^3735 •發明說明 (1) 本發明係指 而使電極量 理。 按，在世界 —般建築物 1:冬共用地線 疋把地球當作 有的電器，2 ΐ間電位或電 條線輪送到 ί共用地線打到 輪的迴路。另在 公司送電力的接 線，所以電力公 有電力的火線即 ;亟， 與處 所 線 就 所 此 從 以 一種以人體為 測到的各種電 上普通使用的 一定會有一條 打入地底，把 零參考電位， 所有電器都以 壓的比較。所 建築物，並且 地底，以地球 建築物中的插 點褚為火線， 司不需要再送 可〇 共同電庫之 生理信號可 共用參考電 超低電阻的 地球當作共 透過共用地 地球當作零 以電力公司 要求該建築 當作零參考 座至少是兩 另一孔是建 一條地線到 零參考 以互相 庫是地 銅線稱 用參考 線接到 參考電 把高電 物和電 電位作 孔，一 築物的 建築物 電位的電 進行運算 球本 為共 電庫 建築 位來 壓的 力公 為電 孔是 共用 ，只 身， 用地 ，也 物内 作彼 電力 司都 力傳 電力 地 要送 古使電器設傷正常操作的是電流， 内流動所造成的，所以電源供應是將 電位’讓電子可以流入電器設備，推 讓電器正常操作的電子流動稱為電流 遇知為正電荷的流動，但後來發現是 動’兩者的流動方向正好相反，因為 係L所以市電送來吸引電子的高壓， 底流入到電器，再由電器流到火線， 電力公司，才把這電子流送回地底， 而電流是電子在導 電子從低電位送到 動其正常操作。這 。這股電流剛開始 負電荷的電子在流 電荷正負相反的關 使電子從建築物的 由火線送到變電站 達到一個完整的電^ 3735 • Description of the invention (1) The present invention refers to the measurement of electrodes. Press, in the world-like building 1: winter common ground wire 疋 treat the earth as some electrical appliances, 2 electric potential or electric wire is sent to the circuit of the common ground wire to the wheel. In addition, in the company's power supply wiring, the hot line of public power is; urgently, with the premises line, from a human body to various types of electricity that are commonly used on the electricity, there must be one into the ground, zero reference Potential, all appliances are compared by voltage. All buildings, and the ground, take the point of insertion in the earth's buildings as the line of fire. The company does not need to send the physiological signal of the common electricity bank. The reference electric ultra-low-resistance earth can be shared by the common ground. The earth is regarded as zero. The power company requires the building to be used as a zero reference seat. At least two other holes are to build a ground wire to the zero reference to store each other. The copper wire is called a reference wire connected to the reference power, and high-electricity objects and electric potentials are used as holes. The calculation of the electric potential of a building's building potential is originally a force that is pressed by the common electric storage building position. The electric holes are shared, single, land, and also used as electricity within the object. The normal operation of electrical appliances is caused by the current and internal flow, so the power supply is a potential that allows electrons to flow into electrical equipment, and the flow of electrons that allows electrical appliances to operate normally is called the flow of positive charge when the current is encountered, but then It is found that the flow direction of the two is exactly the opposite. Because it is L, the mains power sends high voltage to attract electrons, which flows into the appliance at the end, and then flows from the appliance to Line, power companies, before this electron flow back to the bottom, while the current is the electrons in the conduction electrons move from the low potential to its normal operation. This . At the beginning of this current, the negatively charged electrons are flowing. The positive and negative charges are reversed, so that the electrons from the building are sent from the hot wire to the substation to reach a complete electricity.
第5頁 553735 五、發明說明（2) =路：才能”器正常的操作。由於地球是 'i可的電量對地球而言是相當微小= ，電流回路。|作為所有電器設備的共同零參考電位 之丄ΪΓ也或電源而言，其電壓^是指正端和負端 ♦ 3 ϊ ΐ ί 1兩個*電、池或電源供應電力的電器或電路 =做=。對一般有插頭而利用市電的電器或 彼I之Si地球當做共用w而作a零電位參考，所以 身成為二』：ί可以互相比較。然而對電池而言，是以本 2電子回路，、就是一個電子從電池本身送出去， 電子回，，才能完成-個電==電 電庫和零參考電：電：無法接觸地面，不能以地球當共用 或電子產所以兩個電池所負責供應電力的電路 ^ 的電位或電壓是無法比較的。 所供應Ξ雷ί們的認知是不可能把兩個分別來自不同電池 明，：第一圖=電壓拿來作比較。以心電圖當範例來說 電位向量圖^不，係心電圖中三個肢導（ι，π，πι)的 線，分別:ξ’ι里測心電圖最基本的架構是要連接四條電 終=::電極（V2)、左手電極⑴）、左腳電極 運動而產生的雷電極（Vrei )，從不同身體位置去量測心臟 人體的電庫和地ί:右腳參考電極(U是將 參考電位，朴4電枝線相接，以達到兩者相同的零 為其他三個電極相互比較的基礎。而心電圖 第6頁 553735 五、發明說明（3) 的產生如第一圖所示，三個肢導分別是： I = V1 - V 2 II = V3 - V2Page 5 553735 V. Description of the invention (2) = Road: ability "The normal operation of the device. Since the earth's electricity can be quite small for the earth =, the current loop. | As a common zero reference for all electrical equipment Potential 丄 ΪΓ is also referred to as a power source. Its voltage ^ refers to the positive and negative terminals. ♦ 3 ϊ ΐ ί 1 * Two electrical appliances or circuits that supply electricity with electricity, pools, or power sources = do =. For the general use of plugs and use of commercial power The electric appliances or the Si earth of the other two are regarded as a common w and are used as a zero potential reference, so they can be compared to each other. Ί can be compared with each other. However, for batteries, this is the 2 electronic circuit, that is, an electron is sent from the battery itself. It can be completed by going out and returning electronically. -Electricity == Electric storage and zero reference electricity: Electricity: Cannot touch the ground, cannot be used by the earth as a common or electronic product. So the potential or voltage of the circuit supplied by the two batteries is It is impossible to compare. The cognition of the supplied Ξ 雷 ί is that it is impossible to compare the two from different batteries: the first picture = voltage for comparison. Taking the electrocardiogram as an example, the potential vector diagram ^ No, it is the electrocardiogram three Limb lead (ι, π, π) lines, respectively: The most basic structure of an electrocardiogram in ξ'ι is to connect four electrical terminals = :: electrode (V2), left-hand electrode ⑴, and left foot electrode movement Lightning electrode (Vrei), to measure the electrical body and ground of the heart and human body from different body positions: the right foot reference electrode (U is the reference potential, Park 4 electric branches are connected to achieve the same zero for the other as the other The basis for the three electrodes to compare with each other. ECG page 6 553735 V. Description of the invention (3) As shown in the first figure, the three limb guides are: I = V1-V 2 II = V3-V2
III = V3 - VIIII = V3-VI
從這三個肢導（I，π，11 I )可以看出心臟的運轉是否 正常，其中心電圖含有P、Q、R、S、T波等等，是屬專業 領域，不做說明。由於心電圖的產生必須要有參考電極來 作為各電極的零參考電位，才能進行各電極電位之間的運 算而得到心電圖，因而造成無線心電圖有其發展的瓶頸。 從國際期刊找尋很多論文（請查IΕΕΕ期刊）和搜尋許多相 關專利（譬如美國〜專利號碼第5862 803的Wire less Medical Dignosis and Monitoring Equipment )都需要 將參考電極放在右腳或右下方才能進行生理信號的無線傳 輸。這也是目前市售的無線心電圖（見第立圖，是一般市 售之無線心電圖機），都是利用一個無線電路盒一1 〇拉出 四條電極線（VI、V2、V^、Vref )安裝在人體四肢（見第 二圖），電極量測到的信號再透過無線電傳輸到心電圖機 2 Q把心電圖顯示出來。這樣的無線心電圖已經可以讓病 人四處走動，但身體仍然要佈滿電線，尤其還要量測胸腔 位置的心電圖時，電線就更多，相當不方便。 i 鑑於以上所述，本發明為解決這些電線的拘絆， 人體為共用電庫之電極所形成的無線心電圖的構相 如第四圖，本發明之無線心電圖的構想），其中，v 1 工手電極，V2指右手電極、V3指左腳電極，其中V1和” ^From these three limb guides (I, π, 11 I), it can be seen whether the heart is functioning normally, and its central electrogram contains P, Q, R, S, T waves, etc. It belongs to the professional field and will not be explained. Since the generation of the electrocardiogram requires a reference electrode as the zero reference potential of each electrode, the calculation between the electrode potentials can be used to obtain the electrocardiogram, which has caused the bottleneck of its development. Finding many papers from international journals (please check the IEEE journals) and searching for many related patents (such as Wire less Medical Dignosis and Monitoring Equipment of the United States ~ Patent No. 5862 803) require the reference electrode to be placed on the right foot or lower right to perform physiology Wireless transmission of signals. This is also the current commercially available wireless electrocardiogram (see the third figure, which is a general commercially available wireless electrocardiograph), which uses a wireless circuit box 10 to pull out four electrode wires (VI, V2, V ^, Vref) for installation In the human limbs (see the second picture), the signals measured by the electrodes are transmitted to the electrocardiograph 2Q by radio and the electrocardiogram is displayed. Such a wireless electrocardiogram can already allow patients to move around, but the body still needs to be covered with electrical wires, especially when measuring the electrocardiogram at the position of the chest cavity, there are more electrical wires, which is quite inconvenient. In view of the above, in order to solve the problems of these wires in the present invention, the structure of the wireless electrocardiogram formed by the human body as the electrodes of the shared power bank is as shown in the fourth figure, the concept of the wireless electrocardiogram of the present invention), where v 1 Hand electrode, V2 refers to the right hand electrode, V3 refers to the left foot electrode, where V1 and "^
第7頁 553735 五、發明說明（4) 一條鬆緊帶1 〇 〇固定在胸腔，而V 3和心電圖電路則用另外 —條鬆緊帶1 0 0固定在腰部，兩條鬆緊帶1 〇 〇之間則有一條 彈性電線2 0 0相連，使V 1和V2信號可以接到心電圖電路， 產生心電圖，再用無線電傳輸出去。注意第四圖中並沒有 特別提到參考電極，這會在下列作驗證說明。我們進行如 第五圖的實驗（第五圖是無線心電圖，其中每個電極電路 、都用不同的電池VB1〜VB涞供應電源），其中T1指無線傳送 _電路，E 1指電極電路（由緩衝放大器形成），E2指心電圖 電路（由差動放大器形成）。各電極電壓在第一級差動放 器作相減，分別得到A1A2(V卜Vref)和A1A2(V2-Vref)，目 的是要讓V 1和V2能以V ref當零參考電位，最後一級的差動 放大器輸出心電圖的第I肢導 其中 增益。結 片。把第 取代，或 I，兩者 一直無法 是以 零參考電 訊號的量 電庫，利 電極能有 =G[(V1 -Vref) - (Ύ2 -Vref) ] = G(V1 - V2) G = A 1 A 2 A 3是A 1放大器和a 2、A 3差動放大器的總 果在示波器上看不到任何心電圖，只有雜訊一 五圖的Vre在E2心電圖電路端，用電源％鉤地線 者只用一個差動放大器讓¥1和V2直接相減來得 的結果仍然是雜訊一片，這也是至今無線心電 改進的主因。 ， ’本發明最重要的創見是如何使各電極有共 位且有完整的電流迴路，而使電極可以進行生理 測。本發提出之技術手段係以人體當共用參 用一般電器以地球當共用參考電庫的原理，使各 共同的零參考電位’且提供完整的電流迴路。解Page 7 553735 V. Description of the invention (4) An elastic band 100 is fixed in the chest cavity, while V 3 and the electrocardiogram circuit are fixed with another one elastic band 100 at the waist, and one between the two elastic bands 100 The flexible wires 2 0 are connected so that the V 1 and V 2 signals can be connected to the ECG circuit to generate an ECG and then transmit it by radio. Note that the reference electrode is not specifically mentioned in the fourth figure, which will be verified in the following. We perform the experiment as shown in the fifth figure (the fifth figure is a wireless electrocardiogram, in which each electrode circuit uses a different battery VB1 ~ VB 涞 to supply power), where T1 refers to the wireless transmission circuit and E 1 refers to the electrode circuit (by The buffer amplifier is formed), E2 refers to the electrocardiogram circuit (formed by a differential amplifier). The voltage of each electrode is subtracted from the first stage differential amplifier to obtain A1A2 (V and Vref) and A1A2 (V2-Vref) respectively. The purpose is to make V 1 and V2 use V ref as the zero reference potential. The differential amplifier outputs the gain of the first limb of the electrocardiogram. Pieces. Substituting or I, the two have not been able to use the zero-reference signal measuring library, the electrode can have = G [(V1 -Vref)-(Ύ2 -Vref)] = G (V1-V2) G = A 1 A 2 A 3 is the total result of A 1 amplifier and a 2, A 3 differential amplifier. I can't see any ECG on the oscilloscope. Only Vre of Noise One or Five is on the E2 ECG circuit end. The result of using only a differential amplifier to directly subtract ¥ 1 and V2 is still noise, which is the main reason for the improvement of wireless ECG so far. "The most important idea of the present invention is how to make the electrodes have a common and complete current loop, so that the electrodes can be measured physiologically. The technical means proposed by the present invention is based on the principle that the human body is used as a common reference and the earth is used as a common reference library, so that each common zero reference potential is provided and a complete current loop is provided. solution
^^735 五、發明說明（5) I決前述技術障礙之手段主要 ' 共用端接觸身體任何部位以各電極上的電池之負端或 電極可以藉由人體電庫擁有‘所謂的共用電#，造成各 極提供給各電極形成完整的^、i參考電位，且藉由共用電 號。在運用上，也可以用—迴路而得以擷取電生理信 電源的負端或共用端接觸身:電源供給各電極，而把這個 |可以達成前述相同的功用。|壬何部份形成共用電極，也 故可知本發明之最 |電極之共同參考電庫的用二2在於提供一種以人體為各 理訊號的量測，而可用、電極，而使各電極可以進行生 |礙。 ^於解決現有無線心電圖之技術障 以下便就本於日日 |說明。 X 斤採用之技術手段，舉出實施例予以 I用」本用：人體為共用電庫的共用電極及其應 極、放大電：、ί:的無線心電圖，其基本架構包含電 |其中： 電源供應、差動放大器、無線傳輸電路， I的金屬把、^用以感測電位或電壓的元件，其材質從簡單 雷 ’艮加銀化氯混合物，到複雜的半導體製程之微 |電極與微移液管（micropipet)電極等等皆可。 |大放大電路’是有高輸入卩且抗和高增益的電路，用來放 極感2的微弱電信號，以利後續的信號處理。 電源供應’是電池、太陽能電源、或其可供電力給放 态、無線傳輪電路的能源。^^ 735 V. Explanation of the invention (5) The means to resolve the aforementioned technical obstacles are mainly that the common terminal contacts any part of the body, and the negative terminal of the battery on each electrode or the electrode can have the so-called common electricity # through the human body's library. As a result, each electrode is provided to each electrode to form a complete reference potential i and i, and a common electric number is used. In application, you can also use the loop to capture the electrophysiological signal. The negative or common terminal of the power supply contacts the body: the power supply is supplied to each electrode, and this can achieve the same function as described above. | Which part forms the common electrode, so we can know the most of the present invention. The common reference of the electrode library is to provide a measurement using the human body as the physical signal, and the electrodes can be used, so that each electrode can be used. Progressive | hinder. ^ To solve the technical obstacles of the existing wireless ECG The technical methods used by X Jin are listed in the examples and used for the purpose. "Intended use: The human body is a common electrode of a shared power bank and its stress, and amplifying the wireless electrocardiogram. Its basic structure includes electricity | of which: power supply Supply, differential amplifiers, wireless transmission circuits, I metal handles, and components used to sense potentials or voltages, from materials ranging from simple thorium and silver chloride mixtures to complex semiconductor process micro | electrodes and micro Micropipet electrodes and the like can be used. | Large amplifier circuit 'is a circuit with high input chirp, high impedance, and high gain. It is used to amplify the weak electric signal of pole 2 to facilitate subsequent signal processing. The power supply 'is a battery, a solar power source, or an energy source that can be used to supply power to a stateless, wireless transmission circuit.
第9頁 553735 五、發明說明（6) 差動放大 號。 無線傳輸 送出去。無線 式，若為數位 電路，把類比 輸。 而本發明 端或共用端相 k寻各電極以人 額外的參考電 電極感測信號 ，亦可以用 端或共用端接 供給各量測電 信號。 另外，可 自動增益控制 濾波器， 去除，以增 雜訊消除 雜訊去除，以 自動增益 的輸出電壓範 器，是把兩電極電壓相減，以形成心電圖信 電路，是把電極量測到的信號用無線方式傳 傳輸電路之無線傳輸方式可為數位式和類比 式，則需要在放大電路之後用類比數位轉換 信號轉換成數位信號，以進行數位無線傳 之主要創意在於：每個電極的獨立電源之負 連接於人體電庫，形成所謂的共用電極，使 體電庫當作共同的零參考電位，而不再需要 極，就可以提供足夠的電流迴路，而可進行 之間的運算與處理，以得到電生理資訊；當 單一電源供應各電極的電力，而讓電源的負 觸人體的共用電庫，形成單一共用電極，提 極作為電流迴路之用，以得到準確的電生理 增設包含輔助電路如濾波器、雜訊消除器、 、信號處理技術等，其中： 是把一些不屬於電生理信號頻率範圍内的雜 加信號雜訊比。 器，是把一些屬於電生理信號頻率範圍内的 增加信號雜訊比。 控制，是自動控制放大器的增益，使放大器 圍符合無線傳輸電路的規範。Page 9 553735 V. Description of the invention (6) Differential amplification. Wireless transmission Wireless, if it is a digital circuit, the analog input. In the present invention, the terminal or common terminal is used to search each electrode to sense the signal by using an extra reference electrode, and the terminal or the common terminal can also be used to supply various measurement electric signals. In addition, the automatic gain control filter can be removed to increase noise and eliminate noise. The output voltage ranger with automatic gain is to subtract the two electrode voltages to form an ECG signal circuit. The electrodes are measured. The wireless transmission method of signal transmission circuit can be digital and analog. You need to use analog digital conversion signal to convert the digital signal after the amplification circuit. The main idea of digital wireless transmission is that each electrode is independent The negative side of the power supply is connected to the human body's electricity bank, forming a so-called common electrode, so that the body electricity bank can be regarded as a common zero reference potential, without the need for poles, it can provide sufficient current loops, and can perform calculations and processing between them. In order to obtain electrophysiological information; when a single power supply supplies the power of each electrode, and the negative of the power supply contacts the common electricity bank of the human body, a single common electrode is formed, and the electrode is used as a current loop to obtain accurate electrophysiological additions including assistance Circuits such as filters, noise cancellers, signal processing technologies, etc., where: Heteroaryl signal plus noise ratio within the signal frequency range. The device is to increase the signal-to-noise ratio within the frequency range of the electrophysiological signal. Control is to automatically control the gain of the amplifier so that the amplifier range meets the specifications of the wireless transmission circuit.
第10頁 553735 五、發明說明（7) 信號雜訊：增Ϊ :讓：：U :信號的軟硬體技術，使得 、 曰八和讓無線傳輸更容易。 思的：i心ί ΐ:施例如第六圖所示（第六圖係本發明構 庳，i1 &回為，其中把各電極的獨立電源接通人體電 犀，使得各無線電極 书T饮艰八m电 體電庫，产主有/、同的零參考電位），其中B指人 放大，而^右手，M、A2分別為放大器和差動 vre/作把各電電路E1部份，⑨有如第五圖的參考電極 近的身一=位\上的R)電池^負:也別連接各 θί雜考電位。由於人體大部份是電解液，是個 良導體，/、有皮膚阻抗稍大，人體内整個 電量，對各電極所需電*，簡直可說是無窮大t很大的 為說明更清楚，第七圖 >、顯示第六圖的電極部份 七圖係本發明之無線心電圖的電路模擬圖），並且加弟 池和人體電庫B之間的阻抗（以和R2, R1指左手阻抗σ，上電 指右手阻抗），而成為一個完整的模擬電路圖。每~個R2 器經由迴授控制後，其輸入阻抗相當大約丨〇 〇 ，—大 電圖的電壓約2mV，所以造成又體大約有〇. 02pA(1() 12又心 Ampere)的電流流入放大器A1，若要造成迴路，此2〇pA 流需要透過電池流回人體，才能完成以人體電庫B為$ ^ 考電位的完整迴路。在這完整迴路當中，唯一阻梏 / 坑的疋阻 抗R1或R2。一般電極和皮膚接觸的阻抗一定在1 〇 ΚΩ以 下，以0· 02ρΑ的迴路電流，造成R1或R2上的電壓只有 0.2nV(101〇US)，相對于電池電壓（i.5V以上/和電極Page 10 553735 V. Description of the invention (7) Signal noise: Zengjiao: Let :: U: The hardware and software technology of the signal makes wireless transmission easier. Thinking: i heart ΐ 施: The example is shown in the sixth figure (the sixth figure is the structure of the present invention, i1 & return is, in which the independent power of each electrode is connected to the human body, so that each wireless electrode book T The electric power bank is 8m, the owner has the same zero reference potential), where B refers to the person's amplification, and ^ the right hand, M, A2 are the amplifier and the differential vre, respectively, each part of the electrical circuit E1 As shown in the fifth figure, the reference electrode is close to the body of the battery. Negative: Don't connect each θ miscellaneous test potential. Since most of the human body is an electrolyte, it is a good conductor, and it has a slightly larger skin impedance. The entire amount of electricity in the human body, the electricity required for each electrode *, can be said to be infinite. T is clearer for illustration. Figure > The seventh part of the electrode part showing the sixth figure is a circuit simulation diagram of the wireless electrocardiogram of the present invention), and the impedance between Gaddy's Pool and the human body bank B (with R2, R1 refers to the left-hand impedance σ, Power-up refers to the right-hand impedance), and it becomes a complete analog circuit diagram. After each R2 device is controlled by feedback, its input impedance is about 丨 〇〇, the voltage of the large electric diagram is about 2mV, so the current of about 0.02pA (1 () 12 and Ampere) flows into the body. If the amplifier A1 is to cause a loop, this 20 pA current needs to flow back to the human body through the battery, in order to complete the complete loop with the human body bank B as the $ ^ test potential. In this complete circuit, the only impedance / pit impedance is R1 or R2. In general, the impedance between the electrode and the skin must be below 10 κΩ, and the loop current of 0.02ρΑ, resulting in a voltage of only 0.2nV (101〇US) on R1 or R2, relative to the battery voltage (above i.5V / and electrode
第11頁 553735 五、發明說明（8) 電壓2 mV (1 0 _3Vol ts)而言，是絕對可以忽略不計的。所 以各電池和電極與人體電庫之間可以有完整的電流迴路， ，使得各電池和電極電壓有共同的零參考電位，結果各電極 電壓才可進行運算與處理，而得到有意義的電生理資訊。 因為對2 Ο p A而言，人體電庫是毫無匱乏的供應，猶如地球 電庫供應全球電器產品一樣的容易。 第八圖是示波器上顯示第I肢導V的結果：其中（a) 是第五圖的結果；（b)是第五圖中，去掉參考電極，直 接用心電圖電路上的電池V B共用端連接到放大器A 2的負 端；（c)是第六圖用人體電庫當零參考電位；（d)是第 六圖中，去掉人體電庫，只有將兩電池的負端連接在一 起；（e)是第六圖中，把兩電池的負端先連接後形成共 用端，再用共用端去接觸人體電庫，形成所謂的共用電 極。結果事實證明，沒有以人體電庫當零參考電位的設 計，是無法進行心電圖的量測，所以第八圖（a) 、 ( b) 只有6 Ο Η z的雜訊（因為實驗電路相當簡單，沒有進行雜訊 消除），而沒有任何心電信號。而第八圖（d)有些電容 充放電的信號夾雜著6 Ο Η z的市電雜訊，這是因為把電池的 負端接在一起，雖然兩個電極有共同的零參考電位，但是 _人體從放大Is輸入的電子流卻無法流回人體而產生完整的 迴路。因此雖然兩電極有共同的零參考電位，但卻無完整 的電流迴路，仍然是無法進行正確的電生理訊號的暈測。 第八圖（d)的充放電信號是因為兩電池負端相接點透過 鱼氣，有小雜散電容與人體電庫相接，所以在信號高頻時Page 11 553735 V. Description of the invention (8) The voltage of 2 mV (1 0 _3Vol ts) is absolutely negligible. Therefore, there can be a complete current loop between each battery and electrode and the human body's electrical library, so that each battery and electrode voltage have a common zero reference potential. As a result, each electrode voltage can be calculated and processed to obtain meaningful electrophysiological information. . Because for 2 0 p A, the human body electricity bank is a supply without shortage, just as the earth electricity bank supplies global electrical products as easily. The eighth figure is the result of the first limb V displayed on the oscilloscope: (a) is the result of the fifth figure; (b) is the fifth figure, with the reference electrode removed, and directly connected to the common terminal of the battery VB on the ECG circuit To the negative terminal of amplifier A 2; (c) is the sixth figure using the human body battery as the zero reference potential; (d) is the sixth picture, removing the human body battery, only the negative terminals of the two batteries are connected together; e) In the sixth figure, the negative terminals of the two batteries are connected first to form a common terminal, and then the common terminal is used to contact the human body electrical library to form a so-called common electrode. It turns out that it is impossible to measure the ECG without the design of the human body as a zero reference potential, so the eighth graph (a) and (b) only have noise of 6 Η 的 z (because the experimental circuit is quite simple, No noise cancellation is performed) without any ECG signal. In the eighth figure (d), some capacitor charging and discharging signals are mixed with 6 杂 Η z mains noise. This is because the negative terminals of the battery are connected together. Although the two electrodes have a common zero reference potential, The electron flow input from the amplified Is cannot flow back to the human body to produce a complete circuit. Therefore, although the two electrodes have a common zero reference potential, there is no complete current loop, and it is still impossible to perform a corona measurement of the correct electrophysiological signal. The charge-discharge signal of the eighth figure (d) is because the negative contact point of the two batteries passes through the fish gas, and there is a small stray capacitor connected to the human body's power bank.
第12頁 553735 五、發明說明（9) (即心電圖的QRS波），電容的阻抗變小，造成一短暫的 完整迴路，才會有信號突波出現又隨即不見，而產生充放 電的現象。然而這充放電現象不會發生在第八圖之（a) 和（b)，因為兩者沒有共同零參考電位，所以只有60Hz 的雜訊存在。有完整的電流迴路的是第八圖之（c)和（e )，兩者皆以人體電庫當零參考電位且有完整電流迴路， 所以可以進行心電信號的運算與處理而得到心電圖。注意 看第八圖之（c)和（e)，可以發現P、QRS' T波，其中 以QRS和T波較明顯。以上的實驗足以證明第六圖的電極電 路設計是正確的，而人體電庫的容量相當龐大，足可當零 參考電位，且皮膚阻抗不足以影響零參考電位的形成。第 九圖是第八圖之（c)和（e)中，把60Hz雜訊消除的結 果，可清楚的看出心電圖中的P、Q、R、S、T波。 根據上述用實驗去證明理論推導的正確性，供應電極 電路的電源之負端或共用端去接觸人體電庫，各電極彼此 之間就有共同的零參考電位且提供電流迴路，作為電生理 資訊的量測，其應用領域相當廣泛，舉凡心電圖（ECG )、肌電圖（EMG)、眼電圖（EOG)、腦波圖（EEG)等 生理信號圖。 根據上述的理論與實驗證明運用電源的負端或共用端 接觸人體，形成所謂的共用電極，提供電生理信號的電流 迴路，以完成正確的量測技術是本發明的重點。根據這項 重點，再大膽進行下列實驗如第十圖〜第十四圖所示。第 十圖是第六圖的實際電路安裝，A1是電極放大電路，增益Page 12 553735 V. Description of the invention (9) (ie, QRS wave of the electrocardiogram), the impedance of the capacitor becomes small, resulting in a short complete circuit, and then a signal surge will appear and then disappear, which will cause the phenomenon of charging and discharging. However, this charging and discharging phenomenon does not occur in (a) and (b) of the eighth figure, because there is no common zero reference potential, so only 60Hz noise exists. The complete current loop is shown in (c) and (e) of the eighth figure, both of which use the human body's electric bank as the zero reference potential and have a complete current loop, so the ECG signals can be calculated and processed to obtain the ECG. Note Looking at Figure 8 (c) and (e), we can find P and QRS 'T waves, among which QRS and T waves are more obvious. The above experiments are sufficient to prove that the electrode circuit design of the sixth figure is correct, and the capacity of the human body library is quite large, which can be used as the zero reference potential, and the skin impedance is not enough to affect the formation of the zero reference potential. The ninth graph is the result of eliminating the 60Hz noise in (c) and (e) of the eighth graph, and the P, Q, R, S, and T waves in the ECG can be clearly seen. According to the above experiments to prove the correctness of the theoretical derivation, the negative or common end of the power supply to the electrode circuit contacts the human body's electrical library, and each electrode has a common zero reference potential and provides a current loop as electrophysiological information. Its measurement has a wide range of application fields, such as electrocardiogram (ECG), electromyogram (EMG), electrooculogram (EOG), and electroencephalogram (EEG). According to the above-mentioned theory and experiment, it is proved that using the negative terminal or the common terminal of the power source to contact the human body to form a so-called common electrode to provide a current loop for electrophysiological signals to complete a correct measurement technique is the focus of the present invention. Based on this emphasis, the following experiments are boldly performed as shown in Figures 10 to 14. The tenth figure is the actual circuit installation of the sixth figure, A1 is the electrode amplifier circuit, the gain
553735 五、發明說明（10) 是篆；A 2是差動放大器，A 3是簡單的2階濾波器，·單一電源 用兩個9伏特的電池形成正負電與〆個共用蠕（c〇m)°第十 圖〜第十一圖的電極擺放位置和/般心電圖最大的不同是 將電極^放在胸腔或腰部的左右雨側’而不是左右手。第十 二圖和第十西圖更把電源共用端放在左右兩電極之間，去 接觸人體以形成共用電極，這和傳統心電圖一定要把參考 電極放在右腳或右下方來進行生理量測，有非常大的不 同。若沒有前述理論與實驗證明，則無法進行如此創新實 ▲驗。實驗結果完全支持本發明的重點，第十一圖和第十二 鐺hi由於沒有共用電極提供完整的迴路，就和第八圖（d)得 到相同的結果，只可看到QRg波所形成的脈衝，這也是一 般市售知名的POLAR無線心跳測速器無法用來量測心電圖 的主因·，而第十三圖和第十四圖玎以明顯且準確地量測出 第Ϊ肢導的心電圖，只是第十四圖的電極離開心臟稍遠， 〜電圖彳§號稍弱而造成信號雜訊比相對地小，不過只要使 甩相當不錯的濾波及雜訊消除技術就可以得到心電 圖。我們曾經把共用電極隨意接觸人體的任= 2心電信號仍然如第十三（b)圖和第十四付」 性。根據第十三圖和第十四 的 方式，可以用一條鬆緊帶彳一 ^ ^ }梆成條直線的 ^ ^ ▼ 1 ϋ 0將二個電極串在一去已，丄 無線傳輸，就可形成帶狀式的無線 串在（加上 =腰部之間（：第十五圖所示在胸 電極’其右手侧為右側量測電極，左手；側個553735 V. Description of the invention (10) is 篆; A 2 is a differential amplifier, A 3 is a simple second-order filter. · A single power supply uses two 9-volt batteries to form positive and negative electricity and one common creep (c0m). ) ° The biggest difference between the electrode placement position and the general ECG in the tenth to eleventh pictures is that the electrodes are placed on the left and right rain sides of the chest or waist, instead of the left and right hands. In the twelfth figure and the tenth west figure, the common end of the power supply is placed between the left and right electrodes to contact the human body to form a common electrode. This and the traditional electrocardiogram must place the reference electrode on the right foot or the lower right to perform physiological measurements. Test, there are very big differences. Without the foregoing theoretical and experimental proof, such an innovative experiment cannot be performed. The experimental results fully support the focus of the present invention. Since there is no common electrode to provide a complete circuit in the eleventh and twelfth hi, the same results are obtained as in the eighth (d). Only the QRg wave can be seen. Pulse, which is also the main reason why the well-known POLAR wireless heart rate monitors cannot be used to measure the ECG, and the 13th and 14th figures 明显 clearly and accurately measure the ECG of the second limb. The electrodes in Figure 14 are a little farther away from the heart. The signal of the electrogram 彳 § is slightly weaker, which causes the signal noise to be relatively small. However, as long as the filtering and noise cancellation techniques are quite good, the ECG can be obtained. We used to let the common electrode randomly contact the human body = 2 The ECG signal is still as shown in Figure 13 (b) and Figure 14. According to the methods of the thirteenth figure and the fourteenth, an elastic band can be used 彳 ^ ^} 梆 to form a straight line ^ ^ ▼ 1 ϋ 0 The two electrodes are stringed together and 丄 wirelessly transmitted to form a band The shape of the wireless string is between (plus = between the waist (: shown on the fifteenth figure on the chest electrode 'the right-hand side is the right-hand measuring electrode, the left-hand side; the side
Ιΐ4 頁 二 —--ί 553735 五、發明說明（11) 極，而中間者為共用電極，以作為心電圖的量測與監控， 尤其以放在腰間最為適合，不但可有醫療用途，又可以用V 在健身和運動訓練上，比市售只提供心跳速率的用途更加 廣泛。更對老人社會的居家保健，提供更舒暢的心臟監控 與訓練！第十六圖是根據第十三圖和第十四圖驗證而發展 的完整無線心電圖量測，不但可以量測三個肢導，又可量 測各方位的胸導（chest lead)。第十六圖仿造第四圖只用 二個鬆緊帶1 0 0分別固定在胸腔和腰部，兩鬆緊帶1 0 0之間 有一條彈性電線2 0 0作為電源供應及電極信號集中在無線 主機盒之用，以進行心電圖運算及無線傳輸，某中胸腔處 鬆緊帶1 0 0之右手側為右手電極，左手側為左手電極，腰 部鬆緊帶1 0 0之左腳側為左腳電極，而中間處則為共用電 極、電源、心電圖電路及無線發射電路，可置放在任何地 方。第十七圖是三個肢導及胸導的心電圖信號，完全相同 於市售心電圖機所量測到的信號，只是雜訊信號大些，因 為這裡尚未使用雜訊消除技術和較好的濾波器。 根據第十二圖和苐十四圖的運用，本共用電極的技術 亦可使用於手握式的健身或運動訓練的設備上。譬如騎腳 踏車的左右手把各安裝量測電極去測量第I肢導心電圖， 而共用電極可以只一個放在左手或右手量測電極旁，或者 為了美觀，也可以左右手各放一個共用電極於量測電極 旁，讓雙手可以同時握住量測電極和共用電極，就可如同 第十三圖和第十四圖一樣，測得第I肢導心電圖。 另外，為了使本發明範例的無線心電圖之外觀一體成Ιΐ4 Page 2—ί 553735 V. Description of the invention (11) pole, and the middle electrode is the common electrode, which is used for ECG measurement and monitoring, especially for the waist. It is not only suitable for medical use, but also Using V for fitness and sports training is more versatile than commercially available only heart rate. Provide more comfortable heart monitoring and training for the home health of the elderly society! Figure 16 is a complete wireless electrocardiogram measurement developed based on the verification of Figures 13 and 14. It can measure not only three limb leads, but also chest leads in all positions. Figure 16 is a copy of Figure 4. Only two elastic bands 100 are fixed to the chest cavity and waist respectively. There is an elastic wire 2 0 between the two elastic bands 100 as the power supply and the electrode signals are concentrated in the wireless host box. In order to perform ECG calculation and wireless transmission, the right-hand side of the elastic band 100 in the middle chest is the right-hand electrode, the left-hand side is the left-hand electrode, the left-foot side of the waist-elastic band 100 is the left-foot electrode, and the middle is shared The electrodes, power supply, ECG circuit and wireless transmitting circuit can be placed anywhere. The seventeenth figure is the ECG signals of the three limb guides and chest guides, which are exactly the same as those measured by commercially available ECG machines, except that the noise signal is larger because the noise cancellation technology and better filtering have not been used here. Device. According to the application of the twelfth figure and the twenty-fourth figure, the technology of the common electrode can also be used in hand-held fitness or sports training equipment. For example, the left and right hands of a bicyclist can measure the electrocardiogram of the first limb with each of the measurement electrodes installed, and the common electrode can be placed next to the left or right hand measurement electrode, or for the sake of aesthetics, one common electrode can be placed in the left and right hand for measurement. Next to the electrodes, let both hands hold the measuring electrode and the common electrode at the same time, as in the thirteenth and fourteenth pictures, the ECG of the first limb can be measured. In addition, in order to integrate the appearance of the wireless electrocardiogram of the example of the present invention into one,
第15頁 553735 五、發明說明（12) 型，可將量測電路（即放大器）和無，線傳輸電路用1(：(積 體電路）技術製造，以達到小型化之目標，又其傳輸功率 ，和距離只要1 0公尺以内即可，以減輕電池電力消耗的速 度。一般而言，量測I C電路的消耗電流約1 m a以下，無線 傳輸1C的消耗電流約1mA ( 1〇公尺以内），以3〇〇mA χ h〇ur 的薄膜電池來說，可連續操作達1 5 0小時，相當實用。又 若要進行遠距離傳輸’可以用中繼站的方式，無線電極以 小功率在10公尺内傳送給中繼站，再由中繼站满給遠處的 *生理信號監視器，以作遠端監控。在應用方面，可以製作 手錶型無線心電圖顯示裝置’以利使用者隨時監控自己的 心跳速度或心臟運轉狀況，也可裝上專家系統的病情分 析，給使用者作出初步建議，或發出警示訊號。另亦可製 作中繼站女裝在身體或身體附近，可藉中繼站作長距離發 f，進行遠端監控，如中繼站可利用現代的行動電話通訊 曰曰片。至於無線傳輸技術可用熟知習用的低頻載波通訊 (=40MHz〜900MHz)、或微波載波通訊（1GHz以上）、 =最新的藍芽通訊名通訊網路科技都可以，但此不是本發Page 15 553735 V. Description of the invention (12) type, can measure circuit (ie amplifier) and non-line transmission circuit using 1 (: (integrated circuit) technology to manufacture, to achieve the goal of miniaturization, and its transmission The power and distance can be less than 10 meters to reduce the speed of battery power consumption. Generally speaking, the consumption current of IC circuits is less than about 1 ma, and the current consumption of wireless transmission 1C is about 1 mA (10 meters Within), for a 300mA χ h〇ur thin film battery, it can be continuously operated for up to 150 hours, which is quite practical. And for long-distance transmission, you can use a relay station, wireless electrodes with low power at It is transmitted to the relay station within 10 meters, and then the relay station is full to the remote * physiological signal monitor for remote monitoring. In terms of application, a watch-type wireless ECG display device can be made to facilitate users to monitor their heartbeat at any time. Speed or heart movement status, can also be equipped with an expert system for disease analysis, make preliminary recommendations to the user, or issue a warning signal. In addition, a relay station can be made for women to be near or to the body. The relay station is used for long-distance transmission f for remote monitoring. For example, the relay station can use modern mobile phone to communicate with the film. As for the wireless transmission technology, the well-known low frequency carrier communication (= 40MHz ~ 900MHz) or microwave carrier communication (1GHz) can be used. Above), = the latest Bluetooth communication name communication network technology can be used, but this is not the present
丘 術手#又及貫施例之說明，可知本發明是以人體 二二=電庫與共用電極的概念，確使各電極有零參考電位 ^=檀!!電流迴路，而可進行準確地電生理信號的量測及 i測^ ί。以無線心電圖為例，本發明使得無線心電圖的 传相當舒適且容易，本發明配合舒適的固定裝置、 、··等之安裝’使其運用之範圍極廣，涵蓋了醫療儀丘 术 手 # And the description of the embodiment, it can be known that the present invention uses the concept of the human body 22 = electric library and common electrodes to ensure that each electrode has a zero reference potential ^ = Tan !! current loop, and can accurately perform Measurement and measurement of electrophysiological signals ^ ί. Taking wireless electrocardiogram as an example, the present invention makes wireless electrocardiogram transmission quite comfortable and easy. The present invention cooperates with the installation of a comfortable fixing device, ..., etc. to make its application range very wide, covering medical instruments
553735 五、發明說明（13) 器、健身設備、運動訓練設備、復健設備..等等，不勝牧 舉，故使得本發明之發明效用可說極大，而俾於產業界利 用當無問題，且本發明之新穎性具備，及如前所述，其進 步性更無疑問，因此，足以符合發明專利之要件而無庸置 疑0553735 V. Description of the invention (13) devices, fitness equipment, sports training equipment, rehabilitation equipment, etc., are endless, so the utility of the invention of the present invention can be said to be extremely great, and there is no problem when used in the industrial world. Moreover, the novelty of the present invention is provided, and as mentioned above, its progress is more doubtless, so it is sufficient to meet the requirements of the invention patent without doubt. 0
第17頁 553735 圖式簡單說明 圖式 第一 ，量圖。 第二 第三 第四 第五 第六 第七 ’第八 零參考電 號之實驗 第九 第九 第十 第十 及其得到 第十 b意圖。 第十 心電圖信 圖號Page 17 553735 Brief description of the diagram Second third fourth fifth fifth sixth seventh 'eighth zero reference number experiment ninth ninth tenth tenth and getting tenth b intention. Tenth ECG letter No.
說明= 圖係心電圖中三個肢導（I I I、I I I )的電位向 圖係一般 圖係一般 圖係本發 圖係無線 圖係本發 圖係本發 圖（a〜e 位，才能 輔助說明 圖係第八 圖係本發 圖係第六 -—ytj 生理信號 五、十六 市售之無線心電 市售之無線心電 明之無線心電圖 心電圖機之示意 明構思的無線心 明構思之無線電 )係實驗證明各 各電極電壓的運 圖。 圖（c )中 60 Hz 明之無線電極之 圖之實際電路安 圖係本發明之各 之實驗輔助說明 圖係第十三、十 圖機之示意圖。 圖機之實施示意圖。 機的實施構想示意圖。 圖。 電圖機之不意圖。 極的電路模擬圖。 量測電極必須有共同的 算與處理來得到生理信 雜訊被消除後的情形。 一實施例平面結構圖。 裝圖。 安裝實施例示意（a ) (b )圖。 四圖之之實際實施例示 七圖（a〜d )分別係本發明的三個肢導及胸導之 號0 0Explanation = The diagram of the potentials of the three limb guides (III, III) in the electrocardiogram of the graph is a general graph. The general graph is a wireless graph. The wireless graph is a current graph. The eighth diagram is the sixth diagram of this issue. Ytj physiological signals. Five and sixteen commercially available wireless electrocardiograms. Commercially available wireless electrocardiograms. Wireless electrocardiograms. The experiment proves the operation of each electrode voltage. The actual circuit safety of the wireless electrode shown in Figure (c) at 60 Hz is shown in the experimental auxiliary description of the present invention. Figures 13 and 10 are schematic diagrams of the chart machine. The schematic diagram of the implementation of the drawing machine. Schematic diagram of the machine's implementation concept. Illustration. The intention of the electrograph machine. Circuit diagram. The measurement electrodes must have common calculation and processing to get the situation after the physiological signal noise is eliminated. Plan view of an embodiment. Loading map. Installation example (a) (b). The actual illustration of the four pictures The seven pictures (a ~ d) are the numbers of the three limb guides and chest guides of the present invention. 0 0
VI ..無線電路盒 左手電極 2 0 ..心電圖機 V2..右手電極VI: Wireless circuit box Left-hand electrode 2 0: Electrocardiograph V2: Right-hand electrode
第18頁 553735 圖式簡單說明 V 3 ..左腳電極 E 1..電極電路 B..人體電庫 R..右手 A2..差動放大器 R 1..左手阻抗 1 0 0 ..鬆緊帶 T 1..無線傳送電路 E 2 ..心電圖電路 L..左手 A 1..放大器 A 3 ..渡波器 R 2 ..右手阻抗 2 0 0 ..彈性電線Page 18 553735 Simple illustration V 3 .. Left foot electrode E 1. Electrode circuit B. Human body library R. Right hand A2. Differential amplifier R 1. Left hand impedance 1 0 0 .. Elastic band T 1. Wireless transmission circuit E 2 .. ECG circuit L .. Left hand A 1. Amplifier A 3 .. Wavelet R 2 .. Right hand impedance 2 0 0 .. Flexible wire
第19頁Page 19
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| TW091109062ATW553735B (en) | 2002-05-01 | 2002-05-01 | Common electrode using human body as common electric reservoir and application thereof |
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| TW091109062ATW553735B (en) | 2002-05-01 | 2002-05-01 | Common electrode using human body as common electric reservoir and application thereof |
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| TW553735Btrue TW553735B (en) | 2003-09-21 |
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| TW091109062ATW553735B (en) | 2002-05-01 | 2002-05-01 | Common electrode using human body as common electric reservoir and application thereof |
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| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| US8542123B2 (en) | 2008-03-05 | 2013-09-24 | Proteus Digital Health, Inc. | Multi-mode communication ingestible event markers and systems, and methods of using the same |
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| US8545436B2 (en) | 2008-12-15 | 2013-10-01 | Proteus Digital Health, Inc. | Body-associated receiver and method |
| US8547248B2 (en) | 2005-09-01 | 2013-10-01 | Proteus Digital Health, Inc. | Implantable zero-wire communications system |
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| US8718193B2 (en) | 2006-11-20 | 2014-05-06 | Proteus Digital Health, Inc. | Active signal processing personal health signal receivers |
| US8730031B2 (en) | 2005-04-28 | 2014-05-20 | Proteus Digital Health, Inc. | Communication system using an implantable device |
| US8858432B2 (en) | 2007-02-01 | 2014-10-14 | Proteus Digital Health, Inc. | Ingestible event marker systems |
| US8868453B2 (en) | 2009-11-04 | 2014-10-21 | Proteus Digital Health, Inc. | System for supply chain management |
| US8932221B2 (en) | 2007-03-09 | 2015-01-13 | Proteus Digital Health, Inc. | In-body device having a multi-directional transmitter |
| US8945005B2 (en) | 2006-10-25 | 2015-02-03 | Proteus Digital Health, Inc. | Controlled activation ingestible identifier |
| US8956288B2 (en) | 2007-02-14 | 2015-02-17 | Proteus Digital Health, Inc. | In-body power source having high surface area electrode |
| US8956287B2 (en) | 2006-05-02 | 2015-02-17 | Proteus Digital Health, Inc. | Patient customized therapeutic regimens |
| US8961412B2 (en) | 2007-09-25 | 2015-02-24 | Proteus Digital Health, Inc. | In-body device with virtual dipole signal amplification |
| US9014779B2 (en) | 2010-02-01 | 2015-04-21 | Proteus Digital Health, Inc. | Data gathering system |
| US9198608B2 (en) | 2005-04-28 | 2015-12-01 | Proteus Digital Health, Inc. | Communication system incorporated in a container |
| US9235683B2 (en) | 2011-11-09 | 2016-01-12 | Proteus Digital Health, Inc. | Apparatus, system, and method for managing adherence to a regimen |
| US9270503B2 (en) | 2013-09-20 | 2016-02-23 | Proteus Digital Health, Inc. | Methods, devices and systems for receiving and decoding a signal in the presence of noise using slices and warping |
| US9439599B2 (en) | 2011-03-11 | 2016-09-13 | Proteus Digital Health, Inc. | Wearable personal body associated device with various physical configurations |
| US9439566B2 (en) | 2008-12-15 | 2016-09-13 | Proteus Digital Health, Inc. | Re-wearable wireless device |
| US9577864B2 (en) | 2013-09-24 | 2017-02-21 | Proteus Digital Health, Inc. | Method and apparatus for use with received electromagnetic signal at a frequency not known exactly in advance |
| US9603550B2 (en) | 2008-07-08 | 2017-03-28 | Proteus Digital Health, Inc. | State characterization based on multi-variate data fusion techniques |
| US9659423B2 (en) | 2008-12-15 | 2017-05-23 | Proteus Digital Health, Inc. | Personal authentication apparatus system and method |
| US9756874B2 (en) | 2011-07-11 | 2017-09-12 | Proteus Digital Health, Inc. | Masticable ingestible product and communication system therefor |
| US9883819B2 (en) | 2009-01-06 | 2018-02-06 | Proteus Digital Health, Inc. | Ingestion-related biofeedback and personalized medical therapy method and system |
| TWI624256B (en)* | 2015-12-28 | 2018-05-21 | Xie Guo Zhang | Core muscle training electrode clothing |
| US10084880B2 (en) | 2013-11-04 | 2018-09-25 | Proteus Digital Health, Inc. | Social media networking based on physiologic information |
| US10187121B2 (en) | 2016-07-22 | 2019-01-22 | Proteus Digital Health, Inc. | Electromagnetic sensing and detection of ingestible event markers |
| TWI652042B (en) | 2016-03-08 | 2019-03-01 | 財團法人紡織產業綜合研究所 | Electrode for detecting electrical signals from body skin |
| US10223905B2 (en) | 2011-07-21 | 2019-03-05 | Proteus Digital Health, Inc. | Mobile device and system for detection and communication of information received from an ingestible device |
| US10398161B2 (en) | 2014-01-21 | 2019-09-03 | Proteus Digital Heal Th, Inc. | Masticable ingestible product and communication system therefor |
| US10529044B2 (en) | 2010-05-19 | 2020-01-07 | Proteus Digital Health, Inc. | Tracking and delivery confirmation of pharmaceutical products |
| US11158149B2 (en) | 2013-03-15 | 2021-10-26 | Otsuka Pharmaceutical Co., Ltd. | Personal authentication apparatus system and method |
| US11612321B2 (en) | 2007-11-27 | 2023-03-28 | Otsuka Pharmaceutical Co., Ltd. | Transbody communication systems employing communication channels |
| CN116491959A (en)* | 2023-03-24 | 2023-07-28 | 电子科技大学 | A method for transforming EEG signals with different electrode distributions based on zero-reference technology |
| US11744481B2 (en) | 2013-03-15 | 2023-09-05 | Otsuka Pharmaceutical Co., Ltd. | System, apparatus and methods for data collection and assessing outcomes |
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| US9597010B2 (en) | 2005-04-28 | 2017-03-21 | Proteus Digital Health, Inc. | Communication system using an implantable device |
| US9198608B2 (en) | 2005-04-28 | 2015-12-01 | Proteus Digital Health, Inc. | Communication system incorporated in a container |
| US8674825B2 (en) | 2005-04-28 | 2014-03-18 | Proteus Digital Health, Inc. | Pharma-informatics system |
| US8730031B2 (en) | 2005-04-28 | 2014-05-20 | Proteus Digital Health, Inc. | Communication system using an implantable device |
| US8847766B2 (en) | 2005-04-28 | 2014-09-30 | Proteus Digital Health, Inc. | Pharma-informatics system |
| US8547248B2 (en) | 2005-09-01 | 2013-10-01 | Proteus Digital Health, Inc. | Implantable zero-wire communications system |
| US11928614B2 (en) | 2006-05-02 | 2024-03-12 | Otsuka Pharmaceutical Co., Ltd. | Patient customized therapeutic regimens |
| US8956287B2 (en) | 2006-05-02 | 2015-02-17 | Proteus Digital Health, Inc. | Patient customized therapeutic regimens |
| US11357730B2 (en) | 2006-10-25 | 2022-06-14 | Otsuka Pharmaceutical Co., Ltd. | Controlled activation ingestible identifier |
| US10238604B2 (en) | 2006-10-25 | 2019-03-26 | Proteus Digital Health, Inc. | Controlled activation ingestible identifier |
| US8945005B2 (en) | 2006-10-25 | 2015-02-03 | Proteus Digital Health, Inc. | Controlled activation ingestible identifier |
| US8718193B2 (en) | 2006-11-20 | 2014-05-06 | Proteus Digital Health, Inc. | Active signal processing personal health signal receivers |
| US9083589B2 (en) | 2006-11-20 | 2015-07-14 | Proteus Digital Health, Inc. | Active signal processing personal health signal receivers |
| US9444503B2 (en) | 2006-11-20 | 2016-09-13 | Proteus Digital Health, Inc. | Active signal processing personal health signal receivers |
| US10441194B2 (en) | 2007-02-01 | 2019-10-15 | Proteus Digital Heal Th, Inc. | Ingestible event marker systems |
| US8858432B2 (en) | 2007-02-01 | 2014-10-14 | Proteus Digital Health, Inc. | Ingestible event marker systems |
| US8956288B2 (en) | 2007-02-14 | 2015-02-17 | Proteus Digital Health, Inc. | In-body power source having high surface area electrode |
| US11464423B2 (en) | 2007-02-14 | 2022-10-11 | Otsuka Pharmaceutical Co., Ltd. | In-body power source having high surface area electrode |
| US8932221B2 (en) | 2007-03-09 | 2015-01-13 | Proteus Digital Health, Inc. | In-body device having a multi-directional transmitter |
| US8540632B2 (en) | 2007-05-24 | 2013-09-24 | Proteus Digital Health, Inc. | Low profile antenna for in body device |
| US10517506B2 (en) | 2007-05-24 | 2019-12-31 | Proteus Digital Health, Inc. | Low profile antenna for in body device |
| US8961412B2 (en) | 2007-09-25 | 2015-02-24 | Proteus Digital Health, Inc. | In-body device with virtual dipole signal amplification |
| US9433371B2 (en) | 2007-09-25 | 2016-09-06 | Proteus Digital Health, Inc. | In-body device with virtual dipole signal amplification |
| US11612321B2 (en) | 2007-11-27 | 2023-03-28 | Otsuka Pharmaceutical Co., Ltd. | Transbody communication systems employing communication channels |
| US9060708B2 (en) | 2008-03-05 | 2015-06-23 | Proteus Digital Health, Inc. | Multi-mode communication ingestible event markers and systems, and methods of using the same |
| US9258035B2 (en) | 2008-03-05 | 2016-02-09 | Proteus Digital Health, Inc. | Multi-mode communication ingestible event markers and systems, and methods of using the same |
| US8542123B2 (en) | 2008-03-05 | 2013-09-24 | Proteus Digital Health, Inc. | Multi-mode communication ingestible event markers and systems, and methods of using the same |
| US8810409B2 (en) | 2008-03-05 | 2014-08-19 | Proteus Digital Health, Inc. | Multi-mode communication ingestible event markers and systems, and methods of using the same |
| US9603550B2 (en) | 2008-07-08 | 2017-03-28 | Proteus Digital Health, Inc. | State characterization based on multi-variate data fusion techniques |
| US11217342B2 (en) | 2008-07-08 | 2022-01-04 | Otsuka Pharmaceutical Co., Ltd. | Ingestible event marker data framework |
| US10682071B2 (en) | 2008-07-08 | 2020-06-16 | Proteus Digital Health, Inc. | State characterization based on multi-variate data fusion techniques |
| US8583227B2 (en) | 2008-12-11 | 2013-11-12 | Proteus Digital Health, Inc. | Evaluation of gastrointestinal function using portable electroviscerography systems and methods of using the same |
| US9659423B2 (en) | 2008-12-15 | 2017-05-23 | Proteus Digital Health, Inc. | Personal authentication apparatus system and method |
| TWI424832B (en)* | 2008-12-15 | 2014-02-01 | Proteus Digital Health Inc | Body-associated receiver and method |
| US8545436B2 (en) | 2008-12-15 | 2013-10-01 | Proteus Digital Health, Inc. | Body-associated receiver and method |
| US9149577B2 (en) | 2008-12-15 | 2015-10-06 | Proteus Digital Health, Inc. | Body-associated receiver and method |
| US9439566B2 (en) | 2008-12-15 | 2016-09-13 | Proteus Digital Health, Inc. | Re-wearable wireless device |
| US9883819B2 (en) | 2009-01-06 | 2018-02-06 | Proteus Digital Health, Inc. | Ingestion-related biofeedback and personalized medical therapy method and system |
| US10305544B2 (en) | 2009-11-04 | 2019-05-28 | Proteus Digital Health, Inc. | System for supply chain management |
| US8868453B2 (en) | 2009-11-04 | 2014-10-21 | Proteus Digital Health, Inc. | System for supply chain management |
| US9941931B2 (en) | 2009-11-04 | 2018-04-10 | Proteus Digital Health, Inc. | System for supply chain management |
| US9014779B2 (en) | 2010-02-01 | 2015-04-21 | Proteus Digital Health, Inc. | Data gathering system |
| US10376218B2 (en) | 2010-02-01 | 2019-08-13 | Proteus Digital Health, Inc. | Data gathering system |
| US10529044B2 (en) | 2010-05-19 | 2020-01-07 | Proteus Digital Health, Inc. | Tracking and delivery confirmation of pharmaceutical products |
| US9439599B2 (en) | 2011-03-11 | 2016-09-13 | Proteus Digital Health, Inc. | Wearable personal body associated device with various physical configurations |
| US9756874B2 (en) | 2011-07-11 | 2017-09-12 | Proteus Digital Health, Inc. | Masticable ingestible product and communication system therefor |
| US10223905B2 (en) | 2011-07-21 | 2019-03-05 | Proteus Digital Health, Inc. | Mobile device and system for detection and communication of information received from an ingestible device |
| US9235683B2 (en) | 2011-11-09 | 2016-01-12 | Proteus Digital Health, Inc. | Apparatus, system, and method for managing adherence to a regimen |
| US11744481B2 (en) | 2013-03-15 | 2023-09-05 | Otsuka Pharmaceutical Co., Ltd. | System, apparatus and methods for data collection and assessing outcomes |
| US11158149B2 (en) | 2013-03-15 | 2021-10-26 | Otsuka Pharmaceutical Co., Ltd. | Personal authentication apparatus system and method |
| US11741771B2 (en) | 2013-03-15 | 2023-08-29 | Otsuka Pharmaceutical Co., Ltd. | Personal authentication apparatus system and method |
| US9787511B2 (en) | 2013-09-20 | 2017-10-10 | Proteus Digital Health, Inc. | Methods, devices and systems for receiving and decoding a signal in the presence of noise using slices and warping |
| US10498572B2 (en) | 2013-09-20 | 2019-12-03 | Proteus Digital Health, Inc. | Methods, devices and systems for receiving and decoding a signal in the presence of noise using slices and warping |
| US9270503B2 (en) | 2013-09-20 | 2016-02-23 | Proteus Digital Health, Inc. | Methods, devices and systems for receiving and decoding a signal in the presence of noise using slices and warping |
| US11102038B2 (en) | 2013-09-20 | 2021-08-24 | Otsuka Pharmaceutical Co., Ltd. | Methods, devices and systems for receiving and decoding a signal in the presence of noise using slices and warping |
| US10097388B2 (en) | 2013-09-20 | 2018-10-09 | Proteus Digital Health, Inc. | Methods, devices and systems for receiving and decoding a signal in the presence of noise using slices and warping |
| US9577864B2 (en) | 2013-09-24 | 2017-02-21 | Proteus Digital Health, Inc. | Method and apparatus for use with received electromagnetic signal at a frequency not known exactly in advance |
| US10084880B2 (en) | 2013-11-04 | 2018-09-25 | Proteus Digital Health, Inc. | Social media networking based on physiologic information |
| US10398161B2 (en) | 2014-01-21 | 2019-09-03 | Proteus Digital Heal Th, Inc. | Masticable ingestible product and communication system therefor |
| US11950615B2 (en) | 2014-01-21 | 2024-04-09 | Otsuka Pharmaceutical Co., Ltd. | Masticable ingestible product and communication system therefor |
| TWI624256B (en)* | 2015-12-28 | 2018-05-21 | Xie Guo Zhang | Core muscle training electrode clothing |
| TWI652042B (en) | 2016-03-08 | 2019-03-01 | 財團法人紡織產業綜合研究所 | Electrode for detecting electrical signals from body skin |
| US10797758B2 (en) | 2016-07-22 | 2020-10-06 | Proteus Digital Health, Inc. | Electromagnetic sensing and detection of ingestible event markers |
| US10187121B2 (en) | 2016-07-22 | 2019-01-22 | Proteus Digital Health, Inc. | Electromagnetic sensing and detection of ingestible event markers |
| CN116491959A (en)* | 2023-03-24 | 2023-07-28 | 电子科技大学 | A method for transforming EEG signals with different electrode distributions based on zero-reference technology |
| Publication | Publication Date | Title |
|---|---|---|
| TW553735B (en) | Common electrode using human body as common electric reservoir and application thereof | |
| Valchinov et al. | Wearable ECG system for health and sports monitoring | |
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| Kunnath et al. | Wicard: a context aware wearable wireless sensor for cardiac monitoring |
| Date | Code | Title | Description |
|---|---|---|---|
| GD4A | Issue of patent certificate for granted invention patent | ||
| MM4A | Annulment or lapse of patent due to non-payment of fees |