JPH03131227A - Cardiac output measuring apparatus - Google Patents
Cardiac output measuring apparatusInfo
- Publication number
- JPH03131227A JPH03131227A JP1268223A JP26822389A JPH03131227A JP H03131227 A JPH03131227 A JP H03131227A JP 1268223 A JP1268223 A JP 1268223A JP 26822389 A JP26822389 A JP 26822389A JP H03131227 A JPH03131227 A JP H03131227A
- Authority
- JP
- Japan
- Prior art keywords
- cardiac output
- temperature
- calibration
- blood
- measurement
- 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.)
- Granted
Links
- 230000000747 cardiac effect Effects 0.000 title claims abstract description 128
- 239000008280 blood Substances 0.000 claims abstract description 57
- 210000004369 blood Anatomy 0.000 claims abstract description 57
- 238000005259 measurement Methods 0.000 claims abstract description 57
- 230000017531 blood circulation Effects 0.000 claims abstract description 17
- 238000000034 method Methods 0.000 claims description 20
- 238000001514 detection method Methods 0.000 claims description 12
- 239000007788 liquid Substances 0.000 claims description 11
- 238000010438 heat treatment Methods 0.000 abstract description 3
- 238000001816 cooling Methods 0.000 abstract 1
- 238000009529 body temperature measurement Methods 0.000 description 20
- 239000000523 sample Substances 0.000 description 17
- 230000008859 change Effects 0.000 description 8
- 238000004891 communication Methods 0.000 description 8
- 238000002955 isolation Methods 0.000 description 7
- 210000005245 right atrium Anatomy 0.000 description 7
- 238000012937 correction Methods 0.000 description 6
- 238000003113 dilution method Methods 0.000 description 6
- 230000006870 function Effects 0.000 description 6
- 210000001147 pulmonary artery Anatomy 0.000 description 6
- YURDCJXYOLERLO-LCYFTJDESA-N (2E)-5-methyl-2-phenylhex-2-enal Chemical compound CC(C)C\C=C(\C=O)C1=CC=CC=C1 YURDCJXYOLERLO-LCYFTJDESA-N 0.000 description 5
- 238000010586 diagram Methods 0.000 description 5
- 239000003978 infusion fluid Substances 0.000 description 5
- 230000005484 gravity Effects 0.000 description 4
- 239000007924 injection Substances 0.000 description 4
- 238000002347 injection Methods 0.000 description 4
- 230000003287 optical effect Effects 0.000 description 4
- 210000005241 right ventricle Anatomy 0.000 description 3
- 230000005540 biological transmission Effects 0.000 description 2
- 230000036760 body temperature Effects 0.000 description 2
- 238000009792 diffusion process Methods 0.000 description 2
- 230000000694 effects Effects 0.000 description 2
- 239000011521 glass Substances 0.000 description 2
- 230000004217 heart function Effects 0.000 description 2
- 208000015181 infectious disease Diseases 0.000 description 2
- 239000013307 optical fiber Substances 0.000 description 2
- 230000008569 process Effects 0.000 description 2
- 238000012545 processing Methods 0.000 description 2
- 238000012360 testing method Methods 0.000 description 2
- 101000616556 Homo sapiens SH3 domain-containing protein 19 Proteins 0.000 description 1
- 102100021782 SH3 domain-containing protein 19 Human genes 0.000 description 1
- 230000008901 benefit Effects 0.000 description 1
- 210000004204 blood vessel Anatomy 0.000 description 1
- 239000013256 coordination polymer Substances 0.000 description 1
- 238000010790 dilution Methods 0.000 description 1
- 239000012895 dilution Substances 0.000 description 1
- 210000003191 femoral vein Anatomy 0.000 description 1
- 210000004731 jugular vein Anatomy 0.000 description 1
- 238000000691 measurement method Methods 0.000 description 1
- 230000007246 mechanism Effects 0.000 description 1
- 230000008054 signal transmission Effects 0.000 description 1
- 230000001131 transforming effect Effects 0.000 description 1
- 210000003462 vein Anatomy 0.000 description 1
- 210000002620 vena cava superior Anatomy 0.000 description 1
- 238000010792 warming Methods 0.000 description 1
Landscapes
- Measuring Pulse, Heart Rate, Blood Pressure Or Blood Flow (AREA)
Abstract
Description
【発明の詳細な説明】
〔産業上の利用分野］
本発明は、病院等の医療施設における検査室、手術室、
ＩＣＵ等において心機能検査並びに循環動態の把握に用
いられる心拍出量測定装置に関する。[Detailed Description of the Invention] [Industrial Application Field] The present invention is applicable to examination rooms, operating rooms,
The present invention relates to a cardiac output measuring device used for cardiac function testing and understanding of circulatory dynamics in ICUs and the like.
［従来の技術］
従来、心機能検査のために右心カテーテル法によって心
拍出量を測定するには指示薬希釈法が用いられており、
この指示薬希釈法には熱拡散から心拍出量を求める熱希
釈法、色素の拡散による照度の変化から心拍出量を求め
る色素希釈法等がある。ここでは熱希釈法について説明
する。[Prior Art] Conventionally, an indicator dilution method has been used to measure cardiac output by right heart catheterization for cardiac function testing.
Examples of the indicator dilution method include a thermodilution method that determines cardiac output from thermal diffusion, and a dye dilution method that determines cardiac output from changes in illuminance due to dye diffusion. Here, the thermodilution method will be explained.
右心カテーテル法では、頚静脈、大腿静脈、封帯静脈等
よりカテーテルが導管され、上大静脈あるいは工大静脈
、右心房、右心室を経て、その先端が肺動脈中に位置す
るように留置される。カテーテルには右心房に位置する
ように吐出口と、肺動脈に位置するようにサーミスタが
配置されている。いま、吐出口より、血液温度より高温
もしくは低温の液体が右心房に注入されると、液体は右
心房、右心室において拡散され、希釈される。In right heart catheterization, a catheter is introduced from the jugular vein, femoral vein, zonal vein, etc., passes through the superior vena cava or vena cava, the right atrium, and the right ventricle, and is placed so that its tip is located in the pulmonary artery. . The catheter has an outlet located in the right atrium and a thermistor located in the pulmonary artery. Now, when a liquid with a temperature higher or lower than the blood temperature is injected into the right atrium from the discharge port, the liquid is diffused and diluted in the right atrium and right ventricle.
この希釈された液体の温度を肺動脈中に位置したサーミ
スタによって検知し、その温度の希釈曲線（時間に対す
る温度変化の図）を得て、その曲線の面積等からスチュ
ワート・ハミルトン法による下記（１）式によって心拍
出量を算出する。The temperature of this diluted liquid is detected by a thermistor located in the pulmonary artery, and a dilution curve (diagram of temperature change with respect to time) of the temperature is obtained, and from the area of the curve, etc., the following (1) is performed using the Stewart-Hamilton method. Calculate cardiac output using the formula.
Ｓ、・ＣＩ、・Ｓ、ｌ△Ｔｂｄｔ
ここで、
ＣＯ：心拍出量、Ｓｌ：注入液体の比重Ｃ１：注入液体
の比熱、
ｖｌ：注入液体量
Ｔ１：注入液体の温度、Ｔ１：血液の温度Ｓよ：血液の
比重、Ｃゎ：血液の比熱
Ｓ、の△Ｔ、ｃｔｔ：熱希釈曲線の面積である。S,・CI,・S,l△Tbdt where, CO: cardiac output, Sl: specific gravity of injected liquid C1: specific heat of injected liquid, vl: amount of injected liquid T1: temperature of injected liquid, T1: blood Temperature S: specific gravity of blood, C: specific heat S of blood, ΔT, ctt: area of thermodilution curve.
また、熱希釈法により求めた心拍出量と熱式流量測定に
より求めた連続的な血流速度とから連続的に心拍出量の
計測が行なえる心拍出量測定装置もある（例えば、特開
昭６１−１２５３２９号公報参照）。There are also cardiac output measurement devices that can continuously measure cardiac output from the cardiac output determined by the thermodilution method and the continuous blood flow velocity determined by thermal flow measurement (for example, , see Japanese Patent Application Laid-Open No. 61-125329).
ｃ本発明が解決しようとする課題］
上記従来例では、例えば、熱希釈法あるいは指示薬希釈
法を用いた心拍出量測定装置は、測定が間欠的であり連
続的な心拍出量の計測には使用できず、また頻繁に測定
しようとすると注入する液体の総量が増え、被験者の負
担が増大すると共に、操作による感染の危険性も増大す
るという欠点がある。c) Problems to be Solved by the Present Invention] In the above-mentioned conventional examples, for example, cardiac output measurement devices using a thermodilution method or an indicator dilution method perform intermittent measurement and cannot continuously measure cardiac output. Moreover, frequent measurements increase the total amount of liquid to be injected, which increases the burden on the subject and increases the risk of infection due to operation.
また、特開昭６１−１２５３２９号にて開示した連続的
に心拍出量の計測が行なえる心拍出量測定装置において
は、血流速の絶対値を計測しなければならないこと、並
びに血流速の絶対値の測定において必ずしも理論式通り
にプローブ出力が変化せず、測定誤差を生じるという欠
点があった。In addition, in the cardiac output measurement device that can continuously measure cardiac output disclosed in Japanese Patent Application Laid-Open No. 61-125329, it is necessary to measure the absolute value of blood flow velocity, and When measuring the absolute value of flow velocity, the probe output does not necessarily change according to the theoretical formula, resulting in measurement errors.
さらに、血流速の変化を温度変化として検出し、その温
度変化情報から一義的な関数並びにパラメータ（定数）
によって心拍出量を演算する場合、必ずしも温度変化情
報と心拍出量とが一致しないため心拍出量の演算値に測
定誤差が生じたり、標準のプローブの特性と個々のプロ
ーブの特性とが異なる場合、その特性の違いにより心拍
出量の演算値にも差が生じて心拍出量の測定精度が低下
するという欠点がある。Furthermore, changes in blood flow velocity are detected as temperature changes, and unique functions and parameters (constants) are determined from the temperature change information.
When calculating cardiac output using If they are different, there is a drawback that the difference in characteristics causes a difference in the calculated value of the cardiac output, resulting in a decrease in the accuracy of measuring the cardiac output.
［課題を解決するための手段］
本発明は、上述の課題を解決することを目的として成さ
れたもので、上述の課題を解決する一手段として以下の
構成を備える。[Means for Solving the Problems] The present invention has been made for the purpose of solving the above-mentioned problems, and includes the following configuration as one means for solving the above-mentioned problems.
即ぢ、血液の温度を検出１゛る血液温度検出手段と、一
定電流により加温が行なわれ血流によって冷却されて平
衡状態に達した温度を検出する平衡温度検出手段と、指
示薬液を注入して心拍出量を測定する心拍出量測定手段
と、電気的な受動素子の特性値を示す１５号を発生ずる
特性値検出手段と、連続心拍出量の演算に際して使用す
る定数を選択する定数選択手段と、前記血液温度検出手
段、前記平衡温度検出手段、前記心拍出量測定手段、前
記特性値検出手段および前記定数選択手段からのデータ
に基づいて心拍出量を算出する連続心拍出量演算手段と
を備える。Specifically, a blood temperature detection means for detecting the temperature of the blood, an equilibrium temperature detection means for detecting the temperature at which the blood is heated by a constant current and cooled by the blood flow and reaches an equilibrium state, and an indicator liquid is injected. a cardiac output measuring means for measuring the cardiac output; a characteristic value detecting means for generating No. 15 indicating the characteristic value of the electrical passive element; and a constant for use in calculating the continuous cardiac output. Calculate cardiac output based on data from the constant selection means to be selected, the blood temperature detection means, the equilibrium temperature detection means, the cardiac output measurement means, the characteristic value detection means, and the constant selection means. continuous cardiac output calculation means.
［作用］
以上の構成において、計測時並びに校正時の中枢部の体
温（肺動脈中での血液温度）、加温が行なわれ血流によ
り冷却され平衡状態に達したときの平衡温度、及び心拍
出量が得られ、血流速の変化を温度変化として検出しそ
の温度変化情報から直接心拍出量の変化を求め、実験的
にプローブ出力に合わせた関数、パラメータ（定数）を
個々のプローブの複数の特性に対して自動的に選択を行
なって演算することにより、血流速の絶対値を計測せず
に連続的に心拍出量の測定が行なえるようにしたもので
ある。[Function] In the above configuration, the central body temperature (blood temperature in the pulmonary artery) at the time of measurement and calibration, the equilibrium temperature when heating is performed and cooled by blood flow and reaches an equilibrium state, and the heartbeat. Once the output is obtained, changes in blood flow velocity are detected as temperature changes, changes in cardiac output are directly determined from the temperature change information, and functions and parameters (constants) tailored to the probe output are experimentally determined for each probe. By automatically selecting and calculating a plurality of characteristics, cardiac output can be continuously measured without measuring the absolute value of blood flow velocity.
［実施例］
以下、添付図面を参照して本発明に係る好適な一実施例
を詳細に説明する。[Embodiment] Hereinafter, a preferred embodiment of the present invention will be described in detail with reference to the accompanying drawings.
第１図は本発明に係る一実施例である、心拍出量測定装
置のブロック図である。FIG. 1 is a block diagram of a cardiac output measuring device, which is an embodiment of the present invention.
第１図において、】は心拍出量測定装置の本体であり、
外部に交換自在型の心拍出量測定用カテーテル２及び７
を接続する。カテーテル２は、熱希釈法に基づく指示薬
注入用及び指示薬温度検出用カテーテルであり、内部に
は指示薬温度を検出する感温素子３、及び前記感温素子
の特性のバラツキを補正する補正抵抗器４から成る指示
薬検温プローブ回路１５を備える。そして、この指示薬
検温プローブ回路１５はコネクタ５及び６を介して心拍
出量測定装置本体の計測部２０の注入液温度計測回路２
４に電気的に接続され、心拍出量測定の際は心臓の右心
房に位置する。In FIG. 1, ] is the main body of the cardiac output measuring device;
Externally exchangeable cardiac output measurement catheters 2 and 7
Connect. The catheter 2 is a catheter for injecting an indicator and detecting the temperature of the indicator based on the thermodilution method, and includes a temperature sensing element 3 for detecting the temperature of the indicator and a correction resistor 4 for correcting variations in the characteristics of the temperature sensing element. An indicator thermometer probe circuit 15 is provided. The indicator temperature probe circuit 15 is connected to the injectate temperature measurement circuit 2 of the measurement unit 20 of the cardiac output measurement device main body via the connectors 5 and 6.
4 and is located in the right atrium of the heart during cardiac output measurements.
カテーテル７ば、血液の温度を検出したり、定電流源回
路２３からの一定電流によって加温され血流によって冷
却される感温素子の温度（以下、平衡温度と呼ぶ）を検
出する血液温度・平衡温度検出用カテーテルであり、内
部には右心房、及び右心室で熱希釈された血液温度を検
出するサーミスタ８と前記サーミスタの特性を補正する
補正抵抗器９から成る血液検温プローブ回路１６、そし
て熱式流量測定法により血流速変化を平衡温度として検
出するサーミスタ１０（好ましくは自己加温型サーミス
タ）から成る平衡温度検温プローブ回路１７を備える。The catheter 7 is a blood temperature sensor that detects the temperature of blood and the temperature of a thermosensor that is heated by a constant current from the constant current source circuit 23 and cooled by blood flow (hereinafter referred to as equilibrium temperature). This is an equilibrium temperature detection catheter, and includes a blood temperature probe circuit 16 that includes a thermistor 8 that detects the temperature of blood thermodiluted in the right atrium and right ventricle, and a correction resistor 9 that corrects the characteristics of the thermistor. An equilibrium temperature measuring probe circuit 17 is provided, which includes a thermistor 10 (preferably a self-warming thermistor) that detects changes in blood flow velocity as an equilibrium temperature using a thermal flow measurement method.
また、電気的受動素子として抵抗器１３を備え、その特
性値によりプローブの特性を認識する。Further, a resistor 13 is provided as an electrical passive element, and the characteristics of the probe are recognized based on its characteristic value.
血液検温プローブ回路１６及び平衡温度検温プローブ回
路１７は、コネクタ１１及び１２を介して、それぞれ心
拍出量測定装置本体の計測部２０の血液温度計測回路２
５と平衡温度計測回路２６に電気的に接続され、心拍出
量測定の際は肺動脈に位置し、中枢部の体温を血液温度
信号として検出する。尚、上述したカテーテル２とカテ
ーテル７は、それぞれ外観上一体したものとして製造さ
れる。The blood temperature measurement probe circuit 16 and the equilibrium temperature measurement probe circuit 17 are connected to the blood temperature measurement circuit 2 of the measurement unit 20 of the cardiac output measurement device main body via the connectors 11 and 12, respectively.
5 and the equilibrium temperature measurement circuit 26, and is located in the pulmonary artery when measuring cardiac output, and detects the central body temperature as a blood temperature signal. Incidentally, the catheter 2 and catheter 7 described above are each manufactured as being integral in appearance.
次に、実施例である心拍出量測定装置の動作を第１図を
参照して説明する。Next, the operation of the cardiac output measuring device according to the embodiment will be explained with reference to FIG.
心拍出量測定装置１は、機能の面から以下の如く分けら
れる。即ち、カテーテル２及び７を介して各種温度計測
を実行する計測部２０と、計測部２０で計測した測定デ
ータ等を光学的手段により伝送するオプトアイソレーシ
ョン通信回路３５と、オプトアイソレーション通信回路
３５を介して入力した測定データに基づいて熱希釈法に
より間欠的に、あるいは平衡温度測定により連続的に心
拍出量を演算し出力するメインＣＰＵ部４０と、前記メ
インＣＰＵ部４０が演算して求めた心拍出量値を表示す
る表示器５１、そして前記各部に直流電源を供給する電
源部６０とに分けられる。The cardiac output measuring device 1 can be divided into the following types in terms of functions. That is, a measurement unit 20 that performs various temperature measurements via the catheters 2 and 7, an opto-isolation communication circuit 35 that transmits measurement data etc. measured by the measurement unit 20 by optical means, and an opto-isolation communication circuit 35. The main CPU section 40 calculates and outputs the cardiac output intermittently by the thermodilution method or continuously by measuring the equilibrium temperature based on the measurement data input through the main CPU section 40; It is divided into a display 51 that displays the determined cardiac output value, and a power supply section 60 that supplies DC power to each of the sections.
計測部２ｏにおいて、注入液温度、計測回路２４はカテ
ーテル２の開口部から右心房に吐出する指示薬温度を検
出し、その温度に対応する電圧信号を出力する。また、
血液温度計測回路２５は肺動脈において血液温度を検出
して、対応する電圧信号を出力し、平衡温度計測回路２
６は、例えば自己加温型のサーミスタに加えた熱量と周
囲の血液の流速によって奪われる熱量との関係から平衡
温度を検出し、対応する電圧信号を出力する。そして、
特性値計測回路２２は抵抗器１３の特性を読み取り、そ
の値からプローブの特性を認識してプローブの特性を表
わす信号を発生する。In the measurement unit 2o, the infusion liquid temperature measurement circuit 24 detects the temperature of the indicator discharged from the opening of the catheter 2 into the right atrium, and outputs a voltage signal corresponding to the temperature. Also,
The blood temperature measuring circuit 25 detects the blood temperature in the pulmonary artery and outputs a corresponding voltage signal, and the equilibrium temperature measuring circuit 2
6 detects an equilibrium temperature from the relationship between the amount of heat applied to a self-heating thermistor and the amount of heat removed by the flow rate of surrounding blood, and outputs a corresponding voltage signal. and,
The characteristic value measuring circuit 22 reads the characteristic of the resistor 13, recognizes the characteristic of the probe from the read value, and generates a signal representing the characteristic of the probe.
メインＣＰＵ４４はローカルＣＰＵ３０に対して、ＲＯ
Ｍ４５に格納された、例えば第３図に示すプログラムに
従い前記各計測回路（注入液温度計測回路２４、血液温
度計測回路２５、平衡温度計測回路２６および特性値計
測回路２２）に計測の実行を指示し、計測動作を制御す
る信号を送る。ＲＡＭ４６には制御に必要なデータを一
時的に格納する。これらの信号は、後述する伝送形式に
てオプトアイソレーション通信回路を介して伝えられる
。また、ローカルＣＰＵ３０は前記各計測回路からの計
測データを選択するために、アナログスイッチ２７に選
択信号を送る。その結果、各計測回路からの計測データ
はアナログスイッチを介してＡ／Ｄ変換器２８に達し、
そこでデジタルデータに変換された後ローカルＣＰＵ３
０に取り込まれる。そして、ローカルＣＰＵ３０は、Ｒ
ＯＭ２９に格納されたプログラムに従い、自己の有する
シリアル通信機能により受（Ｕデータをシリアルデータ
としてオプトアイソレーション通信回路３５に送る。The main CPU 44 provides RO to the local CPU 30.
Instruct each of the measurement circuits (infusion liquid temperature measurement circuit 24, blood temperature measurement circuit 25, equilibrium temperature measurement circuit 26, and characteristic value measurement circuit 22) to perform measurement according to the program stored in M45 and shown in FIG. 3, for example. and sends signals to control measurement operations. The RAM 46 temporarily stores data necessary for control. These signals are transmitted via an opto-isolation communication circuit in a transmission format described below. Further, the local CPU 30 sends a selection signal to the analog switch 27 in order to select measurement data from each of the measurement circuits. As a result, the measurement data from each measurement circuit reaches the A/D converter 28 via the analog switch,
There, after being converted to digital data, the local CPU3
It is taken into 0. Then, the local CPU 30
According to the program stored in the OM 29, it receives (U data) as serial data and sends it to the opto-isolation communication circuit 35 using its own serial communication function.
オプトアイソ１／−ジョン通信回路３５は、計測部２０
とメインＣＰＵ部４０間のデータの送受信を電気的に完
全に絶縁した状態で行ない、計測部２０側及びメインＣ
ＰＵ４０側それぞれに、）第１・ダイオード回路及びフ
ォトトランジスタ回路から成る光送受信回路３６．３７
と、前記光送受信回路を互いに電気的に絶縁させ、両者
の信号伝達媒体どなる光フアイバグラス３８とで構成さ
れる。従って、計測部２０の電圧信号とメインＣＰＵ部
４０の電圧信号との電気的接続は完全に遮断され、被験
者人体とメインＣＰ ｔ、Ｊ側とは如何なる閉ループも
形成されることがないので、安全な計測が行なえる。The opto-isolation 1/-john communication circuit 35 is connected to the measuring section 20.
Transmission and reception of data between the main CPU section 40 and the measuring section 20 side and the main CPU section 40 is performed in a completely electrically insulated state.
Optical transmitter/receiver circuits 36 and 37 each consisting of a first diode circuit and a phototransistor circuit are installed on each of the PU40 sides.
and an optical fiber glass 38 which electrically insulates the optical transmitting and receiving circuits from each other and serves as a signal transmission medium for both. Therefore, the electrical connection between the voltage signal of the measuring section 20 and the voltage signal of the main CPU section 40 is completely cut off, and no closed loop is formed between the human subject's body and the main CP t, J side, so it is safe. measurements can be performed.
次に、メインＣＰＵ部４０の動作を説明する。Next, the operation of the main CPU section 40 will be explained.
イブ１−アイソレーション通侶回路３５からのシリアル
データけ、メインＣＰＵ４４にて受信される。心拍出量
校正手段４１は、心拍出量の校正が熱希釈法によって行
なわれる場合を例にとると、冷却された、あるいは暖め
られた注入液の注入によって生じる血液の温度変化を計
測する前記血液温度計測回路２５から、熱希釈さね、た
血液温度に関する信号をメインＣＰ Ｕ４４から受は取
る。同時に心拍出量校正手段４１は、スヂュヮート・ハ
ミルトンの式（１）に基づいて注入液温度、注入液比熱
、注入液比重、血液比重、血液比熱、及び熱希釈された
血液温度から熱希釈心拍出量を演Ｗし、結果を校正時心
拍出量信号として校正時信号記憶手段４２に出力する。Eve 1 - Serial data from the isolation communication circuit 35 is received by the main CPU 44. For example, when the cardiac output is calibrated by the thermodilution method, the cardiac output calibration means 41 measures the temperature change of the blood caused by the injection of cooled or warmed infusion fluid. The main CPU 44 receives a signal related to the thermodilution blood temperature from the blood temperature measuring circuit 25 . At the same time, the cardiac output calibration means 41 calculates the thermodilution heart from the injectate temperature, the injectate specific heat, the injectate specific gravity, the blood specific gravity, the blood specific heat, and the thermodiluted blood temperature based on the Stewart-Hamilton equation (1). The stroke volume is calculated and the result is outputted to the calibration signal storage means 42 as a calibration cardiac output signal.
尚、重篤な患者で熱希釈法による指示薬の注入が行なえ
ない場合には、サムホイールスイッチやデジタルスイッ
チ等の設定スイッチ、並びにキーボードより成る心拍出
量入力手段５０により相応の心拍出量の値が入力され、
校正時の心拍出量値として校正時信号記憶手段４２に出
力するという方法を採る。If the patient is seriously ill and cannot inject the indicator using the thermodilution method, the appropriate cardiac output can be determined using the cardiac output input means 50, which consists of a setting switch such as a thumbwheel switch or digital switch, and a keyboard. The value of is entered and
A method is adopted in which the value is outputted to the calibration signal storage means 42 as the cardiac output value at the time of calibration.
校正時信号記憶手段４２は、熱希釈法による心拍出量値
、あるいは前記心拍出量入力手段５０によって入力され
た心拍出量値を校正時心拍出量として記憶保持すると共
に、血液温度計測回路２５からの血液温度信号と平衡温
度計測回路２６からの平衡温度信号を、それぞれ校正時
血液温度、校正時平衡温度として保持記憶する。そして
、連続心拍出量演算手段４３から要求があった場合、記
憶保持したデータを出力する。The calibration signal storage means 42 stores the cardiac output value obtained by the thermodilution method or the cardiac output value input by the cardiac output input means 50 as the calibration cardiac output value, and also The blood temperature signal from the temperature measurement circuit 25 and the equilibrium temperature signal from the equilibrium temperature measurement circuit 26 are held and stored as the blood temperature at the time of calibration and the equilibrium temperature at the time of calibration, respectively. Then, when there is a request from the continuous cardiac output calculation means 43, the stored data is outputted.
定数選択手段４７は、前記校正時信号記憶手段４２が記
憶保持している校正時心拍出量に基づいて連続心拍出量
の算出に用いる定数を選択し、結果を連続心拍出量演算
手段４３に送る。The constant selection means 47 selects a constant to be used for calculating continuous cardiac output based on the cardiac output during calibration stored in the calibration signal storage means 42, and calculates the continuous cardiac output using the result. It is sent to the means 43.
連続心拍出量演算手段４３は、前記校正時信号記憶手段
４２が記憶保持している校正時心拍出量、校正時血液温
度、校正時平衡温度、並びに計測時の血液温度、計測時
の平衡温度および定数とから、以下の算出式に基づいて
連続心拍出量を演算する。The continuous cardiac output calculating means 43 calculates the cardiac output at the time of calibration, the blood temperature at the time of calibration, the equilibrium temperature at the time of calibration, the blood temperature at the time of measurement, and the equilibrium temperature at the time of measurement, which are stored and held in the signal storage means 42 at the time of calibration. Continuous cardiac output is calculated from the equilibrium temperature and constant based on the following calculation formula.
連続心拍出量の算出式として、
ＣＯ＝ＣＯＣＡＬ Ｘ
（（Ｔｔｐ −ＫＩＴＢ −ＴＢｃＡｔ）） ／ Ｔｔ
ｃＡｉ、）”Ａ（２）ここで、
ＣＯ：心拍出量、Ｃ０ＣＡ＋、：校正時の心拍出量Ｔｔ
、、：計測時の平衡温度、ＴＢ：血液温度ＴＢＣＡＬ：
校正時の血液温度、Ｋ：温度補正定数Ｔｔｅｍｉ、：校
正時の平衡温度、Ａ：定数があり、本式により校正時か
らの血液温度変化に伴う平衡温度変化の補正も成されて
いることがわかる。The formula for calculating continuous cardiac output is: CO=COCAL X ((Ttp - KITB - TBcAt)) / Tt
cAi,)”A(2) where, CO: cardiac output, C0CA+,: cardiac output at the time of calibration Tt
,,: Equilibrium temperature at the time of measurement, TB: Blood temperature TBCAL:
Blood temperature at the time of calibration, K: temperature correction constant Ttemi,: equilibrium temperature at the time of calibration, A: constant, and this formula also compensates for changes in equilibrium temperature due to changes in blood temperature since the time of calibration. Recognize.
そこで、上記（２）式を得る過程を一連の関連式を参照
しながら説明する。Therefore, the process of obtaining the above equation (2) will be explained with reference to a series of related equations.
心拍出量は、一般的に、
Ｃ０＝ｓ−■ ・・・・・・・・・・・・
（３）但し、Ｃｏ：心拍出量、Ｓ：血管断面積Ｖ：血流
速
にて表現され、また血流速と平衡温度とは実験的に以下
のように定めることができる。Cardiac output is generally calculated as C0=s−■ ・・・・・・・・・・・・
(3) However, Co: cardiac output, S: blood vessel cross-sectional area, V: blood flow velocity, and the blood flow velocity and equilibrium temperature can be determined experimentally as follows.
１ｏｇＴｔ＝Ａ−１ｏｇｖ＋Ｂ （４）但し、
Ｔｔ：平衡温度、Ａ、Ｂ：定数
上記（３）、（４）式より、校正時の心拍出量をＣＯＣ
ＡＬ ｓ同じ（校正時の平衡温度なＴｔｃＡＬとした場
合、次の関係式が得られる。1ogTt=A-1ogv+B (4) However,
Tt: equilibrium temperature, A, B: constants From equations (3) and (4) above, the cardiac output at the time of calibration is COC
If AL s is the same (TtcAL is the equilibrium temperature at the time of calibration), the following relational expression is obtained.
Ｃ０＝ＣｏｃＡＬ・（Ｔｔｚ ＴｔｃＡＬν／Ａ （
５）一方、校正時からの血液温度変化に伴う平衡温度変
化の補正は、次式により行なう。C0=CocAL・(Ttz TtcALν/A (
5) On the other hand, the equilibrium temperature change due to the blood temperature change from the time of calibration is corrected using the following equation.
Ｔ ｔ ＝Ｔｔ＊ −Ｋ・（ＴＢ −ＴＢＣＡＬ）
（６）但し、Ｔｔ＊ ：計測時の平衡温度
ＴＢ：血液温度、Ｋ：温度補正定数
ＴＢｃＡＬ：校正時の血液温度
よって、（５）式に対して（６）式の温度補正を行なう
と、連続心拍出量の演算式である（２）式が得られる。T t =Tt* −K・(TB −TBCAL)
(6) However, if Tt*: Equilibrium temperature at the time of measurement TB: Blood temperature, K: Temperature correction constant TBcAL: Blood temperature at the time of calibration, temperature correction of Equation (6) is performed on Equation (5). Equation (2), which is an arithmetic expression for continuous cardiac output, is obtained.
上記（２）式にて得られる連続心拍出量の演算の精度を
さらに上げるために、心拍出量の校正値の大きさにより
定数Ａの場合分けを行なう。つまり、式（２）、（４）
及び（５）にてＡを一つの定数としていたが、これを流
速に依存する特性値として扱い、本実施例では校正時の
心拍出量値がある基準（本実施例では２．７５）に対し
て大きい場合にはＡＨ１小さい場合はＡＬとして場合分
けを行なう。そして、これら二つに分割された定数を演
算に用いた場合について説明する。In order to further improve the accuracy of the calculation of the continuous cardiac output obtained by the above equation (2), the constant A is divided into cases depending on the magnitude of the calibrated value of the cardiac output. In other words, equations (2), (4)
In and (5), A was taken as one constant, but this is treated as a characteristic value that depends on the flow velocity, and in this example, the cardiac output value at the time of calibration is a certain standard (2.75 in this example). Cases are divided into cases such as AH1 when it is larger than that, and AL when it is smaller. Next, a case will be described in which these two constants are used in calculations.
上記（５）式を変形すると、
Ｔｔ ＝ＴｔｃＡＬＩＣＯ／Ｃ０ＣＡＬ）Ａ （７
）を得るので、心拍出量の校正値がＣ０ｃＡＬ≧２．７
５の場合の連続心拍出量の演算式を以下に示す。Transforming the above equation (5), Tt = TtcALICO/C0CAL)A (7
), the calibrated value of cardiac output is C0cAL≧2.7.
The calculation formula for continuous cardiac output in case of 5 is shown below.
心拍出量ＣＯが２．７５のときの平衡温度Ｔｔ２．ｙａ
は、（７）式から定数ＡをＡＨとしてＴ ｔａ７ｓ ＝
Ｔ ｔＣＡＬ’（２，７５／ＣＯＣＡＬ）ＡＨ（８）
となる。そして、実際の計測時には（６）式により平衡
温度Ｔｔが容易に求まるので、そのＴｔの値と上記（８
）式より得たＴｔｚ、ｔｓの値を比較した結果で次に示
す場合分けを行ない、連続心拍出量の演算を行なう。即
ち、
（ａ） Ｔｔ ＞Ｔｔ２．ｒｓのとき、ＣＯＣＡＬ”２
．７５とすると（８）式からＴ ｔｃＡＬ” Ｔ Ｌ、
７ｇとなるので、
Ｃ０＝２．７５・（”ｒ ｔ／Ｔｔｚ、 ｙｓ） ”Ａ
Ｌ（９）が得られ、また
（ｂ）’Ｔｔ≦Ｔｔｚ、ｔｓのとき、Ｃ００ＡＬは校正
時の値をそのまま用い、
ＣＯ＝ ＣＯｃＡＬ−（Ｔ ｔ／Ｔ ｔｃＡｔ、）”Ａ
Ｈ（ｌ Ｏ）により、連続心拍出量を演算する。Equilibrium temperature Tt2 when cardiac output CO is 2.75. ya
From equation (7), T ta7s =
T tCAL'(2,75/COCAL)AH(8)
becomes. During actual measurement, the equilibrium temperature Tt can be easily determined using equation (6), so the value of Tt and the above (8
) Based on the results of comparing the values of Ttz and ts obtained from the equation, the following cases are divided and the continuous cardiac output is calculated. That is, (a) Tt >Tt2. When rs, COCAL”2
．． 75, then from equation (8) T tcAL” T L,
7g, so C0=2.75・("r t/Ttz, ys) "A
When L(9) is obtained and (b)'Tt≦Ttz, ts, the value at the time of calibration is used as is for C00AL, and CO= COcAL-(T t/T tcAt,)”A
Continuous cardiac output is calculated by H(l O).
一方、心拍出量の校正値がＣ０ＣＡＬ ＜２． ７５の
場合の連続心拍出量の演算式は、以下のようになる。On the other hand, the calibration value of cardiac output is C0CAL <2. The calculation formula for continuous cardiac output in case of 75 is as follows.
この場合、心拍出量Ｃ○が２．７５のときの平衡温度Ｔ
ｔｚ、ｙｓは、（′ｌ）式の定数ＡをＡＬとして、
Ｔｔｘ、ｔｓ ＝ ＴｔｃＡＬ’（２，７５／ＣＯｅ
Ａｌ、）ＡＬ（１１）となる。そして、実際の計測時に
は（６）式により平衡温度Ｔｔを求め、そのＴｔの値と
上記（１１）式より得たＴｔｉ、ｙｓの値を比較した結
果で次に示す場合分けを行ない、連続心拍出量の演算を
行なう、即ち、
（ａ）Ｔｔ≧Ｔｔｉ、ｔｉのとき、Ｃ０ＣＡＬは校正時
の値を用い、
ｃ ｏ ＝ ｃ ｏ ｃＡＬｉ Ｔｔ／ＴｔｃＡＬ）”
ＡＬ（１２）が得られ、また
（ｂ）Ｔｔ ＜Ｔｔｚ？ｓのとき、ＣＯＣＡＬ＝２．７
５とすると（８）式からＴ ｔｅＡＬ” Ｔ ｔｉ、
ｔｓとなるので、
Ｇ Ｏ＝ ２．７５・（Ｔ ｔ／Ｔｔｚ、 ｖｓ） ”
ＡＨ（ｔ ａ ）により、連続心拍出量を演算する。従
って、血流速の絶対値を計測しなくても、連続的に高精
度な心拍出量の測定が可能となる。In this case, the equilibrium temperature T when the cardiac output C○ is 2.75
tz, ys are Ttx, ts = TtcAL' (2,75/COe
Al,)AL(11). Then, during actual measurement, the equilibrium temperature Tt is determined using equation (6), and the following cases are divided based on the results of comparing the value of Tt with the values of Tti and ys obtained from equation (11) above. Calculate stroke volume, i.e. (a) When Tt≧Tti, ti, C0CAL uses the value at the time of calibration, c o = co cALi Tt/TtcAL)”
AL(12) is obtained and (b) Tt <Ttz? When s, COCAL=2.7
5, then from equation (8), T teAL” T ti,
ts, so G O = 2.75・(T t/Ttz, vs) ”
Continuous cardiac output is calculated using AH(t a ). Therefore, it is possible to continuously and accurately measure cardiac output without measuring the absolute value of blood flow velocity.
第２図は、流速に対する平衡温度の関係を示しており、
従来の理論式、
ｌ Ｉｃ・ｖｏ
但し、Ｉｅ：電流値、■、：出力電位
Ｔゎ：血液温度、Ｋ：定数
であり、Ｔゆけ一定
かう得られる特性曲線、及び（２）、（９）（１０）、
（１２）そして（１３）式を導入するための基本式で実
験的に定めた（４）式から得られる特性曲線、並びに実
測データ（図中の黒丸印）を示しており、実験的に定め
た式の方が実測値に良く一致していることがわかるや
電源部６０では、電源トランス６１が外部からの交流電
源を降圧し、それを直流電源回路６２に供給するや直流
電源回路は、電源トランスからの交流出力電圧を平滑し
、且つ安定化した直流電圧に変換し、Ｄ Ｃ／Ｄ Ｃコ
ンバータ回路６３には計測部２０用直流電圧を、メイン
ＣＰＵ部にはメインＣＰ ０部用の直流電圧をそれぞれ
供給する。Figure 2 shows the relationship between equilibrium temperature and flow rate,
Conventional theoretical formula, l Ic・vo where Ie: current value, ■: output potential T: blood temperature, K: constant, characteristic curve obtained when T is constant, and (2), (9) (10),
It shows the characteristic curve obtained from equation (4), which was experimentally determined as the basic equation for introducing equations (12) and (13), as well as actual measurement data (black circles in the figure). In the power supply section 60, the power transformer 61 steps down the external AC power and supplies it to the DC power circuit 62. The AC output voltage from the power transformer is smoothed and converted into a stabilized DC voltage, and the DC/DC converter circuit 63 receives the DC voltage for the measuring section 20, and the main CPU section receives the DC voltage for the main CPU 0 section. DC voltage is supplied respectively.
ここで、本実施例の心拍出量測定装置における連続心拍
出量の測定処理手順について、第３図に示すフローチャ
ートを参照して説明する。Here, the continuous cardiac output measurement processing procedure in the cardiac output measuring device of this embodiment will be explained with reference to the flowchart shown in FIG.
連続心拍出量の測定を開始するにあたり、ステップＳ１
で心拍出量の校正が必要か否かの判定が行なわれる０校
正が必要とあらばステップＳ２で校正の方法を選択し、
ステップＳ３にて指示薬希釈法による心拍出量の測定を
する。To start measuring continuous cardiac output, step S1
If 0 calibration is necessary, select a calibration method in step S2.
In step S3, cardiac output is measured by the indicator dilution method.
一方、校正が必要と判断されても指示薬希釈法が実行で
きない場合は、ステップＳ９にて心拍出量入力手段を用
いて相応の心拍出量をマニュアル操作にて入力する。On the other hand, if it is determined that calibration is necessary but the indicator dilution method cannot be performed, in step S9, a corresponding cardiac output is manually input using the cardiac output input means.
次に、ステップＳ４では血液温度計測回路にて血液温度
を測定し、続くステップＳ５では平衡温度計測回路にて
平衡温度を測定する。以上の測定結果を心拍出量の校正
値、血液温度の校正値、平衡温度の校正値として、ステ
ップＳ６．Ｓ７゜Ｓ８で校正時信号記憶手段に記憶保持
し、校正の処理を終了する。また、ステップＳ１４で平
衡温度の校正値をもどに心拍出量算出の定数を選択する
。Next, in step S4, the blood temperature is measured by the blood temperature measuring circuit, and in the subsequent step S5, the equilibrium temperature is measured by the equilibrium temperature measuring circuit. The above measurement results are used as the cardiac output calibration value, the blood temperature calibration value, and the equilibrium temperature calibration value, and step S6. In S7 and S8, the calibration signal is stored in the signal storage means, and the calibration process is completed. Further, in step S14, a constant for calculating cardiac output is selected based on the calibration value of the equilibrium temperature.
前記ステップＳ１で校正が不要と判断されれば、直ちに
ステップＳＩＯの血液温度計測回路での血液温度の測定
、及びステップＳｌｌの平衡温度計測回路での平衡温度
の測定に入る。これらの測定結果並びに演算定数をもと
にステップＳＬ２で連続心拍出量の演算が行なわれ、次
のステップＳ１３で演算結果が連続心拍出量として表示
器に表示される。If it is determined in step S1 that calibration is not necessary, blood temperature measurement in the blood temperature measurement circuit in step SIO and equilibrium temperature measurement in the equilibrium temperature measurement circuit in step Sll are immediately started. Based on these measurement results and calculation constants, continuous cardiac output is calculated in step SL2, and in the next step S13, the calculation result is displayed on the display as continuous cardiac output.
以上説明した如く、本実施例によれば、交換自在な用途
の異なるカテーテルを用意して、一方で熱希釈法に基づ
き指示薬温度（注入液温度）を、他方で血液温度及び平
衡温度をそれぞれ校正時、計測時に測定し、得られた値
を電気信号に変換して電気的な演算によって連続的な心
拍出量を求めることができるという効果がある。As explained above, according to this embodiment, exchangeable catheters for different purposes are prepared, and one calibrates the indicator temperature (infusion liquid temperature) based on the thermodilution method, and the other calibrates the blood temperature and equilibrium temperature. This method has the advantage that it is possible to measure the cardiac output at the time of measurement, convert the obtained value into an electrical signal, and use electrical calculation to determine the continuous cardiac output.
また、血流速の変化を温度変化として検出し、その温度
変化情報から直接心拍出量の変化を求め、実験的にプロ
ーブ出力に合わせた関数、パラメータによって演算する
ので、血流速の絶対値を計測せずに連続的に心拍出量の
測定が行なえ、しかも計測範囲に応じた定数を演算に用
いるので測定精度の向上も図れるという効果がある。In addition, changes in blood flow velocity are detected as temperature changes, and changes in cardiac output are directly determined from the temperature change information, and calculated using functions and parameters that are experimentally matched to the probe output. The cardiac output can be measured continuously without measuring the value, and since a constant corresponding to the measurement range is used in calculations, the measurement accuracy can be improved.
さらに、被験者に対する熱希釈法による指示薬の注入が
行なえない場合、心拍出量をマニュアル入力でき、また
、人体に直接的に関わる計測部と電気的な演算を実行す
るメインＣＰＵ部とが電気的に遮断されているので、測
定に対する被験者の負担軽減、及び感染の危険性の減少
が図れ、安全な計測が行なえるという効果がある。Furthermore, if it is not possible to inject the indicator into the subject using the thermodilution method, the cardiac output can be manually input, and the measurement section directly related to the human body and the main CPU section that performs electrical calculations can be connected electrically. This has the effect of reducing the burden on the subject during measurement and reducing the risk of infection, allowing safe measurement.
尚、カテーテル２とカテーテル７を外観上一体したもの
として製造することなく、カテーテル２の指示薬注入機
構部のみをカテーテル７に一体して設け、指示液検温プ
ローブ回路は独立した構成にして指示薬注入用タンクに
挿入するようにしてもよい。Note that the catheter 2 and the catheter 7 are not manufactured as one unit in appearance, but only the indicator injection mechanism of the catheter 2 is integrated with the catheter 7, and the indicator liquid temperature measurement probe circuit is configured independently for indicator injection. It may also be inserted into a tank.
［発明の効果］
以上説明したように、本発明によれば、血流速の絶対値
を計測することなく連続的に、しかも高精度で心拍出量
を測定できる効果がある。[Effects of the Invention] As described above, according to the present invention, cardiac output can be measured continuously and with high accuracy without measuring the absolute value of blood flow velocity.
第１図は本発明に係る一実施例である心拍出量測定装置
のブロック図、
第２図は流速に対する平衡温度の関係を示す図、
第３図は本実施例に係る心拍出量測定装置の連続心拍出
量の測定処理手順を示すフローチャートである。
図中、■・・・心拍出量測定装置、２・・・指示薬注入
用及び指示薬温度検出用カテーテル、３・・・感温素子
、４，９・・・補正抵抗器、５，６，１１．１２・・・
コネクタ、７・・・血液温度・平衡温度検出用カテーテ
ル、８，１０・・・サーミスタ、１３・・・抵抗器、１
５・・・指示薬検温プローブ回路、１６・・・血液検温
プローブ回路、１７・・・平衡温度検温プローブ回路、
２０・・・計測部、２１・・・定電圧回路、２２・・・
特性値計測回路、２３・・・定電流源回路、２４・・・
注入液温度計測回路、２５・・・血液温度計測回路、２
６・・・平衡温度計測回路、２７・・・アナログスイッ
チ、２８−Ａ ／ Ｄ変換器、２９．４５・ ＲＯＭ、
３０・・・ローカルＣＰＵ、３１．４６・・・ＲＡＭ。
３５・・・オプトアイソレーション通信回路、３６゜３
７・・・光送受信回路、３８・・・光フアイバグラス、
４ｏ・・・メインＣＰＵ部、４１・・・心拍出量校正手
段、４２・・・校正時信号記憶手段、４３・・・連続心
拍出量演算手段、４４・・・メインＣＰＵ、４７・・・
定数選択手段、５０・・・心拍出量入力手段、５１・・
・表示器、６０・・・電源部、６１・・・電源トランス
、６２・・・直流電源回路、６３・・・Ｄ Ｃ／Ｄ Ｃ
コンバータ回路である。Fig. 1 is a block diagram of a cardiac output measuring device which is an embodiment of the present invention, Fig. 2 is a diagram showing the relationship between equilibrium temperature and flow velocity, and Fig. 3 is a diagram showing the cardiac output according to the present embodiment. 3 is a flowchart showing a continuous cardiac output measurement processing procedure of the measuring device. In the figure, ■... Cardiac output measuring device, 2... Catheter for indicator injection and indicator temperature detection, 3... Temperature sensing element, 4, 9... Correction resistor, 5, 6, 11.12...
Connector, 7... Catheter for detecting blood temperature/equilibrium temperature, 8, 10... Thermistor, 13... Resistor, 1
5... Indicator temperature measuring probe circuit, 16... Blood temperature measuring probe circuit, 17... Equilibrium temperature measuring probe circuit,
20... Measuring section, 21... Constant voltage circuit, 22...
Characteristic value measurement circuit, 23... constant current source circuit, 24...
Infusion fluid temperature measurement circuit, 25...Blood temperature measurement circuit, 2
6...Equilibrium temperature measurement circuit, 27-analog switch, 28-A/D converter, 29.45-ROM,
30...Local CPU, 31.46...RAM. 35...Opto isolation communication circuit, 36°3
7... Optical transmitting/receiving circuit, 38... Optical fiber glass,
4o... Main CPU section, 41... Cardiac output calibration means, 42... Calibration signal storage means, 43... Continuous cardiac output calculation means, 44... Main CPU, 47.・・・
Constant selection means, 50... Cardiac output input means, 51...
・Display unit, 60...Power supply unit, 61...Power transformer, 62...DC power supply circuit, 63...D C/D C
It is a converter circuit.
Claims (7)
電流により加温が行なわれ血流によつて冷却されて平衡
状態に達した温度を検出する平衡温度検出手段と、指示
薬液を注入して心拍出量を測定する心拍出量測定手段と
を備え、校正時において血液温度、平衡温度および心拍
出量を測定し、前記校正時の平衡温度および心拍出量と
前記校正時の心拍出量に基づき特定した心拍出量および
定数とから新たに平衡温度を算出し、また計測時におい
て血液温度と平衡温度を求め、前記校正時に求めた血液
温度と前記計測時の血液温度および平衡温度とから新た
な平衡温度を算出し、これら校正時および計測時に新た
に算出した平衡温度と前記校正時に測定した平衡温度お
よび心拍出量と前記校正時の心拍出量に基づき特定した
心拍出量および定数とから連続心拍出量を算出すること
を特徴とする心拍出量測定装置。(1) A blood temperature detection means for detecting the temperature of blood, an equilibrium temperature detection means for detecting the temperature that is heated by a constant current, cooled by blood flow, and reaches an equilibrium state, and injects an indicator liquid. and a cardiac output measurement means for measuring cardiac output during calibration, and measuring blood temperature, equilibrium temperature, and cardiac output during calibration, and measuring the equilibrium temperature and cardiac output during calibration and the calibration. The equilibrium temperature is newly calculated from the cardiac output and constant specified based on the cardiac output at A new equilibrium temperature is calculated from the blood temperature and the equilibrium temperature, and the equilibrium temperature newly calculated at the time of calibration and measurement, the equilibrium temperature and cardiac output measured at the time of the calibration, and the cardiac output at the time of the calibration. What is claimed is: 1. A cardiac output measurement device that calculates continuous cardiac output from the cardiac output and a constant specified based on the calculated cardiac output.
し、前記計測範囲の各々に関数並びに定数を設定して連
続心拍出量を算出する連続心拍出量演算手段を有するこ
とを特徴とする請求項第１項に記載の心拍出量測定装置
。(2) It has a continuous cardiac output calculation means that divides the measurement range into a plurality of parts based on the cardiac output at the time of calibration, sets a function and a constant for each of the measurement ranges, and calculates the continuous cardiac output. The cardiac output measuring device according to claim 1, characterized in that:
心拍出量演算手段とから成ることを特徴とする請求項第
１項に記載の心拍出量測定装置。(3) The cardiac output measuring device according to claim 1, wherein the cardiac output measuring means comprises a blood temperature measuring means and a thermodilution method cardiac output calculating means.
の算出に際して使用する定数を、校正時および計測時に
算出した平衡温度に基づいて選択する定数選択手段を有
することを特徴とする請求項第１項に記載の心拍出量測
定装置。(4) The feature includes constant selection means for selecting a constant specified based on the cardiac output at the time of calibration and used in calculating the continuous cardiac output based on the equilibrium temperature calculated at the time of calibration and measurement. The cardiac output measuring device according to claim 1.
設定が可能であることを特徴とする請求項第１項に記載
の心拍出量測定装置。(5) The cardiac output measurement device according to claim 1, wherein the cardiac output during calibration can be set by the operator without being measured.
動素子を備え、前記受動素子の特性値を示す信号を発生
する特性値検出手段を有することを特徴とする請求項第
１項に記載の心拍出量測定装置。(6) The heart according to claim 1, wherein the blood temperature detection means or the equilibrium temperature detection means includes a passive element and characteristic value detection means for generating a signal indicating a characteristic value of the passive element. Stroke volume measuring device.
拍出量測定装置。(7) The cardiac output measuring device according to claim 6, wherein the passive element is a resistor.
Priority Applications (1)
| Application Number | Priority Date | Filing Date | Title |
|---|---|---|---|
| JP1268223A JP2511153B2 (en) | 1989-10-17 | 1989-10-17 | Cardiac output measuring device |
Applications Claiming Priority (1)
| Application Number | Priority Date | Filing Date | Title |
|---|---|---|---|
| JP1268223A JP2511153B2 (en) | 1989-10-17 | 1989-10-17 | Cardiac output measuring device |
Publications (2)
| Publication Number | Publication Date |
|---|---|
| JPH03131227A true JPH03131227A (en) | 1991-06-04 |
| JP2511153B2 JP2511153B2 (en) | 1996-06-26 |
Family
ID=17455624
Family Applications (1)
| Application Number | Title | Priority Date | Filing Date |
|---|---|---|---|
| JP1268223A Expired - Fee Related JP2511153B2 (en) | 1989-10-17 | 1989-10-17 | Cardiac output measuring device |
Country Status (1)
| Country | Link |
|---|---|
| JP (1) | JP2511153B2 (en) |
Citations (8)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| JPS61125329A (en) * | 1984-11-21 | 1986-06-13 | テルモ株式会社 | Heart pulse output measuring apparatus |
| JPS62207435A (en) * | 1986-03-07 | 1987-09-11 | テルモ株式会社 | Catheter for measuring cardiac output |
| JPS63216538A (en) * | 1987-03-05 | 1988-09-08 | テルモ株式会社 | Apparatus for continuously measuring and recording heart rate output quantity |
| JPS63216540A (en) * | 1987-03-05 | 1988-09-08 | テルモ株式会社 | Apparatus for measuring heart rate output quantity |
| JPS63216537A (en) * | 1987-03-05 | 1988-09-08 | テルモ株式会社 | Apparatus for measuring heart rate output quantity |
| JPS63216539A (en) * | 1987-03-05 | 1988-09-08 | テルモ株式会社 | Apparatus for continuously measuring relative change of heart rate output quantity |
| JPS63216536A (en) * | 1987-03-05 | 1988-09-08 | テルモ株式会社 | Apparatus for measuring heart rate output quantity |
| JPS6470024A (en) * | 1987-03-05 | 1989-03-15 | Terumo Corp | Cardiac output measuring apparatus equipped with automatic starting function of measurement |
-
1989
- 1989-10-17 JP JP1268223A patent/JP2511153B2/en not_active Expired - Fee Related
Patent Citations (8)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| JPS61125329A (en) * | 1984-11-21 | 1986-06-13 | テルモ株式会社 | Heart pulse output measuring apparatus |
| JPS62207435A (en) * | 1986-03-07 | 1987-09-11 | テルモ株式会社 | Catheter for measuring cardiac output |
| JPS63216538A (en) * | 1987-03-05 | 1988-09-08 | テルモ株式会社 | Apparatus for continuously measuring and recording heart rate output quantity |
| JPS63216540A (en) * | 1987-03-05 | 1988-09-08 | テルモ株式会社 | Apparatus for measuring heart rate output quantity |
| JPS63216537A (en) * | 1987-03-05 | 1988-09-08 | テルモ株式会社 | Apparatus for measuring heart rate output quantity |
| JPS63216539A (en) * | 1987-03-05 | 1988-09-08 | テルモ株式会社 | Apparatus for continuously measuring relative change of heart rate output quantity |
| JPS63216536A (en) * | 1987-03-05 | 1988-09-08 | テルモ株式会社 | Apparatus for measuring heart rate output quantity |
| JPS6470024A (en) * | 1987-03-05 | 1989-03-15 | Terumo Corp | Cardiac output measuring apparatus equipped with automatic starting function of measurement |
Also Published As
| Publication number | Publication date |
|---|---|
| JP2511153B2 (en) | 1996-06-26 |
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