CN114010794A - 一种基于纳米纤维材料的抗炎药物可控缓释体系 - Google Patents
一种基于纳米纤维材料的抗炎药物可控缓释体系 Download PDFInfo
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Abstract
本发明公开了一种基于纳米纤维材料的抗炎药物可控缓释体系,是以聚氨酯(PU)为溶质,以N,N‑二甲基甲酰胺(DMF)和四氢呋喃(THF)作为溶剂,再加入导电体和抗炎药物后制得的具有电‑应变双重刺激响应性的纳米纤维材料。该纳米纤维载体材料,具有良好的导电性能和弹性变形能力,即具有电‑应变双重刺激响应性。将该材料作为药物载体后,载药释放时间延长,释放速度变得更均匀,载药释放效率可以达到98.89%。总之,该材料能产生稳定波动的电刺激信号,为刺激治疗提供更广泛、可靠的实验依据。并且制备方法简单,可操作性强,制备得到的纳米纤维材料具有优异的导电性能、机械性能、湿态稳定性以及生物相容性。
Description
技术领域
本发明属于材料制备技术领域,涉及一种基于纳米纤维材料的抗炎药物可控缓释体系,尤其涉及一种电-应变双重刺激响应长效可控缓释纳米纤维载体材料及其制备方法。
背景技术
1、常用载药释放的生物材料:
随着材料技术的发展,越来越多的生物材料应用于药物递送系统(DDS)当中,从而提高药物的靶向性、水溶性,减少药物的毒副作用,提高药物的治疗疗效,最终减少患者的痛苦。高分子材料通常被用作载药释放系统的载体材料,按其降解性能的不同,可以分为生物可降解材料和不可降解材料。可生物降解的系统己经在药物释放领域获得了很大的关注和发展,而对于不可降解材料,由于其引入人体后需要收回或进一步处理而发展较慢。聚酯类和聚酸酯类高分子通常被用来作控制释放的材料。对于可降解的材料来说,虽然随着时间变化,药物的含量逐渐降低,释出的速率也会降低,但可以通过基体的降解来提高药物的释放速率,使得药物以恒定的速率释放。
聚酯是生物降解性能最好、研究最广泛的体系,聚酯己被广泛应用在药物释放系统中,性能方面良好的生物材料。有更好的相容性。聚合物来源于自身代谢产物的单体,因此这些材料的降解产生对应的羟基酸在体内应用时是安全的。天然可生物降解材料在医学上有着悠久的历史,可以追溯到3000多年前,古埃及人使用植物纤维、毛发和羊毛作为缝合材料。开发更安全的可生物降解缝合线和改进常用缝合线的需求,对合成生物可降解聚合物材料提出了更高的要求。上世纪60和70年代,PGA、PLA、PLGA被开发用作可以降解的缝合线。自那时以来,由于它们良好的相容性和降解特性,它们可以在体内分解产生无毒的天然副产品,例如水和二氧化碳,并且很容易被消除,这使得其在药物释放中的应用变得突出。尽管控制释放系统中的许多开创性工作是使用不可降解聚合物进行的,但可降解和生物降解聚合物才是发展聚合物药物释放系统更好的选择。
聚羟基丁酸酯(PHB)是一种生物可降解的、无毒的、生物相容的聚合物,这种从天然中获得的聚合物适合用于生物医药领域。由于它适当的相容性以及可控制的降解是目前最有前景的生物医用材料。我们把PHB与其他生物聚合物结合产生的药物释放系统去研宄药物扩散动力学。左旋聚乳酸(PLLA)因其生物降解性、相容性和杰出的力学特性而被大量应用于各种生物医药中。因此,我们把PHB和PLLA结合去产生新的药物释放系统。
聚合物载药释放系统尚未解决的问题包括:制备纳米微粒和囊泡的效率低,工艺复杂,药物释放效率低等。
2、常用纤维材料载药释放材料
天然以及合成的高分子材料常常被用作药物的载体以提升药物释放系统的效率。以生物相容性良好、可生物降解的蚕丝丝素(SF)和聚环氧乙烷(PEO)为电纺材料,以水为溶剂,利用混合比例的不同,在一定纺丝条件下,获得了珠粒形貌、尺寸可调的电纺串珠纤维材料。研究了电纺SF/PEO光滑纤维材料、串珠纤维材料在不同条件下对抗肿瘤药物盐酸阿霉素的释放行为,结果表明电纺串珠纤维材料对药物的释放更缓慢,持续时间更长,药物缓释效果优于电纺光滑纤维材料。还探究了采用同轴电纺方法制备同轴串珠纤维材料的条件,并对其药物缓释行为进行研究,结果表明SF/PEO同轴串珠纤维材料的药物缓释能力明显优于串珠纤维材料和光滑纤维材料,制备的材料在生物医用领域及过滤领域具有潜在的应用价值。
有研究将天然高分子聚合物CS、合成高分子聚合物和无机物正硅酸乙酯(TEOS)混合,采用静电纺丝技术,利用各物质间特性,通过调节各物质间浓度、配比等进行条件优化,获得最佳比例,合成具有一定比表面积、一定孔隙度的载药纤维膜。将药物添加到最佳配比的纺丝液中制得载药复合纤维膜,探讨了不同含量的药物对复合纤维膜的影响及对纤维的缓释性能的影响。具体内容如下:1.利用聚酰胺(PA)/壳聚糖(CS)/正硅酸乙酯(TEOS)为原料,采用静电纺丝技术合成复合纤维膜。通过调节纺丝共混液中各项参数,确定最优配比为1:0.13:0.67;在最佳配比的纺丝液中添加不同浓度的氧氟沙星(OFLO)药物,进行体外释放,研究得到当药物含量在0.2%时,纤维缓释性能最好,累计释放量达到71%。2.替换高分子聚合物为聚乙烯醇,利用聚乙烯醇(PVA)/壳聚糖(CS)/正硅酸乙酯(TEOS)为原料,采用静电纺丝技术合成复合纤维膜。通过调节纺丝共混液中各项参数来优化纺丝条件,确定最优的配比为1:0.43:1.2;纤维膜具有一定比表面积(7.805m2/g)和狭窄的孔径结构。在最佳配比的纺丝液中添加不同浓度的氧氟沙星(OFLO)药物,进行体外释放,研究发现所制纤维膜具有一定缓释效果,累计释放量达69%。
还有研究以水为溶剂,利用静电纺丝的方法制备聚乙烯醇(PVA)超细纤维膜,利用静电纺丝法可将阿斯匹林、牛血清清蛋白包载入PVA超细纤维中,制成具有药物释放功能的PVA超细纤维膜。超细纤维膜放入生理盐水中后,纤维中的阿斯匹林、牛血清清蛋白以较快的速率释放出来,与含有等量药物的浇铸膜相比,释放动力学曲线有明显差异。
3、静电纺丝载药方法
浸药法是先制备出静电纺纳米纤维毡,将纤维毡浸渍到药物溶液或载药纳米粒的溶液中,使药物吸附到纤维毡中。浸药法在开始阶段可实现药物突释,之后缓慢持续释放药物,总体持续释放效果优于直接给药,在术后抗感染、抗菌抗炎方面效果显著。KHATSEE等通过制备聚乳酸(PLA)和聚己二酸丁二醇酯-对苯二甲酸酯(PBAT)纤维垫达到突释的效果,并且载药PLA/PBAT纤维垫具有抗菌活性,可以作为抗感染等药物的载体。魏晓慧等利用静电纺丝技术制得聚醚砜纳米纤维毡,并将纳米Mg O颗粒与制得的聚醚砜纳米纤维毡复合,提高了纳米Mg O粉末使用的效率。
共混包埋法主要是把聚合物溶液与药物或载药纳米粒混合制备成载药静电纺纳米纤维,药物较为均匀地分布在纤维的内部,与浸药法相比药物突释现象得到改善,缓释效果较好。ADEPU等将醋酸纤维素(CA)负载低半衰期药物双氯芬酸钠制成载药静电纺纳米纤维,可有效地防止双氯芬酸钠的初始突释现象,为低半衰期药物的可控扩散奠定基础。MORGANE等通过静电纺丝制备了透明质酸(HA)的纳米纤维,加入聚乙烯醇(PVA)作为载体聚合物并嵌入羟丙基-β-环糊精,使用支架原位交联过程确保无毒,选用非甾体类抗炎药萘普生(NAP)作为模型药物,结果显示模型药物在该支架纤维上的缓释性能良好,为抗炎类药物缓释特性的伤口敷料应用提供了基础。
同轴静电纺是使药物或载药纳米粒与高聚物的溶液进入两个同心的喷丝头管道,制备出芯-壳结构的复合纳米纤维。较共混包埋法缓释效果更强,载药量更大。李荣俊等使用玉米醇溶蛋白和左旋聚乳酸(PLLA),采用同轴静电纺丝技术制备新型纳米纤维材料,将骨诱导传导生长因子和骨传导结合,减少了感染的风险,增强了手术安全性。
乳液静电纺是将药物与高聚物溶液制备成乳液并电纺制备出芯-壳结构的复合纳米纤维。乳液静电纺丝相对于同轴静电纺丝可控性更好,应用领域更广泛,在制备含有活性物质、特殊药物和其他功能纤维方面有特殊意义。但在乳液制备过程中,表面活性剂等物质的添加可能会影响药物的生物相容性。崔银等以卡铂水溶液为水相,PLLA的二氯甲烷溶液为油相,Poloxamer188~为乳化剂,制备出卡铂纤维膜。研究表明,当Poloxamer188~的质量分数为10%、20%和30%时,缓释时间均超过10h。Poloxamer188~释放曲线符合Freundlich方程式,卡铂释放曲线符合0级释放动力学。乳液静电纺丝法能够制得有缓释作用并可抑制He La细胞的卡铂纤维膜。
4、静电纺纳米纤维抗炎药物
甲基泼尼松龙(MP)、皮质松(HC)和氟美松(Dx),以及非甾体抗炎药消炎痛、布洛芬和阿司匹林等非甾体抗炎药(NSAIDs)抗炎药在心肌梗死中的使用范围很广。糖皮质激素是有效建立炎症反应,从而抑制炎症介质的转导,减少趋化因子的表达,促进凋亡细胞的清除,诱导巨噬细胞形成抗炎表型。
甲基泼尼松龙(MP)已被提出可以减少炎症,减少心肌损伤和胶原蛋白沉积,并增加毛细血管密度在心肌梗死的实验模型中。此外,甲基泼尼松龙的影响依赖于高级通路、治疗剂量和持续时间。例如,糖皮质激素治疗被认为是心力衰竭的一个危险因素和大剂量甲基泼尼松龙会导致梗死变薄腔扩张。相比用盐水载体局部注射,小分子的局部传递一种生物材料载体,具有持续释放与简单的系统管理的优点。有刺激性反应的基于生物的高分子材料,具有广泛的应用前景各领域,因为其优异的性能和优势,特别是在药物控制释放中。
小分子抗炎药物包括天然提取和人工合成类药物。具有抗炎作用的人工合成类药物包括非固醇类的阿司匹林、安乃近和对乙酰氨基酚等,和固醇类的地塞米松、可的松和糖皮质激素类药物等,具有一定抗炎和免疫抑制等作用,但这些药物都普遍存在长期服用增加消化系统和泌尿系统负担等隐患,导致肾组织萎缩、过敏、消化道溃疡等疾病。
5、实现可控缓释的方法
药物缓释体系对比传统载药给药过程,具有可减少给药次数、降低药物对机体的毒副作用、延长药物在体内作用时间等优点。利用可降解生物高分子聚合物材料制成的载药纤维具有较大的比表面积、较多的孔隙结构、良好的机械性能等特点,对药物输送、组织工程、生物医药等领域的发展具有重大意义。因此,为进一步扩展纤维在药物缓释载体中的应用,开发一种具备缓释性能的载药纤维材料具有一定研究意义。静电纺丝技术是一种简单、易操作的制备纤维的方法,所制备的纤维具有尺寸可控、富含高孔隙率、具有较大比表面积等特点,广泛应用于药物释放材料、组织工程、吸附实验等领域。
溶液静电纺丝方法己被广泛应用于制备药物控制释放系统,它能以简单、低成本、可控的方式得到纳米纤维,具有可用多种材料以及纤维直径小等优点。此外,这种技术是非常方便的,因为这些纤维可以涂覆在任何无纺布和有序纤维表面上。然而,对于药物释放系统,溶液静电纺丝往往需要用到毒性溶剂来溶解药物和载体,这不但可能会影响药物的活性,纺丝过程中会对人产生一定的危害,并且这种溶剂在纺丝过程中往往不能完全的挥发。在生物医学领域,这些纤维中残留的溶剂对细胞和组织会有一定的毒性作用。
值得注意的是,熔体静电纺丝能以无溶剂的方式获得聚合物纤维,它可以提供一个安全、环保的过程,并且不会破坏药物的活性。因此,溶液静电纺丝的缺点,如昂贵的溶剂回收费用、溶剂爆炸的危险和溶剂的残留等都可以避免。以扩散为主的药物释放主要发生在非降解的释放系统中。然而对于可降解的材料,它们通常会带有不稳定的化学键,可能被水解反应影响,特别是末端官能团的自催化反应机制。在这方面,尽管在制备超细纤维方面取得了令人印象深刻的技术成就,然而在药物释放过程中,出现在纤维材料的扩散和水解问题只有有限的工作去研宄。显然这些问题需要我们进行综合的实验和理论检测。为了解决内在的扩散动力问题,需要测量在不同的内在条件下药物从宏观纤维膜控制释放的量。对于水难溶或不溶的药物,在服用后具有较低的溶出度,因此很难让身体吸收。不但造成了药物的浪费,并且达不到人们预期的效果。
研究者已经尝试通过不同的方法来改善其溶出度,但关于通过超细纤维来改善溶出度的研宄却很少,静电纺丝产生的纳米纤维,具有高的比表面积、纤维直径小、主要是无定型结构等特点利于药物的溶出,因而可以通过载体将药物制备成纤维,以此来增加药物的溶出度,提高它的生物利用度。
通常摄入人体体内的药物浓度会急剧上升到最大,经过人体的分解和排泄药物浓度又会很快降低。因此,很难使人体内的药物长期处于治疗水平。传统的给药方法不能对病灶部位直接产生效果,会对组织和器官产生毒副作用。传统的给药方式需要多次给药,给病人带来很大的不便。传统的给药方式通常每6小时就需要一次注射,并且药物浓度会产生较大的波动范围。过高的药物浓度会对人体产生毒性,造成身体上的危害。过低的药物浓度会使药物效果降低,达不到治疗的目的。药物只在很短的时间内,可以起到治疗的效果。
不同的纳米纤维载体材料所达到的体外药物释放情况不同。甲基泼尼松龙作为一种经典的抗炎药物,抗炎作用较强,就好像把消炎药附在伤口上面。但是其需要长期稳定缓慢释放,才能够达到更加理想的临床疗效。因此,实现测定甲基泼尼松龙的体外释放情况,是载药制备工艺中的重点所在。本发明将抗炎药物(尤其是如MP)引入基于导电高分子的药物控释系统,提供一种电-应变双重刺激响应长效可控缓释纳米纤维载体材料。该体系展现了良好的药物释放模式,具有可调性、稳定性和精确的定量给药,为长期供药提供了很好的条件。
发明内容
本发明的目的在于克服上述现有技术的不足,提供一种基于纳米纤维材料的抗炎药物可控缓释体系,将抗炎药物如MP引入基于导电高分子的药物控释系统,制备一种电-应变双重刺激响应的长效可控的缓释纳米纤维载体材料。
本发明采用如下技术方案:
一种基于纳米纤维材料的抗炎药物可控缓释体系,是以聚氨酯(PU)为溶质,以N,N-二甲基甲酰胺(DMF)和四氢呋喃(THF)作为溶剂,再加入导电体和抗炎药物后制得的具有电-应变双重刺激响应性的纳米纤维材料。
所述的导电体可以为金属盐(如硝酸银等)、氧化石墨烯、碳纳米管、聚苯胺、聚吡咯、聚噻吩及其衍生物中的一种或多种。
所述的抗炎药物通常为甲基泼尼松龙(MP)、皮质松(HC)和氟美松(Dx)中的一种或多种。
进一步的,所述纳米纤维材料采用静电纺丝法制得。静电纺丝的参数为:喷丝距离为10~15cm,供液速度为0.5~2mL/h,滚筒转速为250~300rad/min,电压为10~20kV,温度25~40℃,湿度35%以下。
进一步的,所述的导电体优选采用硝酸银和氧化石墨烯,所述的抗炎药物为MP,所述体系的原料按重量份计为:
进一步的,制得的纳米纤维的直径为480-814nm。
所述体系载药释放效率达98.89%以上。
本发明以聚氨酯作为药物释放系统的原材料,通过加入导电体及抗炎药物,可以获得兼具有电-应变双重刺激响应的长效可控药物缓释体系,与传统的药物剂型相比,副作用较小,安全性高。可在短时间内先实现部分药物的快速释放过程,药物释放速度较快,有效控制炎症,然后实现药物的缓慢持续释放,达到药物“双重释放”的目的。尤其是当采用硝酸银和氧化石墨烯共同作为导电体加入体系中,以甲基泼尼松龙(MP)为抗炎药物,能够实现在有电刺激以及良好的弹性变形的情况下,载药释放时间变长,释放速度变得更均匀,载药释放效率可以达到98.89%。
本发明的有益效果在于:
本发明方法工艺简单,可操作性强,制备得到的纳米纤维载体材料可以为柔性膜,且具有优异的导电性能、机械性能、湿态稳定性以及生物相容性。并且在有电刺激以及良好的弹性变形的情况下,载药释放时间长,释放速度均匀,从MP的累积释放曲线可以看出释放效率最终可达到98%以上。该纳米纤维材料具有较广阔的应用前景,可以应用在药物释放系统、骨组织修复、神经损伤的治疗、心血管疾病、组织工程支架、医用辅料、生物效应器、生物传感器等方面。
附图说明
图1是实施例3制备的纳米纤维材料的扫描电镜照片(1000倍)。
图2是甲基泼尼松龙(MP)的标准曲线。
图3是实施例1、实施例2、实施例3制备的纳米纤维载体材料中MP的累积释放量与时间的关系示意图。
具体实施方式
下面结合附图和具体实例对本发明的技术方案做进一步的说明。由于抗炎药物的效果与所使用的药物的浓度和剂量有关,下述实例中均使用甲基泼尼松龙(分子式C22H30O5,分子量为374.47)纯度为98%以说明效果,对于其他抗炎药物同样适用。
实施例1
以聚氨酯(PU)、甲基泼尼松龙(MP)为静电纺丝的原材料,N,N-二甲基甲酰胺(DMF)和四氢呋喃(THF)作为溶剂。
按重量份计算的组分:
其中,溶剂为N,N-二甲基甲酰胺(DMF)和四氢呋喃(THF),比例为1:1。
用电子天平称取DMF/THF(1/1)=4.725g,作为溶剂,置于一个干净的玻璃搅拌瓶中。再称取0.5g的PU放入玻璃搅拌瓶中。在数显控温加热搅拌器中60℃搅拌3小时,使得PU完全溶解,最终得到均匀稳定的纺丝液。接着进行静电纺丝制备负载MP的纳米纤维材料。静电纺丝参数为:温度为40.0℃,湿度为23.1%,喷丝距离为11cm,供液速度为2mL/h,滑台速度为15mm/s,滚筒转速为300rad/min,电压为15kV。
所制备的柔性纳米纤维载体材料的平均直径为250nm,平均厚度为0.14mm,透气性为884.30mm/s,由于水滴停留在纳米纤维表面,因此,从接触角测试可以知道,该材料是亲水的。拉伸应力和应变分别为327674Pa和169%。
制备的纳米纤维载体材料在只有弹性变形的情况下,载药释放效率不是很高,从MP的累积释放曲线可以看出释放效率最终达到88.62%以上。此实施例因为没有加入导电体,制备的纳米纤维载体材料无法产生电刺激,因此载药释放效率并不高。
实施例2
以聚氨酯(PU)、硝酸银(AgNO3)、甲基泼尼松龙(MP)为静电纺丝的原材料,N,N-二甲基甲酰胺(DMF)和四氢呋喃(THF)作为溶剂。按重量份计算的组分:
其中,溶剂为N,N-二甲基甲酰胺(DMF)和四氢呋喃(THF),比例为1:1。用电子天平称取DMF/THF(1/1)=4.7g,作为溶剂,置于一个干净的玻璃搅拌瓶中。再称取0.05g的AgNO3和0.5g的PU,放入玻璃搅拌瓶中。在数显控温加热搅拌器中60℃搅拌3小时,使得PU完全溶解,最终得到均匀稳定的纺丝液。进行静电纺丝制备负载MP的纳米纤维材料。静电纺丝参数为:温度为40.0℃,湿度为23.1%,喷丝距离为11cm,供液速度为2mL/h,滑台速度为15mm/s,滚筒转速为300rad/min,电压为15kV。
所制备的纳米纤维载体材料的平均直径为750nm,平均厚度为0.14mm,透气性为1512.71mm/s,由于水滴停留在纳米纤维表面,因此,从接触角测试可以知道,该材料是亲水的。拉伸应力和应变分别为559875Pa和126%。
制备的纳米纤维载体材料在弹性变形和单一的导电体(硝酸银)作用的情况下,载药释放效率有提高,从MP的累积释放曲线可以看出释放效率最终达到96.38%以上。此实施例因为加入了单一的导电体,制备的纳米纤维载体材料可以部分电刺激,载药释放效率有明显提高。
实施例3
以聚氨酯(PU)、硝酸银(AgNO3)、氧化石墨烯(GO)、甲基泼尼松龙(MP)为静电纺丝的原材料,N,N-二甲基甲酰胺(DMF)和四氢呋喃(THF)作为溶剂。按重量份计算的组分:
其中,溶剂为N,N-二甲基甲酰胺(DMF)和四氢呋喃(THF),比例为1:1。用电子天平称取DMF/THF(1/1)=4.6895g,作为溶剂,置于一个干净的玻璃搅拌瓶中。再称取0.05g的AgNO3和0.003g的GO,放入玻璃搅拌瓶中。接着将玻璃瓶放入超声波清洗器中,超声60min,使得GO完全分散在溶液中。然后再加入0.5g的PU,纺丝溶液总质量为10g。在数显控温加热搅拌器中60℃搅拌3小时,使得PU完全溶解,最终得到均匀稳定的纺丝液。通过静电纺丝法制备纳米纤维载体材料。静电纺丝参数为:温度为40.0℃,湿度为23.1%,喷丝距离为11cm,供液速度为2mL/h,滑台速度为15mm/s,滚筒转速为300rad/min,电压为15kV。
所制备的纳米纤维材料的平均直径为710nm,平均厚度为0.19mm,透气性为1358.13mm/s,由于水滴停留在纳米纤维表面,因此,从接触角测试可以知道,该材料是亲水的。拉伸应力和应变分别为462139Pa和149%。用DM3068数字万用表测试电信号,制得的纳米纤维材料平铺时电压以0.0076mV为节点上下波动,拉伸10%时电压以0.0029mV为节点上下波动,拉伸20%时电压以0.0086mV为节点上下波动。
制备的纳米纤维载体材料在弹性变形和多个导电体(硝酸银和氧化石墨烯)作用的情况下,硝酸银和氧化石墨烯一起作用,起到导电作用;聚氨酯起到弹性形变的应变要求。从释放曲线可知,在电刺激和弹性应变的双重刺激下,载药释放效率大大提高,释放效率最终可达到98.89%以上。此实施例因为加入了多个导电体,制备的纳米纤维载体材料可以产生相对较强的电刺激,载药释放效率进一步提高。这说明在电-应变双重刺激的情况下,载药的释放效果好。
可以看出,本发明所制得的纳米纤维载体材料,具有良好的弹性变形并且导电性能良好。研究纳米纤维载体材料载药释放的情况,根据载药的累积释放曲线,可以看出没有加入导电体的纳米纤维载体材料,载药释放效率只有88.62%。而在加入导电体后,材料具有电刺激以及良好的弹性变形,载药释放时间变长,释放速度变得更均匀,载药释放效率甚至可以达到98.89%以上。该材料能产生稳定波动的电刺激信号,为刺激治疗提供更广泛、可靠的实验依据。并且制备方法简单,可操作性强,制备得到的纳米纤维载体材料具有优异的机械性能、导电性能以及生物相容性。
研究证明,内生电场广泛存在于生物体中,对于组织生长和创伤愈合起重要作用。外加人工电场可以对细胞形态、细胞迁移、细胞增殖、细胞因子分泌等产生重大影响,尤其是电剌激,电刺激信号与细胞的生长速度、再生能力、向特定方向分化有关系。本发明同时加入导电性物质和抗炎药物,通过产生任意频率和幅值的电刺激信号后,为刺激治疗提供更广泛、可靠的实验依据。电刺激作用下还可以促进细胞的生长和新组织的形成。因此,本发明的一种电-应变双重刺激响应长效可控缓释纳米纤维载体材料具有良好的应用前景。电刺激下控制载药的释放,减少手术的二次伤害,可以加快伤口愈合。该纳米纤维材料具有较广阔的应用前景,可以应用在药物释放系统、骨组织修复、神经损伤的治疗、心血管疾病、组织工程支架、医用辅料、生物效应器、生物传感器等方面。
Claims (7)
1.一种基于纳米纤维材料的抗炎药物可控缓释体系,其特征在于,该体系是以聚氨酯(PU)为溶质,以N,N-二甲基甲酰胺(DMF)和四氢呋喃(THF)作为溶剂,再加入导电体和抗炎药物后制得的具有电-应变双重刺激响应性的纳米纤维材料。
2.根据权利要求1所述的基于纳米纤维材料的抗炎药物可控缓释体系,其特征在于,所述的导电体为金属盐、氧化石墨烯、碳纳米管、聚苯胺、聚吡咯、聚噻吩及其衍生物中的一种或多种。
3.根据权利要求1所述的基于纳米纤维材料的抗炎药物可控缓释体系,其特征在于,所述的抗炎药物为甲基泼尼松龙(MP)、皮质松(HC)和氟美松(Dx)中的一种或多种。
4.根据权利要求1所述的基于纳米纤维材料的抗炎药物可控缓释体系,其特征在于,所述纳米纤维材料采用静电纺丝法制得。
6.根据权利要求5所述的基于纳米纤维材料的抗炎药物可控缓释体系,其特征在于,所述的纳米纤维的直径为480-814nm。
7.根据权利要求5所述的基于纳米纤维材料的抗炎药物可控缓释体系,其特征在于,所述体系载药释放效率达98.89%以上。
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Publication number | Priority date | Publication date | Assignee | Title |
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CN115554477A (zh) * | 2022-09-29 | 2023-01-03 | 浙江理工大学 | 地塞米松心肌补片及其制备方法 |
WO2024079488A1 (en) * | 2022-10-14 | 2024-04-18 | Liberum Health Ltd | Drug delivery device |
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2021
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Cited By (2)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
CN115554477A (zh) * | 2022-09-29 | 2023-01-03 | 浙江理工大学 | 地塞米松心肌补片及其制备方法 |
WO2024079488A1 (en) * | 2022-10-14 | 2024-04-18 | Liberum Health Ltd | Drug delivery device |
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