JPS62501267A - Human tissue monitoring device and method - Google Patents
Human tissue monitoring device and methodInfo
- Publication number
- JPS62501267A JPS62501267A JP60505007A JP50500785A JPS62501267A JP S62501267 A JPS62501267 A JP S62501267A JP 60505007 A JP60505007 A JP 60505007A JP 50500785 A JP50500785 A JP 50500785A JP S62501267 A JPS62501267 A JP S62501267A
- Authority
- JP
- Japan
- Prior art keywords
- impedance
- voltage
- tissue
- recorder
- signal
- Prior art date
- Legal status (The legal status is an assumption and is not a legal conclusion. Google has not performed a legal analysis and makes no representation as to the accuracy of the status listed.)
- Pending
Links
- 238000000034 method Methods 0.000 title claims description 7
- 238000012806 monitoring device Methods 0.000 title description 2
- 238000005259 measurement Methods 0.000 claims description 3
- 238000002955 isolation Methods 0.000 claims description 2
- 230000010363 phase shift Effects 0.000 claims description 2
- 230000009278 visceral effect Effects 0.000 claims description 2
- 238000000926 separation method Methods 0.000 claims 2
- 230000002596 correlated effect Effects 0.000 claims 1
- 230000000875 corresponding effect Effects 0.000 claims 1
- 238000004519 manufacturing process Methods 0.000 claims 1
- 210000001015 abdomen Anatomy 0.000 description 7
- 230000008602 contraction Effects 0.000 description 7
- 238000001514 detection method Methods 0.000 description 5
- 210000002216 heart Anatomy 0.000 description 4
- 230000003187 abdominal effect Effects 0.000 description 3
- 238000010586 diagram Methods 0.000 description 3
- 238000012544 monitoring process Methods 0.000 description 3
- 230000000747 cardiac effect Effects 0.000 description 2
- 201000010099 disease Diseases 0.000 description 2
- 208000037265 diseases, disorders, signs and symptoms Diseases 0.000 description 2
- 238000006073 displacement reaction Methods 0.000 description 2
- 230000002496 gastric effect Effects 0.000 description 2
- 210000004072 lung Anatomy 0.000 description 2
- 230000010355 oscillation Effects 0.000 description 2
- 210000003932 urinary bladder Anatomy 0.000 description 2
- 210000004291 uterus Anatomy 0.000 description 2
- 210000001835 viscera Anatomy 0.000 description 2
- XLYOFNOQVPJJNP-UHFFFAOYSA-N water Substances O XLYOFNOQVPJJNP-UHFFFAOYSA-N 0.000 description 2
- 241000282994 Cervidae Species 0.000 description 1
- 208000032544 Cicatrix Diseases 0.000 description 1
- 239000008280 blood Substances 0.000 description 1
- 210000004369 blood Anatomy 0.000 description 1
- 210000001124 body fluid Anatomy 0.000 description 1
- 239000010839 body fluid Substances 0.000 description 1
- 230000007423 decrease Effects 0.000 description 1
- 239000003814 drug Substances 0.000 description 1
- 229940079593 drug Drugs 0.000 description 1
- 235000013399 edible fruits Nutrition 0.000 description 1
- 239000000835 fiber Substances 0.000 description 1
- 208000015181 infectious disease Diseases 0.000 description 1
- 239000007788 liquid Substances 0.000 description 1
- 235000012054 meals Nutrition 0.000 description 1
- 231100000241 scar Toxicity 0.000 description 1
- 230000037387 scars Effects 0.000 description 1
- 230000035945 sensitivity Effects 0.000 description 1
Classifications
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
- A61B5/00—Measuring for diagnostic purposes; Identification of persons
- A61B5/05—Detecting, measuring or recording for diagnosis by means of electric currents or magnetic fields; Measuring using microwaves or radio waves
- A61B5/053—Measuring electrical impedance or conductance of a portion of the body
- A61B5/0535—Impedance plethysmography
Landscapes
- Health & Medical Sciences (AREA)
- Life Sciences & Earth Sciences (AREA)
- Heart & Thoracic Surgery (AREA)
- Medical Informatics (AREA)
- Physics & Mathematics (AREA)
- Nuclear Medicine, Radiotherapy & Molecular Imaging (AREA)
- Biophysics (AREA)
- Pathology (AREA)
- Engineering & Computer Science (AREA)
- Biomedical Technology (AREA)
- Hematology (AREA)
- Radiology & Medical Imaging (AREA)
- Molecular Biology (AREA)
- Surgery (AREA)
- Animal Behavior & Ethology (AREA)
- General Health & Medical Sciences (AREA)
- Public Health (AREA)
- Veterinary Medicine (AREA)
- Measurement And Recording Of Electrical Phenomena And Electrical Characteristics Of The Living Body (AREA)
- Measuring And Recording Apparatus For Diagnosis (AREA)
Abstract
(57)【要約】本公報は電子出願前の出願データであるため要約のデータは記録されません。 (57) [Summary] This bulletin contains application data before electronic filing, so abstract data is not recorded.
Description
【発明の詳細な説明】 人」り化急jヒニ!」1厄」じε方ユLこの発明は、人体の中空の内臓組織をモ ニタするための装置に関する。[Detailed description of the invention] ``People'' are suddenly j hini! "1 Misfortune" This invention is based on the model of the hollow internal organs of the human body. This invention relates to a device for monitoring.
この発明は、心臓、肺、膀胱及び子宮の容積と、これら組織のいずれかの中にあ る体液の圀とを、複数の電極を用いて問題となる組織を介した人体の両端間のイ ンピーダンスの差を測定することにより、電子的に測定することを含む、例えば 、腹部などの中空の内臓組織機能の人体機能をモニタできるという観測に基づい ている。This invention relates to the volumes of the heart, lungs, bladder, and uterus and the A field of body fluids is connected between two ends of the human body through the tissue in question using multiple electrodes. including measuring electronically by measuring the difference in impedance, e.g. , based on the observation that human body functions can be monitored in hollow visceral tissue functions such as the abdomen. ing.
この発明によれば、人体機能モニタ装置は、高周波数の振動を発生するための発 振器手段と、発振器により駆動される定電流発生源と、患者の体に付着するため の少なくとも一対の電流駆動電極と、患者の体に付着するための少なくとも二対 の電圧検出電極と、発生手段の周波数に同調された同調器電圧増幅器手段と、電 圧検出電極対の間に表われるインピーダンス変化を測定するためのコンバータ手 段と、インピーダンスコンバータからの信号を受信するための回路手段を隔離す るインピーダンス指示手段と、装備又は被験者及びインピーダンスオフセット制 御装置からの電子的又は生物学的な変動を除去するためのフィルタ手段と、被験 者信号を記録するためのレコーダ手段とを備え、被験者信号がレコーダ手段によ り分離信号として受信される。According to this invention, the human body function monitoring device includes a generator for generating high frequency vibrations. an oscillator means, a constant current source driven by the oscillator, and for attaching to the patient's body; at least one pair of current-driven electrodes for attachment to the patient's body; a voltage sensing electrode, a tuner voltage amplifier means tuned to the frequency of the generating means; Converter hand for measuring the impedance change appearing between the pressure sensing electrode pair and the circuit means for receiving the signal from the impedance converter. impedance indicating means, equipment or subject, and impedance offset system. filter means for removing electronic or biological fluctuations from the control equipment; and recorder means for recording the subject signal, the subject signal being recorded by the recorder means. is received as a separated signal.
レコーダ手段は、例えば、図表レコーダ又はオシロスコープと、テープレコーダ 又はマイクロコンピュータとを備えていてもよく、好ましくは、異なる電極対か らの信号を分離して受信する能力を持つ上に、信号の位相変位を修正する能力と 信号の組み合わせを記録する能力とを持つ。The recorder means may be, for example, a chart recorder or an oscilloscope and a tape recorder. or a microcomputer, preferably with different electrode pairs. In addition to having the ability to separate and receive signals from other sources, it also has the ability to correct the phase shift of the signal. and the ability to record combinations of signals.
この装置は1人体、例えば、腹部、心臓、肺、膀胱及び子宮なとの、中空の内臓 組織内の、大きさ、満たすか又は空にする比率、及び壁収縮のモニタに用いろこ とができる。This device can be used to measure the hollow internal organs of a human body, such as the abdomen, heart, lungs, bladder, and uterus. Used to monitor size, filling or emptying ratio, and wall contraction within the tissue. I can do it.
レコーダにより生成される記録は、インピーダンス変化の連続的な記録となる。The record produced by the recorder will be a continuous record of impedance changes.
それは、インピーダンス変化を引き起こす組織壁内の収縮を示す変動を伴う基準 線を表わす0組織が痕跡を満たして最大値に上昇し、その後、基準レベル線に減 少するとき、陥没した痕跡は、組織壁内の収縮を示す変動により、同様に付加さ れる。組織を満たし及び空にする時間は、極大値への上昇及び引き続いて起こる 減衰の速度により示される。容積はインピーダンス変化量の関数として測定でき る。壁の収縮量は、主な痕跡上に付加された小さい極大値領域の関数として示さ れる。例えば、信号のフーリエ分析による処理は、電極により覆われる異なる領 域内の組織収縮を示し、例えば、痕跡を時間間隔に分割することにより、異なる 時間における収縮差が測定でき、例えば、食事、薬又は他の刺激に対する応答を 示す結果となる。It is a criterion with fluctuations indicative of contraction within the tissue wall causing impedance changes. The 0 tissue representing the line fills the trace and rises to a maximum value, then decreases to the reference level line. Over time, depression scars are similarly added due to fluctuations indicative of shrinkage within the tissue wall. It will be done. Tissue filling and emptying times rise to a maximum and are followed by Indicated by the rate of decay. Volume can be measured as a function of impedance change. Ru. The amount of wall shrinkage is shown as a function of the small local maximum area added over the main trace. It will be done. For example, processing the signal by Fourier analysis It shows tissue contraction within a region, e.g. by dividing the trace into time intervals, different Differences in contraction over time can be measured, e.g. in response to meals, drugs or other stimuli. The result is shown below.
多数の電極からの信号を組み合わせることにより生成される痕跡は、組織の最大 インピーダンス変位を示すため、分割された信号から得られることができる容積 を更に高感度に示すことになる。The traces produced by combining signals from a large number of electrodes are The volume that can be obtained from the split signal to indicate the impedance displacement will be shown with even higher sensitivity.
この装置の1つの特定的な形態において、発生手段は1、00 k II z発 振器であり、電流制御手段は、極値から極値までが4111八で一定の駆動電流 を生成する。In one particular form of this device, the generating means emit 1,00k IIz. The current control means is a constant driving current of 41118 from extreme value to extreme value. generate.
腹部容積と、満たすか及び又は空にする比率とをモニタするための、健康な組織 を冒さない方法は、胃腸病の医師達により長く探索されてきた。健康な組織を冒 さない方法は、X線又は等方性方法と異なる繰り返しの利点を有するため、病気 の進行又は治療の効果が1111定可能である。提案された新しい方策は、この 能力を有し、又、実際上、腹部の収縮量を計るのにも用いることができるほど高 感度であることが証明された。腹部収縮をモニタするのに電極対が分離使用可能 なため、腹部を通る収縮進行は評価されることができる。同時に、複数の電極が 用いられるため、人体の増加した領域を調査することにより測定容積の精度は増 大するので、たとえ腹部の正確な位置が外部から確認できなくても、腹部の完全 な領域と含んでいる。Healthy tissue for monitoring abdominal volume and filling and/or emptying rates Gastrointestinal physicians have long sought ways to avoid the risk of infection. attack healthy tissue Non-disease methods have the advantage of repeatability, different from X-ray or isotropic methods. The progress of the disease or the effectiveness of treatment can be determined. The proposed new strategy is to In fact, it is so high that it can be used to measure the amount of abdominal contraction. proved to be sensitive. Electrode pairs can be used separately to monitor abdominal contractions Therefore, contraction progression through the abdomen can be assessed. At the same time, multiple electrodes The accuracy of the measured volume is increased by surveying an increased area of the human body. Because of the large size of the abdomen, even if the exact location of the abdomen cannot be confirmed externally, It includes a wide range of areas.
更に、少なくとも二対の電圧検出電極を用いることは、外部から確認できない人 体内の重要な領域からの信号を記録する能力を増加させる。Furthermore, the use of at least two pairs of voltage detection electrodes is prohibited by anyone who cannot confirm this externally. Increases the ability to record signals from important areas within the body.
更に、心臓容積の変化比率従って収縮力及び心臓筋肉をモニタするために5イン ピーダンス方法が提案されてきたので、その結果は量を計ることはできなかった 。従って、心臓出力として知られている、心臓から放出される血液旦の正確な測 定は実行不可能であった。もし、新しい方策の電極が、腹部と、飲まれた水又は 他の適当な液体の測定量とを覆って配置されたとすると、インピーダンス変化が 測定できるのて、インピーダンス変1ヒは飲まれた旦と関係することができる。Additionally, a 5-in. Since the pedance method has been proposed, the results could not be quantified. . Therefore, an accurate measurement of blood pumped out by the heart, known as cardiac output. The determination was not feasible. If the new strategy electrodes are placed on the abdomen and in the water that is drunk or If placed over a measured volume of another suitable liquid, the impedance change will be Since it can be measured, the change in impedance can be related to the amount of water consumed.
こうして、池のt iが心臓の変化を記録するのに用いられるとき、得られる結 果は、記録された胃の変化の結果を参照することにより、量が計られることがで きる。この方法において、心臓性能をモニタするための、新しい、健康な組織を 冒すことのない方策が役立つ。Thus, when Ike's ti is used to record changes in the heart, the results obtained The fruit can be quantified by referring to the recorded results of gastric changes. Wear. In this way, new, healthy tissue is harvested for monitoring cardiac performance. Low-impact strategies are helpful.
更に、人体のモニタされる組織及び他のあらゆる領域からの信号間の9叩、比較 、又は標準化が必要な機能のどのような測定においても、電極の付加的セy ) −が用いられる。Furthermore, the comparison between the signals from the monitored tissues and all other areas of the human body , or the additional safety of electrodes in any measurement of functions that require standardization). - is used.
以下、例えば一対の電圧検出TLFftのみを示した単一のチャネル回路のブロ ック図を示す図面を参照することによって、この発明を非常に詳、11Ilに説 明する。しかし、実際には、少なくとも2つの電圧検出チャネルが用いられる。Below, for example, a block diagram of a single channel circuit showing only a pair of voltage detection TLFft is shown. The invention will be explained in greater detail in 11Il by reference to the drawings which show the diagrams. I will clarify. However, in practice at least two voltage detection channels are used.
図面において、1は100 k II zの発振3じ、2は極値から極値までが 4+nAの定電流駆動W置、3は腹部、11は一対の電流駆動電極、5は一対の 電圧検出電極、6は]0OkHzの同調器電圧増幅器、7はインピーダンス変( ヒを回復する検出器、8はインピーダンスメータ、9は肢験者信号隔m増幅器、 10はローパスフィルタ及びインピーダンスメータ・・lト制(耳装置、11は 図表レコーダ、そして、12はチープレコータ又はマイクロコンピコ、−夕であ る。In the drawing, 1 indicates 3 times the oscillation of 100 kIIz, and 2 indicates the oscillation from extreme value to extreme value. 4 + nA constant current drive W position, 3 is the abdomen, 11 is a pair of current drive electrodes, 5 is a pair of Voltage detection electrode, 6 is ]0 kHz tuner voltage amplifier, 7 is impedance changer ( 8 is an impedance meter, 9 is a limb tester signal interval m amplifier, 10 is a low-pass filter and impedance meter (ear device), 11 is a chart recorder, and 12 is a cheap recorder or micro computer, Ru.
この装置を用いる場き、電流駆動装置及び電圧検出電極・1及び5は1.・患者 の体上のモニタされるべきK(l繊の近くに配置される。電圧検出電極5により 記録された信号は、増幅器6に通され、検出器コンバータ7によりインピーダン スに変換される。検出器コンバータ7からの信号は、インピーダンスの直接的読 み出しができるインピーダンスメータ8と、信号隔離増幅器9との両方に通され 、そこからローパスフィルタ及びレコーダに通される。When using this device, the current drive device and voltage detection electrodes 1 and 5 are 1. ·patient is placed near the K(l) fiber to be monitored on the body of the person. The recorded signal is passed through an amplifier 6 and impeded by a detector converter 7. converted to The signal from the detector converter 7 provides a direct reading of the impedance. The signal is passed through both the impedance meter 8 and the signal isolation amplifier 9. , from there it is passed through a low pass filter and a recorder.
1つ以上の電圧検出チャネルが用いられたとき、分離した電圧検出電極対からの 信号は、分離を維持され、個々にレコーダに通されるので、電圧検出電極の各対 により検出されたインピーダンス変化は、個々に記録されることができる。しか し、レコーダは、好ましくは、個々の信号の位相変位を訂正し且つ信号を組み合 わせるための手段をも含むので、多数の電極により記録されるインピーダンス変 化の合計は、レコーダにより同様に示されることができる。When more than one voltage sensing channel is used, the The signals are kept separate and passed to the recorder individually so that each pair of voltage sensing electrodes The impedance changes detected by can be recorded individually. deer However, the recorder preferably corrects phase displacements of the individual signals and combines the signals. impedance changes recorded by multiple electrodes. The sum of the values can be indicated by the recorder as well.
第2図及び第3図は、更に詳細な自明の回路図であり、装置の種々の構成要素を 示すために同様の参照符号が用いられている。これらの図面においては電極5の 1つのセラl〜のみが示され、又、回路装置は電極5のセットから供給するのに 適したように対をなすであろうことが認識されるだろう。Figures 2 and 3 are more detailed self-explanatory circuit diagrams showing the various components of the device. Similar reference numerals are used to indicate. In these drawings, the electrode 5 Only one cell is shown, and the circuit arrangement is supplied from a set of electrodes 5. It will be appreciated that they may be paired as appropriate.
同様に、図示された回路装置が、この発明の特に1つの好適な実施例の単なる典 型例であり、又、この発明はどの点においても、図示された配列に制限されると みなされるべきではないということが認識されるだろう。Similarly, the illustrated circuit arrangement is merely an example of one particularly preferred embodiment of the invention. This invention is not intended to be limited in any respect to the arrangement shown, which is exemplary only. It will be recognized that it should not be considered.
図面の簡単な説明 国際調査報告Brief description of the drawing international search report
Claims (7)
Applications Claiming Priority (2)
Application Number | Priority Date | Filing Date | Title |
---|---|---|---|
GB8428831 | 1984-11-15 | ||
GB848428831A GB8428831D0 (en) | 1984-11-15 | 1984-11-15 | Monitoring organs of body |
Publications (1)
Publication Number | Publication Date |
---|---|
JPS62501267A true JPS62501267A (en) | 1987-05-21 |
Family
ID=10569750
Family Applications (1)
Application Number | Title | Priority Date | Filing Date |
---|---|---|---|
JP60505007A Pending JPS62501267A (en) | 1984-11-15 | 1985-11-15 | Human tissue monitoring device and method |
Country Status (5)
Country | Link |
---|---|
EP (1) | EP0235137A1 (en) |
JP (1) | JPS62501267A (en) |
AU (1) | AU5069685A (en) |
GB (2) | GB8428831D0 (en) |
WO (1) | WO1986002819A1 (en) |
Families Citing this family (6)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
EP0359397B1 (en) * | 1988-08-19 | 1995-05-03 | Hewlett-Packard Company | Device for detection of uterine contractions |
WO1995035060A1 (en) * | 1994-06-20 | 1995-12-28 | Auckland Uniservices Limited | Brain damage monitor |
US6631292B1 (en) * | 2001-03-23 | 2003-10-07 | Rjl Systems, Inc. | Bio-electrical impedance analyzer |
AU2002952265A0 (en) * | 2002-10-25 | 2002-11-07 | Upfal, Jonathan | Implantable sensor |
US7758522B2 (en) * | 2007-01-03 | 2010-07-20 | General Electric Company | Combined uterine activity and fetal heart rate monitoring device |
US20090204017A1 (en) * | 2008-02-12 | 2009-08-13 | Pandit Ashit M | Uterine activity monitoring using impedance plethysmography |
Family Cites Families (6)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
US387436A (en) * | 1888-08-07 | o neil | ||
US3874368A (en) * | 1973-04-19 | 1975-04-01 | Manfred Asrican | Impedance plethysmograph having blocking system |
FR2294677A1 (en) * | 1973-11-09 | 1976-07-16 | Thomson Medical Telco | Cardio-pulmonary diagnostic appts using HF current - has electrodes mounted in front and rear of thorax |
US4059169A (en) * | 1976-02-09 | 1977-11-22 | Hagen Winston H | Monitor for biological volume changes |
FR2354744A1 (en) * | 1976-06-16 | 1978-01-13 | Commissariat Energie Atomique | OCCLUSION RHEOPLETHYSMOGRAPHY DEVICE |
US4506678A (en) * | 1982-06-07 | 1985-03-26 | Healthdyne, Inc. | Patient monitor for providing respiration and electrocardiogram signals |
-
1984
- 1984-11-15 GB GB848428831A patent/GB8428831D0/en active Pending
-
1985
- 1985-11-15 GB GB08711445A patent/GB2190751B/en not_active Expired
- 1985-11-15 JP JP60505007A patent/JPS62501267A/en active Pending
- 1985-11-15 WO PCT/GB1985/000521 patent/WO1986002819A1/en not_active Application Discontinuation
- 1985-11-15 EP EP85905646A patent/EP0235137A1/en not_active Withdrawn
- 1985-11-15 AU AU50696/85A patent/AU5069685A/en not_active Abandoned
Also Published As
Publication number | Publication date |
---|---|
GB8711445D0 (en) | 1987-06-17 |
GB2190751B (en) | 1988-07-13 |
GB2190751A (en) | 1987-11-25 |
AU5069685A (en) | 1986-06-03 |
GB8428831D0 (en) | 1984-12-27 |
WO1986002819A1 (en) | 1986-05-22 |
EP0235137A1 (en) | 1987-09-09 |
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