JPS6157764B2 - - Google Patents
Info
- Publication number
- JPS6157764B2 JPS6157764B2 JP57029476A JP2947682A JPS6157764B2 JP S6157764 B2 JPS6157764 B2 JP S6157764B2 JP 57029476 A JP57029476 A JP 57029476A JP 2947682 A JP2947682 A JP 2947682A JP S6157764 B2 JPS6157764 B2 JP S6157764B2
- Authority
- JP
- Japan
- Prior art keywords
- electrodes
- pair
- liquid
- skin
- coil
- 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.)
- Expired
Links
- 239000007788 liquid Substances 0.000 claims description 13
- 239000013060 biological fluid Substances 0.000 claims description 2
- 210000001175 cerebrospinal fluid Anatomy 0.000 description 8
- 210000000683 abdominal cavity Anatomy 0.000 description 4
- 210000004556 brain Anatomy 0.000 description 4
- 238000001514 detection method Methods 0.000 description 4
- 239000012530 fluid Substances 0.000 description 4
- 238000005259 measurement Methods 0.000 description 4
- 238000000034 method Methods 0.000 description 4
- 238000001356 surgical procedure Methods 0.000 description 4
- 208000035143 Bacterial infection Diseases 0.000 description 2
- 208000022362 bacterial infectious disease Diseases 0.000 description 2
- 238000001816 cooling Methods 0.000 description 2
- 238000010586 diagram Methods 0.000 description 2
- 230000000694 effects Effects 0.000 description 2
- 238000005868 electrolysis reaction Methods 0.000 description 2
- 208000003906 hydrocephalus Diseases 0.000 description 2
- 238000009434 installation Methods 0.000 description 2
- 210000000056 organ Anatomy 0.000 description 2
- 229920002379 silicone rubber Polymers 0.000 description 2
- 239000004945 silicone rubber Substances 0.000 description 2
- UFHFLCQGNIYNRP-UHFFFAOYSA-N Hydrogen Chemical compound [H][H] UFHFLCQGNIYNRP-UHFFFAOYSA-N 0.000 description 1
- 239000004698 Polyethylene Substances 0.000 description 1
- QVGXLLKOCUKJST-UHFFFAOYSA-N atomic oxygen Chemical compound [O] QVGXLLKOCUKJST-UHFFFAOYSA-N 0.000 description 1
- 230000005540 biological transmission Effects 0.000 description 1
- 238000006243 chemical reaction Methods 0.000 description 1
- 239000004020 conductor Substances 0.000 description 1
- 230000007423 decrease Effects 0.000 description 1
- 239000012777 electrically insulating material Substances 0.000 description 1
- 239000001257 hydrogen Substances 0.000 description 1
- 229910052739 hydrogen Inorganic materials 0.000 description 1
- 239000007943 implant Substances 0.000 description 1
- 208000015181 infectious disease Diseases 0.000 description 1
- 238000002347 injection Methods 0.000 description 1
- 239000007924 injection Substances 0.000 description 1
- 210000003734 kidney Anatomy 0.000 description 1
- 239000000463 material Substances 0.000 description 1
- 239000001301 oxygen Substances 0.000 description 1
- 229910052760 oxygen Inorganic materials 0.000 description 1
- 210000003200 peritoneal cavity Anatomy 0.000 description 1
- -1 polyethylene Polymers 0.000 description 1
- 229920000573 polyethylene Polymers 0.000 description 1
- 230000002285 radioactive effect Effects 0.000 description 1
- 210000003625 skull Anatomy 0.000 description 1
- 210000000278 spinal cord Anatomy 0.000 description 1
- 229910001220 stainless steel Inorganic materials 0.000 description 1
- 239000010935 stainless steel Substances 0.000 description 1
- 238000002604 ultrasonography Methods 0.000 description 1
- 210000000626 ureter Anatomy 0.000 description 1
- 210000002700 urine Anatomy 0.000 description 1
Description
【発明の詳細な説明】
本発明は主として水頭症の治療に用いられる脳
室−腹腔短絡管設置手術後の短絡管内の脳脊髄液
の流量を、生体の外部から無侵襲で計測するよう
にした生体用液体流量測定装置に関するものであ
る。[Detailed Description of the Invention] The present invention is designed to non-invasively measure the flow rate of cerebrospinal fluid in a shunt tube after a ventricular-peritoneal shunt tube installation surgery, which is mainly used for the treatment of hydrocephalus, from outside the living body. The present invention relates to a biological fluid flow rate measuring device.
従来このような脳室−腹腔短絡管内の脳脊髄液
の流量を測定するためには、短絡管の一部を人工
的に皮膚を隔て即ち皮膚上より冷却し、短絡管の
下流に於いて皮膚上にサーミスタ等の温度計を設
置して置き、冷却された脳脊髄液が冷却部より温
度計に到達する迄の時間を測定し、短絡管内の液
体の流量を知るようにした方法が提案されている
が、この場合は皮膚を隔て短絡管を冷却している
ために、この生体内の冷却の伝達速度が一定せ
ず、よつてその計測が不正確となり実用的でない
欠点がある。 Conventionally, in order to measure the flow rate of cerebrospinal fluid in such a ventricular-peritoneal shunt, a part of the shunt is artificially separated from the skin, that is, it is cooled from above the skin, and a part of the shunt is cooled from above the skin downstream of the shunt. A method has been proposed in which a thermometer such as a thermistor is placed on top of the tube, and the time taken for the cooled cerebrospinal fluid to reach the thermometer from the cooling section is measured to determine the flow rate of the fluid in the short-circuit tube. However, in this case, since the shunt tube is cooled through the skin, the transmission rate of the cooling within the body is not constant, and therefore the measurement is inaccurate, making it impractical.
その他の方法としては、注射器を用いて放射性
アイソトープを脳室内に注入し、外部よりこのア
イソトープの移動速度をガイドー計数管によつて
測定する方法が考えられているが、放射性アイソ
トープの注入に際して細菌感染の危険を伴い、又
放射性による副作用から考えても、度々測定する
ことは困難である欠点がある。又細菌感染は脳に
重大な結果をもたらすことは論をもたない。 Another method is to inject a radioactive isotope into the ventricles of the brain using a syringe and measure the movement speed of this isotope externally using a guide counter, but bacterial infection may occur during injection of the radioisotope. It also has the disadvantage that it is difficult to measure frequently due to the risk of radioactivity and the side effects caused by radioactivity. It is also undeniable that bacterial infection has serious consequences for the brain.
本発明は上述した欠点を回避し、所要の機器
を、短絡管設置手術時に生体の皮下に埋設し、手
術後は全て生体外部より無侵襲で髄時且つ連続的
に計測を行うことができるようにしたものであ
り、従つて全く感染やその他の副作用の心配を回
避し得るようにしたものである。尚、本発明によ
る装置は上述した脳脊髄液の流量計測に限られる
ものではなく、腎から膀胱への輸尿管内の尿の流
量測定等にも使用できるものである。 The present invention avoids the above-mentioned drawbacks, and makes it possible to implant the necessary equipment under the skin of the living body during the surgery to install the shunt tube, and to perform continuous and continuous measurements of the spinal cord from outside the living body after the surgery. Therefore, there is no need to worry about infection or other side effects. The device according to the present invention is not limited to measuring the flow rate of cerebrospinal fluid as described above, but can also be used to measure the flow rate of urine in the ureter from the kidney to the bladder.
以下図面について本発明による装置の一例を説
明する。第１図に於いて１は生体、２はその皮
膚、３は頭蓋骨、４は脳室、５は腹腔を示す。 An example of the device according to the invention will be described below with reference to the drawings. In FIG. 1, 1 is the living body, 2 is the skin, 3 is the skull, 4 is the ventricle of the brain, and 5 is the abdominal cavity.
上述したように水頭症の治療に於いては、脳室
４と腹腔５とを液体流通管いわゆる短絡管６によ
り連結し、脳室内に溜る脳脊髄液を腹腔５内に逃
すようにして治療している。この短絡管６は、内
径が例えば1.2mmのシリコンゴムにより製造され
たものを使用することができる。 As mentioned above, in the treatment of hydrocephalus, the ventricles 4 and the abdominal cavity 5 are connected by a fluid flow tube, so-called a shunt tube 6, and the cerebrospinal fluid accumulated in the ventricles is released into the abdominal cavity 5. ing. This short-circuit tube 6 may be made of silicone rubber and have an inner diameter of, for example, 1.2 mm.
本発明では、このような短絡管６に対して、気
泡発生手段７と、その下流に位置した気泡検知手
段８とを設けるものである。 In the present invention, such a short-circuit pipe 6 is provided with a bubble generating means 7 and a bubble detecting means 8 located downstream thereof.
まず気泡発生手段７についてその一例を説明す
る。この気泡発生手段７は第１図に示すように、
外部機器７ａと、生体１内に埋設される内部機器
７ｂとより構成される。外部機器７ａは、所定の
周波数例えば200KHzの周波数の信号を発振する
発振器９と、その出力が供給される外部コイル１
０とより構成されている。 First, an example of the bubble generating means 7 will be explained. This bubble generating means 7, as shown in FIG.
It is composed of an external device 7a and an internal device 7b embedded within the living body 1. The external device 7a includes an oscillator 9 that oscillates a signal at a predetermined frequency, for example, 200 KHz, and an external coil 1 to which the output is supplied.
0.
次に内部機器７ｂについて第２図を参照して説
明する。１１はこの内部機器７ｂを包んだ包埋体
であつて、例えばシリコンゴムにより形成するこ
とができる。その内部にはコイル１２、ダイオー
ド１３、定電圧素子１４等が埋込まれており、コ
イル１２の出力がダイオード１３により整流さ
れ、且つ定電圧素子例えばツエナーダイオード１
４により一定の電圧に保持されるように成されて
いる。この場合の電圧としては例えば20V程度で
ある。包埋体１１の一部には短絡管６とほゞ同様
の内径を有する貫通孔６′が形成されており、そ
の内部に１対の電解用電極１５ａ及び１５ｂが取
付けられている。この電極１５ａ，１５ｂ間には
上述したツエナーダイオード１４の両端の電圧が
印加される。この両電極１５ａ，１５ｂは図面に
示すように内部に液体が通り得るように夫々環状
に形成されている。このような１対の電解用電極
１５ａ，１５ｂを挾むようにして、更に、集電電
極１６ａ及び１６ｂが貫通孔６′の両端に取付け
られており、これら両電極１６ａ，１６ｂが短絡
線１７により電気的に短絡されている。そしてこ
のような電極１６ａ及び１６ｂが包埋体１１外の
短絡管６に連結されるように成されている。 Next, the internal device 7b will be explained with reference to FIG. Reference numeral 11 denotes an embedding body that encloses the internal device 7b, and can be made of silicone rubber, for example. A coil 12, a diode 13, a constant voltage element 14, etc. are embedded inside the coil 12, and the output of the coil 12 is rectified by the diode 13.
4 to maintain a constant voltage. The voltage in this case is, for example, about 20V. A through hole 6' having an inner diameter substantially the same as that of the short-circuit tube 6 is formed in a part of the embedded body 11, and a pair of electrolytic electrodes 15a and 15b are attached inside the through hole 6'. The voltage across the Zener diode 14 described above is applied between the electrodes 15a and 15b. As shown in the drawing, both electrodes 15a and 15b are each formed into an annular shape so that a liquid can pass therethrough. Further, current collecting electrodes 16a and 16b are attached to both ends of the through hole 6' so as to sandwich such a pair of electrolytic electrodes 15a and 15b, and these electrodes 16a and 16b are electrically connected by a shorting wire 17. is shorted to. The electrodes 16a and 16b are connected to the short-circuit tube 6 outside the embedding body 11.
尚、気泡発生手段７としてはこの他に通常周知
の注射器を使用でき、この場合は、この注射器に
より単に空気を短絡管６内に注入すればよい。 In addition, a commonly known syringe can be used as the bubble generating means 7, and in this case, air may simply be injected into the short-circuit pipe 6 using this syringe.
次に気泡検知手段８について説明する。この検
知手段８は同様に外部機器８ａと内部機器８ｂと
より構成されている。まず内部機器８ｂについて
説明する。これに短絡管６の長手方向即ち液体の
流通方向に沿つて所定の距離ｌだけ隔てて複数個
（図示の実施例では２個）の第１及び第２の電気
ギヤツプ１８ａ及び１８ｂを設け、これらを互に
電気的に直列に接続するものである。このため図
に示すように短絡管６と同様の材質より成る短絡
管６″を設け、その長さをｌより僅かに小に選定
して置き、その両端に於いて上述した電気ギヤツ
プ１８ａ及び１８ｂを形成しているものである。 Next, the bubble detection means 8 will be explained. This detection means 8 is similarly composed of an external device 8a and an internal device 8b. First, the internal device 8b will be explained. A plurality of (two in the illustrated embodiment) first and second electric gap 18a and 18b are provided at a predetermined distance l along the longitudinal direction of the short-circuiting pipe 6, that is, along the flow direction of the liquid. are electrically connected to each other in series. For this purpose, as shown in the figure, a short-circuit tube 6'' made of the same material as the short-circuit tube 6 is provided, the length of which is selected to be slightly smaller than 1, and the above-mentioned electric gap 18a and 18b are connected at both ends of the short-circuit tube 6''. It is what forms the.
これら両電気ギヤツプは本例では共に同様に形
成されているのでギヤツプ１８ａについてのみに
説明し、他方はその説明を省略する。即ち短絡管
６に連結される電極１９と、上述した短絡管６″
の先端に取付けられる電極２０とを、電気的絶縁
材料例えばポリエチレンより成る連結管２１によ
り、所定の間隔ｈを隔て互いに連結したものであ
る。この場合電極１９及び２０はその内部に液体
が通り得るように夫々透孔を設け、即ち筒状に形
成しているものである。又これら電極１９及び２
０は夫々ステンレスにより構成することができ
る。又短絡管６″の両端に設けられた電極２０
は、夫々短絡管６″の内部に埋設されている電気
導体部２２により互いに電気的に連結されてお
り、これにより両電気ギヤツプ１８ａ及び１８ｂ
が直列に接続される。尚、外側の電極１９として
は、図に示すように外表面を大きく彎曲させ、即
ち全体として外表面が球状となるように構成して
いるが、これは後述するように外部電極との対向
面を広く構成し得るように成すと共に、この電極
１９の存在位置を皮膚上より容易に判知し得るよ
うにしたためである。 Since both of these electric gaps are formed in the same manner in this example, only the gap 18a will be explained, and the explanation of the other one will be omitted. That is, the electrode 19 connected to the short-circuit tube 6 and the above-mentioned short-circuit tube 6''
The electrodes 20 attached to the tips of the tubes are connected to each other at a predetermined distance h by a connecting tube 21 made of an electrically insulating material such as polyethylene. In this case, the electrodes 19 and 20 are each provided with a through hole, that is, formed in a cylindrical shape, so that liquid can pass therethrough. Also, these electrodes 19 and 2
0 can be made of stainless steel. Further, electrodes 20 provided at both ends of the short-circuit tube 6''
are electrically connected to each other by electrical conductor portions 22 buried inside the short-circuit pipes 6'', thereby connecting both electrical gaps 18a and 18b.
are connected in series. As shown in the figure, the outer electrode 19 is configured to have a largely curved outer surface, that is, to have a spherical outer surface as a whole. This is because the electrode 19 can be configured in a wide range of configurations, and the position of the electrode 19 can be easily determined from the skin.
一方外部機器８ａは、第１図及び第３図より明
らかなように、インピーダンス検出器２３を有
し、その両端に皮膚電極２４ａ及び２４ｂを接続
している。このインピーダンス検出器２３は従来
周知であるから、その詳細な説明を省略するも例
えば100KHz程度の高周波信号を電極２４ａ及び
２４ｂ間に供給し、これに流れる高周波電流値を
測定することにより、いわゆる電極２４ａ及び２
４ｂ間のインピーダンスを検出すればよいもので
ある。２５は流量表示器である。 On the other hand, as is clear from FIGS. 1 and 3, the external device 8a has an impedance detector 23, and skin electrodes 24a and 24b are connected to both ends of the impedance detector 23. Since this impedance detector 23 is conventionally well known, a detailed explanation thereof will be omitted. However, by supplying a high frequency signal of, for example, about 100 KHz between the electrodes 24a and 24b and measuring the value of the high frequency current flowing therein, the impedance detector 23 is connected to the so-called electrode 24a and 2
It is sufficient to detect the impedance between 4b. 25 is a flow rate indicator.
上述した本発明による装置は、脳室−腹腔短絡
管設置手術に際して生体の皮下数mmの深さに埋設
されるものである。 The above-described device according to the present invention is implanted at a depth of several mm under the skin of a living body during a ventricular-peritoneal shunt tube installation surgery.
次にその使用方法及び動作について説明する。 Next, its usage and operation will be explained.
まず外部機器７ａの発振器９を動作させて、コ
イル１０に例えば200KHzの信号を供給する。こ
のコイル１０は内部機器７ｂのコイル１２と対向
させておくものであり、これにより内部機器７ｂ
のコイル１２に電圧が誘起される。この電圧はダ
イオード１３により整流され、且つツエナーダイ
オード１４により一定電圧に制御されて電解用電
極１５ａ，１５ｂ間に供給される。よつて脳室よ
り短絡管６を通じて腹腔に向つて流れている液
体、この場合は脳脊髄液はこの電極１５ａ，１５
ｂ間に於いて電解作用を受ける。即ち電気分解作
用により酸素十水素の気泡が発生する。 First, the oscillator 9 of the external device 7a is operated to supply a signal of, for example, 200 KHz to the coil 10. This coil 10 is arranged to face the coil 12 of the internal device 7b, so that the internal device 7b
A voltage is induced in the coil 12 of. This voltage is rectified by a diode 13, controlled to a constant voltage by a Zener diode 14, and supplied between the electrolysis electrodes 15a and 15b. Therefore, fluid flowing from the ventricles toward the abdominal cavity through the shunt tube 6, in this case cerebrospinal fluid, is transferred to the electrodes 15a, 15.
It is subjected to electrolytic action between b and b. That is, bubbles of oxygen and hydrogen are generated by electrolysis.
このような気泡が貫通孔６′の内室を満す大き
さになると、脳脊髄液の流れにより下流に向つて
押し流される。尚この気泡が万一電解用電極１５
ａ，１５ｂ間に停留した場合には、この両電極間
に生じる電流は短絡管内の脳脊髄液を伝わつて脳
あるいは心臓等の重要器官を刺激するおそれがあ
るが、本例ではこれら電解用電極１５ａ及び１５
ｂを挾むように、集電電極１６ａ，１６ｂを設
け、これらを短絡線１７により短絡してあるため
に、上述した電流はこの短絡回路を通り、上述し
た器官に通ずるおそれはないので、その危険性を
自動的に予防することができる。一方気泡検知手
段８の内部機器８ｂに於いては、短絡管６及び
６″を通じて脊髄液が順次流通しており、これに
より電極１９と２０とが電気的にほとんど短絡し
ている。即ち１対の電気ギヤツプ１８ａ及び１８
ｂ間のインピーダンスは非常に低い状態にある。 When such bubbles reach a size that fills the inner chamber of the through hole 6', they are swept downstream by the flow of cerebrospinal fluid. In addition, in the unlikely event that this bubble
If the current remains between electrodes a and 15b, there is a risk that the current generated between these two electrodes will travel through the cerebrospinal fluid in the shunt tube and stimulate important organs such as the brain or heart, but in this example, these electrolytic electrodes 15a and 15
Since the current collecting electrodes 16a and 16b are provided so as to sandwich the electrodes 16a and 16b, and these are short-circuited by the short-circuit wire 17, there is no risk that the above-mentioned current will pass through this short-circuit and reach the above-mentioned organs, so there is no risk of this happening. can be automatically prevented. On the other hand, in the internal device 8b of the bubble detection means 8, spinal fluid is sequentially flowing through the short-circuit tubes 6 and 6'', so that the electrodes 19 and 20 are almost electrically short-circuited. electric gap 18a and 18
The impedance between b and b is in a very low state.
よつて今インピーダンス検出器２３の皮膚電極
２４ａ及び２４ｂを、上述した内部機器８ｂの
夫々の電極１９に対向させておくときは、この皮
膚電極２４ａ及び２４ｂ間のインピーダンスがこ
れにより計測され、第４図に於いて時点t1以前に
示すように低いインピーダンス値Z1を示す。 Therefore, when the skin electrodes 24a and 24b of the impedance detector 23 are placed opposite the respective electrodes 19 of the internal device 8b described above, the impedance between the skin electrodes 24a and 24b is measured thereby, and the fourth In the figure, a low impedance value Z 1 is shown before time t 1 .
このような状態で上述した気泡が検知手段８の
内部機器８ｂに於ける第１の電気ギヤツプ１８ａ
に到達すると、この電極１９及び２０間に於ける
インピーダンスが急激に上昇する。この値を第４
図に於いてZ2として示している。この気泡が短絡
管６″内に入ると再び電極１９及び２０間は液に
より短絡され、それら間のインピーダンスが低下
し、Z1となる。斯くして気泡が順次押し流され、
これが更に第２の電気ギヤツプ１８ｂに到達する
と、再びイピーダンスがZ2まで上昇する。この時
点をt2で示している。このようにして気泡が第１
のギヤツプ１８ａ及び第２のギヤツプ１８ｂを通
過する時間Ｔを知ることにより、管６及び６″の
内径が知られていることからして、斯かる管内を
通ずる液体の流量を知ることができる。 In such a state, the above-mentioned air bubbles are detected in the first electric gap 18a in the internal device 8b of the detection means 8.
When this point is reached, the impedance between the electrodes 19 and 20 increases rapidly. Set this value to 4th
It is shown as Z 2 in the figure. When this bubble enters the short-circuit tube 6'', the electrodes 19 and 20 are again short-circuited by the liquid, and the impedance between them decreases to Z 1.The bubbles are thus successively swept away,
When this further reaches the second electric gap 18b, the impedance increases again to Z2 . This point is designated as t2 . In this way, the bubbles
By knowing the time T for passing through the first gap 18a and the second gap 18b, the flow rate of the liquid through the tubes can be determined, given that the inner diameters of the tubes 6 and 6'' are known.
上述した流量表示器２５はその換算によつて自
動的に表示する機器である。この機器の構成も本
発明の要旨に直接関係がなく、周知の技術で構成
し得るものであるから、その詳細な説明を省略す
る。 The above-mentioned flow rate indicator 25 is a device that automatically displays the value based on the conversion. The configuration of this device is also not directly related to the gist of the present invention and can be configured using well-known technology, so detailed explanation thereof will be omitted.
尚以上は電気ギヤツプを第１及び第２の１８ａ
及び１８ｂとして２個設けた場合であるが、これ
に限らず３個以上設け、電極２４ａ及び２４ｂを
夫々最外側の電気ギヤツプの外側の電極に対向さ
せることにより、夫々の電気ギヤツプ１８ａ，１
８ｂ……において順次第４図に示す如きパルスが
得られ、よつて夫々の通過時間を平均して検出す
ることができ、よつて、更に平均的な速度を知る
ことができ、より正確な流量を検出することが可
能となる。 In the above, the electric gap is connected to the first and second 18a.
This is a case where two or more electrodes 24a and 18b are provided, but the present invention is not limited to this, and by providing three or more electrodes and making the electrodes 24a and 24b face the outer electrodes of the outermost electric gap, the respective electric gaps 18a, 1
At 8b..., pulses as shown in Fig. 4 are obtained in sequence, and therefore each passing time can be averaged and detected, and the average speed can be determined to obtain a more accurate flow rate. It becomes possible to detect.
尚、従来気泡の移動速度を測定するため、超音
波を使用したドツプラー法が用いられていたが、
流量が少なく気泡の移動速度が遅い場合にはこの
ドツプラー法では検出できない欠点があつた。例
えば0.033ml／分以下の流量のときは、測定でき
ない欠点があつたが、上述した本発明によればこ
の従来の欠点を回避しより正確に測定ができる特
徴を有するものである。 Conventionally, the Doppler method using ultrasound was used to measure the moving speed of bubbles, but
This Doppler method had the disadvantage that it could not be detected when the flow rate was small and the moving speed of the bubbles was slow. For example, when the flow rate was 0.033 ml/min or less, there was a drawback that measurement was not possible, but the present invention described above avoids this conventional drawback and has the feature of being able to perform measurements more accurately.
第１図は本発明による装置の使用状態の概略を
示す一部を断面とした説明図、第２図及び第３図
はその一部の機器を示す縦断面図、第４図は本発
明の説明に使用する波形図である。
１は生体、４は脳室、５は腹腔、６は短絡管、
７は気泡発生手段、８は気泡検知手段、１８ａ，
１８ｂは第１及び第２の電気ギヤツプ、１９及び
２０は夫々電極、２３はインピーダンス検出器、
２４ａ，２４ｂはその皮膚電極である。
FIG. 1 is an explanatory diagram, partially in cross section, showing an outline of the usage state of the device according to the present invention, FIGS. 2 and 3 are longitudinal sectional views showing some of the equipment, and FIG. It is a waveform diagram used for explanation. 1 is the living body, 4 is the ventricle, 5 is the peritoneal cavity, 6 is the shunt duct,
7 is a bubble generating means, 8 is a bubble detecting means, 18a,
18b is a first and second electric gap, 19 and 20 are electrodes, 23 is an impedance detector,
24a and 24b are the skin electrodes.
Claims (1)
の気泡を検知する気泡検知手段を有し、該気泡検
知手段は、外部機器と内部機器とよりなり、上記
内部機器は、上記液体流通管の一部に連結されて
該液体流通管と共に生体内に埋設されるものであ
つて、上記液体流通管を通ずる液体の流通方向に
沿つて所定の距離を隔てて複数個の電気ギヤツプ
を有し、これらの各電気ギヤツプは夫々対をなす
電極が互に対向して構成されてなり、上記外部機
器は、最外側に位置する上記電気ギヤツプの外側
の電極に対して、上記生体の皮膚上より対向して
配置される一対の皮膚電極と、該一対の皮膚電極
間のインピーダンスを測定する機器よりなること
を特徴とする生体用液体流量測定装置。 ２ 上記特許請求の範囲の第１項に記載した気泡
発生手段は、電磁波により電圧が誘起されるコイ
ルと、該コイルにより生じた電圧が印加され且
つ、上記液体流通管を通じて流れる液体と接触す
る如く、配置された一対の電解用電極と、該一対
の電解用電極を挾むように対向して配置された一
対の集電電極と、該一対の集電電極を電気的に短
絡する短絡線とよりなることを特徴とする生体用
液体流量測定装置。[Scope of Claims] 1. A bubble detecting means for detecting bubbles in a liquid flow pipe generated by a bubble generating means, the bubble detecting means comprising an external device and an internal device, and the internal device comprises the above-mentioned internal device. A plurality of electric gears are connected to a part of the liquid distribution tube and buried in the living body together with the liquid distribution tube, and are separated by a predetermined distance along the flow direction of the liquid through the liquid distribution tube. Each of these electric gap is configured with a pair of electrodes facing each other, and the external device is configured to detect the temperature of the living body with respect to the outer electrode of the outermost electric gap. 1. A biological fluid flow measuring device comprising: a pair of skin electrodes that are placed facing each other on the skin; and a device that measures impedance between the pair of skin electrodes. 2. The bubble generating means described in claim 1 includes a coil to which a voltage is induced by electromagnetic waves, and a coil to which the voltage generated by the coil is applied and which is in contact with the liquid flowing through the liquid flow pipe. , consisting of a pair of electrolytic electrodes arranged, a pair of current collecting electrodes arranged facing each other so as to sandwich the pair of electrolytic electrodes, and a shorting line that electrically shorts the pair of current collecting electrodes. A biological liquid flow rate measuring device characterized by:
Priority Applications (1)
| Application Number | Priority Date | Filing Date | Title |
|---|---|---|---|
| JP57029476A JPS58146334A (en) | 1982-02-25 | 1982-02-25 | Apparatus for measuring flow amount of liquid for living body |
Applications Claiming Priority (1)
| Application Number | Priority Date | Filing Date | Title |
|---|---|---|---|
| JP57029476A JPS58146334A (en) | 1982-02-25 | 1982-02-25 | Apparatus for measuring flow amount of liquid for living body |
Publications (2)
| Publication Number | Publication Date |
|---|---|
| JPS58146334A JPS58146334A (en) | 1983-08-31 |
| JPS6157764B2 true JPS6157764B2 (en) | 1986-12-08 |
Family
ID=12277136
Family Applications (1)
| Application Number | Title | Priority Date | Filing Date |
|---|---|---|---|
| JP57029476A Granted JPS58146334A (en) | 1982-02-25 | 1982-02-25 | Apparatus for measuring flow amount of liquid for living body |
Country Status (1)
| Country | Link |
|---|---|
| JP (1) | JPS58146334A (en) |
Families Citing this family (2)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| US6685638B1 (en) * | 2002-12-23 | 2004-02-03 | Codman & Shurtleff, Inc. | Acoustic monitoring system |
| WO2010062997A2 (en) * | 2008-11-26 | 2010-06-03 | Pronk Technologies, Inc. | Pump tester |
-
1982
- 1982-02-25 JP JP57029476A patent/JPS58146334A/en active Granted
Also Published As
| Publication number | Publication date |
|---|---|
| JPS58146334A (en) | 1983-08-31 |
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