传感器类型
其他(BioCapacitor/酶燃料电池-电容器生物传感器)
检测对象
葡萄糖(glucose);样品基质:100 mM 磷酸盐缓冲液(PPB, pH 7.0)/葡萄糖溶液,文中未用血清,面向血糖连续监测
检测原理
FADGDH 作为阳极生物识别元件,催化葡萄糖氧化并通过直接电子传递向碳布阳极输出电子;阴极 Pt/C 催化氧气还原,形成酶燃料电池回路。葡萄糖浓度升高使阳极催化电流和闭环电压/功率增大,电荷泵 IC 将低电压升压至 1.8 V 并向电容器充电;电容器达到 1.8 V 后放电至 1.4 V,再重新充电。充放电循环频率取决于燃料电池输出功率和电容器容量,因此随葡萄糖浓度升高而增加。放电电流驱动 IRLED 发光,红外光电晶体管接收并转换为电信号,实现无需外部电源的无线葡萄糖浓度读出。
检测灵敏度
LOD: 0.1 mM;无线系统最低可检测: 约0.2 mM;频率饱和: >7.4 mM(BioCapacitor)/约20 mM(无线)
效应效果
文中未报告选择性、抗干扰、实际样品回收率或与 ELISA/HPLC/qPCR 的对比。同一 BioCapacitor 对葡萄糖信号的重复测量变异系数低于 10%。BioCapacitor 电路最低可检测葡萄糖为 0.1 mM,充放电频率在 7.4 mM 以上饱和;无线 IRLED 系统最低可检测约 0.2 mM,频率在约 20 mM 以上饱和。系统无需外部电源,仅靠葡萄糖氧化产生的电能驱动 IRLED 并无线传输,作者认为其可发展为植入式连续血糖监测(CGM)装置。但文中未验证血液或血清基质、长期稳定性、生物相容性和体内干扰,仍需优化酶用量、阴极面积、电极材料和电子传递效率。
传感器的构成
- 阳极基底:碳布(carbon cloth, SYCC18-00000-00),作为阳极导电基底
- 阳极识别/催化层:FADGDH 复合物(FAD-dependent glucose dehydrogenase)与 Ketjen black 碳黑(ECP600JD)混合涂覆,催化葡萄糖氧化并提供电子传递
- 固定化层:1% 戊二醛(glutaraldehyde)处理,固定 FADGDH
- 阴极基底:碳布(carbon cloth),作为阴极导电基底
- 阴极催化层:Pt/C 墨水(TEC10E50E, 50 wt% Pt)涂覆,催化氧气还原
- 阴极修饰层:PDMS(poly(dimethylsiloxane), 3.0% w/v)涂覆,形成阴极表面层
- 储能换能元件:电容器(0.47–100 μF)储存酶燃料电池电能,充放电频率用于浓度读出
- 电荷泵与信号读出:电荷泵 IC(S-882Z18-M5T1G)升压并控制充放电;黄色 LED(OSYL5161A-QR)或 IRLED(TLN103A)输出信号,IR 光电晶体管(SPS-135C)无线接收
中文摘要
本研究报道了一种新型生物传感器——BioCapacitor,其将生物识别元件与作为换能器的电容器相结合。BioCapacitor 的分析原理是:作为生物识别元件的生物催化剂氧化或还原分析物并产生电能,该电能经电荷泵电路(开关电容稳压器)向电容器充电,直至电容器达到满容量。由于电容器充电速率取决于分析物的生物催化反应,因此可通过监测电荷泵电路中充放电循环所需的时间或频率来确定分析物浓度。作为代表性模型,作者以黄素腺嘌呤二核苷酸依赖性葡萄糖脱氢酶(FADGDH)为阳极催化剂构建了 BioCapacitor,并用于葡萄糖检测。结果表明,BioCapacitor 的充放电频率随葡萄糖浓度升高而增加,并与葡萄糖浓度呈良好相关性。此外,作者将 BioCapacitor 与红外发光二极管(IRLED)及红外光电晶体管接收系统结合,构建了无线传感系统。在葡萄糖存在下,BioCapacitor 放电驱动 IRLED 发出信号,并被无线接收器中的红外光电晶体管检测。因此,采用 FADGDH 作为阳极催化剂的 BioCapacitor 可作为自供电酶传感器运行。
英文摘要
This research reports on the development of an innovative biosensor, known as BioCapacitor, in which biological recognition elements are combined with a capacitor functioning as the transducer. The analytical procedure of the BioCapacitor is based on the following principle: a biocatalyst, acting as a biological recognition element, oxidizes or reduces the analyte to generate electric power, which is then charged into a capacitor via a charge pump circuit (switched capacitor regulator) until the capacitors attains full capacity. Since the charging rate of the capacitor depends on the biocatalytic reaction of the analyte, the analyte concentration can be determined by monitoring the time/frequency required for the charge/discharge cycle of the BioCapacitor via a charge pump circuit. As a representative model, we constructed a BioCapacitor composed of FAD-dependent glucose dehydrogenase (FADGDH) as the anodic catalyst, and attempted a glucose measurement. Charge/discharge frequency of the BioCapacitor increased with the increasing glucose concentration, exhibiting good correlation with glucose concentration. We have also constructed a wireless sensing system using the BioCapacitor combined with an infrared light emitting diode (IRLED), an IR phototransistor system. In the presence of glucose, the IRLED signal was observed due to the discharge of the BioCapacitor and detected by an IR phototransistor in a wireless receiver. Therefore, a BioCapacitor employing FADGDH as its anodic catalyst can be operated as a self-powered enzyme sensor.