經濟部中央標隼局員工消費合作社印裝 4 }S〇8 ι ·. A7 _ B7五、發明説明（1 ) 【發明之背景】【發明範疇】 本發明係有關於非侵入式血氧濃度計，尤其係有關於一 使用光學調變技術，擷取人體血液中帶氧血紅素及去氧血 紅素的濃度訊號時，可自動調整光源強度以及消除人為因 素產生之基線飄移以及劇烈變動混亂波形的血氧濃度計及 其偵測方法，以及一種波形訊號之波峰波谷偵測方法。 【相關技術說明】 一般醫院之急診醫療單位中’能夠正確地評估病患動脈-中氧合（oxygenation)程度，對於了解有缺氧或呼吸功能障礙 的病人之狀況是非常重要。血氧濃度計是用來量測人體動 脈血液中血紅素帶氧之濃度含量。1970年代在急診加護單 位中，開始以抽取病患的動脈血液來進行動脈血液氣體分 析，俾得到血液中的氧分壓及二氧化碳分壓來評估病患的 氧氣傳輸及供給狀況。由於抽取動脈血液是侵入式的量測 方式，在需要連續監測病人的狀況下，重複丨也柚血不僅造 成病人的痛苦，且增加了檢查之時間及成本°非侵入式血· 氧濃度計不同於抽血採樣分析的量測方式’而是利用光脈 衝式調變技術，藉由雙波長光源，照射人體血管密集的組 織一如耳垂或手指等處，由於帶氧血紅素及去氡血紅素在 光吸收頻譜上的差異，造成兩個穿透光強度不同之波長’ 根據血氧濃度的計算理論可求得血氧濃度值。根據定義’ 血氧濃度的數學公式如下： -4 .. 本紙張尺度適用中國國家標準（CNS > A4规格（2I0X297公釐） (請先閎讀背面之注意事項> 冩本頁} -裝' γ·1 4 1S〇8 if A7 B7 五、發明説明（2 )Printed by the Consumer Standards Cooperative of the Central Bureau of Standards of the Ministry of Economic Affairs 4} S〇8 ι ·. A7 _ B7 V. Description of the invention (1) [Background of the invention] [Scope of the invention] The present invention relates to a non-invasive oximeter In particular, it is related to the use of optical modulation technology to capture the concentration of oxygenated heme and deoxyheme in human blood, which can automatically adjust the intensity of the light source and eliminate the baseline drift caused by human factors and drastically changing chaotic waveforms. Oximeter and its detection method, and a method for detecting peaks and troughs of waveform signals. [Relevant technical description] In an emergency medical unit of a general hospital, it is very important to be able to correctly evaluate the degree of oxygenation in the arteries of the patient, which is very important for understanding the condition of patients with hypoxia or respiratory dysfunction. The oximeter is used to measure the concentration of oxygen in the hemoglobin in the arterial blood. In the 1970s, in emergency care units, arterial blood gas analysis was performed by extracting the patient's arterial blood, and the oxygen partial pressure and carbon dioxide partial pressure in the blood were obtained to evaluate the patient's oxygen transmission and supply status. Since the extraction of arterial blood is an invasive measurement method, repeated monitoring of the patient's condition not only causes pain to the patient, but also increases the time and cost of the examination. Non-invasive blood and oxygen concentration meters are different The measurement method for blood sampling analysis is to use light pulse modulation technology to illuminate the dense tissue of human blood vessels such as earlobe or fingers with dual-wavelength light source. The difference in the light absorption spectrum results in two wavelengths with different transmitted light intensities. According to the calculation theory of blood oxygen concentration, the blood oxygen concentration value can be obtained. According to the definition, the mathematical formula of blood oxygen concentration is as follows: -4 .. This paper size applies the Chinese national standard (CNS > A4 size (2I0X297mm)) (Please read the precautions on the back > 冩 This page}-Packing 'γ · 1 4 1S〇8 if A7 B7 V. Description of the invention (2)
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[HbOi] xlOO% 經濟部中央標準局員工消費合作社印聚 其中，[Hb02]表帶氧血紅素濃度，[Hb]表去氧血紅素濃 度。 血氧濃度計的發展最早可回溯至1940年代，Millikan發明 了一台儀器可從额頭量得動脈血氧.濃度。1960年代，發光 二極體和光二極體被用來當作反射式血氧濃度計的皮膚探_ 頭。到了 1980年代，Yoshiya等人結合了傳統的光學血氧計... 和體積描記術(plethymography)提供非侵入式光學血氧濃度理 論模型，且成功的運用手指探頭設計穿透式的光脈衝血氧 濃度計。1993年DeKock針對脈衝式血氧濃度計提出更為完 整的理論與實驗模型，將修正的全血的模型代入Beer-Lambert Law中。本發明之研究背景主要即根據Yoshiya和 DeKock的研究理論為基礎而發展之血氧濃度計。 光學原+理應用在人體及生理訊號的量測可達到非侵入式 量測的目的，由於非侵入式量測不僅可以降低受試者量測 時的痛苦，而且利用光學量測的方式，可以避免直接以電 訊號接觸人體，提高量測的安全性。此外，光學量測可以 避免量測訊號受到人體之體電位及外界電訊號的干擾，提 高量測的準確性。但是，因為血氧濃度計會因手指位置的 不同，會有不同訊號，若量測過程中移動手指或身體，將 造成血氧濃度信號飄移，假如晃動程度過大，甚至會造成 劇烈變動的混亂波形（motion artifact)。由於上述現象會影響 本紙張尺度適用中國國家橾準（CNS ) A4規格（210X297公釐） 奸衣------1T------^ 「诗先閱t背面之注意事項f /寫本頁) 經濟部中央橾準局員工消費合作杜印裝 4 fS〇e fj 4 I 808 i A7 ________ B7 五、發明説明（3) 到對金氧濃度波形作逐點追縱的結果，而與是否能正確找 尋到波形的波峰值及波谷值有關，因此需對這類情況予以 處理。根據新的偵'測方法，將可克服基線飄移以及混亂波 形之影響，⑥能夠㈣有效地計算* *氧》農度值與心跳速 率值。 此外，在量測人體血管密集的组織時，若能讓光源亮度 隨其膚色深淺及組織厚薄之不同，自動調整其強弱程度， 將能夠擷取到任何受測者的血氧濃度訊號波形。 【發明之概述】 .. 本發明之目的在於提供一可依據膚色深淺及組織厚薄之 不同，自動調整光源強度，來擷取人體之血氧濃度訊號的 非侵入式血氧濃度計與偵測方法。 本發明之另一目的在於提供一可消除血氧濃度訊號因人 為因素產生之基線飄移以及劇烈變動混亂波形的非侵入式 血氧濃度計與/[貞測方法。 本發明之又另一目的在於提供一可以防止因重搏脈波而 引起誤判的血氧濃度計與偵測方法。 .、 本發明之再另一目的在於提供一可用於任何有關訊號的 波峰波谷侦測之方法。 為達成上述目的’本發明是藉由非侵入式血氧濃度計， 量測人體血液中血紅素帶氧之濃度含量所得的訊號資料， 再加以數位信號處理’快速計算出正確的心跳速率以及血 氧濃度值。此裝置包含偵測探頭、光源驅動電路、電流轉 換電壓、可程式增益放大器、同步解調、低通濾波器 —6 - 本纸張尺度適用中國國家標準（CNS ) Λ4規格（210X297公釐） 餐------1T------線 (#先閱t背面之注意事項其:¾本Va〇 經濟部中央樣隼局貝工消費合作杜印裝 ;4ίδ〇βι Α7 ____Β7 五、發明説明（4 ) (LPF)、類比至數位訊號轉換（A/D)以及脈衝寬度調變（pwM) 等=脈衝寬度調變（PWM)提供可調電壓至光源驅動電路控 制偵測探頭之光源強度’根據膚色深淺及組織厚薄之不 同’光源強度亦隨之不同。至於電流轉換電壓電路係將電 流訊號轉換成電壓訊號，以便於信號處理。同步解調電路 係將説號冗整解调出來’去除外界雜訊干擾。而低通遽波 器（LPF)是滤除不屬於血氧濃度訊號-的高頻雜訊。最後，類 比至數位訊號轉換（A/D)電路’是將血氧濃度訊號之類比訊 號換成數位訊號’傳送至微處理器作數位信號處理。 欲求得凱號之心跳速率及血氧濃度值，須找尋波形之波 峰與波谷值，以往是利用單一準位或閥值（threshold)當成波 峰與波谷的判斷標準。若量測過程中移動手指或身體，將 造成血氧濃度信號飄移，對血氧濃度波形作逐點追縱時， 導致閥值準位出現錯誤甚至無法偵測；為了解決人為因素 產生雜訊（motion artifact)之影響，本發明提出新的訊號追縱 方法，採用所謂交替動態雙閥（alternate PV dynamic threshold)， 不同於只利用單一動態閥值的訊號準位；所謂交替動態雙· 閥是指用兩種訊號準位當成閥值，追蹤波形之波峰與波谷 時不再只用單一的閥值，改為有兩種閥值來處理波形；也 就是說，其中一閥值只追蹤波形之波峰準位，而另一閥值 專門追蹤波形之波谷準位，並將追蹤波形之波峰準位的閥 值稱為波蜂·閥值（peak thresholid)，而追縱波形之波谷準位的閥 值稱為波谷閥值（valley threshold)。欲解決人為動作所造成的 信號飄移影響，須修正波峰及波谷之閥值準位，以往做法 本紙張尺度逋用中國國家標準（CNS )八4规格（210X297公釐） — . 装------II------^ {請先閡讀背面之注意事項V '〔寫本頁〕 經濟部中央樣準局員工消費合作杜印衷 ，〇8| ' 41808 1a7 —___________B7____ 五、發明説明（5 ) 是隨時間變更閥值準位去追蹤波形，而本案之做法是只在 特定位置改變準位值，也就是在找尋到波形的波峰之時， 改變波谷之閥值準位，同樣地，在找尋到波形的波谷之 時’改變波峰之閥值準位，因為是互相修正彼此之閥值準 位的緣故，故稱為交替動態雙閥（alternate PV dynamic threshold);利用交替動態雙閥追蹤波形，可正確無誤地找 尋到已嚴重飄移的血氧濃度波形之波峰與波谷值°另一方 面’減少變更動態閥值準位之次數，可減少微處理器運算 的動作，大幅提升追蹤波形處理的速度。 ·· 【圖式之簡單說明】 圖1表示一根據本發明而成之非侵入式金氧濃度計之構 成方塊圖。 圖2表示一自動調整紅光及紅外光之光源亮度強弱的方 法流程圖。 圖3為一表示交替動態雙閥之概念圖示。 圖4為一表示波峰狀態及波谷狀態的概念圖示。 圖5為·一表示交替動態雙閥之變動流程圖。 圖6為一用以表示供計算血氧濃度以及心跳速率之決定 時機的推演方法流程圖。 圖7為一表示供測量血氧濃度之波形之動態波峰閥值訊 號修正情形之圖示。 圖8為一表示供測量血氧濃度之波形的波峰上緣訊號偵 測情形之圖示。 圖9為一表示供測量血氧濃度之波形的動態波谷閣值訊 —8 — 本紙張尺度適用中國國家標率（CNS ) Α4規格（2丨0Χ297公釐） I^1T線 Γ請先閱诊背面之注意事項Μ .寫本頁) 經濟部中央標準局員工消費合作社印製 180 類比至數位訊號轉換（A/D)單元 190 微處理器（CPU) 【發明之詳細說明】 * 本發明可自動調整光源強度以及消除訊號基線飄移的菸 響，其所使用之非侵入式血氧濃度量測裝置可由圖1所示 装置完成。本發明之裝置所利用之硬體單元均是一般性元 件，包含偵測探頭100、光源驅動電路110、電流轉換電歷r 單元120、直流可程式增益放大器no '同步解調單元140 ' 低通濾波器（LPF) 150、交流可程式增益放大器160、脈衝寬 度調變（PWM)單元170以及類比至數位訊號轉換（A/D)單元 180。而從光源驅動電路n〇開始、經由電流轉換電壓單元 41808 4ίδ〇8ί Α7 _Β7 五、發明説明（6) 號修正情形之圖示。 圖10為一表示供測量血氧濃度之波形的波谷下緣訊號偵 測情形之圖示。 圖1丨為一表示供測量血氧濃度之波形的動態波峰閥值及 動態波谷閥值訊號連續修正情形之圖示。 圖12為一表示供測量血氧濃度之波形的波峰上緣及波谷 下緣訊號憤測情形之圖示。 【符號對照說明】 100 偵測探頭 110 光源驅動電路 120 電流轉換電塵單元 130 直流可程式增益放大器 140 同步解調單元 150 低通濾波器 160 交流可程式增益故大器 170 脈衝寬度調變（PWM)單元 本纸張尺度適用中國國家標準（CMS ) A4規格（210X297公釐） ---------x±衣------II------0 (請先閱讀背面之注意事項--寫本頁) 經濟部中央標準局貝工消費合作社印裝 4 1 P * Λ ^ Β ^ ^ ^ Α7 Β7 五、發明説明（7 ) 120、直流可程式增益放大器13〇、同步解調單元〖40、低通 濾波器（LPF) 150、交流可程式增益故大器、以及類比至數 位訊號轉換（A/D)單元180等形成一回授裝置，再由戚衝寬 度調變（PWM)單元170回到光源驅動電路11〇，這一連串的 單元*形成一個具有封閉迴路的回授控制（feedback control)之 系統架構= 當用手指形偵測探頭100量測血氧濃度時，光源驅動電路 110會依據脈衝寬度調變（PWM)單元丨7〇的大小，提供電壓 至偵測探頭去控制光源亮度的強弱，經由光源穿透手指 後，由於人體血液中帶氧血紅素及去氧血紅素在光吸收頻 譜上的差異’造成兩個波長穿透光強度不同；而電流轉換 電壓單元120會根據探頭的電流大小轉換成電壓準位的血 氧濃度訊號，便於做訊號處理之工作；接下來，直流可程 式增益放大器130將血氧濃度訊號放大至適當之電壓準位 大小，而同步解調單元140會去除掉可能造成影響的雜 訊，將血氧濃度訊號完整重現出來，低通濾波器（LPF) 150 只過濾屬於血氧濃度頻帶之訊號，使血氧濃度波形更令 滑*交流可程式增益放大器丨60則是將血氧濃度波形放大 至適當之振幅大小，增加訊號處理之準確度；最後，類比 至數位訊號轉換單元（A/D) 180則是將類比式的血氧濃度訊 號轉換成數位式訊號，傳送至微處理器190作數位信號處 理工作，去計算也氧濃度與心跳速率值。 在量測人體血管密集的組織時，因性別或人種及年齡之 不同，其膚色的深淺及組織的厚薄亦隨之不同，假如使用 -10 - 本纸浪尺度適用中國國家標準（CNS ) Α4規格（210X297公董） 裳 訂 線 {請先聞發背面之注意事項κ 寫本頁} 經濟部中央標準局員工消費合作社印装 4 1808 f at ______B7 五、發明説明（8 ) 固定的光源亮度，對膚色較淺或組織較薄的部份，光源亮 度太強會造成穿透效應，變成偵測不到血氧濃度訊號波 形，無法正常量測，但對膚色較深或組織較厚的部份，光 源亮度若太弱，會偵測不到正常之血氧濃度訊號波形，亦 造成無法正常量測。因此，須讓光源亮度能夠隨其膚色深 淺及組織厚薄之不同’自動調整其強弱程度，能夠擷取到 任何受測者的血氧濃度訊號波形。 至於自動調整光源亮度的強弱，則是利用系統具有回授 控制（feedback control)架構之特性所達成的。光源驅動電路-110是依據脈衝寬度調變（PWM)單元170的大小，提供電壓 至倩測探頭100去控制紅光及紅外光之光源亮度，經由電 流轉換電壓單元120，轉變成電壓準位之訊號，而直流可 程式增益放大器130是根據控制值將訊號放大，最後，類 比至數位訊號轉換單元（A/D) 180將訊號轉換成數位訊號， 微處理器190比較其訊號直流成份之上下限後，修正脈衝 寬度調變（PWM)的大小以及直流增益之放大倍率，重複上 述全部過程，直到滿足判斷標準為止。 、 整個自動調整紅光及紅外光之光源亮度強弱的演算方法 可見圖2，紅光及紅外光之光源亮度分別是由兩個脈衝寬 度調變器PWM0及PWM1來控制，PWM0控制紅外光之光源 亮度，PWM1則是控制紅光之光源亮度；首先，根據紅外 光之光源所偵測出的血氧濃度訊號之直流成份’做上下限 比較後（步驟200 )去修正PWM0及直流增益之放大倍率，而 光源驅動電路110所接收來自PWM0的值愈小’則表示相對 -11 _ 本纸張尺度適用中國國家標準（CNS ) A4規格（2:0 X 297公釐） n^— ii^i HI· 1^1 ' (_請先閱请背面之注意事項-寫本頁) 丁 線 經济部令夹揉準局員工消費合作社印裝 卜 41808 1 A7 ______ B7_ 五、發明説明（9) 應的紅外光源亮度就愈強，所以說，假如紅外光之光源所 谓測出的直流成份太小（步驟220 )，可能就是光源的亮度 較弱，造成所偵測出的血氧濃度訊號太小或訊號不良之現 象；此時，須要減少PWM0送出的值，增強紅外光源亮 度。若PWM0送出之值已到最小，所偵測出的直流成份仍 是太小，這可能是膚色較深或組織較厚的情況，須增加直 流增益之放大倍率’使血氧濃度訊號増強；另一方面，假 如紅外光之光源所偵測出的直流成份太大（步驟21〇 )，可 能就是光源的亮度較強，造成所偵測出的血氧濃度訊號太 太或訊號飽和之現象，此時，須要增加PWM〇所送出的 值’減弱紅外光源亮度，若PWMO送出之值已到最大，所 偵測出的直流成份仍是太大，這可能是膚色較淺或组織較 薄的情況，須減少直流增益之放大倍率，使血氧濃度訊號 減弱；繼續調整PWM0和直流增益之放大倍率之步驟，直 到紅外光直流成份達到上下限之判斷標準為止。 同樣地，對於紅光之忠源而言，光源驅動電路UO所接收 之來自PWM1的值愈小，則表示相對應的紅光源亮度就愈· 強，跟紅外光光源調整之步騾不同點，是在於只調整 PWM1的大小改變紅光光源亮度，而直流增益之放大倍率 在紅外光光源調整之步驟中己決定好了，不必要重複調整 直流增益之放大倍率；同理，假如紅光之光源所偵測出的 直流成份太小（步驟250 )，就減少PWM1送出的值，增強紅 光光源亮度，若紅光之光源所偵測出的直流成份太大（步 騾240 )，須要增加PWM1送出的值’減弱紅光源亮度，同 -12 - 本紙張尺度適用中國國家標隼（CNS > Μ規格（2丨〇><297公釐） !^------、1T----------0 (請先閱讀背面之注意事項-:寫本頁) 41808 1 經濟部中央標準局貝工消費合作杜印製 A7 B7 五、發明説明（10) 樣繼續調整PWM1之步驟，直到紅光直流成份達到上下限 之判斷標準（步驟230 )為止。 當紅外光及紅光之直流成份皆符合標準時，表示當時 PWM0、PWM1值所提供的光源亮度和直流增益之放大倍率 疋瑕適合該受測者的設定值’能夠偵測出最佳的灰氧濃度 訊號波形。系統能夠自動因性別或人種及年齡之不同，對 於其膚色的深淺及組織的厚薄之不同，去調整光源亮度的 強弱’此功能對偵測血氧濃度訊號是必須具備而且非常重 要的。假設所偵測到的血氧濃度訊號非常正常，接下來的 數位信號處理工作，就可快速且正確地計算出血氧濃度與 心跳速率值；反之，因光源亮度和直流增益之放大倍率控 制不正確’所偵測到的金氧濃度變成訊號不良甚至於沒有 訊號出現’造成計算錯誤或無法正常工作。本案利用回授 控制系統（feedback control system)架構特性，配合推演方法自動 碉整光源亮度和直流增益之放大倍率控制，設定系統正確 的設定值。 ' 擷取到的血氧濃度訊號，經由類比至數位訊號轉換單元、 (A/D) 180將類比式的血氧濃度訊號轉換成數位式訊號，傳 送至微處理器作數位信號處理工作，計算血氧濃度與心跳 速率值=根據血氧濃度的計算理論，欲求得血氧濃度值， 須準確地找到波形之波峰及波谷值，但須克服血氧濃度訊 號因人為動作產生之基線飄移以及變成劇烈變動混亂波形 之影響，迅速地追縱波形，仍能正確找到波峰及波谷之位 置。本案提出新的訊號追蹤方法，採用所謂交I動態雙閥 胃13 — 本紙張尺度適用中國國家橾率（CNS ) Α4規格（210X297公釐） ΐ衣------.訂------^ (.請先閱请背面之注意事項-本頁) 經濟部中央棣準局貝工¾費合作社印製 4 1808 1_ b7 五、發明説明（ii) (alternate PV dynamic threshold! ’不同於只利用單一動態閥值的 訊號準位；交替動態雙閥’顧名思義是用兩種訊號準位當 成動態閥值，追縱波形之波♦與波谷時不再只用單一的閱 值’改為有兩種動態閥值來處理波形；也就是說，其中一 動態閥值只追蹤波形之波峰準位，而另一動態閥值則追蹤 波形之波谷準位，將追蹤波形之波峰準位的動態閥值稱為 動態波峰閥值（dynamic peak threshold) ’而追縱波形之波谷準位 的動怨閥值稱為動態波谷閥值（dynamic valley threshold彡。 交替動態雙閥之概念如圖3，利用動態波峰閥值p,和 動態波谷閥值（330)兩種訊號準位，追跪血氧濃度波形 (300) ’找出波形之波峰與波谷位置；當波形訊號大於動態 波峰閥值（340)時，才進行追蹤波形的波峰工作，若訊號大 於波峰上緣（320)，則將訊號重設成為波峰上緣，假如波♦ 上緣成為一水平線時’表示已找尋到波形的波辛。同理， 當波形訊號小於動態波谷閥值（330)時，才進行追縱波形的 波谷工作，若訊號小於波谷下緣（31〇)，則將訊號重設成為 波谷下緣，假如波谷下緣成為一水平線時，表示已找尋到、 波形的波谷。因此，只有當訊號大於動態波峰閥值（45〇)或 小於動態波谷閥值（470)時，才進行追縱波形的工作，其餘 時間則不做處理，大幅減低了波形追蹤的運算時間，增加 了系統反應速度。 藉由兩種動閥值來追縱血氧濃度波形’亦可避免血氧 濃度波形之重搏脈（350)問題。所謂重搏脈，如圖3，波形 除了所具有的脈波（360)之外，另外在波形中段又有—脈 本紙浪尺度適用中國國家標準（CNS ) A4規格（2:0X297公着） ! If I . H ^ Ηπ---n ---In - (.請先閲·讀背面之注意事項 f·寫本頁) 經濟郏中夫搮率扃員工消費合作社印装 Λίβοδί Α7 _______Β7五、發明説明（12 ) ^ 波，稱為重搏脈（350)。因重搏脈（35〇)也具有上升以及下降 波形，在追蹤波形時，會被誤判為波峰或波谷；假如使用 重搏脈之波峰或波谷來計算血氧濃度值，會產生錯誤結 果。但使用交替動態雙閥，只有當訊號大於波峰上緣（32〇) 或小於波谷下緣（310)時，才會進行追蹤波形之波峰及波谷 的動作’對於波形中段之重搏脈則不做處理，因此輕易地 避開重搏脈的問題。 至於如何偵測到正確的波峰及波谷位置，.根據波峰上緣 (320)及波谷下緣（310) ’只能夠決定波峰及波谷值的大小，-無法斷定波峰及波谷發生之時機；因此，須要隨時記錄波 形之狀態’此推演方法採用分別記錄波峰及波谷之偵測情 況’如圖4所示’波形曲線上方的邏輯信號準位（〇或〖）， 代表專門記錄波峰的偵測狀態，稱為波峰狀態（44〇)，而波 形曲線下方的邏輯信號準位’則代表專門記錄波谷的偵測 狀態’稱為波谷狀態（450)。進行追蹤波形的動作時，當訊 號太於波峰上緣（460)，就將波峰狀態（44〇)設定成邏輯準位 -0 ’否則設定成邏輯準位-1，如圖可知當波峰狀態由〇變、 成I時’就決定了波峰（400)發生之時機：同理可推，當訊 號小於波谷下緣（470)時，就將波谷狀態（450)設定成邏輯準 位-0 ’否則設定成邏輯準位-]，同樣地，當波谷狀態由〇 變成1時’就決:定了波谷（410)發生之時機。所以，採用波 峰狀態（440)及波谷狀態（450)，可以很正確地偵測出波峰及 波谷發生之時機，那麼心跳速率與血氧濃度的計算就準確 無誤了 13 -15 - .f請先閲讀背面之注意事項_-Tr寫本頁) 裝 -訂 本紙浪尺度適用中國國家標孳（CNS > Μ規格（21〇X297公釐） 4 18 0 8 1 A7 B7 經濟部中央標準局負工消費合作社印製 五、發明説明（13) 圖5顯示出一推演交替動態雙閥之方法，步驟判斷訊 號是否大於動恐波峰閥值或小於動態波谷閥值，若是，才 進行步騾520及530追縱波形的工作，若不是，則不做處 理’而步驟520是決定波峰狀態的邏輯準位值，步騾53〇則 疋決足波谷狀,g|的邏輯準位值；接下來，步驟54〇及55〇是 決定波峰及波谷發生之時機，步驟54〇是根據波峰狀態之 變化（由0變成1 )找到波形之波峰發生之時機，並將波峰旗 ^設定為1，且此表示偵測波峰之動作已完成，而步驟55〇 則疋根據波谷狀態之變化（由〇變成丨）找到波谷發生之時 機，並將波谷旗標設定為i，且此表示偵測波谷之動作己 完成。 但所偵測的波形可能會有訊號不良，或因人為動作所產 生之基線飄移以及變成劇烈變動混亂波形之情況；為了克 服因訊號不良、人為因素所可能造成計算錯誤的影響，計 算血氧濃度與心跳速率值的時機變成非常重要；在進行追 蹤波形的工作時，何時去計算血氧濃度以及何時去計算心 跳率，才不會因上述現象造成誤判而導致結果錯誤。根據、 圖I系統方塊圖可知，電路是利用低通濾波器（LPF) 15〇將高 瀕雜訊濾除，波形之波峰部份較不易有高頻雜訊的干優， 因此，在找到波形的波峰時去計算血氧濃度以及心跳率， 即可避免4算錯誤或重複計算的問題。另一方面，在找到 波形的波♦及波谷時，利用計數器去決定計算血氧濃度以 及心跳速率的時機，可克服訊號不良的情況。如圖4所 示，當找到波形的波峰（400)時，並沒有立即作處理，而是 16 本紙張尺度適财(eNS丨(21{)χ29^^ !,------^-----^-i 訂------^ ('請先閲讀背面之注意事項/槟寫本頁) 41808 1 經濟部中央梂隼局員工消費合作杜印製 A7 B7 —----—一______ 五，發明説明（Μ ) " 等計數器計數一段時間後’確定所找到的波峰仍然是最高 點（如圖4的（420))’才處理相對應的動作，而（4〇〇)和（420)之 間的問隔即是計數器所延遲的時間；同樣地，當找到波形 的波谷（410)時，亦是等計數器計數一段時間後，確定所找 到的波谷仍然是最低點（如圖4的（430))，則處理相對應的 動作，而（410)和（430)之間的間隔即是計數器所廷遲的時 間。利用上述方法可有效地克服訊號不良、混亂波形之情 況，正確地計算出血氧濃度與心跳速率值，並減少重複計 算的機會，提升訊號處理的速度及品質。 圖6是決定計算血氧濃度以及心跳率的時機之推演方 法’步騾600判斷波峰旗標及波學狀態是否為1，若是，表 示找到波形的波峰；步驟610及620是計數器延遲時間的步 驟’假如時間的間隔大於8，才進行步驟630，去計算血氧 濃度以及心跳速率的動作’以及修正動態波谷閥值。同 理’步驟640判斷波谷旗標及波谷狀態是否為1，若是，表 示找到波形的波谷；步騾650及660是計數器廷遲時間的步 鄉’假如時間的間隔大於8，則進行（步驟670 )修正動態波、 ♦閥值的動作。 設定動態波谷閥值是利用當時偵測的波峰值（亦即是波學 上緣）’和前一個所偵測的波谷值（亦即是波谷下緣），採 内插法一起作波谷準位值的修正，以方程式來表示即是 動態波谷閥值=IU*波谷下緣[n-l]+K2*波峰上緣[η] 且其中Κ1+Κ2=1 ’且Κ1>Κ2，亦即取偏靠波谷之值。 而設定動態波峰閥值則是利用當時偵測的波谷值（亦即是 -17 - -- -- i— -I --1 -- I— _ I ('讀先閱请背面之注意事項·-马本頁) *π 線 本紙張尺度適财關家料（CNS ) Μ規格（加公慶） 經濟部中央標率局貝工消費合作社印裝 4 1808 1 A7 —__________ B7 五、發明説明（U ；) '皮谷下.'彖）和如個所债測的波峰值（亦即是波峰上 緣）’採内插法一起作油峰進p β τ 、 F收Τ早位值的修正，以万程式來表 示即是 動態波峰閥值=Κ3*波峰上緣卜丨卜以*波谷下緣间 且其中Κ3 + Κ4 = I，且Κ3 > Κ4，亦即取偏靠波峰之值。 因為是用目前和前一個所偵測到的波峰或波谷值，以交 替方式互相修正動態波峰及波谷閥值，因此可以了解波形 變化的情況，能夠非常迅速並正確地修正準位值，對於人' 為動作所產生之基線飄移以及變成劇烈變動混亂波形之情--況，以交替動態波峰或波谷閥方式，可輕易克服因訊號不 良、人為動作所可能造成計算錯誤的影響。 進而’在找到波形訊號之波峰與波谷後，根據所求得波 辛與波谷之時機與大小’以及直流成分，依據推算理論， 即可推算出血氧濃度值與心跳速率。 圖7至圖1 2是根據本發明的推演方法所分析的結果，偵 測探頭100所量測的波形是人體手指頭的血氧濃度訊號α 圖7是顯示血氧濃度波形的動態波峰閥值訊號修正過程，、 如圖所示，動態波峰閥值會隨著波形之起伏而跟著調整修 正’維持正確的判斷準位，而圖8是顯示血氧濃度波形的 波峰上緣訊號偵測過程，雖然波形已明顯地晃動，推演方 法仍能正確地找出波形之波峰；圖9則是顯示血氧濃度波 形的動態波谷閥值訊號修正過程，動態波谷閥值亦會隨著 波形之起伏而跟著調整修正，維持正確的判斷準位，而圖 10是顯示血氧濃度波形的波谷下緣訊號偵測過程，波形雖 本紙張又度逋用中國國家標準（CMS ) Α4規格（2ΙΟΧ 2们公釐） (請先閱讀背面之注意事項r‘寫本頁) 裝- 訂 Α7 Β7 五、發明説明（16 ) 然已大幅地晃動’推演方法仍能正確地找出波形之波谷。 圖π是顯示推演方法修正企氧濃度波形的動態波峰閥值和 動態波谷閥值訊號過程，圖12是顯示推演方法偵測血氧濃 度訊號的波峰上緣及波谷下緣訊號過程。 本發明利用交替動態雙閥推演方法，可迅速並正確地找 到血氧濃度訊號的波峰及波谷訊號，而且可輕易克服因訊 號不良、人為動作所產生之基線飄移以及變成劇烈變動混 亂波形之情況《然而應用範圍並非只限於血氧濃度的訊號 處理’任何有關偵測訊號的波峰及波谷的動作，皆能採用— 本發明之推演方法。 ----------^------1Τ------^ (請先閱讀背面之注意事項兵ίίϊ.·7本f ) 經濟‘邓中央操隼局員工消費合作社印製 -19 - 本紙張尺度適用中國國家標準（CNS )A4規格（210X 297公釐）[HbOi] x100% Printed by the Consumer Cooperatives of the Central Standards Bureau of the Ministry of Economic Affairs, where [Hb02] indicates the concentration of oxygenated heme, and [Hb] indicates the concentration of deoxyheme. The development of the oximeter can be traced back to the 1940s. Millikan invented an instrument to measure the arterial oxygen concentration from the forehead. In the 1960s, light-emitting diodes and photodiodes were used as skin probes for reflective oximeters. By the 1980s, Yoshiya et al. Combined a traditional optical oximeter ... and plethysmography to provide a non-invasive theoretical model of optical blood oxygen concentration, and successfully used a finger probe to design a penetrating light pulse blood Oxygen concentration meter. In 1993, DeKock proposed a more complete theoretical and experimental model for the pulse oximeter, and substituted the modified whole blood model into Beer-Lambert Law. The research background of the present invention is mainly a oximeter developed based on the research theory of Yoshiya and DeKock. Optical principle + theory applied to the measurement of human and physiological signals can achieve the purpose of non-invasive measurement, because non-invasive measurement can not only reduce the pain of the subject when measuring, but also use the optical measurement method, which can Avoid directly contacting the human body with electric signals to improve the safety of measurement. In addition, optical measurement can prevent the measurement signal from being interfered by the human body potential and external electrical signals, and improve the accuracy of the measurement. However, because the oximeter will have different signals depending on the position of the finger, if the finger or body is moved during the measurement, the blood oxygen concentration signal will drift. If the degree of shaking is too large, it may even cause a chaotic waveform that changes drastically. (Motion artifact). Because the above phenomenon will affect the size of this paper, applicable to China National Standards (CNS) A4 (210X297 mm) rape .----- 1T ------ ^ "Notes on the back of the poem f / (Write this page) Consumption Cooperation of Employees of the Central Bureau of Standards, Ministry of Economic Affairs, Du Yinzhuang 4 fS〇e fj 4 I 808 i A7 ________ B7 V. Description of the Invention (3) The result of point-by-point tracking of the gold oxygen concentration waveform, and It is related to whether the peak and trough values of the waveform can be found correctly, so this kind of situation needs to be handled. According to the new detection method, the effects of baseline drift and chaotic waveforms can be overcome. ⑥ Can be effectively calculated * * Oxygen >> Agronomic value and heart rate value. In addition, when measuring the dense tissue of human blood vessels, if the brightness of the light source can be adjusted according to the skin tone and the thickness of the tissue, the intensity can be automatically adjusted to capture the intensity. The waveform of the blood oxygen concentration signal of any subject. [Summary of the invention]. The purpose of the present invention is to provide a system that can automatically adjust the intensity of the light source to capture the blood oxygen concentration signal of the human body according to the difference in skin tone and tissue thickness. Non-invasive Oxygen concentration meter and detection method. Another object of the present invention is to provide a non-invasive blood oxygen concentration meter and a method for measuring blood oxygen concentration signals which can eliminate the baseline drift caused by human factors and the sharp and chaotic waveforms. Yet another object of the present invention is to provide a oximeter and a detection method which can prevent misjudgment due to heavy pulse waves. Yet another object of the present invention is to provide a crest and trough which can be used for any relevant signal Method of detection. In order to achieve the above-mentioned object, the present invention uses a non-invasive oximeter to measure the signal data obtained by measuring the concentration of oxygen contained in human blood, and then digitally processes the signal to quickly calculate the correctness. Heart rate and blood oxygen concentration value. This device includes a detection probe, a light source drive circuit, a current conversion voltage, a programmable gain amplifier, synchronous demodulation, and a low-pass filter—6-This paper size is applicable to Chinese national standards (CNS ) Λ4 specification (210X297 mm) Meal ----- 1T ------ line (#Notes on the back of the first t Cooperated with Du printed equipment; 4ίδ〇βι Α7 ____ Β7 V. Description of the Invention (4) (LPF), Analog to Digital Signal Conversion (A / D), and Pulse Width Modulation (pwM), etc. = Provided by Pulse Width Modulation (PWM) Adjustable voltage to the light source drive circuit controls the intensity of the light source of the detection probe according to the difference in skin tone and thickness of the tissue. The intensity of the light source varies accordingly. As for the current conversion voltage circuit, the current signal is converted into a voltage signal for signal processing. The synchronous demodulation circuit is to demodulate the signal redundantly to 'remove external noise interference. The low-pass filter (LPF) filters out high-frequency noise that is not a blood oxygen concentration signal. Finally, the analogy to digital The signal conversion (A / D) circuit 'is to convert the analog signal of the blood oxygen concentration signal to a digital signal' and send it to the microprocessor for digital signal processing. In order to obtain the Kai heartbeat rate and blood oxygen concentration value, it is necessary to find the peak and trough of the waveform. In the past, a single level or threshold was used as the criterion for judging the peak and trough. If you move your finger or body during the measurement process, the blood oxygen concentration signal will drift, and the blood oxygen concentration waveform will be traced point by point, which will cause the threshold level to be incorrect or even impossible to detect. In order to solve the artificial factors, noise ( motion artifact), the present invention proposes a new signal tracking method, using the so-called alternate dynamic dynamic double valve (alternate PV dynamic threshold), different from the signal level using only a single dynamic threshold; the so-called alternating dynamic double valve Use two signal levels as thresholds. When tracking the peaks and troughs of a waveform, instead of using a single threshold, use two thresholds to process the waveform; that is, one of the thresholds only tracks the peaks of the waveform. Level, and another threshold is dedicated to tracking the trough level of the waveform, and the threshold that tracks the peak level of the waveform is called the peak thresholid, and the threshold that follows the trough level of the waveform It is called the valley threshold. In order to solve the signal drift caused by human motion, the threshold levels of the peaks and troughs must be corrected. In the past, this paper used the Chinese National Standard (CNS) 8-4 specification (210X297 mm) —. --II ------ ^ {Please read the precautions on the back V '[write this page] Du Yinzhong, employee cooperation of the Central Procurement Bureau of the Ministry of Economic Affairs, 〇8 |' 41808 1a7 —___________ B7____ V. Invention Explanation (5) is to change the threshold level over time to track the waveform, and the method in this case is to change the threshold value only at a specific position, that is, to change the threshold level of the trough when the peak of the waveform is found. Ground, when finding the trough of the waveform, 'change the threshold level of the crests, because it is to modify each other's threshold levels, it is called alternate PV dynamic threshold; using alternating dynamic dual The valve tracking waveform can accurately find the peaks and troughs of the blood oxygen concentration waveform that has drifted seriously. On the other hand, 'reducing the number of times to change the dynamic threshold level can reduce the operation of the microprocessor calculation and greatly improve Waveform processing speed tracing. [Brief Description of the Drawings] Fig. 1 shows a block diagram of a non-invasive gold oxygen concentration meter made according to the present invention. Figure 2 shows a flowchart of a method for automatically adjusting the brightness of a red light source and an infrared light source. FIG. 3 is a conceptual diagram showing an alternating dynamic double valve. FIG. 4 is a conceptual diagram showing a peak state and a valley state. Fig. 5 is a flow chart showing the change of the alternate dynamic double valve. Fig. 6 is a flowchart showing a derivation method for determining the timing for calculating blood oxygen concentration and heart rate. Fig. 7 is a diagram showing a dynamic peak threshold signal correction situation of a waveform for measuring blood oxygen concentration. Fig. 8 is a diagram showing the detection condition of the upper edge signal of the waveform for measuring the blood oxygen concentration. Fig. 9 is a dynamic wave trough value report showing the waveform for measuring blood oxygen concentration—8 — This paper scale is applicable to China National Standards (CNS) Α4 specification (2 丨 0 × 297 mm) I ^ 1T line Γ Please consult first Note on the back M. Write this page) Printed by the Consumer Standards Cooperative of the Central Bureau of Standards of the Ministry of Economics 180 Analog to Digital Signal Conversion (A / D) Unit 190 Microprocessor (CPU) [Detailed Description of the Invention] * The invention can be automated The non-invasive blood oxygen concentration measuring device used to adjust the intensity of the light source and eliminate the smoke drift of the signal baseline can be completed by the device shown in FIG. 1. The hardware units used by the device of the present invention are general components, including a detection probe 100, a light source driving circuit 110, a current conversion calendar r unit 120, a DC programmable gain amplifier no 'synchronous demodulation unit 140', and low pass A filter (LPF) 150, an AC programmable gain amplifier 160, a pulse width modulation (PWM) unit 170, and an analog-to-digital signal conversion (A / D) unit 180. Starting from the light source driving circuit no, via the current conversion voltage unit 41808 4ίδ〇8ί Α7 _Β7 V. Graphical illustration of the correction situation of invention description (6). Fig. 10 is a diagram showing a bottom edge signal detection situation of a waveform for measuring blood oxygen concentration. FIG. 1 is a diagram showing the continuous correction of the dynamic peak threshold value and the dynamic valley threshold signal of the waveform for measuring the blood oxygen concentration. Fig. 12 is a diagram showing the signal of the upper edge of the peak and the lower edge of the trough of the waveform for measuring the blood oxygen concentration. [Comparison of symbols] 100 Detection probe 110 Light source driving circuit 120 Current conversion dust unit 130 DC programmable gain amplifier 140 Synchronous demodulation unit 150 Low-pass filter 160 AC programmable gain amplifier 170 Pulse width modulation (PWM ) The paper size of this unit applies the Chinese National Standard (CMS) A4 specification (210X297 mm) --------- x ± 衣 ------ II ------ 0 (Please read first Note on the back-write this page) Printed by the Central Standards Bureau of the Ministry of Economic Affairs, Shellfish Consumer Cooperative, 4 1 P * Λ ^ Β ^ ^ ^ Α7 Β7 V. Description of the invention (7) 120, DC programmable gain amplifier 13〇, The synchronous demodulation unit [40, low-pass filter (LPF) 150, AC programmable gain amplifier, and analog-to-digital signal conversion (A / D) unit 180, etc. form a feedback device, which is then adjusted by Qi Chong width The PWM unit 170 returns to the light source driving circuit 110. This series of units * forms a system architecture with feedback control with a closed loop = when the blood oxygen concentration is measured with the finger-shaped detection probe 100 , The light source driving circuit 110 will adjust according to the pulse width The size of the (PWM) unit 70 provides voltage to the detection probe to control the brightness of the light source. After penetrating the finger through the light source, due to the difference in the light absorption spectrum of oxygenated heme and deoxyheme in human blood 'As a result, the intensity of the light transmitted through the two wavelengths is different; and the current conversion voltage unit 120 will convert the blood oxygen concentration signal of the voltage level according to the current of the probe, which is convenient for signal processing. Next, the DC programmable gain amplifier 130 The blood oxygen concentration signal is amplified to an appropriate voltage level, and the synchronous demodulation unit 140 will remove the noise that may affect the signal and reproduce the blood oxygen concentration signal completely. The low-pass filter (LPF) 150 filters The signal that belongs to the blood oxygen concentration band makes the blood oxygen concentration waveform smoother. * The AC programmable gain amplifier 丨 60 is to enlarge the blood oxygen concentration waveform to a proper amplitude and increase the accuracy of signal processing. Finally, the analogy to digital The signal conversion unit (A / D) 180 converts the analog blood oxygen concentration signal into a digital signal and sends it to the microprocessor 190 for digital No. processing work, but also to calculate the heart rate and oxygen concentration values. When measuring dense tissues of human blood vessels, due to different genders, races, and ages, the depth of skin color and the thickness of tissues will also vary. If you use -10-this paper wave scale applies Chinese National Standard (CNS) Α4 Specifications (210X297 public directors) Thread ordering {please note on the back of the hair κ write this page} Printed by the Consumer Cooperatives of the Central Standards Bureau of the Ministry of Economic Affairs 4 1808 f at ______B7 V. Description of the invention (8) Fixed light source brightness, For parts with lighter skin or thinner tissues, too strong a light source will cause a penetrating effect, and it will not detect the blood oxygen concentration signal waveform, which cannot be measured normally, but for parts with deeper skin or thicker tissues If the brightness of the light source is too weak, the normal blood oxygen concentration signal waveform will not be detected, and normal measurement will not be possible. Therefore, it is necessary to allow the brightness of the light source to automatically adjust its intensity according to the difference in skin tone, thickness, and tissue thickness, so as to capture the blood oxygen concentration signal waveform of any subject. As for the automatic adjustment of the brightness of the light source, it is achieved by using the characteristics of the system having a feedback control architecture. The light source driving circuit -110 is based on the size of the pulse width modulation (PWM) unit 170, and provides a voltage to the measuring probe 100 to control the brightness of the red and infrared light sources. The current is converted to a voltage level by the current conversion voltage unit 120. Signal, and the DC programmable gain amplifier 130 amplifies the signal according to the control value. Finally, the analog to digital signal conversion unit (A / D) 180 converts the signal to a digital signal, and the microprocessor 190 compares the upper and lower limits of the DC component of the signal. After that, the size of the pulse width modulation (PWM) and the magnification of the DC gain are corrected, and all the above processes are repeated until the judgment criteria are met. The entire calculation method for automatically adjusting the brightness of the red and infrared light sources is shown in Figure 2. The brightness of the red and infrared light sources is controlled by two pulse width modulators PWM0 and PWM1, respectively. PWM0 controls the light source of infrared light Brightness, PWM1 is to control the brightness of the red light source. First, after comparing the upper and lower limits of the DC component of the blood oxygen concentration signal detected by the infrared light source (step 200), modify the magnification of PWM0 and the DC gain. , And the smaller the value received from the PWM0 by the light source driving circuit 110 is, it means that it is relatively -11 _ This paper size applies the Chinese National Standard (CNS) A4 specification (2: 0 X 297 mm) n ^ — ii ^ i HI · 1 ^ 1 '(_Please read the precautions on the back first-write this page) Dingxian Ministry of Economic Affairs ordered the printing and printing of employees' cooperatives of the Prospective Bureau 41808 1 A7 ______ B7_ 5. Description of the invention (9) Infrared The brightness of the light source is stronger, so if the so-called measured DC component of the infrared light source is too small (step 220), the brightness of the light source may be weak, causing the detected blood oxygen concentration signal to be too small or the signal to be bad. Phenomenon In this case, the need to reduce the value sent PWM0, enhanced infrared light source brightness. If the value sent by PWM0 has reached the minimum value, the detected DC component is still too small. This may be the case of darker skin or thicker tissue. The magnification of DC gain must be increased to make the blood oxygen concentration signal strong. On the one hand, if the DC component detected by the infrared light source is too large (step 21), the brightness of the light source may be strong, causing the detected blood oxygen concentration signal wife or signal saturation. At this time, It is necessary to increase the value sent by PWM0 'to reduce the brightness of the infrared light source. If the value sent by PWMO has reached the maximum, the detected DC component is still too large, which may be the case of lighter skin or thinner tissue. The magnification of the DC gain must be reduced to weaken the blood oxygen concentration signal; the steps of adjusting the magnification of PWM0 and the DC gain are continued until the infrared light DC component reaches the upper and lower limits of the judgment standard. Similarly, for the loyal source of red light, the smaller the value of PWM1 received by the light source drive circuit UO, the stronger the brightness of the corresponding red light source, which is different from the step of adjusting the infrared light source. It is only adjusting the size of PWM1 to change the brightness of the red light source, and the magnification of the DC gain is determined in the step of adjusting the infrared light source. It is not necessary to repeatedly adjust the magnification of the DC gain. Similarly, if the red light source The detected DC component is too small (step 250), then reduce the value sent by PWM1 to enhance the brightness of the red light source. If the DC component detected by the red light source is too large (step 240), PWM1 needs to be increased The sent value 'reduces the brightness of the red light source, the same as -12-this paper size applies to the Chinese national standard (CNS > Μ specifications (2 丨 〇 > < 297 mm)! ^ ------, 1T- --------- 0 (Please read the note on the back-: write this page) 41808 1 Printed A7 B7 by the Shellfish Consumer Cooperation Department of the Central Standards Bureau of the Ministry of Economic Affairs 5. Description of the invention (10) Continue to adjust Step of PWM1 until the red light DC component reaches the upper and lower limits (Step 230). When the DC components of the infrared light and red light meet the standards, it means that the brightness of the light source brightness and the DC gain provided by the PWM0 and PWM1 values at that time are suitable for the set value of the subject. The best gray oxygen concentration signal waveform. The system can automatically adjust the brightness of the light source according to the difference of the skin or the thickness of the skin and the thickness of the tissue according to the difference of gender or race and age. This function can detect the blood oxygen concentration. The signal is necessary and very important. Assuming that the detected blood oxygen concentration signal is very normal, the next digital signal processing work can quickly and accurately calculate the blood oxygen concentration and heart rate value; otherwise, due to the light source Incorrect brightness and DC gain magnification control. 'The detected concentration of gold and oxygen becomes a bad signal or even no signal appears' causing calculation errors or failure to work properly. This case uses the feedback control system architecture characteristics. With the deduction method, the magnification control of the brightness of the light source and the DC gain is automatically adjusted to set the system positive The correct setting value. 'The captured blood oxygen concentration signal is converted into an analog blood oxygen concentration signal into a digital signal through an analog-to-digital signal conversion unit (A / D) 180 and sent to the microprocessor for digital Signal processing, calculate blood oxygen concentration and heart rate value = According to the calculation theory of blood oxygen concentration, in order to obtain the blood oxygen concentration value, the peak and trough value of the waveform must be accurately found, but the blood oxygen concentration signal must be overcome due to human actions. The baseline drift and the effect of becoming a chaotic waveform with rapid changes can quickly track the waveform and still correctly find the positions of the peaks and troughs. This case proposes a new signal tracking method using the so-called cross I dynamic double valve stomach 13 — this paper scale applies China National Standard (CNS) Α4 specification (210X297 mm) ΐ 衣 --------. Order ------ ^ (.Please read the notes on the back first-this page) Printed by the Bureau Cooper ¾ Fee Cooperative 4 1808 1_ b7 V. Description of the Invention (ii) (alternate PV dynamic threshold! 'Different from the signal level using only a single dynamic threshold; alternating dynamic double valves' as the name implies The signal level is used as a dynamic threshold to follow the wave of the waveform. ♦ There is no longer only a single reading value when the wave is trough. Instead, there are two types of dynamic thresholds to handle the waveform; that is, one of the dynamic thresholds only tracks the waveform. Peak level of the waveform, and another dynamic threshold value tracks the trough level of the waveform. The dynamic threshold value that tracks the peak level of the waveform is called the dynamic peak threshold, and tracks the trough level of the waveform. The dynamic complaint threshold is called the dynamic valley threshold. The concept of the alternating dynamic double valve is shown in Figure 3. Using the two signal levels of the dynamic peak threshold p and the dynamic valley threshold (330), follow the blood oxygen concentration waveform (300) 'to find the peak and valley positions of the waveform; When the waveform signal is greater than the dynamic peak threshold (340), the peak of the waveform is tracked. If the signal is greater than the upper edge of the peak (320), the signal is reset to the upper edge of the peak. If the upper edge of the wave becomes a horizontal line 'Indicates that Posin has found a waveform. Similarly, when the waveform signal is less than the dynamic trough threshold (330), the trough of the waveform is tracked. If the signal is less than the bottom trough (31), the signal is reset to the bottom trough. When it becomes a horizontal line, it indicates that the trough of the waveform has been found. Therefore, only when the signal is greater than the dynamic peak threshold (45) or less than the dynamic valley threshold (470), the waveform tracking work is performed, and the rest of the time is not processed, which greatly reduces the calculation time of waveform tracking and increases The system response speed. Tracking the blood oxygen concentration waveform by two moving thresholds can also avoid the heavy pulse (350) problem of the blood oxygen concentration waveform. The so-called heavy pulse, as shown in Figure 3, in addition to the pulse wave (360), in the middle of the waveform-the paper paper wave scales apply the Chinese National Standard (CNS) A4 specification (2: 0X297)! If I. H ^ Ηπ --- n --- In-(. Please read first, read the notes on the back f, write this page) Economy 郏 Zhongfu 搮 Rate 印 Printed by the employee consumer cooperative Λίβοδί Α7 _______ Β7 V. Invention Explanation (12) ^ wave, called heavy pulse (350). Because the pulse of the heavy pulse (35) also has rising and falling waveforms, it will be misjudged as a peak or valley when the waveform is tracked; if the peak or valley of the pulse is used to calculate the blood oxygen concentration value, an incorrect result will be produced. However, using the alternating dynamic double valve, only when the signal is greater than the upper edge of the peak (32) or lower than the lower edge of the trough (310), the action of tracking the peaks and troughs of the waveform will be performed. Processing, so easily avoid the problem of heavy pulse. As for how to detect the correct position of the peaks and troughs, according to the upper and lower edges of the crests (320) and (310), you can only determine the values of the crests and troughs-you cannot determine the timing of the crests and troughs; It is necessary to record the state of the waveform at any time. 'This derivation method records the detection conditions of the peaks and troughs separately', as shown in Figure 4. The logic signal level (0 or 〖) above the waveform curve represents the detection status of the recorded peaks. It is called the peak state (44), and the logic signal level below the waveform curve 'represents the detection state of the recorded valley' is called the valley state (450). When tracking the waveform, when the signal is too high on the peak edge (460), the peak state (44) is set to a logic level-0 '; otherwise it is set to a logic level -1, as shown in the figure. 〇 Change and become I 'determines the timing of the peak (400): Similarly, it can be inferred that when the signal is less than the lower edge of the trough (470), the trough state (450) is set to the logic level-0' Otherwise Set to logic level-]. Similarly, when the trough state changes from 0 to 1, it is determined: the timing of the trough (410) occurs. Therefore, using the peak state (440) and the valley state (450) can accurately detect the timing of the peak and valley, then the calculation of heart rate and blood oxygen concentration is accurate. 13 -15-.f Read the notes on the back _-Tr write this page) Binding-bound paper scales are applicable to Chinese national standards (CNS > M specifications (21 × 297 mm) 4 18 0 8 1 A7 B7 Printed by the Consumer Cooperative V. Description of the invention (13) Figure 5 shows a method of deriving an alternate dynamic double valve. The steps determine whether the signal is greater than the threshold value of the dynamic terror peak or lower than the threshold value of the dynamic trough. If so, perform steps 520 and 530. Follow the work of the waveform, if not, do not process' and step 520 is to determine the logical level of the peak state, and step 53 is to determine the logical level of the valley, g |; next, step 54 ° and 55 ° determine the timing of peaks and valleys. Step 54 ° is to find the timing of peaks of the waveform according to the changes in the state of the peaks (from 0 to 1), and set the peak flag ^ to 1, and this indicates detection. The wave measurement operation has been completed Step 55 is to find the time when the trough occurs according to the change of the trough state (from 0 to 丨), and set the trough flag to i, which indicates that the detection of the trough has been completed. But the detected waveform There may be poor signal, or the baseline drift caused by human motion, and it may become a chaotic waveform with drastic changes; in order to overcome the calculation error caused by poor signal and human factors, the timing of calculating the blood oxygen concentration and heart rate value Becomes very important; when the waveform tracking work is performed, when to calculate the blood oxygen concentration and when to calculate the heartbeat rate, will the result be wrong due to the above phenomenon, which will lead to incorrect results. According to the block diagram of the system in Figure I, we know that the circuit is using The low-pass filter (LPF) 15 removes high-end noise, and the peak portion of the waveform is less prone to interference from high-frequency noise. Therefore, when the peak of the waveform is found, the blood oxygen concentration and heart rate are calculated. It can avoid the problem of 4 calculation errors or double calculation. On the other hand, when the wave and valley of the waveform are found, the counter is used to determine the calculation. The timing of blood oxygen concentration and heartbeat rate can overcome the bad signal situation. As shown in Figure 4, when the peak (400) of the waveform is found, it is not immediately processed, but the 16 paper size is appropriate (eNS 丨 ( 21 () χ29 ^^!, ------ ^ ----- ^-i Order ------ ^ ('Please read the precautions on the back / write this page) 41808 1 Ministry of Economy Duo printed A7 B7 for employee cooperation of the Central Government Bureau ---------- One ______ Five, invention description (M) " wait for a counter to count for a period of time 'to determine that the found peak is still the highest point (Figure 4 (420)) 'only handles the corresponding action, and the interval between (400) and (420) is the delay time of the counter; Similarly, when the trough (410) of the waveform is found, it also After the counter counts for a period of time, it is determined that the found trough is still the lowest point (as shown in (430) of Figure 4), then the corresponding action is processed, and the interval between (410) and (430) is the counter. Ting Chi's time. The above method can effectively overcome the situation of bad signal and chaotic waveform, correctly calculate the blood oxygen concentration and heart rate value, reduce the chance of repeated calculation, and improve the speed and quality of signal processing. FIG. 6 is a deduction method for determining the timing of calculating blood oxygen concentration and heart rate. Step 600 determines whether the peak flag and wave state are 1. If yes, it indicates that the peak of the waveform is found. Steps 610 and 620 are steps of counter delay time. 'If the time interval is greater than 8, then proceed to step 630 to calculate the action of blood oxygen concentration and heart rate' and modify the dynamic trough threshold. Similarly, step 640 determines whether the flag of the trough and the trough state are 1. If yes, it means that the trough of the waveform is found; steps 650 and 660 are the steps of the counter time. 'If the time interval is greater than 8, proceed (step 670 ) Correction of dynamic wave and threshold operation. The dynamic trough threshold is set by using the peak value detected at the time (that is, the upper edge of the wave science) 'and the previous detected trough value (that is, the lower edge of the trough). The correction of the value is expressed by the equation, that is, the dynamic trough threshold = IU * the lower edge of the trough [nl] + K2 * the upper edge of the crest [η], and where KK1 + Κ2 = 1 'and KK1 > KK2, that is, biased Trough value. The setting of the dynamic crest threshold is to use the detected trough value (that is, -17---i--I --1-I-_ I -Material page) * π The paper size of the paper is suitable for financial affairs (CNS) M specifications (Canada Day) Printed by the Shell Standard Consumer Cooperative of the Central Standards Bureau of the Ministry of Economic Affairs 4 1808 1 A7 —__________ B7 V. Description of the invention ( U;) 'Under Pigu.' 彖) and the peak value (ie, the upper edge of the peak) as measured by a debt 'interpolation using the interpolation method to correct the early value of the oil peak advance p β τ and F receive T, Expressed in 10,000 formulas, it is the dynamic peak threshold value = κ3 * the upper edge of the peak, and the lower edge of the trough and where κ3 + Κ4 = I, and κ3 > κ4, that is, the value leaning against the peak. Because the current and previous detected peaks or troughs are used to modify the dynamic peaks and troughs of each other in an alternating manner, the situation of waveform changes can be understood, and the level value can be corrected very quickly and correctly. 'For the baseline drift caused by the action and the situation that it changes into a chaotic waveform with drastic changes-by alternating dynamic crests or trough valves, the influence of calculation errors caused by poor signals and human actions can be easily overcome. Furthermore, after finding the peaks and troughs of the waveform signal, according to the obtained timing and magnitude of the wave sins and troughs, and the DC component, according to the estimation theory, the blood oxygen concentration value and the heartbeat rate can be estimated. FIG. 7 to FIG. 12 are the analysis results according to the deduction method of the present invention. The waveform measured by the detection probe 100 is the blood oxygen concentration signal α of a human finger. FIG. 7 is a dynamic peak threshold value showing the blood oxygen concentration waveform. The signal correction process, as shown in the figure, the dynamic peak threshold value will be adjusted and adjusted as the waveform fluctuates to maintain the correct judgment level, and Figure 8 shows the signal detection process of the upper edge of the peak showing the blood oxygen concentration waveform. Although the waveform has obviously shaken, the deduction method can still correctly find the peaks of the waveform; Figure 9 shows the correction process of the dynamic valley threshold signal of the blood oxygen concentration waveform, and the dynamic valley threshold will follow the waveform. Adjust and revise to maintain the correct judgment level, and Figure 10 shows the bottom edge signal detection process of the blood oxygen concentration waveform. Although the waveform is again based on the Chinese National Standard (CMS) A4 specification (2ΙΟ × 2 mm) ) (Please read the precautions on the back of this page to write this page) Binding-Order Α7 Β7 V. Description of the invention (16) However, the method of deduction can still correctly find the wave troughs. Figure π shows the dynamic peak threshold value and dynamic valley threshold signal process of the modified oxygen concentration waveform by the derivation method. Figure 12 shows the peak edge and bottom valley signal signals of the blood oxygen concentration signal by the derivation method. The invention uses the alternating dynamic two-valve deduction method to quickly and correctly find the peaks and troughs of the blood oxygen concentration signal, and can easily overcome the baseline drift caused by poor signals, human actions, and the situation that the waveform changes into chaotic waveforms. However, the scope of application is not limited to the signal processing of blood oxygen concentration. Any action related to the detection of the peaks and troughs of the signal can be used—the deduction method of the present invention. ---------- ^ ------ 1Τ ------ ^ (Please read the precautions on the back first. 7 books f) Economic 'Deng Central Operating Bureau Staff Consumption Printed by Cooperatives-19-This paper size applies to China National Standard (CNS) A4 (210X 297 mm)