JP5253251B2 - Dental implant protection - Google Patents

Description

  The present invention relates to a protective material for a dental implant for the purpose of protecting an implant that has been implanted immediately after the implantation of the implant in a dental implant treatment.

  Conventionally, in dental treatment, a technique using a dental implant is frequently used as a kind of denture mounting method. Here, the structure of the dental implant is shown in the schematic diagram of FIG. That is, the dental implant generally includes a fixture 1 fixed to the alveolar bone 5 of the jaw bone as a tooth root, and an abutment 2 screwed on the fixture, and a denture structure not shown in the abutment 2. Is fixed. As a therapy, the fixture 1 is fixed to the jawbone, the fixture 1 is firmly fixed, the abutment 2 is attached, and the denture structure is attached to the abutment. Therefore, many fixtures and various fixtures, abutments, and the like have been developed from the advantages that there is no “slip”, “displacement”, etc. in dentures and the like and that care is easy.

  In dental implants, if the fixture is not fixed and the abutment fixed to the fixture is not securely fixed, it will cause inflammation of the jawbone and gums, which will cause problems in the alignment and meshing of the denture structure. May occur. In addition, depending on the state of the jawbone etc. that fixes the fixture (brittle, too thin, etc.), it may be difficult to fix the fixture and it may jeopardize the fixture fixing in the abutment installation ( Depending on the health condition of the patient, especially the condition of the jawbone, etc., the work of removing and attaching the abutment may occur several times, which may jeopardize the fixation of the fixture), teeth alignment, meshing, etc. There are many cases where adjustment work becomes very difficult.

  Furthermore, when the fixture is fixed to the jaw bone or the like, it must be embedded avoiding the nerve, and there are cases where the fixture cannot be embedded in the jaw bone or the like in a substantially vertical direction. Since the protruding direction of the teeth must be inward according to the meshing, an angled abutment has been developed.

  To date, fixtures and abutments having various forms have been developed, and various surgical procedures are also required in order to implant them such as gums and jawbones. There are several means for surgical treatment for the purpose of implantation, and examples are as follows (see, for example, Patent Document 1 and Non-Patent Document 1).

  After incising the gum using a drill, carving a hole in the jawbone and embedding the fixture, it is sutured once (primary treatment). The suture is removed for about one week while observing the follow-up, and then the fixture and the jawbone are joined by leaving an interval of 3 to 6 months. Thereafter, the gums are opened with a scalpel, abutments and the like are attached, and left for several more weeks until the gums heal (secondary treatment).

  In addition to this method, there is a method in which the fixture and the abutment are integrated, and the method can be completed by only one treatment.

  As described above, the positions and angles of the fixtures and abutments are extremely important in forming an appropriate denture structure when implant processing is performed, and if these are shifted, the final denture structure is finally obtained. The occlusal position and accuracy will also greatly go wrong. Therefore, confirmation of the position and angle at the time of implantation and the subsequent protection of the stable period are extremely important.

Japanese Patent Laid-Open No. 9-238956

Takeda Takayuki, Hayashi Yasuharu, Shiikai Tatsuo, "Reliable and safe implant treatment", Ishiyaku Shuppan Co., Ltd., May 2008

  Depending on the treatment of the dental implant, the patient often wears a temporary denture for the purpose of protecting the surgical site and assisting eating after the secondary treatment until the gums and mucous membranes are healed. At this time, if the temporary denture and the fixture or abutment continue to collide with each other due to occlusion, there is a risk that the position and angle of the dental prosthesis will be distorted. Moreover, when a fixture or abutment shifts due to such a load, the surrounding mucous membrane may be compressed to cause inflammation. Therefore, until the position of the fixture is settled, a recess is provided on the back of the portion of the temporary denture to reduce the collision between the temporary denture and the fixture or the abutment, or some kind of protection. It will be necessary to take measures.

  However, providing a recess on the back surface of the temporary denture is troublesome in operation, and the stability of the provision of the temporary denture is also impaired, and there are many problems. In addition, there is currently no dedicated material that plays a role in protecting fixtures or abutments. Therefore, it is necessary to provide an optimal material for maintaining the position and angle of the fixture and the abutment after the primary treatment and the secondary treatment of the dental implant and protecting the peripheral mucosa.

  Therefore, the object of the present invention is to receive the position of the fixture and abutment during the implant treatment period and to prevent inflammation of the surrounding mucosa by occlusion even in the presence of the implant material in the submucosa. An object of the present invention is to provide a protective material for a dental implant that can relieve the force and keep its properties.

  As a result of intensive studies to solve the above-mentioned problems, the present inventors use a temporary denture with a material having a specific softness interposed above the embedded fixture or abutment. It has been found that the angle is maintained and that it also contributes to the prevention of inflammation of the surrounding mucous membranes, and the present invention has been completed.

  That is, the present invention is a protective material for dental implants characterized in that a soft material having a Shore A hardness in the range of 5 to 50 is used.

  By applying the protective material for dental implants of the present invention to the back surface of the temporary denture, it is possible to protect the planting position and angle of the fixture planted on the alveolar bone by surgery from the force received by occlusion, etc. Can be maintained. Therefore, the problem that the planting position and angle of a fixture shift | deviate and the occlusal position and precision of the denture structure finally obtained will go wrong is solved favorably.

  Further, in the case where the fixture or the abutment is displaced as described above, it is possible to greatly suppress the peripheral mucous membrane from being pressed and causing inflammation.

FIG. 1 is a schematic view showing a state in which the dental implant protection material of the present invention is applied to the back surface of a temporary denture and used for protecting the implant. FIG. 2 is a schematic view showing another embodiment in which the dental implant protective material of the present invention is applied to the back surface of a temporary denture and used for protecting the implant. FIG. 3 is a schematic view showing the structure of a dental implant. FIG. 4 is a schematic view showing a method of a repeated impact durability test in the examples.

  The protective material for dental implants of the present invention is made of a soft material having a Shore A hardness of 5 to 50. The Shore A hardness referred to here is an index of hardness in a rubber body defined in JIS standards, and specifically measured based on a durometer hardness test method shown in JIS K7215. It is.

  By applying the protective material for dental implants of the present invention to the inner surface of a temporary denture used on the mucous membrane after performing an operation for implanting an implant (fixture or abutment), the occlusal fixture can be applied. The load applied can be greatly reduced, and the planting position and angle of the precisely applied fixture can be protected, and the mucous membrane in contact with the fixture can be protected together.

  The soft material used for the dental implant protective material of the present invention can be used without limitation as long as it has a Shore A hardness in the range of 5-50. If the Shore A hardness is less than 5, the fluidity of the paste is too high. Therefore, if a load is applied to the temporary denture, the paste will be washed away from the inner surface and a protective effect will not be obtained, and if the Shore A hardness exceeds 50, It is too hard to obtain a protective effect. The Shore A hardness, which is superior in protective effect, varies depending on the shape and angle of the planted fixture, but is generally preferably in the range of 10-30.

  The soft material used for the dental implant protective material of the present invention is intended to protect the fixture, but at the same time, this material also comes into contact with the mucous membrane around the fixture. The postoperative mucosa usually changes gradually with the healing of the surgical wound, but if the change is large, when using the protective material of the present invention, the mucosa and the protective material There is a possibility that the gap is generated and the temporary denture moves, and as a result, the protective effect is reduced. Therefore, it is preferable that the present protective material has a property of being deformed to some extent as the shape of the mucous membrane changes.

  In the present invention, viscoelasticity is given as an index indicating the shape retention / deformability of the dental implant protective material, and a sine tangent calculated when measuring the viscoelasticity is a standard. The sine tangent is an index representing the viscoelasticity of a substance, and can be measured by a stress-controlled viscosity measuring apparatus (CS rheometer) used in the above-described viscosity measurement. The sine tangent is expressed as the ratio of elasticity to the viscosity of the material. The greater the number, the greater the viscosity, i.e., the impact absorption and fluidity, and vice versa. Means that it will grow.

  For use as a protective material for a dental implant, a material having moderate shock absorption and shape stability is more suitable, and is preferably in the range of 0.01 to 0.80 in terms of sine tangent, and 0.20. More preferably, it is -0.50.

  As a soft material that can be used as a protective material for dental implants of the present invention, any organic material or inorganic material can be applied without limitation as long as it satisfies the Shore A hardness requirement and is solid at 37 ° C. It is. In general, an organic material is preferably used because it is easy to obtain one that satisfies the above conditions. Examples of such an organic material include a soft material obtained by combining a solid polymer at 37 ° C. having a mass average molecular weight of 20,000 or more with a plasticizer as necessary.

  In this soft material, the polymer component is a solid component at 37 ° C. from the viewpoint of operability, and the mass average molecular weight of the polymer for ensuring the property is generally 20,000 or more. is there. Further, the mass average molecular weight is more preferably 50,000 or more. Further, the mass average molecular weight of the polymer is preferably 5 million or less, and more preferably 1 million or less from the viewpoint of a soft material. Typical examples of such polymers include (meth) acrylic polymer systems, silicone polymer systems, olefin polymer systems, styrene polymer systems, butadiene polymer systems, isoprene polymer systems, and phosphazene polymer systems. It is done. There is no problem even if these polymers are composed of a plurality of components, and even if these components are mixed and used, they can be effectively used as long as the soft polymer composition having the above requirements can be obtained. In addition, a polymerization reaction or the like may be caused during mixing to exhibit the above-mentioned hardness property.

  Among the polymers shown above, (meth) acrylic non-crosslinked polymers are useful as materials because they are not only easily available but also very inexpensive. The (meth) acrylic non-crosslinked polymer can be used without limitation as long as it is used for dental materials. In general, in terms of chemical stability and transparency, methyl acrylate, methyl methacrylate (abbreviated as MMA), ethyl acrylate, ethyl methacrylate (abbreviated as EMA), propyl acrylate, propyl methacrylate, butyl acrylate, butyl methacrylate, hexyl Acrylate, hexyl methacrylate, 2-ethylhexyl acrylate, 2-ethylhexyl methacrylate, octyl acrylate, octyl methacrylate, decyl acrylate, decyl methacrylate, lauryl acrylate, lauryl methacrylate, benzyl acrylate, benzyl methacrylate, 4-butoxycarbonylphenyl acrylate, 4-butoxycarbonyl Phenyl methacrylate, hexadecyl acrylate, hexade Homopolymers such as dimethacrylate, neopentyl acrylate, neopentyl methacrylate, phenyl acrylate, phenyl methacrylate, N-butyl acrylamide, etc., or copolymers thereof are preferably used, but methyl methacrylate, Ethyl methacrylate, propyl methacrylate, butyl methacrylate, benzyl acrylate, benzyl methacrylate, 4-butoxycarbonylphenyl acrylate, 4-butoxycarbonylphenyl methacrylate, hexadecyl acrylate, hexadecyl methacrylate, neopentyl acrylate, neopentyl methacrylate, phenyl acrylate, N A homopolymer such as butyl acrylamide is preferably used.

  On the other hand, the plasticizer has an action of dissolving these solid polymers and imparting flexibility and plasticity. The plasticizer is used in combination with the polymer, particularly when the (meth) acrylic non-crosslinked polymer is used as the solid polymer. The amount of the plasticizer blended is not limited as long as the obtained soft material is an amount in which the Shore A hardness is in the range of 5 to 50, but in general, the mass average molecular weight is 20,000 or more at 37 ° C. In the range of 50 to 300 parts by mass, more preferably 80 to 250 parts by mass with respect to 100 parts by mass of the solid polymer.

  Any known plasticizer can be used without particular limitation as long as it has the properties. Specifically, phthalate plasticizers such as diethyl phthalate, dibutyl phthalate, dioctyl phthalate, bis (ethylhexyl) phthalate, and butyl phthalyl butyl glycolate, or diethyl sebacate, dibutyl sebacate, dioctyl sebacate, bis ( Examples thereof include sebacate plasticizers such as ethylhexyl) sebacate.

  These plasticizers all have a low molecular weight, and the soft polymer composition formed by blending with the solid polymer loses viscoelasticity in a relatively short period of time due to the outflow of the plasticizer, and may become hard. . In order to solve this problem, it is preferable to use a specific liquid polymer instead of the low molecular weight plasticizer. As such a liquid polymer, for example, 37 ° C. described in JP-A-2006-225281 having a mass average molecular weight in the range of 1000 to 10,000 and a ratio of oligomer having a molecular weight of 500 or less is 10% by mass or less. A liquid polymer or the like can be preferably used.

  That is, in the present invention, a soft material that can be particularly preferably used is a polymer that is liquid at 37 ° C., having a mass average molecular weight in the range of 1000 to 10,000, and a proportion of oligomers having a molecular weight of 500 or less, and 10 mass% or less, A soft polymer composition mainly composed of a solid polymer at 37 ° C. having a mass average molecular weight of 20,000 or more dissolved in the liquid polymer. By using a soft polymer composition using a liquid polymer as such a plasticizer, the protective material for dental implants of the present invention can maintain its excellent viscoelasticity for a long time even when used in the oral cavity. It is preferable. Furthermore, when the low molecular weight plasticizer is used, coloring components and dirt may easily adhere to the fixture through the plasticizer due to the outflow. This is preferable because it is suppressed.

  The material of the liquid polymer is not particularly limited, but it is preferably a (meth) acrylic liquid polymer in terms of easy availability and excellent kneading properties and various physical properties of the resulting paste. However, (meth) acrylic acid esters are more preferred in that a liquid polymer can be easily obtained within the above molecular weight range.

  The method for producing such a liquid polymer is not particularly limited, and those produced by known methods can be used without particular limitation. Typically, (meth) acrylic monomers, or ( What is necessary is just to superpose | polymerize a meth) acrylic-type monomer and the other monomer copolymerizable with this (meth) acrylic-type monomer so that it may become the range of mass average molecular weight 1000-10000.

  Monomers used for obtaining the above liquid polymer include methyl (meth) acrylate, ethyl (meth) acrylate, propyl (meth) acrylate, isopropyl (meth) acrylate, butyl (meth) acrylate, isobutyl (meth) acrylate, and hexyl. (Meth) acrylate, 2-ethylhexyl (meth) acrylate, cyclohexyl (meth) acrylate, glycidyl (meth) acrylate, methoxyethyl (meth) acrylate, ethoxymethyl (meth) acrylate, methoxypropyl (meth) acrylate, and the like. Examples of other monomers copolymerizable with the (meth) acrylate monomer include vinyl acetate and styrene. In this case, it is possible to use a copolymer obtained by polymerizing one or more (meth) acrylate monomers and one or more other copolymerizable monomers. From the aspect, it is preferable to contain 50 mol% or more, preferably 80 mol% or more of a monomer unit based on the (meth) acrylate monomer.

  Among them, liquid polymers include ethyl (meth) acrylate, propyl (meth) acrylate, isopropyl (meth) acrylate, butyl (meth) acrylate, 2-ethylhexyl (meth) acrylate, methoxyethyl (meth) acrylate, ethoxymethyl (meth) A homopolymer obtained by polymerizing one kind selected from acrylate and glycidyl (meth) acrylate, or a copolymer obtained by polymerizing two or more kinds of these monomers is particularly preferably used.

  More specific examples of such (meth) acrylate polymers include polyethyl (meth) acrylate, polypropyl (meth) acrylate, polyisopropyl (meth) acrylate, polybutyl (meth) acrylate, poly {2-ethylhexyl (meth) ) Acrylate}, poly {ethyl (meth) acrylate-butyl (meth) acrylate}, poly {ethyl (meth) acrylate-2-ethylhexyl (meth) acrylate}, poly {ethyl (meth) acrylate-methoxyethyl (meth) acrylate }, Poly {ethyl (meth) acrylate-glycidyl (meth) acrylate}, poly {butyl (meth) acrylate-methoxyethyl (meth) acrylate}, poly {butyl (meth) acrylate-glycidyl (meth) acrylate Etc. The.

  A method for obtaining a liquid polymer having a mass average molecular weight in the range of 1,000 to 10,000 as in the above examples can be obtained by a method using a general polymerization reaction. That is, a liquid polymer having a desired average molecular weight can be obtained by controlling the mixing ratio of the monomer and the polymerization initiator. Ionic polymerization or living radical polymerization, which can easily control the average molecular weight, is preferably used. Particularly in anionic polymerization, a molecular weight distribution is very sharp, and a polymer (polymer) close to monodispersion of 2 or less can be obtained in almost all cases of a mass average molecular weight / number average molecular weight, and a polymer having a molecular weight of 500 or less is not included. It is easy to satisfy the condition.

  Of course, as a liquid polymer to be blended in the protective material for dental implants of the present invention, a polymer having a broad molecular weight distribution may be used as long as the above-mentioned molecular weight conditions are satisfied, or two or more polymers having different molecular weight distributions may be used. May be used in combination. Furthermore, you may use together 2 or more types of liquid polymers from which the kind and ratio of the monomer unit which comprise a polymer differ.

  There is no restriction | limiting in particular in the packaging form of the protective material for dental implants of this invention, Either a single packaging and a separate packaging may be sufficient. In the case of single packaging, for example, it is kneaded in advance using a kneading device such as a mixer and filled in an appropriate packaging container. Examples of the packaging container include an ointment basket, a box-type container, a syringe, and a tube. In either case, the surgeon removes the necessary amount from the container immediately before use and puts it on the denture for use. As a kneading apparatus, a planetary mixer used for food production or the like is suitable.

  In the case of separate packaging, the use form varies depending on the sealed container to be used, and examples thereof include means for separate packaging into a powder component and a liquid component. That is, a powder material and a liquid material are mixed and kneaded immediately before use to form a uniform paste-like soft material. Any packaging form can be used without any problem, but a powder type that changes fluidity and properties to some extent according to the operator's intention is preferably used.

  Specific examples of the dental implant protective material in the case of the powder liquid type described above include, for example, (1) the powder material is a solid polymer at 37 ° C. having a mass average molecular weight of 20,000 or more dissolved in the liquid polymer. (2) The liquid material is a plasticizer, in particular, a liquid polymer having a mass average molecular weight in the range of 1000 to 10,000 and an oligomer having a molecular weight of 500 or less in a proportion of 10% by weight or less. The plasticizer which consists of consists of. In such a powder liquid type, (1) As the solid polymer to be contained in the powder material, those having a glass transition temperature in the range of 10 to 80 ° C. are usually used. The polymer having a Tg of less than 0 ° C. has extremely strong solid polymer particles while the powder material is stored at room temperature (environmental temperature at which the protective material for dental implants before use is stored; about 18 to 35 ° C.). There is a tendency to agglomerate. As a result, it becomes difficult to obtain a paste by kneading with the liquid material.

  When Tg exceeds 80 ° C., the paste obtained by kneading the powder material and the liquid material becomes hard, and the flexibility that can be used as a protective material for implants is insufficient. The Tg of the solid polymer is preferably in the range of 10 to 70 ° C. in view of making the flexibility more suitable as a protective material for implants and preventing aggregation during storage.

  As such a solid polymer having a Tg in the range of 10 to 80 ° C., for example, in the case of a (meth) acrylic non-crosslinked polymer, propyl methacrylate, butyl methacrylate, benzyl acrylate, 4-butoxycarbonylphenyl acrylate, hexadecyl Homopolymers such as acrylate, neopentyl acrylate, neopentyl methacrylate, phenyl acrylate, N-butyl acrylamide, etc. are exemplified. Among them, homopolymers of propyl methacrylate, butyl methacrylate, neopentyl methacrylate and the like are easily available. Most preferably used. Etc.

  In such a powder liquid type dental implant protective material, for the purpose of controlling kneadability, a solvent may be used in (2) the liquid material as necessary. As such a solvent, various solvents can be used without particular limitation as long as they meet the above purpose. Alcohols are suitable from the viewpoint of irritation in the oral cavity, and examples thereof include ethanol and isopropyl alcohol. However, ethanol that is easily available and less irritating is preferable.

  The amount of the solvent is not particularly limited as long as the effects of the present invention can be obtained, but from the viewpoint of handling of the composition, odor, and the possibility that the physical property change after elution from the paste becomes large, the liquid material It is preferable that it is the range of 1-30 mass parts with respect to 100 mass parts of plasticizers mix | blended with. A favorable operational feeling can be acquired by setting it as the range of 3-20 mass parts especially.

  Furthermore, by replacing a part of the liquid polymer with the low molecular weight plasticizer described above, the mixing time can be shortened when mixing the liquid material and the powder material, and a better operational feeling can be obtained. Therefore, a low molecular weight plasticizer may be added to the liquid material. In this case, as described above, when the low molecular weight plasticizer is used alone, it flows out of the soft polymer composition and fluctuates the viscoelasticity. However, when used in combination with a liquid polymer within the above-mentioned range, the blending amount can be suppressed, and the above phenomenon is alleviated so as not to cause a problem.

  Thus, in the powder-liquid type dental implant protective material, when the liquid polymer and the low molecular weight plasticizer are used in combination as the plasticizer, the blending amount of the low molecular weight plasticizer is within a range where the effects of the present invention can be obtained. If there is too much blending amount, there is a possibility that problems such as a decrease in viscoelasticity and hardness due to outflow may occur, so the mixing ratio of liquid polymer / low molecular weight plasticizer is 55 or more / 45 or less. The range of 55/45 to 90/10 is more preferable, and the range of 75/25 to 85/15 is particularly preferable.

  If necessary, an inorganic powder may be added to the dental implant protective material of the present invention. By adding inorganic powder, the viscoelasticity of the final composition can be adjusted. That is, final hardness becomes high by mix | blending inorganic powder with the protective material for dental implants of this invention. Therefore, when the hardness of the obtained soft material becomes too soft, it is desirable to add inorganic powder to the desired hardness suitable as a protective material for dental implants.

  The kind of such inorganic powder is not particularly limited, and can be selected from reinforcing materials and fillers added to general resin compositions. Specifically, calcium carbonate, calcium sulfate, magnesium oxide, barium carbonate, barium sulfate, titanium oxide, potassium titanate, barium titanate, aluminum hydroxide, magnesium hydroxide, meteorite powder, glass powder, diatomaceous earth, silica, Examples include calcium silicate, talc, alumina, bentonite, zeolite, kaolin clay, mica, and quartz glass. Silica and alumina are preferably used from the viewpoints of ease of handling, compatibility with liquid materials, solubility in saliva (elution), and the like.

  The particle size of the inorganic powder is not particularly limited, but preferably has a volume average particle size of 1 μm or less, more preferably 0.1 μm or less from the viewpoint of storage stability, kneadability and the like. Considering the availability of such inorganic particles, fumed silica is most preferable. Of course, you may use together 2 or more types of inorganic powder from which a material, an average particle diameter, etc. differ.

  Furthermore, in addition to the above components, the dental implant protective material of the present invention may contain coloring materials such as dyes and pigments, fragrances, antibacterial agents, antifungal agents and the like, if necessary.

The use method of the protective material for dental implants of the present invention varies depending on the packaging form. Basically, in the temporary denture used after implant (fixture) implantation surgery, as shown in FIG. Apply to the part corresponding to the back of the gingival part to be embedded. With the implant protective material 6 applied in this manner, the temporary denture 3 is attached to the oral cavity, and the implant protective material 6 relaxes the force received by occlusion and the like. In addition, the occurrence of a shift in angle is suppressed. In order to sufficiently exert the protective effect on the fixture 1, the application of the implant protective material 6 is usually performed on an area of 1.5 cm ³ or more, which is at least five times the upper end diameter of the fixture 1. It is preferred to do so. In addition, it is preferable from the viewpoint of the stability of the temporary denture to form the recess 7 by hollowing out the portion corresponding to the application site of the implant protective material 6 on the back surface of the temporary denture 3. In these coatings, the coating thickness of the implant protective material 6 to be formed is not particularly limited, but is generally 100 to 5000 μm.

  In FIG. 2, the fixture 1 is fixed to the alveolar bone of the jawbone and then sutured so that the upper part is covered with gums. Also good. Further, as shown in FIG. 3, the present invention may be applied to a state in which an abutment 2 is screwed to the upper end of the fixture 1.

  The temporary denture used for application of the implant protective material may be either a complete denture or a partial denture. In the case of a complete denture or a large partial denture close to it, on the back surface of the temporary denture 3 other than the portion to which the implant protective material 6 is applied, a denture base fixing paste, a soft lining material, a dental mucosa Other denture base-related materials such as a conditioner may be applied and used. The material of the temporary denture is generally a (meth) acrylic polymer such as poly (methyl methacrylate).

  Taking the case where the dental implant protective material of the present invention is in the form of powder liquid packaging as an example, the use method will be described in detail. A predetermined amount of powder material and liquid material are weighed, mixed and kneaded at the time of use. Use. The mixing ratio of the powder material and the liquid material is appropriately set and depends on the other compounding components as described above. Preferably, it is blended in the liquid material with respect to 100 parts by mass of the solid polymer blended in the powder material. The amount of the plasticizer such as the liquid polymer is preferably in the range of 50 to 300 parts by mass, and more preferably in the range of 80 to 250 parts by mass, as described above.

  Further, if there is a large difference in the ratio between the powder material and the liquid material, the paste may not be formed even if both are mixed. From this viewpoint, the powder material and the liquid material are in a mass ratio of powder / liquid = 0. It is preferable that each compounding component is adjusted so that it may be mixed in the range of 5 to 2.5, and in terms of easy weighing and mixing at the time of use, powder / liquid = 0.8 to It is more preferable to adjust so that it may be mixed at about 2.0.

  In addition, the protective material for implants of this invention does not necessarily have high adhesiveness with respect to the temporary denture which consists of a (meth) acrylic-type polymer. Therefore, it is preferable to apply an appropriate adhesive to the back surface of the temporary denture in advance when applying the applied portion on the back surface. Thereby, it is possible to firmly bond the protective material for implant and the denture base. Such an adhesive is not particularly limited, but is preferably a monomer unit based on methyl (meth) acrylate and a monomer unit based on (meth) acrylate of an alcohol having 3 or more carbon atoms. The composition which consists of an organic-solvent solution containing 0.5-30 mass% of the polymer which has both is mentioned. Such an adhesive has already been proposed by the present inventors as an adhesive that strengthens the adhesive strength of the mucosa-adjusting agent on the denture base (see Japanese Patent Application No. 2006-225281). The implant protective material of the present invention can also be used effectively to increase the adhesive force with the temporary denture.

  EXAMPLES The present invention will be specifically described below with reference to examples, but the present invention is not limited to these examples. The evaluation methods of various physical properties in each example and comparative example are as follows.

(1) Method of measuring hardness Shore A hardness, which is an index of flexibility, was measured based on JIS-K7215 (durometer type A). The measurement was performed when the mixture was allowed to stand at 37 ° C. overnight after kneading and when it was immersed in water at 37 ° C. for one month.

(2) Measuring method of sine tangent (tan δ) After measuring oscillation using a viscoelasticity measuring device CS rheometer “CVO120HR” (manufactured by Borin) and measuring storage elastic modulus and loss elastic modulus for each hour Tan δ, which is an index of viscoelasticity, was calculated from the following formula.

tan δ = loss elastic modulus / storage elastic modulus As a measurement condition in the CS rheometer, a diameter of 20 mm, a parallel plate was used, and measurement was performed at a measurement temperature (plate temperature) of 37 ° C. and a shore stress of 500 Pa. The measurement was performed on the same sample from the start of the test. After setting the sample, the sample was left as it was, and the measurement was performed 24 hours later. In the measurement, the periphery of the plate was covered with a resin plate, and the sample and the plate were immersed in water (37 ° C.).

(3) Repeated Impact Durability Test The following test was conducted to evaluate the durability of the embedded fixture against impact.

  A specimen as shown in FIG. 4 was prepared. That is, after a SUS cylindrical test body 9 (corresponding to a fixture) of 6 mmΦ × height 20 mm is embedded in the acrylic resin 10 (pseudoalveolar bone) at a lower 15 mm portion and sufficiently cured, A portion 3 mm in height from the acrylic resin surface was further embedded with a commercially available silicone impression material 11 (pseudo gum). At this time, specimens with angles of 60 ° and 45 ° other than the planting angle of 90 ° were prepared.

  Separately from the above-mentioned test body, a denture base resin cured body 12 (made by “Acron” GC Corporation) of 60 mmΦ × 2 mm thickness is prepared, and a dental implant protective material 6 is pasted thereon, and the pasting surface and the SUS column The test piece was placed horizontally so that it touched the head of the test body, and was subjected to a load test 10,000 times from above using a repeated load tester “Servo Pulser” 13 (manufactured by Shimadzu Corporation). The test with “Servo Pulser” was performed under the conditions of a load of 10 kg and a frequency of 1.2 Hz.

  After completion of the load load test, the denture base resin cured body and the dental implant protective material affixed thereto were removed, and the planting angle of the SUS cylindrical specimen was measured and compared with the angle before the start of the test. Furthermore, the silicone impression material formed by observing the deformation (fracture) of the silicone impression material (pseudogum) in contact with the SUS cylindrical test body planted at 45 ° with a digital microscope (magnification 10 times) And the above-mentioned cylindrical specimen were measured for conformity and determined as follows.

  ○: No gaps were observed between the silicone impression material (pseudo gum) and the cylindrical specimen, and the silicone impression material was kept in close contact.

  Δ: Slight voids were observed between the silicone impression material (pseudo gum) and the cylindrical specimen, but no cracks or breakage were observed in the silicone impression material.

X: Remarkable voids were observed between the silicone impression material (pseudo gingiva) and the cylindrical specimen, and cracks and breakage were observed in the silicone impression material.
(4) Impact absorbability test A dental implant protective material was affixed to a 60 mmΦ × 2 mm thick denture base resin cured body with a thickness of 2 mm, and was allowed to stand in water at 37 ° C. for 24 hours.

A dental implant protective material was placed on top of a horizontal base, and a 10 g nylon sphere was dropped from the surface through a transparent pipe made of acrylic resin. Height was measured and shock absorption was evaluated.
(5) Colorability test The dental implant protective material was toned with a pigment or the like in advance, and the test (3) was performed in that state. However, the repeated load test by “Servo Pulser” was performed 100,000 times. After the end of the load test, the color transfer of pigment or the like to the SUS test piece was visually observed and evaluated.
(6) Mixing time measurement method 1.74 g of powder material and 1.14 g of liquid material were weighed and mixed in a rubber cup using a plastic spatula. Time was measured.

Moreover, each material used by each Example and the comparative example is as follows.
A) Soft material (Meth) acrylic polymer soft material The raw materials used to prepare the (meth) acrylic polymer soft material are as follows.
・ Polyethyl methacrylate “Techpolymer EMA35” (manufactured by Sekisui Plastics)
・ Polybutyl methacrylate "Hyperl M6003" (Negami Kogyo Co., Ltd.)
・ Plasticizer Low molecular plasticizer Dibutyl phthalate (abbreviated as DBP; manufactured by Tokyo Chemical Industry Co., Ltd.)
Dibutyl sebacate (abbreviated as DBS, manufactured by Tokyo Chemical Industry Co., Ltd.)
Liquid polymer Polypropyl acrylate (PPA); synthesized in Production Example 1 Polyethyl acrylate (PEA); synthesized in Production Example 2 Polybutyl acrylate (PBA-1); synthesized in Production Example 3 Polybutyl acrylate (PBA-2) ); Synthesized in Production Example 4 Fumed silica “Leosil MT-10” (manufactured by Tokuyama Corporation)
・ Red colorant Red No. 1 <Method of synthesizing liquid polymer>
Production Example 1
Production Example of PPA: 3.0 ml (3.0 mmol) of a toluene solution (1.0 mol / l) of tri (n-butyl) aluminum was mixed with 40 ml of toluene and cooled to -78 ° C. To this was added 7.4 ml (7.4 mmol) of a toluene solution of t-butyllithium (1.0 mol / l), and after stirring for several minutes, 14.8 g (130 mmol) of propyl acrylate was added at a temperature in the reaction system. It was added with care not to go up. This reaction was performed in a standard Schlenk tube under a nitrogen atmosphere, and the reagent was transferred using a syringe. Toluene was refluxed over sodium and then distilled under a nitrogen atmosphere. Propyl acrylate was purified through a basic alumina column and a molecular sieves 4A column. After stirring for 24 hours, methanol was added to stop the reaction. After washing with a 50% aqueous methanol solution using a separatory funnel, it was vacuum dried at 120 ° C. to obtain 10.2 g of a colorless and transparent liquid compound (yield 69%). As a result of GPC measurement, the mass average molecular weight was 2000 (polystyrene conversion), Mw / Mn = 1.15, and 5% of the molecular weight was less than 500.

Production Example 2
Example of PEA production: 2.4 ml (2.4 mmol) of a toluene solution (1.0 mol / l) of tri (n-butyl) aluminum, 5.9 ml (5 mol) of a toluene solution (1.0 mol / l) of t-butyllithium 0.9 mmol) and 13.0 g (130 mmol) of ethyl acrylate were synthesized in the same manner as in Production Example 4 to obtain 8.5 g of a colorless and transparent liquid compound (yield 65%). As a result of GPC measurement, the mass average molecular weight was 2000 (polystyrene conversion), Mw / Mn = 1.20, and 5% of the molecular weight was less than 500.

Production Example 3
Production Example of PBA-1: A toluene solution (1.0 mol / l) of tri (n-butyl) aluminum (3.0 ml, 3.0 mmol) was mixed with 40 ml of toluene and cooled to -78 ° C. To this was added 7.4 ml (7.4 mmol) of a toluene solution of t-butyllithium (1.0 mol / l), and after stirring for several minutes, 16.1 g (126 mmol) of butyl acrylate was added at a temperature in the reaction system. It was added with care not to go up. This reaction was performed in a standard Schlenk tube under a nitrogen atmosphere, and the reagent was transferred using a syringe. Toluene was refluxed over sodium and then distilled under a nitrogen atmosphere. Butyl acrylate was purified through a basic alumina column and a molecular sieves 4A column. After stirring for 24 hours, methanol was added to stop the reaction. After washing with a 50% aqueous methanol solution using a separatory funnel, it was vacuum dried at 120 ° C. to obtain 11.6 g of a colorless and transparent liquid compound (yield 72%). As a result of GPC measurement, the mass average molecular weight was 2000 (polystyrene conversion), Mw / Mn = 1.15, and 5% of the molecular weight was less than 500.

Production Example 4
PBA-2: Tri (n-butyl) aluminum in toluene (1.0 mol / l) 1.0 ml (1.0 mmol), t-butyllithium in toluene (1.0 mol / l) 2.5 ml (2. 5 mmol) was synthesized in the same manner as in Production Example 2 to obtain 10.1 g of a colorless and transparent liquid compound (yield 63%). As a result of GPC measurement, the mass average molecular weight was 6000 (polystyrene conversion), Mw / Mn = 1.12, and the molecular weight less than 500 was less than 1%.

<Method for producing (meth) acrylic polymer-based soft material>
Production Example 5
Preparation of powder liquid type (meth) acrylic polymer-based soft materials A to L, N, O; using the powder material and liquid material having the composition shown in Table 1 below, and mixing them at the powder liquid ratio shown in Table 1 A soft resin was used. Each (meth) acrylic polymer was previously made into a powder material by removing coarse particles through a 200-mesh sieve. Further, 80 parts by weight of the liquid polymer or plasticizer shown in Table 1 and 20 parts by weight of ethanol were mixed to obtain a solution obtained by mixing until uniform. Ultimately, the operator mixed and used the powder material and the liquid material immediately before use.

Production Example 6
Preparation of paste type (meth) acrylic soft material M; prepared in the composition shown in Table 1. All the raw materials were mixed in advance, and a paste obtained by kneading for 15 minutes under reduced pressure using a planetary mixer (manufactured by Inoue Seisakusho) was filled in a tube to obtain a (meth) acrylic soft material M.

2. Styrene polymer soft material The raw materials used to prepare the styrene polymer soft material are as follows.
・ Methacryl-styrene copolymer “Hyperl M-6701”
Copolymerization ratio: methacryl / styrene = 30/70
・ Plasticizer Low molecular weight plasticizer dibutyl phthalate (manufactured by Tokyo Chemical Industry)
・ Ethanol (Wako Pure Chemicals)
<Method for producing styrene polymer-based soft material>
Production Example 7
M-6701 was prepared in advance by removing coarse particles through a 200-mesh sieve. A solution obtained by mixing 80 parts by weight of dibutyl phthalate and 20 parts by weight of ethanol and mixing until uniform was used as a liquid material. Ultimately, the operator mixed and used the powder material and the liquid material immediately before use.

3. Silicone polymer soft material The raw materials used for preparing the silicone polymer soft material are as follows.
・ Divinylpolysiloxane “ME-91” (manufactured by Toshiba Silicone)
・ Polyhydrogensiloxane "TSF-484" (manufactured by Toshiba Silicone)
-Fumed silica "Leoro seal MT-10" (manufactured by Tokuyama)
・ Chloroplatinic acid (manufactured by Tokyo Chemical Industry Co., Ltd.)
<Method for producing silicone polymer soft material>
Production Example 8
100 parts by weight of ME91, 3 parts by weight of TSF-484, 10 parts by weight of MT-10, A paste kneaded using a planetary mixer, and 100 parts by weight of ME91, 10 parts by weight of MT-10 Then, 0.5 parts by weight of chloroplatinic acid was mixed and the B paste kneaded using a planetary mixer was separated into tubes. These A paste and B paste were finally weighed by a surgeon immediately before use and kneaded with a spatula to obtain a soft material.

4). Vinyl acetate polymer-based soft material The raw materials used to prepare the vinyl acetate polymer-based soft material are as follows.
・ Vinyl acetate resin (Aldrich)
・ Ethanol (Wako Pure Chemical Industries)
<Method for producing vinyl acetate polymer soft material>
Production Example 9
70 parts by weight of vinyl acetate resin and 30 parts by weight of ethanol were mixed and kneaded using a planetary mixer to prepare a paste. The obtained paste was filled into a tube to obtain a composition.

5. Polyolefin polymer-based soft material The following products were obtained as polyolefin polymer-based soft materials, and cut into sheet shapes having a thickness of 2 mm.
・ Polyolefin elastomer resin “EXCELLINK1101” (manufactured by JSR)
B) Adhesive Adhesive was used as necessary when adhering the dental implant protective material to the denture base resin in each Example and Comparative Example. The adhesive used was as follows.
・ General instant adhesive "Aron Alpha" (Product name: Toagosei Co., Ltd.)
-Preparation adhesive material It synthesize | combines in the following manufacture examples 10. In addition, the abbreviation used in the manufacture example 10 points out the following (meth) acrylate type monomers.

MMA; methyl methacrylate BMA; n-butyl methacrylate Production Example 10
Synthesis of MMA and BMA (30:70) copolymer; MMA 3.0 g (30 mmol), BMA 10.0 g (70 mmol), AIBN 0.02 g, and toluene 10 ml were added to three necks, and nitrogen gas was added at a rate of 5 ml / min. And kept running for 2 hours. After stopping the nitrogen gas, an oil bath was attached and stirring was continued at a bath temperature of 70 ° C. for 6 hours. The reaction product was placed in 10 times the amount of methanol, and the resulting precipitate was collected and washed with methanol. The resulting precipitate was dissolved in benzene and freeze-dried to recover 8.6 g of residue (yield 66%). As a result of GPC measurement, the mass average molecular weight was 180,000 (polystyrene conversion), and Mw / Mn = 2.10.

  The obtained polymer was dissolved in ethyl acetate to obtain a 5 wt% solution. The insoluble matter was removed with filter paper, and it was subdivided into brown bottles to obtain adhesives.

Examples 1-15
Using powder-type (meth) acrylic polymer-based soft materials A to L, hardness, sine tangent (tan δ), repeated impact durability test, impact absorption test, colorability test, and mixing time measurement were performed.
The evaluation results are shown in Table 2.

  As shown in Table 2, repeated impact tests were conducted on SUS cylindrical test specimens planted at three different planting angles, and the planting angles after completion of the test were measured. It was found that the angle at the time of planting was maintained. In addition, when the conformity state of the silicone impression material in contact with the test specimen was observed, some of the examples showed slight voids, but none of the silicone impression material was damaged, and repeated impacts were observed. It was found that it was hardly affected by. Furthermore, when the impact absorbability was measured, a rebound height of 5 cm to 11 cm was observed in some examples, but the rebound height was 0 cm, which absorbed most of the initial impact. It has been suggested. Further, when a coloring test was performed, it was found that a slight red portion remained in Example 8 and Example 9, but in the other examples, no coloring was observed in the specimen. Examples 14 to 15 showed examples in which a liquid polymer and a plasticizer were used in combination, but when the mixing time was measured, it was shortened to 5 to 9 seconds, and even better operability could be obtained. As a result of the measurement, it was confirmed that the difference in hardness between the time of standing overnight after kneading and the time of immersion in water for about 1 month was about 4 and the change in hardness was small.

  From the above test results, it has been confirmed that the use of these soft resins helps to protect the position and angle of the planted solid and the mucous membrane while appropriately absorbing impact.

Comparative Example 1
Using the powder liquid type (meth) acrylic polymer soft resin P, hardness, sine tangent (tan δ), repeated impact durability test, impact absorbability test, coloring property test, and mixing time measurement were performed. The evaluation results are shown in Table 2.

  As shown in Table 2, the soft resin P had a hardness of 3 and a tan δ of 0.80, and was very soft and highly viscous. When repeated impact tests were conducted on SUS cylindrical test specimens planted at three different planting angles, most of the soft material affixed to the denture base resin had flowed out, and the effect was significant by the end of the test. It was suggested that it was reduced. When the planting angle after completion of the test was measured, it was found that the angle was greatly shifted in each specimen. Moreover, when the conformity state of the silicone impression material which touches the said test body was observed, the big space | gap was seen and the crack was seen in a part of silicone impression material. From these facts, it was found that they were strongly affected by repeated impacts and almost no protective effect on the mucous membrane was observed.

  From the above test results, it was found that when this soft material was used, the obtained kneaded product was likely to flow out, and the expected position and angle of the planted solid and the mucous membrane could not be protected.

Comparative Example 2
Using powder-type (meth) acrylic polymer-based soft resin Q, hardness, sine tangent (tan δ), repeated impact durability test, impact absorbability test, colorability test, and mixing time measurement were performed. The evaluation results are shown in Table 2.

  The soft resin Q had a hardness of 57 and a tan δ of 0.12, indicating that it has a hard property. When the impact test was repeatedly performed on the SUS cylindrical test specimens planted at three planting angles and the planting angles were measured after the completion of the test, the angles of the specimens planted at 60 ° and 45 ° shifted. I found out. Moreover, when the conformity state of the silicone impression material which touches the said test body was observed, the big space | gap was seen and the crack was seen in a part of silicone impression material. From these facts, it was found that they were strongly affected by repeated impacts and almost no protective effect on the mucous membrane was observed.

  From the above test results, it was found that when this soft resin was used, the obtained kneaded product was hard and the effect of protecting the expected position and angle of the planted solid and the mucous membrane could not be obtained.

Comparative Example 3
Without applying any soft material to the denture base resin cured body, the impact durability test, the impact absorption test, and the colorability test were repeated as they were. The evaluation results are shown in Table 2.

  As shown in Table 2, when the planting angle after completion of the test was measured, it was found that the angle was shifted in any specimen planted at any angle. Moreover, when the conformity state of the silicone impression material which touches the said test body was observed, the big space | gap was seen and the crack was seen in a part of silicone impression material. From these facts, it was found that they were strongly affected by repeated impacts and almost no protective effect on the mucous membrane was observed. Furthermore, when the impact absorbability was measured, the rebound height was 15 cm, and it was suggested that the rebound height greatly rebounded without any treatment.

  From the above test results, it was found that when no treatment was performed on the denture base resin surface, there was almost no protective effect on the position and angle of the transplanted solid and the mucous membrane.

Example 16
Using the styrene polymer soft material obtained in Production Example 7, hardness, sine tangent (tan δ), repeated impact durability test, impact absorption test, and colorability test were performed. The evaluation results are shown in Table 2.

  As shown in Table 2, the cured body made from this soft material had a hardness of 15 and a tan δ of 0.32. When the impact test was repeatedly performed on the SUS cylindrical test specimens planted at three different planting angles and the planting angles were measured after the completion of the test, no deviation in the angle was observed between the test specimens. I found that the angle was maintained. In addition, when the conformity state of the silicone impression material in contact with the test specimen was observed, no gap was seen between the test specimen and the silicone impression material, and the specimen was kept in close contact with each other. I found out. Furthermore, when the impact absorbability was measured, the rebound height was 0 cm, suggesting that most of the initial impact was absorbed. Further, when a coloring test was performed, it was confirmed that a red component remained slightly in the test body.

  From the above test results, it was suggested that the use of this soft material helps to protect the position and angle of the planted solid and the mucous membrane while absorbing a moderate amount of impact.

Example 17
Using the silicone polymer soft material obtained in Production Example 8, hardness, sine tangent (tan δ), repeated impact durability test, impact absorption test, and colorability test were performed. The evaluation results are shown in Table 2.

  As shown in Table 2, the cured body made from this soft material had a hardness of 25 and a tan δ of 0.05. When the impact test was repeatedly performed on the SUS cylindrical test specimens planted at three different planting angles and the planting angles were measured after the completion of the test, no deviation in the angle was observed between the test specimens. I found that the angle was maintained. In addition, when the conformity state of the silicone impression material in contact with the above test specimen was observed, there was a slight gap, but the silicone impression material was not destroyed and was hardly affected by repeated impacts. I understood. Furthermore, when the impact absorbability was measured, the rebound height was 11 cm, suggesting that the initial impact was absorbed. Moreover, although the coloring test was done, coloring was not seen by the test body.

  From the above test results, it was suggested that the use of this soft material helps to protect the position and angle of the planted solid and the mucous membrane while absorbing a moderate amount of impact.

Example 18
Using the vinyl acetate polymer-based soft material obtained in Production Example 9, hardness, sine tangent (tan δ), repeated impact durability test, impact absorbability test, and colorability test were performed. The evaluation results are shown in Table 2.

  As shown in Table 2, the cured body made from this soft material had a hardness of 9 and a tan δ of 0.45. When the impact test was repeatedly performed on the SUS cylindrical test specimens planted at three different planting angles and the planting angles were measured after the completion of the test, no deviation in the angle was observed between the test specimens. I found that the angle was maintained. In addition, when the conformity state of the silicone impression material in contact with the above test specimen was observed, there was a slight gap, but the silicone impression material was not destroyed and was hardly affected by repeated impacts. I understood. Furthermore, when the impact absorbability was measured, the rebound height was 0 cm, suggesting that most of the initial impact was absorbed. Moreover, although the coloring test was done, coloring was not seen by the test body.

  From the above test results, it was suggested that the use of this soft material helps to protect the position and angle of the planted solid and the mucous membrane while absorbing a moderate amount of impact.

Example 19
Using a sheet of polyolefin elastomer resin “EXCELLINK1101” (manufactured by JSR), hardness, sine tangent (tan δ), repeated impact durability test, impact absorption test, and colorability test were performed. The evaluation results are shown in Table 2.

  As shown in Table 2, the cured body made from this soft material had a hardness of 15 and a tan δ of 0.15. When the impact test was repeatedly performed on the SUS cylindrical test specimens planted at three different planting angles and the planting angles were measured after the completion of the test, no deviation in the angle was observed between the test specimens. I found that the angle was maintained. In addition, when the conformity state of the silicone impression material in contact with the test specimen was observed, no gap was seen between the test specimen and the silicone impression material, and the specimen was kept in close contact with each other. I found out. Furthermore, when the impact absorbability was measured, the rebound height was 5 cm, suggesting that most of the initial impact was absorbed. Moreover, although the coloring test was done, coloring was not seen by the test body.

  From the above test results, it was suggested that the use of this soft material helps to protect the position and angle of the planted solid and the mucous membrane while absorbing a moderate amount of impact.

DESCRIPTION OF SYMBOLS 1; Fixture 2; Abutment 3; Temporary denture 4; Gingiva 5; Alveolar bone 6; Implant protection material 7; Recessed part 8; Gingival suture part 9; Cylindrical specimen 10; Acrylic resin (pseudoalveolar bone)
11; Silicone impression material (pseudo gingiva)
12; Denture base resin cured body 13; Repeat load tester

Claims (7)

A protective material for dental implants, wherein a soft material having a Shore A hardness of 5 to 50 is used. The dental implant protective material according to claim 1, wherein the sine tangent at 37 ° C is in the range of 0.01 to 0.80.   The soft material has a mass average molecular weight in the range of 1000 to 10,000, and the proportion of oligomers having a molecular weight of 500 or less is 10% by mass or less, a liquid polymer at 37 ° C., and the mass average molecular weight dissolved in the liquid polymer is 2 The protective material for dental implants according to claim 1 or 2, comprising a soft polymer composition mainly composed of a solid polymer at 37 ° C which is not less than 10,000.   The dental implant protection according to any one of claims 1 to 3, wherein the solid polymer at 37 ° C having a mass average molecular weight of 20,000 or more dissolved in the liquid polymer is a (meth) acrylic non-crosslinked polymer. Wood.   The packaging form is divided into (1) powder material and (2) liquid material, and is used as a paste in which both materials are mixed at the time of use. (1) Mass dissolved in liquid polymer in powder material A polymer powder which is solid at 37 ° C. having an average molecular weight of 20,000 or more, and (2) the liquid material contains an oligomer having a mass average molecular weight in the range of 1000 to 10,000 and a molecular weight of 500 or less The protective material for dental implants according to any one of claims 1 to 4, which comprises a liquid polymer having a proportion of 10% by mass or less.   (1) The solid polymer at 37 ° C. having a mass average molecular weight of 20,000 or more, which is contained in the powder material and dissolved in the liquid polymer, has a glass transition temperature of 10 to 80 ° C. The protective material for dental implants as described.   (2) The protective material for dental implants according to any one of claims 5 to 6, wherein the liquid material contains a low molecular weight plasticizer.

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