Injectable porous selenium-loaded antibacterial bone cement material and preparation method thereof

Abstract

The invention discloses an injectable porous selenium-loaded antibacterial bone cement material and a preparation method thereof, and relates to the field of biomedical materials. The bone cement material is prepared from solid-phase powder and curing liquid, the solid-phase powder comprises beta-calcium phosphate, monocalcium phosphate monohydrate, selenocystine, bioactive glass, calcium carbonate, magnesium powder, stearic acid and carbon powder; the curing liquid is a sodium hyaluronate solution; the preparation method comprises the following steps: grinding magnesium powder and stearic acid, adding carbon powder, and continuously grinding to obtain composite pore-forming agent powder; the preparation method comprises the following steps: grinding and mixing beta-calcium phosphate, monocalcium phosphate monohydrate and selenocystine to obtain antibacterial matrix powder; grinding and mixing the composite pore-forming agent powder, bioactive glass and calcium carbonate to obtain auxiliary functional powder; and mixing and grinding the two powders, adding a sodium hyaluronate curing liquid, uniformly mixing, and curing to obtain the product. The material obtained by the invention has excellent broad-spectrum antibacterial ability, can construct an alkalescent microenvironment to synergistically promote bone repair, and has a good clinical application prospect.

Description

Technical Field

[0001] This invention relates to the field of biomedical materials, and more particularly to an injectable porous selenium-loaded antibacterial bone cement material and its preparation method. Background Technology

[0002] In orthopedic surgery, especially in cases involving severe bone defects, bone grafts are often implanted to replace missing bone tissue, provide structural support, and promote bone healing. However, infection during bone grafting surgery has become an extremely challenging global problem. Bone grafting is an open procedure, making it easy for bacteria to invade the body. Despite strict aseptic techniques and prophylactic antibiotics, the infection rate of bone grafting surgery is significantly higher than that of routine orthopedic surgery. This is because after the bone graft material enters the body, its surface is quickly covered by host proteins, creating a breeding ground for bacteria. Once colonized, bacteria can easily form highly drug-resistant biofilms, leading to deep infections, especially in patients with open fractures or underlying conditions such as diabetes. If a deep infection occurs, bacteria within the biofilm can periodically release airborne bacteria, causing recurrent and spreading infections. Infection can damage newly formed bone tissue, leading to nonunion, enlarged bone defects, and ultimately, complete surgical failure. This infection is also prone to becoming chronic and difficult to cure, developing into intractable chronic osteomyelitis, which is extremely difficult to treat and can even be life-threatening in severe cases, ultimately necessitating amputation. Patients often need to undergo multiple surgeries, long-term antibiotic treatment (which may involve intravenous infusions for weeks to months), a lengthy recovery process, and may even lose their ability to work, placing a heavy burden on individuals, families, and society.

[0003] Given that bone graft materials are directly implanted into bone defect areas, developing bone graft materials with their own antibacterial properties has become an important research direction for preventing bone graft infections and treating infected bone defects. Currently, bone graft materials with anti-infection capabilities are mainly divided into the following categories: First, artificial bone graft materials loaded with high doses of antibiotics, achieving antibacterial effects by releasing high concentrations of antibiotics at the infection site. This method is effective and widely used clinically, but the side effects of long-term antibiotic use, such as liver and kidney toxicity, allergic reactions, intestinal flora imbalance, and the development of drug-resistant strains, cannot be ignored. With the widespread emergence of multidrug-resistant bacteria such as methicillin-resistant Staphylococcus aureus (MRSA), vancomycin-resistant enterococci (VRE), and carbapenem-resistant enterobacteriaceae (CRE), the number of effective antibiotics available is decreasing, and the difficulty of treatment is constantly increasing. Second, introducing heavy metal ions (such as copper, silver, cobalt, zinc, iron, etc.) into bone graft materials, utilizing their charge properties or oxidizing effects to achieve antibacterial effects. While these methods have antibacterial effects, the cumulative toxicity of heavy metals in the body is a concern, and the processing technology is complex; ions released into the environment may also cause ecotoxicity. Thirdly, loading photosensitizers onto bone graft materials and applying laser irradiation utilizes photothermal or photodynamic effects to achieve antibacterial effects. Although this method has lower toxicity, its clinical application is still some time away due to the limited light penetration of bone located deep within the body.

[0004] Selenium, an essential trace element for the human body, plays multiple roles in maintaining health, including antioxidation, immune enhancement, endocrine regulation, cardiovascular protection, and adjuvant anti-cancer effects. Selenium is also crucial for bones; selenium deficiency can lead to Kashin-Beck disease, while selenoproteins help maintain the balance between bone formation and resorption, protect osteocyte function, and thus support bone density and strength. Given selenium's osteogenesis-promoting properties, its application in orthopedics, particularly in the development of antibacterial selenium-loaded bone grafts, is receiving increasing attention. Currently, antibacterial selenium-loaded bone grafts often utilize elemental selenium (zero valent selenium) as a coating on the material surface, which can be enhanced with photothermal methods to increase antibacterial activity. However, while zero valent selenium typically exhibits good inhibitory effects against Staphylococcus aureus, its antibacterial effect against Gram-negative bacteria is weaker. Furthermore, although selenium is an essential element, excessive intake is toxic, and inorganic selenium is generally significantly more toxic than its organic form. Summary of the Invention

[0005] The purpose of this invention is to provide an injectable porous selenium-loaded antibacterial bone cement material. The material uses selenocysteine ​​as an organic selenium antibacterial agent and a porous bioceramic containing bioactive glass and permealuminate as a matrix. It has a broad-spectrum antibacterial effect, exhibiting strong antibacterial ability against both Gram-negative and Gram-positive bacteria, and is non-cytotoxic. The material has a moderate curing time, is injectable and resistant to disintegration, and can conformally fill complex bone defects, making it suitable for minimally invasive procedures.

[0006] Another object of the present invention is to provide a method for preparing the above-mentioned injectable porous selenium-loaded antibacterial bone cement material.

[0007] Another object of the present invention is to provide the application of the above-mentioned injectable porous selenium-loaded antibacterial bone cement material.

[0008] To achieve the above objectives, the technical solution adopted by the present invention is as follows: In a first aspect, the present invention provides an injectable porous selenium-loaded antibacterial bone cement material, comprising a solid powder and a curing liquid; the solid powder comprises β-calcium phosphate, calcium dihydrogen phosphate monohydrate, selenocysteine, bioactive glass, calcium carbonate, and a composite pore-forming agent, wherein the composite pore-forming agent is composed of magnesium powder, stearic acid, and carbon powder; and the curing liquid is a sodium hyaluronate solution.

[0009] As a preferred embodiment, the solid powder contains the following components in parts by mass: 16-20 parts of β-calcium phosphate, 13 parts of calcium dihydrogen phosphate monohydrate, 0.006-0.03 parts of selenocystine, 1.1 parts of bioactive glass, 0.8 parts of calcium carbonate, and 0.5 parts of composite pore-forming agent.

[0010] As a preferred embodiment, the mass ratio of magnesium powder, stearic acid and carbon powder in the composite pore-forming agent is 20:1:80.

[0011] As a preferred embodiment, the concentration of the sodium hyaluronate solution is 1% to 2%.

[0012] Secondly, the present invention provides a method for preparing the above-described injectable porous selenium-loaded antibacterial bone cement material, comprising the following steps: S1. Magnesium powder sieved through 300 mesh is mixed and ground with stearic acid at a mass ratio of 20:1 to obtain magnesium powder-stearic acid mixed powder. S2, add carbon powder with a mass of 4 times that of magnesium powder to the magnesium powder-stearic acid mixed powder obtained in step S1, and continue grinding to obtain composite pore-forming agent powder; S3. Weigh out sodium hyaluronate solid powder, add triple-distilled water and stir to prepare a uniform solution with a mass fraction of 1% to 2%, which will be used as a curing liquid for later use. S4, β-calcium phosphate, calcium dihydrogen phosphate monohydrate and selenocysteine ​​are mixed and ground to obtain mixed powder A; S5, the composite pore-forming agent powder obtained in step S2 is mixed and ground with bioactive glass and calcium carbonate to obtain mixed powder B; S6. Mix and grind the mixed powder A obtained in step S4 with the mixed powder B obtained in step S5 to obtain a composite solid powder. S7. Add the curing liquid prepared in step S3 to the composite solid powder obtained in step S6 at a solid-liquid ratio of 1.6 g / mL, mix evenly to obtain bone cement paste, which is then cured.

[0013] As a preferred embodiment, the grinding time in steps S1 and S2 is 2 hours, and the stirring time in step S3 is 2 hours.

[0014] As a preferred embodiment, in step S4, the β-calcium phosphate is 16-20 parts, the calcium dihydrogen phosphate monohydrate is 13 parts, and the selenocysteine ​​is 0.006-0.03 parts, and the mixture is ground until homogeneous.

[0015] As a preferred embodiment, in step S5, the composite pore-forming agent powder is 0.5 parts, the bioactive glass is 1.1 parts, and the calcium carbonate is 0.8 parts.

[0016] Thirdly, the present invention provides an application of the injectable porous selenium-loaded antibacterial bone cement material as described above in the preparation of bone defect repair materials.

[0017] According to the above technical solution, the beneficial effects of the present invention are: 1. Organic selenium is used as an antibacterial agent, and long-lasting broad-spectrum antibacterial effect is achieved through matrix incorporation.

[0018] Existing selenium-loaded bone graft materials mostly employ nano-zero-valent selenium coatings. Inorganic selenium has a low toxicity threshold, which, while imparting antibacterial properties, easily compromises the material's biocompatibility; furthermore, coating methods suffer from problems such as easy detachment and uneven distribution, leading to unsustainable antibacterial performance. This invention uses naturally derived organic selenium—selenocysteine—as an antibacterial agent, uniformly incorporating it into the material matrix. This organic selenium exhibits excellent inhibitory capabilities against both Gram-negative and Gram-positive bacteria, overcoming the limitation of traditional selenium particles being insensitive to Gram-negative bacteria. Selenocysteine ​​more closely approximates the physiologically utilized form of selenium, maintaining excellent biocompatibility while achieving high antibacterial activity. Furthermore, selenocysteine ​​possesses antioxidant and immune-regulating biological functions, further synergistically enhancing the material's biocompatibility. Incorporating it into the matrix rather than as a surface coating allows for the continuous and controlled release of selenium, achieving a long-term stable antibacterial effect.

[0019] 2. Construct a slightly alkaline permeable calcium phosphate scaffold system to synergistically optimize the bone repair microenvironment.

[0020] This invention uses calcareous phosphate rock as a ceramic matrix. While calcareous phosphate rock possesses excellent degradation properties, it releases protons upon dissolution in body fluids, creating an acidic microenvironment that is detrimental to the growth and function of basophilic osteoblasts. This invention addresses this by synergistically regulating the microenvironment through multiple factors: introducing magnesium powder as a pore-forming agent, which consumes protons and releases OH- during the reaction. - Adding an appropriate amount of bioactive glass contributes OH through ion exchange. -A slightly alkaline sodium hyaluronate solution is used as the curing liquid. Upon contact with body fluids, the material forms a slightly alkaline microenvironment conducive to osteoblast growth. This not only solves the acidity problem of the calcium phosphate itself but also significantly promotes the adhesion, proliferation, and differentiation of basophilic osteoblasts. While effectively controlling infection, it ensures and accelerates the bone repair process, providing a safe, stable, and functionally synergistic microenvironment for bone defect repair. The slightly alkaline nature is also mild, and combined with the protection of hyaluronic acid and the hydrogen reduction environment generated by the magnesium powder reaction, it is beneficial for the loading and performance stability of selenocysteine.

[0021] 3. Innovatively construct a composite pore-forming system to achieve a porous structure that does not rely on acidic spacers.

[0022] Due to their material properties, bioceramics often struggle to achieve high porosity structures during injection molding. Existing technologies often employ rapidly degradable polymeric hollow microspheres such as polylactic acid (PLA) as site-forming agents to create pores. However, for the DCPD system, which degrades to an acidic state, the addition of acidic PLA microspheres further exacerbates local acidification, severely hindering osteogenic processes. This invention, through precise chemical proportioning, utilizes biocompatible stearic acid and carbon powder to co-encapsulate magnesium powder, constructing a composite pore-forming agent system that successfully achieves effective control over the pore-forming reaction rate and pore structure. This method achieves efficient pore formation without relying on acidic hollow microspheres for site formation, fundamentally avoiding the problem of increased system acidity due to the addition of acidic substances, thus creating a more favorable microenvironment for osteoblasts. Attached Figure Description

[0023] Figure 1 This is a graph showing the curing time results of the material of the present invention; Figure 2 This is a graph showing the injectability performance results of the material of the present invention; Figure 3 Photographs of the porous structure of the material of this invention; Figure 4 The diagram shows the anti-collapse performance of the material of this invention. Figure 5 This is a graph showing the pH change of the material of the present invention in the soaking liquid; Figure 6 This is a photograph of the plate-shaped antibacterial effect of the material of the present invention against Escherichia coli. Figure 7 This is a statistical result diagram showing the diameter of the inhibition zone of the material of the present invention against Escherichia coli; Figure 8 This is a photograph of the plate-mounted antibacterial activity of the material of the present invention against Staphylococcus aureus. Figure 9 This is a statistical result diagram showing the diameter of the inhibition zone against Staphylococcus aureus by the material of this invention; Figure 10 This is a graph showing the statistical results of the cytotoxicity of the materials of this invention; Figure 11 The figure shows the cytotoxicity test results of the material of this invention. Detailed Implementation

[0024] The present invention will be further described below with reference to embodiments. It should be understood that the embodiments are for illustrative purposes only and are not intended to limit the scope of protection of the present invention.

[0025] Example 1 This embodiment provides a method for preparing an injectable porous bone repair material with excellent antibacterial properties, including the following steps: Step S1: Take 1 g of magnesium powder sieved through 300 mesh and mix it with 0.05 g of stearic acid. Grind for 2 hours to make it evenly mixed and set aside.

[0026] Step S2: Add 4 g of carbon powder to the magnesium powder-stearic acid mixed powder obtained in step S1, and continue grinding for 2 hours to make it evenly mixed and ready for use.

[0027] Step S3: Weigh out sodium hyaluronate solid powder, add triple-distilled water, stir for 2 hours, and prepare a homogeneous solution with a mass fraction of 2% for use as a curing liquid.

[0028] Step S4: Weigh 0.20 g of β-calcium phosphate solid powder, 0.130 g of calcium dihydrogen phosphate monohydrate, and 0.00006 g of selenocysteine ​​solid powder, place them in a mortar and grind them evenly to obtain mixed powder A1.

[0029] Step S5: Weigh 0.005 g of the composite pore-forming agent powder, 0.011 g of the bioactive glass, and 0.008 g of the calcium carbonate solid powder obtained in step S2, place them in a mortar and grind them evenly to obtain mixed powder B1.

[0030] Step S6: Place the mixed powder A1 obtained in step S4 and the mixed powder B1 obtained in step S5 into a mortar and grind them evenly to obtain a composite solid powder.

[0031] Step S7: Add the curing liquid prepared in step S3 to the composite solid powder obtained in step S6 at a solid-liquid ratio of 1.6 g / mL, mix evenly, and obtain bone cement paste; after the paste is cured, the composite material is obtained.

[0032] Example 2 Step S1: Take 1 g of magnesium powder sieved through 300 mesh and mix it with 0.05 g of stearic acid. Grind for 2 hours to make it evenly mixed and set aside.

[0033] Step S2: Add 4 g of carbon powder to the magnesium powder-stearic acid mixed powder obtained in step S1, and continue grinding for 2 hours to make it evenly mixed and ready for use.

[0034] Step S3: Weigh out sodium hyaluronate solid powder, add triple-distilled water, stir for 2 hours, and prepare a uniform solution with a mass fraction of 1.5% for use as a curing liquid.

[0035] Step S4: Weigh 0.18 g of β-calcium phosphate solid powder, 0.130 g of calcium dihydrogen phosphate monohydrate, and 0.00015 g of selenocysteine ​​solid powder, place them in a mortar and grind them evenly to obtain mixed powder A2.

[0036] Step S5: Weigh 0.005 g of the composite pore-forming agent powder, 0.011 g of the bioactive glass, and 0.008 g of the calcium carbonate solid powder obtained in step S2, place them in a mortar and grind them evenly to obtain mixed powder B2.

[0037] Step S6: Place the mixed powder A2 obtained in step S4 and the mixed powder B2 obtained in step S5 into a mortar and grind them evenly to obtain a composite solid powder.

[0038] Step S7: Add the curing liquid prepared in step S3 to the composite solid powder obtained in step S6 at a solid-liquid ratio of 1.6 g / mL, mix evenly, and obtain bone cement paste; after the paste is cured, the composite material is obtained.

[0039] Example 3 This embodiment provides a method for preparing an injectable porous bone repair material with excellent antibacterial properties, including the following steps: Step S1: Take 1 g of magnesium powder sieved through 300 mesh and mix it with 0.05 g of stearic acid. Grind for 2 hours to make it evenly mixed and set aside.

[0040] Step S2: Add 4 g of carbon powder to the magnesium powder-stearic acid mixed powder obtained in step S1, and continue grinding for 2 hours to make it evenly mixed and ready for use.

[0041] Step S3: Weigh out sodium hyaluronate solid powder, add triple-distilled water, stir for 2 hours, and prepare a uniform solution with a mass fraction of 1% for use as a curing liquid.

[0042] Step S4: Weigh 0.16 g of β-calcium phosphate solid powder, 0.130 g of calcium dihydrogen phosphate monohydrate, and 0.0003 g of selenocystine solid powder, place them in a mortar and grind them evenly to obtain mixed powder A3.

[0043] Step S5: Weigh 0.005 g of the composite pore-forming agent powder, 0.011 g of the bioactive glass, and 0.008 g of the calcium carbonate solid powder obtained in step S2, place them in a mortar and grind them evenly to obtain mixed powder B3.

[0044] Step S6: Place the mixed powder A3 obtained in step S4 and the mixed powder B3 obtained in step S5 into a mortar and grind them evenly to obtain a composite solid powder.

[0045] Step S7: Add the curing liquid prepared in step S3 to the composite solid powder obtained in step S6 at a solid-liquid ratio of 1.6 g / mL, mix evenly, and obtain bone cement paste; after the paste is cured, the composite material is obtained.

[0046] The injectable porous selenium-loaded antibacterial bone cement materials prepared in Examples 1, 2, and 3 above were subjected to the following performance tests and characterizations: (1) Curing time test After thoroughly mixing the material paste, use a 1 mm diameter steel needle to vertically penetrate the material surface with a force of 20 N every minute, observing whether a needle mark is left. Record the curing time when no mark is left. Figure 1 As shown, the curing times of Examples 1, 2 and 3 are approximately 18 minutes, 16 minutes and 15 minutes, respectively, indicating that the material has a moderate curing time that meets the needs of clinical operation.

[0047] (2) Injectability test Using a constant force of 20 N, push the syringe plunger to squeeze the well-mixed paste material out of a 2.5 mL syringe, and observe whether the material can be injected continuously and completely. Figure 2 As shown, the ointments of Examples 1, 2 and 3 can all be extruded smoothly without clogging or breakage, indicating that the materials have good injectability and are suitable for minimally invasive procedures.

[0048] (3) Observation of porous structure After the injected paste material solidifies, it is broken open, and its cross-sectional morphology is photographed using a digital camera to observe the porous structure of the material. For example... Figure 3 As shown, Examples 1, 2 and 3 all exhibit obvious porous structures; the control group is a material without added bioactive glass, magnesium powder, stearic acid and carbon powder, with other components and preparation methods the same as in Example 1, and its pore structure is significantly less.

[0049] (4) Anti-collapse performance test Using a constant force of 20 N, push the syringe plunger to inject the well-mixed paste material from a 2.5 mL syringe into water, and observe whether the material disintegrates at different time points. Figure 4As shown, the materials in Examples 1, 2 and 3 retained their initial shape after being injected into water for 1 hour, without obvious collapse or dissolution, indicating that the materials have good anti-collapse properties.

[0050] (5) Immersion pH change test The material was prepared into cylindrical blocks with a diameter of 9 mm and a thickness of 3 mm, and immersed in PBS solution at a solid-liquid ratio of 1 g / 20 mL. The pH value of the solution was measured at different time points. The immersion solution was not changed throughout the process. Pure permealumina material was used as a control. Figure 5 As shown, the pH value of the soaking solution in Examples 1, 2 and 3 was maintained in the weakly alkaline range, while the pH value of the pure calcium phosphate group was acidic, indicating that this material can effectively regulate the local microenvironment and form weakly alkaline conditions that are conducive to osteogenic formation.

[0051] (6) Antibacterial performance test Plate inhibition tests were conducted according to GB / T 38483-2020 standard. Sterilized samples were placed on agar plates coated with *Escherichia coli* and *Staphylococcus aureus*, and the plates were inverted and incubated at 37°C for 18 hours. The diameter of the inhibition zone was measured using calipers and photographed. Each test was repeated three times. Figures 6 to 9 As shown, the inhibition zone diameters of Examples 1, 2, and 3 against Escherichia coli were 2.5 cm, 3.6 cm, and 3.7 cm, respectively; and the inhibition zone diameters against Staphylococcus aureus were 1.2 cm, 2.0 cm, and 2.2 cm, respectively, indicating that the material has excellent broad-spectrum antibacterial ability against both Gram-negative and Gram-positive bacteria.

[0052] (7) Cytotoxicity test Following GB / T 16886.12, sterilized materials were extracted in culture medium at 37°C for 24 hours (solid-liquid ratio 1 g / 5 mL). The supernatant was filtered through a 0.22 μm filter, and the resulting extract was mixed with 10% FBS as cell culture medium. Cytotoxicity assays were performed using the MTT assay according to GB / T 16886.5, with L929 cells used as the experimental cells. Figure 10 and Figure 11 As shown, the relative cell proliferation rates of Examples 1, 2 and 3 were 109.77%, 104.45% and 94.16%, respectively, all of which were higher than or close to the negative control group, indicating that none of the materials had obvious cytotoxicity and good biocompatibility.

[0053] The above test results show that the injectable porous selenium-loaded antibacterial bone cement material prepared by the present invention has a suitable curing time, good injectability, stable anti-collapse properties, controllable porous structure, weakly alkaline microenvironment regulation ability, excellent broad-spectrum antibacterial properties, and good cell compatibility, making it suitable for filling and repairing complex bone defects.

[0054] The types and amounts of reagents involved in this invention are not limited to the above embodiments, and can be adapted according to application requirements; the solvent used to mix solid powders can also be replaced with other organic substances that can effectively mix β-TCP and MCPM.

[0055] It should be noted that the above embodiments are only used to illustrate the present invention, but the present invention is not limited to the above embodiments. Any simple modifications, equivalent changes and alterations made to the above embodiments based on the technical essence of the present invention shall fall within the protection scope of the present invention.

Claims

1. An injectable porous selenium-loaded antibacterial bone cement material, characterized in that: It includes a solid powder and a curing liquid; the solid powder includes β-calcium phosphate, calcium dihydrogen phosphate monohydrate, selenocysteine, bioactive glass, calcium carbonate, and a composite pore-forming agent, wherein the composite pore-forming agent is composed of magnesium powder, stearic acid, and carbon powder; the curing liquid is a sodium hyaluronate solution.

2. The injectable porous selenium-loaded antibacterial bone cement material according to claim 1, characterized in that: The solid powder contains the following components in parts by mass: 16-20 parts of β-calcium phosphate, 13 parts of calcium dihydrogen phosphate monohydrate, 0.006-0.03 parts of selenocystine, 1.1 parts of bioactive glass, 0.8 parts of calcium carbonate, and 0.5 parts of composite pore-forming agent.

3. The injectable porous selenium-loaded antibacterial bone cement material according to claim 1, characterized in that: In the composite pore-forming agent, the mass ratio of magnesium powder, stearic acid and carbon powder is 20:1:

80.

4. The injectable porous selenium-loaded antibacterial bone cement material according to claim 1, characterized in that: The concentration of the sodium hyaluronate solution is 1% to 2%.

5. A method for preparing the injectable porous selenium-loaded antibacterial bone cement material as described in any one of claims 1-4, characterized in that: Includes the following steps: S1. Magnesium powder sieved through 300 mesh is mixed and ground with stearic acid at a mass ratio of 20:1 to obtain magnesium powder-stearic acid mixed powder. S2, add carbon powder with a mass of 4 times that of magnesium powder to the magnesium powder-stearic acid mixed powder obtained in step S1, and continue grinding to obtain composite pore-forming agent powder; S3. Weigh out sodium hyaluronate solid powder, add triple-distilled water and stir to prepare a uniform solution with a mass fraction of 1% to 2%, which will be used as a curing liquid for later use. S4, β-calcium phosphate, calcium dihydrogen phosphate monohydrate and selenocysteine ​​are mixed and ground to obtain mixed powder A; S5, the composite pore-forming agent powder obtained in step S2 is mixed and ground with bioactive glass and calcium carbonate to obtain mixed powder B; S6. Mix and grind the mixed powder A obtained in step S4 with the mixed powder B obtained in step S5 to obtain a composite solid powder. S7. Add the curing liquid prepared in step S3 to the composite solid powder obtained in step S6 at a solid-liquid ratio of 1.6 g / mL, mix evenly to obtain bone cement paste, which is then cured.

6. The preparation method according to claim 5, characterized in that: In steps S1 and S2, the grinding time is 2 hours, and in step S3, the stirring time is 2 hours.

7. The preparation method according to claim 5, characterized in that: In step S4, the β-calcium phosphate is 16-20 parts, the calcium dihydrogen phosphate monohydrate is 13 parts, and the selenocysteine ​​is 0.006-0.03 parts, and they are ground until they are evenly mixed.

8. The preparation method according to claim 5, characterized in that: In step S5, the composite pore-forming agent powder is 0.5 parts, the bioactive glass is 1.1 parts, and the calcium carbonate is 0.8 parts.

9. The application of the injectable porous selenium-loaded antibacterial bone cement material as described in any one of claims 1-4 in the preparation of bone defect repair materials.

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