KR20170055315A - Water-settable composition for medical restoration using thermoreversible hydrogel and application method using atificial biomaterial manufactured by the same - Google Patents

Abstract

The present invention relates to a medical water-curing restoration material composition comprising a thermoreversible hydrogel, and a method for applying an artificial biomaterial using the sake. More specifically, a thermoreversible hydrogel, which is in a liquid state at room temperature and in a gel form at the body temperature, is used as a water-providing substance for water-curing of MTA According to the present invention, the composition compensates weakness that a water-curing type requires longer curing time, thereby instantly applying a shape and performing curing. Also, the composition can be prevented from washing out by the oral environment during the curing process, and it is possible to apply creamy properties to facilitate the workability.

Description

TECHNICAL FIELD [0001] The present invention relates to a medical water-curing restoration material composition comprising a thermoreversible hydrogel, and a method of applying an artificial biomaterial using the same. BACKGROUND ART < RTI ID = 0.0 >

The present invention relates to a medical water-curing restoration material composition comprising a thermoreversible hydrogel, and a method of applying an artificial biomaterial using the composition. More particularly, The present invention relates to a technique for utilizing a thermoreversible hydrogel as a moisture providing material for water hardening of MTA.

Calcium silicate has been used as a mineral trioxide aggregate (MTA) in various medical fields, especially dental field. The MTA is a breakthrough bioceramic material that was first introduced in the JOE Journal of the United States in 1993 to treat natural teeth such as neuropathy, and has been widely recognized as a material that can overcome the limitations of conventional materials.

MTA is mainly composed of CaO, SiO ₂ , Bi ₂ O _3, etc. It has excellent analgesic effect, high biocompatibility, excellent airtightness, ability to regenerate periodontal tissues (cementum and alveolar bone) and antibacterial effect against bacteria causing inflammation , It is usually used as a water-hardening type which hardens when there is water, so that it can be used in a place where there is a watery mouth or blood.

MTAs are composed of powders and distilled water solutions and have been supplied for immediate mixing in clinical use. Conventional MTA consists of Portland cement (Portland cement) about 80% and bismuth oxide (about 20%) and because it has the advantage of water hardening, it can be cured at the bleeding site. .

The MTA has the property of releasing a large amount of calcium ions and alkalizing the surrounding environment during the water hardening process. When calcium ions are released, it induces cell differentiation of surrounding tissue to help formation of hard tissue, and alkali environment makes environment that microorganism does not grow, and it can prevent from infection.

Despite the above advantages, conventional water-curing type products require a long curing time of about 180 minutes. Therefore, it is inconvenient to visit a hospital twice or more without completing a one-time clinical treatment. In addition, due to the long curing time, there is a possibility of being washed-out in a variety of body environments, particularly in an oral environment with a large amount of body fluids during the curing process. In addition, when a liquid such as distilled water is simply used as a water- Workability was a problem.

Korean Patent Laid-Open Publication No. 2010-0037979 ('Premixed cement paste and method for producing cement characteristic material', published on Apr. 12, 2010)

Disclosure of Invention Technical Problem [8] Accordingly, the present invention has been made keeping in mind the above problems occurring in the prior art, and it is an object of the present invention to provide a moisture providing material for curing a water repellent material so as to minimize the water hardening time, Which is thermally reversible hydrogel.

In order to achieve the above-mentioned object, the present invention provides a medical water-curing restoration material composition according to an embodiment of the present invention, wherein the composition comprises an inorganic filler powder and a hydrating agent for inducing water hardening of the inorganic filler powder, Wherein the inorganic filler powder comprises calcium silicate powder and the hydrocracking agent comprises a thermoreversible hydrogel which is in the form of a gel under a body temperature condition and a liquid form under a normal temperature condition as an active ingredient And a medical water-curing restoration material composition.

The thermoreversible hydrogel may be any one selected from the group consisting of polyethylene glycol (PEG), polypropylene glycol (PPG), and block copolymers of polyethylene glycol and polypropylene glycol.

In addition, the thermoreversible hydrogel may be a three-block copolymer of polyethylene glycol and polypropylene glycol, preferably a PEG-PPG-PEG 3 block copolymer.

In addition, the thermoreversible hydrogel may be a compound represented by the following formula (1).

[Chemical Formula 1]

(Wherein x, y and z are each an integer of 1 or more).

The hydrocracking agent may be a mixture of the thermoreversible hydrogel and distilled water. Preferably, the hydrocracking agent may be a mixture of the thermoreversible hydrogel and distilled water in a concentration of 5 to 40 wt%, more preferably, And the thermoreversible hydrogel may be mixed with distilled water at a concentration of 20 to 30 wt%.

In addition, the thermoreversible hydrogel may be a material having a phase transition temperature in the range of 10 to 20 ° C.

According to another aspect of the present invention, there is provided a method of applying a water-cured cement-type artificial biomaterial using a medical water-curing restoration material composition, the method comprising: Preparing a hydrocracking agent by mixing a thermoreversible hydrogel having a liquid form under distilled water at room temperature and distilled water; Blending the inorganic filler powder comprising calcium silicate powder with the hydraulic agent; And applying a restorative material composition that is formulated to a customer in need of direct or indirect restoration, filling, or implantation of a water-cured, cement-like artificial biomaterial.

At this time, in the step of mixing the inorganic filler powder and the hydrocuring agent, the inorganic filler powder and the hydrocracking agent may be blended in a ratio of 3: 1 based on mass (g) to volume (ml).

In addition, the step of applying the restoration material composition may be a dimension demodulation process for filling a dentin hole of a tooth, a process of filling a root canal of a tooth, or a process of implanting into the body as an artificial bone material.

The thermoreversible hydrogel may be a PEG-PPG-PEG 3 block copolymer, and preferably a compound of the following formula (1).

[Chemical Formula 1]

(Wherein x, y and z are each an integer of 1 or more).

The hydrocracking agent may be a mixture of the thermoreversible hydrogel and distilled water. The thermoreversible hydrogel may be a mixture of 20 to 30 wt% of the thermoreversible hydrogel in distilled water. The material may have a phase transition temperature in the range of 10 to 20 ° C. .

The medical water-curing restoration material composition comprising the thermoreversible hydrogel of the present invention as described above and the method of applying the artificial biomaterial using the same, It is possible to minimize the hardening time through immediate shaping of the hardening agent, prevent the restoration material from being washed by the body fluid or the like in the hardening process, and improve the workability by imparting a creamy property.

1 is a photograph showing the hydrogel of Example 1-5 (H5, H10, H20, H30, H40) of the present invention at room temperature.
2 is a graph showing the phase transition temperatures of Examples 1-5 (H5, H10, H20, H30, H40) of the present invention measured by differential scanning calorimetry (DSC).
3 is a graph plotting a phase transition temperature according to Example 1-5 of the present invention.
4 shows the flow characteristics of Example 1-5 (H5, H10, H20, H30, H40) and Comparative Example (MDW) of the present invention at room temperature (12 ± 2 ° C) and body temperature (37 ± 2 ° C) The graphs (A) and (B) show the measured values.
5 is a graph (upper) and a photograph (lower) in which film characteristics of Examples 1-5 (H5, H10, H20, H30, H40) and Comparative Example (MDW) of the present invention were measured.
6 is a graph showing solubility (g) values of Examples 1-5 (H5, H10, H20, H30, H40) and Comparative Example (MDW) of the present invention.
FIG. 7 is a graph showing the release of calcium ions over time in Examples 1-5 (H5, H10, H20, H30, H40) and Comparative Example (MDW) of the present invention.
8 is a graph showing changes in pH over time of Examples 1-5 (H5, H10, H20, H30, H40) and Comparative Example (MDW) of the present invention.
9 is a graph showing compression strength (MPa) of Examples 1-5 (H5, H10, H20, H30, H40) and Comparative Example (MDW) of the present invention.
10 is a photograph of results of bioactivity measurement experiments for Examples 1-5 (H5, H10, H20, H30, H40) and Comparative Example (MDW) of the present invention.
11 is a graph showing the toxicity test result of hydrogel as a part of the cytotoxicity test for Example 1-5 (H5, H10, H20, H30, H40) of the present invention.
FIG. 12 is a graph showing experimental toxicity test results as a part of the cytotoxicity test for Examples 1-5 (H5, H10, H20, H30, H40) and Comparative Example (MDW) of the present invention.
FIG. 13 is a graph showing the results of bone morphogenesis in a control group (Blank control, BC) and a control group (Osteogenic media control, OC) in which bone marrow does not occur in addition to Examples 3 and 4 (H20, H30) Alkaline phosphatase activity (ALP test) is a graph and a photograph of the result of the ALP test for measuring the cell differentiation.
FIG. 14 is a graph showing the results of bone morphogenesis in a control group (Blank control, BC) and a control group (Osteogenic media control, OC) in which bone marrow does not occur in addition to Examples 3 and 4 (H20, H30) (Alizarin red-S staining, ARS-S) for the measurement of cell differentiation.

Hereinafter, preferred embodiments of the present invention will be described in detail with reference to the drawings. Prior to the description, terms and words used in the present specification and claims should not be construed as limited to ordinary or dictionary meanings and should be construed in accordance with the technical concept of the present invention.

Throughout this specification, when a member is " on " another member, this includes not only when the member is in contact with another member, but also when there is another member between the two members.

Throughout this specification, when an element is referred to as "including" an element, it is understood that it may include other elements as well, without departing from the other elements unless specifically stated otherwise.

The terms "first "," second ", and the like are intended to distinguish one element from another, and the scope of the right should not be limited by these terms. For example, the first component may be referred to as a second component, and similarly, the second component may also be referred to as a first component.

In each step, the identification code is used for convenience of explanation, and the identification code does not describe the order of the steps, and each step may be performed differently from the stated order unless clearly specified in the context. have. That is, each of the steps may be performed in the same order as described, or may be performed substantially concurrently or in the reverse order.

First, the present invention provides a medical water-curing restoration material composition according to a preferred embodiment, wherein the composition comprises an inorganic filler powder and a hydrating agent for inducing water hardening of the inorganic filler powder, wherein the inorganic filler powder comprises calcium silicate Wherein the hydrocracking agent comprises a thermoreversible hydrogel which is in the form of a gel under a body temperature condition and a liquid form under a normal temperature condition as an active ingredient, Lt; / RTI >

The term "medical use" is meant to encompass all kinds of artificial biomaterials such as bone cement, artificial bone substitute materials, implant materials, and the like, as well as the use of dimensional demodulation materials for root canal treatment used in dentistry.

The restoration material composition of the present invention mainly comprises an inorganic filler powder serving as a physical filler and a hydrating agent for supplying water to induce water hardening. The inorganic filler powder includes calcium silicate powder, and the hydrocracker contains a thermoreversible hydrogel which is in the form of a gel under the body temperature condition but forms a liquid form at the normal temperature condition.

In order to perform the above functions in relation to the temperature of the phase change, the thermoreversible hydrogel is any one selected from the group consisting of polyethylene glycol (PEG), polypropylene glycol (PPG), and block copolymers of polyethylene glycol and polypropylene glycol And is preferably a three-block copolymer of polyethylene glycol and polypropylene glycol, more preferably a PEG-PPG-PEG 3 block copolymer.

Specifically, in order to exhibit the effect of water-curing inherent calcium ion release and alkaline environment composition in addition to the optimum phase change condition, workability condition, washout prevention condition, and the like, the thermothermal hydrogel is most preferably a compound represented by the following formula (1).

[Chemical Formula 1]

(Wherein x, y and z are each an integer of 1 or more).

In addition, it is preferable that the hydrocracking agent is used in a form in which a thermoreversible hydrogel and distilled water as described above are blended, and the 100% raw material of the thermoreversible hydrogel is usually handled as a powder.

Particularly, the blending ratio of the raw material powder and the distilled water is preferably 5 to 40 wt% in view of improving the workability by imparting the function of the hydrogel and imparting a creamy property, and particularly 20 to 30 wt% %, And this can be supported by various experimental examples to be described later.

In order to exhibit the function of the present invention, a hydrocuring agent containing a thermoreversible hydrogel must have a phase transition temperature of 10 to 20 占 폚 because it must be cured at a living body temperature range to have a gel shape and at the same time, Material.

According to a preferred embodiment of the present invention, there is provided a method of applying a water-cured cement-type artificial biomaterial using a medical water-curing restoration material composition according to a preferred embodiment of the present invention, wherein a gel form is formed under body temperature conditions, Preparing a hydrocracking agent by mixing a thermoreversible hydrogel with distilled water; Blending the inorganic filler powder comprising calcium silicate powder with the hydraulic agent; And applying a restorative material composition that is formulated to a customer in need of direct or indirect restoration, filling, or implantation of a water-cured, cement-like artificial biomaterial.

The above-mentioned 'artificial biomaterial' is meant to encompass not only restoration materials for endodontic treatment used in dentistry but also artificial biomaterials such as orthopedic bone cement, artificial bone replacement materials, and implant materials. 'Application method of artificial biomaterials' refers to the process of applying inorganic filler powder and hydrants to the application site of artificial biomaterials in vivo, Treatment, and diagnosis.

It is preferable that the inorganic filler powder and the water-hardening agent are blended in a ratio of 3: 1 based on the mass (g) of the filler powder and the volume (ml) of the water-reducing agent in view of the effect of the present invention.

Next, the step of applying the restoration material composition to a living body in a living body includes a step of demolishing a dentin hole of a tooth, a step of filling a root canal of a tooth, a step of implanting the material into the body as an artificial bone material, and the like .

BEST MODE FOR CARRYING OUT THE INVENTION Hereinafter, embodiments of a medical water-curing restoration material composition comprising a thermoreversible hydrogel of the present invention and a method of applying an artificial biomaterial using the same will be described. It will be understood by those skilled in the art that various changes in form and details may be made therein without departing from the spirit and scope of the invention as defined by the appended claims and their equivalents. shall.

Various comparative experimental results between various embodiments and comparative examples according to the present invention will be described below.

Examples according to the present invention (Examples 1-5, or H5, H10, H20, H30, and H40 in order) are prepared by preparing inorganic filler powders and preparing hydrocrackers containing hydrogels .

Inorganic filler powder is a commonly used medical MTA product using white portland cement powder and consists of 80% Portland cement component and 20% bismuth oxide component.

Next, a hydrogel containing a hydrogel is prepared by mixing a material of the following formula (1) (polyethylene-polypropylene glycol) with distilled water, mixing ratio is 5% (Example 1, H5) Each experimental group is prepared by varying 10% (Example 2, H10), 20% (Example 3, H20), 30% (Example 4, H30) and 40% (Example 5, H40).

[Chemical Formula 1]

(Wherein x, y and z are each an integer of 1 or more).

On the other hand, the comparative example (MDW) used as the control group was used by mixing only ordinary medical MTA and distilled water. In the above Examples 1-5 and Comparative Examples, the compounding ratio of inorganic filler powder and water- Based on the volume ratio, in a ratio of 3: 1.

Comparisons of the components of the prepared experimental groups (Examples 1-5 and Comparative Examples) are shown in Table 1 below.

division Hydrogel
Content ratio (wt%) Hydroponics
Amount added (ml) Distilled water
Amount added (ml) Amount of inorganic filler powder added (g) Example 1 (H5) 5 0.3 -

0.9 Example 2 (H10) 10 0.3 - Example 3 (H 2 O) 20 0.3 - Example 4 (H30) 30 0.3 - Example 5 (H40) 40 0.3 - Comparative Example (MDW) - - 0.3

[ Experimental Example  One] Hydrogel  Properties: Room temperature conditions

1 is a photograph showing the hydrogel of Example 1-5 (H5, H10, H20, H30, H40) of the present invention at room temperature.

Referring to FIG. 1, it was confirmed that in Examples 1-4, a liquid state was observed at room temperature, and in Example 5 in which the content ratio of hydrogel was close to 40 wt%, a slightly cured gel Respectively.

[ Experimental Example  2] Hydrogel  Properties: Phase-to-phase temperature measurement (differential scanning calorimetry)

FIG. 2 is a graph showing the phase transition temperatures of Examples 1-5 (H5, H10, H20, H30, H40) of the present invention measured by differential scanning calorimetry (DSC) 5 is a graph plotting the phase transition temperature of Example 1-5.

Referring to FIG. 2, it was confirmed that the higher the concentration of the hydrogel, the lower the phase transition temperature, and the phase transition temperature close to room temperature was found in Example 1-4.

FIG. 3 is a graph plotting the phase transition temperature of each example according to the differential scanning calorimetry of FIG. 2 according to the concentration of the hydrogel, showing that there is a correlation between the phase transition temperature and the hard gel concentration.

[ Experimental Example  3] Flow measurement

4 shows the flow characteristics of Example 1-5 (H5, H10, H20, H30, H40) and Comparative Example (MDW) of the present invention at room temperature (12 ± 2 ° C) and body temperature (37 ± 2 ° C) The graphs (A) and (B) show the measured values.

4, statistically significant results were obtained in Examples 3 and 4 (H20 and H30) under two different temperature conditions, the operable temperature (12 占 폚 2 占 폚) and the human body temperature (37 占 2 占 폚) Flow characteristics.

On the other hand, both of the MDW and the H 1 and H 2 in the comparative examples (MDW) and H 2 (H 5 and H 10) exhibited well-flowing properties. In Example 5 (H40)

[ Experimental Example  4] Measurement of film thickness

5 is a graph (upper) and a photograph (lower) in which film characteristics of Examples 1-5 (H5, H10, H20, H30, H40) and Comparative Example (MDW) of the present invention were measured.

Referring to FIG. 5, Examples 3 and 4 (H20 and H30) showed statistically significant coatings. In Examples 3 and 4, as the hydrogel was contained, it was deformed into a cream-like texture that was the same as wet sand in the prior art. It can be seen that the lubrication between the powder particles is improved and uniformly spread, and this property can be supported by a low value of the film thickness.

As a result, it can be seen that the present invention has a property of being easily injected into the body by having a low degree of coating from a clinical viewpoint.

[ Experimental Example  5] Solubility measurement

6 is a graph showing solubility (g) values of Examples 1-5 (H5, H10, H20, H30, H40) and Comparative Example (MDW) of the present invention.

Experiments were carried out based on the assumption that mass loss should be within 3% of the original specimen mass according to the Root canal sealer specification (ISO 6876: 2008). Referring to FIG. 6, the reference line in which each weight loss is 3% in each experimental group is a light gray graph. The standards for each experimental group and the results of the experiments (graphs of light gray and dark gray) showed large solubilities in Example 4 (H30) and Example 5 (H40).

[ Experimental Example  6] Calcium ion emission measurement

FIG. 7 is a graph showing the release of calcium ions over time in Examples 1-5 (H5, H10, H20, H30, H40) and Comparative Example (MDW) of the present invention.

Referring to FIG. 7, it can be seen that Example 3 (H20) and Example 4 (H30) have a relatively high calcium ion release amount, and the state is maintained even when the entire period is covered.

[ Experimental Example  7] Measurement of pH change

8 is a graph showing changes in pH over time of Examples 1-5 (H5, H10, H20, H30, H40) and Comparative Example (MDW) of the present invention.

As shown in FIG. 8, in comparison with Comparative Example (MDW) in which general distilled water other than the hydrogel according to the present invention was blended, Example 1-5 of the present invention can maintain the high pH for a long period of time and effectively form an alkaline environment composition Respectively.

[ Experimental Example  8] Compressive strength measurement

9 is a graph showing compression strength (MPa) of Examples 1-5 (H5, H10, H20, H30, H40) and Comparative Example (MDW) of the present invention.

Referring to FIG. 9, it was confirmed that the compressive strengths of Examples 1-3 (H5, H10, and H20) were equivalent to those of Comparative Example (MDW), which is a control group. The compressive strength of Example 4 (H30) was evaluated to be comparatively low. However, the compressive strength was not so large when applied to implantable bone graft materials or tooth restoration / demodulation instead of bone support.

[ Experimental Example  9] Life castle  Property test

10 is a photograph of results of bioactivity measurement experiments for Examples 1-5 (H5, H10, H20, H30, H40) and Comparative Example (MDW) of the present invention.

As a result of checking the crystals formed on the surfaces of the examples and comparative examples by SEM, platelet and needle-like crystals were confirmed. This means that it is similar to hydroxyapatite.

As a result of XRD analysis, hydroxyapatite and calcium-rich surface were observed in all experimental groups including the comparative example. As a result of EDS analysis, Ca / P value of crystals formed on the surface of each test group was found to be ideal hydroxy It can be confirmed that it falls within the range of values for the apatite crystal (Ca / P = 1.67) or in the body (Ca / P = 1.5 to 1.7).

[ Experimental Example  10] Cytotoxicity test: Hydrogel  Toxicity experiment

11 is a graph showing the toxicity test result of hydrogel as a part of the cytotoxicity test for Example 1-5 (H5, H10, H20, H30, H40) of the present invention.

Referring to FIG. 11, it was confirmed that cell viability was 80% or more for all the hydrogel test groups.

[ Experimental Example  11] Cytotoxicity test: Experimental group  Toxicity experiment

FIG. 12 is a graph showing experimental toxicity test results as a part of the cytotoxicity test for Examples 1-5 (H5, H10, H20, H30, H40) and Comparative Example (MDW) of the present invention.

Materials were applied to the human mesenchymal stem cell line (hMSC) for cell differentiation experiments. All cytotoxicity (less than 20% cell viability) was observed in all experimental groups including 100% efflux (100% ext.) (Light gray graph) and comparative example. However, when 50% eluate (50% ext.) Was applied, cell viability was over 100% for all experimental groups.

[ Experimental Example  12] Cell differentiation experiment: ALP activity test and ARS-S test

FIG. 13 is a graph showing the results of bone morphogenesis in a control group (Blank control, BC) and a control group (Osteogenic media control, OC) in which bone marrow does not occur in addition to Examples 3 and 4 (H20, H30) FIG. 14 is a graph and photographs of results of Alkaline phosphatase activity (ALP test) for measuring cell differentiation of the cells according to Examples 3 and 4 (H20, H30) and Comparative Example (MDW) Alizarin red-S staining (ARS-S) was used to measure cell differentiation for control (Blank control, BC) and osteogenic media control (OC) ) Is a graph and a photograph of the result.

The BC (blank control) experimental group showed that the cells did not respond to the reagents in the unstimulated cell group. The composition is basic DMEM-Glutamax medium + 10% fetal bovine serum + 1% Antibiotics.

The osteogenic media control (OC) experimental group is a control group for bone differentiation, and it is confirmed that the cells have differentiation characteristics when they grow in the bone differentiation medium. The composition is basic DMEM-Glutamax medium + 10% fetal bovine serum + 1% Antibiotics + 50 μl / ml L-ascorbic acid + 10 mM beta-glycerol phosphate.

All experiments were carried out in an OC environment and all experimental results were normalized to BC, and the bone marrow differentiation was differentiated in the bone marrow differentiation group and several times more differentiated in the additional group.

Specifically, the experimental procedure is as follows.

After the cells are placed on the plate, after 24 hours, confirm that the cells adhere to the bottom of the plate and replace the base solution with the test solution. First, the experimental group was selected as Example 3 (H20) and Example 4 (H30), which are excellent in physical properties. Each experimental group is prepared and cured according to the previously prepared method. The cured test group is sterilized in UV light for 30 minutes. Calculate the area of the specimen according to ISO 10993-12 according to 3 cm ² / ml and immerse in the medium. And then eluted in a shaking incubator at 37 ° C for 24 hours.

After cell attachment, the supernatant, which is a normal medium, is removed and replaced with MDW eluate mixed with each diluted BC, OC, H20, H30 and conventional water. The remaining experimental group except BC is diluted with OC. The cell lysate is exchanged with fresh solution once every 2-3 days.

After 7 days, ALP activity and ALP staining test were carried out and Alizarin red staining was carried out 14 days later. ALP activity was measured by quantifying the ALP enzyme in the cytoplasm using the ALP kit as the protein of each group and expressing the relative value. In another plate, cells were stained with ALP staining kit and stained.

After 14 days, ARS was carried out. Cells were fixed and stained with 2% filtered alizarin red dye. After photographing, add 10% Cethylpyridium chloride solution to the same stained plate, dissolve all the stained minerals for 30 minutes, and measure the absorbance at 560 nm.

As a result, the medical water-curing restorative material composition comprising the thermoreversible hydrogel of the present invention as described above and the method of applying the artificial biomaterial using the same can not provide advantages such as hydration type calcium ion release and alkali environment composition It is possible to minimize the hardening time through immediate shaping in the body, to prevent the restoration material from being washed by the body fluid or the like in the hardening process, and to impart the creamy property to improve the workability.

In particular, it has been found that the use of a hydrogel containing a hydrogel at a concentration of 20 to 30 wt% in order to mix an inorganic filler powder such as MTA is most suitable as a biomaterial for medical use including dental use, The concentration was also equivalent or superior to the comparative example in which distilled water was simply mixed. In addition, the composition of the present invention is expected to be widely applicable to the field of biomedical devices such as bone cements and bone substitute materials in addition to dentistry.

The present invention is not limited to the above-described specific embodiment and description, and various changes and modifications may be made by those skilled in the art without departing from the scope of the present invention as claimed in the claims. And such modifications are within the scope of protection of the present invention.

Claims (16)

In a medical water-curing restoration material composition,
Wherein the composition comprises an inorganic filler powder and a hydrating agent to induce water hardening of the inorganic filler powder,
Wherein the inorganic filler powder comprises calcium silicate powder,
Wherein the hydrocracking agent comprises a thermoreversible hydrogel in the form of a gel under body temperature conditions and a liquid form under normal temperature conditions as an active ingredient. The method according to claim 1,
Wherein said thermoreversible hydrogel is any one selected from the group consisting of polyethylene glycol (PEG), polypropylene glycol (PPG), and block copolymers of polyethylene glycol and polypropylene glycol. The method according to claim 1,
Wherein the thermoreversible hydrogel is a three-block copolymer of polyethylene glycol and polypropylene glycol. The method of claim 3,
Wherein said thermoreversible hydrogel is a PEG-PPG-PEG 3 block copolymer. The method of claim 4,
Wherein the thermoreversible hydrogel is a compound of the following formula (1).
[Chemical Formula 1]

(Wherein x, y and z are each an integer of 1 or more). The method according to claim 1,
Wherein the water-hardening agent is a mixture of the heat-reversible hydrogel and distilled water. The method of claim 6,
Wherein the hydrocracking agent is a mixture in which the thermoreversible hydrogel is mixed with distilled water at a concentration of 5 to 40 wt%. The method of claim 7,
Wherein the hydrocracking agent is a mixture in which the thermoreversible hydrogel is mixed with distilled water at a concentration of 20 to 30 wt%. The method according to claim 1,
Wherein the thermoreversible hydrogel is a substance having a phase transition temperature within a range of 10 to 20 占 폚. A method of applying a water-hardened cement-type artificial biomaterial using a medical water-curing restoration material composition,
Preparing a hydrocracking agent by mixing a thermoreversible hydrogel in the form of a gel under a body temperature condition and a liquid form under a normal temperature condition with distilled water;
Blending the inorganic filler powder comprising calcium silicate powder with the hydraulic agent; And
Applying a restorative material composition formulated to a body site requiring direct or indirect restoration, filling or implantation of a hydroentangled cementitious artificial biomaterial;
Wherein the method comprises the steps of: The method of claim 10,
In the step of blending the inorganic filler powder and the hydrocracking agent,
Wherein the inorganic filler powder and the hydrocracking agent are compounded in a ratio of 3: 1 based on mass (g) to volume (ml). The method of claim 10,
The step of applying the restoration material composition comprises:
The method of applying an artificial biomaterial according to any one of claims 1 to 3, wherein the dentin hole of the tooth is demolded, the tooth root is filled, or the implant is implanted into the body as an artificial bone material. The method of claim 10,
Wherein the thermoreversible hydrogel is a PEG-PPG-PEG 3 block copolymer. 14. The method of claim 13,
Wherein the thermoreversible hydrogel is a compound represented by the following formula (1).
[Chemical Formula 1]

(Wherein x, y and z are each an integer of 1 or more). The method of claim 10,
Wherein the hydrocreating agent is a mixture of the thermoreversible hydrogel and distilled water, wherein the thermoreversible hydrogel is mixed with distilled water at a concentration of 20 to 30 wt%. The method of claim 10,
Wherein the thermoreversible hydrogel is a substance having a phase transition temperature in the range of 10 to 20 占 폚.

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