CN116712594B - Multifunctional antibacterial wound dressing and preparation method and application thereof - Google Patents
Multifunctional antibacterial wound dressing and preparation method and application thereof Download PDFInfo
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- Y—GENERAL TAGGING OF NEW TECHNOLOGICAL DEVELOPMENTS; GENERAL TAGGING OF CROSS-SECTIONAL TECHNOLOGIES SPANNING OVER SEVERAL SECTIONS OF THE IPC; TECHNICAL SUBJECTS COVERED BY FORMER USPC CROSS-REFERENCE ART COLLECTIONS [XRACs] AND DIGESTS
- Y02—TECHNOLOGIES OR APPLICATIONS FOR MITIGATION OR ADAPTATION AGAINST CLIMATE CHANGE
- Y02A—TECHNOLOGIES FOR ADAPTATION TO CLIMATE CHANGE
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- Y02A50/30—Against vector-borne diseases, e.g. mosquito-borne, fly-borne, tick-borne or waterborne diseases whose impact is exacerbated by climate change
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- Materials For Medical Uses (AREA)
Abstract
The invention discloses a multifunctional antibacterial wound dressing and a preparation method and application thereof. The antibacterial wound dressing is a porous membrane containing three components, hydroxyapatite particles are contained in a bracket of the porous membrane, a bracket main body of the porous membrane is chitosan, and a bracket outer layer of the porous membrane is coated by MOF, and the preparation method comprises the following steps: the porous membrane is formed by a simple pouring method by two biocompatible materials of hydroxyapatite and chitosan, and then the antibacterial component ZIF-8 is fixed on the porous membrane of the hydroxyapatite/chitosan through in-situ growth, so that the antibacterial porous membrane is prepared. The multifunctional antibacterial wound dressing prepared by the invention has excellent antibacterial property, mechanical property and biocompatibility, can accelerate the metabolic activity of skin cells around a wound and the maturation of collagen fibers to promote wound healing, has the potential for wound healing application, and can be applied to the preparation of antibacterial materials, wound dressings and medical appliances.
Description
Technical Field
The invention relates to the technical field of biomedical materials, in particular to a multifunctional antibacterial wound dressing and a preparation method and application thereof.
Background
The skin serves as the first defense line of the body and has the function of maintaining the balance of the internal environment and biological barrier in the body. After the skin is damaged, wound infection bacteria, aggravated inflammatory response and the like can destroy the normal process of wound healing, inhibit wound healing and even threaten life. Therefore, the nursing device has important practical significance for promoting wound healing, reducing postoperative complications, reducing treatment cost and the like. The wound dressing commonly used in clinic is gauze, but has single function, and lacks ideal wound dressing performances such as antibacterial property, air permeability, biocompatibility, hemostasis promotion, tissue growth promotion and the like. Therefore, it is of great importance to develop a multifunctional wound dressing that is economical and has desirable properties.
Chitosan (CS) is a natural polymer biomaterial with a natural content inferior to that of cellulose, and has unique advantages of wide and easily available sources, good biocompatibility, coagulation performance, biodegradation and the like, so that the Chitosan (CS) can be used as a wound dressing. However, pure CS has poor chemical stability and its functionality and mechanical properties are to be improved for use as a dressing. Hydroxyapatite (HAP) is an important component of bone and teeth, has a certain mechanical strength, promotes cell proliferation, and releases coagulation factor Ca 2+ The ability to accelerate hemostasis can be widely applied to biomedical materials. Research shows that the HAP and CS are compounded into the film, so that the biocompatibility of the HAP and CS can be maintained, and the mechanical property of the composite film can be effectively improved. In addition, the HAP is expected to endow the composite membrane with good coagulation capability, tissue growth promotion capability and porous structure possibly capable of guaranteeing the air permeability. However, the antibacterial performance thereof is still to be further improved.
ZIF-8 is a metal organic frame material formed by connecting zinc ions and 2-methylimidazole through covalent bonds, and has the advantages of large specific surface area, adjustable aperture, various structures and the like, and is used in the fields of hydrogen storage, gas adsorption separation, sensing, catalysis and the likeThe domain is widely used. The research shows that the ZIF-8 loaded bioactive material can better promote the healing of infected wounds, can be used as a reservoir of antibacterial metal ions, and can be used as a carrier of antibacterial drugs. Zn released by ZIF-8 at the same time 2+ But also to the aggregation of platelets and the activation of clotting factors, thereby accelerating the clotting of the wound. However, the current antibacterial mode of the bioactive material supported ZIF-8 still mainly comes from ZIF-8 supported antibiotics, which can lead to bacterial resistance.
Disclosure of Invention
In order to solve the defects in the prior art, the invention aims to provide a multifunctional antibacterial wound dressing and a preparation method and application thereof.
The technical scheme for solving the technical problems is as follows:
a multi-functional antimicrobial wound dressing comprising: the antibacterial wound dressing is a porous membrane containing three components, hydroxyapatite particles are contained in a bracket of the porous membrane, a bracket main body of the porous membrane is chitosan, and the outer layer of the bracket of the porous membrane is coated by MOF.
Further, the MOF includes ZIF-8.
Further, the mass ratio of chitosan, hydroxyapatite and ZIF-8 is 25-40: 20-30: 12-18.
Further, the chitosan has a degree of deacetylation of 75-95% or a degree of deacetylation of more than 95%, a viscosity of less than 200 mPas, or a viscosity of 200-400 mPas, or a viscosity of more than 400 mPas.
The preparation method of the multifunctional antibacterial wound dressing comprises the following steps:
1) Preparing a hydroxyapatite/chitosan porous membrane (HC porous membrane);
2) Preparation of hydroxyapatite/chitosan/ZIF-8 porous membrane (HCZ porous membrane): soaking the hydroxyapatite/chitosan porous membrane prepared in the step 1) in zinc salt solution for zinc ion adsorption, wherein the concentration of the zinc salt solution is 2-20mg/mL, then adding the soaked hydroxyapatite/chitosan porous membrane into 2-methylimidazole solution for covalent bond connection of zinc ions and 2-methylimidazole, reacting for 0.5-24h at 20-50 ℃, and drying to obtain the porous hydroxyapatite/chitosan porous membrane.
Preferably, the zinc salt in step 2) is zinc nitrate, and the concentration of the zinc nitrate solution is 2, 5, 10 or 20mg/mL.
Further, step 1) adopts polyethylene glycol to blend with hydroxyapatite and chitosan to prepare the hydroxyapatite/chitosan porous membrane, the mass ratio of the polyethylene glycol to the chitosan is 0.5-1:1, and the molecular weight of the polyethylene glycol is 200-20000.
Preferably, the mass ratio of polyethylene glycol to chitosan is 0.8:1, the molecular weight of the polyethylene glycol is 200, 400, 1000, 8000, 10000 or 20000.
Further, the step 1) specifically includes the steps of: dissolving chitosan in an acid solution with the mass fraction of 3-7%, stirring in an oil pot bath until the chitosan is completely dissolved, dripping hydroxyapatite dispersion liquid and polyethylene glycol solution, continuously stirring, pouring the mixed solution on a glass plate to form a liquid film, volatilizing the solvent in an oven, neutralizing excessive acetic acid in the film with strong alkali, washing with deionized water, and drying at 20-50 ℃ for 10-24 hours to obtain the hydroxyapatite/chitosan porous film.
Further, the drying temperature in the step 2) is 20-50 ℃, and the drying time is 10-24 hours.
The multifunctional antibacterial wound dressing is applied to the preparation of antibacterial materials, wound dressings and medical appliances.
The antibacterial material comprises a water antibacterial material.
A multifunctional antimicrobial material/wound dressing/medical device comprising the above antimicrobial wound dressing.
The invention has the following beneficial effects:
(1) The invention takes chitosan and hydroxyapatite as active ingredients, synthesizes a hydroxyapatite/chitosan porous membrane by a simple green method, fixes ZIF-8 on the hydroxyapatite/chitosan porous membrane by in-situ growth, and successfully constructs the hydroxyapatite/chitosan/ZIF-8 multifunctional antibacterial wound dressing. The active ingredient of the multifunctional antibacterial wound dressing has excellent coagulation capability, mechanical property, biocompatibility and capability of promoting tissue regeneration.
(2) The multifunctional antibacterial wound dressing prepared by the invention can effectively remove wound infection bacteria, and accelerate the metabolic activity of skin cells around the wound and the maturation of collagen fibers, thereby promoting wound healing. Finally, hydroxyapatite/chitosan/ZIF-8 porous membranes were prepared as portable medical devices similar to commercial wound dressings, which can be tightly fitted to the skin and sized to exhibit potential for wound healing applications.
Drawings
FIG. 1 is a process flow diagram of the preparation of a multifunctional antimicrobial wound dressing, comprising two parts, namely the preparation of an HC porous membrane and the preparation of a HCZ porous membrane;
FIG. 2 is an infrared spectrum of a HCZ porous film prepared in example 18;
FIG. 3 shows inhibition zone experiments on Staphylococcus aureus (A) and Escherichia coli (D) with HCZ porous membranes prepared in example 18, the diameter of the inhibition zone and nw of Staphylococcus aureus (B, C) and Escherichia coli (E, F) halo Diameter;
FIG. 4 is a graph showing the coagulation index of HCZ porous membranes prepared in examples 16-19;
FIG. 5 is an evaluation of cytotoxicity of HCZ porous membrane extract prepared in example 18 on L929 cells, wherein the leaching solutions of 20, 50, 100, 200, 500 μg/mLHCZ-10 membranes were sequentially from left to right;
FIG. 6 is a living study of wound healing by a HCZ porous membrane in test example 5, wherein, A is the visual appearance of rats in the non-infected groups on days 3, 7, 10 and 14, B is the wound closure rate (%) of rats in the non-infected groups during wound healing, C is the visual appearance of rats in the infected groups on days 3, 7, 10 and 14, D is the wound closure rate (%) of rats in the infected groups during wound healing, and B and D are test groups treated with gauze, HC and HCZ in this order from left to right in the histogram;
FIG. 7 shows the histopathological evaluation and statistics of a wound by using a HCZ porous membrane in test example 6 of the present invention, wherein, the A chart shows the histopathological evaluation of wound tissues of a non-infected group by Masson's trichromatic staining, the B chart shows the histopathological evaluation of wound tissues of an infected group by Masson's trichromatic staining, the C chart shows the collagen fiber content of the non-infected group, the D chart shows the collagen fiber content of the infected group, and the C chart and the D chart show the test groups treated with gauze, HC and HCZ in sequence from left to right.
Detailed Description
The examples given below are only intended to illustrate the invention and are not intended to limit the scope thereof. The specific conditions are not noted in the examples and are carried out according to conventional conditions or conditions recommended by the manufacturer. The reagents or apparatus used were conventional products commercially available without the manufacturer's attention.
Example 1:
a method for preparing an HC porous film, comprising the steps of:
1g of chitosan (degree of deacetylation greater than 95%, viscosity 200-400 mPas) was dissolved in 35mL of 5wt.% acetic acid solution and stirred in an oil bath at 60 ℃; after the chitosan was completely dissolved, a solution of hydroxyapatite dispersion (0.428 g,5 ml) and polyethylene glycol (molecular weight 1000,0.8g,5 ml) was dropped and vigorously stirred for 3 hours; then standing for defoaming, and pouring the mixed solution on a glass plate to slowly diffuse the mixed solution to form a uniform liquid film. Then the liquid film is placed in a 35 ℃ oven, the solvent is evaporated for 6 hours, and 5wt.% sodium hydroxide solution is used for neutralizing the redundant acetic acid in the film; and finally, washing with deionized water and soaking for 1h to remove polyethylene glycol and form a porous structure, and drying at 35 ℃ for later use to obtain the HC porous membrane.
Examples 2 to 9:
a preparation method of HC porous membrane changes the raw materials for preparing HC porous membrane and the proportion and parameters thereof, and other preparation conditions are the same as in example 1.
The specific parameters are shown in Table 1.
Table 1 raw materials for preparing HC porous film, and ratio and parameter thereof
Examples 10 to 15:
a method for preparing a HCZ porous membrane, comprising the steps of:
200mg of the HC porous membrane prepared in example 1 was put into 20mL of a zinc nitrate solution with a certain concentration, and zinc ions were adsorbed on a constant temperature shaking table for 1h. And then taking out the membrane, wiping the membrane, placing the membrane into 20mL of 20.5mg/mL of 2-methylimidazole solution, continuously reacting for a period of time, washing the membrane with deionized water to be neutral, and drying the membrane at 35 ℃ to obtain the HCZ porous membrane.
Examples 10-15 differ only in the reaction time from 2-methylimidazole, and the specific parameters are shown in Table 2.
TABLE 2 preparation of HCZ porous membranes at different reaction times
Examples 16 to 19:
a method for preparing a HCZ porous membrane, comprising the steps of:
200mg of the HC porous membrane prepared above was put into 20mL of zinc nitrate solution with a certain concentration, and zinc ions were adsorbed on a constant temperature shaker for 1h. And then taking out the membrane, wiping the membrane, placing the membrane into 20mL of 20.5mg/mL of 2-methylimidazole solution, continuously reacting for a period of time, washing the membrane with deionized water to be neutral, and drying the membrane at 35 ℃ to obtain the HCZ porous membrane.
Examples 17 to 19 and example 12 differ only in adsorption time of zinc ions, and specific parameters are shown in Table 3.
TABLE 3 preparation of zinc ion concentration HCZ porous membranes
The different synthesis conditions have a great influence on the performance of the HCZ porous membrane, and the HC porous membrane prepared by the method described in example 1 and the HCZ-10 porous membrane prepared by the parameters described in example 18 are selected for analysis of the structural characteristics, antibacterial performance, biocompatibility and in-vivo wound healing condition from the comprehensive consideration of the structure and application of materials.
Test example 1: infrared spectrum test
To investigate whether ZIF-8 was successfully immobilized on the HC membrane, the HC porous membranes prepared in example 1 and HCZ-10 porous membranes prepared in example 18 were infrared-characterized, and the infrared-characterized results are shown in FIG. 2.
First, the interaction of CS with HAP in HC porous membranes was explored, and infrared spectra showed that all characteristic peaks of pure CS powder and commercial pure HAP nanoparticles were present in FTIR spectra of HC porous membranes. However, compared to pure CS, the-OH stretch absorption peak of the HC porous membrane red shifted to 3416cm -1 And broadens, indicating that interactions between CS and HAP may occur.
Further explored the interaction between ZIF-8 and HC porous membrane in HCZ-10, characteristic absorption peak of ZIF-8 was observed on the infrared spectrogram of HCZ-10 porous membrane, indicating that ZIF-8 was successfully attached to HC porous membrane, consistent with XRD results. However, compared to pure ZIF-8, the imidazole ring was present at 1309cm in a HCZ porous membrane -1 、1424cm -1 、1495cm -1 The relative intensities of the absorption bands produced at the sites are all reduced, probably due to the formation of N-H.N and N-H.O hydrogen bonds between the N atom on imidazole and-NH/-OH on chitosan in the HC porous membrane, resulting in a reduction in the infrared absorption intensity of the corresponding functional groups. However, the porous film HCZ-10 was formed at 421cm -1 The absorption peak of Zn-N stretching vibration is higher than that of pure ZIF-8, and the absorption peak is probably Zn in ZIF-8 in HCZ-10 film 2+ Is connected with-NH on CS in the form of Zn-N bond.
In combination, there is an interaction between CS and HAp in the HC porous membrane, rather than simple physical mixing. HCZ-10 porous membranes, ZIF-8 is attached to the membrane surface by two actions, one of which is hydrogen bonding with chitosan through the N atom on the ligand imidazole ring; secondly, through metal ion Zn 2+ Forms Zn-N bond with-NH on chitosan.
Test example 2: antibacterial property test
The HC porous films prepared in example 1 and the porous films HCZ-2, HCZ-5, HCZ-10 and HCZ-20 prepared in examples 16-19 were subjected to antibacterial property test to investigate the antibacterial properties thereof, and the test results are shown in FIG. 3.
The ability of HCZ porous membranes to inhibit bacterial growth was assessed by disc diffusion, as represented by the common pathogenic bacteria staphylococcus aureus and escherichia coli. The results are shown in FIGS. 3A and D, and the HC porous membrane did not show significant antibacterial activity against Staphylococcus aureus and Escherichia coli. In contrast, ZIF-8 loaded porous membranes (HCZ-2, HCZ-5, HCZ-10 and HCZ-20) exhibited significant antibacterial activity against both bacteria, probably due to the Zn released by ZIF-8 in the HCZ porous membrane 2+ Destroying the bacterial cell membrane, resulting in leakage of intracellular components.
Further statistics of the results of the zone of inhibition revealed that with increasing ZIF-8 loading in the HCZ porous membrane, the zone of inhibition diameters of both bacteria showed a trend of increasing followed by decreasing, and an optimal bacteriostatic effect was achieved at HCZ-10 (fig. 3B and C). The reason for this may be that Zn was released as the ZIF-8 content in the HCZ porous film was increased 2+ The concentration is gradually increased, and the sterilization effect is enhanced; however, when the content of ZIF-8 in the HCZ porous membrane is too high, the pore structure of the membrane can be blocked, and Zn is reduced 2+ The release rate eventually results in a decrease in the bactericidal effect.
It is noted that the initial diameter of the membranes taken in fig. 3 is 6mm, and that the diameter of the membranes after use is increased compared to the initial diameter due to the water-absorbing expansion of the membranes themselves. To attenuate the effect of membrane swelling on the diameter of the zone of inhibition, we calculated the antibacterial "halo" (nw) of the sample halo ) Is shown (fig. 3C and F). The results showed that the trend of the antibacterial "halo" was consistent with the above results, and the antibacterial "halo" of both bacteria showed a trend of increasing followed by decreasing with increasing ZIF-8 loading in the HCZ porous membrane. HCZ-10 the normalized diameter of the porous membrane is the largest and the antibacterial performance is the best.
Test example 3: coagulation ability test
The hemostatic effect of the material is related to the blood coagulation capacity, and the stronger the blood coagulation capacity is, the better the corresponding hemostatic effect is. The clotting ability was inversely proportional to the clotting index (BCI) value, and thus was evaluated by calculating BCI values for the HC porous membranes prepared in example 1 and the porous membrane samples HCZ-2, HCZ-5, HCZ-10 and HCZ-20 prepared in examples 16-19, and the test results are shown in FIG. 4.
As can be seen from the graph, the BCI values of the HCZ porous membranes with different ZIF-8 loadings are lower than those of the HC porous membranes, which indicates that the combination of ZIF-8 enhances the clotting capacity of the HC porous membranes. This is due to the fact that zn2+ released by ZIF-8 contributes to platelet aggregation and activation of coagulation factors, thereby accelerating coagulation. And with the increase of ZIF-8 load in the HCZ porous membrane, the clotting capacity of the HCZ porous membrane is gradually enhanced, and the optimal value is achieved at HCZ-10, and the BCI value is only 7.24+/-0.3%. However, as the loading of ZIF-8 in the HCZ porous membrane further increased, the clotting ability of the material decreased instead, probably due to the increased hydrophobicity of the HCZ porous membrane with a too high ZIF-8 content.
Test example 4: cytotoxicity test
Cytotoxicity evaluation was performed on the HCZ-10 porous membrane prepared in example 18, cytotoxicity of the HCZ-10 membrane was evaluated by MTT assay, and the extract of the HCZ-10 membrane was gradient diluted to 20, 50, 100, 200, 500. Mu.g/mL, and then co-cultured with L929 fibroblasts.
The results of the experiment are shown in FIG. 5, and the relative growth rate of HCZ-10 membrane group cells is far higher than that of the blank group by 80% after incubation for 24h, 48h and 72 h. ISO 10993-5 (ISO, 2009) states that cell viability above 80% is considered non-cytotoxic. Therefore, the HCZ-10 membrane prepared by the invention has good biocompatibility.
Test example 5: test of wound healing promoting Property of HCZ-10 porous Membrane
Wound healing properties for the HC porous membranes prepared in example 1 and the HCZ-10 porous membranes prepared in example 18 in full-thickness skin defect models and bacterial infection full-thickness skin defect models. In which an in vivo healing experiment was performed on a full-thickness skin defect model of bacterial infection in order to further investigate the anti-infective ability of HCZ-10 membranes. In vivo healing experiments were thus set up into two groups: uninfected and infected groups, the experimental procedure was as follows:
non-infected group: healthy male SD rats were taken 27 (6-8 weeks old, about 250 g), anesthetized with isoflurane and shaved back hair, and after skin was sterilized with 70% ethanol to create full-thickness skin defects to fascia layers, creating a wound of approximately 1cm in length and width. After molding, rats were randomly divided into 3 groups, and applied to the wound with gauze, HC and HCZ-10, respectively, and secured with breathable tape. Wound areas were measured and photographed on postoperative day 0, day 3, day 7, day 10, and day 14.
Infection group: the molding was performed in the same manner as for the non-infected group. After molding, each rat wound was inoculated with 50. Mu.L (5X 107 CFU/mL) of Staphylococcus aureus. The wound surface was treated with three dressing materials, namely gauze, HC and HCZ-10, on day 0 after 12h of infection, and the other steps were the same as those of the non-infected group. In addition, bacteria on the wound surface were collected on day 3 and day 7 for coating observation.
The wound healing rate is expressed by the degree of wound closure, calculated by equation (1):
wherein A is 0 Represents the area of the initial wound, A t Is the wound area on days 3, 7, 10 and 14.
(1) Wound healing promoting properties of HCZ-10 porous membranes in full-thickness skin defect model
The wound healing promoting properties of HCZ-10 films were studied in a full-thickness skin defect model using gauze (a common commercial dressing) as a control, and the test results are shown in fig. 6 and 7.
First, wound healing was observed on day 0, day 3, day 7, day 10 and day 14 for the uninfected groups of gauze, HC and HCZ-10. As shown in fig. 6A, the macroscopic area of wound in rats treated with the three groups of materials decreased with time, with HCZ-10 groups of wound areas being the smallest. Compared with gauze, HC and HCZ-10 porous membranes had better promotion of wound healing at various stages of wound healing, with rates of wound closure greater than 95% by day 14 for both HC (95.2+ -0.8%) and HCZ-10 (95.4+ -0.5%) groups, approaching complete closure (FIG. 6B). Overall, HCZ-10 is slightly more potent in promoting wound healing than HC porous membranes without bacteria infection, but both are more potent in promoting wound healing than gauze.
Masson trichromatic staining revealed that, 3 days after surgery, the non-infected wound tissue HCZ-10 group had significantly higher collagen fiber content than the gauze and HC groups (FIGS. 7A and 7C). On days 7 and 14, the HCZ-10 groups had more collagen fibers generated and the collagen bundles were more ordered. This is because the CS and HAP active ingredients contained in the HC and HCZ-10 films promote wound healing.
(2) Wound healing promoting properties of HCZ-10 porous membranes in full-thickness skin defect model of bacterial infection
In vivo healing experiments were performed on full-thickness skin defect models after staphylococcus aureus infection using gauze (a common commercial dressing) as a control, and the test results are shown in fig. 6 and 7.
As shown in fig. 6C, the infected group had some shrinkage of the wound on day zero compared to the uninfected group. In the early stages of wound healing (first 3 days), HCZ-10 porous membranes exhibited very excellent wound healing properties (44.5±1.5%) well above that of gauze group (7.3±0.4%) and HC group (4.8±1.0%) (fig. 6D). This is attributable to the fact that the infected group has a large amount of bacterial growth on the early moist wound surface, but the gauze and HC film are not effective in inhibiting bacterial growth, so that the wound healing is slow, while the HCZ-10 film has a very excellent bactericidal ability and good biological activity, and can kill bacteria at early stage and accelerate wound healing. The wound closure rate of HCZ-10 groups had reached 94.6.+ -. 0.51% on day 10 and nearly 100% on day 14. In combination, HCZ-10 porous membranes retain high bacteriostatic and wound healing capabilities for each time period of wound healing, with more pronounced early in wound healing. Meanwhile, the capability of promoting healing of the HC in early-stage wounds is slightly lower than that of gauze, and the HC is probably shrinkage of the wounds due to more water loss of a gauze group. However, in the subsequent healing stage, the healing speed of the HC group wound is higher than that of the gauze group, and the HC porous membrane plays a role in healing the wound and can be attributed to active ingredients such as CS, HAp and the like in the HC porous membrane.
Furthermore, it was found that while wound healing was accompanied by rapid growth of hair in group HCZ-10, new hair growth was observed markedly on day 3 and the hair at the wound had been substantially and peripherally consistent by day 14, but in order to observe the wound size, a portion of the hair around the wound was cut off again. However, this was not observed for gauze and HC groups and no small amounts of hair were generated until day 14. This demonstrates from another point of view the ability of the HCZ-10 porous membrane to promote wound healing and excellent biocompatibility.
Masson trichromatography can observe that the ratio of collagen fibers to infected wound tissue HCZ-10 to HC groups was relatively close on both day 3 and day 7 and slightly higher than in the gauze group (FIGS. 7B and 7D). However, on day 14, the collagen fiber content of HCZ-10 and HC groups was significantly higher than that of gauze groups, and the fiber matrix of HCZ-10 groups was more densely ordered, probably HCZ-10 could accelerate collagen fiber synthesis and maturation at the later stage of healing of infected wounds, significantly promoting tissue regeneration. The comprehensive effect HCZ-10 has good capability of promoting the growth of collagen fibers and can effectively promote the wound healing.
In summary, the invention synthesizes the HC porous membrane, fixes ZIF-8 to the HC porous membrane by in-situ growth, and successfully constructs the HCZ porous membrane antibacterial dressing. The HCZ porous membrane has excellent coagulation capability, mechanical property, biocompatibility and capability of promoting tissue regeneration, can effectively remove wound infection bacteria, accelerates the metabolic activity of skin cells around a wound and the maturation of collagen fibers to promote wound healing, and can be used as a multifunctional antibacterial wound dressing.
The foregoing description of the preferred embodiments of the invention is not intended to limit the invention to the precise form disclosed, and any such modifications, equivalents, and alternatives falling within the spirit and scope of the invention are intended to be included within the scope of the invention.
Claims (7)
1. A multi-functional antimicrobial wound dressing, comprising: the antibacterial wound dressing is a porous membrane containing three components, hydroxyapatite particles are contained in a bracket of the porous membrane, a bracket main body of the porous membrane is chitosan, and a bracket outer layer of the porous membrane is coated by ZIF-8;
the mass ratio of the chitosan, the hydroxyapatite and the ZIF-8 is 25-40: 10-30: 12-18;
the preparation method of the multifunctional antibacterial wound dressing comprises the following steps:
1) Preparing a hydroxyapatite/chitosan porous membrane;
2) Preparation of a hydroxyapatite/chitosan/ZIF-8 porous membrane: soaking the hydroxyapatite/chitosan porous membrane prepared in the step 1) in a zinc salt solution for zinc ion adsorption, wherein the concentration of the zinc salt solution is 2-20mg/mL, then adding the soaked hydroxyapatite/chitosan porous membrane into a 2-methylimidazole solution for reaction for 0.5-24h, and drying at the reaction temperature of 20-50 ℃ to obtain the hydroxyapatite/chitosan porous membrane.
2. The multifunctional antimicrobial wound dressing of claim 1, wherein the chitosan has a degree of deacetylation of 75-95% or a degree of deacetylation greater than 95%, a viscosity of less than 200 mPa-s, or a viscosity of 200-400 mPa-s, or a viscosity of greater than 400 mPa-s.
3. The multifunctional antibacterial wound dressing according to claim 1, wherein in the step 1), polyethylene glycol is adopted to blend with the hydroxyapatite and the chitosan to prepare the hydroxyapatite/chitosan porous membrane, the mass ratio of the polyethylene glycol to the chitosan is 0.5-1:1, and the molecular weight of the polyethylene glycol is 200-20000.
4. The multifunctional antimicrobial wound dressing according to claim 1, wherein the drying temperature in step 2) is 20-50 ℃ and the drying time is 10-24 hours.
5. Use of a multifunctional antimicrobial wound dressing according to any one of claims 1-4 for the preparation of antimicrobial materials, wound dressings and medical devices.
6. The use of a multifunctional antimicrobial wound dressing according to claim 5 for the preparation of antimicrobial materials, wound dressings and medical devices, wherein the antimicrobial materials comprise water body antimicrobial materials.
7. An antimicrobial material/wound dressing/medical device comprising the multifunctional antimicrobial wound dressing of any one of claims 1-4.
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| CN113171754A (en) * | 2021-04-27 | 2021-07-27 | 郑州大学 | Hierarchical porous metal organic framework material ZIF-8 and preparation method and application thereof |
| CN114668894A (en) * | 2022-04-07 | 2022-06-28 | 吉林大学 | Preparation method of MOF coating modified polyether-ether-ketone base material implantation material |
| CN115814141A (en) * | 2022-12-12 | 2023-03-21 | 广东省人民医院 | Medical dressing with antibacterial and anti-adhesion functions and preparation method thereof |
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| WO2019235742A1 (en) * | 2018-06-04 | 2019-12-12 | 광운대학교 산학협력단 | Antibacterial agent comprising metal-organic framework compound, and antibacterial silicone and antibacterial hydrogel comprising same |
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| RU2748799C1 (en) * | 2020-07-29 | 2021-05-31 | Федеральное государственное бюджетное учреждение науки Институт химии Дальневосточного отделения Российской академии наук (ИХ ДВО РАН) | Method for producing composite biomaterial chitosan/hydroxyapatite |
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| CN114668894A (en) * | 2022-04-07 | 2022-06-28 | 吉林大学 | Preparation method of MOF coating modified polyether-ether-ketone base material implantation material |
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