composite and at the same time to reduce the polymerization shrinkage that occurs during curing. These properties are also decisive for the long-term success of the denture material.
• the object of the invention was to provide a dental composite material which is suitable for the production of larger blocks of material, in particular of geometric shaped bodies, such as milling blocks. Furthermore, the object was a dental composite material to provide a homogeneous, monochrome staining before and after the polymerization. In this case, the homogeneous, monochrome dyeing should be feasible even with larger blocks of material. Furthermore, polychrome, ie multi-colored blocks of material with defined color should be produced. In addition, a dental composite material should be provided which is easily flowable in the unpolymerized state and yet has excellent mechanical properties in the polymerized state and has low shrinkage in the polymerization, even when producing larger blocks of material.
• the composite material during curing even in large-volume material blocks, neither cracks or pores develop.
• the filler system, the monomer mixture, and the pigment system had to be modified.
• the wide particle size distribution advantageous for a high packing density and excellent mechanical properties could not be maintained.
• a narrow particle size distribution has been developed.
• the mean value of the particle size distribution was set to a range of 0.7 ⁇ m to 7.5 ⁇ m.
• further dental glass fractions with differing smaller and / or larger particle size distributions can be added in order to optimally match the packing density.
• the matched packing density enables optimal adjustment of mechanical properties and reduced shrinkage.
• the shaping for the production of the blocks of material takes place by introducing the polymerizable dental composite material into a casting mold, hereinafter referred to as mold only, in particular under pressure.
• the applied pressure is preferably 500 to 300 MPa. or [N / mm 2 ].
• the polymerization is carried out at elevated temperature, which is preferably in the range of about 90 to 150 ° C. It is polymerized in a closed mold to minimize, preferably avoid, the formation of air bubbles. Preference is given to polymerizing under a pressure of from 120 to 320 MPa, preferably to less than or equal to 300 MPa, and / or at a temperature of from 100 to 180 ° C., preferably around 140 ° C., for at least 10 minutes to 10 hours.
• the material blocks preferably have at least one dimension of 1 cm in all spatial directions and are present as geometric shaped bodies.
• composites based on a urethane monomer with alicyclic structural element, such as tetrahydrodicyclopentadiene are extremely well suited for the production of indirect dental prostheses, since surprisingly high flexural strengths can be achieved by the thermally initiated polymerization.
• the high level of polymer strength compared to the already described photopolymerization in the case of light-curing dental composites was surprising and not expected with these significantly increased values.
• the low-shrinkage crosslinking of the relatively large composite quantity in one process step is advantageous in order to avoid stress cracks in the block / blank.
• High crosslinking densities, which are desirable for the material strength can often lead to unusability of the polymerized molded parts due to the high shrinkage stresses.
• the invention relates to a polymerizable, dental composite material, in particular a thermally polymerizable composite material comprising
• Urethane (meth) acrylates preferably a mixture of at least three different urethane (meth) acrylates, in particular of di- to deca-functional urethane (meth) acrylates, (iii) 0.01 to 5% by weight of at least one di-, tri-, tetra- or multi-functional monomer which is not a urethane (meth) acrylate,
• thermally polymerizable composite material is additionally polymerizable photochemically.
• a thermally polymerizable composite material is understood as meaning a composite material that can be polymerized at greater than or equal to 60 to 150 ° C., preferably at greater than or equal to 70 to 150 ° C., particularly preferably from 90 to 150 ° C. It is further preferred according to the invention if the volume shrinkage is less than or equal to 1, 5%.
• a polymerized composite material having a flexural strength of greater than or equal to 200 MPa, in particular greater than or equal to 220 MPa, and a modulus of elasticity of from 15 to 20 GPa, in particular 16 GPa to 20 GPa, is stored in dry storage.
• This composite material preferably has a flexural strength of greater than or equal to 170 MPa and a modulus of elasticity of 14 to 21 GPa after storage in deionized water for 7 days at 37 ° C followed by thermocycling.
• the polymerized composite material is preferably present as a material block, in particular in the form of a milling blank having a dimension of at least 10 mm in all spatial directions.
• the composite material according to the invention is thermally polymerizable, wherein a polymerized composite material is obtainable with a flexural strength of greater than or equal to 200 MPa to 260 MPa (7 days, 23 ⁇ 2 ° C, dry) and a modulus of elasticity greater than or equal to 15 to 20 GPa (7 days, 23 ⁇ 2 ° C, dry) according to EN ISO 6872: 2008, in particular with a flexural strength of greater than or equal to 210 MPa, preferably greater than or equal to 220 MPa and an modulus of greater than or equal to 16 to 20 GPa, preferably greater than or equal to 17 GPa to 20 GPa, more preferably from 18 to 20 GPa.
• the subject matter of the invention is a thermally polymerisable composite material, wherein a polymerized composite material is obtainable with a flexural strength of greater than or equal to 160 MPa to 260 MPa (7 days stored in H 2 O deionized at 37 ° C, followed by greater than or equal to 1000 cycles, in particular greater than or equal to about 5000 cycles (5 ° C to 55 ° C, residence time greater than or equal to 30 seconds, optionally up to 60 seconds)) and a modulus of elasticity greater than or equal to 14 to 21 GPa (7 days stored in H 2 O deionized at 37 ° C, followed by greater than or equal 1000 cycles, in particular 5000 cycles (5 ° C to 55 ° C, residence time greater than or equal to 30 seconds) according to EN ISO 6872: 2008, in particular with a flexural strength of greater than or equal to 170 MPa, preferably greater than or equal to 210 MPa and an modulus of greater than or equal to 15 to 21 GPa, preferably greater than or equal to 16
• the inorganic filler component consists of at least one dental glass or a mixture of dental glasses, in particular an aforementioned average particle size, and an amorphous metal oxide, in particular a non-agglomerated amorphous metal oxide, preferably a silanized amorphous metal oxide.
• the dental glass may preferably also be silanized.
• Preferred dental glasses are: aluminosilicate glasses or fluoroaluminosilicate glasses, barium aluminum silicate, strontium silicate, strontium borosilicate, lithium silicate and / or lithium aluminum silicate and mixtures of at least two of the aforementioned dental glasses.
• amorphous metal oxide or as a mixture of amorphous metal oxides it is possible to use amorphous spherical fillers based on oxide or mixed oxide, such as amorphous SiO 2 , ZrO 2 or mixed oxides of SiO 2 and ZrO 2 .
• the invention also provides a dental composite material comprising
• a dental glass having a mean particle size d 50 of 1, 5 ⁇ with plus / minus 0.25 ⁇ and preferably d 99 less than or equal to 10 ⁇ , especially d 99 less than or equal to 10 ⁇ , or
• a dental glass comprising a mixture of dental glasses of different fractions with average particle sizes with i) d 50 of 2 to 8 ⁇ optionally with plus / minus 0.5 ⁇ , in particular with 4 to 6 ⁇ optionally with plus / minus 0.25 ⁇ , ii) d 50 of 1, 0 to 2.0 ⁇ optionally with plus / minus 0.25 ⁇ , in particular with 1, 2 to 1, 7 ⁇ optionally with plus / minus 0.5 ⁇ , preferably with 1, 5 ⁇ optional with plus / minus 0.15 ⁇ , and iii) d 5 o of 0.5 ⁇ to 1, 2 ⁇ optionally with plus / minus 0.15 ⁇ , 0.7 to 0.9 ⁇ optionally with plus / minus 0, 5 ⁇ , wherein the fractions of i) to ii) to iii) in Ratio of 1 to 4: 1: 4 to 8, in particular from 2 to 3: 1: 6 to 7 are present.
• d 5 o of 5 ⁇ optionally with plus / minus 0.5 ⁇
• iii) d 5 o of 0.85 ⁇ optional plus / minus 0.15 ⁇ wherein the fractions of i) to ii) to iii) in the ratio of 1 to 4: 1: 4 to 8, in particular from 2 to 3: 1: 6 to 7 are present.
• the dental composite material comprises at least one dental glass, in particular a radiopaque dental glass, an average particle size d 50 of 1, 2 to 1, 7 ⁇ , preferably with an average particle size of 1, 35 to 1, 65 ⁇ , in particular with d 50 of 1, 5 ⁇ optional plus / minus 0.15 ⁇ , and preferably with d 99 less than or equal to 10 ⁇ .
• a dental glass present with an average particle size of d 5 o of about 0.85 ⁇ optional plus / minus 0.1 ⁇ , in particular plus / minus 0.05 ⁇ , preferably plus / minus 0.03 ⁇ , and preferably with d 99 less than or equal to 10 ⁇ .
• a particularly preferred dental glass comprises barium aluminum borosilicate glass.
• a barium aluminum silicate glass having a refractive index of n 1, 52 to 1, 55, preferably 1, 53, is particularly preferred.
• a particularly preferred particle size distribution can be in the range of di 0 with greater than or equal to 0.2 ⁇ to d 99 less than or equal to 7.5 ⁇ , preferably with dio greater than or equal to 0.4 ⁇ to d 99 smaller than 7.5 ⁇ and a mean diameter d 50 from 0.7 to 7.5 ⁇ .
• -% is present in relation to the composite material, in particular from greater than or equal to 55 to 76 wt .-%, preferably greater than or equal to 60 to 75 wt .-%, particularly preferably greater than or equal to 60 to 71 wt .-% in the overall composition. More preferably in combination with an amorphous silica with 4 to 7.5 wt .-% in the total composition.
• the invention further provides a dental composite material comprising (i) from 70 to 85% by weight of at least one inorganic filler component comprising at least one dental glass comprising barium aluminum borosilicate glass, barium aluminum borofluorosilicate glass, in particular silanized, preferably functionalized with methacryloxypropyl groups and optionally at least one non-agglomerated amorphous metal oxide having a primary particle size of 2 to 45 nm, the amorphous metal oxide being precipitated silica, precipitated silica, Zirconia, mixed oxides or mixtures thereof, in particular the metal oxides are silanized.
• the dental composite material preferably comprises as inorganic filler component (i.1) 66 to 84% by weight of at least one dental glass, in particular from 68 to 78% by weight, alternatively from 75 to 78% by weight and optionally (i.2) 2 to 10% by weight of amorphous metal oxide, in particular from 3 to 10% by weight, preferably 4 to 8% by weight, in the overall composition.
• the ratio of dental glass to amorphous metal oxide is preferably from 20: 1 to 5: 1, preferably from 15: 1 to 10: 1.
• inorganic filler component are preferably from 85 to 99 wt .-% of at least one dental glass or a mixture of dental glasses, preferably from 85 to 91 wt .-%, alternatively 92 to 99 wt .-%, and optionally 1 to 13 wt. %, in particular 8 to 15 wt .-%, alternatively 1 to 8 wt .-% of amorphous metal oxide or mixture of metal oxides, in particular fumed silica and / or precipitated silica, in the filler component before.
• the dental composite material comprises
• At least one dental glass having an average particle size d 50 of 0.7 to 7.5 ⁇ m, in particular of 1.5 ⁇ m, optionally with a standard deviation mentioned above, and optionally (i.2) 1 to 34% by weight, in particular from 3 to 15 wt .-%, preferably 3 to 10 wt .-%, particularly preferably 4 to 10 wt .-% of at least one amorphous, silanized metal oxide and / or fumed silica of a primary particle size of 2 to 45 nm, with respect the overall composition,
• the di- to deca-functional urethane (meth) acrylates are used as monomers and do not include peroxy groups.
• the dental composite material (ii) comprises 10 to 30% by weight of a mixture of at least two different urethane (meth) acrylates, preferably of three different urethane (meth) acrylates, comprising at least one difunctional urethane (meth) A bivalent alicyclic acrylate, in particular comprising bis- (4 ', 7'-dioxa-3', 8'-dioxo-2'-aza-decyl-9'-ene) tetrahydro-dicyclopentadiene, bis (4 ' , 7'-dioxa-3 ', 8'-dioxo-2'-aza-9'-methyl-decyl-9'-ene) tetrahydrodicyclopentadiene and / or mixtures thereof and optionally mixtures of 3,8- / 3, 9- / 4,8- / 3,10- / 4,10-isomers and / or the cis and trans is
• the dental composite material (ii) comprises 10 to 30% by weight of a mixture of at least two different urethane (meth) acrylates comprising at least one difunctional bivalent alicyclic urethane (meth) acrylate selected from Bis- (4 ', 7'-dioxa-3', 8'-dioxo-2'-aza-decyl-9'-ene) tetrahydrodicyclopentadiene, bis- (4 ', 7'-dioxa-3', 8'- dioxo-2'-aza-9'-methyl-decyl-9'-ene) tetrahydro-dicyclopentadiene and / or mixtures thereof and, optionally, mixtures of the 3,8- / 3,9- / 4,8- / 3,10- / 4,10-isomers and / or the cis and trans isomers of the abovementioned compounds, and at least one further difunctional urethane (meth) acryl
• the dental composite material (ii) comprises a mixture of at least two different urethane (meth) acrylates, preferably of three different urethane (meth) acrylates.
• (meth) acrylates or urethane (meth) acrylate with (meth) in parenthesis means that the term can include acrylates or urethane acrylates with and without methyl group.
• the dental composite material (ii) comprises 10 to 30 wt .-% of a mixture of at least two different urethane (meth) acrylates, preferably of at least three different urethane (meth) acrylates comprising at least one difunctional urethane (meth ) bivalent alicyclic group-containing acrylate and at least one difunctional urethane (meth) acrylate having a bivalent alkylene group and optionally at least one at least tetrafunctional dentrist urethane (meth) acrylate, preferably at least one hexafunctional dendritic urethane (meth) acrylate.
• bifunctional alicyclic difunctional urethane (meth) acrylates comprising or selected from bis (4 ', 7'-dioxa-3', 8'-dioxo-2'-aza-decyl-9'-ene) tetrahydrodicyclopentadiene, Bis (4 ', 7'-dioxa-3', 8'-dioxo-2'-aza-9'-methyl-decyl-9'-ene) tetrahydrodicyclopentadiene and / or mixtures thereof and, optionally, mixtures of the 3,8- / 3,9- / 4,8- / 3,10- / 4,10-isomers and / or the cis and trans isomers of the aforementioned compounds.
• the difunctional bicyclic alicyclic urethane acrylate is particularly preferably selected from bis (4 ', 7'-dioxa-3', 8'-dioxo-2'-aza-decyl-9'-ene) tetrahydrodicyclopentadiene, bis (4 ' , 7'-dioxa-3 ', 8'-dioxo-2'-aza-9'-methyl-decyl-9'-ene) tetrahydrodicyclopentadiene and / or mixtures thereof and, optionally, mixtures of the 3,8- / 3,9- / 4,8- / 3,10- / 4,10-isomers and / or the cis and trans isomers of the aforementioned compounds.
• the bivalent alkylene difunctional urethane (meth) acrylate is preferably selected from linear or branched bivalent alkylene functionalized urethane dimethacrylates, urethane dimethacrylate functionalized polyethers having alkylene group (s) such as bis (methacryloxy-2-ethoxycarbonylamino) alkylene , Bis (methacryloxy-2-ethoxycarbonylamino) substituted polyalkylene ethers, preferably 1,6-bis (methacryloxy-2-ethoxycarbonylamino) -2,4,4-trimethylhexane, UDMA with alternative designation HEMA-TDMI.
• alkylene group (s) such as bis (methacryloxy-2-ethoxycarbonylamino) alkylene , Bis (methacryloxy-2-ethoxycarbonylamino) substituted polyalkylene ethers, preferably 1,6-bis (methacryloxy-2-ethoxycarbonylamino) -2,4,4-
• alkylene comprises linear or branched C3 to C20, preferably C3 to C6, more preferably a methyl group substituted alkylene, such as HEMA-TMDI.
• the bivalent alkylene preferably comprises 2,2,4-trimethylhexamethylene and / or 2,4,4-trimethylhexamethylene.
• the at least tetra-functional dendritic urethane methacrylate comprises tetra- to deca-functional dendritic urethane methacrylates.
• (ii) comprises 10 to 30% by weight of a mixture of at least two different urethane (meth) acrylates relative to the total composition, preferably 15 to 20% by weight, such as at least one difunctional urethane (meth ) bivalent alicyclic group-containing acrylate and at least one hexafunctional dendritic urethane (meth) acrylate and optionally at least one bivalent alkylene difunctional urethane (meth) acrylate.
• the composite material comprises from 5 to 25% by weight, in particular from 15 to 19% by weight, of bis (4 ', 7'-dioxa-3', 8'-dioxo-2'-aza-decyl-9 ' -en) tetrahydrodicyclopentadiene, bis (4 ', 7'-dioxa-3', 8'-dioxo-2'-aza-9'-methyl-decyl-9'-ene) tetrahydrodicyclopentadiene and / or mixtures thereof and optionally mixtures of the 3,8- / 3,9- / 4,8- / 3,10- / 4,10-isomers and / or of the cis and trans isomers of the abovementioned compounds, 1 to 15% by weight, in particular 5 to 6 wt .-% UDMA (1,6-bis (methacryloxy-2-ethoxycarbonylamino) -2,4,4-trimethylhexane
• the composite material comprises 10 to 20% by weight of a mixture of at least three different urethane (meth) acrylates selected from 10 to 18% by weight comprising bis (4 ', 7'-dioxa-3'8'-dioxo -2'-aza-decyl-9'-ene) tetrahydrodicyclopenta-diene, bis- (4 ', 7'-dioxa-3', 8'-dioxo-2'-aza-9'-methyl-decyl-9 ' -en) tetrahydrodicyclopentadiene and / or mixtures thereof and optionally mixtures of the 3,8- / 3,9- / 4,8- / 3,10- / 4,10-isomers and / or the cis and trans isomers of the abovementioned Compounds containing 3 to 8% by weight of a difunctional urethane (meth) acrylate having a bivalent alkylene group, in
• the dental composite material as component (iii) comprises 0.01 to 5% by weight of at least one di-, tri-, tetra- or multifunctional monomer which is not urethane acrylate and is selected from di-methacrylic esters of polyethers, tri-, tetra- or multifunctional methacrylic esters of polyethers.
• the content of components (iii) is preferably from 0.15 to 5% by weight, particularly preferably from 0.1 to 2% by weight, of a di-methacrylic ester of a polyether, such as preferably a dimethacrylate-polyethylene glycol, dimethacrylate-polypropylene glycol. Particularly preferred are dimethacrylate triethylene glycol (TEGDMA), diethylene glycol dimethacrylate (DEGMA) and dimethacrylate tetraethylene glycol (TEDMA).
• TEGDMA dimethacrylate triethylene glycol
• DEGMA diethylene glycol dimethacrylate
• TEDMA dimethacrylate tetraethylene glycol
• Water was added to the composite dental material as a stabilizer to improve the consistency and flowability of process engineering processability. Stabilizers have been added to the composite material to prevent premature polymerization and to give the material some shelf life.
• the composite material in component (iv) comprises at least one stabilizer selected from water, at least one benzophenone derivative, preferably alkoxy-substituted benzophenone and / or phenol derivative such as 2-hydroxy-4-methoxybenzophenone, 2,6-bis (1, 1-dimethyl) -4-methylphenol, or a mixture of the three stabilizers.
• the stabilizers are preferably present in the total composition at from 0.01 to 14% by weight, more preferably from 0.7 to 10% by weight, in particular of 0.5 to 2 wt .-%.
• the composite material contains 0.01 to 2% by weight of water as stabilizer, preferably 0.1 to 1.0% by weight of water.
• At least one pigment comprising at least one fluorescent pigment and optionally at least one organic color pigment and / or at least one inorganic color pigment, in particular non-fluorescent color pigments, are added to the composite material.
• the at least one fluorescent pigment is preferably an organic fluorescent pigment, in particular a non-polymerizable organic fluorescent pigment optionally comprising arylcarboxylic acid esters, arylcarboxylic acids, coumarin, rhodamine, naphthanimide or a derivative of the respective substance.
• Inorganic fluorescent pigments may include CaAl 4 O 7 : Mn 2+ , (Ba 0 .98 Eu 0 .2) MgAl 10 Oi 7 , BaMgF 4 : Eu 2+ , Y (1,995) Ce (0.005) SiO 5 .
• the composite may comprise organic pigments and also inorganic pigments, in particular comprising diethyl 2,5-dihydroxyterephthalate, N, N'-bis (3,5-xylyl) perylene-3,4: 9, 10-bis (dicarbimide), copper phthalocyanine, titanate pigment, especially chromium titanate titanate (rutile structure), spinel black, especially pigments based on iron oxide black (Fe 3 O 4 ), wherein iron (Fe) is partially substituted by chromium and copper or nickel and chromium or manganese , Zinc-iron chrome spinel brown spinel; ((Zn, Fe) (Fe, Cr) 2 0 4 ) Cobalt zinc aluminate blue spinel and / or titanium oxide.
• organic pigments and also inorganic pigments in particular comprising diethyl 2,5-dihydroxyterephthalate, N, N'-bis (3,5-xylyl) perylene-3,4: 9, 10-bis (dicarbimide
• the pigments comprising fluorescent and color pigments are preferably present at 0.01 to 10 wt .-% in the total composition, particularly preferably from 0.01 to 5 wt .-%, preferably from 0.01 to 1 wt .-%.
• the choice of pigments must be specifically tailored to the dental composite composition in order to be able to set a homogeneous color both in the polymerizable composite and in the polymerized composite. Also, the production of the large blocks of material requires a vote on the selection, as well as the concentration of the pigments to avoid unwanted discoloration due to the dimensioning of the polymerized blocks of material.
• Suitable initiators in particular thermal initiators or initiator systems, are peroxides, hydroxyperoxides, optionally azo compounds, or mixtures thereof.
• Suitable thermal initiators can be used as free-radical initiators in the temperature range from 70 to 150 ° C., preferably from 90 to 150 ° C, can be used.
• Preferred thermal initiators comprise at least one initiator selected from: dilauroyl peroxide, di-tert-butyl peroxide, tert-butyl peroxy-2-ethylhexanoate, dibenzoyl peroxide, dicumyl peroxide, dicumyl hydroperoxide, 2,2'-azobisisobutyronitrile, benzylbarbituric acid derivative, particularly preferably tert-butyl peroxy-2-ethylhexanoate, dibenzoyl peroxide, dicumyl peroxide, dicumyl hydroperoxide, azobisisobutyronitrile, benzylbarbituric acid derivative.
• the dental composite material comprises component (i) which forms the filler component, wherein the filler component comprises (i.1) 85 to 95% by weight of at least one dental glass, in particular from 90 to 94.5% by weight. %, preferably from 92 to 94.5 wt .-% and optionally (i.2) from 5 to 15 wt .-% of amorphous metal oxide, in particular 5 to 10 wt .-%, preferably 5.5 to 8 wt .-% , in the filler component, wherein (i.1) and (i.2) are 100% by weight of the filler component.
• the dental composite material comprises the components (ii) and (iii) which form the monomer component, the monomer component comprising (ii.1) 55 to 75% by weight of at least one bis (4 ', 7 '-dioxa-3', 8'-dioxo-2'-aza-decyl-9'-ene) tetrahydrodicyclopentadiene, bis- (4 ', 7'-dioxa-3', 8'-dioxo-2'-aza- 9'-methyl-decyl-9'-ene) tetrahydrodicyclopentadiene and / or mixtures thereof and optionally mixtures of the 3,8- / 3,9- / 4,8- / 3,10- / 4,10-isomers and / or the cis and trans isomers of the abovementioned compounds and (ii.2) from 21 to 38% by weight of at least one difunctional urethane (meth
• % in particular 0.2 to 9 wt .-% of at least one tetra to deca functional dendritic urethane methacrylate, in particular a dendritic six-fold urethane methacrylate, and (iii) 1 to 10 wt .-% of at least one di-, tri-, tetra- or multi-functional monomer, which is not a urethane (meth) acrylate, wherein the monomers (ii.1), (u-2), (ii.3) and (iii) are 100 wt .-% in the monomer component.
• the polymerization preferably takes place in a casting mold, which preferably has a geometric shape.
• the polymerization under elevated pressure minimizes or avoids the formation of air bubbles in the polymerized composite material.
• the shrinkage of the polymerizable composite material is preferably less than 2.0%, in particular less than 1, 5%, particularly preferably less than or equal to 1.4%.
• the polymerized composite material preferably has no voids or cracks of a size greater than or equal to 200 nm; in particular, a block of material has no voids or cracks.
• the polymerized composite material has a density greater than or equal to 2.0 g / cm 3 , in particular a density greater than or equal to 2.1 g / cm 3 .
• the polymerized dental composite material which is obtainable in particular by thermal polymerization of the composite material, has a synergistic combination of high flexural strength and a modulus of elasticity in the area of the tooth hard substance.
• the flexural modulus and modulus of elasticity can be measured by storing thermally polymerized specimens under dry conditions at room temperature (23 ⁇ 2 ° C) for 7 days, or specimens stored in 37 ° C deionized water for 7 days, followed by 5000 thermal cycles (5 ° C to 55 ° C, residence time 30 s) by means of a thermocycling device (HA-K178, Tokyo Giken Inc., Tokyo, Japan) and then measuring the flexural strength and modulus of elasticity.
• a thermocycling device HA-K178, Tokyo Giken Inc., Tokyo, Japan
• the polymerized dental composite material obtainable in particular by thermal polymerization of the composite material has a flexural strength of greater than or equal to 210 MPa, preferably greater than or equal to 220 MPa, and an modulus of greater than or equal to 16 to 20 GPa, preferably greater equal to 17 GPa to 20 GPa, more preferably from 18 to 20 GPa (7 days, 23 ⁇ 2 ° C, dry) according to EN ISO 6872: 2008 and a flexural strength greater than or equal to 160 MPa to 260 MPa (7 days stored in H 2 0 deionized at 37 ° C, followed by greater than or equal to 1000 cycles, in particular 5000 cycles (5 ° C to 55 ° C, residence time greater than or equal to 30 seconds, optionally up to 60 seconds) and a modulus of elasticity greater than or equal to 14 to 21 GPa (stored for 7 days in H 2 O deionized at 37 ° C., followed by greater than or equal to 1000 cycles, in particular 5000 cycles
• flexural strength of a dental composite is not limited to large values (> 100 MPa), balanced / optimal elasticity is advantageous for the application.
• the modulus of elasticity should ideally correspond to that of the dentine of the tooth hard substance, so that in the intended application a failure is avoided as far as possible.
• Brittle (high modulus) materials are prone to chipping or fracture.
• To elastic materials (low modulus of elasticity) deform under the chewing load and the cementation dissolves (debonding).
• the invention therefore also relates to a polymerized, dental composite material, in particular a thermally polymerized composite material, which has been polymerized preferably for 10 minutes to 10 hours at 80 to 150 ° C, preferably a polymerized at 90 to 150 ° C composite material, and a composite material obtainable by thermal polymerization, having a flexural strength greater than or equal to 200 MPa to 260 MPa (7 days, 23 ⁇ 2 ° C, dry) and a modulus of elasticity greater than or equal to 15 to 20 GPa (7 days, 23 ⁇ 2 ° C, dry) according to EN ISO 6872: 2008, in particular with a flexural strength of greater than or equal to 210 MPa, preferably greater than or equal to 220 MPa and an modulus of greater than or equal to 16 to 20 GPa, preferably greater than or equal to 17 GPa to 20 GPa, more preferably from 18 to 20 GPa.
• a polymerized, dental composite material in particular a thermally polymerized composite material
• the invention also relates to a polymerized composite material, in particular a thermally polymerized composite material having a flexural strength of greater than or equal to 160 MPa to 260 MPa (7 days stored in H 2 0 deionized at 37 ° C, followed by greater than or equal to 1000 cycles (5 ° C up to 55 ° C, residence time greater than or equal to 30 seconds) and one Young's modulus greater than or equal to 14 to 21 GPa (7 days stored in H 2 0 deionized at 37 ° C, followed by greater than or equal 1000 cycles, in particular 5000 cycles (5 ° C to 55 ° C, residence time greater than 30 seconds) according to EN ISO 6872 : 2008, in particular with a flexural strength greater than or equal to 170 MPa, preferably greater than or equal to 210 MPa and an modulus of greater than or equal to 15 to 21 GPa, preferably greater than or equal to 16 GPa to 20 GPa, more preferably from 18 to 20 GPa.
• the aforementioned publication also compares further measurement results of the three-point bending test for CAD / CAM blocks of different dental materials in Table 3.
• the dental materials measured there have flexural strengths after dry storage of 170 MPa and an E modulus of 9.6 or 14.5 GPa and a flexural strength of 1.17.6 MPa or 120.1 and an E modulus of 7.2 or 12.2 GPa Thermocycling on.
• Even dental materials with a flexural strength of 242 or 204 MPa and an elastic modulus of 10.0 or 14.7 GPa after dry storage have only flexural strengths of 194.3 or 165.1 MPa with an E-modulus of 8.7 GPa or 13, 2 GPa on. Therefore, it becomes clear that the setting of an elastic modulus analogous to that of hard tooth substance in the range of 15 to 20 GPa both in dry storage and storage at 37 ° C plus thermocycling was previously not possible.
• the invention relates to a polymerized, dental composite material comprising 70 to 85 wt .-% of at least one inorganic filler component comprising at least one dental glass having an average particle size d 50 in the range of 0.8 to 5.5 ⁇ , and preferably d 99 is less than or equal to 7.5 ⁇ and optionally at least one amorphous, silanized metal oxide, in particular precipitated silica and / or fumed silica of a primary particle size of 2 to 45 nm, 10 to 30 wt .-% of at least one polymer based on at least one monomer, preferably based on a mixture of the following monomers comprising at least one bis-urethane derivative of tetrahydrodicyclopentadiene, in particular a difunctional urethane (meth) acrylate of tetrahydrodicyclopentadiene and at least one di-
• the polymerized, dental composite material may preferably be in the form of a block of material, in particular as a three-dimensional block of material in the form of a geometric shaped body, in particular in the form of a milling blank with adapter for fixing in an automated material-removing device, particularly preferably in the form of a cylinder, a cuboid, preferably in FIG Shape of a cube. Furthermore, it is preferred if the edges and / or corners of the shaped bodies are rounded.
• the dimensions of the cylinder are preferably: height greater than or equal to 10 mm to less than or equal to 15 mm with a radius of greater than or equal to 3 to less than or equal to 7 mm, alternatively with a height greater than or equal to 10 mm to less than or equal to 20 mm and a radius greater than or equal to 5 to less than or equal to 7 mm.
• the dimensions of the cuboid are preferably greater than or equal to 4 mm, in particular greater than or equal to 10 mm and a smaller than or equal to 20 mm, in particular smaller than or equal to 18 mm, smaller than or equal to 14 mm and c smaller than or equal to 20, in particular smaller than or equal to a, b and c 18 mm.
• a three-dimensional block of material has at least one edge length of at least 10 mm, preferably 14 mm.
• Material blocks that are used as milling blocks preferably have the shape of cuboids, wherein the cuboid preferably has a volume of 12 mm x 14 mm x 17 or 18 mm, alternatively from 14 x 14 mm, or 15x15 mm and a height of 17 to 18 mm.
• One to all edges and corners can be straight or rounded.
• the invention further relates to the use of a dental composite material for the production of dental prosthetic restorations, in particular for the production of indirect dentures, in a material-removing method, in particular in a method in which the polymerized composite material by means of milling, cutting, polishing, breaking, chipping and / or boring, more preferably in a process in which the polymerized composite material is removed by laser energy.
• a particularly preferred use for the material is the use in a method of making dental prosthetic restorations in a material ablation process in which the material is ablated by laser energy.
• the particle size, and preferably the particle size distribution has been specially adapted to a process in which the polymerized composite material is removed by means of laser energy and the prosthetic restorations can be produced.
• a particular advantage of the dental material according to the invention is that it allows the possibility of a significant process simplification in the production of indirect dentures by the dentist or the dental technician performs at least one Intraoralscan in the mouth of the patient and then directly using the thus obtained digital dental information prosthetic dental restoration, such as a crown or an inlay, taking into account other device parameters, etc. can produce.
• the prepared dental prosthetic restoration can then be inserted into the patient, attached and, if necessary, slightly reworked. For example, an intra-oral scan is taken before grinding a tooth to make a tooth stump for a crown and another intra-oral scan of the tooth stump.
• the polymerized composite material can be used to make dental prosthetic restorations including crowns, inlays, onlays, superstructures, artificial teeth, denture teeth, dental bridges, dental bars, spacers, abutments or veneers.
• the polymerizable composite material can also be used as a composite material for making direct adhesive dental restorations.
• the urethane (meth) acrylates according to the invention are likewise preferably the following: (ii) at least one urethane (meth) acrylate, in particular a urethane dimethacrylate, preferably a bis (methacryloxy-2-ethoxycarbonylamino) alkylene, diurethane acrylate oligomer, Alkyl-functional urethane dimethacrylate Oligomers, aromatically-functionalized urethane dimethacrylate Oligomers, aliphatic unsaturated urethane acrylates, bis (methacryloxy-2-ethoxycarbonylamino) substituted polyether, aromatic urethane diacrylate oligomers, aliphatic urethane diacrylate oligomers, aliphatic urethane diacrylates, hexafunctional aliphatic urethane resins, aliphatic urethane triacrylate, aliphatic urethane acrylate oligomer, unsatur
• difunctional and polyfunctional urethane (meth) acrylates in particular urethane di (meth) acrylates, particularly preferably at least one (iii) urethane dimethacrylate selected from linear or branched alkyl-functionalized urethane dimethacrylates, urethane dimethacrylate functionalized polyethers, in particular bis (methacryloxy-2-) ethoxycarbonylamino) alkylene, bis (methacryloxy-2-ethoxycarbonylamino) substituted polyether, preferably 1,6-bis (methacryloxy-2-ethoxycarbonylamino) -2,4,4-trimethylhexane.
• Suitable urethane (meth) acrylates are available under the following trade names: Ebecryl 230 (aliphatic urethane diacrylate), Actilane 9290, Craynor 9200 (di-urethane acrylate oligomer), Ebecryl 210 (urethane diacrylate oligomeric oligomers), Ebecryl 270 (aliphatic urethane diacrylate oligomer), Actilane 165, Actilane 250, Genomer 1 122 (monofunctional urethane acrylate), Photomer 6210 (cas no.
• the urethane (meth) acrylates may preferably be selected from the abovementioned urethane (meth) acrylates or from a mixture of at least two different, preferably at least three, different urethane (meth) acrylates mentioned above.
• the at least one di-, tri-, tetra- or multi-functional monomer which is not a urethane (meth) acrylate is preferably selected from at least one of the following monomers, in particular a mixture of monomers comprising 1, 4-butanediol dimethacrylate ( 1, 4-BDMA) or pentaerythritol tetraacrylate, bis-GMA monomer (bisphenyl-A-glycidyl methacrylate), triethylene glycol dimethacrylate (TEGDMA) and diethylene glycol dimethacrylate (DEGMA), tetraethylene glycol di (meth) acrylate, decandioldi ( meth) acrylate, dodecanediol di (meth) acrylate, hexyldecanediol di (meth) acrylate, trimethylolpropane tri (meth) acrylate, pentaerythritol tetra (meth) acryl
• Typical difunctional monomers are tri- or tetraethylene glycol di (meth) acrylate, BDMA, 1,4-butanediol dimethacrylate (1,4-BDMA), bis-GMA monomer (bisphenyl-A-glycidyl Methacrylate, an addition product of methacrylic acid and bisphenol A diglycidyl ether), diethylene glycol di (meth) acrylate, bisphenol A di (meth) acrylate, decanediol di (meth) acrylate, dodecanediol di (meth) acrylate, hexyldecandioldi (meth) acrylate, as well as butanediol di (meth) acrylate, ethylene glycol di (meth) acrylate, polyethylene glycol di (meth) acrylates, ethoxylated / propoxylated bisphenol A di (meth)
• Tri- and tetra-functional monomers or multi-crosslinkers include trimethylolpropane tri (meth) acrylate, tris (2-hydroxyethyl) isocyanurate triacrylate, pentaerythritol tetraacrylate.
• At least one of the following monomers may be present in the composite material comprising at least one monomer, in particular a mixture of monomers of methyl methacrylate, ethyl methacrylate, propyl methacrylate, butyl methacrylate, n-hexyl methacrylate, 2- Phenoxyethyl methacrylate, isobornyl methacrylate, isodecyl methacrylate, polypropylene glycol mono-methacrylate, tetrahydrofuryl methacrylate, polypropylene glycol mono-methacrylate, methyl acrylate, ethyl acrylate, propyl acrylate, butyl acrylate, n-hexyl acrylate, 2-phenoxyethyl acrylate, isobornyl acrylate, isodecyl acrylate, Polypropylene glycol mono-acrylate, tetrahydr
• the invention further provides a composite material which preferably additionally contains at least one or more substances from the groups of fillers, pigments, stabilizers, regulators, antimicrobial additives, UV absorbers, thixotropic agents, catalysts and crosslinkers.
• Such additives are - as well as pigments, stabilizers and regulators - used in rather small amounts, eg. B. in total from 0.01 to 3.0, especially 0.01 to 1, 0 wt.% Based on the total mass of the material.
• Suitable stabilizers are, for. As hydroquinone monomethyl ether or 2,6-di-tert-butyl-4-methylphenol (BHT).
• the following initiators and / or initiator systems for auto or cold polymerization comprise a) at least one initiator, in particular at least one peroxide and / or azo compound, in particular LPO: dilauroyl peroxide, BPO: dibenzoyl peroxide, t-BPEH: tert-butyl per-2-ethylhexanoate, AIBN : 2,2'-azobis (isobutyronitrile), DTBP: di-tert-butyl peroxide, and optionally b) at least one activator, in particular at least one aromatic amine, such as N, N-dimethyl-p-toluidine, N, N- Dihydroxyethyl-p-toluidine and / or p-dibenzylaminobenzoic acid diethyl ester or c) at least one initiator system selected from redox systems, in particular a combination selected from dibenzoyl peroxide, dilauroyl peroxide
• the initiator system may be a redox system comprising a peroxide and a reducing agent selected from ascorbic acid, ascorbic acid derivative, barbituric acid or a barbituric acid derivative, sulfinic acid, sulfinic acid derivative, particularly preferred is a redox system comprising (i) barbituric acid or thiobarbituric acid or a barbituric acid or thiobarbituric acid derivative and (ii) at least one copper salt or copper complex and (iii) at least one compound having an ionic halogen atom, particularly preferred is a redox system comprising 1-benzyl-5-phenylbarbituric acid, copper acetylacetonate and benzyldibutylammonium chloride.
• the polymerization in the 2-component prosthesis base material is particularly preferably started via a barbituric acid derivative.
• Suitable initiators for the polymerization reaction of cold-curing or autopolymerizing starting mixtures are, in principle, those with which free-radical polymerization reactions can be started.
• Preferred initiators are peroxides and azo compounds, such as the following: LPO: dilauroyl peroxide, BPO: dibenzoyl peroxide, t-BPEH: tert-butyl per-2-ethylhexanoate, AIBN: 2,2'-azobis (isobutyronitrile), DTBP: di tert-butyl peroxide.
• suitable activators for.
• aromatic amines are added.
• suitable amines are N, N-dimethyl-p-toluidine, N, N-dihydroxyethyl-p-toluidine and diethyl p-dibenzylaminobenzoate.
• the amines regularly act as co-initiators and are usually present in an amount of up to 0.5 wt .-%.
• the flexural properties were determined using a three-point bending test according to ISO 6872: 2008 (ISO 6872: 2008 Dentistry - Ceramic Materials, 3rd ed, International Organization for Standardization, Geneva, 2008).
• the rod-shaped specimens, 4.0 mm wide, 14.0 mm long and 1.2 mm thick, were made with a low-speed diamond saw (Isomet, Buehler, Lake Bluff, IL, USA).
• Samples from the first group were stored for 7 days under dry conditions at room temperature (23 ⁇ 2 ° C).
• the width and thickness of each sample were measured by a digital micrometer (MDC-25M, Mitsutoyo Co., Tokyo, Japan, minimum value: 0.001 mm).
• E FL 3 / 4bh 3 d
• F the load at a suitable location in the rectilinear part of the spring characteristic
• L is the span (12,0 mm)
• b is the width of the sample
• h is the thickness of the sample
• d is the bend at the Last F is.
• the hardness test was carried out with the Zwick universal device:
• the measured values of samples according to the invention are in the range from 800 to 850.
• Example 1 The following are comparative examples of the light-curing products Venus Diamond (VD) and Venus Pearl (VP) according to ISO 4049 and ISO 6872 (The exposure was carried out selectively according to the method described in EN ISO 4049: 2009 7.1 1 with a Translux 2Wave (1200 mW / cm 2 ) by an exposure time of 20 seconds per exposure point.) And have been compared with Example 1 according to the invention.
• the polymerization of the dental composite according to the invention is usually carried out for about 3 hours at 95 ° C.
• Table 4 Bending strengths (according to EN ISO 6872)

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