Microcurrent sponge dressing for promoting pressure ulcer healing and its application

Abstract

This application belongs to the technical field of medical dressings, and particularly relates to a microcurrent sponge dressing for promoting pressure ulcer healing and its application. It includes a diaphragm, a cathode sponge, and an anode sponge; the cathode sponge is annularly wrapped outside the diaphragm; the anode sponge is cylindrically distributed inside the diaphragm. In the microcurrent sponge dressing provided by the present invention, the cathode sponge and the anode sponge generate a redox reaction in the wound exudate to produce an electric current; this microcurrent can promote collagen regeneration, and at the same time can generate zinc metal ions with antibacterial effects, which can reduce the risk of wound infection and promote wound healing; in addition, the microcurrent sponge dressing has a three-dimensional porous structure, has excellent water absorption performance, can fully absorb wound exudate, and also has good elasticity, and can provide a buffer layer between the patient and the support surface to reduce the wound surface pressure, ultimately promoting the healing of the pressure ulcer wound surface.

Description

Technical Field

[0001] This application belongs to the technical field of medical dressings, and particularly relates to a microcurrent sponge dressing for promoting pressure ulcer healing and its application. Background Art

[0002] The condition of pressure ulcers is relatively complex, with slow self-healing, severe tissue necrosis, and easy repeated infections, which can further develop into chronic wounds. In addition, chronic wounds will in turn exacerbate the primary disease, which not only causes great physical and psychological pressure on patients, but also brings a heavy burden to families and society. The pathogenesis of pressure ulcers is very complex, involving many disciplines and the interaction of multiple factors, such as local tissue hypoxia, wound bacterial infection, ischemia-reperfusion injury, etc. Although there are many factors, tissue ischemia caused by mechanical force is widely considered to be the initiating factor. Common dressings currently used in the market for treating pressure ulcers include foam dressings, hydrogel dressings, hydrocolloid dressings, transparent films, alginate dressings, etc. These dressings have single functions and are difficult to meet the needs of complex wound healing.

[0003] Studies have shown that microcurrent has antibacterial, anti-inflammatory, cell migration guiding, and collagen regeneration promoting effects during wound healing; currently, microcurrent dressings used for wound healing, such as PED-10 electronic dressings and Posifect (Biofisica) dressings, require an external power supply, and the portability of the dressings cannot be guaranteed; at the same time, dressings for pressure ulcers should have elasticity to provide a buffer layer between the patient and the support surface to reduce the wound surface pressure and ultimately promote the healing of pressure ulcer wounds. Summary of the Invention

[0004] The technical problem to be solved by the present invention is: to provide a microcurrent sponge dressing that is convenient to use, does not require external power supply, can generate microcurrent by itself, and has a three-dimensional porous structure and good elasticity to relieve the pressure on pressure ulcer wounds.

[0005] The present invention provides a microcurrent sponge dressing for promoting pressure ulcer healing and its application, specifically adopting the following technical solutions:

[0006] In the first aspect, a microcurrent sponge dressing for promoting pressure ulcer healing includes a cathode sponge, an anode sponge, and a diaphragm; the cathode sponge is annularly wrapped outside the diaphragm; the anode sponge is cylindrically distributed inside the diaphragm;

[0007] The preparation methods of the cathode sponge and the anode sponge specifically include the following steps:

[0008] Add carboxymethyl chitosan to a phosphate buffer solution and stir to obtain a chitosan dispersion;

[0009] Mix the chitosan dispersion and the bacterial cellulose solution to obtain dispersion A;

[0010] Place the silane coupling agent in the dispersion liquid A, stir evenly to obtain dispersion liquid B, then add titanium powder or zinc powder, and then place it in a mold, freeze, freeze-dry, and vacuum-dry to obtain the anode sponge and the cathode sponge respectively;

[0011] The preparation method of the separator includes the following steps:

[0012] Coat a layer of acrylic emulsion on the upper surface and side surface of the anode sponge, and vacuum-dry to obtain the separator.

[0013] As a further preferred embodiment, the mass ratio of the carboxymethyl chitosan, phosphate buffer solution, bacterial cellulose solution, and silane coupling agent is 1:57:40:2.

[0014] As a further preferred embodiment, the solid content in the bacterial cellulose solution is 0.8%.

[0015] As a further preferred embodiment, the silane coupling agent includes one or more of KH550, KH560, and KH570.

[0016] As a further preferred embodiment, the pH of the phosphate buffer solution is 7.5 - 9.0.

[0017] As a further preferred embodiment, the temperature for stirring the carboxymethyl chitosan dispersed in the phosphate buffer solution is 40 °C - 60 °C.

[0018] In the second aspect, the present invention also provides the application of the above microcurrent sponge dressing in the preparation of an antibacterial material for promoting wound healing.

[0019] As a further preferred embodiment, the wound includes a pressure ulcer wound surface.

[0020] In the third aspect, the present invention also provides an antibacterial material for pressure ulcer wound surface healing, and this antibacterial material includes the above microcurrent sponge dressing.

[0021] The beneficial effects of the present invention are:

[0022] The present invention provides a microcurrent sponge dressing, which includes a diaphragm, a cathode sponge, and an anode sponge. The cathode sponge is annularly wrapped outside the diaphragm, and the anode sponge is cylindrically distributed inside the diaphragm. The cathode sponge and the anode sponge generate a redox reaction in the wound exudate to produce an electric current. According to the data results of the embodiments of the present invention, simulating the moist environment of the wound can release a voltage greater than 0.2V; this microcurrent can promote the regeneration of collagen, and at the same time can generate zinc metal ions with antibacterial effects, which can reduce the risk of wound infection and promote wound healing; in addition, the microcurrent sponge dressing has a three-dimensional porous structure, has excellent water absorption performance, can fully absorb the wound exudate, maintain a moist wound healing environment, and accelerate wound surface healing; it also has good resilience performance, can provide a buffer layer between the patient and the support surface to reduce the wound surface pressure, relieve the inflammatory damage caused by ischemia and hypoxia of the skin due to long-term pressure in pressure ulcer patients, and ultimately promote the healing of pressure ulcer wounds. Description of the Drawings

[0023] In order to more clearly illustrate the technical solutions in the embodiments of the present invention, the following will briefly introduce the drawings required for use in the embodiments. Obviously, the drawings in the following description are only some embodiments of the present invention. For those of ordinary skill in the art, without creative efforts, other drawings can also be obtained based on these drawings.

[0024] Figure 1 The figure shows the CCK-8 cytotoxicity test results of the microcurrent sponge dressings prepared in Examples 1-3;

[0025] Figure 2 The figure shows the results of the cell live / dead staining experiment of the microcurrent sponge dressings prepared in Examples 1-3;

[0026] Figure 3 The figure shows the antibacterial results of the microcurrent sponge dressings prepared in Examples 1-3;

[0027] Figure 4 The figure shows the SEM and EDS characterization diagrams of the microcurrent sponge dressings prepared in Examples 1-3;

[0028] Figure 5 The figure shows the voltage and current change diagrams of the microcurrent sponge dressings prepared in Examples 1-3;

[0029] Figure 6 The figure shows the water absorption rate results of the microcurrent sponge dressings prepared in Examples 1-3;

[0030] Figure 7 The figure shows the stress-strain curve diagrams of the microcurrent sponge dressings prepared in Examples 1-3;

[0031] Figure 8 The figure shows the physical picture of the microcurrent sponge dressing prepared in Example 1 after being moistened. Detailed implementation manners

[0032] Next, the technical solutions in the embodiments of the present application will be clearly and completely described in conjunction with the accompanying drawings in the embodiments of the present application. Obviously, the described embodiments are part of the embodiments of the present application, rather than all the embodiments. Based on the embodiments in the present application, all other embodiments obtained by those of ordinary skill in the art without creative efforts belong to the scope of protection of the present application.

[0033] Example 1

[0034] A microcurrent sponge dressing for promoting pressure ulcer healing, and its preparation method specifically includes the following steps:

[0035] (1) Preparation of columnar anode sponge and diaphragm:

[0036] Step 1: Add 1 g of carboxymethyl chitosan to 57 g of phosphate buffer solution with pH = 8, stir well for 2 hours, and the temperature during stirring is 45 °C to prepare a chitosan dispersion;

[0037] Step 2: Add 40 g of bacterial cellulose dispersion with a solid content of 0.8% to the chitosan dispersion in Step 1, stir for 30 minutes to prepare dispersion A, and then add 2 g of silane coupling agent KH560 to dispersion A, stir for 30 minutes to obtain dispersion B;

[0038] Step 3: Add 0.5 g of titanium powder to dispersion B in Step 2, stir well for 10 hours, then inject it into a circular mold, place it in a -40 °C refrigerator for 8 hours, then put it into a freeze dryer for freeze-drying for 24 hours, and then vacuum-dry it at 110 °C for 50 minutes to obtain an anode sponge. Then, coat a layer of acrylic emulsion on the upper surface and side of the sponge, and vacuum-dry it for 24 hours to form an anode sponge diaphragm, that is, obtain the BCK@Ti 0.5 sponge.

[0039] (2) Preparation of annular cathode sponge:

[0040] Step 1: Add 1 g of carboxymethyl chitosan to 57 g of phosphate buffer solution with pH = 8, stir well for 2 hours, and the temperature during stirring is 45 °C to prepare a chitosan dispersion;

[0041] Step 2: Add 40 g of bacterial cellulose dispersion with a solid content of 0.8% to the chitosan dispersion described in step (1), stir for 30 minutes to prepare dispersion A, and then add 2 g of silane coupling agent KH560 to dispersion A, stir for 30 minutes to obtain dispersion B;

[0042] Step 3: Add 0.5 g of zinc powder into the dispersion liquid B described in Step 2, stir well for 10 hours, then pour it into a ring mold, freeze it in a -40 °C refrigerator for 8 hours, and then freeze-dry it in a freeze dryer for 24 hours. Then, vacuum-dry it at 110 °C for 50 minutes to obtain a cathode sponge, namely BCK@Zn 0.5 sponge;

[0043] (3) Preparation of microcurrent sponge dressing:

[0044] Nest the anode sponge coated with a diaphragm into the cathode sponge to obtain a microcurrent sponge dressing, namely BCK@Ti / Zn 0.5 sponge.

[0045] The physical photo of the microcurrent sponge dressing prepared by the present invention after being moistened is as Figure 8 shown (where 1, cathode sponge; 2, upper surface diaphragm; 3, anode sponge; 4, side surface diaphragm). When the sponge is used to treat pressure ulcer wounds, it can fully absorb the wound exudate. The anode sponge (titanium electrode) and the cathode sponge (zinc electrode) form a circuit in a humid environment and undergo an electrochemical reaction. The electrochemical reaction of the zinc electrode is: . At the titanium electrode, the reaction formula that occurs is: . The content of zinc in the human body is second only to iron. About 20% of the zinc in the adult body exists in the skin. It is one of the most important trace elements in the human body. As a coenzyme factor and the active center of proteins, zinc is essential for many enzymes and macromolecules. The direct effect of zinc ions on wound repair is mainly to promote the proliferation of repair cells and protein synthesis through zinc-dependent enzymes (such as DNA polymerase, RNA polymerase), thereby promoting wound healing.

[0046] Example 2

[0047] A microcurrent sponge dressing for micro-promoting pressure ulcer healing, and its preparation method specifically includes the following steps:

[0048] (1) Preparation of columnar anode sponge and diaphragm:

[0049] Step 1: Add 1 g of carboxymethyl chitosan into 57 g of phosphate buffer solution with a pH of 8, stir well for 2 hours, and the temperature during stirring is 45 °C to prepare a chitosan dispersion liquid;

[0050] Step 2: Add 40 g of bacterial cellulose dispersion liquid with a solid content of 0.8% into the chitosan dispersion liquid described in Step 1, stir for 30 minutes to prepare dispersion liquid A, and then add 2 g of silane coupling agent KH560 into dispersion liquid A and stir for 30 minutes to obtain dispersion liquid B;

[0051] Step 3: Add 1 g of titanium powder into the dispersion B described in Step 2, stir well for 10 hours, then pour it into a circular mold, place it in a refrigerator at -40 °C for 8 hours, then put it into a freeze dryer for freeze-drying for 24 hours, and then vacuum-dry it at 110 °C for 50 minutes to obtain an anodic sponge. Then, coat a layer of acrylic emulsion on the upper surface and side of the sponge, and vacuum-dry it for 24 hours to form an anodic sponge diaphragm, that is, BCK@Ti1 sponge is obtained.

[0052] (2) Preparation of annular cathode sponge:

[0053] Step 1: Add 1 g of carboxymethyl chitosan into 57 g of phosphate buffer solution with pH = 8, stir well for 2 hours, and the temperature during stirring is 45 °C to prepare a chitosan dispersion;

[0054] Step 2: Add 40 g of bacterial cellulose dispersion with a solid content of 0.8% into the chitosan dispersion described in step (1), stir for 30 minutes to prepare dispersion A, and then add 2 g of silane coupling agent KH560 into dispersion A, stir for 30 minutes to obtain dispersion B;

[0055] Step 3: Add 1 g of zinc powder into the dispersion B described in Step 2, stir well for 10 hours, then pour it into an annular mold, place it in a refrigerator at -40 °C for 8 hours, then put it into a freeze dryer for freeze-drying for 24 hours, and then vacuum-dry it at 110 °C for 50 minutes to obtain a cathode sponge, that is, BCK@Zn1 sponge.

[0056] (3) Preparation of microcurrent sponge dressing:

[0057] Nest the anodic sponge coated with the diaphragm into the cathode sponge to obtain the microcurrent sponge dressing, that is, BCK@Ti / Zn1 sponge.

[0058] Example 3

[0059] A microcurrent sponge dressing for micro-promoting pressure ulcer healing, and its preparation method specifically includes the following steps:

[0060] (1) Preparation of columnar anodic sponge and diaphragm:

[0061] Step 1: Add 1 g of carboxymethyl chitosan into 57 g of phosphate buffer solution with pH = 8, stir well for 2 hours, and the temperature during stirring is 45 °C to prepare a chitosan dispersion;

[0062] Step 2: Add 40 g of bacterial cellulose dispersion with a solid content of 0.8% into the chitosan dispersion described in step (1), stir for 30 minutes to prepare dispersion A, and then add 2 g of silane coupling agent KH560 into dispersion A, stir for 30 minutes to obtain dispersion B;

[0063] Step 3: Add 2 g of titanium powder into the dispersion B described in Step 2, stir well for 10 hours, then pour it into a circular mold, place it in a -40°C refrigerator and freeze for 8 hours, and then put it into a freeze dryer for freeze drying for 24 hours. Then, vacuum dry it at 110°C for 50 minutes to obtain an anodic sponge. Then, coat a layer of acrylic emulsion on the upper surface and side of the sponge, and vacuum dry it for 24 hours to form an anodic sponge diaphragm, that is, BCK@Ti2 sponge is obtained.

[0064] (2) Preparation of the annular cathodic sponge:

[0065] Step 1: Add 1 g of carboxymethyl chitosan into 57 g of phosphate buffer solution with a pH of 8, stir well for 2 hours, and the temperature during stirring is 45°C to prepare a chitosan dispersion;

[0066] Step 2: Add 40 g of bacterial cellulose dispersion with a solid content of 0.8% into the chitosan dispersion described in step (1), stir for 30 minutes to prepare dispersion A, and then add 2 g of silane coupling agent KH560 into dispersion A, stir for 30 minutes to obtain dispersion B;

[0067] Step 3: Add 2 g of zinc powder into the dispersion B described in Step 2, stir well for 10 hours, then pour it into an annular mold, place it in a -40°C refrigerator and freeze for 8 hours, and then put it into a freeze dryer for freeze drying for 24 hours. Then, vacuum dry it at 110°C for 50 minutes to obtain a cathodic sponge, that is, BCK@Zn2 sponge.

[0068] (3) Preparation of the microcurrent sponge dressing:

[0069] Nest the anodic sponge diaphragm into the cathodic sponge to obtain the microcurrent sponge dressing, that is, BCK@Ti / Zn2 sponge.

[0070] Characterize and test the cross-section of the above-prepared microcurrent sponge dressing. The SEM and EDS characterization results are as Figure 4 shown, where Figure 4 (a) in is the SEM and EDS diagrams of BCK@Zn 0.5 , BCK@Zn1 and BCK@Zn2, Figure 4 (b) in is the SEM and EDS diagrams of BCK@Ti 0.5 , BCK@Ti1 and BCK@Ti2; It can be seen from (a) in Figure 4 and Figure 4 (b) in that the sponge has a porous structure, and EDS shows the distribution of zinc element in the cathodic sponge and the distribution of titanium element in the anodic sponge; Figure 4 (c) in is the SEM diagram of BCK@Ti 0.5 at 300 μm. From Figure 4It can be seen from (c) in that the microcurrent sponge has a three-dimensional porous structure and is easy to absorb liquid.

[0071] Example 4

[0072] The microcurrent sponge dressing prepared in the above examples was used for CCK-8 cytotoxicity test, and the specific process is as follows:

[0073] The CCK-8 experiment was performed using L929 fibroblasts to evaluate the in vitro biocompatibility of the microcurrent. First, the cells were cultured in a medium containing 10% fetal bovine serum and 1% penicillin streptomycin; the medium was placed in an incubator at 37 °C with 5% CO2 and 100% humidity. 5×10 3 L929 fibroblasts were placed in each well of a 96-well plate and cultured overnight to allow the cells to adhere; then, the sponge extracts (0.01 g / mL) of different groups (the microcurrent sponge dressings prepared in Examples 1-3) were added to each well for co-culture. The group without extract was used as a blank control. After incubating for 1 day, 3 days, and 7 days respectively, 10 μL of CCK-8 reagent was added to the medium and incubated for another 1 h. Finally, 100 μL of the culture solution was aspirated from the wells into a new 96-well plate, and the absorbance at 450 nm was measured using a microplate reader.

[0074] The results are as Figure 1 shown. It can be seen from the results that the microcurrent sponge dressing has no obvious cytotoxicity and exhibits good biocompatibility.

[0075] Example 5

[0076] Cell viability and cytotoxicity staining experiment

[0077] The biocompatibility of the hydrogel was evaluated by live / dead staining. L929 fibroblasts were co-cultured with the sponge extracts of different groups (the microcurrent sponge dressings prepared in Examples 1-3) for 1 day, 3 days, and 7 days, and the group without extract was used as a blank control. Live cells were stained with Calcein-AM to detect green fluorescence, and dead cells were stained with PI to detect red fluorescence. Confocal laser scanning microscopy was used to obtain the fluorescence images of L929 cells.

[0078] The results are as Figure 2 shown. It can be seen from the results that during the co-culture for 1 day, 3 days, and 7 days, the cells under different treatments increased significantly and showed green fluorescence, indicating that the microcurrent sponge dressing has good biocompatibility.

[0079] Example 6

[0080] The microcurrent sponge dressing prepared in the above examples was subjected to an antibacterial experiment test, and the specific process is as follows:

[0081] The samples of different groups (the microcurrent sponge dressings prepared in Examples 1 - 3) after ultraviolet sterilization treatment were washed three times with PBS and placed in a 12 - well plate. In the control group, no dressing was added. 1 mL of a bacterial solution with a concentration of 10 8 CFU / mL was added to each well, and they were co - cultured for 18 - 24 hours. 50 μL of the bacterial solution was taken and spread on an agar plate at an appropriate dilution factor, incubated at 37°C for 18 - 24 hours, and the number of colonies was counted. Three parallel tests were carried out for each group of samples and the average value was taken.

[0082] The results are as Figure 3 shown. From the results, the average number of colonies of the experimental group (denoted as B) and the control group (denoted as A) was statistically analyzed, and the antibacterial rate (%) was calculated as (A - B) / A×100%. The results showed that the antibacterial rates of BCK@Ti / Zn 0.5 , BCK@Ti / Zn1, and BCK@Ti / Zn2 dressings against Staphylococcus aureus were 97.6%, 99.4%, and 99.8% respectively, the antibacterial rates against methicillin - resistant Staphylococcus aureus were 97.9%, 99.7%, and 100% respectively, and the antibacterial rates against Escherichia coli were 51.1%, 52.4%, and 69.6% respectively. It was proved that the microcurrent sponge dressings had strong antibacterial ability against Staphylococcus aureus and methicillin - resistant Staphylococcus aureus, and had relatively strong antibacterial ability against Escherichia coli, thus preventing and reducing wound infections and promoting wound healing.

[0083] Example 7

[0084] The voltage of the microcurrent sponge dressings prepared in the above examples was measured, and the specific process was as follows:

[0085] The sponge dressings of different groups were fully moistened with phosphate - buffered solution (simulating the moist wound environment), and the voltage and current on the 0th day and the 3rd day were measured using a multimeter respectively.

[0086] The results are as Figure 5 shown, and from the results, it can be seen that the sponge dressings can continuously generate voltage and current for more than 3 days without an external energy source.

[0087] Example 8

[0088] The water absorption rate of the microcurrent sponge dressings prepared in the above examples was measured, and the specific process was as follows:

[0089] At room temperature, the sponge was placed in water for a period of time to fully absorb, then taken out and weighed. The calculation formula for the water absorption rate is: water absorption rate = (W1 - W0) / W0×100%, where W0 and W1 are the masses of the sample before and after immersion respectively.

[0090] The results are as Figure 6As shown, and it can be seen from the results that the sponge exhibits excellent liquid absorption capacity, which is beneficial to accelerating the absorption of wound exudate, maintaining a moist wound healing environment, and accelerating wound healing.

[0091] Example 9

[0092] The microcurrent sponge dressing prepared in the above example was subjected to a cyclic compression experiment, and the specific process is as follows:

[0093] The mechanical properties of the sponge were evaluated by a cyclic compression test using a universal testing machine at room temperature. The cyclic compression test was carried out after the sponge was completely wetted. First, it was compressed to a preset strain of 50% at a speed of 2 mm / min, and then restored to 0% strain at the same speed for 5 cycles.

[0094] Its stress-strain curve is as Figure 7 shown, Figure 7 in which (a) is the stress-strain curve of the first compression cycle in the 5 - compression cycle experiment of the microcurrent sponge dressings prepared in Examples 1 - 3, Figure 7 and (b) in which is the stress-strain curve of the continuous 5 - compression cycle experiment of the microcurrent sponge dressing prepared in Example 2. It can be seen from Figure 7 this that the sponge has good mechanical properties. After five compressions, the mechanical properties are stable, indicating that it has excellent resilience, which can reduce skin stress and relieve the inflammatory damage caused by ischemia and hypoxia of the skin due to long - term pressure in pressure ulcer patients, thus promoting the healing of pressure ulcer wounds.

[0095] The embodiments of the present application have been described above with reference to the accompanying drawings. Specific examples have been used in this article to elaborate on the principles and implementation manners of the present application. The description of the above embodiments is only used to help understand the core idea of the present application. However, the present application is not limited to the above - mentioned specific implementation manners. The above - mentioned specific implementation manners are only illustrative and not restrictive. Under the inspiration of the present application, those of ordinary skill in the art can also make many forms without departing from the purpose of the present application and the scope protected by the claims, and all of them belong to the protection scope of the present application.

Claims

1. Use of a microcurrent sponge dressing in the preparation of an antibacterial material for promoting the healing of pressure ulcer wounds, characterized in that, The bacteria include Staphylococcus aureus and methicillin-resistant Staphylococcus aureus; The microcurrent sponge dressing includes a cathode sponge, an anode sponge, and a diaphragm; the cathode sponge is annularly wrapped outside the diaphragm; the anode sponge is cylindrically distributed inside the diaphragm; The preparation method of the cathode sponge and the anode sponge specifically includes the following steps: Add carboxymethyl chitosan to a phosphate buffer solution and stir to obtain a chitosan dispersion; Mix the chitosan dispersion and a bacterial cellulose solution to obtain dispersion A; Place a silane coupling agent in dispersion A, stir evenly to obtain dispersion B; add titanium powder and zinc powder to dispersion B respectively, then place them in molds respectively, freeze, freeze-dry, and vacuum-dry to obtain a titanium-containing anode sponge and a zinc-containing cathode sponge respectively; The preparation method of the diaphragm includes the following steps: Coat a layer of acrylic emulsion on the upper surface and side surface of the anode sponge, and vacuum-dry to obtain the diaphragm; The mass ratio of the carboxymethyl chitosan, the phosphate buffer solution, the bacterial cellulose solution, the silane coupling agent to the titanium powder or to the zinc powder is 1:57:40:2:

2.

2. The application according to claim 1, characterized in that, The solid content in the bacterial cellulose solution is 0.8%.

3. The application according to claim 1, wherein The silane coupling agent includes one or more of KH550, KH560, and KH570.

4. The application according to claim 1, characterized in that, The pH of the phosphate buffer solution is 7.5 - 9.

0.

5. The application according to claim 1, wherein The temperature for dispersing the carboxymethyl chitosan in the phosphate buffer solution and stirring is 40 °C - 60 °C.

6. An antibacterial material for the healing of pressure ulcer wounds, characterized in that, It includes the microcurrent sponge dressing described in claim 1.

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