固定有四硫富瓦烯.四氰基奎诺二甲烷的杂聚吡咯膜微葡萄糖电极

铂比互铂化处理后，形成疏松，粗糙的表面，将四硫富瓦烯－四氰基奎诺二甲烷导电有机盐入到铂化的铂黑微粒中。将３－羰基丁酸吡咯与吡咯按适当的比例在其表面用电化学聚合方法，将葡萄糖氧化酶固定于聚合形成的杂聚膜中制成微酶电极。该微酶电极测定时几乎不受氧分压影响，灵敏度高，响应快。     

层层自组装制备基于多壁碳纳米管的胆碱生物传感器

以经混酸处理的多壁碳纳米管(MWCNTs)修饰铂(Pt)电极,在此基础上固定(PAA/PVS)3复合膜,采用层层自组装技术将高分子聚电解质PDDA与胆碱氧化酶交替组装在已修饰的电极上,构建了电流型胆碱生物传感器。实验结果表明,MWCNTs的引入使电极对H2O2的催化电流明显增大,制成的酶电极可以有效控制酶量的使用,酶膜组装层数为8时最优,对胆碱的线性响应范围为5×10-7～1×10-4mol/L;灵敏度为12.53μA/mmol;响应时间为7.60s;检出限为2×10-7mol/L(S/N=3)。传感器的抗干扰能力强,稳定性好,30d时的响应电流值仍保持最初的89.5%。3次平行实验的RSD为3.64%。     

聚亚甲基蓝和纳米金修饰玻碳电极的葡萄糖生物传感器

用循环伏安法在玻碳电极上电聚合一层稳定的亚甲蓝聚合物膜,研究了这层膜在0.1mol/L磷酸缓冲溶液(pH7.0)中的电化学性质。用纳米金溶胶与聚乙烯醇缩丁醛(PVB)构成复合固酶基质,采用溶胶-凝胶法固定葡萄糖氧化酶(GOD)于亚甲蓝修饰的玻碳电极表面,制成了新型葡萄糖生物传感器。实验发现,加入纳米金后提高了酶电极对葡萄糖的电流响应,所制备的传感器具有响应快、灵敏度高、稳定性好,对葡萄糖的线性响应范围为1×10-6~3×10-3mol/L,检出限为5×10-7mol/L。并具有抗尿酸、抗坏血酸干扰的特点。     

氧化铜-过氧化聚吡咯-还原氧化石墨烯复合膜修饰电极非酶检测葡萄糖

先以氧化石墨烯(Graphen oxide,GO)为阴离子掺杂剂,采用电化学聚合法制备了聚吡咯-氧化石墨烯复合膜(PPy-GO)。分别在0.10 mol/L Na Cl和0.10 mol/L NaOH溶液中对其进行还原和过氧化处理,制得过氧化聚吡咯-还原氧化石墨烯复合膜(OPPy-ERGO)。再以此OPPy-ERGO复合膜为载体,采用电化学沉积法制备了氧化铜-过氧化聚吡咯-还原氧化石墨烯复合膜修饰电极(CuO-OPPy-ERGO/CCE)。通过扫描电镜和电化学方法对此电极进行表征,研究了葡萄糖在此修饰电极上的电化学行为。结果表明,此电极对葡萄糖的电氧化过程表现出高的催化活性和良好的抗干扰能力。在0.20 mol/L NaOH溶液中,安培法检测葡萄糖的线性范围为5.0×10~(-7)~1.0×10~(-3)mol/L,检出限(3Sb)为2.0×10~(-7)mol/L,灵敏度为121.8μA/(mmol·L~(-1))。该电极用于血清中葡萄糖含量的测定,加标回收率为96.0%~110.1%。     

聚吡咯尿酸酶电极的生物电化学活性

聚吡咯尿酸酶电极具有快速的生牧电化学响应.在5.9×10^-6mol·dm^-3至1.5×10^-3mol·dm^-3的尿酸浓度范围内,酶电极的响应电流与底物浓度之间呈线性关系.固定酶的催化反应活化能为34.81kJ ·mol^-1.与可溶性的尿酸酶相比,聚吡咯尿酸酶电极的一些生物活性,如与溶液的pH和温度的关系,发生了有利的变化.     

电流型聚吡咯碘离子化学修饰电极的制备与性能研究

在玻碳电极(GCE)表面上修饰了一层导电聚合物 聚吡咯(Ppy)薄膜,用循环伏安法制备了新型的基于电流响应的掺杂碘离子的聚吡咯修饰电极;研究了电极的电化学特性。此修饰电极对碘离子的响应是基于碘离子在Ppy膜与电解质溶液中的掺杂平衡以及Ppy膜中的碘离子在修饰电极表面的氧化还原过程;制成的电流型电极对5 0×10-2mol/L～1 0×10-5mol/L的碘离子呈良好的线性响应关系,检出限为6 0×10-6mol/L。     

聚吡咯修饰乳酸氧化酶电极的研制

根据聚吡咯修饰电极掺杂和去掺杂原理，将乳酸氧化酶固定在玻碳电极表面形成一种新型的乳酸酶电极，该电极灵敏度高，稳定性好，易于制作。本文报道了该电极的研制过程，探讨了影响电极响应的各种因素，找出了最佳实验条件。将此电极用于实际样品中乳酸含量的测定，结果令人满意。     

基于聚吡咯纳米线修饰玻碳电极的硝酸根电流型传感器研究

在玻碳电极表面,采用电聚合方法一步制备聚吡咯纳米线。由于聚吡咯的电化学氧化还原过程伴随有硝酸根的掺杂/脱掺杂,基于此构建了硝酸根电流型传感器。详细探讨了电聚合溶液的pH值、电聚合电位、电聚合时间、富集电位和富集时间对聚吡咯纳米线形貌,以及对硝酸根在修饰电极表面电化学响应的影响。在最佳条件下,构建的硝酸根传感器的线性范围为1.0×10-3～4.0×10-3 mol/L,检出限(S/N=3)达到2.2×10-4 mol/L,且具有良好的稳定性、重现性以及抗干扰能力。     

基于石墨/聚吡咯电极的葡萄糖生物传感器

采用电化学聚合技术,在掺杂的导电聚吡咯薄膜修饰过的铅笔芯电极上,吸附葡萄糖氧化酶制备葡萄糖生物传感器。首先在含有0.1 mol/L吡咯和0.01 mol/L HCl的溶液中,于0.7 V恒电位下吡咯单体氧化聚合,在铅笔芯电极表面形成聚吡咯薄膜;然后将葡萄糖氧化酶吸附在修饰过的电极上制备出葡萄糖氧化酶-聚吡咯-铅笔芯电极电流型生物传感器。实验考察了吡咯聚合时间、聚合温度、葡萄糖氧化酶吸附量、检测电压以及干扰物对传感器性能的影响。实验结果表明,在优化条件下,传感器的灵敏度为17.78μA/mmol/L,线性范围0.8 mmol/L,线性相关度R=0.9918,响应时间小于16 s,检测下限为18.75μmol/L,有较强的抗干扰能力。     

刀豆球蛋白层层自组装双酶电极对芳香胺物质的检测

基于生物识别组装方法将辣根过氧化物酶(HRP)和葡萄糖氧化酶(Gox)固定在金电极表面制备了HRP/Gox双酶多层膜电极.HRP/Gox双酶电极通过Gox催化氧化葡萄糖"原位"产生过氧化氢的方式分析检测芳香胺物质.探讨了葡萄糖浓度和酶组装层数对双酶电极电流响应的影响.在优化条件下,制备的双酶电极在p-苯二胺的浓度为7.6 ～53.2 μmol/L时有良好的线性响应,灵敏度为146.04 mA·L/mol.常见的干扰物葡萄糖和抗坏血酸对该双酶电极无干扰.     

Nonenzymatic Electrochemical Glucose Sensor Based on Novel Copper Film

Novel copper (Cu) film composed of pillar‐like structure was synthesized on indium‐doped tin oxide (ITO) substrate by electrodeposition in acetate bath with proline as additive for the first time and used to construct nonenzymatic glucose sensor. When applied to detect glucose, such prepared electrode showed low operating potential (0.4 V), high sensitivity (699.4499 µA mM⁻¹ cm⁻²), and fast response time (<3 s) compared with other Cu‐based electrodes. In addition, the prepared electrode also offered good anti‐interference ability to ascorbic acid, uric acid and acetaminophen. Present study provides new insights into the control of Cu film morphology for sensor fabrication.     

壳聚糖-Cu^2＋复合物膜固定葡萄糖氧化酶用于葡萄糖传感

利用壳聚糖(CS)对Cu2 的配位吸附作用,制得壳聚糖-Cu2 复合膜修饰电极,进一步通过Cu2 与蛋白质的配位作用,再将葡萄糖氧化酶(GOD)固定在金电极上制得GOD-Cu2 -CS/Au电极.该酶电极检测葡萄糖的线性范围为0.03～2.5 mmol·L-1,线性相关系数为0.997,检出限(S/N=3)为1 μmol·L-1.以电化学石英晶体微天平(EQCM)技术监测了各修饰过程.     

基于谷胱甘肽-壳聚糖自组装的葡萄糖生物传感器

采用壳聚糖-谷胱甘肽复合膜固定葡萄糖氧化酶构建电流型葡萄糖生物传感器。通过循环伏安法对酶膜状态进行表征,实验结果表明,壳聚糖-谷胱甘肽复合膜可以辅助电子传递,提高电极的电流响应。选用正交表L9(34)设计实验方案,分析最佳实验条件。在优化条件下,该传感器对葡萄糖溶液浓度有良好的线性关系,线性范围为1～18 mmol/L,检出限为1.3 mmol/L。实验表明,此传感器具有响应快、稳定性及选择性良好的特点。适用于临床尿样中葡萄糖的测定。     

基于蛋壳膜固定酶和纳米银膜光度法对葡萄糖的检测

利用蛋壳膜固定酶和静电作用组装纳米银膜,建立了一种新型的光度法检测微量葡萄糖.采用共价交联法在蛋壳膜上固定葡萄糖氧化酶.酶促反应产生的H_2O_2氧化纳米银导致纳米银膜吸光度减小,日光强度的变化值与葡萄糖浓度有关,据此实现了对葡萄糖的检测.该方法检测快速,线性范围为6.0×10~(-5)～66.0×10~(-5)mol/L(r=0.999 7,n=11),检出限(S/N=3)为1.8×10~(-5) mol/L.方法成功用于临床血清样品中葡萄糖含量的检测.     

Glucose Biosensor Based on the Fabrication of Glucose Oxidase in the Bio-Inspired Polydopamine-Gold Nanoparticle Composite Film

A highly efficient enzyme immobilization method has been developed for electrochemical biosensors using polydopamine films with gold nanoparticles (AuNPs) embedded. This simple enzyme fabrication method can be performed in very mild conditions and stored in a long time with high bioactivity. The fabricated amperometric glucose biosensor exhibited a high and reproducible sensitivity, wide linear dynamic range and low limit of detection (LOD) (0.1 μmol·L^?1). A low value of 1.5 mmol·L^?1 for the apparent Michaelis‐Menten constant K^app_M was obtained. The high sensitivity, wide linear range, good reproducibility and stability make this biosensor a promising candidate for portable amperometric glucose biosensor.     

基于层-层自反应的葡萄糖氧化酶有序多层膜电极

以胱胺修饰的金电极为基础电极, 利用席夫碱反应使经高碘酸根氧化的葡萄糖氧化酶在该电极表面进行自身的层-层有序组装. 用电化学交流阻抗法对多层酶膜形成过程的跟踪结果表明, 该多层酶膜的生长是一个逐步形成的均匀过程. 用循环伏安法和I-t曲线法研究了该酶电极对葡萄糖的电催化氧化. 实验结果表明, 当采用羟基二茂铁作为人工电子转移媒介体时, 该酶电极对葡萄糖具有很好的电催化氧化功能. 该传感器制作简便, 响应迅速, 性能稳定, 催化电流与葡萄糖浓度在一定范围内成正比, 并且可以通过控制葡萄糖氧化酶的组装层数来调节该生物传感器的灵敏度与检测限.     

Glucose Monitoring by a Biosensor Based on Mercury Thin Film Electrodes

Abstract

Mercury film electrodes consist of a thin film of mercury deposited on an electrode surface (typically glassy carbon) by reduction of a mercury (II) salt in solution. The surface area/volume ratio is larger for the mercury film electrode, and this electrode is more stable than mercury drop electrode, which allows a faster stirring rate to be used in the deposition step. An enzyme electrode is described, based on glucose oxidase immobilized by gelatin and glutaraldehyde and held over a glassy carbon electrode coated with a thin mercury film. This biosensor responds fast and linearly to glucose in a wide concentration range, which is significant because monitoring of glucose levels is a critical component of diabetes care. Certain optimization and characterization studies were carried out. Average value, standard deviation (SD), and variation coefficient (CV) were calculated with the help of the repeatability studies. Finally, glucose content of human blood samples was monitored with the help of the biosensor presented.     

A Chemiluminescence Optical Fiber Glucose Biosensor Based on Co-immobilizing Glucose Oxidase and Horseradish Peroxidase in a Sol-gel Film

IntroductionIn recent years chemiluminescence (CL)biosensor prepared by immobilization of a sensitivereagent such as peroxidase or oxidase onto a solidmatrix has attracted much attention due to the highsensitivity of the chemiluminescent reaction of thesensitive reagent even with a simple instrument.Generally,CL biosensors can be divided into twocategories.One consists of hydrogen peroxide sen-sors prepared by immobilizing a kind of peroxidaseonto a suitable solid support[1,2 ] ,and the immo…     

Amperometric Glucose Determination by Means of Glucose Oxidase Immobilized on a Cellulose Acetate Film: Dependence on the Immobilization Procedures

Glucose microelectrodes were prepared by immobilizing glucose oxidase onto a cellulose acetate film coating a platinum wire. Hexamethylenediamine (HMDA) and Glutaraldehyde (GA) were employed as spacer and coupling agent, respectively. Sensitivities and linear response ranges were studied as a function of the relative amounts of HMDA and GA. The best sensitivity was found when HMDA and GA were 5% and 2.5% in aqueous solutions, respectively. Taking as a reference the functioning of this biosensor, the roles of HMDA and GA percentages appear to be opposed when the extension of the linear response range is considered. Indeed, an increase of one unit in HMDA percentage (from 5 to 6 %) induces an increase in the extension of the linear response range equal to that obtained with a decrease of one unit of GA percentage (from 2.5 to 1.5%).