JPH0361448B2 - - Google Patents
Info
- Publication number
- JPH0361448B2 JPH0361448B2 JP59013379A JP1337984A JPH0361448B2 JP H0361448 B2 JPH0361448 B2 JP H0361448B2 JP 59013379 A JP59013379 A JP 59013379A JP 1337984 A JP1337984 A JP 1337984A JP H0361448 B2 JPH0361448 B2 JP H0361448B2
- Authority
- JP
- Japan
- Prior art keywords
- pressure
- catheter
- sensor
- measuring
- metal plate
- 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 - Lifetime
Links
- 229910052751 metal Inorganic materials 0.000 claims description 13
- 239000002184 metal Substances 0.000 claims description 13
- PXHVJJICTQNCMI-UHFFFAOYSA-N Nickel Chemical compound [Ni] PXHVJJICTQNCMI-UHFFFAOYSA-N 0.000 claims description 6
- 230000002785 anti-thrombosis Effects 0.000 claims description 6
- BASFCYQUMIYNBI-UHFFFAOYSA-N platinum Chemical compound [Pt] BASFCYQUMIYNBI-UHFFFAOYSA-N 0.000 claims description 6
- PCHJSUWPFVWCPO-UHFFFAOYSA-N gold Chemical compound [Au] PCHJSUWPFVWCPO-UHFFFAOYSA-N 0.000 claims description 4
- 229910052737 gold Inorganic materials 0.000 claims description 4
- 239000010931 gold Substances 0.000 claims description 4
- BQCADISMDOOEFD-UHFFFAOYSA-N Silver Chemical compound [Ag] BQCADISMDOOEFD-UHFFFAOYSA-N 0.000 claims description 3
- 238000001727 in vivo Methods 0.000 claims description 3
- 229910052759 nickel Inorganic materials 0.000 claims description 3
- 229910052697 platinum Inorganic materials 0.000 claims description 3
- 229910052709 silver Inorganic materials 0.000 claims description 3
- 239000004332 silver Substances 0.000 claims description 3
- KDLHZDBZIXYQEI-UHFFFAOYSA-N Palladium Chemical compound [Pd] KDLHZDBZIXYQEI-UHFFFAOYSA-N 0.000 description 4
- 239000004033 plastic Substances 0.000 description 4
- 239000000463 material Substances 0.000 description 3
- XLYOFNOQVPJJNP-UHFFFAOYSA-N water Substances O XLYOFNOQVPJJNP-UHFFFAOYSA-N 0.000 description 3
- 208000007536 Thrombosis Diseases 0.000 description 2
- 238000010521 absorption reaction Methods 0.000 description 2
- 229910045601 alloy Inorganic materials 0.000 description 2
- 239000000956 alloy Substances 0.000 description 2
- 230000036772 blood pressure Effects 0.000 description 2
- 238000010586 diagram Methods 0.000 description 2
- 238000003780 insertion Methods 0.000 description 2
- 230000037431 insertion Effects 0.000 description 2
- 238000005259 measurement Methods 0.000 description 2
- 239000012528 membrane Substances 0.000 description 2
- 150000002739 metals Chemical class 0.000 description 2
- 238000000034 method Methods 0.000 description 2
- 229910052763 palladium Inorganic materials 0.000 description 2
- 210000003462 vein Anatomy 0.000 description 2
- JOYRKODLDBILNP-UHFFFAOYSA-N Ethyl urethane Chemical compound CCOC(N)=O JOYRKODLDBILNP-UHFFFAOYSA-N 0.000 description 1
- 206010040844 Skin exfoliation Diseases 0.000 description 1
- RTAQQCXQSZGOHL-UHFFFAOYSA-N Titanium Chemical compound [Ti] RTAQQCXQSZGOHL-UHFFFAOYSA-N 0.000 description 1
- 210000000709 aorta Anatomy 0.000 description 1
- 230000004872 arterial blood pressure Effects 0.000 description 1
- 230000001746 atrial effect Effects 0.000 description 1
- 238000011888 autopsy Methods 0.000 description 1
- 230000017531 blood circulation Effects 0.000 description 1
- 210000001715 carotid artery Anatomy 0.000 description 1
- 239000011248 coating agent Substances 0.000 description 1
- 238000000576 coating method Methods 0.000 description 1
- 230000000694 effects Effects 0.000 description 1
- 238000009713 electroplating Methods 0.000 description 1
- 238000007917 intracranial administration Methods 0.000 description 1
- 210000004731 jugular vein Anatomy 0.000 description 1
- 230000003204 osmotic effect Effects 0.000 description 1
- 230000035699 permeability Effects 0.000 description 1
- 230000035945 sensitivity Effects 0.000 description 1
- 238000004544 sputter deposition Methods 0.000 description 1
- 229920003051 synthetic elastomer Polymers 0.000 description 1
- 239000005061 synthetic rubber Substances 0.000 description 1
- 229910052719 titanium Inorganic materials 0.000 description 1
- 239000010936 titanium Substances 0.000 description 1
- 238000001771 vacuum deposition Methods 0.000 description 1
- 238000005303 weighing Methods 0.000 description 1
Description
【発明の詳細な説明】
〔産業上の利用分野〕
血圧、頭蓋内圧、子宮内圧等を測定する方法と
しては、小型の圧力トランスデユーサーを直接体
内に挿入する方法と、カテーテルによつて生体圧
を体外に導き体外にある圧力トランスデユーサー
で測定する方法の2通りがある。本発明は前者の
方法における圧力センサーの改良に関するもので
ある。[Detailed Description of the Invention] [Industrial Application Field] There are two methods for measuring blood pressure, intracranial pressure, intrauterine pressure, etc., including directly inserting a small pressure transducer into the body, and measuring biological pressure using a catheter. There are two ways to measure the pressure using a pressure transducer outside the body. The present invention relates to improvements in pressure sensors in the former method.
カテーテルの先端に圧力トランスデユーサーを
内蔵したタイプの圧力センサーは、外部トランス
デユーサー型に見られる、カテーテルの振動によ
る圧波形の乱れが少ないうえ、波形の遅れや鈍化
もなく、生体内圧の精密測定には特に有用であ
る。
A pressure sensor with a built-in pressure transducer at the tip of the catheter has less disturbance in the pressure waveform due to catheter vibration, which is seen with external transducer types, and there is no delay or blunting of the waveform, making it possible to accurately measure in-vivo pressure. Particularly useful for measurements.
しかしながら、受圧面が直接体内に挿入される
ために、この部分の温度、湿度、浸透圧等の環境
は、挿入前、挿入後、あるいは挿入箇所によつて
大きく変化する。一方、圧力変換素子を封入する
コート材は、合成ゴム、ウレタン等のプラスチツ
ク材料であり、その吸水性のためにベースライン
(圧力の基準点)のドリフトや感度の変化がおこ
る欠点がある。 However, since the pressure-receiving surface is directly inserted into the body, the environment such as temperature, humidity, and osmotic pressure of this part changes significantly before and after insertion, and depending on the insertion location. On the other hand, the coating material that encloses the pressure transducer element is a plastic material such as synthetic rubber or urethane, and its water absorption properties have the disadvantage of causing drift in the baseline (pressure reference point) and changes in sensitivity.
そこで本発明者等は、このような欠点を改良
し、測定時における安定性に優れ、安全性および
抗血栓性を向上させた生体内圧力測定用センサー
を得ることを目的として、種々検討を行なつた。
Therefore, the present inventors conducted various studies with the aim of improving the above-mentioned drawbacks and obtaining a sensor for measuring in-vivo pressure that has excellent stability during measurement and improved safety and antithrombotic properties. Summer.
その結果として、圧力センサーの受圧部あるい
は、カテーテル全体に電気メツキ、真空蒸着また
は、スパツタリング等の方法で、金、銀、ニツケ
ル、白金、パラジウム、チタニウム等の金属ある
いは、合金等の簿膜を付着させることによつて、
吸水性を押さえ、安定性および抗血栓性の高い圧
力センサーを得ることを見い出したものである。
As a result, a film made of metals such as gold, silver, nickel, platinum, palladium, titanium, or alloys is attached to the pressure receiving part of the pressure sensor or the entire catheter by electroplating, vacuum deposition, sputtering, etc. By letting
It has been discovered that a pressure sensor with low water absorption and high stability and antithrombotic properties can be obtained.
本発明の1実施例を図面に従い詳述する。 One embodiment of the present invention will be described in detail with reference to the drawings.
第1図に、ダイアフラム1、ピエゾ素子2,
3,4,5、金属板6、連結棒7、筐体8、プラ
スチツクコート9、金属簿膜10、カテーテル本
体11よりなるカテーテル型の圧力センサーを示
す。 In Figure 1, a diaphragm 1, a piezo element 2,
3, 4, 5, a catheter-type pressure sensor consisting of a metal plate 6, a connecting rod 7, a housing 8, a plastic coat 9, a metal membrane 10, and a catheter body 11 is shown.
金属簿膜10およびプラスチツクコート9を通
して、ダイアフラム1に圧力が伝わると、これに
連結する連結棒7が金属板6を押し下げ、歪みを
起こさせる。金属板6の上下には、第1図のよう
に4個のピエゾ素子2,3,4,5が接着されて
おり、これらによつて第2図のようなブリツジ回
路を形成している。圧力が加わると、金属板6上
のピエゾ素子2,3は縮小、反対側のピエゾ素子
4,5、は伸びるので、各々のピエゾ素子の抵抗
値が変化し、ブリツジ内に抵抗変化に比例した電
流が流れる。この出力電流をカテーテル内を通し
てアンプ系に伝え、圧力を測定する。ピエゾ素子
は、金属板6の片側だけでも良く、この時には第
2図において、2,3は固定抵抗となる。 When pressure is transmitted to the diaphragm 1 through the metal membrane 10 and the plastic coat 9, the connecting rod 7 connected thereto pushes down the metal plate 6, causing distortion. Four piezo elements 2, 3, 4, and 5 are bonded to the top and bottom of the metal plate 6 as shown in FIG. 1, thereby forming a bridge circuit as shown in FIG. When pressure is applied, the piezo elements 2 and 3 on the metal plate 6 contract, and the piezo elements 4 and 5 on the opposite side expand, so the resistance value of each piezo element changes, and a voltage proportional to the resistance change is created within the bridge. Current flows. This output current is passed through the catheter to an amplifier system and the pressure is measured. The piezo element may be provided only on one side of the metal plate 6, and in this case, 2 and 3 in FIG. 2 are fixed resistors.
本発明による、表面の金属簿膜の材質は、金、
銀、白金、パラジウム、ニツケル等の単一金属あ
るいは、合金が良くその厚みは0.005μm〜0.5μm
の範囲が望ましいが、透水性防止の目的からは、
0.03μm以上の厚みがあれば更に望ましい。また
抗血栓性の面からは、厚さ0.05μm以上の方が望
ましい。密着強度の上ではできうる限り簿い方が
良く、0.5μm以上の厚みではカテーテルの曲げ等
によつて剥離する恐れがある。 According to the present invention, the material of the surface metal film is gold,
Single metals such as silver, platinum, palladium, nickel, etc. or alloys are good, and the thickness is 0.005μm to 0.5μm.
However, for the purpose of preventing water permeability,
It is more desirable if the thickness is 0.03 μm or more. Further, from the standpoint of antithrombotic properties, a thickness of 0.05 μm or more is desirable. In terms of adhesion strength, it is best to keep it as low as possible; if the thickness is 0.5 μm or more, there is a risk of peeling off when the catheter is bent.
以下に、本発明による生体内圧測定例について
述べる。体重10〜15Kgの雑種成犬を用い、頚道脈
および頚静脈の頭側を結紮、側面より、表面に金
をスパツタリングさせたセンサーを心臓に向つて
挿入し、センサー受圧部が各々大動脈起始部およ
び中心静脈に来るように留置した。留置後1日、
3日、5日目で動脈圧波形および右房圧波形を測
定したが、血栓によるものと思われる波形の鈍化
はなく、血圧も妥当な値を示した。また、留置5
日目の剖検所見でも、血流の遮断されている頚部
動静脈にわずかな血栓が認められたものの、感圧
部には全く血栓は見られず、抗血栓性に関しても
良好な結果が得られ、測定値に関しても信頼性が
保たれていた。 In the following, an example of measuring internal pressure in a living body according to the present invention will be described. Using an adult mongrel dog weighing 10 to 15 kg, the carotid pulse and jugular vein were ligated cranially, and a sensor with gold sputtered on the surface was inserted from the side toward the heart, with the pressure receiving part of the sensor located at the origin of each aorta. It was placed so that it was in the central and central veins. 1 day after detention
Arterial pressure waveforms and right atrial pressure waveforms were measured on the 3rd and 5th days, but there was no slowing of the waveforms, which was thought to be due to thrombus, and the blood pressures showed reasonable values. Also, detention 5
The autopsy findings on the same day showed a slight thrombus in the carotid arteries and veins where blood flow was blocked, but no thrombi were found in the pressure-sensitive areas, and good results were obtained regarding antithrombotic properties. The reliability of the measured values was also maintained.
以上のとおり、本発明は、各種生体内圧測定用
センサーとして、その安定性、安全性ならびに抗
血栓性に優れ、工業上極めて有用なるものであ
る。
As described above, the present invention has excellent stability, safety, and antithrombotic properties as a sensor for measuring various internal pressures in a living body, and is extremely useful industrially.
第1図は、本発明の1実施例を示すカテーテル
型圧力センサーの概略図、第2図は、そのブリツ
ジ回路の図である。
図中、1はダイアフラム、2,3,4および5
はピエゾ素子、6は金属板、7は連結棒、8は筐
体、9はプラスチツクコート、10は金属簿膜、
11はカテーテル本体……である。
FIG. 1 is a schematic diagram of a catheter-type pressure sensor showing one embodiment of the present invention, and FIG. 2 is a diagram of its bridge circuit. In the figure, 1 is a diaphragm, 2, 3, 4 and 5
is a piezo element, 6 is a metal plate, 7 is a connecting rod, 8 is a housing, 9 is a plastic coat, 10 is a metal film,
11 is a catheter body...
Claims (1)
圧面のダイアフラムと圧力変換素子およびカテー
テル等からなり、表面に金、白金、銀、ニツケル
等の金属簿膜を付着させることにより、安定性お
よび抗血栓性を向上させた生体内圧力測定用セン
サー。1 It has a pressure-receiving surface on the tip or the side of the tip, and consists of a diaphragm on the pressure-receiving surface, a pressure transducer, a catheter, etc., and has a metal film made of gold, platinum, silver, nickel, etc. attached to the surface to improve stability and A sensor for measuring in-vivo pressure with improved antithrombotic properties.
Priority Applications (1)
Application Number | Priority Date | Filing Date | Title |
---|---|---|---|
JP59013379A JPS60158833A (en) | 1984-01-30 | 1984-01-30 | Pressure sensor |
Applications Claiming Priority (1)
Application Number | Priority Date | Filing Date | Title |
---|---|---|---|
JP59013379A JPS60158833A (en) | 1984-01-30 | 1984-01-30 | Pressure sensor |
Publications (2)
Publication Number | Publication Date |
---|---|
JPS60158833A JPS60158833A (en) | 1985-08-20 |
JPH0361448B2 true JPH0361448B2 (en) | 1991-09-19 |
Family
ID=11831459
Family Applications (1)
Application Number | Title | Priority Date | Filing Date |
---|---|---|---|
JP59013379A Granted JPS60158833A (en) | 1984-01-30 | 1984-01-30 | Pressure sensor |
Country Status (1)
Country | Link |
---|---|
JP (1) | JPS60158833A (en) |
Families Citing this family (2)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
JPS62263429A (en) * | 1986-05-12 | 1987-11-16 | Sumitomo Bakelite Co Ltd | Temperature sensor |
JPS62263430A (en) * | 1986-05-12 | 1987-11-16 | Sumitomo Bakelite Co Ltd | Temperature sensor |
Citations (2)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
JPS5436083A (en) * | 1977-08-24 | 1979-03-16 | Toho Beslon Co | Medical catheter |
JPS5918051A (en) * | 1982-07-20 | 1984-01-30 | Japan Electronic Control Syst Co Ltd | Rear wiper drive controlling device for automobile |
-
1984
- 1984-01-30 JP JP59013379A patent/JPS60158833A/en active Granted
Patent Citations (2)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
JPS5436083A (en) * | 1977-08-24 | 1979-03-16 | Toho Beslon Co | Medical catheter |
JPS5918051A (en) * | 1982-07-20 | 1984-01-30 | Japan Electronic Control Syst Co Ltd | Rear wiper drive controlling device for automobile |
Also Published As
Publication number | Publication date |
---|---|
JPS60158833A (en) | 1985-08-20 |
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