CN1168988C - 用于血液中葡萄糖测定的试剂测试条 - Google Patents
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Abstract
一种试剂测试条适合在血液葡萄糖浓度计中采用。将未经稀释的纯血液试样涂覆到该条上的基质的一个表面上,该测量仪表测量基质的对侧表面对大约635毫微米和700毫微米波长的光的反射率,并由该反射率计算在试样中的葡萄糖浓度。透过基片并由测试表面可见的部分涂覆试样不明显吸收波长为700毫微米的光。但是含葡萄糖的试样与含试剂的基质的成分反应使模拟血液颜色效果的700毫微米光的反射率变化。因此,该测试条可以用于在有可见的血红蛋白存在情况下测量未经稀释的纯血液中的葡萄糖浓度的测量仪表。
Description
技术领域
本发明涉及一种用于测量在生物体液中的分析物浓度的干态测试条;更具体地说,涉及一种通过颜色测定在未经稀释的纯血液中的葡萄糖浓度的测试条。
背景技术
为了测量在生物体液中包含的分析物的浓度已经研究开发了很多利用目视的测试装置。这些装置用于测量例如在血液、尿或唾液的葡萄糖、胆固醇、蛋白质、酮、苯基丙氨酸或酶。
包含以酶为基的化合物的干态试剂条广泛用于医院、临床实验室、医生工作室和家中,以便测试生物体液试样的葡萄糖浓度。实际上,对于各国的几百万糖尿病患者,试剂条已经成为日用必需品。由于糖尿病能够引起血液化学性质出现危险的异常,所以会导致失明,肾功能衰竭以及其它严重的医学后果。为了使这些后果的危险降到最小,现在通常劝告患有糖尿病的人根据他们个人病情的情况和严重程度,每天测量2到7次他们的血液葡萄糖浓度。根据对所测量的葡萄糖含量观察的结果,病人和医生一起对饮食、锻练和胰岛素摄取量进行调节,以便更好地控制病情。很明显,通过利用简便实用的测量仪表和测试条组成的快速、低成本和精确的装置,病人可以迅速得到这种信息。
已知在试剂条中含有一种指示剂,这种指示剂根据施加到试剂条上的生物体液中的葡萄糖浓度,呈现出不同的颜色层。虽然,某些试样条使用较少的化学试剂,但是它们大多包含可氧化的染色物或染色物耦合剂。某些测试条包括酶,例如葡萄糖氧化酶,这种氧化酶能够将葡萄糖氧化成葡萄糖酸和过氧化氢。它们还包含一种可氧化的染色物和一种具有过氧化活性的物质,能够可选择地对存在于过氧化氢中的可氧化的染色物的氧化产生催化作用。
1990年6月19日授权给Rhillips等人的美国专利US-4935346中公开了一种用于测定在未经稀释的纯血液试样中的葡萄糖浓度的测量仪表、试样条和方法(还参见US-5304468)。该方法包含简单地将未经稀释的纯血液的试样涂覆到用试剂浸渍的惰性的微孔基质的第一(试样)表面。在葡萄糖与试剂发生反应而形成一种吸收光的反应产物时,该试样朝反面的“测试”表面移动。对于测试表面反射率的测定指示出葡萄糖浓度。为了消除干扰,反射率的测量是在两个不同的波长下进行的。计时电路是由通过基质的试样浸湿测试表面而引起的反射率的起始下降触发的。
1994年4月26日授权给Kister等人的美国专利US-5306623中公开了一种可目测的血液葡萄糖测试条,其包含将含有葡萄糖的未经稀释的纯血液试样涂到测试条的一侧,在红血球细胞已经分离出来,并且试样已经与测试条中的试剂发生反应之后,在相反的一侧测量葡萄糖含量。已经发现一种各向异性的聚砜薄膜作为测试条的单层基质是特别实用的。
1995年9月26日授权给Y.S.Yu的美国专利US-5453360中公开了一种用于检测在生物体液中的分析物例如葡萄糖的干态试剂条中的染色物耦合剂。该染色物耦合剂包含3-甲基-2-苯并噻唑啉酮(benzothiazorinone)腙和8-苯氨基-1-磺酸萘(naphthalenesulfonate),并用作在产生很强的氧化剂例如过氧化氢的级联反应中的指示剂。这种耦合剂的优点在于,它可溶解在水溶液中,但由于氧化耦合作用变成不可溶的,因此使褪色最小,提供稳定的最终结果。
已经广泛投入使用的自行监测血液葡萄糖的测量仪表是One TouchII型测量仪表,其采用上述US-4935346和US-5304468中所介绍的测试条。该测量仪表和测试条让使用者可经快速简易和精确地测量在未经稀释的纯血液试样中的葡萄糖浓度。将试样涂覆到测试条的一个表面上,在相反表面上进行测量。一部分未经稀释的纯血液试样从采样表面向测试表面渗透,从测试表面可观察到血液的颜色。
发明内容
本发明提供一种在测定未经稀释的纯血液试样中的葡萄糖浓度的装置中使用的试剂测试条。该装置包含光学装置,用于检测由靠近测试条一端配置的至少一部分基质反射的约635毫微米和约700毫微米波长的光的强度,该基质包含:
(a)试样接收表面,用于接受未经稀释的纯血液试样,该试样的一部分朝着与接收表面相反的测试表面透过,
(b)一种结构,选择性地阻滞红血球细胞通过该基质并使得在该基质中的红血球细胞溶解得最少,因此,由测试表面可以看到的试样的任何部分不吸收任何明显程度的约700毫微米的光,以及
(c)一种试剂,用于通过在测试表面上对约700毫微米的光的反射率变化来指示葡萄糖浓度,这种变化基本上等效于由在血液中的血红蛋白的吸收率产生的变化以及在指示葡萄糖浓度的大约635毫微米光的反射率的变化。
在本说明书和所提出的权利要求中,所述事实“从测试表面可见的试样不吸收任何明显程度的约700毫微米的光”意指当通过测试表面观察时,试样对700毫微米光的吸收率比由于试样与试剂反应所引起的对700毫微米光的吸收率小大约20%。
本发明的另一实施例也提供一种在用于测定未经稀释的纯血液试样中的葡萄糖浓度的装置中使用的试剂测试条。该装置包含的光学装置,用于检测从靠近测试条的一端配置的至少一部分基质反射的大约635毫微米和700毫微米波长的光的强度,该基质包含:
(a)试样接收表面,用于接收未经稀释的纯血液试样和使其一部分朝着与该表面相反一侧的测试表面透过,当测试表面变湿时,测试表面对约700毫微米光的反射率产生变化,其基本上等效于由在血液中的血红蛋白吸收率所产生的变化,
(b)一种结构,选择性地阻滞红血球细胞通过该基质并使得在该基质中的红血球细胞溶解得最少,因此,从测试表面可见的试样任何部分不吸收任何明显程度的约700毫微米的光,以及
(c)一种试剂,用于在测试表面产生在约635毫微米光下的反射率变化来指示葡萄糖浓度。
本发明提供的试剂测试条适合于在One Touch纯血液葡萄糖浓度计中使用。由于条的结构选择性地阻滞红血球细胞通过该基质并使它们的溶解降到最少,使葡萄糖测定与纯血液试样的血红蛋白相对无关。
附图说明
图1是本发明的测试条的一个实施例的透视图。
具体实施方式
本发明提供了一种快速简单的方法,其采用了一种可靠而易于操作的装置,用于测定在未经稀释的纯血液中的葡萄糖含量。该方法包含将少量的未经稀释的纯血液涂覆到惰性的微孔基质的一个表面(“试样表面”)上,使该基质饱和。当涂覆血液时,该基质通常在一反射率测量装置中。至少一部分液体试样透过该基质,导致在相反的(“测试”)表面的反射率开始发生变化。在试样中的葡萄糖与结合到基质上的一种或多种试剂反应,形成一种改变基质反射率的产物,在起始的反射率变化之后,进行一次或多次测量读数,以将在反应测试表面上或基质中的反射率的进一步变化和试样中葡萄糖浓度关连起来。
图1表示本发明的一个实施例。一个薄的亲水性的基质试剂片11利用粘接剂13定位在一塑料支撑物12的一端,这种粘接剂直接和牢固地使试剂片附着到该支撑物上。该支撑物使试剂条具有一定物理形状和刚性,但它是可有可无的。在塑料支撑物12上附着试剂片的区域内有孔14,使得试样可以通过孔14涂覆到试剂片的试样侧,而光从另一侧即测试侧反射。
将待测试的未经稀释的纯血液试样涂覆到片11上。通常试剂片表面面积约为10到100平方毫米,特别是10到50平方毫米,所提供的试样体积一般为5-10微升,使之能多于饱和。
关于测试条的结构的另外的细节在上述美国专利US4935346(’346)和US-5304468(’468)中做了介绍,这里引用作为参考。
本发明的分析方法依据吸收率的变化,即对漫反射率的测量结果,这个测量结果依赖于在待测试的试样中存在的葡萄糖浓度。这种变化通过以一个或多个时间间隔测量反射率的变化来测定。
在操作过程中,在涂覆试样之前将测试条首先装到一利用反射率测量光吸收率(例如对彩色光强度)的仪器上。然后,将例如通过刺手指得到的含葡萄糖的血液试样涂覆到测试条中的基质上。最好,使其数量超过使在所要测量所射率的区域内的基质饱和所需的数量(即约5-10微升)。在将试样涂覆之后,当液体穿透基质时,测量时间被自动激发,并且装置检测所形成的测试表面反射率的变化。由于形成反应产物的作用结果,在预定时间范围内的反射率的变化与试样中的葡萄糖浓度相关。在本说明书和所提出的权利要求中反射率是针对可见光、红外线和紫外线范围的光。
一种适当的仪器例如利用适当软件的漫反射光度计可以按照一个或多个时间间隔测量反射率,计算反射率变化以及利用校正系数输出在血液试样中的葡萄糖浓度。这种仪器的细节包括利用仪器将反射率的测量值变换为血液中的葡萄糖浓度的方法在’346和’468中介绍。特别是商用的One Touch计适合与本发明的试剂条结合使用,来测量在未经稀释的纯血液试样中的葡萄糖浓度。这类测量仪表可测量在约635毫微米和700毫微米光的在试剂条上的测试表面的反射率。
本发明中的基质最好是一种薄膜,其有效地从未经稀释的纯血液试样中将红血球细胞和血红蛋白分离而留下含葡萄糖的血浆。当试样从试样表面向测试表面透过薄膜时实现这种分离。实现这种分离的薄膜形成有可截获红血球细胞的孔,孔的尺寸通常大约0.1到5微米。最好,在孔的尺寸范围方面薄膜是各向异性的,更为优选的是孔的尺寸有一定的范围。当基质包含一各向异性的薄膜时,试样侧面最好具有较大的孔。例如,延伸通过薄膜的孔的尺寸的变化梯度可以从约0.1到约150微米。在大孔一侧,孔尺寸最好处在从约30到约40微米的范围内。在孔最小的薄膜一侧上(即测试表面),空隙的体积是相对小的,薄膜材料通常是十分致密的(通常可能构成薄膜厚度20%)。在这一层内,孔的尺寸最好处在从约0.1到0.8微米的范围内,而标称的孔的尺寸最好约0.3微米。
当将未经稀释的纯血液试样涂覆到该试样侧时,随着试样透过薄膜,该试样会遇到越来越小的孔,最终,固体物质例如红血球细胞到达通常接近试样表面的薄膜的一定位置,在该处它们不再继续透过。薄膜不仅在接近试样表面处截获红血球细胞,而且还使细胞的溶解降至最少,使得从测试表面可见到的试样的任何部分不会吸收任何明显程度的大约700毫微米的光。仍然包含溶解的葡萄糖的剩余试样穿透到测试侧。当其通过薄膜时,试样中的葡萄糖与试剂反应,在靠近测试侧产生吸收光的染色物,从而显著影响测试表面的反射率。薄膜的各向异性的特性和/或分离成分的使用(下面讨论)使得试样能以相对快的速度通过薄膜,最终产生固体微粒的分离。
基质是亲水性的微孔薄膜,试剂可以利用共价键或非共价键的方式结合到其上。该基质使含水的介质能够通过其间。它还能在对蛋白质的生物活性例如酶的活性不产生明显有害影响情况下将蛋白质组合物结合到基质上。为了使蛋白质以共价键的方式结合到一定程度,基质将有活性区域提供共价键结合或者可以利用已知的现有技术使基质活化。基质的构成会产生反射,并具有足够的厚度使得在空隙的容积内或在表面上能形成吸收光的染色物,对由基质产生的反射产生实质的影响。基质可以是均匀的组合物或在基片上能提供必需的结构和物理性能(例如亲水性)的涂层。
聚砜和聚酰胺(尼龙)是适宜的基质材料的实例。也可以采用具有类似性能的其它聚合物,该聚合物可以改进,引入其它官能基团来形成带电结构,使基质的表面可以是中性的、带正电或负电。
制备该形成基质的微孔材料的优选方法是通过不用承载芯体来浇注聚合物。这种基质为例如从Memtec,Inc.,Timonium,MD购得的各向异性的聚砜薄膜。在这里术语“基质”和“薄膜”是可互换使用的。要理解每一术语并不局限单层,例如可以包括一吸收层。通常采用厚度约小于500微米的基质,最好为115到155微米。大约130到140微米的厚度是最适宜的,特别是当该基质是尼龙或各向异性的聚砜时。该基质通常不因受潮而变形,因此维持其原有的结构和尺寸,具有足够耐湿强度,使得能进行例行的加工。
浸渍该薄膜使能与葡萄糖反应产生吸收光的产物的测试试剂浸入微孔。试剂对薄膜的处理可以通过将薄膜浸入含一些成分的混合物从而使薄膜饱和。多余的试剂可以利用机械工具例如气动刀,刮刀或玻璃棒除去。然后将薄膜干燥。在薄膜的小孔侧(测试侧)附近的试剂倾向于浓缩。用于将试剂涂覆到薄膜上的其它适宜的方法对于本技术领域的一般熟练人员也易于采用。
测试试剂包含用于将葡萄糖变为过氧化氢的成分和用于检测过氧化氢的成分。试剂还可以包含一种分离用成分,其使固体微粒例如红血球细胞变为在基质中可被截获的,从而有效地从未经稀释的纯血液中除去该固体。如下所述,还可以包括其它的成分。
用于将葡萄糖变为过氧化氢的优选的成分包括葡萄糖氧化酶,即通常由黑曲霉属(Aspergillus niger)或盘尼西林(Penicillium)得到的酶。葡萄糖氧化酶与葡萄糖和氧反应产生葡糖酸内脂和过氧化氢。最佳的葡萄糖氧化酶浓度取决于指示剂体系的成分;然而,从约500到10000单位/毫升(U/mL)范围的葡萄糖氧化酶通常是适宜的,更可取的是约700-2000单位/毫升(U/mL)。通常,葡萄糖氧化酶的浓度越高使反应进行得越快,浓度越低,速度越慢。通过例行实验可以确定最佳浓度。
这样产生的过氧化氢与用于检测过氧化氢的成分反应,该成分包含选择性地催化过氧化氢和指示剂之间反应的过氧化酶。过氧化酶利用过氧化氢作为氧化剂,其能从各种基质除去氢原子。高铁原卜啉(ferriprotoporphyrin),一种从植物(Plants)得到的红色的氯高铁血红素,可以作为一种适宜的过氧化酶。由动物例如由动物的甲状腺得到的过氧化酶也是适用的。辣根过氧化酶(HRPO)作为一用于检测过氧化氢的成分的组分是特别适宜的。最好利用过氧化酶催化的过氧化氢或者直接或者间接反应形成在测试表面降低635毫微米光的反射率的指示剂染色物。测试表面反射率是在两种波长—约635毫微米和700毫微米下测量的。
接时间顺序进行反射率测量。由试样的一部分到达测试表面导致在635毫微米光的反射率下降开始测试程序。我们将这一时间的起始称为“反射率转换”。在经15秒之后测量在700毫微米光下的反射率。到这时,血液将使试剂片饱和,含葡萄糖的血液试样与含试剂的薄膜的反应将会引起在700毫微米光下的反射率降低,即基本等效于在测试表面上可见的血液颜色产生的褪色。因此,从测试表面可见的试样不会吸收任何明显程度的波长为700毫微米的光,测量仪表检测与因血液颜色的吸收作用相关的在700毫微米光的反射率的下降,并且其后在约635毫微米光下进行反射率测量。由635毫微米光的反射率计算试样中的葡萄糖浓度,利用700毫微米光的反射率来计算校正系数。应指出,由于血液在635毫微米时产生吸收,血液模拟材料也应是对700毫微米光的吸收剂。按理想方式,血液模拟材料应当具有与纯血液相同的对700毫微米波长光的吸收率与对635毫微米波长光的吸收率之间的比率,但是为了简单明了,我们仅涉及在700毫微米下的血液模拟材料的吸收率。计算的细节,包括对在700毫微米下的“血液”反射率的校正,在上述‘346中作了介绍。
模拟血液颜色的在700毫微米波长光下降低的测试表面反射率可以按4种不同的方式来影响。首先,可以使薄膜包含一种吸收700毫微米光线的成分,并且该测试表面可以是基本上不透明的,直到当受潮时对700毫微米的光才变得较为透明。吸收700毫微米光的成分可以是一种非织品,例如在干的测试表面是不可见的。该成分也可以是一种薄膜浇注在其上的支承体、在薄膜的试样表面上的涂覆层或类似物。
第二,薄膜可以包含一种水溶性的染色物,其在700毫微米光下具有较小的(light)吸收率,当该染色物溶解时则明显增加。例如,该染色物最初可以制成精细的分散的水溶性的晶体,作为散布的固体微粒涂到薄膜上,呈白色,在700毫微米的光下吸收率基本上为零。含水的试样溶解该染色物,在这种情况下其变为带色,吸收在700毫微米的光。这种染色物的一个实例是酞菁铜。
第三,在葡萄糖和在薄膜中的试剂之间的反应可能导致形成生色团,其吸收在635和700毫微米的光,从而指示葡萄糖浓度,同时模拟血液的存在。
最终,血液—试剂反应可以产生两种生色团,其中之一吸收635毫微米的光,另一个吸收700毫微米的光。此外,由于仅需要700毫微米的光的反射率足够降低以模拟血液颜色的出现,最好仅出现少量的吸收700毫微米的光的生色团。
在前两种情况下,其中700毫微米光的吸收率(即降低的反射率)是由另一种薄膜成分形成的,700毫微米光的吸收率不需要生色团。在第三和第四种情况下,700毫微米光的反射率的下降是受生色团影响。然而在每一种情况下,在反射率转换之后15秒从测试表面观察的700毫微米光的反射率下降必能模拟血液颜色,正如在‘346中详细介绍的。
在测试时间程序的起始之后的一适当的时间正如按在‘346中所公开的调节的,635毫微米光的反射率下降的幅度用来测量在未经稀释的纯血液度样中的葡萄糖浓度。适于用作指示剂的染色物耦合剂包括4-氨基安替比林(AAP)和变色酸;AAP和8-苯胺基-1-磺酸萘(ANS);AAP和P-乙基-N(2羟基-3-硫代丙基(sulfopropyl)-m-丙苯胺(TOOS);3-甲基-2-苯并噻唑啉酮腙氢氯化物(benzothiazolinone hydrozone hydrochloride)(MBTH)和ANS;与3-二甲基氨基苯甲酸(DMAB)组合的MBTH;以及与其甲醛丫嗪(formaldehyde azine)组合的MBTH。
虽然,作为优选的基质的各向异性的薄膜滤出了红血球细胞并将它们截留远离测试侧,也可以通过选择使测试剂包含一种分离用的成分(例如参阅上述授予Kiser等人的US-5306,623)。通过分离在基质中的红血球细胞,并且最好还分离少量的游离的血红蛋白,该分离用成分能够由包含红血球细胞的液体例如未经稀释的纯血液产生相对清晰的无色液体。在本发明中使用的分离用成分包含但不局限于聚乙二醇、聚(乙烯基甲基醚/顺丁烯二酸)酐、聚丙二醇、聚苯乙烯磺酸、聚丙烯酸、聚乙烯醇以及pH值约4.0-8.0的聚乙烯磺酸。这些存在于基质中的分离用的成分的数量将随它们的电荷以及分子量、置入基质的其它成分、基质PH值和孔和尺寸以及干燥之后基质中的剩余水分而变化。这些参数易于由本技术领域的熟练人员所测定。例如,当采用聚丙二醇作为分离用成分(例如PPG-410,由BASF,Wyandotte,MI购得)时,最好单位体积重量(W/V)约占2-30%,更优选8-10%(W/V)。浓度大约2-30%W/V的其它分离用成分也可以采用。在薄膜制造过程之中,可以将聚合物的分离用成分通过浸渍和灌注进入基质中。
某些水溶性的盐类也可以影响血液的分离。在适用于分离血液成分的盐类之中有柠檬酸盐、甲酸盐、硫酸盐以及某些酸,例如氨基酸、柠檬酸、植酸(例如参见1971,1.5授予MC.Fetter的US-3552928)。分离用成分最好包含在测试试剂中,因为它们会在保证没有明显数量的红血球透过方面而提高薄膜的有效性。因此,它们保证从测试表面可见的试样不明显吸收波长为700毫微米的光。
另一些成分可以置入基质以便增强试剂条的显色性和可读性以及保持基质的均匀性和整体性。例如,测试剂可以包括有助于分离在基质中的染色物的盐类和/或缓冲剂。这些缓冲剂例如可以包含存在于溶液中从大约0.01M(摩尔)到大约1.0M的柠檬酸盐,优选大约0.1M。也可以采用其它缓冲剂。
还可以采用使基质成为亲水性的成分和可以用作稳定剂的成分。这些成分例如包括但不局限于牛白血清蛋白、多酞以及低分子量蛋白,由Crotein SPA(CRODA,Inc,New Yorh,N,Y)可购得。这些成分使用浓度例如为约1到100毫克/毫升。在Crotein的情况下,最好为约30毫克/毫升。
在用于基质的涂覆层中还可以包括其它稳定剂和防腐剂。例如乙二胺四乙酸(EDTA)、二亚乙基三胺五乙酸(DTPA),以及相关化合物例如可以按照从约0.01到10毫克/毫升的浓度采用。
在不脱离本发明的范围和构思的情况下,可以对其中的细节进行各种改变。
Claims (13)
1、一种试剂测试条,用在用于测定在未经稀释的纯血液试样中的葡萄糖浓度的装置中,该装置包含用于检测由靠近该条一端配置的至少一部分基质反射的约635毫微米和约700毫微米波长的光的强度的光学装置,该基质包含:
a)试样接收表面,用于接收未经稀释的纯血液试样以及使其一部份朝与该表面相反的测试表面透过,当测试表面变湿时测试表面对700毫微米光的反射率产生变化,其等效于在血液中由于血红蛋白的吸收率产生的变化,
b)一种结构,其选择性地阻滞红血球细胞通过基质并使在基质中该细胞的溶解最少,因此由测试表面可见的任何试样部分不明显吸收波长约为700毫微米的光,以及
c)一种试剂,用于通过在测试表面处使在约635毫微米的光的反射率的变化来指示葡萄糖浓度。
2、如权利要求1所述的测试条,其特征在于:所说的基质包含一具有能截获未经稀释的纯血液试样中的红血球细胞的微孔的薄膜。
3、如权利要求1所述的测试条,其特征在于:所说的基质包含一在孔的尺寸方面各向异性的薄膜。
4、如权利要求3所述的测试条,其特征在于:所说的薄膜具有的微孔靠近试样接收表面较大,而靠近测试表面较小。
5、如权利要求1所示的测试条,其特征在于:所说的基质包含聚酰胺薄膜。
6、如权利要求1所示的测试条,其特征在于:所说的基质具有内部区域,该内部区域吸收700毫微米波长的光,并且当测试表面变湿时才能从测试表面看到。
7、如权利要求6所述的测试条,其特征在于:所说的基质内部区域包含实质吸收700毫微米的光的非织材料。
8、如权利要求1所述的测试条,其特征在于:所说的基质还包含水溶性的染色物,其对700毫微米的光的吸收率当染色物变为溶液时明显增加。
9、如权利要求8所述的测试条,其特征在于:所说的染色物包含酞菁铜。
10、如权利要求1所述的测试条,其特征在于:所说的试剂包含染色物的母体,其形成指示葡萄糖浓度的生色团,该生色团吸收635毫微米波长的光。
11、如权利要求10所述的测试条,其特征在于:所说的试剂染色物母体选自:
a)与3-二甲基氨基苯甲酸组合的3-甲基-2苯并噻唑啉酮腙氢氯化物;
b)与8-苯胺基-1-一磺酸萘组合的3-甲基-2苯并噻唑啉酮腙氢氯化物;
c)与其甲醛丫嗪化合的3-甲基-2苯并噻唑啉酮腙氢氯化物;以及
上述a)、b)、c)中的至少两种的组合物。
12、如权利要求10所述的测试条,其特征在于:所说的试剂染色物母体是与8-苯胺基-1-一磺酸萘组合的3-甲基-2苯并噻唑啉酮腙氢氯化物。
13、如权利要求10所述的测试条,其特征在于:所说的试剂染色物母体是与3-二甲基氨基苯甲酸组合的3-甲基-2苯并噻唑啉酮腙氢氯化物。
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CNB971116741A Expired - Lifetime CN1168988C (zh) | 1996-04-04 | 1997-04-04 | 用于血液中葡萄糖测定的试剂测试条 |
Country Status (15)
Country | Link |
---|---|
US (1) | US5753452A (zh) |
EP (1) | EP0800082B1 (zh) |
JP (1) | JPH1031024A (zh) |
KR (1) | KR100553108B1 (zh) |
CN (1) | CN1168988C (zh) |
AT (1) | ATE222365T1 (zh) |
CA (1) | CA2201571C (zh) |
DE (1) | DE69714637T2 (zh) |
DK (1) | DK0800082T3 (zh) |
ES (1) | ES2181991T3 (zh) |
IL (1) | IL120586A (zh) |
MX (1) | MX9702503A (zh) |
NO (1) | NO317632B1 (zh) |
PT (1) | PT800082E (zh) |
TW (1) | TW507076B (zh) |
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CN104749169A (zh) * | 2013-12-31 | 2015-07-01 | 比亚迪股份有限公司 | 血糖检测装置以及血糖检测试剂盒 |
TWI699535B (zh) * | 2019-10-09 | 2020-07-21 | 林文貴 | 檢測條之製造方法 |
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- 1997-04-02 CA CA002201571A patent/CA2201571C/en not_active Expired - Lifetime
- 1997-04-03 DE DE69714637T patent/DE69714637T2/de not_active Expired - Lifetime
- 1997-04-03 AT AT97302306T patent/ATE222365T1/de active
- 1997-04-03 PT PT97302306T patent/PT800082E/pt unknown
- 1997-04-03 ES ES97302306T patent/ES2181991T3/es not_active Expired - Lifetime
- 1997-04-03 JP JP9099565A patent/JPH1031024A/ja active Pending
- 1997-04-03 EP EP97302306A patent/EP0800082B1/en not_active Expired - Lifetime
- 1997-04-03 DK DK97302306T patent/DK0800082T3/da active
- 1997-04-03 NO NO19971514A patent/NO317632B1/no not_active IP Right Cessation
- 1997-04-04 CN CNB971116741A patent/CN1168988C/zh not_active Expired - Lifetime
- 1997-04-04 MX MX9702503A patent/MX9702503A/es unknown
- 1997-04-04 KR KR1019970012450A patent/KR100553108B1/ko not_active IP Right Cessation
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Publication number | Priority date | Publication date | Assignee | Title |
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CN104749169A (zh) * | 2013-12-31 | 2015-07-01 | 比亚迪股份有限公司 | 血糖检测装置以及血糖检测试剂盒 |
CN104749169B (zh) * | 2013-12-31 | 2018-04-20 | 比亚迪股份有限公司 | 血糖检测装置以及血糖检测试剂盒 |
TWI699535B (zh) * | 2019-10-09 | 2020-07-21 | 林文貴 | 檢測條之製造方法 |
Also Published As
Publication number | Publication date |
---|---|
ATE222365T1 (de) | 2002-08-15 |
IL120586A0 (en) | 1997-08-14 |
NO317632B1 (no) | 2004-11-29 |
KR970071006A (ko) | 1997-11-07 |
CA2201571A1 (en) | 1997-10-04 |
EP0800082B1 (en) | 2002-08-14 |
NO971514L (no) | 1997-10-06 |
DK0800082T3 (da) | 2002-12-02 |
KR100553108B1 (ko) | 2006-06-21 |
US5753452A (en) | 1998-05-19 |
CA2201571C (en) | 2007-03-27 |
JPH1031024A (ja) | 1998-02-03 |
DE69714637T2 (de) | 2003-04-10 |
PT800082E (pt) | 2002-12-31 |
IL120586A (en) | 2000-10-31 |
CN1171553A (zh) | 1998-01-28 |
TW507076B (en) | 2002-10-21 |
MX9702503A (es) | 1998-04-30 |
EP0800082A3 (en) | 1998-12-23 |
DE69714637D1 (de) | 2002-09-19 |
EP0800082A2 (en) | 1997-10-08 |
ES2181991T3 (es) | 2003-03-01 |
NO971514D0 (no) | 1997-04-03 |
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