技术领域technical field
本申请涉及医疗器械，尤其涉及一种脑电电极传感器。The present application relates to medical equipment, in particular to an electroencephalogram electrode sensor.
背景技术Background technique
麻醉是现代临床手术中必不可少的关键环节，但实施麻醉具有较高的风险性，错误的麻醉剂量都会给患者带来伤害如何为患者提供安全可靠的麻醉，是目前麻醉学研究相关领域的重点课题。脑电信号是大脑皮层神经细胞群突触电位变化的综合反映，有反映意识活动的优势及无创性特点。脑电信号是目前客观评估麻醉深度中最有潜力的方法之一，已取得较好的研究成果，通过脑电信号来评估临床手术中麻醉状态具有重要的临床应用价值。因而脑电信号的获取对于麻醉深度监测至关重要。Anesthesia is an indispensable key link in modern clinical operations, but the implementation of anesthesia has high risks, and the wrong anesthesia dose will bring harm to patients. How to provide safe and reliable anesthesia for patients is the current research field of anesthesiology. Key topics. The EEG signal is a comprehensive reflection of the changes in the synaptic potential of the cerebral cortex nerve cell population, and has the advantage of reflecting the consciousness activity and non-invasive characteristics. EEG signal is currently one of the most promising methods for objectively evaluating the depth of anesthesia, and good research results have been achieved. EEG signal evaluation of the anesthesia state in clinical operations has important clinical application value. Therefore, the acquisition of EEG signals is very important for monitoring the depth of anesthesia.
目前常见用于获取脑电信号的电极传感器主要有BIS（bispectralindex，脑电双频指数）传感器。BIS传感器由4个电极芯片、聚酯感光层和银-氯化银传感导线组成，电极芯片由PE白色泡沫、凝胶和Velcro触针组成，不含乳胶。但是BIS传感器存在售价高的缺点，增加了手术的应用成本。At present, the electrode sensors commonly used to obtain EEG signals mainly include BIS (bispectral index, EEG bispectral index) sensors. The BIS sensor is composed of 4 electrode chips, polyester photosensitive layer and silver-silver chloride sensing wire, the electrode chip is composed of PE white foam, gel and Velcro contact pin, latex free. However, the BIS sensor has the disadvantage of high price, which increases the application cost of surgery.
发明内容Contents of the invention
本申请提供一种脑电电极传感器。The present application provides an electroencephalogram electrode sensor.
本申请要解决的技术问题通过以下技术方案加以解决：The technical problem to be solved in this application is solved through the following technical solutions:
一种脑电电极传感器，包括薄膜PCB电路层、粘连层、触针层和导电水凝胶，所述薄膜PCB电路层的一端为插接端口，所述薄膜PCB电路层的另一端设有四个电极芯，所述粘连层设置在所述薄膜PCB电路层上，且所述粘连层与所述电极芯相对的位置处设有四个通孔，所述通孔的大小与所述电极芯配合，所述触针层和所述导电水凝胶的大小与所述通孔配合且由下向上依次设置在所述电极芯上。A kind of electroencephalogram electrode sensor, comprises thin film PCB circuit layer, adhesion layer, stylus layer and conductive hydrogel, one end of described thin film PCB circuit layer is a plug-in port, and the other end of described thin film PCB circuit layer is provided with four An electrode core, the adhesive layer is arranged on the thin film PCB circuit layer, and four through holes are arranged at the position opposite to the electrode core, the size of the through holes is the same as that of the electrode core. Cooperate, the size of the stylus layer and the conductive hydrogel are matched with the through hole and are sequentially arranged on the electrode core from bottom to top.
还包括夹持在所述触针层和所述电极芯之间的连接柱。It also includes a connection column clamped between the contact pin layer and the electrode core.
所述连接柱包括圆柱体形，且由双面含胶泡沫材料制成。The connecting column has a cylindrical shape and is made of double-sided glue-containing foam material.
还包括夹持在所述触针层和所述导电水凝胶之间的附着层，所述附着层包括丝状棉。An adhesive layer sandwiched between the stylus layer and the conductive hydrogel is also included, the adhesive layer includes filamentary cotton.
所述触针层包括带有触针的塑料圆盘。The stylus layer comprises a plastic disc with stylus.
所述导电水凝胶为含有Nacl的胶状液体。The conductive hydrogel is a colloidal liquid containing Nacl.
所述胶状液体为卡波树脂三乙醇胺、NaCl和水，其中卡波树脂：三乙醇胺：NaCl：水=0.5～1.5%：1～2%：1.5～2.5%：94～97%。The colloidal liquid is carbo resin triethanolamine, NaCl and water, wherein carbo resin: triethanolamine: NaCl: water = 0.5-1.5%: 1-2%: 1.5-2.5%: 94-97%.
所述薄膜PCB电路层包括PET薄膜基底和设置在所述PET薄膜基底上的铜箔导线，所述电极芯由铜箔制成。The thin film PCB circuit layer includes a PET film base and copper foil wires arranged on the PET film base, and the electrode core is made of copper foil.
由于采用了以上技术方案，使本申请具备的有益效果在于：Owing to adopting above technical scheme, the beneficial effect that makes this application possess is:
⑴在本申请的具体实施方式中，由于包括薄膜PCB电路层、粘连层、触针层和导电水凝胶，粘连层设置在薄膜PCB电路层上，且粘连层与电极芯相对的位置处设有四个通孔，触针层和所述导电水凝胶的大小与所述通孔配合且由下向上依次设置在所述电极芯上。本申请结构简单，保证信号质量，同时价格低廉，可降低应用成本。(1) In the specific embodiment of the application, due to including the film PCB circuit layer, the adhesive layer, the stylus layer and the conductive hydrogel, the adhesive layer is arranged on the thin film PCB circuit layer, and the position where the adhesive layer is opposite to the electrode core is set There are four through holes, and the size of the contact pin layer and the conductive hydrogel are matched with the through holes, and are sequentially arranged on the electrode core from bottom to top. The application has a simple structure, ensures signal quality, and has low price, which can reduce the application cost.
⑵在本申请的具体实施方式中，本申请的脑电电极传感器以薄膜PCB电路层为基础层，叠加粘连层，连接柱穿过粘连层的通孔与基础层的电极芯相连，连接柱又与触针层相连，在触针层上叠加附着层，在附着层上浸入导电水凝胶，导电效果好，测量精确。(2) In the specific embodiment of the present application, the EEG electrode sensor of the present application takes the thin film PCB circuit layer as the base layer, superimposes the adhesive layer, and the connecting column passes through the through hole of the adhesive layer to be connected with the electrode core of the base layer, and the connecting column is connected to the electrode core of the base layer. It is connected with the stylus layer, and an adhesion layer is superimposed on the stylus layer, and the conductive hydrogel is immersed in the adhesion layer, so that the conductive effect is good and the measurement is accurate.
附图说明Description of drawings
图1为本申请的脑电电极传感器在一种实施方式中的元件分立示意图；FIG. 1 is a schematic diagram of the separation of components of the EEG electrode sensor of the present application in an embodiment;
图2为本申请的薄膜PCB电路层在一种实施方式中的结构示意图。FIG. 2 is a schematic structural diagram of a thin film PCB circuit layer in an embodiment of the present application.
具体实施方式Detailed ways
下面通过具体实施方式结合附图对本申请作进一步详细说明。The present application will be described in further detail below through specific embodiments in conjunction with the accompanying drawings.
如图1、图2所示，本申请的脑电电极传感器，其一种实施方式，包括薄膜PCB电路层10、粘连层20、触针层30和导电水凝胶40。薄膜PCB电路层10的一端为插接端口，薄膜PCB电路层10的另一端设有四个电极芯和控制模块13，在一种实施方式中，该控制模块13采用加密芯片，如可以是1024位的1-WireEEPROM芯片，该芯片13能够限制耗材使用时限，且在应用级上可以识别每一个终端产品。通过该加密芯片可以限定本传感器使用时间和配套监测设备，从而保证本传感器的安全。四个电极芯分别为电极A、电极B、电极C和电极D，其中电极A为参考电极，电极B为接地电极，电极D为肌电信号监测电极，电极C为感知电极，电极A、电极B、电极C和电极D构成了将脑电信号转换为电信号的中介。粘连层20设置在薄膜PCB电路层10上，在一种实施方式中，粘连层20由两面含胶的泡沫材料构成，与电极芯相对的位置镂空。粘连层20的一面粘贴于薄膜PCB电路层10，另一面粘贴于患者的额头处。粘连层20设有通孔21，通孔21有四个，通孔21与电极芯的位置相对，通孔21的大小与电极芯配合。触针层30和导电水凝胶40的大小与电极芯配合，触针层30和导电水凝胶40且由下向上依次设置在电极芯上。As shown in FIG. 1 and FIG. 2 , an embodiment of the EEG electrode sensor of the present application includes a thin film PCB circuit layer 10 , an adhesive layer 20 , a stylus layer 30 and a conductive hydrogel 40 . One end of the thin-film PCB circuit layer 10 is a plug-in port, and the other end of the thin-film PCB circuit layer 10 is provided with four electrode cores and a control module 13. In one embodiment, the control module 13 uses an encryption chip, such as a 1024 1-bit 1-Wire EEPROM chip, the chip 13 can limit the life of consumables, and can identify each terminal product at the application level. The use time of the sensor and supporting monitoring equipment can be limited through the encryption chip, so as to ensure the safety of the sensor. The four electrode cores are electrode A, electrode B, electrode C and electrode D, in which electrode A is the reference electrode, electrode B is the grounding electrode, electrode D is the electromyographic signal monitoring electrode, electrode C is the sensing electrode, electrode A, electrode B. Electrodes C and D constitute an intermediary for converting EEG signals into electrical signals. The adhesive layer 20 is disposed on the thin film PCB circuit layer 10. In one embodiment, the adhesive layer 20 is made of a foam material containing glue on both sides, and the position opposite to the electrode core is hollowed out. One side of the adhesive layer 20 is pasted on the film PCB circuit layer 10, and the other side is pasted on the patient's forehead. The adhesive layer 20 is provided with through holes 21 , there are four through holes 21 , the positions of the through holes 21 are opposite to the electrode cores, and the size of the through holes 21 matches the electrode cores. The size of the stylus layer 30 and the conductive hydrogel 40 is matched with the electrode core, and the stylus layer 30 and the conductive hydrogel 40 are sequentially arranged on the electrode core from bottom to top.
本申请的脑电电极传感器，还可以包括连接柱50，连接柱50夹持在触针层30和电极芯之间。连接柱50包括圆柱体形，且由双面含胶泡沫材料制成。连接柱50的高度在为0.5mm～1.5mm。在本实施方式中，连接柱50的高度为1mm，连接柱50可将触针层30与薄膜PCB电路层10上的电极芯相连。The EEG electrode sensor of the present application may further include a connection post 50 clamped between the stylus layer 30 and the electrode core. The connecting post 50 has a cylindrical shape and is made of double-sided glue-containing foam material. The height of the connecting column 50 is 0.5mm˜1.5mm. In this embodiment, the height of the connection post 50 is 1 mm, and the connection post 50 can connect the contact pin layer 30 with the electrode core on the thin film PCB circuit layer 10 .
本申请的脑电电极传感器，还可以包括附着层60，附着层60夹持在触针层30和导电水凝胶40之间。在一种实施方式中，附着层60包括丝状棉。附着层60的大小与触针层30大小一样，附着层60放置于触针层30上，是一层薄薄的丝状棉，用于附着导电水凝胶40。导电水凝胶40在附着层的丝状棉上，是含有Nacl的有机物，有机物为三乙醇胺和卡波树脂的混合物，为胶状液体，导电水凝胶40包括卡波树脂三乙醇胺、NaCl和水，其中卡波树脂：三乙醇胺：NaCl：水=0.5～1.5%：1～2%：1.5～2.5%：94～97%。在一种实施方式中，卡波树脂：三乙醇胺：NaCl：水=1%：1.35%：2%：95.65%。The EEG electrode sensor of the present application may further include an adhesion layer 60 sandwiched between the stylus layer 30 and the conductive hydrogel 40 . In one embodiment, the adhesive layer 60 includes filamentary cotton. The size of the adhesion layer 60 is the same as that of the stylus layer 30 . The adhesion layer 60 is placed on the stylus layer 30 and is a thin layer of silky cotton for attaching the conductive hydrogel 40 . The conductive hydrogel 40 is an organic matter containing Nacl on the silky cotton of the adhesion layer, and the organic matter is a mixture of triethanolamine and carbo resin, which is a colloidal liquid. The conductive hydrogel 40 includes carbo resin triethanolamine, NaCl and Water, of which Carboresin: Triethanolamine: NaCl: Water = 0.5-1.5%: 1-2%: 1.5-2.5%: 94-97%. In one embodiment, carbomer: triethanolamine: NaCl: water = 1%: 1.35%: 2%: 95.65%.
该混合液体无毒，无刺激性，不含过敏成分。同时，附着层60在触针层30上可加大导电水凝胶40与皮肤的接触程度，导电水凝胶40也与电极芯相接触，导电水凝胶40通过离子进行导电，具有良好的导电性能。The mixed liquid is non-toxic, non-irritating and does not contain allergic ingredients. At the same time, the adhesion layer 60 can increase the degree of contact between the conductive hydrogel 40 and the skin on the stylus layer 30, and the conductive hydrogel 40 is also in contact with the electrode core. The conductive hydrogel 40 conducts electricity through ions, and has good Electrical conductivity.
在一种实施方式中，触针层30包括带有触针的塑料圆盘。触针层30通过连接柱与电极芯连接。通过触针可以加大与患者皮肤的接触程度，同时又因为触针质地较软，不会伤害到患者皮肤。In one embodiment, the stylus layer 30 comprises a plastic disc with stylus. The contact pin layer 30 is connected to the electrode core through the connecting post. The degree of contact with the patient's skin can be increased through the stylus, and at the same time, because the stylus is soft, it will not hurt the patient's skin.
本申请的脑电电极传感器，薄膜PCB电路层10包括PET薄膜基底11和铜箔导线12，铜箔导线12设置在PET薄膜基底11上，电极芯由铜箔制成，采用沉金工艺加强导电性能。In the EEG electrode sensor of the present application, the film PCB circuit layer 10 includes a PET film substrate 11 and a copper foil conductor 12, the copper foil conductor 12 is arranged on the PET film substrate 11, and the electrode core is made of copper foil, and the immersion gold process is used to strengthen the conductivity performance.
以上内容是结合具体的实施方式对本申请所作的进一步详细说明，不能认定本申请的具体实施只局限于这些说明。对于本申请所属技术领域的普通技术人员来说，在不脱离本申请构思的前提下，还可以做出若干简单推演或替换。The above content is a further detailed description of the present application in conjunction with specific implementation modes, and it cannot be considered that the specific implementation of the present application is limited to these descriptions. For those of ordinary skill in the technical field to which the present application belongs, some simple deduction or replacement can also be made without departing from the concept of the present application.
| Application Number | Priority Date | Filing Date | Title |
|---|---|---|---|
| CN201510633541.2ACN105193411A (en) | 2015-09-29 | 2015-09-29 | Electroencephalogram electrode sensor |
| Application Number | Priority Date | Filing Date | Title |
|---|---|---|---|
| CN201510633541.2ACN105193411A (en) | 2015-09-29 | 2015-09-29 | Electroencephalogram electrode sensor |
| Publication Number | Publication Date |
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| CN105193411Atrue CN105193411A (en) | 2015-12-30 |
| Application Number | Title | Priority Date | Filing Date |
|---|---|---|---|
| CN201510633541.2APendingCN105193411A (en) | 2015-09-29 | 2015-09-29 | Electroencephalogram electrode sensor |
| Country | Link |
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| CN (1) | CN105193411A (en) |
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| WO2018218968A1 (en)* | 2017-06-02 | 2018-12-06 | 深圳市前海未来无限投资管理有限公司 | Medical glue dropping electrode and use thereof |
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| WO2011143490A2 (en)* | 2010-05-12 | 2011-11-17 | Irhythm Technologies, Inc. | Device features and design elements for long-term adhesion |
| CN102319068A (en)* | 2011-07-29 | 2012-01-18 | 上海交通大学 | Electroencephalo-graph dry electrode based on capacitive coupling principle |
| CN203873754U (en)* | 2014-05-05 | 2014-10-15 | 浙江普可医疗科技有限公司 | Disposable electroencephalogram sensor |
| CN104224167A (en)* | 2014-09-21 | 2014-12-24 | 北京师范大学 | Disposable brain state monitoring flexible patch electrode |
| CN205072866U (en)* | 2015-09-29 | 2016-03-09 | 深圳大学 | Brain electricity electrode sensor |
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| WO2011143490A2 (en)* | 2010-05-12 | 2011-11-17 | Irhythm Technologies, Inc. | Device features and design elements for long-term adhesion |
| CN102319068A (en)* | 2011-07-29 | 2012-01-18 | 上海交通大学 | Electroencephalo-graph dry electrode based on capacitive coupling principle |
| CN203873754U (en)* | 2014-05-05 | 2014-10-15 | 浙江普可医疗科技有限公司 | Disposable electroencephalogram sensor |
| CN104224167A (en)* | 2014-09-21 | 2014-12-24 | 北京师范大学 | Disposable brain state monitoring flexible patch electrode |
| CN205072866U (en)* | 2015-09-29 | 2016-03-09 | 深圳大学 | Brain electricity electrode sensor |
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| WO2018218968A1 (en)* | 2017-06-02 | 2018-12-06 | 深圳市前海未来无限投资管理有限公司 | Medical glue dropping electrode and use thereof |
| Publication | Publication Date | Title |
|---|---|---|
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