基于纳米金/硫堇层层自组装的新型电流型酶-癌胚抗原免疫传感器

将Nafion 膜固定在金电极(Au)表面, 通过静电吸附和共价键合作用将硫堇(Thi)和纳米金颗粒(nano-Au)层层自组装到Nafion膜修饰的金电极表面. 再通过形成的纳米金单层吸附癌胚抗体(anti-CEA), 最后用辣根过氧化物酶(HRP)代替牛血清白蛋白(BSA)封闭电极上的非特异性吸附位点, 并同时起到放大响应电流信号的作用, 从而制得高灵敏、高稳定电流型酶-癌胚抗原(CEA)免疫传感器. 通过循环伏安和交流阻抗考察了电极表面的电化学特性, 并对该免疫传感器的性能进行了详细的研究. 该传感器对CEA检测的线性范围为2.5~80.0 ng/mL, 检测限为0.90 ng/mL.     

纳米金自组装膜的IgM压电免疫传感器的研究

利用等离子体聚合膜沉积技术和纳米金亚单层自组装技术设计传感器界面，用 于固定羊抗人M抗体，研制了一种新的M压电免疫传感器．先在石英品振上沉积正丁 胺等离子体聚合膜，通过戊二醛交联结合一半肮胺单层膜，利用膜上流基与纳米金 键合组装纳米金亚单层，得到可用于固定18kI抗体的界面，再以牛血清白蛋白 (BSA)和聚乙二醇(PEG)封闭晶振上的非特异性吸附位点．实验探讨了影响纳米金自 组装和抗体包被等主要实验参数和条件；考察了采用此固定化方法传感器的响应性 能，与戊二醛共价交联固定法和金电极表面直接吸附固定法进行了比较．结果表明 ，以纳米金单层作界面固定抗体时，具有传感界面不需活化、固定抗体的活性高、 检测时的非特异性吸附小、传感器能反复再生等优点．将传感器用于实际样品的检 测，结果令人满意．     

新型磁性纳米金修饰过氧化氢生物传感器的研制

利用共沉淀法合成纳米Fe3O4颗粒,将半胱氨酸吸附到纳米Fe3O4微粒表面,借助半胱氨酸的巯基(-SH)对纳米金的强烈吸附,使纳米金自组装到磁性颗粒上,再通过静电吸附作用自组装辣根过氧化酶(HRP),合成了Fe3O4/Cys/Au/HRP纳米复合粒子,最后通过磁力将其修饰到固体石蜡碳糊电极表面,制得新型过氧化氢生物传感器.以对苯二酚作为电子媒介,用计时电流法对H2O2进行测定,线性范围为2.4 X10-3～6.0×10-6mol/L,检出限(S/N=3)为2.5 X 10-6mol/L,响应时间小于10 s.磁性纳米微粒Fe3O4/Cys/Au能够高效地保持HRP的生物活性.该新型传感器已用于实际样品测定.     

静电组装金纳米粒子制备局域表面等离子体共振传感膜

采用聚电解质自组装技术制备局域表面等离子体共振(LSPR)传感膜的方法, 在玻璃基片上依次沉积聚电解质PDDA, PSS和PVTC, 并通过静电吸附构建胶体金纳米粒子自组装膜形成LSPR传感膜. 利用扫描电镜对LSPR传感膜表面形貌以及膜中金纳米粒子的粒径进行了表征, 同时通过紫外-可见消光光谱对其灵敏度和渗透深度等重要参数进行检测. 研究结果表明, 所制备的LSPR传感膜粒子分布均匀、单分散性好、稳定性高、重现性好; 消光峰位对样品溶液折射率的检测灵敏度为71 nm/RIU, 相应的峰强检测灵敏度为0.21 AU/RIU, 对表面吸附层的渗透深度约为16 nm.     

基于纳米金和硫堇固定酶的过氧化氢生物传感器

在铂电极上自组装一层纳米金(GNs), 构建负电荷的界面, 然后通过金-硫、金-氮共价键合作用和静电吸附作用自组装一层阳离子电子媒介体硫堇(Thio). 再以同样的作用自组装一层GNs和辣根过氧化酶(HRP)的混合物, 最后在电极最外层滴加一层疏水性聚合物壳聚糖(Chit), 由此制备了一种新型的过氧化氢生物传感器. 研究了工作电位、检测底液pH、温度对响应电流的影响, 以及GNs和HRP之间的相互作用, 探讨了传感器的表面形态、交流阻抗、重现性和稳定性. 该传感器的酶催化反应活化能为12.4 kJ/mol, 表观米氏常数为6.5×10^－4 mo/L, 在优化的实验条件下, 所研制的传感器对H₂O₂的线性范围为5.6×10^－5～2.6×10^－3 mol/L, 检出限为1.5×10^－5 mol/L. 应用此方法制备了HRP和葡萄糖氧化酶(GOD)双酶体系葡萄糖生物传感器, 并应用于实验样品葡萄糖含量的测定.     

程序自组装DNA纳米花封装酶分子用于光热法检测循环肿瘤细胞

DNA纳米技术在生物传感领域引起人们广泛的研究兴趣,现已构建多种二维和三维DNA功能纳米结构.滚环扩增(RCA)作为一种等温扩增技术,为DNA纳米材料的设计和自组装提供了新途径.该文通过RCA一锅法合成封装有辣根过氧化物酶(HRP)的DNA纳米花(HRP@DNFs),进一步基于双核酸适体识别构建光热生物传感器,用于肝细...     

基于局域SPR传感器的免疫分析

局域表面等离子体共振(LSPR)是一种由入射光(电磁场)与金属纳米粒子表面自由电子间相互作用产生的物理光学现象,其性质与纳米粒子的组成、尺寸、形状、粒子间距和周围介质折射率等因素有关.溶胶LSPR传感已被成功地应用于免疫分析以及DNA检测等方面.应用聚电解质作为自组装材料,通过静电相互作用,将金纳米粒子组装于玻璃基片上制备LSPR传感膜.此种方法制备的LSPR传感膜中金纳米粒子的单分散性好,制备过程简单、组装时间短.同时,应用紫外.可见分光光度计进行检测,实验操作更加简便.     

基于巯基乙酸与离子液体共修饰的过氧化氢生物传感器的研究

采用静电组装技术,将离子液体[Bmim]PF6与辣根过氧化物酶(HRP)交替固定在巯基乙酸修饰的金电极表面,制备了(HRP/[Bmim]PF6)n多层组装膜,并通过电化学阻抗谱(EIS)和傅立叶红外反射光谱(ATR-FTIR)对制备的组装膜进行了表征.以对苯二酚为电子媒介体,过氧化氢在(HRP/[Bmim]PF6)2双层组装膜传感器上的线性范围为1.6×10-6 ～2.5×10-3 mol/L,检出限为5.7×10-7 mol/L(S/N=3),达到95%稳态电流用时少于5 s,Kappm值为0.048 mmol/L,表明所固定的酶具有较高的生物活性.     

基于磁纳米粒子修饰的SPR传感器

磁纳米粒子是20世纪70年代后逐步产生并发展起来的一种应用前景广阔的新型磁性材料,由于其具有良好的磁响应性、粒径小、比表面积大、生物相容性好等优点而广泛地应用于生物技术领域~([1～3]).采用磁粒子固定抗体的免疫检测与传统的在传感膜上固定抗体的方法相比,不需要金膜和抗体之间的共价连接,因此它极大地简化了抗体的固定,加速了待测物的检测.同时采用层层自组装技术,在金膜的表面交替自组装聚电解质阴阳离子,形成聚电解质膜,不仅对金膜起到了保护的作用,避免了磁纳米粒子与金膜的直接接触,还在一定程度上提高了传感器的灵敏度.     

基于网状混合自组装膜的压电免疫传感器及其应用

结合纳米金及混合自组装技术, 制备了一种新型网状混合膜, 提出了一种新的生物分子固定化方法, 研制了一种用于检测人血清抗精子抗体的压电免疫传感器. 首先, 将纳米金溶胶、巯基丙酸和1,6-二巯基己烷按一定的比例混合制得网状混合自组装膜, 然后将此膜组装到压电石英晶振的金电极表面, 经EDC/NHS活化后, 再将抗原固定到电极上, 实现对抗精子抗体的检测. 结果表明, 该方法能明显提高抗体抗原结合效率, 从而提高传感器的灵敏度, 并降低传感界面的非特异性吸附. 将此传感器应用于人血清抗精子抗体的检测, 线性范围为10~800 mU/mL, 检出限为7 mU/mL. 此传感器为抗精子抗体的临床检测提供了新平台.     

辣根过氧化酶在纳米金／氧化锌球腔微电极阵列上的直接电化学研究

利用Langmuir - Blodgett技术和溶胶-凝胶(sol -gel)法在氧化铟锡(ITO)电极表面制备了有序的纳米金／氧化锌(nano-Au/ZnO)球腔阵列,并采用扫描电镜表征了nano-Au/ZnO球腔阵列的形貌.该阵列的循环伏安曲线具有微电极特性.将辣根过氧化酶(HRP)直接固定于nano-Au/ZnO...     

溶胶-凝胶生物传感器

评述了溶胶－凝胶生物传感器这个领域已取得的成果,主要内容涉及溶胶－凝胶固定化方法的过程,优点与性质,溶胶－凝胶光学生物传感器和安培生物传感器的发展,并展望了其发展趋势。     

氧化铝/聚乙二醇溶胶凝胶对酪氨酸酶的固定及应用研究

氧化铝/聚乙二醇(Al2O3/PEG)溶胶凝胶复合材料对酪氨酸酶具有较好的生物相容性和较高的稳定性。将生物酶固定于其中制备成的生物传感器具有良好的反应活性。实验证明这种生物传感器具有好的稳定性和灵敏度高的特点。     

基于脱乙酰基魔芋葡甘聚糖固定酶的葡萄糖传感器

制备了脱乙酰基魔芋葡甘聚糖(d-KGM)的溶胶-凝胶,用红外光谱表征了其脱乙酰基前后的结构转化.探讨了d-KGM溶胶-凝胶的制备条件对其成膜性能及酶固定化的影响.在此基础上将d-KGM用于电极表面葡萄糖氧化酶的固定,制备了相应的葡萄糖传感器,并对传感器的工作条件进行了优化.所制备的传感器灵敏度为240 nA/mmol/L,线性范围为0.1～8 mmol/L,表观米氏常数KM为19.6 mmol/L,稳定性好,寿命长.实验结果表明d-KGM是一种可用于生物传感器中酶固定化的优良材料.     

ZnO-MWCNTs/Nafion Inorganic-organic composite film： Preparation and application in bioelectrochemistry of hemoglobin

Multi-walled carbon nanotubes(MWCNTs) were coated with ZnO by a hydrothermal method.The resulting nanocomposites were mixed with the Nafion solution to form a composite matrix for the fabrication of hemoglobin(Hb) biosensor.To prevent the leak of Hb molecules of the biosensor,silica sol-gel film was coated on the surface of the Hb/ZnO-MWCNTs/Nafion electrode.The silica sol-gel/Hb/ZnO-MWCNTs/Nafion film exhibited a pair of well-defined,quasi-reversible redox peaks.This biosensor showed excellent electroca...     

An optical fiber biosensor for chlorpyrifos using a single sol-gel film containing acetylcholinesterase and bromothymol blue

An optical fiber biosensor consisting of acetylcholinesterase (AChE) and bromothymol blue (BTB) doped sol-gel film was employed to detect organophosphate pesticide chlorpyrifos. The main advantage of this optical biosensor is the use of a single sol-gel film with immobilized AChE and BTB. The compatibility of this mixture (AChE and BTB) with the sol-gel matrix has prevented leaching of the film. The immobilization of the enzyme and indicator was simple without chemical modification. The biosensing element on single sol-gel film has been placed inside the flow-cell for flow system. In the presence of a constant AChE, a color change of the BTB and the measured reflected signal at wavelength 622nm could be related to the pesticide concentration in the sample solutions. The performance of optical biosensor in the flow system has been optimized, including chemical and physical parameters. The response time of the biosensor is 8min. A linear calibration curve of chlorpyrifos against the percentage inhibition of AChE was obtained from 0.05 to 2.0mg/L of chlorpyrifos (18-80% inhibition, R(2)=0.9869, n=6). The detection limit for chlorpyrifos was 0.04mg/L. The results of the analysis of 0.5-1.5mg/L of chlorpyrifos using this optical biosensor agreed well with chromatographic method.     

Tetraethylorthosilicate film modified with protein to fabricate cholesterol biosensor

Sol-gel derived tetraethylorthosilicate (TEOS) films were prepared by spin coating method on indium tin oxide (ITO) coated glass plate. Hydrophobic interaction method was used to coat the bovine serum albumin film over the surface of tetraethylorthosilicate sol-gel film to minimize cracking, biofouling and to improve the stability of the film. Cholesterol oxidase (ChOx) and horseradish peroxidase (HRP) were immobilized using covalent linkage with bovine albumin serum film to enhance the loading of the enzyme to improve the sensitivity of biosensor. Further ITO-TEOS-BSA-ChOx/HRP film was characterized by UV-vis, FTIR and SEM techniques. The optical response of the ITO-TEOS-BSA-ChOx/HRP biosensor was found to be linear in the range of 2-8 mM for cholesterol concentration with response time approximately 20 s. Amperometric response of ITO-TEOS-BSA-ChOx/HRP was observed to be linear in the range of 2-12 mM of cholesterol concentration with 10-s response time. Michaelis-Menten constant was calculated 21.2 mM .The shelf life of ITO-TEOS-BSA-ChOx/HRP biosensor was approximately about 8 weeks in desiccated conditions at room temperature.     

Glucose biosensors based on platinum nanoparticles-deposited carbon nanotubes in sol-gel chitosan/silica hybrid

A new strategy for fabricating a sensitivity-enhanced glucose biosensor was presented, based on multi-walled carbon nanotubes (CNT), Pt nanoparticles (PtNP) and sol-gel of chitosan (CS)/silica organic-inorganic hybrid composite. PtNP-CS solution was synthesized through the reduction of PtCl(6)(2-) by NaBH(4) at room temperature. Benefited from the amino groups of CS, a stable PtNP gel was obtained, and a CNT-PtNP-CS solution was prepared by dispersing CNT functionalized with carboxylic groups in PtNP-CS solution. The CS/silica hybrid sol-gel was produced by mixing methyltrimethoxysilane (MTOS) with the CNT-PtNP-CS solution. Then, with the immobilization of glucose oxidase (GOD) into the sol-gel, the glucose biosensor of GOD-CNT-PtNP-CS-MTOS-GCE was fabricated. The properties of resulting glucose biosensor were measured by electrochemical impedance spectroscopy (EIS) and cyclic voltammetry (CV). In phosphate buffer solutions (PBS, pH 6.8), nearly interference free determination of glucose was realized at low applied potential of 0.1V, with a wide linear range of 1.2x10(-6) to 6.0x10(-3)M, low detection limit of 3.0x10(-7)M, high sensitivity of 2.08microA mM(-1), and a fast response time (within 5s). The results showed that the biosensor provided the high synergistic electrocatalytic action, and exhibited good reproducibility, long-term stability. Subsequently, the novel biosensor was applied for the determination of glucose in human serum sample, and good recovery was obtained (in the range of 95-104%).     

一步电沉积制备交联型有机-无机生物杂化膜构筑双酶传感器的研究

利用一步电沉积法,以含有环氧基团的γ-环氧丙氧丙基三甲氧基硅烷（GPTMS）为无机杂化试剂和功能性交联试剂,通过壳聚糖（Chitosan,CS）、辣根过氧化物酶（HRP）和葡萄糖氧化酶（GOD）分子中-NH2与环氧基团的反应,在金电极表面原位制备交联型有机-无机生物杂化膜,得到共固定HRP和GOD的新型双酶生物传感器．实验证实了这种有机-无机生物杂化膜在不同酸、碱条件下都具有高的稳定性和耐用性,克服了CS酸溶的不足,从而扩大了其使用范围．在葡萄糖检测中,交联型双酶传感器HRP-GOD／GPTMS／CS,Au比无交联的双酶传感器HRP-GOD／CS／Au具有更高的灵敏度、更宽的线性范围,其线性范围为1μmol／L-351μmol／L,检期4限为0．3μmol／L．     

Laccase Containing Sol-Gel Based Optical Biosensors

Abstract

Laccase-containing sol-gels were synthesized by hydrolysis and condensation-polymerization of tetramethylorthosilicates. Two types of laccase containing sol-gel based optical biosensors were designed and tested. The first type is based on 2–8 mm thick monolith sol-gel blocks. It was observed that laccase-containing sol-gel blocks accumulate high molecular weight products of oxidation of the laccase substrate - 2,6-dimethoxyphenol. This leads to at least ten fold increase of optical bioassay sensitivity in comparison with the homogeneous phase. The response time of such biosensors is 3–24 hours. The second type of biosensor is based on laccase-containing 0.3 mm diameter solgel particles in a flow cell and includes an optical fiber measuring system. This sensor is characterized by a fast response time in comparison with the first type. The latter biosensor also possesses a homogeneous phase assay sensitivity and yields a linear calibration curve.