Self-power-generating medical dressing with self-pumping function and preparation method of self-power-generating medical dressing

Abstract

The invention provides a self-power-generating medical dressing with a self-pumping function and a preparation method of the self-power-generating medical dressing. The self-power-generation medical dressing with the self-pumping function comprises a power generation layer and a seepage moisture absorption and preservation layer which are arranged in sequence, the power generation layer comprises a base material, and a wet electric effect active substance and an electrode material are distributed in the base material. The wound in-situ seepage power generation dressing with the self-pumping function based on the wet electric effect is provided for solving the problems that existing electrical stimulation medical dressings generally cannot achieve simple and stable self-power supply and are single in treatment means, and effective management of wound in-situ power generation and seepage is integrally achieved. The invention further provides a preparation method of the self-generating medical dressing with the self-pumping function.

Description

Technical Field

[0001] The invention belongs to the technical field of medical dressings, and in particular relates to a self-generating medical dressing with a self-pumping function and a preparation method thereof. Background Art

[0002] In recent years, the use of different types of power supply modules and medical dressings in layers has become a common way to design self-powered electrical stimulation dressings. However, the separation of the power supply module from the dressing body leads to complex dressing structure and preparation process, reducing its practical application value.

[0003] Currently available electro-stimulation medical dressings generally have the problems of being unable to simply and stably self-power themselves and having a single treatment method. A large amount of wound exudate cannot be discharged in time, aggravating the wound's inflammatory response, and cannot effectively carry out electro-stimulation-guided cell directional migration, resulting in limited treatment effects. It is difficult to meet the urgent needs of the medical and health field for chronic wound treatment.

[0004] Some scholars use friction nano-generation and piezoelectric nano-generation to convert mechanical energy into electrical energy. The composite nano-generator provides bidirectional pulse electrical stimulation according to the intensity of exercise. The power supply of the dressing depends on exercise, which can easily cause secondary injuries such as tearing and squeezing of the wound, seriously restricting the application effect of electrical stimulation. Other scholars add photoelectric effect materials to the dressing, use external excitation light sources to irradiate to achieve the conversion of light energy into electrical energy, provide unidirectional pulse potential, and use light energy to convert into electrical energy. It needs to rely on external equipment for power supply, and the long-term stable power supply is limited, which reduces its practical application value. Other scholars use magnetron sputtering Zn and Ag electrodes, body fluids as electrolytes, to form primary battery electrical stimulation dressings, and electrospin TPU fibers on commercially available cotton cloth to form a wettability gradient structure to achieve exudate management function. Other scholars have provided a method for preparing Ag / Zn microcurrent medical dressings. The prepared medical dressings can release a voltage of 0.35 to 0.9V in a simulated body fluid environment, accelerate cell migration, promote wound healing, and reduce the healing time of stubborn wounds. However, during the use of zinc / silver microbatteries, due to the redox reaction, the zinc electrode is galvanically corroded, and the silver electrode is protected, so the continuous discharge time is determined by the content of the zinc electrode. For metal microbattery dressings, the potential biosafety risk mainly comes from the metal ions produced in the discharge reaction. If a long-term discharge is required, it means that the concentration of metal ions will increase, which will lead to an increase in biosafety risks. The actual application effect of the dressing will be greatly reduced, and the function is relatively single, lacking the function of exudate moisture absorption and moisturizing.

[0005] Therefore, how to provide a self-generating medical dressing with a self-pumping function is a technical problem to be solved by the present invention. Summary of the invention

[0006] The present invention aims to solve at least one of the above-mentioned technical problems existing in the prior art. To this end, the present invention aims to solve the problems that the existing electrostimulation medical dressings generally have the problem of not being able to simply and stably self-power and having a single treatment method, and proposes a wound in-situ exudate power generation dressing with a self-pumping function based on the hygroelectric effect, which can solve the effective management of wound in-situ power generation and exudate in an integrated manner.

[0007] The present invention also provides a method for preparing a self-generating medical dressing with a self-pumping function.

[0008] By covering the wound with conductive hydrogel, conductive polymer composite membrane, conductive nanofiber membrane and other materials and connecting to an external power source, different forms of electrical stimulation such as DC, pulse, AC, etc. can be directly applied to the wound, which can induce the proliferation and migration of keratinocytes, fibroblasts, and endothelial cells, accelerate wound re-epithelialization, collagen matrix formation, and angiogenesis, and ultimately significantly accelerate wound healing. However, traditional external power supply equipment is bulky and cannot be carried. Electrical stimulation dressings cannot work for a long time. Electrical stimulation is usually applied in a short cycle (<1h / d), which seriously affects the treatment effect. The development of self-powered electrical stimulation dressings has become a research and development trend. In addition, the use of different types of self-powered modules and medical dressings has become a common way to design self-powered electrical stimulation dressings. For example, mechanical energy is converted into electrical energy by using friction nano-generation and piezoelectric nano-generation, and the composite electrical stimulation dressing generates a pulsed AC potential according to the intensity of exercise; by adding materials with photoelectric effect to the dressing, the light energy can be converted into electrical energy by irradiating with an external excitation light source, providing a unidirectional pulse potential; a flexible circuit board is integrated on the surface of the hydrogel, and the wireless radio frequency energy is converted into electrical energy, and a programmed unidirectional pulse potential can be applied to the wound. However, the above-mentioned electrical stimulation dressing depends on conditions such as exercise and external equipment, and the power supply continuity is poor. In addition, the power supply module is separated from the dressing body, resulting in a complicated dressing preparation process, which reduces its practical application value. Furthermore, if the excessive wound exudate of chronic wounds is not discharged in time, it is easy to cause bacterial infection of the wound, inflammatory response and other adverse conditions, resulting in the wound surface not having a good healing microenvironment, and the growth conditions of granulation tissue and epidermal tissue, and the electrical stimulation signal cannot be effectively transmitted to guide the directional migration of cells, resulting in the limited treatment effect of a single means of electrical stimulation. In order to further meet the care needs of chronic wounds, a new self-powered electrical stimulation dressing is needed, which includes functions such as adsorbing exudate, maintaining the wound moistening environment, and electrically stimulating wound healing.

[0009] The first aspect of the present invention provides a self-generating medical dressing with a self-pumping function, comprising a power generation layer and a liquid permeable moisture absorption and moisturizing layer arranged in sequence, wherein the power generation layer comprises a substrate, in which a wet electric effect active substance and an electrode material are distributed.

[0010] One of the technical solutions of the present invention regarding the self-generating medical dressing with self-pump function has at least the following beneficial effects:

[0011] The self-generating medical dressing with self-pumping function of the present invention is composed of a two-layer structure, the bottom layer is a power generation layer, which realizes the self-generating function, and the upper layer is a liquid permeable moisture absorption and moisturizing layer, which realizes the self-pumping function and specifically produces the following technical effects:

[0012] Excellent biocompatibility. Printed biocompatible electrode materials will not cause biological toxicity to wounds. At the same time, there is no electrochemical corrosion reaction between electrodes, and the redox reaction of the electrodes will not cause an increase in metal ion concentration or affect the acid-base balance of the wound, thereby affecting the wound healing effect.

[0013] Efficient exudate management capability. The power generation layer is compounded with the exudate absorbing and moisturizing layer, so that the dressing can actively absorb wound exudate, avoid inflammatory reactions caused by repeated infiltration of exudate, and provide a moist environment conducive to wound healing.

[0014] Suitable for industrial production. The self-generating medical dressing with self-pumping function of the present invention can be prepared by spinning technology and electrode printing technology, both of which have mature industrial production lines. Meltblowing technology is mature and has a fast production speed, while spunbonding has a simple process and high output. The electrospinning production speed is relatively slow, but it can also optimize the overall production efficiency by combining other methods. In addition, the raw materials of the power generation layer are widely selected and low in cost, making it cost-effective.

[0015] According to some embodiments of the present invention, the material of the liquid-permeable moisture-absorbing and moisturizing layer includes at least one of a foam dressing, an alginate dressing, a carboxymethyl cellulose dressing, an activated carbon fiber dressing, a non-woven dressing and a hydrocolloid dressing.

[0016] The power generation layer is compounded with foam, alginate, carboxymethyl cellulose, activated carbon fiber, non-woven fabric or hydrocolloid medical dressings, so that the dressing can actively absorb wound exudate, avoid inflammatory response caused by repeated infiltration of exudate in the wound, and provide a moist environment conducive to wound healing.

[0017] According to some embodiments of the present invention, the material of the substrate includes at least one of PP (polypropylene), PE (polyethylene), PET (polyethylene terephthalate), PA (polyamide), PCL (polycaprolactone), PU (polyurethane), PAN (polyacrylonitrile), PVA (polyvinyl alcohol) and PLA (polylactic acid).

[0018] According to some embodiments of the present invention, the wet electric effect active material includes at least one of GO (graphene oxide), rGO (reduced graphene oxide), PSSA (sulfonated polystyrene acid), CB (carbon black), CNT (carbon nanotube) and graphite.

[0019] According to some embodiments of the present invention, the electrode material includes at least one of CNT (carbon nanotube), CB (carbon black), Ag (silver), Cu (copper), Pt (platinum), Au (gold) and graphite.

[0020] According to some embodiments of the present invention, in the substrate, the mass percentage of the wet electric effect active material is 0.1 to 10 wt %.

[0021] According to some embodiments of the present invention, in the substrate, the mass percentage of the electrode material is 0.1 to 50 wt %.

[0022] According to some embodiments of the present invention, the method for preparing the power generation layer includes: mixing the substrate raw material with the wet electric effect active material, preparing the substrate by meltblowing, spunbond spinning or electrospinning, and printing the electrode material on both sides of the substrate by screen printing.

[0023] According to some embodiments of the present invention, the preparation method of the power generation layer includes: weighing a certain amount of raw material (referring to one of CNT, CB, Ag, Cu, Pt, Au, graphite) powder, dispersing it in at least one of 0.1-100wt% sodium carboxymethyl cellulose (CMC), DMF, ethanol, or Tween dispersion, using ultrasonic dispersion for 5-30 minutes, adding acrylic resin liquid (as a binder, playing a bonding role) and magnetically stirring for 1-2 hours, and finally adding sodium alginate (as a thickener, playing a role in adjusting viscosity) and magnetically stirring for 1-2 hours. The formula ratio of the electrode material is 30-90% dispersion, 0.1-50% raw material powder, 10-20% acrylic resin, and 2-5% sodium alginate. The electrode material is screen-printed on both sides of the non-woven fabric to form a power generation layer.

[0024] According to some embodiments of the present invention, the melt-blowing spinning method can be: weigh a certain amount of high molecular polymer and wet electric effect active substance, mix them in proportion, and then put them into an extruder to melt them. The melt is extruded through a spinneret and stretched into ultrafine fibers by high-temperature air jet, and then solidified to form a non-woven fabric. The polymer particle mixing ratio ranges from 90 to 99.9%, the wet electric effect active substance mixing ratio ranges from 0.1 to 10%, the extrusion temperature is 150 to 300°C, the extruder pressure is 5 to 50 MPa, the air temperature is 100 to 350°C, the melt flow rate is 1 to 1000 kg / h, and the spinneret aperture is 0.1 to 1 mm.

[0025] According to some embodiments of the present invention, the spunbond spinning method can be: weigh a certain amount of high molecular polymer and wet electric effect active substance, mix them in proportion, and put them into an extruder to melt them. The melt is extruded through a spinneret and then cooled and solidified, and the fibers are stretched by a high-speed stretching device to form a non-woven fabric. The polymer particle mixing ratio ranges from 90 to 99.9%, the wet electric effect active substance mixing ratio ranges from 0.1 to 10%, the extrusion temperature is 150 to 300°C, the extruder pressure is 5 to 50 MPa, the melt flow rate is 1 to 1000 kg / h, the spinneret aperture is 0.1 to 1 mm, and the stretching speed is 1000 to 5000 m / min.

[0026] According to some embodiments of the present invention, the electrospinning method can be: weigh a certain amount of high molecular polymer and wet electric effect active substance, dissolve in at least one of DMF, DCM or DMSO solvent, and stir continuously for 4 to 24 hours at room temperature with a magnetic stirrer to obtain a spinning solution with a concentration of 5 to 30 wt% high molecular polymer (0.1 to 10 wt% active substance). The spinning solution is injected into a syringe, and a 10 to 30G metal pillow is used for spinning, the DC positive voltage is 1 to 50 kV, the DC negative voltage is 1 to 50 kV, the spinning solution flow rate is 0.01 to 10 mL / h, and the distance from the nozzle to the receiver is 5 to 30 cm.

[0027] The second aspect of the present invention provides a method for preparing the self-generating medical dressing of the first aspect of the present invention, comprising the step of bonding the power generation layer and the liquid permeable moisture absorption and moisturizing layer by thermal bonding or chemical bonding.

[0028] A technical solution in the method for preparing a self-generating medical dressing of the present invention has at least the following beneficial effects:

[0029] The preparation method of the present invention does not require expensive equipment and complicated process control, has undemanding reaction conditions, has readily available raw materials, has low production costs, and is easy to industrialize. BRIEF DESCRIPTION OF THE DRAWINGS

[0030] Figure 1 This is one of the SEM images of the Janus nonwoven fabric prepared by the electrospinning technology in this example.

[0031] Figure 2 This is the second SEM image of the Janus nonwoven fabric prepared by the electrospinning technology in this example.

[0032] Figure 3 This is one of the SEM images of the two sides of the power generation layer prepared by the electrospinning technology in this embodiment.

[0033] Figure 4 This is the second SEM image of the two sides of the power generation layer prepared by the electrospinning technology in this embodiment.

[0034] Figure 5 This is a cross-sectional SEM image of the composite of the power generation layer and PU foam dressing prepared by the electrospinning technology in this embodiment.

[0035] Figure 6 This is the voltage output performance of E-PGP prepared by electrospinning technology in this example.

[0036] Figure 7 It is one of the moisture absorption and moisturizing properties of the self-generating medical dressing PE-PGP with self-pumping function.

[0037] Figure 8 The second is the moisture absorption and moisturizing properties of the self-generating medical dressing PE-PGP with self-pumping function.

[0038] Fig. 9 The third is the moisture absorption and moisturizing property of the self-generating medical dressing PE-PGP with self-pumping function.

[0039] Fig.10 It is one of the CCK-8 methods to evaluate the biocompatibility of PGP, E-PGP, and PU moisture-absorbing and moisturizing layers.

[0040] Fig.11 This is the second part of the CCK-8 method to evaluate the biocompatibility of PGP, E-PGP, and PU moisture-absorbing and moisturizing layers.

[0041] Fig.12 This is one of the healing effects of PGP and E-PGP in the in vitro L929 cell scratch experiment.

[0042] Fig.13 This is the second healing effect of PGP and E-PGP in the in vitro L929 cell scratch experiment.

[0043] Fig.14 This is one of the wound healing effects of PGP, E-PGP, and PE-PGP in vivo.

[0044] Fig.15 This is the second in vivo wound healing effect of PGP, E-PGP, and PE-PGP.

[0045] Fig.16 This is one of the analysis figures of the epidermal regeneration effect of PGP, E-PGP, and PE-PGP wound tissue sections stained with H&E.

[0046] Fig.17 This is the second analysis diagram of the epidermal regeneration effect of PGP, E-PGP, and PE-PGP wound tissue sections stained with H&E.

[0047] Fig.18 It is one of the effects of Masson staining to analyze collagen deposition in wound tissue.

[0048] Fig.19 This is the second analysis of the collagen deposition effect in wound tissue using Masson staining. DETAILED DESCRIPTION

[0049] The following are specific embodiments of the present invention, and the technical solutions of the present invention are further described in conjunction with the embodiments, but the present invention is not limited to these embodiments.

[0050] In the first aspect, some embodiments of the present invention provide a self-generating medical dressing with a self-pumping function, comprising a power generation layer and a liquid permeable moisture absorption and moisturizing layer arranged in sequence, wherein the power generation layer comprises a substrate, in which a hygroscopic electric effect active substance and an electrode material are distributed.

[0051] It can be understood that the self-generating medical dressing with self-pumping function of the present invention is composed of a two-layer structure, the bottom layer is a power generation layer, which realizes the self-generating function, and the upper layer is a liquid permeable moisture absorption and moisturizing layer, which realizes the self-pumping function and specifically produces the following technical effects:

[0052] Excellent biocompatibility. Printed biocompatible electrode materials will not cause biological toxicity to wounds. At the same time, there is no electrochemical corrosion reaction between electrodes, and the redox reaction of the electrodes will not cause an increase in metal ion concentration or affect the acid-base balance of the wound, thereby affecting the wound healing effect.

[0053] Efficient exudate management capability. The power generation layer is compounded with the exudate absorbing and moisturizing layer, so that the dressing can actively absorb wound exudate, avoid inflammatory reactions caused by repeated infiltration of exudate, and provide a moist environment conducive to wound healing.

[0054] Suitable for industrial production. The self-generating medical dressing with self-pumping function of the present invention can be produced by spinning technology and electrode printing technology, both of which have mature industrial production lines. Melt-blowing technology is mature and has a fast production speed, while spunbonding has a simple process and high output. The electrospinning production speed is relatively slow, but it can also optimize the overall production efficiency by combining other methods. In addition, the raw materials of the power generation layer are widely selected and low in cost, making it cost-effective.

[0055] In combination with the first aspect, in some embodiments of the present invention, the material of the liquid-permeable moisture-absorbing and moisturizing layer includes at least one of a foam dressing, an alginate dressing, a carboxymethyl cellulose dressing, an activated carbon fiber dressing, a non-woven dressing and a hydrocolloid dressing.

[0056] The power generation layer is compounded with foam dressings, alginate dressings, carboxymethyl cellulose dressings, activated carbon fiber dressings, non-woven dressings or hydrocolloid dressings, so that the dressings can actively absorb wound exudate, avoid inflammatory reactions caused by repeated infiltration of exudate in the wound, and provide a moist environment conducive to wound healing.

[0057] In combination with the first aspect, in some embodiments of the present invention, the material of the substrate includes at least one of PP (polypropylene), PE (polyethylene), PET (polyethylene terephthalate), PA (polyamide), PCL (polycaprolactone), PU (polyurethane), PAN (polyacrylonitrile), PVA (polyvinyl alcohol) and PLA (polylactic acid).

[0058] In combination with the first aspect, in some embodiments of the present invention, the wet electric effect active material includes at least one of GO (graphene oxide), rGO (reduced graphene oxide), PSSA (sulfonated polystyrene acid), CB (carbon black), CNT (carbon nanotube) and graphite.

[0059] In combination with the first aspect, in some embodiments of the present invention, the electrode material includes at least one of CNT, CB, Ag, Cu, Pt, Au and graphite.

[0060] In combination with the first aspect, in some embodiments of the present invention, the mass percentage of the wet electric effect active material in the substrate is 0.1-10 wt %.

[0061] In combination with the first aspect, in some embodiments of the present invention, the mass percentage of the electrode material in the substrate is 0.1 to 50 wt %.

[0062] In combination with the first aspect, in some embodiments of the present invention, the method for preparing the power generation layer includes: mixing the substrate raw material with the wet electric effect active substance, preparing the substrate by meltblowing spinning, spunbond spinning or electrospinning, and printing the electrode material on both sides of the substrate by screen printing.

[0063] In combination with the first aspect, in some embodiments of the present invention, the preparation method of the power generation layer includes: weighing a certain amount of raw material (referring to one of CNT, CB, Ag, Cu, Pt, Au, graphite) powder, dispersing it in at least one of 0.1-100wt% sodium carboxymethyl cellulose (CMC), DMF, ethanol, or Tween dispersion, using ultrasonic dispersion for 5-30 minutes, adding acrylic resin liquid (as a binder, playing a bonding role) and magnetically stirring for 1-2 hours, and finally adding sodium alginate (as a thickener, playing a role in adjusting viscosity) and magnetically stirring for 1-2 hours. The formula ratio of the electrode material is 30-90% of the dispersion, 0.1-50% of the raw material powder, 10-20% of the acrylic resin, and 2-5% of the sodium alginate. The electrode material is screen-printed on both sides of the non-woven fabric to form a power generation layer.

[0064] In combination with the first aspect, in some embodiments of the present invention, the melt-blowing spinning method can be: weigh a certain amount of high molecular polymer and wet electric effect active substance, mix them in proportion, and put them into an extruder to melt them. The melt is extruded through a spinneret and stretched into ultrafine fibers by high-temperature air jet, and a non-woven fabric is formed after solidification. The polymer particle mixing ratio ranges from 90 to 99.9%, the wet electric effect active substance mixing ratio ranges from 0.1 to 10%, the extrusion temperature is 150 to 300°C, the extruder pressure is 5 to 50MPa, the air temperature is 100 to 350°C, the melt flow rate is 1 to 1000kg / h, and the spinneret aperture is 0.1 to 1mm.

[0065] In combination with the first aspect, in some embodiments of the present invention, the spunbond spinning method can be: weigh a certain amount of high molecular polymer and wet electric effect active substance, mix them in proportion, and put them into an extruder to melt them. The melt is extruded through a spinneret and then cooled and solidified, and the fibers are stretched by a high-speed stretching device to form a non-woven fabric. The polymer particle mixing ratio ranges from 90 to 99.9%, the wet electric effect active substance mixing ratio ranges from 0.1 to 10%, the extrusion temperature is 150 to 300°C, the extruder pressure is 5 to 50MPa, the melt flow rate is 1 to 1000kg / h, the spinneret aperture is 0.1 to 1mm, and the stretching speed is 1000 to 5000m / min.

[0066] In combination with the first aspect, in some embodiments of the present invention, the electrospinning method can be: weigh a certain amount of high molecular polymer and wet electric effect active substance, dissolve in at least one of DMF, DCM or DMSO solvent, and stir continuously for 4 to 24 hours at room temperature with a magnetic stirrer to obtain a spinning solution with a concentration of 5 to 30 wt% high molecular polymer (0.1 to 10 wt% active substance). Inject the spinning solution into a syringe, use a 10 to 30G metal pillow for spinning, the DC positive voltage is 1 to 50 kV, the DC negative voltage is 1 to 50 kV, the spinning solution flow rate is 0.01 to 10 mL / h, preferably 1 to 2 mL / h, and the distance from the nozzle to the receiver is 5 to 30 cm.

[0067] In a second aspect, some embodiments of the present invention provide a method for preparing the self-generating medical dressing of the first aspect of the present invention, comprising the step of bonding the power generation layer and the liquid permeable moisture absorption and moisturizing layer by thermal bonding or chemical bonding.

[0068] It can be understood that the preparation method of the present invention does not require expensive equipment and complex process control, the reaction conditions are not harsh, the raw materials are easily available, the production cost is low, and it is easy to industrialize production.

[0069] The following will be combined with the embodiments to clearly and completely describe the concept of the present invention and the technical effects produced, so as to fully understand the purpose, characteristics and effects of the present invention. Obviously, the described embodiments are only part of the embodiments of the present invention, not all of them. Based on the embodiments of the present invention, other embodiments obtained by those skilled in the art without creative work are all within the scope of protection of the present invention.

[0070] In the description of the present invention, the description with reference to the terms "one embodiment", "some embodiments", "illustrative embodiments", "examples", "specific examples", or "some examples" means that the specific features, structures, materials or characteristics described in conjunction with the embodiment or example are included in at least one embodiment or example of the present invention. In this specification, the schematic representation of the above terms does not necessarily refer to the same embodiment or example. Moreover, the specific features, structures, materials or characteristics described may be combined in any one or more embodiments or examples in a suitable manner.

[0071] Unless otherwise specified, "room temperature" in the present invention means 25°C±5°C.

[0072] Unless otherwise specified, "about" in the present invention means that the allowable error is within ±2%.

[0073] If the specific conditions are not specified in the examples, the experiments were carried out under conventional conditions or conditions recommended by the manufacturer. If the manufacturers of the reagents or instruments are not specified, they are all conventional products that can be purchased commercially.

[0074] Example 1

[0075] Provided is a self-generating medical dressing with a self-pumping function, which consists of a two-layer structure, including a power generation layer and a liquid permeable moisture absorption and moisturizing layer arranged in sequence, wherein the power generation layer includes a substrate, in which a hygroscopic electric effect active substance and an electrode material are distributed.

[0076] The material of the exudate-absorbing and moisturizing layer is foam dressing.

[0077] The materials of the substrate are PAN and PCL.

[0078] The active material of the wet electric effect is GO.

[0079] The electrode materials are CNT and Ag.

[0080] In the substrate, the mass percentage of the wet electric effect active material is 0.5wt%.

[0081] In the substrate, the mass percentages of the electrode materials are 2%wtCNT and 20%wtAg.

[0082] The preparation method of the power generation layer includes: mixing the substrate raw material with the wet electric effect active material, preparing the substrate by electrostatic spinning, and printing the electrode material on both sides of the substrate by screen printing.

[0083] The specific process of electrospinning is as follows: PAN powder and graphene oxide powder are weighed, dissolved in DMF solvent, and stirred continuously for 12 hours at room temperature with a magnetic stirrer to obtain a spinning solution with a concentration of 10wt% PAN (0.5wt% GO); PCL particles are weighed and dissolved in a mixed solvent of DCM and DMF (mass ratio of 8:2), and stirred continuously for 12 hours at room temperature with a magnetic stirrer to obtain a PCL spinning solution with a concentration of 12wt%. The spinning solution is injected into a syringe, and a 21G metal needle is used for double nozzle spinning, with a DC positive voltage of 12kV and a DC negative voltage of 3kV.

[0084] The flow rate of the spinning solution of 10 wt% PAN (0.5 wt% GO) was 1 mL / h.

[0085] The flow rate of 12wt% PCL spinning solution is 1mL / h~2mL / h (double-nozzle spinning is carried out in the same direction, the spinning speed is 1mL / h, and it is adjusted to 2mL / h as the spinning process proceeds). The diameter of the fiber is controlled by adjusting the propulsion speed of the spinning solution. The greater the propulsion speed, the thicker the diameter of the nanofiber. The composition ratio of the two fibers changes in a gradient, and the diameter and pore size also change in a gradient.

[0086] The distance from the nozzle to the receiver is 15 cm.

[0087] The preparation method of the electrode material is as follows: weigh the carbon nanotube powder, disperse it in a 1wt% sodium carboxymethyl cellulose (CMC) dispersion, use ultrasonic dispersion for 5 minutes, add acrylic resin liquid and stir magnetically for 1 hour, and finally add sodium alginate and stir magnetically for 2 hours. The formula ratio of the electrode material is 78% dispersion, 2% carbon nanotube powder, 17.5% acrylic resin, and 2.5% sodium alginate; weigh a certain amount of silver powder, disperse it in a 2.5wt% Tween dispersion, use ultrasonic dispersion for 30 minutes, add acrylic resin liquid and stir magnetically for 1 hour, and finally add sodium alginate and stir magnetically for 2 hours. The formula ratio of the electrode material is 63% dispersion, 20% raw material powder, 15% acrylic resin, and 2% sodium alginate. The electrode material is screen-printed on both sides of the non-woven fabric to form a power generation layer.

[0088] The preparation method of the self-generating medical dressing is as follows: the power generation layer and the liquid-permeable moisture absorption and moisturizing layer are bonded together by medical glue.

[0089] Example 2

[0090] Provided is a self-generating medical dressing with a self-pumping function, which consists of a two-layer structure, including a power generation layer and a liquid permeable moisture absorption and moisturizing layer arranged in sequence, wherein the power generation layer includes a substrate, in which a hygroscopic electric effect active substance and an electrode material are distributed.

[0091] The material of the exudate-absorbing and moisturizing layer is foam dressing.

[0092] The material of the base material is PP.

[0093] The active material of the wet electric effect is GO.

[0094] The electrode materials are CNT and Ag.

[0095] In the substrate, the mass percentage of the wet electric effect active material is 1.0 wt %.

[0096] In the substrate, the mass percentages of the electrode materials are 2%wtCNT and 20%wtAg.

[0097] The preparation method of the power generation layer includes: mixing the substrate raw material with the wet electric effect active material, preparing the substrate by melt-blowing spinning, and printing the electrode material on both sides of the substrate by screen printing.

[0098] The specific process of melt-blown spinning is as follows: weigh a certain amount of PP particles and graphene oxide powder, pre-mix them in a ratio of 99:1, and put them into the extruder. The melt is extruded through the spinneret and stretched to ultrafine fibers by high-temperature air jet, and then solidified to form PP-GO non-woven fabric; weigh a certain amount of PP particles, put them into the extruder to make the melt extruded through the spinneret and stretched to ultrafine fibers by high-temperature air jet, and then solidified to form PP non-woven fabric. The extrusion temperature is 160°C, the extruder pressure is 5Mpa, the melt flow rate is 20kg / h, the spinneret aperture is 0.2mm, and the air temperature is 250°C. Finally, the PP-GO non-woven fabric is compounded with the PP non-woven fabric by hot pressing at 160°C for 30s.

[0099] The preparation method of the electrode material is as follows: weigh the carbon nanotube powder, disperse it in a 1wt% sodium carboxymethyl cellulose (CMC) dispersion, use ultrasonic dispersion for 5 minutes, add acrylic resin liquid and stir magnetically for 1 hour, and finally add sodium alginate and stir magnetically for 2 hours. The formula ratio of the electrode material is 78% dispersion, 2% carbon nanotube powder, 17.5% acrylic resin, and 2.5% sodium alginate; weigh a certain amount of silver powder, disperse it in a 2.5wt% Tween dispersion, use ultrasonic dispersion for 30 minutes, add acrylic resin liquid and stir magnetically for 1 hour, and finally add sodium alginate and stir magnetically for 2 hours. The formula ratio of the electrode material is 63% dispersion, 20% raw material powder, 15% acrylic resin, and 2% sodium alginate. The electrode material is screen-printed on both sides of the non-woven fabric to form a power generation layer.

[0100] The preparation method of the self-generating medical dressing is as follows: the power generation layer and the liquid-permeable moisture absorption and moisturizing layer are bonded together by medical glue.

[0101] Example 3

[0102] Provided is a self-generating medical dressing with a self-pumping function, which consists of a two-layer structure, including a power generation layer and a liquid permeable moisture absorption and moisturizing layer arranged in sequence, wherein the power generation layer includes a substrate, in which a hygroscopic electric effect active substance and an electrode material are distributed.

[0103] The material of the exudate-absorbing and moisturizing layer is foam dressing.

[0104] The material of the base material is PP.

[0105] The active material of the wet electric effect is GO.

[0106] The electrode materials are CNT and Ag.

[0107] In the substrate, the mass percentage of the wet electric effect active material is 1.0 wt %.

[0108] In the substrate, the mass percentages of the electrode materials are 2%wtCNT and 20%wtAg.

[0109] The preparation method of the power generation layer includes: mixing the substrate raw material with the wet electric effect active material, preparing the substrate by spunbonding and spinning, and printing the electrode material on both sides of the substrate by screen printing.

[0110] The specific process of spunbond spinning is as follows: weigh a certain amount of polypropylene (PP) and graphene oxide (GO), mix them in a ratio of 99:1 and put them into the extruder. The melt is extruded through the spinning assembly and then cooled and solidified. The fiber is stretched by a high-speed stretching device to form a PP-GO non-woven fabric; weigh a certain amount of PP particles, put them into the extruder to make the melt extruded through the spinning assembly and then cooled and solidified. The fiber is stretched by a high-speed stretching device to form a PP non-woven fabric. The extrusion temperature is 160°C, the extruder pressure is 5Mpa, the spinning assembly aperture is 0.3mm, the melt flow rate is 20kg / h, and the stretching speed is 1000m / min. Finally, the PP-GO non-woven fabric is compounded with the PP non-woven fabric by hot pressing at 160°C for 30s.

[0111] The preparation method of the electrode material is as follows: weigh the carbon nanotube powder, disperse it in a 1wt% sodium carboxymethyl cellulose (CMC) dispersion, use ultrasonic dispersion for 5 minutes, add acrylic resin liquid and stir magnetically for 1 hour, and finally add sodium alginate and stir magnetically for 2 hours. The formula ratio of the electrode material is 78% dispersion, 2% carbon nanotube powder, 17.5% acrylic resin, and 2.5% sodium alginate; weigh a certain amount of silver powder, disperse it in a 2.5wt% Tween dispersion, use ultrasonic dispersion for 30 minutes, add acrylic resin liquid and stir magnetically for 1 hour, and finally add sodium alginate and stir magnetically for 2 hours. The formula ratio of the electrode material is 63% dispersion, 20% raw material powder, 15% acrylic resin, and 2% sodium alginate. The electrode material is screen-printed on both sides of the non-woven fabric to form a power generation layer.

[0112] The preparation method of the self-generating medical dressing is as follows: the power generation layer and the liquid-permeable moisture absorption and moisturizing layer are bonded together by medical glue.

[0113] The self-generating medical dressing prepared in Example 1 was characterized and tested.

[0114] Figure 1 and Figure 2 This is a SEM image of the Janus nonwoven fabric prepared by electrospinning technology in Example 1. The substrate materials are PAN and PCL, and the loaded wet electric effect active material is GO. The nonwoven fabric is hereinafter referred to as PGP.

[0115] from Figure 1 It can be seen that the PAN-GO fibers have a thinner diameter and smaller pore size.

[0116] from Figure 2 It can be seen that the PCL fibers have thicker diameters and larger pore sizes.

[0117] Figure 3 and Figure 4 The SEM images of the two sides of the power generation layer prepared by electrospinning technology in Example 1. The CNT electrode is printed on the PCL surface, and the Ag electrode is printed on the PAN-GO surface. The power generation layer is hereinafter referred to as E-PGP.

[0118] from Figure 3 It can be seen that the pore size and fiber morphology of the non-woven fabric did not change significantly after printing the CNT electrode.

[0119] from Figure 4 It can be seen that the pore size and fiber morphology of the non-woven fabric did not change significantly after printing the Ag electrode.

[0120] Figure 5 This is a cross-sectional SEM image of the composite of the power generation layer and the PU foam dressing prepared by the electrospinning technology in Example 1. Hereinafter, the self-generating medical dressing with self-pumping function is referred to as PE-PGP.

[0121] from Figure 5 It can be seen that the PU foam layer contains a large number of micro-nano pores of different sizes, and the two layers of film are tightly fitted without any stratification.

[0122] Figure 6 The voltage output performance of E-PGP prepared by electrospinning technology in Example 1.

[0123] from Figure 6 It can be seen that E-PGP can stably output a low-voltage stable DC potential of 0 to 0.15V for a long period (>12h).

[0124] Figures 7 to 9 The moisture absorption and moisturizing properties of PE-PGP, a self-generating medical dressing with self-pumping function. Figures 7 to 9 It can be seen that after the power generation layer is compounded with the moisture absorption and moisturizing layer, the equilibrium water content of the dressing is close to 90%, and it can absorb nearly 7 times of its own weight in water, and the moisturizing duration is 11 hours.

[0125] Fig.10 and Fig.11 The biocompatibility of PGP, E-PGP, and PU moisture absorption layer was evaluated by CCK-8 method. It can be seen that the cell viability of all experimental groups was above 80%, proving that the dressings have good cell compatibility.

[0126] Fig.12 and Fig.13 The healing effect of PGP and E-PGP in the L929 cell scratch test in vitro. It can be seen that the scratch healing rate of E-PGP within 24 hours is as high as 93.9%.

[0127] Fig.14 and Fig.15 The in vivo wound healing effects of PGP, E-PGP, and PE-PGP are shown. It can be seen that on the 14th day, the wounds of the PE-PGP group were almost completely healed, with a wound healing rate of 98.4%, which was significantly higher than that of the control group (82.0%), the PGP group (84.1%), and the E-PGP group (95.4%).

[0128] Fig.16 and Fig.17 Analysis of the epidermal regeneration effect of PGP, E-PGP, and PE-PGP wound tissue sections stained with H&E. It can be seen that on the 14th day, the E-PGP group and the PE-PGP group formed a completely restored thin epidermis, and the number of attachments (glands, hair follicles) accompanying the skin tissue in the PE-PGP group was the largest.

[0129] Fig.18 and Fig.19Masson staining was used to analyze the collagen deposition effect in wound tissue. After 14 days, the collagen fibers in the E-PGP and PE-PGP groups were closely arranged to form a regular, orderly and high-density collagen network, with collagen volume ratios as high as 62.8% and 69.6%, while that in the control group was only 38.4%.

[0130] It should also be emphasized that in the preparation process of the present invention, meltblowing, spunbonding or electrostatic spinning technology is selected to blend non-woven fabrics loaded with wet electric effect active substances in different proportions. The biocompatible electrode material is printed on the front and back of the non-woven fabric using screen printing technology. When wound exudate flows through the micro-nano channels in the non-woven fabric, a double electric layer is formed on both sides of the channel. Under the action of the double electric layer, anions and cations are separated, and counterions are transported downstream under capillary action to form a flowing current. Since the non-woven fabric is loaded with wet electric effect active substances, the oxygen-containing functional groups dissociate a large number of mobile carriers after absorbing moisture, thereby improving the voltage output performance.

[0131] The present invention has been described in detail above in conjunction with the embodiments, but the present invention is not limited to the above embodiments, and various changes can be made within the knowledge scope of ordinary technicians in the relevant technical field without departing from the purpose of the present invention.

Claims

1. A self-generating medical dressing with self-pumping function, characterized in that: The invention comprises a power generation layer and a liquid permeable moisture absorption and moisture retention layer which are arranged in sequence. The power generation layer comprises a substrate in which wet electric effect active substances and electrode materials are distributed.

2. The self-generating medical dressing according to claim 1, characterized in that: The material of the liquid-permeable moisture-absorbing and moisturizing layer includes at least one of a foam dressing, an alginate dressing, a carboxymethyl cellulose dressing, an activated carbon fiber dressing, a non-woven dressing and a hydrocolloid dressing.

3. The self-generating medical dressing according to claim 1, characterized in that: The material of the substrate includes at least one of PP, PE, PET, PA, PCL, PU, ​​PAN, PVA and PLA.

4. The self-generating medical dressing according to claim 1, characterized in that: The wet electric effect active material includes at least one of GO, rGO, PSSA, CB, CNT and graphite.

5. The self-generating medical dressing according to claim 1, characterized in that: The electrode material includes at least one of CNT, CB, Ag, Cu, Pt, Au and graphite.

6. The self-generating medical dressing according to any one of claims 1 to 5, characterized in that: In the substrate, the mass percentage of the wet electric effect active material is 0.1 to 10 wt %.

7. The self-generating medical dressing according to any one of claims 1 to 5, characterized in that: In the substrate, the mass percentage of the electrode material is 0.1 to 50 wt %.

8. The self-generating medical dressing according to any one of claims 1 to 5, characterized in that: The preparation method of the power generation layer comprises: mixing the substrate raw material with the wet electric effect active material, preparing the substrate by melt-blowing spinning, spunbond spinning or electrostatic spinning, and printing the electrode material on both sides of the substrate by screen printing.

9. A method for preparing the self-generating medical dressing according to any one of claims 1 to 8, characterized in that: The method comprises the steps of bonding the power generation layer and the liquid permeable moisture absorption and moisture retaining layer by means of thermal bonding or chemical bonding.

Images