Improved spacer membrane for an enzymatic in-vivo sensor
A technology of isolation membrane and measuring body, which is applied in the field of electrode system and can solve the problems of not being used publicly
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Embodiment 1
[0165] Example 1 Penetration of enzymatic non-fluid (ENF) glucose sensor with distributed electrodes for percutaneous implantation Permeability, the electrode has a diffusion layer composed of a single block copolymer.
[0166] The sensor was built on a prefabricated palladium conductor structure on a 250 μm thick polyester substrate. Distribute the working electrode (WE) and counter electrode (CE) (e.g. Figure 1-2 Shown).
[0167] Overprint the CE block with carbon paste to insulate the rest of the conductor. The block of WE was overprinted with a mixture of cross-linked glucose oxidase (enzyme), conductive polymer paste, and electrocatalyst (here, manganese (IV) oxide (Technipur)). Insulate the remaining paths of the conductor again. The reference electrode (RE) is made of Ag / AgCl paste. These electrodes cover about 1 cm of the sensor rod.
[0168] The WE block is coated with a block copolymer diffusion layer composed of HEMA blocks and BUMA blocks. The thickness of this ...
Embodiment 2
[0175] Example 2 Mechanism of diffusion layer of ENF glucose sensor soft toughness.
[0176] The sensor is manufactured as described in WO 2010 / 028708, but with the diffusion layer of the invention. It is assumed that the glass transition temperature (Tg) is an alternative parameter for mechanical flexibility. In addition, assuming the glass transition temperature, which can be assigned to the hydrophobic block, determines the mechanical flexibility in in vivo applications. It should be noted that a block copolymer may identify several Tgs, which correspond to the number of blocks.
[0177] The sensor was coated with the same electrode paste as in Example 1. Then, some sensors were coated with a copolymer selected from MMA-HEMA (produced by Polymer Source in Montreal). The total molecular weight of this polymer (referred to as E) is 41kD, and the molar ratio of MMA (hydrophobicity) to HEMA is 60%:40%. The glass transition temperature of the hydrophobic block is 111°C, which ...
Embodiment 3
[0181] Example 3 The optimized ENF glucose sensor with distributed electrodes and diffusion layer according to the present invention Infiltration behavior.
[0182] The sensor is manufactured as described in Example 1, but with an additional isolation layer on the entire sensor rod. For the copolymers A, C, D, and F of Examples 1 and 2, sensors with respective diffusion layers were prepared. For this purpose, a 24% ether solution of the copolymer was generated. Each solution was applied to a set of sensors (N=10) and then dried in a belt dryer. Thus, a diffusion layer having a thickness of 7 μm was obtained.
[0183] Thereafter, these sensors were provided with the isolation layer described in Example 2.
[0184] The sensor is connected to the measurement system on the sensor head, which transfers the measurement data to the data storage. The in vitro measurement was performed as in Example 1, but on a measurement period of 7 days. From the measurement data, the sensitivity d...
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Abstract
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