TW201620439A - Electrocardio recording system - Google Patents
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- 238000004891 communication Methods 0.000 claims abstract description 13
- 238000001914 filtration Methods 0.000 claims abstract description 8
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- 238000006243 chemical reaction Methods 0.000 claims description 22
- 230000000747 cardiac effect Effects 0.000 claims description 12
- 238000004458 analytical method Methods 0.000 claims description 9
- 230000002889 sympathetic effect Effects 0.000 claims description 6
- 229910001369 Brass Inorganic materials 0.000 claims description 4
- 230000002567 autonomic effect Effects 0.000 claims description 4
- 239000010951 brass Substances 0.000 claims description 4
- 230000000903 blocking effect Effects 0.000 claims description 3
- 239000000463 material Substances 0.000 claims description 3
- VYZAMTAEIAYCRO-UHFFFAOYSA-N Chromium Chemical compound [Cr] VYZAMTAEIAYCRO-UHFFFAOYSA-N 0.000 claims 1
- 239000002184 metal Substances 0.000 abstract description 5
- 238000002565 electrocardiography Methods 0.000 description 11
- 238000005259 measurement Methods 0.000 description 5
- 230000000694 effects Effects 0.000 description 4
- 238000012544 monitoring process Methods 0.000 description 4
- 230000003321 amplification Effects 0.000 description 2
- 238000010586 diagram Methods 0.000 description 2
- 230000001939 inductive effect Effects 0.000 description 2
- 238000000034 method Methods 0.000 description 2
- 238000003199 nucleic acid amplification method Methods 0.000 description 2
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- 230000004075 alteration Effects 0.000 description 1
- 108091008698 baroreceptors Proteins 0.000 description 1
- 238000003745 diagnosis Methods 0.000 description 1
- 238000005516 engineering process Methods 0.000 description 1
- 239000007769 metal material Substances 0.000 description 1
- 238000012986 modification Methods 0.000 description 1
- 230000004048 modification Effects 0.000 description 1
- 210000005037 parasympathetic nerve Anatomy 0.000 description 1
- 210000001002 parasympathetic nervous system Anatomy 0.000 description 1
- 230000002093 peripheral effect Effects 0.000 description 1
- 210000001774 pressoreceptor Anatomy 0.000 description 1
- 238000010223 real-time analysis Methods 0.000 description 1
- 230000011514 reflex Effects 0.000 description 1
- 230000029058 respiratory gaseous exchange Effects 0.000 description 1
- 230000003595 spectral effect Effects 0.000 description 1
- 238000001356 surgical procedure Methods 0.000 description 1
- 210000002820 sympathetic nervous system Anatomy 0.000 description 1
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Abstract
Description
本發明是有關於一種心電感測系統，特別是有關於一種能夠提高心電圖記錄的機動性及簡便性的心電感測系統。The present invention relates to a cardiac electrical sensing system, and more particularly to a cardiac electrical sensing system capable of improving the maneuverability and simplicity of electrocardiographic recording.
心電描記技術（Electrocardiography, ECG），是藉由在皮膚上設置接觸電極，經由胸腔將心臟之電生理活動以時間為單位記錄下來的診療技術，屬於無創性的記錄方式。Electrocardiography (ECG) is a non-invasive recording method in which the electrophysiological activity of the heart is recorded in units of time through the chest cavity by providing a contact electrode on the skin.
簡單來說，ECG的工作原理就是利用心臟跳動時，在皮膚表面產生的極小電變化，將此電變化以感測器捕捉並放大即可描繪出心電圖。通常，在肢體上需放置至少3個電極，並將其兩兩組成一對進行測量。例如，左臂電極（LA）、右臂電極（RA）和左腿電極（LL）的組合可包含LA+RA、RA+LL及LA+LL。每個電極對的輸出訊號稱為一組導程，可使醫師從不同的角度獲得心臟的電變化。To put it simply, the ECG works by using the tiny electrical changes that occur on the surface of the skin when the heart beats. This electrical change is captured by the sensor and amplified to map the ECG. Usually, at least 3 electrodes are placed on the limb and they are paired for measurement. For example, a combination of a left arm electrode (LA), a right arm electrode (RA), and a left leg electrode (LL) may include LA+RA, RA+LL, and LA+LL. The output signal of each electrode pair is called a set of leads, allowing the physician to obtain electrical changes in the heart from different angles.
心電圖的種類可以從導程的數量來分類，例如有3導程心電圖、5導程心電圖及12導程心電圖等。12導程心電圖屬於臨床研究中最常見的一種，可以同時記錄體表12組導程的電位變化，並在心電圖紙上描繪出12組導程訊號，常用於一次性的心電圖診斷。3導程及5導程心電圖則多用於需要連續監測心臟活動的情況，如手術過程中或在救護車轉運病人的監護中。根據儀器的不同，連續監測的結果有時可能無法完整的記錄下來。The type of electrocardiogram can be classified by the number of leads, such as a 3-lead electrocardiogram, a 5-lead electrocardiogram, and a 12-lead electrocardiogram. The 12-lead ECG is the most common type of clinical study. It can simultaneously record the potential changes of the 12-group lead of the body surface, and draw 12 sets of lead signals on the ECG drawings, which are often used for one-time ECG diagnosis. 3-lead and 5-lead ECGs are often used for situations where continuous monitoring of cardiac activity is required, such as during surgery or during ambulance transport patient monitoring. Depending on the instrument, the results of continuous monitoring may sometimes not be fully documented.
另外，就心電圖的後續電路而言，目前都是以訂做的線路來完成，並加上專屬的程式以進行訊號或心率變異度的分析。這些訂做的線路都包含大量複雜的放大器電路，而分析程式也都是以相當昂貴的PC或工作站來完成。另外，現今大部分的心電圖測量儀器的體積也都非常巨大，導致心電圖的測量及分析技術，一直無法延伸到醫院以外的區域。In addition, in the follow-up circuit of the ECG, it is currently done on a customized line, and a dedicated program is added for signal or heart rate variability analysis. These custom-made lines contain a large number of complex amplifier circuits, and the analysis programs are all done with fairly expensive PCs or workstations. In addition, most of today's ECG measuring instruments are also very large, leading to the measurement and analysis technology of ECG, which has not been extended to areas outside the hospital.
鑑於以上所述之問題，本發明之主要目的，即在於提供一種心電感測系統，不需身處醫院就可即時測量並監控心臟活動，以達到提高心電圖記錄的機動性及簡便性等功效。In view of the above problems, the main object of the present invention is to provide a cardiac inductive measurement system that can measure and monitor cardiac activity in real time without being in a hospital, so as to improve the mobility and simplicity of electrocardiographic recording.
為具體描述本發明之內容，在此揭露 一種心電感測系統，其包含感測裝置、差動放大電路、濾波電路、快速轉換電路、類比數位轉換介面及通訊電路。感測裝置包含以黃銅鍍鉻之材料形成之二導程金屬電極，用以接收生物電訊號；差動放大電路，與感測裝置電性連接而形成迴路，以放大生物電訊號；濾波電路與差動放大電路電性連接而形成迴路，以從生物電訊號中濾除雜訊而獲得生理特徵訊號；快速轉換電路與濾波電路電性連接而形成迴路，使用心率變異參數頻域分析方法即時分析生理特徵訊號，並輸出功率頻譜曲線；類比數位轉換介面係位於電腦系統中，其電性連接快速轉換電路以接收功率頻譜曲線；通訊電路與電腦系統電性連接而形成迴路，使功率頻譜曲線經由通訊電路儲存於雲端資料庫中，以即時監控生理特徵訊號。To specifically describe the contents of the present invention, a cardiac sensing system is disclosed herein, which includes a sensing device, a differential amplifying circuit, a filtering circuit, a fast switching circuit, an analog digital conversion interface, and a communication circuit. The sensing device comprises a two-lead metal electrode formed of a brass chrome-plated material for receiving a bio-electric signal; a differential amplifying circuit electrically connected with the sensing device to form a loop to amplify the bio-electric signal; the filter circuit and The differential amplifier circuit is electrically connected to form a loop to filter the noise from the bioelectric signal to obtain the physiological characteristic signal; the fast conversion circuit and the filter circuit are electrically connected to form a loop, and the heart rate variability parameter frequency domain analysis method is used for real-time analysis. The physiological characteristic signal and the output power spectrum curve; the analog digital conversion interface is located in the computer system, and is electrically connected to the fast conversion circuit to receive the power spectrum curve; the communication circuit is electrically connected with the computer system to form a loop, so that the power spectrum curve is passed through The communication circuit is stored in the cloud database to monitor physiological characteristic signals in real time.
較佳地，電腦系統從功率頻譜曲線獲得低頻與總頻功率比，以測量出生理特徵訊號中的交感神經定量指標。Preferably, the computer system obtains a low frequency to total frequency power ratio from the power spectrum curve to measure a sympathetic quantitative indicator in the physiological characteristic signal.
較佳地，電腦系統從功率頻譜曲線獲得低高頻比值，以反應出生理特徵訊號中的自主神經平衡指標。Preferably, the computer system obtains a low-frequency ratio from the power spectrum curve to reflect the autonomic balance indicator in the physiological characteristic signal.
較佳地，電腦系統從功率頻譜曲線獲得總功率，以評估生理特徵訊號中的心率變異度。Preferably, the computer system obtains the total power from the power spectrum curve to assess heart rate variability in the physiological signature signal.
較佳地，二導程金屬電極與人體之接觸電阻值介於10Ω~100Ω之間。Preferably, the contact resistance between the two-lead metal electrode and the human body is between 10 Ω and 100 Ω.
較佳地，感測裝置與差動放大電路之間更包含至少一高電阻，用以阻絕高電流，高電阻之電阻值介於1MΩ~10 MΩ之間。Preferably, the sensing device and the differential amplifying circuit further comprise at least one high resistance for blocking high current, and the high resistance has a resistance value between 1 MΩ and 10 MΩ.
較佳地，差動放大電路包含儀表放大器，用以將生物電訊號之電壓以增益1000之放大倍率輸出。Preferably, the differential amplifying circuit includes an instrumentation amplifier for outputting the voltage of the bioelectric signal at a magnification of 1000.
較佳地，差動放大電路更包含補償電路，與儀表放大器電性連接，用以補償所輸出之生物電訊號之電壓，同時提高差動放大電路之放大倍率的精度。Preferably, the differential amplifying circuit further comprises a compensation circuit electrically connected to the instrumentation amplifier for compensating the voltage of the bioelectric signal outputted, and improving the precision of the magnification of the differential amplifying circuit.
較佳地，濾波電路包含帶通濾波器，用以將頻率為60Hz之市電頻率從生物電訊號中濾除。Preferably, the filter circuit includes a band pass filter for filtering a commercial frequency having a frequency of 60 Hz from the bioelectric signal.
較佳地，濾波電路包含低通濾波器及高通濾波器，低通濾波器及高通濾波器係分別將頻率在0.5Hz以下及頻率在100Hz以上之雜訊從生物電訊號中濾除。Preferably, the filter circuit comprises a low pass filter and a high pass filter, and the low pass filter and the high pass filter respectively filter noise having a frequency below 0.5 Hz and a frequency above 100 Hz from the bioelectric signal.
為使本發明之上述特徵對所屬領域之通常知識者能更加地明顯易懂，以下將舉例示性實施例並配合其圖式，做詳細說明如下。In order to make the above-described features of the present invention more comprehensible to those skilled in the art, the following exemplary embodiments will be described in detail below.
以下將參照相關圖式，說明依本發明之心電感測系統之實施例，為使便於理解，下述實施例中之相同元件係以相同之符號標示來說明。The embodiments of the inductive sensing system according to the present invention will be described below with reference to the related drawings. For ease of understanding, the same components in the following embodiments are denoted by the same reference numerals.
請參照第1圖，係根據例示性實施例而顯示本發明之心電感測系統的功能方塊圖。如第1圖所示，本發明係提供心電感測系統100，其包含：感測裝置10、差動放大電路20、濾波電路30、快速轉換電路40、電腦系統50及通訊電路60。Referring to Figure 1, a functional block diagram of a cardiac sensing system of the present invention is shown in accordance with an illustrative embodiment. As shown in FIG. 1, the present invention provides a cardiac inductance measuring system 100 comprising: a sensing device 10, a differential amplifying circuit 20, a filter circuit 30, a fast switching circuit 40, a computer system 50, and a communication circuit 60.
感測裝置10包含以黃銅鍍鉻之材料形成之二導程金屬電極11，用以接收生物電訊號。本發明之感測裝置10主要是藉由金屬電極11接觸雙手手掌以獲得生物電訊號，由於雙手的掌心是整個手掌皮膚較細緻且較薄的位置，因此以雙手的掌心作為感測點可得到較準確的心電訊號值。舉例而言，本發明係利用二導程金屬電極11分別接觸於雙手的掌心，且金屬電極11均為乾式電極並以黃銅鍍鉻之金屬材料形成，因此本發明之二導程金屬電極與人體之接觸電阻值係介於10Ω~100Ω之間。另外，感測裝置10可更包含電源電路12，用以提供後續電路所需之整流電壓。The sensing device 10 includes a two-lead metal electrode 11 formed of a brass chrome-plated material for receiving a bioelectric signal. The sensing device 10 of the present invention mainly contacts the palms of both hands by the metal electrode 11 to obtain a bioelectric signal. Since the palm of the hands is a finer and thinner position of the entire palm skin, the palm of the hands is used as the sensing. Point to get a more accurate ECG signal value. For example, the present invention utilizes the two-lead metal electrodes 11 to respectively contact the palm of both hands, and the metal electrodes 11 are both dry electrodes and formed of a brass chrome-plated metal material, so the two-lead metal electrode of the present invention The contact resistance of the human body is between 10Ω and 100Ω. In addition, the sensing device 10 can further include a power supply circuit 12 for providing a rectified voltage required by the subsequent circuit.
差動放大電路20與感測裝置10電性連接而形成迴路，以放大生物電訊號。其中，差動放大電路20可包含儀表放大器21及補償電路22。儀表放大器21可將生物電訊號之電壓以增益1000之放大倍率輸出，補償電路22可與儀表放大器21電性連接，以補償所輸出之生物電訊號之電壓，同時提高差動放大電路20之放大倍率的精度。另外，感測裝置10與差動放大電路20之間可進一步包含至少一高電阻，用以阻絕高電流藉由雙手掌心進入人體。高電阻之電阻值較佳介於1MΩ~10 MΩ之間。The differential amplifying circuit 20 is electrically connected to the sensing device 10 to form a loop to amplify the bioelectric signal. The differential amplifier circuit 20 can include an instrumentation amplifier 21 and a compensation circuit 22. The instrumentation amplifier 21 can output the voltage of the bio-electric signal at a magnification of 1000, and the compensation circuit 22 can be electrically connected to the instrumentation amplifier 21 to compensate the voltage of the bio-electric signal output, and at the same time increase the amplification of the differential amplifier circuit 20. The accuracy of the magnification. In addition, the sensing device 10 and the differential amplifying circuit 20 may further include at least one high resistance for blocking high current from entering the human body through the palm of both hands. The resistance of the high resistance is preferably between 1 MΩ and 10 MΩ.
濾波電路30與差動放大電路20電性連接而形成迴路，以從生物電訊號中濾除雜訊而獲得生理特徵訊號。其中，濾波電路30包含帶通濾波器31、低通濾波器32以及高通濾波器33。帶通濾波器31可用以將頻率為60Hz之市電頻率從生物電訊號中濾除，低通濾波器32及高通濾波器33則可分別將頻率在0.5Hz以下及頻率在100Hz以上之雜訊從生物電訊號中濾除。The filter circuit 30 is electrically connected to the differential amplifier circuit 20 to form a loop for filtering noise from the bioelectric signal to obtain a physiological characteristic signal. The filter circuit 30 includes a band pass filter 31, a low pass filter 32, and a high pass filter 33. The bandpass filter 31 can be used to filter the commercial frequency of the frequency of 60 Hz from the bioelectric signal, and the low pass filter 32 and the high pass filter 33 can respectively select the noise below 0.5 Hz and the frequency above 100 Hz. Filter out in bioelectric signals.
快速轉換電路40與濾波電路30電性連接而形成迴路，使用心率變異參數頻域分析方法即時分析生理特徵訊號，並輸出功率頻譜曲線。其中，心率變異參數頻域分析方法是把任意的時域函數（time domain）以數學方法，例如，拉普拉斯轉換(Laplace Transform)、傅立葉轉換(Fourier Transform)或Z-轉換(Z-Transform)等，轉換成頻域函數（frequency domain），其可包含週期性函數及非週期性函數等。在本發明的較佳實施例中，快速轉換電路40可為快速傅立葉轉換(Fast Fourier Transform)電路。The fast conversion circuit 40 is electrically connected to the filter circuit 30 to form a loop, and the heart rate variability parameter frequency domain analysis method is used to analyze the physiological characteristic signal in real time and output a power spectrum curve. Wherein, the frequency domain analysis method of the heart rate variability parameter is to mathematically use an arbitrary time domain function, for example, Laplace Transform, Fourier Transform, or Z-Transform (Z-Transform) And so on, converted into a frequency domain, which may include a periodic function, a non-periodic function, and the like. In a preferred embodiment of the invention, the fast conversion circuit 40 can be a Fast Fourier Transform circuit.
根據例示性實施例，本發明是將時域中取得的所有R-R波間期（R-R interval）以非參數方法進行的頻域分析。因此，快速轉換電路40會將從濾波電路30中獲得的生理特徵訊號分割為三個範圍：極低頻、低頻、及高頻部分。According to an exemplary embodiment, the present invention is a frequency domain analysis of all R-R wave intervals (R-R intervals) taken in the time domain in a non-parametric manner. Therefore, the fast conversion circuit 40 divides the physiological characteristic signal obtained from the filter circuit 30 into three ranges: an extremely low frequency, a low frequency, and a high frequency portion.
極低頻（very low frequency, VLF），頻率範圍約在0.00~0.01Hz之間。可根據此頻段作為判斷反應交感與副交感神經系統的指標，影響因子有周邊的壓力感受器、溫度調節反應、以及血管張力反射等。Very low frequency (VLF), the frequency range is between 0.00~0.01Hz. According to this frequency band, it can be used as an index for judging the reaction sympathetic and parasympathetic nervous system. The influencing factors include peripheral baroreceptors, temperature regulation reactions, and vascular tone reflex.
低頻（low frequency, LF），頻率範圍約在0.04~0.15Hz之間。可根據此頻段作為判斷反應副交感神經的活動能力的指標，波峰值會隨著呼吸而有所變動。Low frequency (LF), the frequency range is between 0.04~0.15Hz. According to this frequency band, it can be used as an indicator for judging the activity of the parasympathetic nerve, and the peak value will vary with breathing.
高頻（high frequency, HF），頻率範圍約在0.15~0.40Hz之間。可根據此頻段作為判斷交感神經的活動能力的指標。High frequency (HF), the frequency range is between 0.15~0.40Hz. This frequency band can be used as an indicator for judging the sympathetic activity.
根據上述說明的三個頻段中的功率，快速轉換電路40可輸出功率頻譜曲線，並根據功率頻譜曲線中包含的各個參數來得知心臟在進行活動時的狀況。例如，表示功率頻譜曲線下的面積總和之參數稱為總功率（total power, TP），且根據其頻率大小的不同又可分為低頻功率（low frequency power）及高頻功率（high frequency power）。Based on the power in the three frequency bands described above, the fast conversion circuit 40 can output a power spectrum curve and know the condition of the heart while it is active based on various parameters included in the power spectrum curve. For example, the parameter indicating the sum of the areas under the power spectrum curve is called total power (TP), and can be classified into low frequency power and high frequency power according to the magnitude of the frequency. .
根據例示性實施例，本發明主要使用的頻率功率之參數可歸納為以下三種：低頻與總頻功率比（low frequency and total power proportion, LFP）、低高頻比值（low frequency/ high frequency, LF/HF）、以及總功率。其中，LFP是交感神經的活性定量指標；LF/HF可反應自主神經活性平衡；TP可評估心率整體變異度。另外，使用於本發明之參數頻率範圍及其單位如下表1所示。According to an exemplary embodiment, the parameters of the frequency power mainly used in the present invention can be summarized into the following three types: low frequency and total power ratio (LFP), low frequency/high frequency (LF). /HF), and total power. Among them, LFP is a quantitative indicator of sympathetic activity; LF/HF can reflect the balance of autonomic activity; TP can assess the overall variability of heart rate. Further, the parameter frequency range and its unit used in the present invention are as shown in Table 1 below.
表1
根據本發明之例示性實施例，電腦系統50可包含類比數位轉換介面51，其電性連接快速轉換電路40以接收並分析功率頻譜曲線。其中，電腦系統50可藉由類比數位轉換介面51將轉換後之功率頻譜曲線進行分析。根據以上說明，電腦系統50可從功率頻譜曲線獲得低頻與總頻功率比，以測量出生理特徵訊號中的交感神經定量指標；從功率頻譜曲線獲得低高頻比值，以反應出生理特徵訊號中的自主神經平衡指標；以及從功率頻譜曲線獲得總功率，以評估生理特徵訊號中的心率變異度。In accordance with an exemplary embodiment of the present invention, computer system 50 may include an analog digital conversion interface 51 that is electrically coupled to fast conversion circuit 40 to receive and analyze power spectral curves. The computer system 50 can analyze the converted power spectrum curve by the analog digital conversion interface 51. According to the above description, the computer system 50 can obtain the low frequency to total frequency power ratio from the power spectrum curve to measure the sympathetic quantitative index in the physiological characteristic signal; obtain the low high frequency ratio from the power spectrum curve to reflect the physiological characteristic signal. The autonomic balance indicator; and the total power obtained from the power spectrum curve to assess heart rate variability in the physiological characteristic signal.
通訊電路60與電腦系統50電性連接而形成迴路，使功率頻譜曲線經由通訊電路儲存於雲端資料庫中，以即時監控生理特徵訊號。The communication circuit 60 is electrically connected to the computer system 50 to form a loop, so that the power spectrum curve is stored in the cloud database via the communication circuit to monitor the physiological characteristic signal in real time.
請參照第2圖，係根據例示性實施例而顯示本發明之心電感測系統的實施流程圖。如第2圖所示，本發明之心電感測系統所使用的感測方法包含以下步驟：利用二導程金屬電極分別與雙手手掌接觸，以接收生物電訊號（S1）；使用差動放大電路放大生物電訊號（S2）；藉由濾波電路從生物電訊號中濾除雜訊而獲得生理特徵訊號（S3）；藉由快速轉換電路利用心率變異參數頻域分析方法即時分析生理特徵訊號並輸出功率頻譜曲線（S4）；電腦系統根據功率頻譜曲線而獲得低頻與總頻功率比、低高頻比值、以及總功率（S5）；經由通訊電路將獲得參數儲存於雲端資料庫中以即時監控生理特徵訊號（S6）。Referring to FIG. 2, a flowchart of an implementation of the cardiac inductance measuring system of the present invention is shown in accordance with an exemplary embodiment. As shown in FIG. 2, the sensing method used in the cardiac sensing system of the present invention comprises the steps of: respectively contacting the palms of both hands with a two-lead metal electrode to receive a bioelectric signal (S1); using differential amplification The circuit amplifies the bioelectric signal (S2); the physiological characteristic signal (S3) is obtained by filtering the noise from the bioelectric signal by the filtering circuit; and the physiological characteristic signal is analyzed in real time by using the heart rate variability parameter frequency domain analysis method by the fast conversion circuit and Output power spectrum curve (S4); the computer system obtains the low frequency to total frequency power ratio, the low frequency ratio, and the total power according to the power spectrum curve (S5); the obtained parameters are stored in the cloud database via the communication circuit for real-time monitoring Physiological characteristic signal (S6).
雖然本發明已以實施例揭露如上，但其僅為舉例性，而非為限制性者。任何未脫離本發明之精神與範疇，而對其進行之等效修改或變更，均應包含於後附之申請專利範圍中。The invention has been described above by way of example only, and not by way of limitation. Any equivalent modifications or alterations to the spirit and scope of the invention are intended to be included in the scope of the appended claims.
10‧‧‧感測裝置
100‧‧‧心電感測系統
11‧‧‧金屬電極
12‧‧‧電源電路
20‧‧‧差動放大電路
21‧‧‧儀表放大器
22‧‧‧補償電路
30‧‧‧濾波電路
31‧‧‧帶通濾波器
32‧‧‧高通濾波器
33‧‧‧低通濾波器
40‧‧‧快速轉換電路
50‧‧‧電腦系統
51‧‧‧類比數位轉換介面
60‧‧‧通訊電路
S1~S6‧‧‧步驟10‧‧‧Sensing device
100‧‧‧heart inductance measurement system
11‧‧‧Metal electrodes
12‧‧‧Power circuit
20‧‧‧Differential Amplifying Circuit
21‧‧‧Instrument Amplifier
22‧‧‧Compensation circuit
30‧‧‧Filter circuit
31‧‧‧Bandpass filter
32‧‧‧High-pass filter
33‧‧‧Low-pass filter
40‧‧‧ fast conversion circuit
50‧‧‧ computer system
51‧‧‧ analog digital conversion interface
60‧‧‧Communication circuit
S1~S6‧‧‧Steps
第1圖係根據例示性實施例而顯示本發明之心電感測系統的功能方塊圖。1 is a functional block diagram showing a cardiac inductance measuring system of the present invention in accordance with an exemplary embodiment.
第2圖係根據例示性實施例而顯示本發明之心電感測系統的實施流程圖。2 is a flow chart showing an implementation of the heart-sensing system of the present invention in accordance with an exemplary embodiment.
10‧‧‧感測裝置 10‧‧‧Sensing device
100‧‧‧心電感測系統 100‧‧‧heart inductance measurement system
11‧‧‧金屬電極 11‧‧‧Metal electrodes
12‧‧‧電源電路 12‧‧‧Power circuit
20‧‧‧差動放大電路 20‧‧‧Differential Amplifying Circuit
21‧‧‧儀表放大器 21‧‧‧Instrument Amplifier
22‧‧‧補償電路 22‧‧‧Compensation circuit
30‧‧‧濾波電路 30‧‧‧Filter circuit
31‧‧‧帶通濾波器 31‧‧‧Bandpass filter
32‧‧‧高通濾波器 32‧‧‧High-pass filter
33‧‧‧低通濾波器 33‧‧‧Low-pass filter
40‧‧‧快速轉換電路 40‧‧‧ fast conversion circuit
50‧‧‧電腦系統 50‧‧‧ computer system
51‧‧‧類比數位轉換介面 51‧‧‧ analog digital conversion interface
60‧‧‧通訊電路 60‧‧‧Communication circuit
Claims (10)
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| CN202044262U (en) * | 2011-03-16 | 2011-11-23 | 齐志刚 | Electrocardiographic monitoring system |
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