技术领域technical field
本申请涉及生物电检测中前端配置方案的一种测评方法。This application relates to an evaluation method for front-end configuration schemes in bioelectricity detection.
生物电检测中的前端是指生物电测量电极及电极与皮肤的接触界面。生物电检测前端的配置方案是指关于选择什么样的电极、要不要使用电极膏(液)、使用什么样的电极膏(液)、测点皮肤表面要不要预处理、做什么样的预处理等的方案。The front end in bioelectricity detection refers to the bioelectricity measurement electrode and the contact interface between the electrode and the skin. The configuration scheme of the bioelectric detection front end refers to what kind of electrode to choose, whether to use electrode paste (liquid), what kind of electrode paste (liquid) to use, whether to pretreat the skin surface of the measurement point, and what kind of pretreatment to do and other plans.
电极种类很多，有电极夹、电极球、电极贴等，每种电极又存在多个厂家生产的产品。电极膏(液)也存在着不同成分、不同浓度、不同厂家的差别，生理盐水是一种常见的电极液。典型的测点皮肤预处理方式可分为：不做处理、酒精擦拭、砂纸擦拭等。实际中，不管是医院里还是实验室，任一种电极和任一种电极膏(液)还有任一种皮肤表面预处理方式相结合，都可以构成一种生物电检测前端配置方案，以供使用者选择。There are many types of electrodes, including electrode clips, electrode balls, electrode stickers, etc., and there are products produced by multiple manufacturers for each electrode. Electrode paste (liquid) also has different components, different concentrations, and differences between different manufacturers. Physiological saline is a common electrode liquid. Typical skin pretreatment methods for measuring points can be divided into: no treatment, alcohol wiping, sandpaper wiping, etc. In practice, no matter in a hospital or a laboratory, the combination of any electrode, any electrode paste (solution) and any skin surface pretreatment method can constitute a front-end configuration scheme for bioelectricity detection. for users to choose.
由于不同前端配置方案带来的生物电检测结果的精度不同，有些情况可能误差很大，甚至带来误诊，因此，在确定或确认一种生物电检测前端配置方案时，应对其性能进行量化测评。Due to the different accuracy of bioelectric detection results brought about by different front-end configuration schemes, some cases may have large errors and even cause misdiagnosis. Therefore, when determining or confirming a bioelectric detection front-end configuration scheme, its performance should be quantitatively evaluated. .
背景技术Background technique
目前，国内外关于生物电检测前端配置方案的测评，还是停留在使用阻抗测量的方法。如2000年，芬兰的E.Seitsonen通过测量皮肤-电极阻抗得出结论：价格低廉的心电电极只有在用研磨膏和酒精对皮肤仔细处理之后才能代替昂贵的脑电电极进行脑电检测，而仅仅用酒精处理无法达到效果。2002年，加拿大的Hemmerling通过比较市面上常见的Meditrace心电电极和麻醉深度检测专用传感器的阻抗值后发现：对皮肤进行常规的酒精预处理后，心电电极可以用于麻醉深度检测。2013年，比利时的Y.H.Chen为了评估他们制造的梳状高分子干电极的性能，采用三电极法测量电极与皮肤之间的阻抗。At present, domestic and foreign evaluations of bioelectric detection front-end configuration schemes are still based on the method of using impedance measurement. For example, in 2000, E.Seitsonen of Finland concluded by measuring the skin-electrode impedance: cheap ECG electrodes can replace expensive EEG electrodes for EEG detection only after the skin is carefully treated with abrasive paste and alcohol, while Treatment with alcohol alone will not be effective. In 2002, Hemmerling in Canada found that after routine alcohol pretreatment of the skin, ECG electrodes could be used to detect the depth of anesthesia by comparing the impedance values of common Meditrace ECG electrodes on the market and special sensors for anesthesia depth detection. In 2013, Y.H.Chen of Belgium used the three-electrode method to measure the impedance between the electrode and the skin in order to evaluate the performance of the comb-shaped polymer dry electrode they manufactured.
现有的基于阻抗测量的生物电检测前端配置方案测评方法的不方便之处是：(1)皮肤-电极阻抗是容性阻抗，其大小随激励信号的频率而变化，因此必须具备一个频率可调且频带较宽的信号发生器，这对于一般的检测仪器来说较难满足；(2)现有的高精度阻抗测试仪不仅体积较大不便携带而且价格昂贵，如Agilent4294A精密阻抗分析仪；(3)阻抗测量中既有激励端又有测量端，在共用公共端的情况下也至少需要三个电极；(4)阻抗测试是生物电检测前端配置方案的一种间接测评方法，不能直接评估该方案下检测的生物电的噪声水平。The inconveniences of the existing evaluation methods of bioelectricity detection front-end configuration schemes based on impedance measurement are: (1) The skin-electrode impedance is a capacitive impedance, and its magnitude changes with the frequency of the excitation signal. It is difficult to meet the requirements of general detection instruments; (2) the existing high-precision impedance testers are not only large in size, inconvenient to carry, but also expensive, such as Agilent4294A precision impedance analyzer; (3) There are both excitation terminals and measurement terminals in impedance measurement, and at least three electrodes are required in the case of sharing a common terminal; (4) Impedance testing is an indirect evaluation method for the configuration scheme of the front-end bioelectric detection, and cannot be directly evaluated The bioelectrical noise level detected under this scheme.
参考文献：references:
[1]E.SEITSONEN，A.YLI-HANKALA and K.KORTTILA 2000 Areelectrocardiogram electrodes acceptable for electroencephalogram bispectralindex monitoring？ACTA ANAESTHESIOLOGICA SCANDINAVICA 44 1266-1270[1] E.SEITSONEN, A.YLI-HANKALA and K.KORTTILA 2000 Are electrocardiogram electrodes acceptable for electroencephalogram bispectralindex monitoring? ACTA ANAESTHESIOLOGICA SCANDINAVICA 44 1266-1270
[2]Hemmerling，Thomas M.MD，DEAA，Harvey，Pierre 2002ElectrocardiographicElectrodes Provide the Same Results as Expensive Special Sensors in theRoutine Monitoring of Anesthetic Depth，Anesthesia&analgesia.94 369-371[2] Hemmerling, Thomas M.MD, DEAA, Harvey, Pierre 2002 Electrocardiographic Electrodes Provide the Same Results as Expensive Special Sensors in the Routine Monitoring of Anesthetic Depth, Anesthesia&analgesia.94 369-371
[3]Y.H.Chen，M.Op de Beeck，L.Vanderheyden，V.Mihajlovic，B.Grundlehner，C.Van Hoof 2013 Comb-shaped Polymer-based Dry Electrodes for EEG/ECGMeasurements with High User Comfort，Annual International Conference of theIEEE EMBS 35 3-7[3] Y.H.Chen, M.Op de Beeck, L.Vanderheyden, V.Mihajlovic, B.Grundlehner, C.Van Hoof 2013 Comb-shaped Polymer-based Dry Electrodes for EEG/ECG Measurements with High User Comfort, Annual International Conference of theIEEE EMBS 35 3-7
发明内容Contents of the invention
发明目的。purpose of the invention.
提出一种更为直接的简单方便的生物电检测中前端配置方案的测评方法。A more direct, simple and convenient evaluation method for the front-end configuration scheme in bioelectricity detection is proposed.
技术方案。Technical solutions.
一种生物电检测中前端配置方案的测评方法，包括如下步骤，(1)在体表上选择一对测点，并准备好电压信号采集系统，(2)按待测评的前端配置方案分别安置两电极至一对测点处，并将之接入准备好的电压信号采集系统，(3)采集记录一段此前端配置方案配置状态下两测点的电压数据，(4)依据记录的电压数据值的大小对该前端配置方案进行测评，电压数据值越小意味着该配置方案下的干扰和噪声会越小，其特征是，在第(1)步体表选择一对测点时，一对测点的选取要足够近，在保证连接电极不发生触碰的情况下尽量近，在第(4)步中定义所采集电压数值的大小测度对配置方案进行评估。A method for evaluating front-end configuration schemes in bioelectricity detection, comprising the following steps: (1) selecting a pair of measuring points on a body surface and preparing a voltage signal acquisition system; (2) installing them respectively according to the front-end configuration schemes to be evaluated Two electrodes to a pair of measuring points, and connect them to the prepared voltage signal acquisition system, (3) collect and record a section of voltage data of the two measuring points under the configuration state of the front-end configuration scheme, (4) according to the recorded voltage data The size of the value is used to evaluate the front-end configuration scheme. The smaller the value of the voltage data means the smaller the interference and noise under the configuration scheme. The selection of the measurement points should be close enough, as close as possible without touching the connecting electrodes, and in step (4), define the size measurement of the collected voltage values to evaluate the configuration scheme.
以上测评方法是根据前端配置方案下检测的信号的干扰噪声大小来对其进行评判的，与检测阻抗来对其评判的方法是一致的。附图2和附图3是业界公认的生物电检测系统的干扰噪声模型，其中，附图2为干扰摄入模型，附图3为噪声产生模型。从附图2可知，外部干扰电压源，如高压电网、机电设备、电台及自然界的雷电现象等，通过电容C与检测电路耦合，在接触阻抗(R+jX)和生物电检测仪器输入电阻(Ri)并联的分压作用下进入生物电检测电路；由于输入阻抗(Ri)固定且足够大，因此，检测仪器输入端口引入的外部干扰与接触阻抗(R+jX)的大小成正比。同样，由附图3可知，由电路本身造成的内部噪声电流i通过接触阻抗(R+jX)流回生物电检测电路，同样会产生一个与接触阻抗成正比的噪声电压。The above evaluation method is based on the interference noise of the signal detected under the front-end configuration scheme to evaluate it, which is consistent with the method of evaluating it by detecting impedance. Accompanying drawing 2 and accompanying drawing 3 are the interference noise models of the bioelectric detection system recognized in the industry, wherein, accompanying drawing 2 is the interference intake model, and accompanying drawing 3 is the noise generation model. It can be seen from Figure 2 that external interference voltage sources, such as high-voltage power grids, electromechanical equipment, radio stations, and natural lightning phenomena, etc., are coupled with the detection circuit through the capacitance C, and the contact impedance (R+jX) and the input resistance of the bioelectricity detection instrument ( Ri) enters into the bioelectricity detection circuit under the action of partial pressure in parallel; since the input impedance (Ri) is fixed and large enough, the external interference introduced by the input port of the detection instrument is proportional to the size of the contact impedance (R+jX). Similarly, it can be seen from FIG. 3 that the internal noise current i caused by the circuit itself flows back to the bioelectricity detection circuit through the contact impedance (R+jX), which will also generate a noise voltage proportional to the contact impedance.
另一方面，本方案让两测点在不触碰的情况下足够近，排除了生物电本身和人体阻抗本身对前端配置方案评判的影响，因为当两测点足够近时它们的生物电电位差近似为0、两点间的人体阻抗本身也足够小。On the other hand, this scheme allows the two measurement points to be close enough without touching, and eliminates the influence of bioelectricity itself and human body impedance itself on the evaluation of the front-end configuration scheme, because when the two measurement points are close enough, their bioelectric potential The difference is approximately 0, and the impedance of the human body between the two points is also small enough.
有益效果。Beneficial effect.
为了验证本发明的可行性，发明人对18种前端配置方案进行了测试，这18种前端配置方案如表1所示。每位受试者在每一种配置方案下分别记录了48秒两测点间的电压数据；为了便于对照，发明人同时用仪器测量了两测点间的0.1Hz-1000Hz频率范围内的阻抗(R+jX)。In order to verify the feasibility of the present invention, the inventor has tested 18 front-end configuration schemes, and these 18 front-end configuration schemes are shown in Table 1. Each subject recorded the voltage data between the two measuring points for 48 seconds under each configuration scheme; for the convenience of comparison, the inventor also measured the impedance within the frequency range of 0.1Hz-1000Hz between the two measuring points with an instrument (R+jX).
附图4所示是其中一位受试者在部分前端配置下测得的电压波形图，六个图分别对应表1所列的配置方案(1)到配置方案(6)，显然，不同配置方案产生的干扰和噪声不同。Attached Figure 4 shows the voltage waveforms measured by one of the subjects under some front-end configurations. The six graphs correspond to the configuration schemes (1) to (6) listed in Table 1. Obviously, different configurations Scenarios generate interference and noise differently.
表2给出了五名受试者通过两种测评方法所得结果，其中峰峰值指用本发明方法测得电压信号的峰峰值测度(单位V)，平均阻抗指用阻抗法测得的0.1Hz-1000Hz频率范围内两点间阻抗的平均值(单位Ω)。很明显，本测试方法得到的电压大小规律和阻抗大小规律是完全一致的。Table 2 has provided five test subjects by two kinds of evaluation methods obtained results, wherein peak-to-peak value refers to the peak-to-peak measurement (unit V) of the voltage signal measured by the method of the present invention, and the average impedance refers to the 0.1Hz measured by the impedance method The average value of the impedance between two points within the frequency range of -1000Hz (unit Ω). Obviously, the voltage and impedance obtained by this test method are completely consistent.
与现有的阻抗测试方法比较，本测评方法的优势体现在：(1)不需要增加额外信号源设备，以环境中的干扰信号和检测电路内部的噪声电流作为信号源，检测它们在测试端口引入的干扰和噪声信号大小来评判；(2)操作更简单，方便；(3)阻抗测试是一种间接测评方法，而本方法通过检测干扰噪声水平来评估更直接。Compared with the existing impedance test method, the advantages of this evaluation method are as follows: (1) No need to add additional signal source equipment, use the interference signal in the environment and the noise current inside the detection circuit as the signal source, and detect them at the test port (2) The operation is simpler and more convenient; (3) Impedance testing is an indirect evaluation method, but this method is more direct by detecting the level of interference noise.
表1：用于测评的18种前端配置方案Table 1: 18 front-end configuration schemes for evaluation
表2：5位受试者不同前端配置方案下电压与阻抗的测试结果Table 2: Test results of voltage and impedance of 5 subjects under different front-end configuration schemes
附图说明Description of drawings
图1，本测评方法流程图Figure 1, the flow chart of this evaluation method
图2，生物电检测系统的外部干扰摄入模型Figure 2. The external disturbance intake model of the bioelectricity detection system
图3，生物电检测系统的噪声电流产生输出噪声模型Figure 3. Noise current generation output noise model of bioelectric detection system
图4，用本发明方法对某一受试者六种配置方案下的测试结果Fig. 4, test result under six configuration schemes of a subject with the method of the present invention
图5，实际检测试验示意图Figure 5, the schematic diagram of the actual detection test
具体实施方式(实施例)Specific embodiments (embodiments)
2014年11月-2015年1月，发明人对所在实验室成员共10人(均为18岁以上健康成年人，其中6名男性，4名女性)按表1所示的18种配置方案分别进行了测试。其中5人的测试结果见表2所示。From November 2014 to January 2015, the inventor made a total of 10 members of his laboratory (all healthy adults over the age of 18, including 6 males and 4 females) according to the 18 configuration schemes shown in Table 1. taking the test. The test results of 5 of them are shown in Table 2.
下面是某一受试者一种前端配置方案下测评方法具体实施步骤：(1)让受试者在实验桌旁坐好，被测手臂平置于桌面，内侧光滑面朝上，受试者全身放松，选右手臂内侧皮肤上两个 距离约为5cm的点为测点，并准备好以NI PCI 4461为采集卡搭建的生物电检测仪器；(2)按照待测评的前端配置方案做处理，并分别安置两电极至步骤(1)中选定的测点处，并接入NI PCI4461的采集端口Ai，如附图5所示；(3)采集记录一段此状态下两测点的电压数据，24秒长度，txt格式；(4)计算所记录数据电压的峰峰值测度，以供评价。The following are the specific implementation steps of the evaluation method under a front-end configuration scheme for a certain subject: (1) Let the subject sit by the experimental table, place the tested arm flat on the table, with the inner smooth side facing upwards, and the subject Relax the whole body, choose two points on the skin on the inner side of the right arm with a distance of about 5cm as the measuring points, and prepare a bioelectric detection instrument built with NI PCI 4461 as the acquisition card; (2) Process according to the front-end configuration plan to be evaluated , and respectively place two electrodes to the measuring points selected in step (1), and connect them to the acquisition port Ai of NI PCI4461, as shown in Figure 5; (3) collect and record the voltage of the two measuring points in this state Data, 24 seconds in length, in txt format; (4) Calculate the peak-to-peak measurement of the recorded data voltage for evaluation.
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| CN201510027754.0ACN104523261B (en) | 2015-01-16 | 2015-01-16 | A kind of assessment method of front-end configuration scheme in biological electro-detection |
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| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| DE60223548T2 (en)* | 2001-07-06 | 2008-10-23 | Aspect Medical Systems, Inc., Newton | SYSTEM AND METHOD FOR MEASURING BIOELECTRIC RESISTANCE IN THE EVENT OF INTERFERENCE |
| JP4150402B2 (en)* | 2005-03-03 | 2008-09-17 | 株式会社半導体理工学研究センター | Signal waveform measuring apparatus and signal waveform measuring system |
| EP2101408B1 (en)* | 2008-03-11 | 2012-05-16 | CSEM Centre Suisse d'Electronique et de Microtechnique SA - Recherche et Développement | Floating front-end amplifier and one-wire measuring devices |
| US8583215B2 (en)* | 2009-11-05 | 2013-11-12 | Biosense Webster (Israel) Ltd. | Reduction of catheter electrode loading |
| CN203354538U (en)* | 2013-07-18 | 2013-12-25 | 重庆海睿科技有限公司 | Body skin electric measurement system based on wireless technology |
| Publication number | Publication date |
|---|---|
| CN104523261A (en) | 2015-04-22 |
| Publication | Publication Date | Title |
|---|---|---|
| US10070800B2 (en) | Impedance measurement process | |
| US20230346286A1 (en) | Needle impedance electromyography and electrical impedance imaging for enhanced muscle diagnostics | |
| KR101947676B1 (en) | Method and apparatus for measuring bio signal | |
| US20080287823A1 (en) | Index Determination | |
| CA2777797A1 (en) | Fluid level indicator determination | |
| WO2015123603A1 (en) | Electrical impedance myography | |
| Noveletto et al. | Analog front-end for the integrated circuit AD5933 used in electrical bioimpedance measurements | |
| JP2012500663A5 (en) | ||
| CN104523261B (en) | A kind of assessment method of front-end configuration scheme in biological electro-detection | |
| CN106725474A (en) | A kind of human body impedance detection method | |
| Kumar et al. | Analysis and validation of medical application through electrical impedance based system | |
| Massot et al. | A portable device performing continuous impedance spectroscopy for skin conductivity | |
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| Wang et al. | Study into the repeatability of the electrode-skin interface utilizing electrodes commonly used in Electrical Impedance Tomography | |
| Burgar et al. | Proposed standard measurement techniques for the technical specification of biofeedback devices | |
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