CN100506197C - 创口敷料 - Google Patents
创口敷料 Download PDFInfo
- Publication number
- CN100506197C CN100506197C CNB2005800022160A CN200580002216A CN100506197C CN 100506197 C CN100506197 C CN 100506197C CN B2005800022160 A CNB2005800022160 A CN B2005800022160A CN 200580002216 A CN200580002216 A CN 200580002216A CN 100506197 C CN100506197 C CN 100506197C
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- substrate
- wound dressing
- wound
- polymer
- fiber
- Prior art date
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Abstract
本发明涉及一种创口敷料包括由吸附性基质(12)形成的第一层以及抗菌活性物质，该物质与该基质(12)的一个表面以化学或物理结合方式连接，并在具有该物质的基质表面上涂覆亲水性聚合物。
Description
本发明涉及一种创口敷料。
通常认为潮湿环境会促进创口的痊愈。同时防止形成痂从而几乎不留疤痕。可以通过帮助创口痊愈的介质产生潮湿环境。为了此目的，通常使吸附性材料充满这样的介质从而用于创口。
DE 297 21 345 U1公开了一种创口贴膏，其中在粘贴膜和创口无纺布之间设置一个液体腔室。该液体腔室的放置应使其所含液体能由此渗透该创口无纺布。
DE 196 31 421 A1公开了一种抗菌创口敷料。该创口敷料由含有抗菌活性的化合物的疏水性细菌吸附材料组成，该化合物不会被释放至创口。借助于该疏水性材料并结合抗菌活性化合物，将来自创口液体的细菌吸收在创口敷料上并在此杀灭。通过将创口敷料去除，细菌也被去除。其不再干扰创口的痊愈过程。
DE 197 27 032 A1公开了一种贴膏，其中粘贴区域具有第一粘贴区和配置于第一粘贴区之外的第二粘贴区。第一粘贴区的粘合力比第二粘贴区的小。
DE 198 60 759 C2公开了一种贴膏，借助其可将皮肤表面覆盖，其内部会产生注入。该贴膏由弹性表面组成，该弹性表面具有邻接皮肤一侧的粘贴表面，其间放置由吸附性材料制成的环形药物活性载体。该载体包含用于该载体环绕的注入区域消毒的消毒剂。注入区域之上具有弹性表面，其具有开口、以及覆盖粘贴表面和药物活性载体、且在使用前必须揭掉的保护膜。
DE 697 18 035 T2公开了具有粘合剂组合物的粘性敷料，其形式为含有可调整加固件的至少一部分的层。选择该粘合剂组合物和该加固件使得该粘性敷料具有透气性。
EP 1 005 301 B1公开了粘贴于皮肤上的创口敷料，所具有的第一区域与所具有的用于与创口接触的基质相对，包含抗菌活性化合物的第二区域环绕着第一区域，以防止来自外部环境的细菌侵入。
WO 02/056927 A2公开了一种多层敷料。其包含吸附层、能透气但不能透过液体的外层以及在吸附层中的用于释放液体治疗介质的腔室。该敷料还含有在创口上形成覆盖的穿孔层。该外层可以具有能使该敷料固定在创口周围的粘贴层。借助该敷料，能使创口保持封闭以及湿润。
本发明目的在于提供一种能使创口更好愈合的创口敷料。另外，将公开其制备方法。
本发明通过下面的技术方案实现本发明的目的。
根据本发明所提供的创口敷料包含由吸附性基质和抗菌活性物质形成的第一层，该物质与该基质的一表面呈现化学或者物理结合。该基质的表面包括该物质的表面涂覆有亲水性聚合物。该基质包含纤维并且能由无纺布、纱布、发泡材料或者另一种软吸附材料组成。发泡材料的优点在于其能固定从创口脱离的材料并且由此能保持远离创口，以使其不干扰愈合过程。该基质可以包含至少一种纤维或者由至少一种纤维形成。因而结合该物质的基质表面可以是纤维的表面。该物质优选结合于纤维或者该基质的表面，以使其如所期望的那样在使用时不能或者几乎不能从该基质流失。
该基质或者纤维能够被制备，其中该物质与该基质或者纤维的表面结合而存在，例如，可以是通过处理聚合物形成带有该物质的基质或者纤维以制备该基质或者纤维。在所生成的基质或者纤维中，该物质中的一些存在于纤维或者基质的表面。然而，更多部分通常进入到经聚合物处理的基质或者纤维的内部，以使其不接触来自外部的液体。因此该物质最好完全结合到基质或者纤维的表面。因此，制备中不必使用不必要量的该物质，最终其是难得到的。
好的创口治疗的先决条件在于在基质中以及基质周围的液体中不期望的细菌不会繁殖。为此，该创口敷料含有抗菌活性物质。如果按DE 197 58 598 A1所述进行测试，其能显著地延缓或者完全抑制微生物繁殖，那么该物质就具有抗菌活性。抗菌活性物质还可以是一种物质，其在按要求使用创口敷料的环境中通过转化而产生抗菌活性化合物。举例说，如果抗菌活性化合物是金属离子或者包含金属离子的离子络合物，那么该金属、其合金以及其在创口区域能够释放出上述金属离子或者上述包含金属离子的离子络合物的其它物质也具有抗菌活性。金属离子可以是银、铜或者锌的阳离子。另外，抗菌活性物质可以是金属性的银、铜或者锌或者合金或者在创口区域能释放出所述离子的其它物质。
抗菌活性物质可以具有抗表皮葡萄球菌或者其它微生物的抗菌活性。根据DE 197 58 598 A1公开的方法，使用在每一种情况下都进行研究的微生物而不是葡萄糖球菌对该物质针对其它微生物的抗菌活性进行测定。特别优选的物质是抗一种或者多种微生物的具有抗菌活性的物质，该微生物选自由芽孢杆菌属、芽孢梭菌属、肠杆菌属、埃希氏杆菌属、假单胞菌属、沙门氏菌属、葡萄糖球菌属、耶尔森氏菌属、念珠菌属以及曲霉属组成的组。
已经发现抗菌活性物质，尤其是其有细胞毒性的，会干扰创口愈合。如果其具有如DIN-ISO 10993-5所述的细胞毒害作用，则该抗菌活性物质是有细胞毒性的。为防止干扰，本发明提供的该物质应结合到基质或者基质纤维的表面上。通过结合，可以防止在创口处上述抗菌活性物质达到能干扰创口愈合的数量。而且，由此可以防止该抗菌活性物质由于被吸收进入体内而从创口敷料区域损失而不能在那里有长时间的抗菌活性。而且，由此可以防止该物质吸收或在体内引起所不希望的反应，如过敏。
借助于本发明的创口敷料，可以预防诸如创口处产生的细菌在创口处扩散从而导致创口感染或者创口再感染。通过长时间阻止细菌的繁殖，该创口敷料能一直覆盖在创口上直到创口愈合。因此，可以避免剥离该创口敷料而产生的机械应力，而且可以确保对创口愈合有利的创口静养。本发明所述的创口敷料的主要优点实际在于无菌，同时创口愈合过程中不受抗菌活性物质的干扰。
聚合物的涂层要求薄且聚合物是经过选择的，由此以使该物质的作用不被阻止。例如，上述聚合物可以是由六甲基二硅氧烷通过等离子聚合而形成的聚合物。该涂层增强了该物质对于纤维或者基质的结合。例如通过蒸镀或者沉积镀覆的银的颗粒簇被保护免受机械磨损。由于该层具有亲水性，纤维或者基质的可润湿性是优选的。由此能实现液体在基质上更均匀的分布。而且，通过改善纤维或者基质与液体的接触，能发挥出抗菌活性物质更佳的作用。进而，借助于该亲水性聚合物，尤其是通过等离子聚合得到的，可以减少革兰氏阳性菌和/或革兰氏阴性菌粘附于纤维或者基质。再者，由于直接在经过涂覆的基质或者纤维的表面上形成液膜，该亲水性层改善了该基质或者该基质的各个纤维在潮湿环境中的滑动状态。于是，如果基质存在于创口之上，在发生位移的情况下，其在创口上轻易的滑动，在这一过程中，仅对创口施加小的机械应力。因此，在减小该基质和创口之间的液体垫情况下，创口敷料的佩带舒适度显著增加。而且，在涂覆的薄膜或者基质上的液膜还能防止创口形成新组织生长到基质中。
该创口敷料优选具有由可透过气体但不可透过液体的膜连接在基质上形成的第二层，并具有自粘性第一区域。该基质连接于第二区域的该膜。举例说，该基质与膜连接方式是这样的：其与该膜粘贴在一起或者结合。该自粘性第一区域是该膜的一个区域，其环绕着第二区域，优选有一定间距，通过自粘性第一区域可以将该创口敷料粘贴在人或者动物的皮肤上。粘贴结果形成不透过液体的内部空间，其中充满液体包含基质。该内部空间使得液体创口护理成为可能。
本发明的具体实施方式的理论基础是在通常的潮湿创口治疗中，在创口愈合之前的阶段吸附性材料开始变干燥，因而结果是创口吸取水分。因此，创口愈合过程受到不利的影响。
而且，本发明的实施方式基于这样的认识：创口愈合不仅可以通过创口保湿改善创口的愈合，而且提供更多的液体以使创口上形成液体垫。结果，改善了创口的愈合并且降低了留下疤痕的趋势。这样的创口护理在这里命名为液体创口护理。使用本发明的创口敷料，首先通过将该创口敷料干燥地放置在要治疗的创口上来实现，并且借助自粘性第一区域将其紧贴在创口周围的皮肤上，以使该创口区域由此能被密封而不透过液体来实现。接着，可以借助于套管将该膜刺穿从而液体注入下侧的内部区域。在取出套管之后，在该膜中产生的开口可以通过粘合膜密封。多次注入该液体是有利的，例如每天一次。最终，可以确保该创口永久地保存在液体垫之下直到愈合以及直到将该创口敷料移除。
该自粘性第一区域优选提供粘合剂，该粘合剂具有对皮肤高度亲和性并且不溶于水性液体。这样的粘合剂在现有技术中是已知的，尤其是在贴膏领域。而且，该粘合剂应该能承受内部空间中增大的液体压力而不会从皮肤脱离。液体注入以及该膜施加张力时就已经产生了增大的液体压力。举例说，增大的液体压力也可能由患者引发的创口敷料上的机械应力造成，例如其创口所在的身体部分的移动。
由于事实上该基质与该膜相连接，该基质可以借助于该液体垫而被抬升远离创口。因此，创口与该基质和该抗菌活性物质不直接接触。由于将基质抬升而远离创口，还可以避免所不希望的在创口新形成的组织增生到基质中。因此，正如WO 02/056927 A2所公开的，穿孔层在创口上形成覆盖并且将创口与基质分离不是必需的。正如与已知的创口敷料的情况一样，此处的基质用作该物质的载体而不是为了保持创口潮湿的目的。通过将自粘性第一区域距第二区域一定距离安置，该基质通过该膜连接到第二区域，对于该基质从创口处被提升是帮助的。
创口消毒通过适当选择液体来实现。例如，液体pH低到能最终抑制细菌的繁殖。而且，具有低pH的液体对于创口具有收敛作用，由此有助于愈合过程。而且，该溶液可以包含刺激细胞生长的要素和/或养分。
该物质优选是无机物，尤其是金属或者金属化合物。这样的抗菌活性物质通常不昂贵、易于获得并且易于加工。本文中的金属化合物理解的含义为至少两种金属混合物或者合金。金属离子或者包含金属离子的络合物可以由作为活性物质的金属或者金属化合物形成并被释放。优选地，微动力活性，例如很少量的抗菌活性金属或者微动力活性的抗菌活性金属化合物。
在优选的实施方式中，该物质选自由银、铜和锌、它们的离子以及它们的金属络合物或者混合物或者包含至少一种上述组分的合金。除了上述的金属之外，该合金特别地还含有金和/或铂。这些物质能抗御许多种不同细菌并且能在许多方面干扰它们的新陈代谢。因此，使用这些物质在细菌中发生的抗药性现象要少于使用特殊作用的有机抗菌物质，如抗生素。这些物质优选是银、银的阳离子或者银络合物或者释放银阳离子的络合物或者银合金或者释放银阳离子的合金。尤其是金属银容易加工并且可以相对低的价格获得较大的数量，以至于依次类推，本发明所述的创口敷料也能相对廉价地制备。
该金属或者金属化合物能以簇的形式镀覆在纤维或者基质的表面，尤其通过蒸发作用或者由溅射工艺或者化学气相沉积产生的沉积作用。在蒸发或者沉积的情况下，金属或者金属化合物在真空中加热蒸发随后金属蒸汽沉积在纤维或者基质上。由蒸镀或者沉积镀覆使该金属或者该金属化合物以簇形式存在于纤维或者基质上。该簇具有特别好的抗菌性。
存在于本发明所述的创口敷料中的该物质适宜地呈粒状，优选颗粒或者粒子的平均直径为5-100纳米。该物质可以以独立颗粒或者以相互连结的颗粒的形式存在。可以容易地制备这些抗菌活性物质的细颗粒，尤其对于无机物质，本发明中尤其对于银，而且还对于铜和锌，以及所述这三种金属的混合物、络合物以及合金。由于平均粒径小，该物质的比表面积大，以至于其容易从基质上脱离，尤其是通过扩散。而且，由于比表面积大，该颗粒状活性化合物有时在创口环境中产生化学钝性，但通常仅涉及表面的一部分，以至于在不利环境下可以从基质释放该物质。已经证明该物质的平均粒径是5-50纳米，优选5-20纳米，是有利的。如果该物质是银或者银合金，则这些颗粒粒径分布也认为是纳米级银或者纳米级银合金。
该物质存在的层厚至少1纳米，并且优选不大于1毫米。如果使用颗粒物质，该层至少与活性化合物颗粒一样厚。优选平均层厚至少5纳米-100纳米，特别优选层厚度是10纳米-50纳米，特别地如果该物质是银、铜和/或锌或者它们的离子、金属络合物或者这些元素的混合物或者合金。已经表明即使抗菌物质的、尤其是包含纳米级银的层的厚度小，也足以能实现抗菌但无毒害细胞作用的目的。
该物质优选的含量应使其在使用基质中、尤其全部基质中的液体浸透基质的情况下有抗菌作用。可以通过简单的常规试验测定上述量。如果该物质是金属银，则通过使基质中银含量是基质所覆盖最大面积中每平方厘米1微克-200微克，可以获得足够的抗菌作用。更高的银含量是不利的，因为银离子释放量足以对创口愈合产生不利影响。
优选地，该聚合物是降低细菌粘附于纤维或者基质的聚合物，该细菌优选是革兰氏阴性细菌或者葡萄球菌、尤其是葡萄球菌。除该物质之外，该方法还减少了细菌对基质的移地繁殖。
优选地，通过等离子聚合使纤维或者基质表面涂覆聚合物。因此，涂层非常薄的实施方式成为可能，这几乎不会对该物质的作用有不利地影响。等离子聚合期间，借助于参数的选择，可以改变聚合物的性能。通过常规试验，本领域技术人员能够确定合适的原料以及合适的聚合物层的制备参数。举例说，使用抗菌性物质和等离子聚合对该基质的涂覆可以如下实施：
第一步，纳米级银的颗粒簇镀覆于由无纺布组成的基质上。为此目的，金属银在大约10毫巴的工作压力下于诸如氩气保护气氛下蒸发。在此过程中，银以独立颗粒或者以相互连结的颗粒的形式沉积在基质上。银的颗粒平均粒径大约10纳米-20纳米。银以大约20纳米的厚度镀覆。在第二步，含有六甲基二硅氧烷(HMDSO)的等离子聚合物层作为单体或者前体被涂覆。该等离子聚合在0.07毫巴的工作压力下使用95％氧气和5％ HMDSO作为工作气体。如此进行等离子聚合45秒后，该银镀覆厚度达45纳米并具有强亲水性等离子聚合物层。本文中该涂层表面能为105毫牛/米。
该聚合物涂覆于纤维发生于由纤维制备该基质之前或之后。如果之后发生，则整个基质，如无纺布或者纺织织物要进行涂覆过程，如等离子聚合。如果该聚合物在等离子聚合之后被氧化，则是特别优选的。由此，可以产生高度亲水表面。
在一个优选的实施方式中，该聚合物由丙烯酸的单体、或者由基于硅氧烷尤其是六甲基二硅氧烷的单体形成。这样的聚合物可以将抗细菌粘附性与优异的亲水性相结合。其还使得聚合物所覆盖的物质，如金属银，能对基质有好的作用。
该聚合物优选所在层的平均厚度是5纳米-500纳米。然而，尤其对于等离子聚合聚合物而言，该厚度优选是5纳米-200纳米，优选10纳米-100纳米。以这些层厚，尤其是使用由等离子聚合制备的聚合物层，能产生具有突出的抗菌性和无细胞毒性的涂层。同时，这些涂层很薄，以至于肉眼几乎觉察不到它们或者甚至可以是透明的。
优选地，计算其中该物质的含量以使该物质产生和/或释放的活性化合物的数量在应用情况下不会对创口发生细胞毒害作用。这样的数量可以通过简单的常规试验测定。该活性化合物可以是如金属离子或者这些金属离子的络合物。如果该物质是银，基质中银的合适含量是基质所覆盖最大面积中每平方厘米1微克-200微克，优选5微克-35微克，特别是5微克-15微克。以前一直没有认识到通常使用的含银的创口敷料会释放出银离子，其总量对创口产生细胞毒害作用。因此，干扰了创口愈合。
优选将有助于创口愈合的物质尤其是生长因子结合到基质上。这样的物质可以是如表皮生长因子(EGF)、血小板生长因子(PDGF)、血管内皮细胞生长因子(VEGF)或者角化细胞生长因子(KGF)。优选地，该基质用有助于创口愈合的液体完全浸泡或者充满，尤其是酸性液体或者包含有助于创口愈合的养分的液体。
在一个特别优选的实施方式中，该膜至少部分是透明的。由此，可以观察到该膜以下的液面，从而一旦观测到在内部空间的液体含量减少就可以再充填新液体。
在本发明的另一个特别优选的实施方式中，全部创口敷料包括基质和膜是透光的，尤其对紫外光、红外光或者近红外光。
这可以通过选择适当的材料实现。由此，可以使该创口无需将创口敷料移除就接受光线治疗。光线治疗可以显著加速创口愈合。
优选该创口敷料含有指示剂。该指示剂可以是颜料，其能指示创口敷料或者创口的一定状态。例如，pH指示剂与此有关，其能根据pH改变其颜色。透过至少平常位置是透明的膜可以看到颜色的变化。该指示剂还能由相互作用以指示某种状态的大多数物质形成。该指示剂还可以是传感器。该传感器可以是如导电聚合物，其根据创口或者创口敷料的状态改变其导电性。该传感器还可以是生物传感器。生物传感器理解含义为测量探头，其中生物分子与信号转换器耦合，例如电位器式传感器。信号转换器将某种特定物质与生物分子结合而产生的信号转化为电信号。该传感器可以属于传感器领域或者包含许多传感器的生物传感器领域中的一部分。借助于不同的传感器，可以同时测定许多表征该创口或者该创口敷料的参数。
该指示剂还可以是指示该基质中液体含量的指示剂。因此，可以更好、更早地检测到该基质的干燥。该指示剂还可以是能指示基质或者创口微生物污染程度或者种类的指示剂。例如，这可以通过免疫学指示剂来实现。在此情况下，举例说，微生物或者微生物的局部会由抗体结合，并且由此引发颜色反应。该指示剂还可以是指示创口发炎症状的指示剂。这样的指示剂同样是免疫学指示剂。在此情况下，炎症因子会与抗体特定结合，并且由此引发颜色反应。
而且，本发明涉及一种制备本发明所述创口敷料的方法，具有以下步骤：
-获得吸附性基质，
-获得可透过气体但不透过液体的膜，
-在该膜上涂覆第一自粘性区域(16)以及
-在该膜的第二区域将吸附性基质连接到该膜上，
-该膜的第一区域环绕着该膜的第二区域，
在基质或者形成基质的纤维上，首先通过蒸发或者沉积，溅射工艺或者化学气相沉积抗菌活性物质，然后通过等离子聚合沉积聚合物。
该基质可以是无纺布、纱布、发泡材料或其它软吸附性材料。该物质和该聚合物可以沉积在生成的基质上。该纤维不一定是形成该基质的唯一纤维。形成该基质的纤维可以是该基质制备过程中或之后结合入该基质的纤维。通过蒸发或者沉积，溅射工艺或者化学气相沉积结合等离子聚合，可以获得该物质特别薄并且同时有高抗菌活性的涂覆，以及具有特别性能的该高聚物对于纤维或者基质特别薄的涂覆。仅仅需要少量的物质或者聚合物。该物质为该聚合物所保护，尤其保护不受机械磨损。
以下通过附图更详细解释本发明的一种实施方式：
图1显示的示意图表示本发明创口敷料的侧视图，
图2显示的示意图表示本发明创口敷料的俯视图，
图3显示一系列图，表示与常规的基质以及本发明的创口敷料基质接触时，根据光学密度(OD)形式测量的细菌生长的时间过程。
图1和2显示本发明的创口敷料10具有吸附基质12、可透过气体但不透过液体膜14以及第一自粘性区域16。本文中第一区域16是膜的一个区域，其中涂覆有粘合剂。本文中第一区域16环绕着与基质接触的该膜的第二区域17。当需要使用创口敷料10时，基质12置于创口18之上并且自粘性第一区域16在周围与环绕着创口18皮肤粘贴在一起。之后，液体通过膜14注入通过粘合在一起而形成的内部区域。在注射进入膜14时形成的孔通过粘合膜密封。
在应用研究中，在第一组患者中使用的本发明的创口敷料所具有基质的纤维为银以及通过等离子聚合六甲基二硅氧烷而得到的亲水性聚合物所涂覆。在此情况下的创口敷料使用至少4天以上，用于漏斗胸临床表现的术后液体创口护理。第二组患者使用常规的创口护理以作对比。在第一组患者中无感染发生，而第二组患者偶尔会出现感染。而且，由于亲水性涂层，本发明创口敷料的佩带舒适度显著高于常规护理所用的创口敷料。使用本发明的创口敷料的液体创口护理可以更快痊愈同时形成伤疤的倾向更小。用于创口护理的创口敷料的基质4天后在创口上仍然还有抗菌活性，如图3表示的试验所示。
已经根据DE 197 58 598 A1所公开的方法测定出图3显示的结果。该方法还公开于Bechert，Thorsten等人的Nature Medicine(2000)，第6卷，第8期，第1053-1056页。上述两篇文献所公开的内容为本文所包括。按该试验所述使用进行试验的基质。
在图3中，每个区域显示x-y图，其中时间标注于x轴而光密度标注于y轴。已经按A-H的批次平行试验测定出在图3的第1，2，4，5，11和12列显示的试验结果，相应的行A-H使用以下基质：
列1，行A-H：未涂覆基质，
列2，行A-H：用银和通过等离子聚合六甲基二硅氧烷得到的聚合物涂覆的基质，
列4，行A-H：用银和通过等离子聚合六甲基二硅氧烷得到的聚合物涂覆的基质，其来自上述应用研究中使用4天的第一创口敷料，
列5，行A-H：用银和通过等离子聚合六甲基二硅氧烷得到的聚合物涂覆的基质，其来自上述应用研究中使用4天的第二创口敷料，
列11，行A-H：无菌对比
列12，行A：正面对比
列12，行B：反面对比
列12，行E，F：空白值
在无菌对比的情形下，每种情形仅使用介质而不加入葡萄状球菌，以显示细菌繁殖不是由介质造成的。在正面对比的情况下，使用含金属银聚合物。数值表明所使用细菌对银敏感并且能为之所杀灭。在反面对比的情况下，使用同样的聚合物，然而不含有银。空白数值是在中空的微量滴定盘中测定的数值，在所有测量的计算中将该数值减掉。
试验结果表明，其中基质用银和通过等离子聚合六甲基二硅氧烷而得到的聚合物涂覆的本发明的创口敷料具有高抗菌和杀菌作用。在4天后，创口上仍存在该作用。
Claims (25)
1、创口敷料(10)，包括由吸附性基质(12)形成的第一层以及抗菌活性物质，该抗菌活性物质与该基质(12)的一个表面呈现化学或者物理连接，该基质表面包括涂覆有亲水性聚合物的物质，该创口敷料(10)包括由可透过气体但不可透过液体的膜(14)连接在基质(12)上而形成的第二层，以及具有自粘性第一区域(16)，该基质(12)与膜(14)相连接于第二区域(17)并且第一区域是膜(14)的一个区域，第一区域(16)环绕着第二区域(17)，通过自粘性第一区域可以将创口敷料(10)粘贴在人或者动物的皮肤上，粘贴结果形成不透过液体的内部空间，该内部空间充满液体，该抗菌活性物质是一种金属或者一种金属化合物。
2、如权利要求1所述创口敷料(10)，该基质(12)具有至少一种纤维或者由至少一种纤维形成，并且该抗菌活性物质与该基质(12)的表面结合，该基质(12)的表面是该纤维的表面。
3、如权利要求2所述的创口敷料(10)，将该抗菌活性物质全部地结合到该纤维的表面。
4、如权利要求1或2所述的创口敷料(10)，该抗菌活性物质选自由银、铜和锌、它们的离子以及它们的金属络合物、或者混合物或者包含这些组分中的至少一种的合金组成的组。
5、如权利要求1所述的创口敷料(10)，该金属或者金属化合物能以簇的形式镀覆在基质的表面。
6、如权利要求1或2所述的创口敷料(10)，该抗菌活性物质的平均粒径是5纳米-100纳米。
7、如权利要求1或2所述的创口敷料(10)，该抗菌活性物质所存在层的平均厚度是5纳米-100纳米。
8、如权利要求1或2所述的创口敷料(10)，该抗菌活性物质的存在量能使基质(12)中的液体完全浸透基质(12)的情况下有抗菌活性。
9、如权利要求1所述的创口敷料(10)，该聚合物是降低细菌粘附于纤维或者基质的聚合物。
10、如权利要求2所述的创口敷料(10)，该基质(12)的纤维或者表面是通过等离子聚合涂覆该聚合物的纤维或者表面。
11、如权利要求10所述的创口敷料(10)，该聚合物是在等离子聚合后经过氧化的聚合物。
12、如权利要求1所述的创口敷料(10)，该聚合物由丙烯酸的单体、或者由基于硅氧烷的单体形成。
13、如权利要求1所述的创口敷料(10)，该聚合物所存在层的平均厚度是5纳米-500纳米。
14、如权利要求1或2所述的创口敷料(10)，该抗菌活性物质存在量应使在应用时该抗菌活性物质形成和/或释放的活性化合物的量不会对创口产生细胞毒害作用。
15、如权利要求1或2所述的创口敷料(10)，将有助于创口愈合的该抗菌活性物质，结合到该基质(12)上。
16、如权利要求1或2所述的创口敷料(10)，使用有助于创口愈合的液体，完全浸泡或者充满该基质(12)。
17、如权利要求1所述的创口敷料(10)，该膜(14)是透明的，至少平常位置是透明的。
18、如权利要求1或2所述的创口敷料(10)，该创口敷料可透过光。
19、如权利要求1或2所述的创口敷料(10)，该创口敷料包括指示剂。
20、如权利要求19所述的创口敷料(10)，该指示剂是传感器。
21、如权利要求20所述的创口敷料(10)，该传感器是导电聚合物，该导电聚合物根据创口或者创口敷料的状态改变其导电性。
22、如权利要求19所述的创口敷料(10)，该指示剂还可以是指示该基质(12)中液体含量的指示剂。
23、如权利要求19所述的创口敷料(10)，该指示剂是能指示该基质(12)或者创口微生物污染程度和/或种类的指示剂。
24、如权利要求19所述的创口敷料(10)，该指示剂是能指示创口发炎症状的指示剂。
25、如前述权利要求中任一项所述的创口敷料(10)的制备方法，具有以下步骤：
-获得吸附性基质(12)，
-获得可透过气体但不透过液体的膜(14)，
-在膜(14)上涂覆第一自粘性区域(16)以及
-在膜(14)的第二区域(17)将吸附性基质(12)连接到该膜上，
-第一区域环绕着该膜(14)的第二区域(17)，
在基质(12)或者形成基质(12)的纤维上，首先通过蒸发或者沉积，溅射工艺或者化学气相沉积抗菌活性物质，然后通过等离子聚合沉积聚合物。
Applications Claiming Priority (2)
| Application Number | Priority Date | Filing Date | Title |
|---|---|---|---|
| DE102004001594A DE102004001594B4 (de) | 2004-01-09 | 2004-01-09 | Wundauflage und Verfahren zu deren Herstellung |
| DE102004001594.5 | 2004-01-09 |
Publications (2)
| Publication Number | Publication Date |
|---|---|
| CN1925819A CN1925819A (zh) | 2007-03-07 |
| CN100506197C true CN100506197C (zh) | 2009-07-01 |
Family
ID=34716454
Family Applications (1)
| Application Number | Title | Priority Date | Filing Date |
|---|---|---|---|
| CNB2005800022160A Expired - Fee Related CN100506197C (zh) | 2004-01-09 | 2005-01-05 | 创口敷料 |
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| Country | Link |
|---|---|
| US (1) | US7605298B2 (zh) |
| EP (1) | EP1701676B1 (zh) |
| JP (1) | JP4657222B2 (zh) |
| KR (1) | KR20070001947A (zh) |
| CN (1) | CN100506197C (zh) |
| AT (1) | ATE369825T1 (zh) |
| DE (2) | DE102004001594B4 (zh) |
| DK (1) | DK1701676T3 (zh) |
| ES (1) | ES2293528T3 (zh) |
| HK (1) | HK1101341A1 (zh) |
| PT (1) | PT1701676E (zh) |
| WO (1) | WO2005065603A1 (zh) |
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| AU2001232295A1 (en) * | 2000-02-21 | 2001-08-27 | Daikin Industries Ltd. | Resin composition for preventing attachment of aquatic organism or physiologicalsubstance |
| US6719987B2 (en) * | 2000-04-17 | 2004-04-13 | Nucryst Pharmaceuticals Corp. | Antimicrobial bioabsorbable materials |
| GB0027674D0 (en) * | 2000-11-13 | 2000-12-27 | Johnson & Johnson Medical Ltd | Hydrogel wound dressings |
| CN1529621A (zh) | 2001-01-18 | 2004-09-15 | - | 敷料和用于所述敷料的治疗溶液 |
| US7507870B2 (en) * | 2001-11-23 | 2009-03-24 | Coloplast A/S | Wound dressing |
| EP1465673B1 (en) * | 2001-12-20 | 2007-01-24 | Noble Fiber Technologies, LLC | Wound dressings comprising metallic silver |
| CA2474458A1 (en) * | 2002-01-31 | 2003-08-07 | Mitchell C. Sanders | Method for detecting microorganisms |
| DE102004001594B4 (de) | 2004-01-09 | 2006-09-21 | Bio-Gate Ag | Wundauflage und Verfahren zu deren Herstellung |
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- 2005-01-05 KR KR1020067016039A patent/KR20070001947A/ko not_active Application Discontinuation
- 2005-01-05 DE DE502005001246T patent/DE502005001246D1/de active Active
- 2005-01-05 EP EP05700710A patent/EP1701676B1/de not_active Not-in-force
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Cited By (2)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| CN103052410A (zh) * | 2010-07-09 | 2013-04-17 | 欧瑞康贸易股份公司(特吕巴赫) | 抗菌医疗产品及其制备方法 |
| CN103052410B (zh) * | 2010-07-09 | 2015-04-22 | 欧瑞康贸易股份公司(特吕巴赫) | 抗菌医疗产品及其制备方法 |
Also Published As
| Publication number | Publication date |
|---|---|
| US20070203442A1 (en) | 2007-08-30 |
| DE502005001246D1 (de) | 2007-09-27 |
| KR20070001947A (ko) | 2007-01-04 |
| CN1925819A (zh) | 2007-03-07 |
| EP1701676A1 (de) | 2006-09-20 |
| EP1701676B1 (de) | 2007-08-15 |
| DE102004001594B4 (de) | 2006-09-21 |
| PT1701676E (pt) | 2007-11-22 |
| DE102004001594A1 (de) | 2005-08-04 |
| HK1101341A1 (en) | 2007-10-18 |
| JP4657222B2 (ja) | 2011-03-23 |
| DK1701676T3 (da) | 2007-12-10 |
| WO2005065603A1 (de) | 2005-07-21 |
| US7605298B2 (en) | 2009-10-20 |
| JP2007517557A (ja) | 2007-07-05 |
| ES2293528T3 (es) | 2008-03-16 |
| ATE369825T1 (de) | 2007-09-15 |
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