200534830 玖、發明說明： 【發明所屬之技術領域】 本發明是有關於一種用於血管內血液流動聲音放大 '量 測、比對、顯示與記錄之電子裝置，特別是用於尿毒症病 患，平日對賡管照護之輔助監測上，並早期診斷出是否有 栓塞（thrombosis)或狹窄（stenosis)等症狀，以達到居 家照護之目的。 【先前技術】 爲了從生物體中，有效及淸晰獲取我們感興趣之聲 音，特別是與醫學診斷相關之聲音訊號，因此聲音訊號擷 取及即時訊號處理等工作是不可或缺的。US5,825,895專利 揭露了主要提供醫生作爲心音聽診之電子聽診器設計；隨 著調整不同模式之訊號處理方式，可獲取最佳之聲音輸 出。於US6,228,040專利中則針對腸音訊號進行處理，並 透過電腦紀錄及進行分析，以作爲診斷大腸急躁症之依據。 針對動靜脈瘻管之檢測方面，US5,510,717、 US5,685,989、US6，1 89,388 及 US6,2 1 0,5 9 1 B 1 等專利，利 用注入追蹤劑（marker fluid )方式推測赓管血流速度與再 循環（recirculation)效率；US6,5 82,656 B1 專利則揭露了 一非侵入性之量測方式，其主要藉由直接量測血液中某些 成分之濃度作爲透析儀之血流速率與過濾速率之參數，再 進而推測出瘻管血流速度與再循環效率，達到檢測目的； 於US6,623,443 B1專利中亦揭露了另一個以量測壓力脈衝 200534830 (pressure pulses )爲主之非侵入性檢測裝置；此外，於 US6，167,765、US6,575,927專利中揭露了以非侵入性之都 普勒超音波感測器作爲量測工具，並利用接收到之都普勒 頻率訊號判斷洗腎時賡管之血流速度，藉以調控血液透析 儀之幫浦轉速。唯這些專利皆針對病患進行血液透析期間 之血流速度評估及作爲調控透析儀幫浦轉動速率之用，故 皆配備於血液透析儀之上，除造價昂貴外，並無法獨立運 作於日常生活中。 【發明内容】 對於尿毒症的病患而言，血液透析是病患賴以爲生的 治療方式；而血液透析（洗腎）的治療，血管徑路的通暢代 表了洗腎的品質與生命的延續，洗腎動靜脈廩管狹窄造成 了這些病患極大的困擾，以往僅有外科的血栓淸除術或重 新再接一條新的動靜脈瘻管來治療這類病人。廋管的分 類：可分爲自體血管及人工血管。前者就是將自己的表皮 靜脈和動脈相連，後者則是植入一條人工合成之血管於患 者之皮下，一般而言，自體血管不管在壽命及流速上皆較 人工血管爲佳，故唯有當自體血管太細無法使用時，才考 慮採取人工血管植入。 因洗腎治療時一定要使用到瘻管，且賡管的好壞，直 接關係到洗腎時的血液流速，影響到尿毒的淸潔率，故屢 管可說是尿毒症患者的生命線。如何擁有及保護一條好 用、耐用的廩管、是尿毒症病人及醫護人員關心的問題。 200534830 目前尿毒症患者照顧屢管的方式是以聽診器，每日放在廩 管外聽幾次，若管子暢通無阻，將可聽到沙沙的聲音，如 果聲音變弱或聽不到時，即表示血流狀態不好或已凝固， 這時應趁早到醫院去將凝血塊淸除；因爲早期發現凝血塊 比較容易淸除，血管套管可弄通繼續使用，若凝血已太久， 凝血塊已黏牢在血管壁上則很難將血塊淸除，最後必須重 新手術。 根據赓管血流狀態之重要性，目前除了患者自行使用 聽診器外，尙未有任何產品可以監測賡管血流狀態，提供 給病患瘻管血流即時狀態。本發明即在開發監測瘻管之血 流是否流通順暢之元件，根據瘻管內之血流速度不同會造 成不同聲音的原理來進行元件開發，此發明爲首度揭露可 以監測廩管之血流的元件，特別是提供給尿毒症患者使 用。此賡管監測元件可以直接、長時間放置於廩管外側， 鼙助患者監測麇管之血流流動現況或紀錄廩管之血流情 形，使患者可以在赓管血流不通順時，第一時間到醫院進 行診療。 【實施方式】 有關本發明之較佳實施例，主要用於尿毒症患者進行 屢管之血流狀況監測，茲配合圖式說明於如下： 本元件之外部設計，共包括三個實施例。 第一實施例主要爲殼體1部分與測量端固定扣環i 3部 分採用分離設計方式，請參閱圖1，其中圖1 a爲測量端固 200534830 定扣環部分及圖1 b爲殼體1後視圖。於此設計，殻體1可 至於桌上或其它平面上，再藉由位於殻體1測邊之訊號插 孔24與由量測端延伸出來之外部連接線22前端的訊號插 頭23做接合，麥克風2則置於扣環下方可與待測者受測位 置相吻合之位置內部，當主要聲音訊號被麥克風2接收之 後，將藉由埋藏於扣環內之內部訊號線2 1及外部連接線 22將其傳輸至殼體內之訊號處理電路單元3做進一步處 理，再將量測結果顯示於LCD面版4 1上，或透過蜂鳴器 345進行放音之動作，並進行比對判斷，若於某段時間內 所判讀之結果皆小於臨界値，則警訊指示燈342將發出警 訊。關於裝置之電源ΟΝ/OFF，則由位於裝置側邊之電源 開關341所控制；當電源ON時，電源指示燈343會隨之 開啓，使用者即可進行量測或其他設定。面版上之參數設 定按鍵一 346、參數設定按鍵二347、參數設定按鍵三348 及參數設定按鍵四349主要提供使用者進行簡單之參數設 定用，包括時間之校正、量測臨界値之調整、量測模式之 變換等，若於設定期間發生錯誤，錯誤指示燈344將隨之 動作，告知使用者重新設定。另外，有關裝置電源部分， 則採用內建可充電式鋰電池供應之，位於殼體1側邊之插 孔3 84即提供欲充電時與外部變壓器連接之用。 第二實施例請參閱圖2之側面圖及圖2a之殻體正視 圖，殼體1乃直接結合至腕狀固定扣環11之上，麥克風2 則置於扣環下方可與待測者受測位置相吻合之位置內部， 當主要聲音訊號被麥克風2接收之後，將藉由埋藏於扣環 200534830 內之內部訊號線21將其傳輸至殻體內之訊號處理電路單 元3做進一步處理，再將量測結果顯示於LCD面版41上’ 並進行比對判斷，若於某段時間內所判讀之結果皆小於臨 界値，則警訊指示燈342將發出警訊。關於裝置之電源 ON/OFF，貝[]由位於裝置側邊之電源開關341所控制；當電 源ON時，電源指示燈343會隨之開啓，使用者即可進行 量測或其他設定。面版上之參數設定按鍵一 346、參數設 定按鍵二347、參數設定按鍵三348及參數設定按鍵四349 主要提供使用者進行簡單之參數設定用，包括時間之校* 正、量測臨界値之調整、量測模式之變換等，若於設定期 間發生錯誤，錯誤指示燈344將隨之動作，告知使用者重 新設定。另外，有關裝置電源部分，則採用內建可充電式 鋰電池供應之，位於殻體1側邊之插孔384即提供欲充電 時與外部變壓器連接之用。 第三實施例請參閱圖3之正視圖及圖3a之後視圖，殼 體1乃直接結合至腕帶12之上，腕帶則分爲上腕帶121與 下腕帶1 22兩部分，位於上腕帶1 2 1之背面尖端位置處含# 有一固定區域一 123,及下腕帶122之正面尖端位置處含 有一固定區域二1 24，如此即可將裝置固定於受測者之手 臂上；麥克風2則置於下腕帶可與待測者受測位置相吻合 之位置內部，當主要聲音訊號被麥克風2接收之後，將藉 " 由埋藏於扣環內之內部訊號線21將其傳輸至殼體內之訊 ‘ 號處理電路單元3做進一步處理，再將量測結果顯示於 LCD面版4 1上，並進行比對判斷，若於某段時間內所判讀 200534830 之結果皆小於臨界値，則警訊指示燈342將發出警訊。關 於裝置之電源ΟΝ/OFF，則由位於裝置側邊之電源開關341 所控制；當電源ON時，電源指示燈343會隨之開啓，使 用者即可進行量測或其他設定。面版上之參數設定按鍵一 346、參數設定按鍵二347、參數設定按鍵三348及參數設 定按鍵四349主要提供使用者進行簡單之參數設定用，包 括時間之校正、量測臨界値之調整、量測模式之變換等， 若於設定期間發生錯誤，錯誤指示燈344將隨之動作，告 知使用者重新設定。另外，有關裝置電源部分，則採用內* 建可充電式鋰電池供應之，位於殻體1側邊之插孔384即 提供欲充電時與外部變壓器連接之用。 有關本發明之電路方塊圖，請參閱圖4。其中麥克風2 接收外部訊號後傳輸至訊號處理電路單元3做訊號處理， 前置放大處理電路3 1將麥克風2傳送之訊號做訊號前級放 大與增益自動調整控制，再將訊號傳送至訊號處理器32 做即時訊號處理，見於圖4a，如圖4a爲訊號處理器之內 部訊號處理方塊圖，最後由訊號處理器32輸出訊號傳送至鲁 輸出單元4將訊號處理結果輸出。時脈振盪電路33將提供 時脈訊號輸入訊號處理器3 2，即訊號處理器3 2所需之振 盪頻率。設定及週邊電路34將提供此裝置之各功能設定按 鍵開關、各功能指示燈、3 4 5蜂鳴器、充電電池等之功能 電路，此設定及週邊電路34需將連接訊號處理器32之輸 -出入埠來控制而達到上述之功能。即時時間電路3 5是提供 目前的即時日期時間之功能電路，將即時日期時間的資訊 11 200534830 輸入訊號處理器32，來記錄日期及時間。通訊介面電路3 6 連接至訊號處理器32之通訊介面埠，是提供通訊介面電 路，能使此裝置之資訊及紀錄資料對外連結輸出，此實施 例提供了 RS-232通訊介面電路與電腦做輸出連結，將此裝 置監測紀錄所得之資料傳輸至其他電腦裝置可利於分析及 建檔。充電電路37是提供裝置內建電池之充電功能，充電 電路3 7的控制電路能達到電池充電及電池過溫保護功 能。電源電路38將提供此裝置所需之各項電源，有2.5V 電路3 8 1供給訊號處理器3 2所需之內部核心電源，3.3 V 電路3 82供給電路爲3·3V規格之元件，5.0V電路3 83供給 電路爲5.0V規格之元件。 另外，請參考圖4 a，係本發明之訊號處理器3 2之內部 訊號處理方塊圖，如圖4之前置放大處理3 1輸出訊號傳送 至訊號處理器32，由訊號處理器32之內部抗交疊低通濾 波部分3201接收訊號，將訊號之高頻雜訊濾除，並且使訊 號無交疊情形。再將訊號做取樣經由取樣保持部分3202 處理後，訊後傳送至類比-數位轉換3203，將類比訊號'轉 換成爲數位訊號。接著將數位訊號加入所設計之窗型效應 3204將訊號做過濾，此訊號傳送至離散傅立葉演算3205 做訊號頻譜分析，離散傅立葉演算3205輸出同時有二部 分。其一是將分析後之訊號傳送至功能演算3206將訊號做 各功能演算處理，將訊號演算處理後之訊號結果傳送至輸 出功能3207，由輸出功能3207將訊號處理後之結果做各 項判別輸出，最後經由輸出介面3208將結果送至輸出單元 12 200534830 4。另一處理是離散傅立葉演算3205將訊號送至數位-類比 轉換3 209，將數位訊號轉換成類比訊號，將此類比訊號經 由補償重建濾波3210作處理，再由增益調變3211調整訊 號強弱，最後透過輸出介面3208將結果送至輸出單元4。 於實際量測部分，我們已利用本發明針對接受過動靜脈 廩管手術之洗腎病患進行實驗，結果發現接受到且經前置 放大處理電路31調控後之聲音訊號輸出乃具有一規律性 波動，請參閱圖5及圖7;其中圖5乃針對接受自體賡管 手術之病患進行實際量測之結果，圖7則是針對接受U型 人工賡管手術之病患進行實際量測之結果。隨後我們將此 訊號送至訊號處理器32單元進一步執行時域對頻域之轉 換，其結果請參閱圖6及圖8 ;其中圖6爲圖5進行FFT 轉換後之結果，圖8爲圖7進行FFT轉換後之結果。根據 得到之頻譜分析，即可找出此受測者正常狀態下之頻率特 徵値或分佈，往後只要將平日測得之結果與此頻率特徵値 或分佈進行比對，即可早期發現不對勁，進而隨時通報醫 生，以利及時處理。 上述實施例僅係爲了方便說明而舉例而已，本發明所主 張之權利範圍自應以申請專利範圍所述爲準，而非僅限於 上述實施例。 【圖式簡單說明】 圖1係本發明第一實施例之主機立體正視圖。 圖1 a係本發明第一實施例之配件立體圖。 13 200534830 圖1 b係本發明第一實施例之主機立體背視圖。 圖2係本發明第二實施例之立體側視圖。 圖2 a係本發明第二實施例之立體正視圖。 圖3係本發明第三實施例之立體正視圖。 圖3 a係本發明第三實施例之立體背視圖。 圖3 b係本發明第三實施例之立體側視圖。 圖4係本發明之電路方塊圖。 圖4 a係本發明之訊號處理器內部訊號處理方塊圖。 圖5係針對自體屢管實際量測之聲音訊號輸出圖。 圖6係圖5經轉換後之頻譜圖。 圖7係針對U型人工瘻管實際量測之聲音訊號輸出 圖。 圖8係圖7經轉換後之頻譜圖。 圖9係本發明之時脈振盪電路電路圖。 圖1 〇係本發明之設定及週邊電路之電路圖。 圖1 1係本發明之即時時間電路圖。 圖1 2係本發明之通訊介面電路圖。 圖1 3係本發明之電池充電電路圖。 圖1 4係本發明之電源輸入電路圖。 圖1 5係本發明之電源2 · 5 V電路圖。 圖1 6係本發明之電源3 · 3 V電路圖。 圖1 7係本發明之電源5 · 0 V電路圖。 圖18係本發明之LCD電路圖。 14 200534830 【圖號說明】 1 殻體 1 2 1 上腕帶 1 24 固定區域 2 麥克風 23 訊號插頭 3 訊號處理 電路單元 3 2 0 1抗交疊低 通濾波 3 2 0 4窗型效應 3 2 0 7輸出功能 3 2 1 0補償重建 濾波 3 3 時脈振盪 電路 34 設定及週 11 腕型固定 扣環 122 下腕帶 13 測量端固定 扣環 2 1 內部訊號 線 2 4 訊號插孔 3 1 前置放大 處理電路 3 2 0 2取樣保持 3 2 0 5離散傅立 葉演算 3 2 0 8輸出介面 3 2 1 1增益調變 12 腕帶 123 固定區域 22 外部訊號 線 3 2 訊號處理 器 3 2 0 3類比-數位 轉換 3 2 0 6功能演算 3 2 0 9數位-類比 轉換200534830 发明 Description of the invention: [Technical field to which the invention belongs] The present invention relates to an electronic device for measuring, comparing, displaying, and recording sounds for blood flow in blood vessels, especially for uremia patients. On the auxiliary monitoring of sacral tube care on weekdays, and early diagnosis of symptoms such as thrombosis or stenosis, in order to achieve the purpose of home care. [Previous technology] In order to effectively and clearly obtain the sounds we are interested in from living organisms, especially the sound signals related to medical diagnosis, the tasks of sound signal extraction and real-time signal processing are indispensable. The US 5,825,895 patent discloses the design of an electronic stethoscope that mainly provides doctors as auscultation of heart sounds; the best sound output can be obtained by adjusting the signal processing methods of different modes. In US Pat. No. 6,228,040, intestinal audio signals are processed and recorded and analyzed by a computer as a basis for diagnosing irritability in the large intestine. For the detection of arteriovenous fistulas, US5,510,717, US5,685,989, US6, 1 89,388 and US6, 2 1 0, 5 9 1 B 1 and other patents use marker fluid to inject the sacral blood flow velocity. And recirculation efficiency; US 6,5 82,656 B1 patent discloses a non-invasive measurement method, which mainly uses direct measurement of the concentration of certain components in blood as the blood flow rate and filtration rate of the dialyzer Parameters, and further inferred the fistula blood flow velocity and recirculation efficiency to achieve the purpose of detection; US 6,623,443 B1 patent also disclosed another non-invasive detection device mainly for measuring pressure pulses 200534830 (pressure pulses) In addition, in US Pat. Nos. 6,167,765 and 6,575,927, it is disclosed that the non-intrusive capital Doppler ultrasonic sensor is used as a measuring tool, and the received Doppler frequency signal is used to judge the sacral tube during renal dialysis. The blood flow velocity is used to regulate the pump speed of the hemodialyzer. However, these patents are aimed at assessing the blood flow velocity of patients during hemodialysis and for regulating the pump rotation rate of the dialysis machine. Therefore, they are all equipped on the hemodialysis machine. Besides being expensive, they cannot operate independently in daily life. in. [Summary of the invention] For patients with uremia, hemodialysis is the treatment method on which the patient depends for a living; while in the treatment of hemodialysis (dialysis), the smoothness of the blood vessel path represents the quality of kidney dialysis and the continuation of life Renal dialysis arteriovenous stenosis caused great distress to these patients. In the past, only surgical thrombectomy or a new arteriovenous fistula was used to treat such patients. Classification of sacral canals: can be divided into autogenous blood vessels and artificial blood vessels. The former is to connect its own epidermal vein with the arteries, while the latter is to implant a synthetic blood vessel under the patient's skin. Generally speaking, autologous blood vessels are better than artificial blood vessels in terms of life span and flow rate. When the autologous blood vessels are too thin to be used, an artificial blood vessel implantation is considered. Because the fistula must be used during dialysis treatment, and the quality of the sacral canal is directly related to the blood flow rate during dialysis, which affects the cleanliness rate of uremia, so repeated tube can be said to be the lifeline of uremia patients. How to own and protect a useful and durable sacral canal is a concern for patients with uremia and medical staff. 200534830 At present, the way to take care of patients with uremia is to use a stethoscope and listen to it outside the sacral canal several times a day. If the tube is unobstructed, a rustling sound will be heard. If the sound becomes weak or inaudible, it means blood. The flow state is not good or has coagulated. At this time, you should go to the hospital as soon as possible to remove the clot; because early detection of the clot is easier to remove, the vascular cannula can be opened and continued to be used. It is difficult to remove the blood clot on the blood vessel wall, and the operation must be performed again. According to the importance of sacral blood flow status, there is currently no product that can monitor the status of sacral blood flow, except for patients using their own stethoscopes, to provide patients with fistula blood flow status in real time. The present invention is to develop a component for monitoring whether the blood flow of the fistula is smooth. The component development is based on the principle that different blood flow speeds in the fistula can cause different sounds. This invention is the first to disclose an element that can monitor the blood flow of the fistula. , Especially for patients with uremia. This sacral tube monitoring element can be placed directly outside the sacral tube for a long time, helping patients to monitor the status of sacral blood flow or record the sacral blood flow, so that patients can Time to go to the hospital for treatment. [Embodiment] The preferred embodiment of the present invention is mainly used for monitoring the blood flow condition of patients with uremia, and it is described below with reference to the drawings: The external design of this element includes three embodiments. The first embodiment mainly uses a separate design method for the housing 1 part and the measuring end fixing buckle i 3 part, please refer to FIG. 1, where FIG. 1 a is the measuring end fixing 200534830 fixed buckle part and FIG. 1 b is the housing 1 Rear view. In this design, the casing 1 can be placed on a table or other flat surface, and then the signal jack 24 on the side of the casing 1 is connected to the signal plug 23 at the front end of the external connection line 22 extending from the measuring end. The microphone 2 is placed inside the position under the buckle which can be matched with the position of the test subject. After the main sound signal is received by the microphone 2, the internal signal line 21 and the external connection line buried in the buckle will be used. 22 It is transmitted to the signal processing circuit unit 3 in the casing for further processing, and then the measurement result is displayed on the LCD panel 41, or the sound is played through the buzzer 345, and the comparison is judged. If the results read within a certain period of time are all less than the critical threshold, the warning indicator 342 will issue a warning signal. Regarding the device's power ON / OFF, it is controlled by the power switch 341 located on the side of the device; when the power is ON, the power indicator 343 will be turned on, and the user can make measurements or other settings. The parameter setting button 346, parameter setting button two 347, parameter setting button three 348, and parameter setting button four 349 on the panel mainly provide users with simple parameter settings, including time calibration, measurement threshold adjustment, If there is an error during the setting of the measurement mode, etc., an error indicator 344 will follow to inform the user to reset. In addition, the power supply part of the device is supplied with a built-in rechargeable lithium battery. The socket 3 84 located on the side of the casing 1 is used to connect to an external transformer when charging is required. For the second embodiment, please refer to the side view of FIG. 2 and the front view of the casing of FIG. 2a. The casing 1 is directly coupled to the wrist-shaped fixing buckle 11, and the microphone 2 is placed under the buckle to receive the test subject. Inside the position where the measured positions match, after the main sound signal is received by the microphone 2, it will be transmitted to the signal processing circuit unit 3 in the housing through the internal signal line 21 buried in the buckle 200534830 for further processing, and then The measurement result is displayed on the LCD panel 41 ', and a comparison judgment is made. If the results read within a certain period of time are all less than the critical threshold, the warning indicator 342 will issue a warning signal. Regarding the power ON / OFF of the device, the [] is controlled by the power switch 341 located on the side of the device; when the power is ON, the power indicator 343 will be turned on, and the user can make measurements or other settings. The parameter setting button 346, parameter setting button two 347, parameter setting button three 348, and parameter setting button four 349 on the panel mainly provide users with simple parameter settings, including time calibration, positive, and measurement criticality. For adjustment, measurement mode conversion, etc., if an error occurs during the setting period, the error indicator 344 will act accordingly to inform the user to reset. In addition, the power supply of the device is provided by a built-in rechargeable lithium battery. The jack 384 on the side of the case 1 is used to connect to an external transformer when charging is required. For the third embodiment, please refer to the front view of FIG. 3 and the rear view of FIG. 3a. The casing 1 is directly connected to the wristband 12, and the wristband is divided into an upper wristband 121 and a lower wristband 1 22, which are located on the upper wristband. 1 2 1 has a fixed area # 123 on the back tip position, and a fixed area 2 1 24 on the front tip position of the lower wrist strap 122, so that the device can be fixed on the subject's arm; microphone 2 Then it is placed inside the position where the lower wristband can match the test position of the test subject. After the main sound signal is received by the microphone 2, it will be transmitted to the case by the internal signal line 21 buried in the buckle. The in vivo signal processing circuit unit 3 performs further processing, and then displays the measurement results on the LCD panel 41, and compares and judges. If the results of 200534830 are all less than the threshold value in a certain period of time, then A warning light 342 will sound a warning. The power ON / OFF of the device is controlled by the power switch 341 located on the side of the device; when the power is ON, the power indicator 343 will be turned on, and the user can perform measurement or other settings. The parameter setting button 346, parameter setting button two 347, parameter setting button three 348, and parameter setting button four 349 on the panel mainly provide users with simple parameter settings, including time calibration, measurement threshold adjustment, If there is an error during the setting of the measurement mode, etc., the error indicator 344 will act accordingly to inform the user to reset. In addition, the power supply of the device is provided by a built-in rechargeable lithium battery. The jack 384 on the side of the case 1 is used to connect to an external transformer when charging is required. For a circuit block diagram of the present invention, please refer to FIG. 4. Among them, the microphone 2 receives the external signal and transmits it to the signal processing circuit unit 3 for signal processing. The preamplification processing circuit 3 1 uses the signal transmitted by the microphone 2 for signal pre-amplification and automatic gain control, and then sends the signal to the signal processor. 32 for real-time signal processing, as shown in Figure 4a. Figure 4a is the internal signal processing block diagram of the signal processor. Finally, the signal output by the signal processor 32 is transmitted to the Lu output unit 4 to output the signal processing result. The clock oscillation circuit 33 will provide a clock signal to the signal processor 32, that is, the oscillation frequency required by the signal processor 32. The setting and peripheral circuit 34 will provide the function circuit of each function setting key switch, each function indicator, 3 4 5 buzzer, rechargeable battery, etc. This setting and peripheral circuit 34 will be connected to the signal processor 32. -In and out port to control and achieve the above functions. The real-time circuit 35 is a functional circuit that provides the current real-time date and time. The real-time date and time information 11 200534830 is input to the signal processor 32 to record the date and time. The communication interface circuit 3 6 is connected to the communication interface port of the signal processor 32. It provides the communication interface circuit, which can enable the information and record data of this device to be externally connected to the output. Link, and transfer the data obtained from the monitoring records of this device to other computer devices for analysis and archiving. The charging circuit 37 provides a charging function for the built-in battery of the device. The control circuit of the charging circuit 37 can achieve battery charging and battery over-temperature protection functions. The power supply circuit 38 will provide all the power required for this device. There are 2.5V circuits 3 8 1 for the internal core power required by the signal processor 3 2 and 3.3 V circuits 3 82 for the 3 · 3V specification components. 5.0 The V circuit 3 83 is a 5.0 V component. In addition, please refer to FIG. 4a, which is a block diagram of the internal signal processing of the signal processor 32 of the present invention. As shown in FIG. 4, the pre-amplified processing 3 1 output signal is transmitted to the signal processor 32, which is internal to the signal processor 32. The anti-overlap low-pass filtering section 3201 receives the signal, filters out the high-frequency noise of the signal, and makes the signal non-overlapping. After the signal is sampled and processed by the sample and hold section 3202, the signal is sent to the analog-to-digital conversion 3203, and the analog signal is converted into a digital signal. The digital signal is then added to the designed window effect 3204 to filter the signal, and this signal is transmitted to the discrete Fourier calculus 3205 for signal spectrum analysis. The discrete Fourier calculus 3205 output has two parts at the same time. The first is to send the analyzed signal to the function calculation 3206 to process the signal for each function, and to send the signal result after the signal calculation to the output function 3207. The output function 3207 outputs the processed result to the various judgment outputs. , And finally send the result to the output unit 12 200534830 4 via the output interface 3208. The other process is the discrete Fourier calculus 3205, which sends the signal to digital-to-analog conversion 3 209, converts the digital signal to an analog signal, processes the analog signal through compensation reconstruction filtering 3210, and then adjusts the signal strength by gain modulation 3211. The result is sent to the output unit 4 through the output interface 3208. In the actual measurement part, we have used the present invention to perform experiments on renal dialysis patients who have undergone arteriovenous catheter surgery, and found that the sound signal output received and regulated by the preamplification processing circuit 31 has a regularity Fluctuation, please refer to Figure 5 and Figure 7; Figure 5 is the result of actual measurement for patients undergoing autologous canal surgery, and Figure 7 is the actual measurement for patients undergoing U-shaped artificial canal surgery The result. We then send this signal to the signal processor 32 unit to further perform time-to-frequency domain conversion. For the results, please refer to Figure 6 and Figure 8; Figure 6 is the result of FFT conversion in Figure 5, and Figure 8 is Figure 7 Results after FFT conversion. According to the obtained spectrum analysis, you can find the frequency characteristics or distribution of the subject in the normal state. In the future, as long as the results measured on weekdays are compared with the frequency characteristics or distribution, you can find out early. Further inform the doctor at any time to facilitate timely processing. The above embodiments are merely examples for the convenience of description. The scope of rights claimed in the present invention should be based on the scope of patent application, rather than being limited to the above embodiments. [Brief description of the drawings] FIG. 1 is a perspective front view of a host according to a first embodiment of the present invention. Figure 1a is a perspective view of an accessory according to the first embodiment of the present invention. 13 200534830 Fig. 1b is a three-dimensional back view of the host computer according to the first embodiment of the present invention. Fig. 2 is a perspective side view of a second embodiment of the present invention. Figure 2a is a perspective front view of a second embodiment of the present invention. FIG. 3 is a perspective front view of a third embodiment of the present invention. Fig. 3a is a perspective back view of a third embodiment of the present invention. Figure 3b is a perspective side view of a third embodiment of the present invention. FIG. 4 is a circuit block diagram of the present invention. Figure 4a is a block diagram of an internal signal processing of the signal processor of the present invention. Fig. 5 is a sound signal output diagram for the actual measurement of the self-repeated tube. FIG. 6 is a converted spectrum diagram of FIG. 5. Fig. 7 is a sound signal output diagram for actual measurement of a U-shaped artificial fistula. FIG. 8 is a converted spectrum diagram of FIG. 7. FIG. 9 is a circuit diagram of a clock oscillation circuit of the present invention. Figure 10 is a circuit diagram of the setting and peripheral circuits of the present invention. FIG. 11 is a real-time circuit diagram of the present invention. FIG. 12 is a circuit diagram of a communication interface of the present invention. FIG. 13 is a circuit diagram of a battery charging circuit of the present invention. Fig. 14 is a power input circuit diagram of the present invention. Fig. 15 is a circuit diagram of the 2.5 V power supply of the present invention. Fig. 16 is a circuit diagram of a 3 · 3 V power supply according to the present invention. Fig. 17 is a circuit diagram of a 5 · 0 V power supply according to the present invention. FIG. 18 is an LCD circuit diagram of the present invention. 14 200534830 [Illustration of drawing number] 1 Case 1 2 1 Wrist strap 1 24 Fixed area 2 Microphone 23 Signal plug 3 Signal processing circuit unit 3 2 0 1 Anti-overlap low-pass filtering 3 2 0 4 Window effect 3 2 0 7 Output function 3 2 1 0 Compensation reconstruction filtering 3 3 Clock oscillation circuit 34 Setting and week 11 Wrist-type fixed buckle 122 Lower wrist strap 13 Measuring-end fixed buckle 2 1 Internal signal line 2 4 Signal jack 3 1 Pre-amplification Processing circuit 3 2 0 2 Sample and hold 3 2 0 5 Discrete Fourier calculus 3 2 0 8 Output interface 3 2 1 1 Gain modulation 12 Wristband 123 Fixed area 22 External signal line 3 2 Signal processor 3 2 0 3 Analog-digital Conversion 3 2 0 6 Function calculation 3 2 0 9 Digital-analog conversion
3 4 1 電源開關 3 4 2 警訊指示 15 200534830 邊電路 3 4 3 電源指示 燈 3 4 6 設定按鍵 3 4 9 設定按鍵 四 3 5 即時時間 電路 燈 3 4 4 錯誤指示 3 4 5 蜂 燈 3 4 7 設定按鍵 3 4 8 設 36 通訊介面 電路 3 7 充電電 路 3 8 電源電 路 381 2 . 5 V 電 路 3 8 3 5 .0V 電 路 384 電源插 孔 4 1 LCD顯 示器 鳴器 定按鍵 3 V電路 163 4 1 Power switch 3 4 2 Warning indication 15 200534830 Side circuit 3 4 3 Power indicator 3 4 6 Setting button 3 4 9 Setting button 4 3 5 Instant time circuit light 3 4 4 Error indication 3 4 5 Buzzer light 3 4 7 Setting button 3 4 8 Setting 36 Communication interface circuit 3 7 Charging circuit 3 8 Power circuit 381 2. 5 V circuit 3 8 3 5 .0V circuit 384 Power jack 4 1 LCD display buzzer fixed button 3 V circuit 16