201121501 六、發明說明： 【發明所屬之技術領域】 本發明係相關於—種運動間心率之檢測法，特指一種 可於使用者於運動中即時檢測心率之電子技術手段。 【先前技術】 監控個人的心率變化多半應用在運動或者醫學上，其 主要係透過m貞測裝置來取得心跳速率t訊而現有 技術中之〜率偵測手段較為常見的係利用心電訊號（) 量測裝置直接測出心率。 然而，該類型之心率偵測手段雖然可以精確且直接地 里測出心率，若要將此技術運用在運動期間即時之心率檢 測上時，實際上為相當不便利的，因為該類型之裝置往往 配戴不便，故運動t利用如此之裝置恐將會造成使用者之 不適，且若搭配以高效能微處理器或數位訊號處理器來實 施，其除了功率耗費高之外，設備之成本費用亦高，若是 為了作為輔助運動用之心率量測而言，在生產成本的考量 上將是十分不划算。 而現有技術中亦有利用將心跳所產生的壓力差轉換成 電壓差時域波形圖，並配合以各式演算法來檢測心率然 而其精準度多半因為運動時人體對量測電子儀器所產生的 振動而造成許多干擾雜訊，並且於電壓差時域波形圖中產 生許多不規則之波形，若未能找到一有效消除雜訊波形之 201121501 技術手段，則所_仏 J所檢測出的心率將會嚴重的失真，此亦為現 有技術中輔助谨# 運動用之心率檢測技術所被詬病之處，而本 發明之發明人士 幕於此點，積極地投入開發研究，終成—可 有效率地過濟雜％ • 愿雜汛之心率量測手段，可期為本技術領域帶 來貢獻。 【發明内容】 為解決上述之現有技術不足之處，本發明目的在提供 •一創新之運動間心率之檢測法，以期改良現有技術中之難 點。 本發明主要目的係在提供一種運動間心率之檢測法 包括： , u率讯號採樣並圖表化，其為利用一電子心 跳感測裝置直接於人體局部之血管做測量，並將該處之脈 動於次算法開發環境軟體t以時域演算法波型特性轉化 _ 為時間-電壓波型圖表； 步驟一、心率訊號特徵化，其包括決定出第η個心率 訊號區間及計算出在第η個區間中的訊號振幅Amp⑷;其 中決疋第η個心率訊號區間為將連續複數個截點之取樣值 4加而得Α且進—步將接下來的複數個截點之取樣值 相加，進而可得到β，同時設-遲滯係數TH，其可設定為 介於〇至50之間，並帶入判別式，若Α + ΤΗ<Β則輸出為 ，並於波型圖上輸出—升緣，若Α>Β + ΤΗ則輸出為“财， 201121501 並於波型圖上輸出一降緣，並得到特徵化之連續圖型，而 第η個心率訊號區間即為相鄰之兩個降緣之間，並提取各 降緣作成一降緣特徵圖型；而計算出在第η個區間中的訊 號振幅AmP(n)為於第η個區間中之降緣所對應之波型處， 計算其波峰到波谷間之長度作為訊號振幅Amp(n); 步驟二、濾除振幅較小的訊號，其首先為代入運算式 以取一參考振幅Ramp’參考振幅定義為第η區間處連 籲續二個訊號振幅Amp(n)之最大值，運算式為201121501 VI. Description of the Invention: [Technical Field] The present invention relates to a method for detecting heart rate between sports, and particularly relates to an electronic technical means for instantly detecting a heart rate in a user during exercise. [Prior Art] Most of the heart rate changes of monitoring individuals are applied to sports or medicine. The main reason is to obtain the heart rate t signal through the m measurement device. In the prior art, the rate detection method is more common to use the ECG signal ( The measuring device directly measures the heart rate. However, this type of heart rate detection method can accurately and directly measure the heart rate. If this technique is applied to the heart rate detection during the exercise, it is actually quite inconvenient because the device of this type is often It is inconvenient to wear, so the use of such a device may cause discomfort to the user, and if it is implemented with a high-performance microprocessor or digital signal processor, in addition to high power consumption, the cost of the device is also High, if it is used for the measurement of heart rate as an auxiliary exercise, it will be very uneconomical in terms of production cost. In the prior art, the pressure difference generated by the heartbeat is also converted into a voltage difference time domain waveform diagram, and the heart rate is detected by using various algorithms. However, the accuracy is mostly due to the human body's measurement of the electronic instrument during exercise. Vibration causes many interference noises, and many irregular waveforms are generated in the voltage difference time domain waveform diagram. If a 201121501 technique that effectively eliminates the noise waveform is not found, the heart rate detected by _仏J will be It will be a serious distortion, which is also the case of the heart rate detection technology used in the prior art. The inventor of the present invention actively invests in research and development, and can effectively Excessive % • The willingness to measure the heart rate can contribute to the technical field. SUMMARY OF THE INVENTION In order to solve the above-mentioned deficiencies of the prior art, the object of the present invention is to provide an innovative method for detecting heart rate during exercise, with a view to improving the difficulties in the prior art. The main object of the present invention is to provide a method for detecting heart rate during exercise including: u rate signal sampling and graphing, which is to measure directly from a blood vessel of a human body using an electronic heartbeat sensing device, and pulsate the signal The sub-algorithm development environment software t transforms the waveform characteristics of the time domain algorithm into a time-voltage waveform chart; Step 1: Characterization of the heart rate signal, which includes determining the n-th heart rate signal interval and calculating the n-th The signal amplitude Amp(4) in the interval; wherein the nth heart rate signal interval is obtained by adding the sample value 4 of the continuous plurality of intercept points, and the step is to add the sample values of the next plurality of intercept points, and further β can be obtained, and the hysteresis coefficient TH can be set, which can be set between 〇 and 50, and is brought into the discriminant. If Α + ΤΗ < Β is output, and output on the waveform map - rising edge, If Α>Β + ΤΗ, the output is “Cai, 201121501 and output a falling edge on the waveform graph, and the continuation pattern is characterized, and the nth heart rate signal interval is the adjacent two falling edges. And extract each falling edge into one The edge characteristic pattern is calculated. The signal amplitude AmP(n) in the nth interval is calculated as the waveform corresponding to the falling edge in the nth interval, and the peak-to-valley length is calculated as the signal amplitude Amp. (n); Step 2: Filter out the signal with a small amplitude, which is first substituted into the calculation formula to take a reference amplitude Ramp' reference amplitude is defined as the maximum value of the two signal amplitudes Amp(n) at the nth interval , the expression is
Ramp=Max(AmP(n-2)，AmP(n-l)，Amp(n))’ 而後代入判別 式，若Amp(n)>= RampX6〇%，則保留該區間n，反之則放棄 該區間η’進而可於圖型上得一保留之區間n之特徵圖型， 然於此時即可利用兩相鄰區間之間距時間算出各區間之心 跳速率；Ramp=Max(AmP(n-2), AmP(nl), Amp(n))' and the progeny is entered into the discriminant. If Amp(n)>= RampX6〇%, the interval n is retained, otherwise the interval is discarded. η' can further obtain a characteristic pattern of the reserved interval n on the pattern, but at this time, the heartbeat rate of each interval can be calculated by using the distance between two adjacent intervals;
步驟四、修正雜訊，其首 隔長度計算出該區間之心率值 及第η個區間之時間間隔計算 心率值Pa ’其為以兩連續區間 跳次數； 先以第η個區間中之時間間 Ρη ’繼而利用第n-Ι個區間 出連續2次心跳之雙數平均 t取平均而得到之每分鐘心 再者定義一心率輸出值〇Pn ,其中 於n< = 5時心率輸出值〇pn等於p ; 201121501 而於η>5後且心率值Pn與雙數平均心率值匕其中之_ 與剛個心率輸出值OP"-1相減後所得的差異值在卜⑽❶/之 内時’定義該Pn或雙數平均心率值Pap有效值f; 但於n>5後且心率值Pn與雙數平均心率值匕兩者與前 一個心率輸出值OPh相減後所得的差異值皆在卜之内 時’則定義該pn或雙數平均心率值Pa中較為接％前一個心 率輸出值0Ρ„Μ者為一有效值F ;Step 4: Correct the noise, calculate the heart rate value of the interval and the time interval of the nth interval from the first interval length to calculate the heart rate value Pa ', which is the number of jumps in two consecutive intervals; first between the time intervals in the nth interval Ρη' then uses the n-th interval to extract the average of the consecutive two heartbeats, and obtains a heart rate output value 〇Pn, where the heart rate output value 〇pn is equal to n<= 5 p ; 201121501 and after the η > 5 and the heart rate value Pn and the double-numbered average heart rate value 匕 _ _ _ _ _ _ _ _ _ _ _ _ _ _ _ _ _ _ _ _ _ _ _ _ _ _ _ _ _ Or the double-numbered average heart rate value Pap effective value f; but after n>5 and the heart rate value Pn and the double-numbered average heart rate value 相 are subtracted from the previous heart rate output value OPh, the difference value obtained is in the case of ' Defining the pn or the double-numbered average heart rate value Pa is more than the previous one of the heart rate output values 0 Ρ Μ is a valid value F;
再者，於n>5後且心率值Pn與雙數平均心率值匕兩者 與前一個心率輸出值0IVl相減後所得的差異值皆不在 + -DD%之内時，則心率值匕與雙數平均心率值匕兩者皆視 為無效，則令該有效值F為前一個心率輸出值〇Pni ; 而後定義該心率輸出值01>„則為前述所得之有效值F 與前五個心率輸出值0Pn_6至〇Pn，之總平均； 步驟五、顯示心率值，其為將前述所得之心率輸出值 opn進一步作一後續修補處理’而後以一固定頻率輸出至顯 示器上’其中定義一顯示心率值Dpn，透過運算式 DPn=(DPn-1 + 0Pn)/2而後可將輸出之數值波動幅度減緩，並 以-固定時間為一次間隔取樣一次且輪出該顯示心率值 DPn。 時心率變化作相當精 運動間震動訊號並予 而透過本發明將可對於運動間即 準之量測，且可確實的辨析非心跳之 201121501 以滤除，以接供一 α t & '、近乎實際運動間心跳之輸出效果，如此 來可準確的達到提醒運動中之使用者其自身運動激烈程 度之功效’再者’利用本發明以時域波形特性分析方式為 刀：雜Λ之運算手段’將可以透過相對簡單且廉價之微處 理裔來實現’對於實施上之推廣而言具有相當高的優勢。 【實施方式】Furthermore, after n>5 and both the heart rate value Pn and the double-numbered average heart rate value 相 are subtracted from the previous heart rate output value 0IV1, the difference values are not within +-DD%, then the heart rate value 匕 and the double number The average heart rate value 视为 is regarded as invalid, so that the effective value F is the previous heart rate output value 〇Pni; then the heart rate output value 01> is defined as the aforementioned RMS value F and the first five heart rate output values. 0Pn_6 to 〇Pn, the total average; Step 5, displaying the heart rate value, which is to further perform the aforementioned heart rate output value opn as a subsequent repair process 'and then output to the display at a fixed frequency' where a display heart rate value Dpn is defined Through the operation formula DPn=(DPn-1 + 0Pn)/2, the fluctuation range of the output value can be slowed down, and the fixed heart rate is sampled once at a time interval and the display heart rate value DPn is rotated. The heart rate change is quite fine. The motion signal between the motions and the invention can be measured for the motion room, and the non-heartbeat 201121501 can be discriminated to be filtered to provide an α t & ', almost actual inter-sports heartbeat Output The effect can be accurately achieved to remind the user in the exercise of the intensity of his own exercise. 'There is a use of the present invention to analyze the time domain waveform characteristics as a knife: the operation method of the chowder' will be relatively simple and The cheap micro-processing to achieve 'has a considerable advantage for the implementation of the promotion. [Embodiment]
為利貝審查員瞭解本發明之發明特徵、内容與優點及 ，、所flb達成之功效，茲將本發明配合附圖，並以實施例之 表達形式詳細說明如下，而其中所使用之圖式，其主旨僅 為示意及輔助說明書之用，未必為本發明實施後之真實比 例與精準配置，故不應就所附之圖式的比例與配置關係侷 限本發明於實際實施上的專利範圍，合先敘明。 請參配合參看第一圖所示，本發明運動間心率之檢測 法於一較佳之實施例中可包括下述步驟： 步驟一、心率訊號採樣並圖表化 步驟二、心率訊號特徵化 步驟三、濾除振幅較小的訊號 步驟四、修正雜訊 步驟五、顯示心率值 前述之步驟一、心率訊號採樣並圖表化為利用一電子 心跳感測裝置（其可為利用壓電轉換式或者光學傳感式之 心跳感測裝置）直接於人體局部之灰管做測量，並將該處之 201121501 脈動於一演算法開發環境軟體中以時域演算法波型特性轉 化為時間-電壓波型圖表，為使本發明該部分之技術内容較 易被理解’故將一實際操作之時間-電壓之實施例波型圖表 . 附上如第二圖所示，其中之示例為利用200HZ之頻率取波 型截點而形成的波型圖，然此部份之截取波型圖技術内容 實為本發明所屬之技術領域中具有通常知識者所應能理解 之通常知識，且並非為本發明之技術特徵所在，故不於說 •明書對其實施動作之枝微末節多加贅述。 凊配合參看第三圖所示，前述之步驟二、心率訊號特 徵化可進-步包括決定出第n個心率訊號區間及計算出在For the benefit of the invention, the features, the contents and the advantages of the invention, and the effects achieved by the flb, the present invention will be described in conjunction with the drawings and will be described in detail by way of examples, and the drawings used therein. The subject matter is only for the purpose of illustration and supplementary description. It is not necessarily the true proportion and precise configuration after the implementation of the present invention. Therefore, the proportion of the attached drawings and the configuration relationship should not limit the scope of patent application of the present invention in actual implementation. First described. Referring to the first figure, the method for detecting the heart rate of the exercise in the present invention may include the following steps in a preferred embodiment: Step 1. Heart rate signal sampling and graphing step 2. Heart rate signal characterization step 3. Filtering out the signal with small amplitude Step 4, correcting the noise step 5. Displaying the heart rate value Step 1 of the foregoing, heart rate signal sampling and graphing to utilize an electronic heartbeat sensing device (which may utilize piezoelectric conversion or optical transmission The sensory heartbeat sensing device directly measures the gray tube of the human body, and pulsates the 201121501 in the algorithm development environment software to convert the time domain algorithm waveform characteristics into a time-voltage waveform chart. In order to make the technical content of this part of the invention easier to understand, an embodiment of the time-voltage embodiment of the waveform is shown. Attached as shown in the second figure, an example of which is to use a frequency of 200 Hz to take the waveform. The waveform pattern formed by the interception point. However, the content of the intercepted waveform pattern in this part is a common knowledge that should be understood by those having ordinary knowledge in the technical field to which the present invention pertains. And are not technology-oriented features of the invention lies, it is not to say • instruction manual for its branches are window dressing of the implementation of the action narrated herein. Referring to the third figure, the second step, the heart rate signal feature can further include determining the nth heart rate signal interval and calculating the
四圖所示）；而計算出在第η 即為相鄰之兩個降緣（20)之間，並 降緣特徵圖型（30)(請配合參看第 '第11個區間中的訊號振幅Amp(n) 201121501 為於第η個區間中之降緣（20)所對應之波型處，計算其波 峰到波谷間之長度作為訊號振幅Amp(n)(40)，而於此步驟 中尚可見到許多大小相異甚大之訊號振幅Amp(n)(40)，這 表示仍存在有許多非心跳所造成之震動雜訊。 請配合參看第五圖所示，前述之步驟三、濾除振幅較 小的訊號首先為代入運算式取一參考振幅Ramp，其定義為 第η區間處連續三個訊號振幅Amp(n)之最大值，運算式為 9 Ramp=Max(Amp(n-2)，Amp(n-1 )，Amp(n))，而後代入判別 式，若Amp(n)>= RamPx6 0% ’則保留該區間η，反之則放棄 該區間η，進而可於圖型上得一保留區間η之特徵圖型 (50)，然於此時即可利用兩相鄰區間（亦即連續之兩次心跳） 之間距時間算出各區間之心跳速率，然自圖中可知其中各 兩相鄰區間之時間間距仍參差不齊，仍未能得到精確之心 率數值，故必須藉由進一步之演算步驟進行修正。 β月進一步配合參看第六圖所示，前述之步驟四、修正 雜訊中，首先先以第η個區間中之時間間隔長度計算出該 區間之〜率值Ρη(6〇)，即為該區間所對應每分鐘之心跳次 數’繼而利用第η] 4固區間及第η個區間之時間間隔計算 出連續2次心跳之雙數平均心率值pa(6l)，其為以兩連續 區間中取平均而得到之每分鐘心跳次數； 再者定義一心率輸出值OPn，其中 201121501 於n< = 5時心率輸出值〇Pn等於pn ; 而於n>5後且心率傕p广c^ 、 值pn(60)與雙數平均心率值Pa(61) 其中之-與前-個4輸出值u目減後所得以異值在 卜順⑽值於一較佳實施例為3〇)之内時，則定義該Pn(60) 或雙數平均心率值Pa(6l)為一有效值f;但是於Μ後且 心率值Pn(60)與雙數平均心率值h(⑴兩者與前_個心率 輸出值I相減後所得的差異值皆在卜順DD值於一較 佳實施例為30)之内時，則定義該Pn⑽)或雙數平均心率 值Pa(6l)中較為接近前_個心率輸出值爪，者為—有效值 F;再者，於n>5後且心率值&⑽）與雙數平均心率值以⑴ 兩者與前一個心率輸出氣相減後所得的差異值皆不在 + —_(DD值於一較佳實施例為3〇)之内時，則心率值以⑻ 與縣平均心率值Pa⑽兩者皆視為無效，則令該有效值 F為前—個心率輸出值〇pnM ; a參看第七圖所示，其中可見 值F所成之圖像。 而後定義該心率輸出值〇Pn則為前述所得之有效值F 與前五個心率輸出值（〇U D之總平均，請進-步 心率輸出值〇pn(62)及有效 前述之步驟五、顯示心率值為將前述所得之心率輸出 值0Pn(62)進一步作-後續修補處理’而後以-固定謂 出至顯示器上’請進一步配合參看第八圖所示，其中定義 10 201121501 —顯示心率值DPn(70),透過運算式DPn=(DPn ι+〇Ρη)/2而 後可將輸出之數值波動程度減緩，並以一固定時間（例如每 秒）為=人間隔取樣一次且輸出該顯示心率值j)pn(7〇) ^Figure 4); and calculate the η is the adjacent two falling edges (20), and the falling edge feature pattern (30) (please refer to the signal amplitude in the '11th interval Amp(n) 201121501 calculates the length between the peak and the trough as the signal amplitude Amp(n)(40) at the waveform corresponding to the falling edge (20) in the nth interval, and in this step It can be seen that many different amplitudes of the signal amplitude Amp(n)(40) indicate that there are still many vibration noises caused by non-heartbeats. Please refer to the fifth step, Step 3 above, to filter the amplitude. The smaller signal first takes a reference amplitude Ramp for the substitutional expression, which is defined as the maximum value of three consecutive signal amplitudes Amp(n) at the n-th interval, and the expression is 9 Ramp=Max(Amp(n-2), Amp(n-1), Amp(n)), and the descendant enters the discriminant. If Amp(n)>= RamPx6 0% ', the interval η is retained, otherwise the interval η is discarded, and thus the pattern can be obtained. A characteristic pattern (50) of the interval η is reserved, but at this time, the heartbeat of each interval can be calculated by using the distance between two adjacent intervals (that is, two consecutive heartbeats) However, it can be seen from the figure that the time interval of each of the two adjacent intervals is still uneven, and the accurate heart rate value is still not obtained, so it must be corrected by further calculation steps. In the above step 4, the modified noise first calculates the ratio value Ρη(6〇) of the interval by the length of the interval in the nth interval, that is, the number of heartbeats per minute corresponding to the interval. Then, using the time interval of the η] 4 solid interval and the nth interval, the double-numbered average heart rate value pa(6l) of two consecutive heartbeats is calculated, which is the number of beats per minute obtained by averaging in two consecutive intervals; The heart rate output value OPn is defined, wherein the heart rate output value 〇Pn is equal to pn when n <= 5; and the heart rate 傕p wide c^, the value pn(60) and the double average heart rate value Pa (after n>5) 61) where - and the previous - 4 output values u are reduced by an integer value when the value of the cis (10) value is within 3 〇) of a preferred embodiment, then the Pn (60) or the even average heart rate is defined. The value Pa(6l) is a valid value f; but after the heart rate and the heart rate value Pn(60) and the double number When the average heart rate value h ((1) is subtracted from the previous heart rate output value I, the difference value is equal to 30 in a preferred embodiment, then the Pn(10)) or the double number average is defined. The heart rate value Pa (6l) is closer to the first _ heart rate output value claws, which is - the effective value F; further, after n > 5 and the heart rate value & (10)) and the double-numbered average heart rate value are (1) both before When the difference value obtained by subtracting a heart rate output gas phase is not within +__ (the DD value is 3〇 in a preferred embodiment), the heart rate value is regarded as invalid by both (8) and the county average heart rate value Pa(10). , let the effective value F be the first heart rate output value 〇pnM; a see the seventh figure, where the image formed by the value F is visible. Then, the heart rate output value 〇Pn is defined as the aforementioned effective value F and the first five heart rate output values (the total average of 〇UD, please enter-step heart rate output value 〇pn(62) and the above-mentioned step 5, display The heart rate value is further obtained by the aforementioned heart rate output value 0Pn (62) - subsequent repair processing ' and then - fixed to the display - please further refer to the eighth figure, wherein 10 201121501 - display heart rate value DPn (70), by the arithmetic expression DPn=(DPn ι+〇Ρη)/2, the fluctuation of the numerical value of the output can be slowed down, and the sampling is performed once at a fixed time (for example, every second) and the heart rate value is output. j)pn(7〇) ^
而透過本發明所記載之技術手段可對於運動間即時心 率變化作相當精準之量測，且可確實的辨析非心跳之運動 間震動訊號並予以濾、除，以提供—近乎實際運動間心跳之 輸出效果’如此一來可準確的達到提醒運動中之使用者其 自身運動激烈程度之功效，再者，利用本發明以時域波形 特性分析方式為分離雜訊之運算手段，將可以透過相對簡 單且廉價之微處理器來實現，對於實施上之推廣而言具有 相當高的優勢，而為使本說明書之實際實施内容及實施效 -更為谷易理解’故附錄上本創作之實際實施截圖(請參看 附表一至七）及與傳統技術中ECG量測裝 晴參看附表八），以證本發明之高度產業利用價值/ 综觀上述，可見本發明在突破先前之技術下，確實已 達到所欲增進之功效，且也非孰来 …、，u忒項技藝者所易於思 及，再者，本發明申請前未曾公 開’其所具之進步性、實 用性’顯已符合發明專利之申請要 γ』τ。月要件，羑依法提出發明申 請’懇請責局核准本件發明專利中請案，以勵發明，至 感德便。 以上所述之實施例僅係 為說明本發明之技術思想及特 201121501 點’其目的在使熟習此項技藝之人士能夠瞭解本發明之内 容並據以實施，當不能以之限定本發明之專利範圍，即大 凡依本發明所揭示之精神所作之均等變化或修飾，仍應涵 蓋在本發明之專利範圍内。 【圖式簡單說明】 第一圖係為本發明之步驟流程圖。The technical means described in the present invention can make a fairly accurate measurement of the instantaneous heart rate change between the movements, and can accurately discriminate the non-heartbeat motion vibration signals and filter and remove them to provide - almost actual inter-sports heartbeat The output effect can thus accurately achieve the effect of alerting the user in the exercise to the intensity of his own exercise. Moreover, the use of the present invention to analyze the noise of the time domain waveform is a relatively simple operation method for separating noise. And the cheap microprocessor to achieve, has a very high advantage for the implementation of the promotion, and in order to make the actual implementation content and implementation effect of this specification - more easy to understand, so the actual implementation of this creation screenshot (Please refer to Schedules 1 to 7) and the ECG measurement and clearing in the traditional technology. See Appendix 8) to prove the high industrial utilization value of the present invention. Looking at the above, it can be seen that the present invention has indeed broken through the prior art. To achieve the desired effect, and it is not awkward..., it is easy for the artist to think about it. Moreover, the invention has not been disclosed before the application. The 'progressiveness and practicality' of the invention has been consistent with the application for invention patents. The monthly requirements, 提出 legally filed an invention application 恳 恳 Responsible for the approval of this invention patent application, in order to invent invention, to the sense of virtue. The embodiments described above are merely illustrative of the technical idea of the present invention and the purpose of the present invention is to enable those skilled in the art to understand and implement the contents of the present invention, and the patent of the present invention cannot be limited thereto. </ RTI> </ RTI> <RTIgt; </ RTI> <RTIgt; </ RTI> <RTIgt; </ RTI> <RTIgt; </ RTI> <RTIgt; </ RTI> <RTIgt; BRIEF DESCRIPTION OF THE DRAWINGS The first figure is a flow chart of the steps of the present invention.
第二圖係為本發明之時間_電壓波型步驟操作圖。 第三圖係為本發明之時間_電壓波型步驟操作圖。 圖。 圖。 圖。 圖。 圖。 體中實際操作 第四圖係為本發明之時間-電壓波型步驟操作 第五圖係為本發明之時間-電壓波型步驟操作 第六圖係為本發明之時間_電壓波型步驟操作 第七圖係為本發明之時間_電壓波型步驟操作 第八圖係為本發明之時間_電壓波型步驟操作 附表一至七為本發明於一演算法開發環境軟 之截圖。The second figure is an operation diagram of the time-voltage waveform step of the present invention. The third figure is the operation diagram of the time_voltage wave type step of the present invention. Figure. Figure. Figure. Figure. Figure. The fourth diagram of the actual operation in the body is the time-voltage waveform step operation of the present invention. The fifth diagram is the time-voltage waveform step operation of the present invention. The sixth diagram is the time-voltage waveform step operation of the present invention. The seventh diagram is the time of the invention. The eighth diagram of the operation of the voltage waveform is the time _ voltage waveform step operation of the present invention. The first to seventh steps are screenshots of the invention in an algorithm development environment.
附表八為本發明之操作結果與同 之對照比較圖型。 —情況下利用ECG做對照 【主要元件符號說明】 升緣（1 0 ) 降緣（20) 降緣特徵圖型（3〇) 3凡號振幅Amp(n)(40) 保留區間n之特徵圖型（5〇) 12Table 8 is a comparison of the operation results of the present invention with the same control. - Use ECG as a comparison [Main component symbol description] Ascending edge (1 0 ) Falling edge (20) Falling edge feature pattern (3〇) 3Front amplitude Amp(n)(40) Retention interval n characteristic map Type (5〇) 12
[SI 201121501 心率值Pn(60) 雙數平均心率值Pa(61) 心率輸出值0Pn(62) 顯示心率值DPn(70)[SI 201121501 Heart rate value Pn(60) Double average heart rate value Pa(61) Heart rate output value 0Pn(62) Display heart rate value DPn(70)
• 有效值F• Valid value F