WO2015103988A1 - 一种药用敷料水凝胶复合织物及其制备方法和应用 - Google Patents

一种药用敷料水凝胶复合织物及其制备方法和应用 Download PDF

Info

Publication number
WO2015103988A1
WO2015103988A1 PCT/CN2015/070378 CN2015070378W WO2015103988A1 WO 2015103988 A1 WO2015103988 A1 WO 2015103988A1 CN 2015070378 W CN2015070378 W CN 2015070378W WO 2015103988 A1 WO2015103988 A1 WO 2015103988A1
Authority
WO
WIPO (PCT)
Prior art keywords
composite fabric
hydrogel composite
medicinal
dressing hydrogel
isopropylacrylamide
Prior art date
Application number
PCT/CN2015/070378
Other languages
English (en)
French (fr)
Inventor
韩晋
袁海龙
徐和
徐平华
申宝德
Original Assignee
中国人民解放军第三0二医院
Priority date (The priority date is an assumption and is not a legal conclusion. Google has not performed a legal analysis and makes no representation as to the accuracy of the date listed.)
Filing date
Publication date
Application filed by 中国人民解放军第三0二医院 filed Critical 中国人民解放军第三0二医院
Priority to CN201580000491.2A priority Critical patent/CN105228658B/zh
Publication of WO2015103988A1 publication Critical patent/WO2015103988A1/zh

Links

Classifications

    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61L—METHODS OR APPARATUS FOR STERILISING MATERIALS OR OBJECTS IN GENERAL; DISINFECTION, STERILISATION OR DEODORISATION OF AIR; CHEMICAL ASPECTS OF BANDAGES, DRESSINGS, ABSORBENT PADS OR SURGICAL ARTICLES; MATERIALS FOR BANDAGES, DRESSINGS, ABSORBENT PADS OR SURGICAL ARTICLES
    • A61L15/00—Chemical aspects of, or use of materials for, bandages, dressings or absorbent pads
    • A61L15/16—Bandages, dressings or absorbent pads for physiological fluids such as urine or blood, e.g. sanitary towels, tampons
    • A61L15/22—Bandages, dressings or absorbent pads for physiological fluids such as urine or blood, e.g. sanitary towels, tampons containing macromolecular materials
    • A61L15/28—Polysaccharides or their derivatives
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61L—METHODS OR APPARATUS FOR STERILISING MATERIALS OR OBJECTS IN GENERAL; DISINFECTION, STERILISATION OR DEODORISATION OF AIR; CHEMICAL ASPECTS OF BANDAGES, DRESSINGS, ABSORBENT PADS OR SURGICAL ARTICLES; MATERIALS FOR BANDAGES, DRESSINGS, ABSORBENT PADS OR SURGICAL ARTICLES
    • A61L15/00—Chemical aspects of, or use of materials for, bandages, dressings or absorbent pads
    • A61L15/16—Bandages, dressings or absorbent pads for physiological fluids such as urine or blood, e.g. sanitary towels, tampons
    • A61L15/42—Use of materials characterised by their function or physical properties
    • A61L15/44—Medicaments
    • C—CHEMISTRY; METALLURGY
    • C08—ORGANIC MACROMOLECULAR COMPOUNDS; THEIR PREPARATION OR CHEMICAL WORKING-UP; COMPOSITIONS BASED THEREON
    • C08B—POLYSACCHARIDES; DERIVATIVES THEREOF
    • C08B15/00—Preparation of other cellulose derivatives or modified cellulose, e.g. complexes
    • C08B15/05—Derivatives containing elements other than carbon, hydrogen, oxygen, halogens or sulfur
    • C08B15/06—Derivatives containing elements other than carbon, hydrogen, oxygen, halogens or sulfur containing nitrogen, e.g. carbamates
    • C—CHEMISTRY; METALLURGY
    • C08—ORGANIC MACROMOLECULAR COMPOUNDS; THEIR PREPARATION OR CHEMICAL WORKING-UP; COMPOSITIONS BASED THEREON
    • C08F—MACROMOLECULAR COMPOUNDS OBTAINED BY REACTIONS ONLY INVOLVING CARBON-TO-CARBON UNSATURATED BONDS
    • C08F220/00—Copolymers of compounds having one or more unsaturated aliphatic radicals, each having only one carbon-to-carbon double bond, and only one being terminated by only one carboxyl radical or a salt, anhydride ester, amide, imide or nitrile thereof
    • C08F220/02—Monocarboxylic acids having less than ten carbon atoms; Derivatives thereof
    • C08F220/52—Amides or imides
    • C08F220/54—Amides, e.g. N,N-dimethylacrylamide or N-isopropylacrylamide
    • C—CHEMISTRY; METALLURGY
    • C08—ORGANIC MACROMOLECULAR COMPOUNDS; THEIR PREPARATION OR CHEMICAL WORKING-UP; COMPOSITIONS BASED THEREON
    • C08F—MACROMOLECULAR COMPOUNDS OBTAINED BY REACTIONS ONLY INVOLVING CARBON-TO-CARBON UNSATURATED BONDS
    • C08F251/00—Macromolecular compounds obtained by polymerising monomers on to polysaccharides or derivatives thereof
    • C08F251/02—Macromolecular compounds obtained by polymerising monomers on to polysaccharides or derivatives thereof on to cellulose or derivatives thereof
    • C—CHEMISTRY; METALLURGY
    • C08—ORGANIC MACROMOLECULAR COMPOUNDS; THEIR PREPARATION OR CHEMICAL WORKING-UP; COMPOSITIONS BASED THEREON
    • C08L—COMPOSITIONS OF MACROMOLECULAR COMPOUNDS
    • C08L1/00—Compositions of cellulose, modified cellulose or cellulose derivatives
    • C08L1/08—Cellulose derivatives
    • C—CHEMISTRY; METALLURGY
    • C08—ORGANIC MACROMOLECULAR COMPOUNDS; THEIR PREPARATION OR CHEMICAL WORKING-UP; COMPOSITIONS BASED THEREON
    • C08L—COMPOSITIONS OF MACROMOLECULAR COMPOUNDS
    • C08L5/00—Compositions of polysaccharides or of their derivatives not provided for in groups C08L1/00 or C08L3/00
    • C08L5/04—Alginic acid; Derivatives thereof
    • C—CHEMISTRY; METALLURGY
    • C08—ORGANIC MACROMOLECULAR COMPOUNDS; THEIR PREPARATION OR CHEMICAL WORKING-UP; COMPOSITIONS BASED THEREON
    • C08L—COMPOSITIONS OF MACROMOLECULAR COMPOUNDS
    • C08L51/00—Compositions of graft polymers in which the grafted component is obtained by reactions only involving carbon-to-carbon unsaturated bonds; Compositions of derivatives of such polymers
    • C08L51/02—Compositions of graft polymers in which the grafted component is obtained by reactions only involving carbon-to-carbon unsaturated bonds; Compositions of derivatives of such polymers grafted on to polysaccharides

Definitions

  • the present invention belongs to the technical field of traditional Chinese medicine preparations and preparation methods thereof, and particularly relates to a medical dressing hydrogel composite fabric, a preparation method and application thereof, and is mainly used for hemostasis and tissue repair of various acute and chronic wounds.
  • a hydrogel is a macromolecule having a three-dimensional structure formed by cross-linking between molecules by a hydrophilic polymer compound. Because of the unique hydrophilic structure of the hydrogel polymer, a large amount of moisture can be adsorbed and retained in the hydrogel structure, so that it has good water absorption and water retention properties. Since the British scientist George Winter discovered in 1962 that the moist environment is conducive to wound healing, various new dressings have been developed over the past half century, such as hydrogel dressings, hydrocolloid dressings, mineral dressings and nanotechnology dressings. Wait. Compared with other dressings, hydrogel dressings have unique advantages.
  • Hydrogel dressings can prevent excessive loss of moisture and body fluids and stop bleeding; have good permeability to water and oxygen without allowing bacteria to pass, It can resist the invasion of bacteria and inhibit the growth of bacteria. It has antibacterial and anti-inflammatory functions. It can work well with the wound surface, but it will not adhere to the wound surface to avoid secondary damage caused by changing the dressing. It is moisture-permeable, breathable and makes the wound moist. However, there is no effluent environment, good biocompatibility, and the ability to promote wound healing, which is receiving more and more attention from all countries.
  • Yang Qing et al. Yang Qing, Yan Ying, Zhang Yueting.
  • Hydrogels can be classified into chemical gels and physical gels depending on the manner of cross-linking.
  • the polymer molecular chains of chemical gels are linked by covalent bonds, and the physical gels are combined by non-covalent bonds such as hydrogen bonding, ionic interaction, and hydrophobic interaction.
  • the water absorption of the hydrogel is closely related to the composition, type, link density, and environmental temperature, pH, and ionic strength of the polymer.
  • the particle size of the hydrogel and the size of the micropores contained therein also have an effect on the rate of water absorption.
  • Common hydrogels include polyhydroxyethyl methacrylate, polyhydroxypropyl acrylate, polypyrrolidone, polyacrylic acid, and polyacrylamide.
  • N-isopropylacrylamide-based temperature-sensitive smart hydrogel is a typical heat-shrinkable temperature-sensitive hydrogel that swells or shrinks in response to changes in ambient temperature, the lowest critical solution.
  • the temperature is around 32 °C, close to the surface temperature of the human body, and can be widely used as a medical dressing for tissue repair of body surface wounds.
  • Chitosan has obvious antibacterial effect, and it has obvious inhibitory effects on skin bacteria such as Staphylococcus aureus, Pseudomonas aeruginosa and Streptococcus pyogenes in the human epidermis.
  • chitosan can promote the regeneration of epithelial cells, accelerate the healing of wounds, and improve the quality of wound healing.
  • Chitosan can be degraded into oligosaccharides, oligosaccharides or even monosaccharides, which is beneficial to accelerate cell proliferation and strengthen tissue remodeling.
  • chitosan with different molecular weights has advantages, and the large molecular weight chitosan has good film forming strength, and the small molecular weight chitosan has the characteristics of high biological activity and good water retention, and can be used to prepare excellent performance. Medical dressings.
  • the object of the present invention is to disclose a medicinal dressing hydrogel composite fabric; compared with other dressings, hydrogel composite fabrics have unique advantages as medical dressings, and hydrogel dressings can prevent Excessive loss of moisture and body fluids to stop bleeding; good permeability to water and oxygen without allowing bacteria to pass, can resist bacterial invasion, and inhibit the growth of bacteria, with antibacterial, anti-inflammatory function;
  • the wound surface is well-bonded, but it will not adhere to the wound surface to avoid secondary damage caused by changing the dressing. It is moisture-permeable, breathable and the wound surface is moist but has no effusion environment. It has good biocompatibility and can promote wound healing. .
  • a second object of the present invention is to disclose a method for preparing the above-described medicinal dressing hydrogel composite fabric.
  • a third object of the present invention is to disclose the above-mentioned medicinal dressing hydrogel composite fabric in the preparation of antibacterial anti-inflammatory And the application of the hemostatic drug; the above-mentioned medicinal dressing hydrogel composite fabric as a dressing, some commonly used antibacterial, anti-inflammatory and hemostasis drugs, such as butyl fenfenate, matrine or berberine hydrochloride as active ingredients.
  • a method for preparing a medicinal dressing hydrogel composite fabric comprising the steps of:
  • the cotton cellulose which initiates the reaction in the step (2) is immersed in the solution of the 5 mL step (3) for 30 minutes, and then spread on a dry glass plate and polymerized under nitrogen for 48 hours to obtain poly N-isopropyl.
  • Acrylamide-cotton cellulose
  • step (1) The method for preparing a medicinal dressing hydrogel composite fabric according to the above technical solution, wherein the specific steps of the step (1) are: 0.2 g of ammonium persulfate, 25 mL of N-isopropyl acrylamide and 1.2 g of dimethylformamide was dissolved in 0.1 mol of a nitric acid solution and foamed with nitrogen.
  • a medicinal dressing hydrogel composite fabric wherein the medicinal dressing hydrogel composite fabric is prepared by the preparation method described in the above technical solution.
  • the medicinal dressing hydrogel composite fabric according to the above technical solution wherein the content of N-isopropylacrylamide in the medicinal dressing hydrogel composite fabric is 6% to 30 ⁇ 3 ⁇ 4 by mass.
  • a medicinal dressing hydrogel composite fabric for preparing an antibacterial anti-inflammatory and hemostatic drug, the antibacterial anti-inflammatory and hemostatic drug consisting of a dressing and an active ingredient, wherein the active ingredient is flufenamic acid
  • the dressing is a medicinal dressing hydrogel composite fabric according to the above technical solution.
  • the present invention has the following beneficial effects:
  • the medicinal dressing hydrogel composite fabric of the invention adopts natural biodegradable polymer material, has certain antibacterial and anti-inflammatory effects, has good biocompatibility, and greatly reduces the risk of immune rejection reaction.
  • the medicinal dressing hydrogel composite fabric of the invention is added with drugs, such as butyl fluorofenate, matrine and berberine hydrochloride, etc., so that the hydrogel composite fabric has good antibacterial, anti-inflammatory, hemostasis and It promotes the function of wound healing and avoids the infection in the external environment and dressing process.
  • drugs such as butyl fluorofenate, matrine and berberine hydrochloride, etc.
  • the hydrogel composite fabric has good antibacterial, anti-inflammatory, hemostasis and It promotes the function of wound healing and avoids the infection in the external environment and dressing process.
  • the hydrogel composite fabric has good water absorption and water retention performance, which creates a moist environment for the wound, which is beneficial to wound healing and dressing change.
  • the medicinal dressing hydrogel composite fabric of the present invention is a temperature-sensitive "smart" material, which swells or shrinks due to changes in the temperature of the receptor table, can release the drug slowly, prolongs the drug action cycle, and reduces the frequency of dressing change. The workload is reduced.
  • the preparation process of the medicinal dressing hydrogel composite fabric of the invention is simple and easy, and the reagents and raw materials used are all commercially available and can be continuously produced.
  • FIG. 1 is a swelling kinetic curve of a hydrogel composite fabric at 37 ° C;
  • FIG. 3 is an in vitro release profile of a hydrogel composite fabric.
  • Example 1 Preparation of a medicinal dressing hydrogel composite fabric:
  • the reaction-initiated cotton cellulose was then mixed with 5 mL of N-isopropylacrylamide and dimethylformamide (25 mL of N-isopropylacrylamide and 1.2 g of dimethyl group as a crosslinking agent). After soaking for 30 min in the preparation of the formamide in 0.1 M nitric acid; cotton cellulose was spread on a dry glass plate, and the resulting substrate was polymerized under nitrogen for 48 h. After complete reaction, the product was washed with water to remove surface residues.
  • the clean sample obtained is dried under vacuum at 80 ° C; the principle of washing the water to remove the residue on the surface is that the residue embedded in the hydrogel needs to be repeatedly removed in three swelling and de-swelling cycles, each The aqueous solution is replaced twice; each cycle includes immersion in an aqueous solution at 45 ° C for 2 h and immersion at room temperature for 2 h, that is, at a temperature above or below the minimum critical solution temperature (LCST) of N-isopropyl acrylamide;
  • LCST minimum critical solution temperature
  • the prepared poly-N-isopropylacrylamide-cotton cellulose and a small amount of calcium alginate are dissolved in distilled water to form a hydrosol on the surface layer, and the solvent is removed by a low-pressure rotary evaporator to obtain a medicinal dressing hydrogel composite.
  • the role of calcium alginate in this step is to provide an ion pair for the cross-linking of the hydrogel to form a mesh pore size, and a small amount can promote the effect without a limitation.
  • Example 2 Preparation of a medicinal dressing hydrogel composite fabric:
  • the reaction-initiated cotton cellulose was then mixed with 5 mL of N-isopropylacrylamide and dimethylformamide (25 mL of N-isopropylacrylamide and 1.2 g of dimethyl group as a crosslinking agent). After soaking for 30 min in the preparation of formamide dissolved in 0.1 M nitric acid; cotton cellulose was spread on a dry glass dish; the resulting substrate was in nitrogen The polymerization reaction was carried out under gas conditions for 48 hours. After the complete reaction, the product was washed with water to remove the residue on the surface, and the obtained clean sample was dried under vacuum at 80 ° C; the principle of washing with water to remove the residue on the surface was embedded in water condensation. The residue in the gel needs to be repeatedly removed in three swelling and de-swelling cycles, and the aqueous solution is replaced each time; each cycle includes a 45 °C aqueous solution soak for 2 h and soak at room temperature 2
  • the prepared poly-N-isopropylacrylamide-cotton cellulose and a small amount of calcium alginate are dissolved in a suitable water to form a hydrosol on the surface layer, and the solvent is removed by a low pressure rotary evaporator to obtain a medicinal dressing hydrogel.
  • Composite fabric The role of calcium alginate in this step is to provide an ion pair for the cross-linking of the hydrogel to form a mesh pore size, which can be promoted in a small amount, without limitation.
  • Example 3 Preparation of a medicinal dressing hydrogel composite fabric:
  • the reaction-initiated cotton cellulose was then mixed with 5 mL of N-isopropylacrylamide and dimethylformamide (25 mL of N-isopropylacrylamide and 1.2 g of dimethyl group as a crosslinking agent). After soaking for 30 min in the preparation of the formamide in 0.1 M nitric acid; cotton cellulose was spread on a dry glass plate, and the resulting substrate was polymerized under nitrogen for 48 h. After complete reaction, the product was washed with water to remove surface residues.
  • the clean sample obtained is dried under vacuum at 80 ° C; the principle of washing the water to remove the residue on the surface is that the residue embedded in the hydrogel needs to be repeatedly removed in three swelling and de-swelling cycles, each Replace the aqueous solution twice. Each cycle includes soaking in an aqueous solution at 45 °C for 2 h and soaking at room temperature 2
  • the prepared poly-N-isopropylacrylamide-cotton cellulose and a small amount of sodium alginate are dissolved in a suitable water to form a hydrosol on the surface layer, and the solvent is removed by a low-pressure rotary evaporator to obtain a medicinal dressing hydrogel.
  • the role of calcium alginate in this step is to provide an ion pair for the cross-linking of the hydrogel to form a mesh pore size, which can be promoted in a small amount, without limitation.
  • Example 4 Preparation of a medicinal dressing hydrogel composite fabric:
  • the reaction-initiated cotton cellulose was then mixed with 5 mL of N-isopropylacrylamide and dimethylformamide (25 mL of N-isopropylacrylamide and 1.2 g of dimethyl group as a crosslinking agent). After soaking for 30 min in the preparation of the formamide in 0.1 M nitric acid; cotton cellulose was spread on a dry glass plate, and the resulting substrate was polymerized under nitrogen for 48 h. After complete reaction, the product was washed with water to remove surface residues.
  • the obtained clean sample is dried under vacuum at 80 ° C; wherein the operation of washing with water to remove the residue of the surface is that the residue embedded in the hydrogel needs to be repeatedly removed in three swelling and de-swelling cycles.
  • Each cycle consists of soaking in an aqueous solution at 45 °C for 2 h and soaking for 2 h at room temperature, ie at a temperature above or below the minimum critical solution temperature (LCST) of N-isopropylacrylamide;
  • LCST minimum critical solution temperature
  • the prepared poly-N-isopropylacrylamide-cotton cellulose and a small amount of calcium alginate are dissolved in a suitable water to form a hydrosol on the surface layer, and the solvent is removed by a low-pressure rotary evaporator to obtain a medicinal dressing hydrogel.
  • Composite fabric The role of calcium alginate in this step is to provide an ion pair for the cross-linking of the hydrogel to form a mesh pore size, which can be promoted in a small amount, without limitation.
  • Example S Hydrogel composite fabric of butyl phenanthrate:
  • hydrogel composite fabric prepared in Examples 1-4 was swollen and saturated with a butyl fluoride fentanate solution at 25 ° C, dried, sealed and stored at low temperature.
  • Example 6 Hydrogel composite fabric containing berberine hydrochloride:
  • the hydrogel prepared in Examples 1-4 was swollen with a berberine hydrochloride nanoemulsion solution at 25 ° C, dried, sealed, and stored at low temperature.
  • Real brain I ⁇ Hydrogel composite fabric containing matrine:
  • hydrogel prepared in the preparation of Examples 1-4 was swollen and saturated with a matrine-containing solution at 25 ° C, and dried.
  • Test ride example 1 In vitro antibacterial and anti-inflammatory activity test:
  • the other four groups were given Kaltostat® calcium alginate fiber (positive control group); ordinary gauze and berberine powder (combination group); drug-free hydrogel composite fabric and drug-containing hydrogel composite fabric,
  • the wound was fixed with tape after administration. The drug was changed every 3 days and the animal was sacrificed one week later.
  • the wound skin tissue was removed and fixed with 10% formaldehyde for 24 h, dehydrated, embedded in paraffin, cut into 4 ⁇ sections, stained with HE, and observed by inflammatory cell infiltration and angiogenesis in skin tissue under electron microscope.
  • FIG. 2 shows that the medicated hydrogel composite fabric can effectively treat non-specific inflammatory reactions on the body surface and significantly inhibit infection caused by pathogenic microorganisms introduced during the dressing process, wherein a is a model group and b is normal.
  • Test Example 2 In vitro drug release experiment of hydrogel composite fabric:
  • the in vitro drug release experiment was carried out with 250 mL of physiological saline as the release medium at a temperature of 32 ⁇ 0.5 °C and a rotational speed of lOO r.min -i. Remove 1 mL of release medium at 0, 1, 2, 4, 8, 12, 24, 48, 72 h, and add the same volume of fresh release medium at the same temperature.
  • the hydrogel composite fabric was cumulatively released 46.52% within 24 h, and the results showed that the hydrogel composite fabric carrier had a certain sustained release effect.

Abstract

一种药用敷料水凝胶复合织物及其制备方法和应用。所述制备方法包括，将N-异丙基丙烯酰胺和引发剂用溶剂溶解，用氮气发泡；棉纤维素在引发剂溶液中进行引发反应；引发反应后的棉纤维素在N-异丙基丙烯酰胺和二甲基甲酰胺混合溶液中浸泡，在氮气条件下发生聚合反应得到聚N-异丙基丙烯酰胺-棉纤维素；聚N-异丙基丙烯酰胺-棉纤维素和海藻酸盐溶解在蒸馏水中，在表层形成水凝胶；去除溶剂，得到药用敷料水凝胶复合织物。

Description

说明书 发明名称：一种药用敷料水凝胶复合织物及其制备方法和应用 技术领域
[0001] 本发明属于中药制剂及其制备方法技术领域， 具体涉及一种药用敷料水凝胶复 合织物及其制备方法和应用， 主要用于各种急慢性创伤的止血与组织修复。
背景技术
[0002] 局部创伤及引起的出血、 感染、 溃疡是一种常见伤病， 治疗不当往往会引起伤 口发炎、 化脓， 甚至感染溃疡。 传统方法一般采用无菌纱布及外用抗生素药物 进行处理。 传统的纱布类敷料无法保持创面润湿， 妨碍组织细胞上皮化， 创面 愈合延迟； 敷料纤维易脱落， 造成异物反应， 影响愈合； 创面肉芽组织易长入 敷料的网眼中发生粘连， 换药吋常常破坏新生的上皮和肉芽组织， 引起出血， 这不但不利于伤口的愈合， 而且使病人疼痛难忍； 吸水性不强， 止血效果欠佳 ， 病原体易透过纱布感染伤口； 换药工作量大。
[0003] 水凝胶是由亲水性高分子化合物通过分子之间交叉链接形成的具有三维空间结 构的大分子。 因为水凝胶高分子的特有亲水结构， 大量的水分可以被吸附并保 留在水凝胶结构中， 因此具有良好的吸水保水性能。 自 1962年英国科学家 George Winter发现潮湿的环境有利于创面愈合以来， 在过去的半个世纪各种新式敷料得 到了广泛的发展， 如水凝胶敷料、 水胶体敷料、 矿物质类敷料和纳米技术敷料 等。 与其他敷料相比， 水凝胶敷料具有独特的优势， 水凝胶敷料能够防止水分 和体液的过度散失而起到止血的效果； 对水和氧有良好的通透性而不允许细菌 通过， 可以抵御细菌的入侵， 并抑制细菌的生长， 具有抗菌、 消炎的功能； 能 与创面帖合良好， 但不会与创面粘连以免更换敷料带来二次损伤； 透湿、 透气 并使创面处于湿润但又没有积液的环境， 生物相容性好， 具有能促进伤口愈合 的功能， 越来越受到各国的重视。 如杨庆等人 (杨庆， 邬莹， 章悦庭.一种医用壳 聚糖透明水凝胶创伤敷料及其制备和应用 :20091004724.5[P].2009-3-13)公幵了一 种医用壳聚糖透明水凝胶创伤敷料及其制备和应用。 他们通过配制壳聚糖浆液 、 聚乙烯基吡咯烷酮 PVP溶液和聚乙烯酸钠溶液， 混合加入引发剂和交联剂， 倒 入模具， 40-75°C温度下反应得到初级产品， 表面添加防腐剂， 烘干， 切割包装 即得。 但其存在机械强度差的缺陷， 应用吋往往需要固定， 造成不便。
技术问题
[0004] 水凝胶根据交叉链接的方式不同可分为化学凝胶和物理凝胶。 化学凝胶的聚合 物分子链通过共价键链接， 物理凝胶则通过氢键、 离子作用及憎水性作用等非 共价键结合。 水凝胶的吸水作用与聚合物的组成、 种类、 链接密度以及环境温 度、 酸碱度、 离子强度有密切关系。 另外水凝胶的颗粒大小、 所含微孔的大小 也对吸水的速率具有影响。 常见的水凝胶有聚甲基丙烯酸羟乙酯、 聚丙烯酸羟 丙酯、 聚吡咯烷酮、 聚丙烯酸及聚丙烯酰胺等。
[0005] 基于 N -异丙基丙烯酰胺的温敏性智能水凝胶， 是一种典型的热缩型温敏性水 凝胶， 它响应环境温度的变化而发生溶胀或收缩， 最低临界溶液温度在 32 °C左 右， 接近人体表温度， 可作为医用敷料广泛用于体表创伤的组织修复。 壳聚糖 具有明显著的抑菌作用， 对于一般人体表皮存在的皮肤细菌如金黄色葡萄球菌 、 绿脓杆菌和酿脓链球菌等均有明显的抑制作用。 同吋， 壳聚糖能促进上皮细 胞的再生， 加快伤口愈合的速度， 提高伤口愈合的质量。 壳聚糖可以降解成低 聚糖、 寡糖甚至单糖， 有利于加快细胞增殖和加强组织重塑。 而且， 不同分子 量大小的壳聚糖各具优势， 大分子量的壳聚糖具有成膜强度好， 小分子量的壳 聚糖具有生物活性高、 保水性好的特点， 使用二者可以制备性能优良的医用敷 料。
[0006] 本发明的目的在于公幵了公幵了一种药用敷料水凝胶复合织物； 与其他敷料相 比， 水凝胶复合织物作为医用敷料具有独特的优势， 水凝胶敷料能够防止水分 和体液的过度散失而起到止血的效果； 对水和氧有良好的通透性而不允许细菌 通过， 可以抵御细菌的入侵， 并抑制细菌的生长， 具有抗菌、 消炎的功能； 能 与创面帖合良好， 但不会与创面粘连以免更换敷料带来二次损伤； 透湿、 透气 并使创面处于湿润但又没有积液的环境， 生物相容性好， 具有能促进伤口愈合 的功能。
[0007] 本发明的第二个目的在于公幵了上述药用敷料水凝胶复合织物的制备方法。
[0008] 本发明的第三个目的在于公幵了上述药用敷料水凝胶复合织物在制备抗菌消炎 和止血药物中的应用； 上述药用敷料水凝胶复合织物作为敷料， 一些抗菌消炎 和止血的常用药物， 如氟芬那酸丁酯、 苦参碱或盐酸小檗碱等作为活性成分。 问题的解决方案
技术解决方案
[0009] 本发明的目的是通过以下技术方案实现的：
[0010] 一种药用敷料水凝胶复合织物的制备方法， 包括下述步骤：
[0011] 将 N -异丙基丙烯酰胺和引发剂用溶剂溶解， 用氮气发泡； 所述引发剂选自硝 酸铈铵和过硫酸铵中的一种；
[0012] 称取 200mg棉纤维素用 10mL浓度为 10~20mM的弓 |发剂溶液弓 |发反应 15min;
[0013] 将 25mL N—异丙基丙烯酰胺和 1.2g作为交联剂的二甲基甲酰胺溶于 0.1M硝酸中
， 得到 N -异丙基丙烯酰胺和二甲基甲酰胺混合溶液；
[0014] 步骤 (2)中经引发反应的棉纤维素于 5mL步骤 (3)的溶液中浸泡 30min后， 平铺在 干燥的玻璃盘上在氮气条件下聚合反应 48h， 得到聚 N -异丙基丙烯酰胺 -棉纤 维素；
[0015] 已制备的聚 N -异丙基丙烯酰胺 -棉纤维素和海藻酸盐溶解在蒸馏水中， 在表 层形成水溶胶， 低压旋转蒸发仪去除溶剂， 得到药用敷料水凝胶复合织物。
[0016] 上述技术方案所述的一种药用敷料水凝胶复合织物的制备方法， 其中， 步骤 (1) 中 N—异丙基丙烯酰胺的体积比为 25%~50<¾， 弓 I发剂的质量体积比为 2%~5%。
[0017] 上述技术方案所述的一种药用敷料水凝胶复合织物的制备方法， 其中， 步骤 (1) 的具体步骤为： 将 0.4g硝酸铈铵， 25mL N -异丙基丙烯酰胺和 1.2g二甲基甲酰胺 溶于 O.lmol硝酸溶液， 用氮气发泡。
[0018] 上述技术方案所述的一种药用敷料水凝胶复合织物的制备方法， 其中， 步骤 (1) 的具体步骤为： 将 0.2g过硫酸铵， 25mL N -异丙基丙烯酰胺和 1.2g二甲基甲酰胺 溶于 O.lmol硝酸溶液， 用氮气发泡。
[0019] 上述技术方案所述的一种药用敷料水凝胶复合织物的制备方法， 其中， 步骤 (5) 中的海藻酸盐为海藻酸钠或海藻酸钙。
[0020] 一种药用敷料水凝胶复合织物， 其中， 所述药用敷料水凝胶复合织物是由上述 技术方案所述的制备方法制备。 [0021] 上述技术方案所述的一种药用敷料水凝胶复合织物， 其中， 药用敷料水凝胶复 合织物中 N-异丙基丙烯酰胺的含量为质量百分比 6%~30<¾。
[0022] 一种药用敷料水凝胶复合织物在制备抗菌消炎和止血药物中的应用， 所述抗菌 消炎和止血药物由敷料和活性成分组成， 其中， 所述活性成分为氟芬那酸丁酯 、 苦参碱或盐酸小檗碱， 所述敷料为上述技术方案所述的药用敷料水凝胶复合 织物。
[0023] 上述技术方案所述的一种药用敷料水凝胶复合织物在制备抗菌消炎和止血药物 中的应用， 其中， 活性成分占药物的质量百分比为 2%~5%。
发明的有益效果
有益效果
[0024] 本发明具有以下有益效果：
[0025] 本发明药用敷料水凝胶复合织物采用天然的生物降解型高分子材料， 具有一定 的抗菌消炎功效， 生物相容性好， 大大降低了免疫排斥反应的风险。
[0026] 本发明药用敷料水凝胶复合织物加入了药物， 如氟芬那酸丁酯、 苦参碱和盐酸 小檗碱等， 使水凝胶复合织物具有良好的抗菌、 消炎、 止血和促进伤口愈合的 功能， 避免外界环境及换药过程中的感染； 同吋， 水凝胶复合织物的吸水保水 性能良好， 为伤口创造了一个润湿环境， 有利于伤口愈合及换药。
[0027] 本发明药用敷料水凝胶复合织物为温敏性"智能"材料， 受体表温度的变化而溶 胀或收缩， 可使药物缓慢释放， 药物作用周期延长， 缩小换药的频率， 工作量 减小。
[0028] 本发明药用敷料水凝胶复合织物的制备过程简单易行， 所用试剂及原料均市售 可得， 可连续生产。
对附图的简要说明
附图说明
[0029] 图 1为水凝胶复合织物在 37 °C的溶胀动力学曲线；
[0030] 图 2为大鼠皮肤病理切片 （a为模型组， b为正常组， c为阳性对照组， d为普通 纱布和药物联合用药组， e为不含药水凝胶复合织物组， f为含药水凝胶复合织物 [0031] 图 3为水凝胶复合织物体外释药曲线。
[0032] 为使本发明的技术方案便于理解， 以下结合具体试验例对本发明一种药用敷料 水凝胶复合织物及其制备方法和应用作进一步的说明。
[0033] 实施例 1： 药用敷料水凝胶复合织物的制备：
[0034] 将 0.4g硝酸铈铵， 25mL N—异丙基丙烯酰胺和 1.2g二甲基甲酰胺溶于 O.lmol硝 酸溶液， 并氮气发泡；
[0035] 称取 200mg棉纤维素用 10mL浓度为 20mM的硝酸铈铵溶液引发反应 15min， 用 纸巾吸干除去多余的硝酸铈铵溶液；
[0036] 然后将经引发反应的棉纤维素于 5mL N -异丙基丙烯酰胺和二甲基甲酰胺混合 溶液 (将 25mL N -异丙基丙烯酰胺和 1.2g作为交联剂的二甲基甲酰胺溶于 0.1M硝 酸中制备所得)中浸泡 30min后； 棉纤维素平铺在干燥的玻璃盘上， 所得底物在氮 气条件下聚合反应 48h， 完全反应后产物用水清洗以除去表面的残留物， 得到的 干净样品在真空下 80°C干燥； 其中用水清洗以除去表面的残留物的操作原理为包 埋于水凝胶中的残基需要在三个溶胀、 退溶胀周期中反复除去， 每次均更换水 溶液； 每个周期包括 45°C水溶液浸泡 2h和室温条件下浸泡 2h， 即在高于或低于 N -异丙基丙烯酰胺的最低临界溶液温度 (LCST)条件下；
[0037] 将已制备的聚 N -异丙基丙烯酰胺 -棉纤维素和少量海藻酸钙溶解在蒸馏水中 ， 在表层形成水溶胶， 低压旋转蒸发仪去除溶剂， 得到药用敷料水凝胶复合织 物。 本步骤中海藻酸钙的作用是为水凝胶交联形成网格孔径提供离子对， 少量 即可促进该效果， 没有量的限制。
[0038] 实施例 2： 药用敷料水凝胶复合织物的制备：
[0039] 将 0.4g硝酸铈铵， 25mL N—异丙基丙烯酰胺和 1.6g二甲基甲酰胺溶于 O.lmol硝 酸溶液， 并氮气发泡；
[0040] 称取 200 mg棉纤维素用 10 mL浓度为 20 mM的硝酸铈铵溶液引发反应 15 min， 用纸巾吸干除去多余的硝酸铈铵溶液；
[0041] 然后将经引发反应的棉纤维素于 5mL N -异丙基丙烯酰胺和二甲基甲酰胺混合 溶液 (将 25mL N -异丙基丙烯酰胺和 1.2g作为交联剂的二甲基甲酰胺溶于 0.1M硝 酸中制备所得)中浸泡 30min后； 棉纤维素平铺在干燥的玻璃盘上； 所得底物在氮 气条件下聚合反应 48h， 完全反应后产物用水清洗以除去表面的残留物， 得到的 干净样品在真空下 80°C干燥； 其中用水清洗以除去表面的残留物的操作原理为包 埋于水凝胶中的残基需要在三个溶胀、 退溶胀周期中反复除去， 每次均更换水 溶液； 每个周期包括 45 °C水溶液浸泡 2 h和室温条件下浸泡 2
h， 即在高于或低于 N -异丙基丙烯酰胺的最低临界溶液温度 (LCST)条件下；
[0042] 将已制备的聚 N -异丙基丙烯酰胺 -棉纤维素和少量海藻酸钙溶解在合适的水 中， 在表层形成水溶胶， 低压旋转蒸发仪去除溶剂， 得到药用敷料水凝胶复合 织物。 本步骤中海藻酸钙的作用是为水凝胶交联形成网格孔径提供离子对， 少 量即可促进该效果， 没有量的限制。
[0043] 实施例 3： 药用敷料水凝胶复合织物的制备：
[0044] 将 0.2g过硫酸铵， 25mL N -异丙基丙烯酰胺和 1.2g二甲基甲酰胺溶于 O.lmol硝 酸溶液， 并氮气发泡；
[0045] 称取 200mg棉纤维素用 10mL浓度为 20mM的硝酸铈铵溶液引发反应 15min， 用 纸巾吸干除去多余的硝酸铈铵溶液；
[0046] 然后将经引发反应的棉纤维素于 5mL N -异丙基丙烯酰胺和二甲基甲酰胺混合 溶液 (将 25mL N -异丙基丙烯酰胺和 1.2g作为交联剂的二甲基甲酰胺溶于 0.1M硝 酸中制备所得)中浸泡 30min后； 棉纤维素平铺在干燥的玻璃盘上， 所得底物在氮 气条件下聚合反应 48h， 完全反应后产物用水清洗以除去表面的残留物， 得到的 干净样品在真空下 80°C干燥； 其中用水清洗以除去表面的残留物的操作原理为包 埋于水凝胶中的残基需要在三个溶胀、 退溶胀周期中反复除去， 每次均更换水 溶液。 每个周期包括 45 °C水溶液浸泡 2 h和室温条件下浸泡 2
h， 即在高于或低于 N -异丙基丙烯酰胺的最低临界溶液温度 （LCST) 条件下；
[0047] 将已制备的聚 N -异丙基丙烯酰胺 -棉纤维素和少量海藻酸钠溶解在合适的水 中， 在表层形成水溶胶， 低压旋转蒸发仪去除溶剂， 得到药用敷料水凝胶复合 织物。 本步骤中海藻酸钙的作用是为水凝胶交联形成网格孔径提供离子对， 少 量即可促进该效果， 没有量的限制。
[0048] 实施例 4： 药用敷料水凝胶复合织物的制备：
[0049] 将 0.2g过硫酸铵， 25mL N -异丙基丙烯酰胺和 1.2g二甲基甲酰胺溶于 O.lmol硝 酸溶液， 并氮气发泡；
[0050] 称取 200mg棉纤维素用 10mL浓度为 20mM的硝酸铈铵溶液引发反应 15min， 用 纸巾吸干除去多余的硝酸铈铵溶液；
[0051] 然后将经引发反应的棉纤维素于 5mL N -异丙基丙烯酰胺和二甲基甲酰胺混合 溶液 (将 25mL N -异丙基丙烯酰胺和 1.2g作为交联剂的二甲基甲酰胺溶于 0.1M硝 酸中制备所得)中浸泡 30min后； 棉纤维素平铺在干燥的玻璃盘上， 所得底物在氮 气条件下聚合反应 48h， 完全反应后产物用水清洗以除去表面的残留物， 得到的 干净样品在真空下 80°C干燥； 其中用水清洗以除去表面的残留物的的操作原理为 包埋于水凝胶中的残基需要在三个溶胀、 退溶胀周期中反复除去， 每次均更换 水溶液。 每个周期包括 45 °C水溶液浸泡 2 h和室温条件下浸泡 2 h， 即在高于或低 于 N -异丙基丙烯酰胺的最低临界溶液温度 （LCST) 条件下；
[0052] 将已制备的聚 N -异丙基丙烯酰胺 -棉纤维素和少量海藻酸钙溶解在合适的水 中， 在表层形成水溶胶， 低压旋转蒸发仪去除溶剂， 得到药用敷料水凝胶复合 织物。 本步骤中海藻酸钙的作用是为水凝胶交联形成网格孔径提供离子对， 少 量即可促进该效果， 没有量的限制。
[0053] 实施例 S ： 含氟芬那酸丁酯的水凝胶复合织物：
[0054] 将实施例 1-4制备所得的水凝胶复合织物用含氟芬那酸丁酯溶液在 25°C条件下 溶胀饱和， 干燥， 密封保存， 低温储存。
[0055] 实施例 6： 含盐酸小檗碱的水凝胶复合织物：
[0056] 将实施例 1-4制备所得的水凝胶用含盐酸小檗碱纳米乳溶液在 25°C条件下溶胀 饱和， 干燥， 密封保存， 低温储存。
[0057] 实脑 I Ί： 含苦参碱的水凝胶复合织物：
[0058] 将实施例 1-4制备所得的水凝胶用含苦参碱溶液在 25°C条件下溶胀饱和， 干燥
， 密封保存， 低温储存。
[0059] 以下通过对制备的水凝胶复合织物进行测试， 进一步验证本发明的药用敷料水 凝胶复合织物的性能：
[0060] 1、 平衡溶胀度：
[0061] 测试条件： 37 °C， 溶胀度 =(W t-W。)/W。 [0062] W t_水凝胶复合织物达到溶胀平衡吋的重量， W。_干燥水凝胶复合织物的重
[0063] 按照潘春跃， 于典， 隆清德， 等. NIPAAm系共聚温敏凝胶的溶胀与释药性能 [ J] . 中南大学学报 （自然科学版） ， 2007， 38 (5) ： 906-911 . 中的测试方法， 按照上述测试条件， 实施例 1制备所得的药用敷料水凝胶复合织物的溶胀动力学 性能如图 1所示， 水凝胶复合织物在 5分钟内迅速达到溶胀状态， 并维持长吋间 的溶胀平衡， 吸水保水性能良好。
[0064] 实施例 2〜4经检测后结果与实施例 1的结果相同。
[0065] 以下通过本发明制备的含药水凝胶复合织物的药效学试验和体外释药特性来进 一步阐述本发明产物水凝胶复合织物所具有的有益效果：
[0066] 试骑例一： 体外抗菌抗炎活性试验：
[0067] 30只 SD大鼠随机分为 6组， 分别为模型组、 正常组、 阳性对照组、 普通纱布与 药物联合用药组、 不含药水凝胶复合织物组和含盐酸小檗碱水凝胶复合织物 (实 施例 6制备)。 全身麻醉下， 大鼠背部脱毛， 生理盐水清洗干净脱毛区域， 用手术 刀划出一条长约 2 cm， 全层厚度的切口， 正常组只做脱毛处理； 除正常组外， 其余 5组切口部位接种带有金黄色葡萄球菌的菌液， 24 h后出现伤口感染现象。 除模型组外， 其余四组分别给予 Kaltostat®海藻酸钙纤维 （阳性对照组） ； 普通 纱布与小檗碱粉末 （联合用药组） ； 不含药水凝胶复合织物和含药水凝胶复合 织物， 给药后均用胶带固定保护伤口。 每隔 3天更换一次药物， 一周之后处死动 物。 取出伤口皮肤组织， 10%甲醛固定 24 h之后， 脱水， 石蜡包埋， 切成 4 μηι左 右的切片， HE染色， 电镜下观察皮肤组织炎性细胞浸润和血管生成等情况。
[0068] 结果如图 2， 可知含药水凝胶复合织物能有效治疗体表非特异性炎症反应， 并 明显抑制换药过程中引入的病原微生物所致的感染， 其中 a为模型组， b为正常组 ， c为阳性对照组， d为普通纱布和药物联合用药组， e为不含药水凝胶复合织物 组， f为含药水凝胶复合织物组）
[0069] 试骀例二： 水凝胶复合织物体外释药实验：
[0070] 采用动态透析法测定 (邹东娜， 张典瑞， 张学顺， 等. 苦参碱白蛋白微球的制 备及性质 [J] . 中国医药工业杂志， 2006， 37(12)： 824； 陈永顺， 陈黎. 水飞蓟 宾明胶微球的制备及体外释药 [J] . 中国实验方剂学杂志， 2011,17(24): 23. )小 檗碱水凝胶复合织物的体外释放度。 将小檗碱水凝胶复合织物平行取 3份， 分别 装入处理好的透析袋中， 两端系紧， 固定于溶出仪的搅拌桨上。 以 250 mL生理 盐水为释放介质， 在温度为 32 ± 0.5 °C， 转速为 lOO r.min -i的条件下进行体外释 药实验。 分别于 0， 1， 2， 4， 8， 12， 24， 48， 72 h取出 1 mL释放介质， 同吋补 加同温同体积的新鲜释放介质。
[0071] 结果如图 3所示， 水凝胶复合织物在 24 h内累计释药 46.52%， 结果表明， 水凝 胶复合织物载体有一定的缓释作用。
[0072] 以上所述， 仅为本发明的较佳实施例， 并非对本发明作任何形式上和实质上的 限制， 凡熟悉本专业的技术人员， 在不脱离本发明技术方案范围内， 当可利用 以上所揭示的技术内容， 而作出的些许更动、 修饰与演变的等同变化， 均为本 发明的等效实施例； 同吋， 凡依据本发明的实质技术对以上实施例所作的任何 等同变化的更动、 修饰与演变， 均仍属于本发明的技术方案的范围内。

Claims

权利要求书
一种药用敷料水凝胶复合织物的制备方法， 包括下述步骤： 将 N -异丙基丙烯酰胺和引发剂用溶剂溶解， 用氮气发泡； 所述引 发剂选自硝酸铈铵和过硫酸铵中的一种；
称取 200mg棉纤维素用 10mL浓度为 10~20mM的弓 |发剂溶液弓 |发反 应 15min;
将 25mL N -异丙基丙烯酰胺和 1.2g作为交联剂的二甲基甲酰胺溶 于 0.1M硝酸中， 得到 N -异丙基丙烯酰胺和二甲基甲酰胺混合溶 液；
步骤 (2)中经引发反应的棉纤维素于 5mL步骤 (3)的溶液中浸泡 30min 后， 平铺在干燥的玻璃盘上在氮气条件下聚合反应 48h， 得到聚 N -异丙基丙烯酰胺 -棉纤维素；
已制备的聚 N -异丙基丙烯酰胺 -棉纤维素和海藻酸盐溶解在蒸馏 水中， 在表层形成水溶胶， 低压旋转蒸发仪去除溶剂， 得到药用 敷料水凝胶复合织物。
根据权利要求 1所述的一种药用敷料水凝胶复合织物的制备方法， 其特征在于， 步骤 (1)中 N—异丙基丙烯酰胺的体积比为 25%~50<¾ ， 弓 I发剂的质量体积比为 2%~5<¾。
根据权利要求 1所述的一种药用敷料水凝胶复合织物的制备方法， 其特征在于， 步骤 (1)的具体步骤为： 将 0.4g硝酸铈铵， 25mL N— 异丙基丙烯酰胺和 1.2g二甲基甲酰胺溶于 0. lmol硝酸溶液， 用氮气 发泡。
根据权利要求 1所述的一种药用敷料水凝胶复合织物的制备方法， 其特征在于， 步骤 (1)的具体步骤为： 将 0.2g过硫酸铵， 25mL N— 异丙基丙烯酰胺和 1.2g二甲基甲酰胺溶于 0. lmol硝酸溶液， 用氮气 发泡。
根据权利要求 1所述的一种药用敷料水凝胶复合织物的制备方法， 其特征在于， 步骤 (5)中的海藻酸盐为海藻酸钠或海藻酸钙。 [权利要求 11] 一种药用敷料水凝胶复合织物， 其特征在于： 所述药用敷料水凝 胶复合织物是由权利要求 1〜5所述的制备方法制备。
[权利要求 12] 根据权利要求 6所述的一种药用敷料水凝胶复合织物， 其特征在于
： 药用敷料水凝胶复合织物中 N -异丙基丙烯酰胺的含量为质量百 分比 6<¾~30<¾。
[权利要求 13] —种药用敷料水凝胶复合织物在制备抗菌消炎和止血药物中的应 用， 所述抗菌消炎和止血药物由敷料和活性成分组成， 其特征在 于： 所述活性成分为氟芬那酸丁酯、 苦参碱或盐酸小檗碱， 所述 敷料为权利要求 6或 7所述的药用敷料水凝胶复合织物。
[权利要求 14] 根据权利要求 8所述的一种药用敷料水凝胶复合织物在制备抗菌消 炎和止血药物中的应用， 其特征在于： 活性成分占药物的质量百 分比为 2<¾~5<¾。
PCT/CN2015/070378 2014-01-10 2015-01-08 一种药用敷料水凝胶复合织物及其制备方法和应用 WO2015103988A1 (zh)

Priority Applications (1)

Application Number Priority Date Filing Date Title
CN201580000491.2A CN105228658B (zh) 2014-01-10 2015-01-08 一种药用敷料水凝胶复合织物及其制备方法和应用

Applications Claiming Priority (2)

Application Number Priority Date Filing Date Title
CN201410013667.5 2014-01-10
CN201410013667.5A CN103736140B (zh) 2014-01-10 2014-01-10 一种药用敷料水凝胶复合织物及其制备方法和应用

Publications (1)

Publication Number Publication Date
WO2015103988A1 true WO2015103988A1 (zh) 2015-07-16

Family

ID=50493252

Family Applications (1)

Application Number Title Priority Date Filing Date
PCT/CN2015/070378 WO2015103988A1 (zh) 2014-01-10 2015-01-08 一种药用敷料水凝胶复合织物及其制备方法和应用

Country Status (3)

Country Link
CN (2) CN103736140B (zh)
HK (1) HK1218631A1 (zh)
WO (1) WO2015103988A1 (zh)

Cited By (2)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
CN110105590A (zh) * 2019-04-30 2019-08-09 南京林业大学 基于羧甲基纤维素/氯化锂-聚丙烯酰胺水凝胶的柔性应变传感器的制备方法及其应用
CN112007201A (zh) * 2020-08-12 2020-12-01 山东百多安医疗器械股份有限公司 一种可粘附抗菌止血海绵及其制备方法

Families Citing this family (6)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
CN103736140B (zh) * 2014-01-10 2016-04-27 中国人民解放军第三0二医院 一种药用敷料水凝胶复合织物及其制备方法和应用
CN104258469B (zh) * 2014-08-29 2016-03-02 赵兰 一种除菌抑菌的壳聚糖-纤维素防粘连材料的制备方法
CN109568643B (zh) * 2018-10-21 2021-08-31 浙江理工大学 一种含小檗碱的抗菌止血微球的制备方法及其应用
CN109331218B (zh) * 2018-12-05 2021-08-10 浙江理工大学 一种含抗菌成分小檗碱的止血微球及其制备方法和应用
CN112869948B (zh) * 2021-01-12 2022-10-04 香港理工大学 智能湿响应紧缩织物及其制备方法、智能湿响应紧缩绷带
CN113730642B (zh) * 2021-08-20 2022-05-31 东华大学 一种梯度弹性变形的差别化释药复合敷料及其制备方法

Citations (5)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
WO2008127287A2 (en) * 2006-10-11 2008-10-23 Biolife, L.L.C. Materials and methods for wound treatment
CN101519474A (zh) * 2008-12-11 2009-09-02 淮阴师范学院 高溶胀性双重响应水凝胶及合成方法
CN102444021A (zh) * 2011-08-22 2012-05-09 翔瑞（泉州）纳米科技有限公司 一种智能型防水透湿织物及其制备方法
CN102477136A (zh) * 2010-11-22 2012-05-30 大连创达技术交易市场有限公司 一种高强度温敏性凝胶及其制备方法
CN103736140A (zh) * 2014-01-10 2014-04-23 中国人民解放军第三0二医院 一种药用敷料水凝胶复合织物及其制备方法和应用

Family Cites Families (5)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US6022330A (en) * 1997-06-23 2000-02-08 Institute Of Nuclear Energy Research, Taiwan, R.O.C. Preparation of easily stripped off temporary wound dressing materials by radiation grafting
CN100412259C (zh) * 2006-05-11 2008-08-20 天津工业大学 一种环境响应性智能纺织面料及其制备方法
CN103357062B (zh) * 2012-03-26 2015-10-28 约泰实业股份有限公司 纤维水凝胶及其制备方法
CN103113700A (zh) * 2013-01-18 2013-05-22 盐城工学院 互穿网络结构水凝胶创面敷料及其制备方法
CN103147290B (zh) * 2013-03-07 2015-05-20 中国科学院上海应用物理研究所 一种功能性纳米纺织品及其制备方法

Patent Citations (5)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
WO2008127287A2 (en) * 2006-10-11 2008-10-23 Biolife, L.L.C. Materials and methods for wound treatment
CN101519474A (zh) * 2008-12-11 2009-09-02 淮阴师范学院 高溶胀性双重响应水凝胶及合成方法
CN102477136A (zh) * 2010-11-22 2012-05-30 大连创达技术交易市场有限公司 一种高强度温敏性凝胶及其制备方法
CN102444021A (zh) * 2011-08-22 2012-05-09 翔瑞（泉州）纳米科技有限公司 一种智能型防水透湿织物及其制备方法
CN103736140A (zh) * 2014-01-10 2014-04-23 中国人民解放军第三0二医院 一种药用敷料水凝胶复合织物及其制备方法和应用

Cited By (3)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
CN110105590A (zh) * 2019-04-30 2019-08-09 南京林业大学 基于羧甲基纤维素/氯化锂-聚丙烯酰胺水凝胶的柔性应变传感器的制备方法及其应用
CN110105590B (zh) * 2019-04-30 2021-09-24 南京林业大学 基于羧甲基纤维素/氯化锂-聚丙烯酰胺水凝胶的柔性应变传感器的制备方法及其应用
CN112007201A (zh) * 2020-08-12 2020-12-01 山东百多安医疗器械股份有限公司 一种可粘附抗菌止血海绵及其制备方法

Also Published As

Publication number Publication date
CN103736140B (zh) 2016-04-27
CN103736140A (zh) 2014-04-23
CN105228658A (zh) 2016-01-06
CN105228658B (zh) 2018-04-20
HK1218631A1 (zh) 2017-03-03

Similar Documents

Publication Publication Date Title
WO2015103988A1 (zh) 一种药用敷料水凝胶复合织物及其制备方法和应用
Fan et al. Preparation and characterization of chitosan/gelatin/PVA hydrogel for wound dressings
CN110152051B (zh) 一种吸水烧创伤抗菌敷料及其制备方法和用途
Shyna et al. A nonadherent chitosan-polyvinyl alcohol absorbent wound dressing prepared via controlled freeze-dry technology
CN103736134B (zh) 一种医用海绵敷料及其制备方法
CN110975000A (zh) 一种抗菌改性外泌体烧创伤促愈生物敷料的制备和用途
RU149063U1 (ru) Повязка для заживления ран с противомикробным действием
RU2422133C1 (ru) Гидрофильный гель, способ его получения (варианты), раневое покрытие и перевязочное средство на его основе
CN108853570B (zh) 一种止血海绵及其制备方法
JP2022523780A (ja) 抗菌ドレッシング、ドレッシング構成要素、及び方法
Yuan et al. A cellulose/Konjac glucomannan–based macroporous antibacterial wound dressing with synergistic and complementary effects for accelerated wound healing
CN109731121A (zh) 一种含有介孔二氧化硅的纤维素和壳聚糖复合敷料的制备方法
CN109224116A (zh) 一种高吸收性的抗菌止血医用敷料及制备方法
RU2437681C1 (ru) Раневое покрытие с лечебным действием
CN114732936B (zh) 一种高透气性可降解的载药皮肤创伤敷料
CN111053947A (zh) 一种魔芋葡甘聚糖/鱼明胶水凝胶、其制备方法及应用
CN104906623A (zh) 一种纤维素基敷料及其制备方法和应用
CN112587719A (zh) 一种抗菌止血膜及其制备方法和应用
Dai et al. Silk fibroin/gelatin/calcium alginate composite materials: Preparation, pore characteristics, comprehensive hemostasis in vitro
Song et al. Kaolin-loaded carboxymethyl chitosan/sodium alginate composite sponges for rapid hemostasis
Wang et al. Calcium alginate/silk fibroin peptide/Bletilla striata polysaccharide blended microspheres loaded with tannic acid for rapid wound healing
CN106902383B (zh) 一种改性葡聚糖修饰的纳米凝胶止血材料及其制备和应用
Wang et al. Fabrication of microspheres containing coagulation factors by reverse microemulsion method for rapid hemostasis and wound healing
KR20030060458A (ko) 상처 치료용 수화겔의 제조방법
CN106937941B (zh) 一种医用皮肤伤口消炎凝胶及其制备方法

Legal Events

Date Code Title Description
WWE Wipo information: entry into national phase

Ref document number: 201580000491.2

Country of ref document: CN

121 Ep: the epo has been informed by wipo that ep was designated in this application

Ref document number: 15735047

Country of ref document: EP

Kind code of ref document: A1

NENP Non-entry into the national phase

Ref country code: DE

122 Ep: pct application non-entry in european phase

Ref document number: 15735047

Country of ref document: EP

Kind code of ref document: A1