201134455 六、發明說明： 【發明所屬之技術領域】 ^發明係涉及-術驗侧人體生理_如舰辑 身^呆健等，特別是有關於一塊用布料電極與人體接 = -電容，在外界提供—職下會產生—絲鮮 測人體生理她，躺可酬㈣、啊、吞 至=汗、加速度、角速度、角加速度、澄度、張力、扭力與人# 以產生可分辨的訊號。 都了 ❹ Ο 【先前技術】 為了以讓人沒有錄㈣方絲制人體的生 號，可穿式的感應器是最重要的關鍵。在此技 ^ 述了使用可穿式電容感測㈣初步結果。在國外，也 3技例* Sergi。先生使用兩個導電電及去感測壓 力’八原理疋從外料、統提供―_定_率並侧兩個電 極之間的電容，其壓力變化的呈現是以電壓來表現。 另-細以細呼吸的纟關是脑雜化絲現：當使用 者呼吸時’電容會產生變化並導致電極之間的距離隨其變 化。 、 更有人利用兩導電電極之_電容變化來制空氣渔度。 ^un Rekimoto研發了一個可量測兩導電物體之間距離的技 術，他測量電極以及導電體之間的電容並使用一個轉換器和 一，電，接收器。其輸出端是以電壓的振幅來表現，其訊號 也疋固定的。Cliff Ran(ieii並說明了以兩個導電布形成一 電今，在外部的壓力人的姿勢一有變動，其電容值也跟著變化。在 Jan Meyer的研究中，其原理與上述幾篇相同，只是改變兩導電布之 間的材質。最後，Jingyuan Cheng利用人的身體當一介質，並放了 導電布在身體的兩侧以此形成電容，同時有一電路去測量電容值的變 化’在研究巾他展示了呼吸與喝水可以產生可分觸不同訊號。 201134455 在上述的研究中，電壓的振幅訊號變化並不是非常明顯，因此我們設 計了一個震盪器以產生頻率’並至少有一導電布與人體接觸以形成電 容。當人體產生生理變化時，電容值也隨之改變，因此我們可以偵測 到共振頻率的變化。其訊號非常明顯且容易判別。 本技術的主要貢獻是證明了生理訊號可由可穿式導電布低功耗裝置 中取得。特別的是我們展現了呼吸、吞嚥、咳嗽、姿勢、溼度與壓力 都可以產生可分辨的訊號。 【發明内容】201134455 VI. Description of the invention: [Technical field to which the invention belongs] ^The invention relates to the human physiology of the test side, such as the ship's body, the body, and the like, especially for the use of a cloth electrode and a human body. Provided - the job will produce - silk fresh body physiology she, lying remuneration (four), ah, swallowing = sweat, acceleration, angular velocity, angular acceleration, stiffness, tension, torque and people # to produce a distinguishable signal. All ❹ Ο [Prior Art] In order to make people's numbers without the (4) square wire, the wearable sensor is the most important key. In this article, the preliminary results using the wearable capacitive sensing (4) are described. In foreign countries, also 3 technical examples * Sergi. Mr. uses two conductive and de-sensing pressures. The eight-pronged principle provides the capacitance between the two electrodes from the external material, and the pressure change is represented by voltage. Another - fine breathing is the brain hybridization: when the user breathes, the capacitance changes and causes the distance between the electrodes to change. More people use the _ capacitance change of the two conductive electrodes to make the air catch. ^un Rekimoto has developed a technology that measures the distance between two conductive objects. It measures the capacitance between the electrodes and the conductors and uses a converter and an electric, receiver. Its output is represented by the amplitude of the voltage, and its signal is also fixed. Cliff Ran (ieii also shows that the formation of a current with two conductive cloths, the external pressure of the person's posture changes, the capacitance value also changes. In the study of Jan Meyer, the principle is the same as the above, Just change the material between the two conductive cloths. Finally, Jingyuan Cheng uses the human body as a medium, and puts a conductive cloth on both sides of the body to form a capacitor, and there is a circuit to measure the change in capacitance value. He showed that breathing and drinking can produce different signals. 201134455 In the above study, the amplitude signal change of the voltage is not very obvious, so we designed an oscillator to generate the frequency 'and at least one conductive cloth and the human body. Contact to form a capacitor. When the body changes physiologically, the capacitance value also changes, so we can detect the change of the resonance frequency. The signal is very obvious and easy to discriminate. The main contribution of this technology is to prove that the physiological signal can be Wearable conductive cloth in low-power devices. Especially we show breathing, swallowing, coughing, posture, humidity Both the pressure and the pressure can produce a distinguishable signal.
〇 本發明係涉及一種可用於偵測人體生理能例如體能訓練，醫療，健 身，保健等，特別是有關於一塊用布料電極與人體接觸兩者之間形成 一電容’在外界提供一訊號下會產生一共振頻率利用此共振頻率可偵 測人體生理參數’原先的技術都是看電麼的變化，其變化很小。目前 改成看其共振頻率，其變化很大本發明的目的之一在偵測姿勢其 運動、脚料喊各«的運動: 本發明的另一目的在於偵測吞嚥。 本發明的另一目的在於偵測咳漱。 本發明的另一目的在於偵測出汗。 本發明的目的之一在偵測加速度。 本發明的目的之一在偵測角速度。 本發明的目的之一在偵測角加速度。 生理訊镜 本發明的目的之一在偵測張力。 本發明的目的之一在偵測扭力。 本發明的目的之一在偵測壓力。 【實施方式】 為瞭解本發明之構造及特點所在， 並配合圖示說明如下，其中： 炫举Μ下項較佳實施例， 7 201134455 當物體接觸我們人體表面時’在皮膚表層會形成_等效電容本實驗 使用電極感測器接觸皮膚，且對電極施壓，間接對此等效電容施加壓 力，而等效電容因受壓力而使電容值產生變化，且利用此變化來分辨 電容大小及受力程度。 在實驗前，我們先假設人體（body)為—導體，而我們實驗分成兩區 〇 塊，一為雙感測器；另為單一感測器。 實施例一 電容 針對兩塊平行的極板電容器，如下圖所示，其電容為： d Ο 其中’ Α是每塊極板的表面積，d是二塊極板之間的距離，^介於 兩塊極板之 間的介電常數。由方程式2.1，我們可以得知三個決定因素來決定電 容值的大小： 1. 電谷的大小與平行板的表面積成正比。 2. 電容的大小與二塊平行板的距離成反比。 8 201134455 3.電容的大小與平行板材料的介電常數成正比。 實施例二 原理 綱震in產生-解，經由電極對電極與皮膚間的電容進行充放 電，進而得一相對頻率，且藉由壓力改變電極對皮膚間的電容值，因 而得到不騎對應鮮來分觸受壓力大小。 〇 #電極受壓力，則電極與皮膚間的距離⑷有所改變，進而改變相對 應電容值 實施例三 震盪器 我們將使用555去產生-個無穩態多鎌盡器電路，其接法如下圖所 示，外部電路由R2、C1及消除雜訊的旁路電容C2。電源初切上 時，電谷器C1並沒有充電，此時555的第3腳輸出為高電壓，電容 C1經R1、R2充電，當充電到2/3Vcc時，555的第6腳被觸發動作， 使得輸出腳第3腳轉成低電位(0V)，此時電gC1勢必經R2放電（因 第3腳輸出為” L”可視之為接地），當(^放電到1/3Vcc時，第2腳 被觸發使輸出腳第3腳又再轉態成高電位，如此週而復始的振盪。其 中C2為旁路電容’對控制而言是不太必要的，其作用是免除外界雜 訊從此腳輸入至555造成555發生錯誤，其C1充放電過程及對應的 9 201134455 輸出，由圖所示。 由上面對多諧振盪過程的分析中，我們可得輸出充放電的時間， 充電的時間ti為 (Ri+R〗）Ci tl=- 1.443 (1.1) Ο 放電的時間t2為 R2 Cj 1.443 (1.2) 振盪週期Τ為 (RpR^C, Τ = tl+t2 = — 1.443 (1.3) 其震盪頻率f為 1.443 (^+2¾)^ (1.4) 實施例四 實際應用 由於人體皮膚與感測器之間的變化就是一個電容性變化，因此，我們 運用這個特性，替換無穩態諧電路中的C1。因為可穿戴紡織式電極感 201134455 測器與身體的皮膚接觸壓力的變化，可等效於一個可變電容以。此 可變電容經由無穩態諧電路，並帶入式（1.1-1· 4)可得不同的頻率及 Duty cycle，而這個變化的頻率即為我們所求《替換後如下圖所示： 為更進一步闡述發明為達成預定發明目的的所採取的技術手段及功 效，以下結合附圖及較佳實施例，對依據本發明提出的心電圖監視及 人體姿勢判斷方法，裝置與系統其具體實施方式、結構、特徵及其功 〇 效，詳細說明如後。 有關本發明的前述及其它技術内容、特點及功效，在以下配合參考圖 示的較佳實施例的詳細說明中將可清楚呈現。通過具體實施方式旳說 明’當可對本發明為達成預定目採取的技術手段及功效得一更加深入 且具體的瞭解，然而所附圖式僅是提供參考與說明之用並非來本發明 加以限制。 以下則是導電布财兩個’同時當作電域測絲當作實驗結果，我 們可看到感測的鮮變化會比只有一端是導電布料所得更明顯。同時 可見施壓在沒有包鱗的導電布上，頻輕化比較小；有包海綿的導 電布，若受外力麵下，鮮變減較大，如表对受測者a， 當 沒包海綿的導電布林受壓時頻糊邊z,她啦時頻率為 1· 54khz，受壓 30kg 時頻率為 32Khz。 實施例五 < 數據> 201134455 Α.正極：銀纖維導電布；負極：銀纖維導電布 輕碰 施壓20Kg 施壓30Kg 壓正 極 11K 5.6 5.2 壓負 極 11K 5.6 4.3 Ο B.正極：銀纖維海綿；負極：銀纖維導電布The present invention relates to a method for detecting physiological energy of a human body such as physical training, medical treatment, fitness, health care, etc., in particular, a contact between a cloth electrode and a human body is formed to form a capacitor. Generating a resonant frequency using this resonant frequency to detect physiological parameters of the human body 'The original technique is to look at the change of electricity, and the change is small. At present, it is changed to look at its resonance frequency, which varies greatly. One of the objects of the present invention is to detect the movement of the posture and the movement of the foot material. Another object of the present invention is to detect swallowing. Another object of the invention is to detect cough. Another object of the invention is to detect sweating. One of the objects of the present invention is to detect acceleration. One of the objects of the present invention is to detect angular velocity. One of the objects of the present invention is to detect angular acceleration. Physiological Mirror One of the objects of the present invention is to detect tension. One of the objects of the present invention is to detect torque. One of the objects of the present invention is to detect pressure. [Embodiment] In order to understand the structure and characteristics of the present invention, and with the following description, the following is a description of the following: In the preferred embodiment of the present invention, 7 201134455 When the object touches the surface of our body, 'the surface layer of the skin will form _ etc. Effective Capacitance This experiment uses an electrode sensor to contact the skin, and applies pressure to the electrode, indirectly applying pressure to the equivalent capacitance, and the equivalent capacitance changes the capacitance value due to the pressure, and the change is used to resolve the capacitance and The degree of stress. Before the experiment, we first assumed that the body was a conductor, and our experiment was divided into two zones, one for the dual sensor and the other for the single sensor. The capacitor of the first embodiment is directed to two parallel plate capacitors, as shown in the following figure, the capacitance is: d Ο where 'Α is the surface area of each plate, d is the distance between the two plates, ^ is between two The dielectric constant between the plates. From Equation 2.1, we can see three determinants to determine the magnitude of the capacitance: 1. The size of the valley is proportional to the surface area of the parallel plate. 2. The size of the capacitor is inversely proportional to the distance between the two parallel plates. 8 201134455 3. The size of the capacitor is proportional to the dielectric constant of the parallel plate material. In the second embodiment, the principle is generated in the solution, and the capacitance between the electrode and the skin is charged and discharged through the electrode, thereby obtaining a relative frequency, and the capacitance value of the electrode to the skin is changed by the pressure, thereby obtaining a non-riding response. The touch is affected by the pressure. 〇#The electrode is under pressure, then the distance between the electrode and the skin (4) is changed, and then the corresponding capacitance value is changed. In the third embodiment of the oscillator, we will use 555 to generate an unsteady multi-compressor circuit. As shown in the figure, the external circuit consists of R2, C1 and a bypass capacitor C2 that eliminates noise. When the power is cut, the battery C1 is not charged. At this time, the output of pin 3 of 555 is high voltage, and capacitor C1 is charged by R1 and R2. When charging to 2/3Vcc, the 6th pin of 555 is triggered. , the output pin 3 is turned into a low potential (0V), at this time, the electric gC1 is bound to discharge through R2 (because the output of the third pin is "L" can be regarded as ground), when (^ discharge to 1/3Vcc, the first The 2 pin is triggered to make the output pin 3 turn to a high potential again, so that the oscillation is repeated. The C2 is a bypass capacitor is not necessary for the control. The function is to prevent the noise from being input from this pin. To 555 caused 555 error, its C1 charge and discharge process and the corresponding 9 201134455 output, as shown in the figure. From the above analysis of the multi-resonance process, we can get the charge and discharge time, the charging time ti is (Ri+R))C tl=- 1.443 (1.1) Ο The time t2 of discharge is R2 Cj 1.443 (1.2) The oscillation period Τ is (RpR^C, Τ = tl+t2 = — 1.443 (1.3) The oscillation frequency f 1.443 (^+23⁄4)^ (1.4) The practical application of the fourth embodiment is a capacitive phenomenon due to the change between the human skin and the sensor. Therefore, we use this feature to replace C1 in the non-stationary harmonic circuit. Because the wearable textile electrode sense 201134455 sensor and the skin contact pressure change, can be equivalent to a variable capacitor. The variable capacitors pass through the non-stationary harmonic circuit and are brought into the equation (1.1-1·4) to obtain different frequencies and Duty cycles, and the frequency of this change is what we ask for “replacement as shown below: for further Illustrating the technical means and efficacy of the invention for achieving the intended purpose of the invention, the following describes the electrocardiogram monitoring and human body posture judging method according to the present invention, the specific embodiment and structure of the device and the system, with reference to the accompanying drawings and preferred embodiments, The features and advantages of the present invention will be apparent from the following detailed description of the preferred embodiments of the invention.旳 Describing 'When the invention can achieve a more in-depth and specific understanding of the technical means and effects to achieve the intended purpose, however, the drawing The use of the reference and the description is not limited by the present invention. The following is the conductive cloth two 'simultaneously used as the electric field test wire as the experimental result, we can see that the fresh change of the sense will be more than only one end is The conductive cloth is more obvious. At the same time, it can be seen that the pressure is applied on the conductive cloth without scales, and the frequency is lighter. The conductive cloth with the sponge is reduced by the external force surface, such as the tester. a, when the conductive boolean without the sponge is pressed, the frequency of the paste is z, the frequency of her is 1·54khz, and the frequency is 32Khz when the pressure is 30kg. Example 5 <Data> 201134455 Α. Positive electrode: silver fiber conductive cloth; negative electrode: silver fiber conductive cloth, light pressure, 20Kg, pressure 30Kg, positive pressure, 11K, 5.6, 5.2, negative electrode, 11K, 5.6, 4.3 Ο B. positive electrode: silver fiber sponge Negative electrode: silver fiber conductive cloth
輕碰 施壓20Kg 施壓30Kg 壓正 極 20K 7.2K 5. 5K 壓負 極 20K 5.4K 4.3K C.正極:銀纖維海綿；負極：銀纖維海綿Flip 20Kg pressure 30Kg pressure 20K 7.2K 5. 5K negative pole 20K 5.4K 4.3K C. positive electrode: silver fiber sponge; negative electrode: silver fiber sponge
輕碰 施壓20Kg 施壓30Kg 壓正 極 11K 3.6K 3.3K 壓負 極 11K 3. 2K 3.1K 實施例六 12 201134455 應用 吞喉嚨：偵測吞口水與咳嗷兩個動作數據的不同 吞口水：9〜llkhz，剛剛開始吞口水的頻率是11，當口水正好在喉頭 時變化最劇烈，頻率為最小值9khz，口水一吞完又恢復到llkhz，這 整個變化的過程平緩但明顯。 咳漱:9 khz，一咳嗷頻率馬上變化，一咳完頻率立刻恢復9khz 〇 以上兩個動作，一個電極放在柚口，另外一個放在喉頭。 實施例七 頸部運動： 頭跟身體是直立時：18khz 頭往後仰60度：llkhz 頭往前低30度:12khz 〇 以上的動作’固定電極一個放在袖口，另一個電極放在後頸部與喉嚨。 實施例八 呼吸運動： 吸：50〜67khz 吐：67~52khz &中間頻率變化很規律，如果測試者吸得愈深，其值變化愈大。 以上的動作，固定電極一個放在袖口，另一個電極放在腹部。 13 201134455 實施例九 el bow運動： 手臂伸直時:113khx 手臂彎曲90度：113~64khz 以上動作固定一個電極在袖口，另一個電極放在elbow angle，運動 時手臂彎曲角度愈大，壓迫愈緊。 〇 實施例十 腳跟 腳跟剛剛踩到感測器：1 OOkhz 腳以65kg重力踩感測器：100〜51khz 以上動作固定一個電極在袖口，另一電極放在腳跟下受壓。 【圖式簡單說明】 圖一係使用在本發明的架構示意圖。 圖二係使用在本發明無穩態多諧振盪器示意圖Flip pressure 20Kg pressure 30Kg pressure positive 11K 3.6K 3.3K pressure negative 11K 3. 2K 3.1K example six 12 201134455 application swallowing throat: detect swallowing water and cough two different action data of swallowing water: 9~ Llkhz, the frequency of swallowing water just started is 11, when the saliva just changes sharply in the throat, the frequency is the minimum value of 9khz, the mouth water is swallowed and then returned to llkhz, the whole process of change is gentle but obvious. Cough: 9 khz, the frequency of a cough changes immediately, and the frequency of coughing immediately recovers 9khz 〇 The above two actions, one electrode is placed in the grapefruit mouth and the other is placed in the throat. Example 7 Neck Movement: When the head is upright: 18khz Head backwards 60 degrees: llkhz Head is 30 degrees lower: 12khz 〇 Above action 'Fixed electrode one on the cuff and the other on the back neck Department and throat. Example 8 Respiratory exercise: Suction: 50~67khz Spit: 67~52khz & The intermediate frequency changes very regularly. If the tester absorbs deeper, the value changes more. In the above action, one fixed electrode is placed on the cuff and the other electrode is placed on the abdomen. 13 201134455 Example 9 El bow movement: When the arm is straight: 113khx Arm bending 90 degrees: 113~64khz The above action fixes one electrode in the cuff and the other electrode in the elbow angle. The greater the arm bending angle during exercise, the tighter the compression .实施 Example 10 Heel Heel just stepped on the sensor: 1 OOkhz foot with 65kg gravity step sensor: 100~51khz The above action fixes one electrode in the cuff and the other electrode under the heel. BRIEF DESCRIPTION OF THE DRAWINGS Fig. 1 is a schematic diagram of the architecture used in the present invention. Figure 2 is a schematic diagram of the use of the astable multivibrator in the present invention.