Composite hydrogel for treating dentin hypersensitivity and preparation method thereof

Abstract

The invention discloses composite hydrogel for treating dentin hypersensitivity and a preparation method of the composite hydrogel, and belongs to the field of biomedical materials. The composite hydrogel comprises bioactive glass, gel network composition molecules and water. The composite hydrogel disclosed by the invention has good biocompatibility and can reside in an oral environment for a long time; the excellent induced mineralization characteristic of bioactive glass is reserved, and dentinal tubules can be effectively sealed within 24 hours, so that dentin hypersensitivity is remarkably relieved; the dentin hypersensitivity inhibitor has good plasticity and stability, can be customized according to specific requirements of different patients, is expected to be developed into a novel dentin hypersensitivity treatment medicine, and shows extremely high commercial application potential and value.

Description

Technical Field

[0001] This invention relates to the field of biomedical materials, specifically to a composite hydrogel for the treatment of dentin hypersensitivity and its preparation method. Background Technology

[0002] Dentin hypersensitivity is a common clinical symptom in oral medicine, characterized by brief, sharp pain in response to external physical or chemical stimuli (such as cold, heat, acid, and mechanical friction). It severely impacts patients' quality of life and can lead to more serious dental health problems. The root cause of dentin hypersensitivity lies in the direct action of external stimuli on the dental pulp nerves through open dentinal tubules, triggering a pain response. This process is currently dominated by fluid dynamics theory; that is, after the dentinal tubules are exposed, external stimuli can cause disturbance of the fluid within the tubules, thereby activating the pain receptors at the nerve endings in the dental pulp. The main causes of dentinal tubule exposure include mechanical wear (such as long-term improper brushing), long-term erosion from acidic diets, gingival recession, and periodontal disease. It is important to note that dentin hypersensitivity is not a self-limiting disease; if not treated promptly, it can lead to pulp damage and even tooth loss. Therefore, the treatment of dentin hypersensitivity has significant clinical importance.

[0003] Current treatment strategies for dentin hypersensitivity primarily revolve around two aspects: reducing the sensitivity of the dental pulp nerve and sealing the dentinal tubules. Root canal surgery, which removes the dental pulp tissue inside the tooth, can completely eliminate hypersensitivity symptoms. However, root canal treatment is complex, and the treated tooth may become brittle due to loss of nutrient supply, increasing the risk of fracture. Patients often require post-operative crown restoration to strengthen the tooth; therefore, this method is only suitable for certain severe cases. For patients with relatively mild symptoms, numerous clinical products have been developed for treating dentin hypersensitivity, such as penetrating resins and desensitizing pastes. Penetrating resins can penetrate into exposed dentinal tubules and polymerize and cure without damaging healthy tooth structure, thereby reducing hypersensitivity symptoms. However, penetrating resins often lack sufficient strength and suffer from curing shrinkage and low bonding strength with the tooth. Therefore, they may wear down or even fall out during daily chewing, ultimately leading to seal failure. Desensitizing pastes are widely accepted due to their lower cost and the fact that patients can use them themselves without frequent dentist visits. However, because its residence time on the tooth surface is relatively short, it usually requires continuous use for several weeks to achieve a certain effect, and it is prone to relapse after discontinuation, which places high demands on the patient's self-control. In addition, long-term use of desensitizing paste may cause unnecessary irritation to periodontal tissues, leading to problems such as gingival redness, swelling, pain, or inflammation, thus affecting oral health.

[0004] Bioactive glass reacts with saliva in the oral environment, inducing the formation of hydroxyapatite and forming a tight bond with the hard tooth structure. However, the process of inducing mineralization with bioactive glass takes at least several hours, and its inherent properties make it difficult to maintain a stable presence in a designated location within the oral environment for an extended period, thus limiting its full effectiveness. While combining bioactive glass with infiltrated resin can effectively prolong its residence time on the tooth surface, the hydrophobic properties of the infiltrated resin not only limit the effectiveness of the bioactive glass but also reduce its bonding strength on the tooth surface, increasing the risk of detachment. Summary of the Invention

[0005] To address the aforementioned problems, this invention provides a composite hydrogel for the treatment of dentin hypersensitivity and its preparation method. This invention develops a bioactive glass / hydrogel composite material by combining bioactive glass with a hydrogel. The composite hydrogel of this invention exhibits excellent biocompatibility and can achieve long-term residence in the oral environment; it retains the excellent mineralization-inducing properties of bioactive glass and can effectively seal dentinal tubules within 24 hours, thereby significantly alleviating dentin hypersensitivity.

[0006] The present invention first provides a composite hydrogel comprising bioactive glass, gel network constituent molecules, and water.

[0007] In the above-mentioned composite hydrogel, the contents of each component by weight percentage are as follows: bioactive glass greater than 0 and less than or equal to 99%, gel network constituent molecules greater than 0 and less than or equal to 99%, and water greater than 0 and less than or equal to 99%.

[0008] Specifically, the bioactive glass content is greater than or equal to 1% and less than or equal to 50%, the gel network component is greater than or equal to 1% and less than 50%, and the remainder is water.

[0009] In one embodiment of the present invention, the contents of each component by weight percentage are: 20% bioactive glass, 10% gel network constituent molecules, and the remainder is water.

[0010] In one embodiment of the present invention, the mass ratio of the bioactive glass and the gel network components in the composite hydrogel is 10:1-50; specifically, it can be 2:1, 1:1 or 1:2.

[0011] In one embodiment of the present invention, the composite hydrogel is composed of bioactive glass, gel network molecules, and water.

[0012] The mass ratio of the bioactive glass, gel network components, and water is 10:1-50:1-100; more specifically, it can be 10:5:35.

[0013] In the aforementioned composite hydrogel, the bioactive glass is a phosphosilicate bioactive glass.

[0014] In the above-mentioned composite hydrogel, the bioactive glass is at least one of 45S5, 58S, pH neutral bioactive glass (PSC), and A / W microcrystalline glass.

[0015] In the aforementioned composite hydrogel, according to an embodiment of the present invention, the gel network constituent molecules must possess hydrophilic functional groups, thus enabling sufficient permeability in the oral cavity environment. The gel network constituent molecules in this invention can be selected from various hydrophilic polymers or supramolecular molecules known in the art; preferably, the gel network constituent molecules are at least one of polyvinyl alcohol (PVA), polyacrylamide (PAM), polyacrylic acid (PAA), etc.

[0016] The particle size of the bioactive glass includes all commonly used particle sizes known in the art, such as below 400 mesh (diameter less than 30 μm); 400-200 mesh (diameter: 30-70 μm); 200-120 mesh (diameter: 70-120 μm); 120-80 mesh (diameter: 120-200 μm), etc.

[0017] The present invention also provides a method for preparing the above-mentioned composite hydrogel, which is a repeated freeze-thaw method, a solvent replacement method, a cross-linking method, or a cooling method.

[0018] In the above preparation method, the repeated freeze-thaw method includes the following steps: mixing the bioactive glass, gel network components and water, heating and stirring to fully dissolve the gel network components to obtain a mixed solution; subjecting the mixed solution to repeated freeze-thaw treatments to promote the formation of a gel to obtain the composite hydrogel; The solvent replacement method includes the following steps: mixing the bioactive glass, gel network components and organic solvent, heating and stirring to fully dissolve the gel network components to obtain a mixed system; cooling the mixed system or immersing it in other relatively unsuitable solvents to promote gel formation; immersing the gel in water to perform solvent replacement to completely remove the organic solvent, thereby obtaining the composite hydrogel. The crosslinking method includes the following steps: mixing bioactive glass, gel network components and water, stirring to fully dissolve the gel network components to obtain a mixed solution; adding an initiator and a crosslinking agent to the mixed solution to obtain the composite hydrogel; The cooling method includes the following steps: mixing the bioactive glass, gel network components and water, heating and stirring to fully dissolve the gel network components to obtain a mixed solution; cooling the mixed solution to form a gel to obtain the composite hydrogel.

[0019] In the above preparation methods, in the repeated freeze-thaw method, cross-linking method, and cooling method, the mass ratio of the bioactive glass, gel network constituent molecules, and water is 10:1-50:1-100. In the solvent replacement method, the mass ratio of the bioactive glass, the gel network constituent molecules, and the organic solvent is 10:1-50:1-100. In the repeated freeze-thaw method, the freezing temperature is 0 to -196°C; specifically, it can be -25°C. The thawing temperature is room temperature; Room temperature is well known to those skilled in the art and is generally 15-35°C; The freezing and thawing process is repeated 1-10 times; specifically, it can be repeated 5 times. In the solvent replacement method, the organic solvent is at least one selected from toluene, N-methylpyrrolidone, dimethyl sulfoxide, N,N-dimethylformamide, and N,N-dimethylacetamide; The other relatively unsuitable solvents are anhydrous ethanol and / or tetraethyl orthosilicate; In the crosslinking method, the crosslinking agent is N,N-methylenebisacrylamide and / or divinylbenzene; In the crosslinking method, the initiator is at least one of potassium persulfate, ammonium persulfate, and camphorquinone; In the cooling method, the heating temperature is 40-200℃; the cooling temperature is 30~-80℃.

[0020] The present invention also provides a composite hydrogel for treating dentin hypersensitivity prepared by the above preparation method.

[0021] According to an embodiment of the present invention, the composite hydrogel material has a strong ability to induce mineralization.

[0022] Preferably, the composite hydrogel can detect a significant dentinal tubule mineralization sealing effect within 24 hours.

[0023] According to embodiments of the present invention, the constituent molecules of the gel network have good affinity with water or other organic solvents and can be fully dissolved in water or other organic solvents. The organic solvents of the present invention may be selected from one or more mixtures of various solvents known in the art; preferably, the co-solvent is at least one selected from ethanol, toluene, N-methylpyrrolidone (NMP), dimethyl sulfoxide (DMSO), N,N-dimethylformamide (DMF), N,N-dimethylacetamide (DMA), etc.

[0024] Finally, this invention provides the application of the composite hydrogel in the preparation of drugs for treating dentin hypersensitivity.

[0025] The present invention has the following advantages: (1) The composite hydrogel of the present invention has lower operational sensitivity and is more convenient to use than traditional dentin hypersensitivity treatment drugs; it can stay in the oral environment for a relatively longer time without causing other effects.

[0026] (2) The composite hydrogel of the present invention exhibits a strong ability to induce mineralization while maintaining its high permeability in the oral environment. It can close exposed dentinal tubules in a short time and thus relieve dentin hypersensitivity.

[0027] (3) This invention provides a variety of methods for preparing composite hydrogels. Different methods can be used to prepare composite hydrogels with different properties. They have good plasticity and stability and can be customized according to the specific needs of different patients. They are expected to be developed into new drugs for the treatment of dentin hypersensitivity, showing great commercial application potential and value. Attached Figure Description

[0028] Figure 1 The infrared spectra of gels at different solvent replacement stages in Example 1 are shown.

[0029] Figure 2 The biocompatibility of the PSC / PVA composite hydrogel (PVA:PSC=1:2) prepared in Example 1 is shown in the results of cell live / dead staining tests on day 1 and day 3, respectively.

[0030] Figure 3 The mineralization properties of different composite hydrogels prepared in Example 1 in SBF; wherein, Figure 3 In the figure, a represents the XRD test results of different proportions of PVA and PSC in the composite gel, and b represents the XRD test results of the composite gel (PVA:PSC=1:2) at different mineralization times.

[0031] Figure 4 SEM images of the PSC / PVA composite hydrogel (PVA:PSC=1:2) prepared in Example 1 and the PVA hydrogel prepared in Comparative Example 1 after treatment of the dentin surface. Detailed Implementation

[0032] The present invention will be further described in detail below with reference to specific embodiments. The embodiments given are only for illustrating the present invention and are not intended to limit the scope of the present invention.

[0033] Unless otherwise specified, the experimental methods described in the following examples are conventional methods.

[0034] Unless otherwise specified, the quantitative experiments in the following examples are all repeated three times, and the results are averaged.

[0035] Unless otherwise specified, all materials and reagents used in the following examples are commercially available.

[0036] The PSC bioactive glass used in the following examples was purchased from Huakui Technology Taizhou Co., Ltd., China; 45S5 bioactive glass and 58S bioactive glass were purchased from Schott AG, Germany. The particle size range of the bioactive glass is less than 38 μm.

[0037] Example 1 The composite hydrogel was prepared using a two-step solvent displacement method, and the specific preparation method is as follows: First, 10 g of PSC bioactive glass and 5 g of polyvinyl alcohol (PVA) were added to 35 g of N-methylpyrrolidone (NMP), and stirred at 120 °C for 1 h to ensure complete dissolution of PVA. After vacuum degassing, the mixture was poured into a pre-designed PTFE mold and allowed to cool to room temperature to obtain a PSC / PVA / NMP gel. The resulting PSC / PVA / NMP gel was then immersed in 1000 mL of anhydrous ethanol for 6 h for the first solvent replacement, yielding a PSC / PVA / EtOH gel. Next, the PSC / PVA / EtOH gel was immersed in 1000 mL of deionized water for 6 h for the second solvent replacement, yielding a PSC / PVA composite hydrogel. Finally, the PSC / PVA composite hydrogel was further immersed in 1000 mL of deionized water, with the water replaced every 6 h, repeating this process three times to ensure complete replacement of residual NMP and EtOH.

[0038] The obtained PSC / PVA composite hydrogel was tested for the presence of residual organic solvents using Fourier transform infrared spectroscopy (FTIR). The test conditions were: wavenumber range 4000-400 cm⁻¹. -1 The number of scans was 32, and the resolution was 2 cm. -1 The result is as follows Figure 1 As shown, by Figure 1 It can be seen that after the initial replacement with EtOH, the original PSC / PVA / NMP gel at ~1670 cm⁻¹... -1 The disappearance of the stretching vibrations at C=O in NMP at this point indicates that the NMP in the gel has been completely replaced by EtOH. After the second solvent replacement, the NMP in the original PSC / PVA / EtOH gel at ~2970, 2868, and 1045 cm⁻¹... -1The disappearance of the stretching vibrations attributable to -CH3 and CO in EtOH indicates that the EtOH in the gel was replaced by H2O during this process, laying a good physicochemical foundation for its further applications. In other words, the infrared spectroscopy results of this composite hydrogel show that no characteristic peaks of the corresponding organic solvents were detected in different solvent replacement stages, indicating that the organic solvents can be completely removed from the gel interior during these stages.

[0039] The biocompatibility of the obtained PSC / PVA composite hydrogel was verified using a live / dead staining assay. 1 g of PSC / PVA composite hydrogel sample and 0.2 g of PSC powder were added to 10 mL of DMEM medium and incubated on a rotating shaker at 37°C for 24 h. The supernatant was then collected and filtered through a 0.22 μm filter to obtain extracts of different hydrogel samples for subsequent cell experiments. Results are shown below. Figure 2 ,Depend on Figure 2 As can be seen, live / dead staining of dental pulp cells (DPSCs) on days 1 and 3 showed no significant difference between the PSC group and the PSC / PVA composite hydrogel group, further indicating that the composite hydrogel prepared in this embodiment has good biocompatibility. Therefore, although NMP and EtOH are involved in the preparation of the gel, they can be completely removed at different stages of solvent replacement, and their potential cytotoxicity is negligible.

[0040] The mineralization capacity of the PSC / PVA composite hydrogel was tested by immersing it in SBF (simulated body fluid) for 24 h using an X-ray diffractometer with a scanning range of 10°-70° and a scanning rate of 4° / min.

[0041] See results Figure 3 ,Depend on Figure 3 It can be seen that the composite hydrogel exhibits different mineralization characteristics in SBF as the ratio of PVA to PSC changes. When the PVA:PSC ratio inside the composite hydrogel is 1:2, a distinct diffraction peak belonging to hydroxyapatite can be detected at 31.7° after soaking in SBF for 24 h. X-ray diffraction results show obvious mineralization characteristic peaks.

[0042] PSC / PVA composite hydrogel samples were adhered to the dentin surface and secured with rubber bands. The samples were then immersed in artificial saliva (AS) at 37°C for 24 hours. Dentin sections were dried in a 60°C oven for 24 hours and then observed under a SEM. Obvious mineral adhesion was observed on the surface of the dentin sections under SEM, indicating that this composite hydrogel has good potential for treating dentin hypersensitivity. Results are shown below. Figure 4 ,Depend on Figure 4It is evident that, since PVA hydrogel alone does not possess any mineralization-inducing effect, the dentin surface treated with it shows no significant difference compared to its initial state, and SEM clearly shows that almost all dentinal tubules are in an open state (left image). However, the dentin surface treated with PSC / PVA composite hydrogel shows obvious newly formed minerals covering the dentinal tubules (right image), thus demonstrating promising application prospects in the treatment of dentin hypersensitivity.

[0043] Example 2 The composite hydrogel was prepared using a two-step solvent displacement method, as detailed below: First, 10 g of 45S5 bioactive glass and 5 g of PVA were added to 35 g of NMP and stirred at 120 °C for 1 h to ensure complete dissolution of PVA. After vacuum degassing, the mixture was poured into a pre-designed PTFE mold and allowed to cool to room temperature to obtain a 45S5 / PVA / NMP gel. The resulting 45S5 / PVA / NMP gel was then immersed in 1000 mL of anhydrous ethanol for 6 h for the first solvent replacement, yielding a 45S5 / PVA / EtOH gel. Next, the 45S5 / PVA / EtOH gel was immersed in 1000 mL of deionized water for 6 h for the second solvent replacement, yielding a 45S5 / PVA composite hydrogel. Finally, the 45S5 / PVA composite hydrogel was further immersed in 1000 mL of deionized water, with the water replaced every 6 h, repeating this process three times to ensure complete replacement of residual NMP and EtOH.

[0044] The obtained 45S5 / PVA composite hydrogel was characterized using the same testing methods as in Example 1. Infrared spectroscopy results showed no characteristic peaks of the corresponding organic solvents detected at different solvent replacement stages, indicating that the organic solvents could be completely removed from the gel interior at these stages. Cell experiments further demonstrated that the composite hydrogel exhibits good cell compatibility, and the potential cytotoxicity issues caused by residual organic solvents are negligible. X-ray diffraction results showed obvious mineralization characteristic peaks, and SEM images of the dentin surface also showed significant mineral adhesion, indicating that the composite hydrogel has good potential for treating dentin hypersensitivity.

[0045] Example 3 The composite hydrogel was prepared using a two-step solvent displacement method, as detailed below: First, 10 g of 58S bioactive glass and 5 g of PVA were added to 35 g of NMP and stirred at 120 °C for 1 h to ensure complete dissolution of PVA. After vacuum degassing, the mixture was poured into a pre-designed PTFE mold and allowed to cool to room temperature to obtain a 58S / PVA / NMP gel. The resulting 58S / PVA / NMP gel was then immersed in 1000 mL of anhydrous ethanol for 6 h for the first solvent replacement, yielding a 58S / PVA / EtOH gel. Next, the 58S / PVA / EtOH gel was immersed in 1000 mL of deionized water for 6 h for the second solvent replacement to obtain a 58S / PVA composite hydrogel. Finally, the obtained 58S / PVA composite hydrogel was further immersed in 1000 mL of deionized water, with the water replaced every 6 h, and this process was repeated three times to ensure complete replacement of residual NMP and EtOH.

[0046] The obtained 45S5 / PVA composite hydrogel was characterized using the same testing methods as in Example 1. Infrared spectroscopy results showed no characteristic peaks of the corresponding organic solvents detected at different solvent replacement stages, indicating that the organic solvents could be completely removed from the gel interior at these stages. Cell experiments further demonstrated that the composite hydrogel exhibits good cell compatibility, and the potential cytotoxicity issues caused by residual organic solvents are negligible. X-ray diffraction results showed obvious mineralization characteristic peaks, and SEM images of the dentin surface also showed significant mineral adhesion, indicating that the composite hydrogel has good potential for treating dentin hypersensitivity.

[0047] Example 4 The composite hydrogel was prepared using a repeated freeze-thaw method, the specific method of which is as follows: First, 10 g of PSC bioactive glass and 5 g of PVA were added to 35 g of water and stirred at 90°C for 1 h to ensure complete dissolution of PVA. After vacuum degassing, the resulting aqueous solution was poured into a pre-designed PTFE mold and placed at -25°C for 12 h to ensure complete freezing, followed by thawing at room temperature for 6 h. This process was repeated five times to obtain the PSC / PVA composite hydrogel.

[0048] The biocompatibility, mineralization capacity, and SEM images of the PSC / PVA composite hydrogel after attachment to the dentin surface were tested using the same methods as in the previous examples. Cellular experiments showed that the composite hydrogel exhibited good cell compatibility, and the potential cytotoxicity issues caused by residual organic solvents were negligible. X-ray diffraction results showed obvious mineralization characteristic peaks, and significant mineral adhesion was also observed on the dentin surface under SEM, indicating that the composite hydrogel has good potential for treating dentin hypersensitivity.

[0049] Example 5 The composite hydrogel was prepared using a cross-linking method, the specific method of which is as follows: First, 10 g of PSC bioactive glass and 5 g of acrylamide were added to 35 g of water and stirred at room temperature for 3 min to ensure uniform mixing. Then, 0.05 g of potassium persulfate and 0.05 g of N,N-methylenebisacrylamide were added and allowed to dissolve completely. After vacuum degassing, the resulting aqueous solution was poured into a pre-designed PTFE mold and heated to 70°C to obtain a composite hydrogel.

[0050] The biocompatibility, mineralization capacity, and SEM images of the PSC / PVA composite hydrogel after attachment to the dentin surface were tested using the same methods as in the previous examples. Cellular experiments showed that the composite hydrogel exhibited good cell compatibility, and the potential cytotoxicity issues caused by residual organic solvents were negligible. X-ray diffraction results showed obvious mineralization characteristic peaks, and significant mineral adhesion was also observed on the dentin surface under SEM, indicating that the composite hydrogel has good potential for treating dentin hypersensitivity.

[0051] Comparative Example 1 The preparation method of PVA hydrogel is as follows: PVA hydrogels were prepared using a two-step solvent displacement method: First, 5 g of PVA was added to 45 g of NMP, and the mixture was stirred at 120 °C for 1 h to ensure complete dissolution of PVA. After centrifugation and degassing, the NMP solution containing PVA was poured into a pre-designed PTFE mold and allowed to cool to room temperature to form a PVA / NMP gel. The resulting PVA / NMP gel was then immersed in 1000 mL of anhydrous ethanol for 6 h for the first solvent displacement, yielding a PVA / EtOH gel. Next, the PVA / EtOH gel was immersed in 1000 mL of deionized water for 6 h for the second solvent displacement to obtain a PVA hydrogel. Finally, the PVA hydrogel was further immersed in 1000 mL of deionized water, with the water replaced every 6 h, and this process was repeated three times to ensure complete replacement of residual NMP and EtOH, thus obtaining the PVA hydrogel.

Claims

1. A composite hydrogel, characterized in that: The composite hydrogel comprises bioactive glass, gel network constituent molecules, and water.

2. The composite hydrogel according to claim 1, characterized in that: The contents of each component by weight percentage are as follows: bioactive glass greater than 0 and less than or equal to 99%, gel network constituent molecules greater than 0 and less than or equal to 99%, and water greater than 0 and less than or equal to 99%.

3. The composite hydrogel according to claim 1 or 2, characterized in that: The bioactive glass is a phosphosilicate bioactive glass.

4. The composite hydrogel according to claim 3, characterized in that: The bioactive glass is at least one of 45S5, 58S, pH neutral bioactive glass, and A / W microcrystalline glass.

5. The composite hydrogel according to any one of claims 1-4, characterized in that: The gel network is composed of hydrophilic polymers or supramolecular molecules. Preferably, the gel network components are at least one of polyvinyl alcohol, polyacrylamide, and polyacrylic acid.

6. A method for preparing the composite hydrogel according to any one of claims 1-5, characterized in that: The preparation method is a repeated freeze-thaw method, a solvent replacement method, a cross-linking method, or a cooling method.

7. The preparation method according to claim 6, characterized in that: The repeated freeze-thaw method includes the following steps: mixing the bioactive glass, gel network components and water, heating and stirring to fully dissolve the gel network components to obtain a mixed solution; subjecting the mixed solution to repeated freeze-thaw treatments to promote gel formation to obtain the composite hydrogel. The solvent replacement method includes the following steps: mixing the bioactive glass, gel network components and organic solvent, heating and stirring to fully dissolve the gel network components to obtain a mixed system; cooling the mixed system or immersing it in other relatively unsuitable solvents to promote gel formation; immersing the gel in water to perform solvent replacement to completely remove the organic solvent, thereby obtaining the composite hydrogel. The crosslinking method includes the following steps: mixing bioactive glass, gel network components and water, stirring to fully dissolve the gel network components to obtain a mixed solution; adding an initiator and a crosslinking agent to the mixed solution to obtain the composite hydrogel; The cooling method includes the following steps: mixing the bioactive glass, gel network components and water, heating and stirring to fully dissolve the gel network components to obtain a mixed solution; cooling the mixed solution to form a gel to obtain the composite hydrogel.

8. The preparation method according to claim 7, characterized in that: In the repeated freeze-thaw method, cross-linking method, and cooling method, the mass ratio of the bioactive glass, gel network components, and water is 10:1-50:1-100. In the solvent replacement method, the mass ratio of the bioactive glass, the gel network constituent molecules, and the organic solvent is 10:1-50:1-100. In the repeated freeze-thaw method, the freezing temperature is 0 to -196°C; The freezing and thawing process is repeated 1-10 times. In the solvent replacement method, the organic solvent is at least one selected from toluene, N-methylpyrrolidone, dimethyl sulfoxide, N,N-dimethylformamide, and N,N-dimethylacetamide; The other relatively unsuitable solvents are anhydrous ethanol and / or tetraethyl orthosilicate; In the crosslinking method, the crosslinking agent is N,N-methylenebisacrylamide and / or divinylbenzene; In the crosslinking method, the initiator is at least one of potassium persulfate, ammonium persulfate, and camphorquinone; In the cooling method, the cooling temperature is 30~-80℃.

9. The use of the composite hydrogel according to any one of claims 1-5 in the preparation of a drug for treating dentin hypersensitivity.

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