JPH11128344A - Infusion device - Google Patents
Infusion deviceInfo
- Publication number
- JPH11128344A JPH11128344A JP9297606A JP29760697A JPH11128344A JP H11128344 A JPH11128344 A JP H11128344A JP 9297606 A JP9297606 A JP 9297606A JP 29760697 A JP29760697 A JP 29760697A JP H11128344 A JPH11128344 A JP H11128344A
- Authority
- JP
- Japan
- Prior art keywords
- flow rate
- liquid
- flow
- flow path
- infusion device
- 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.)
- Withdrawn
Links
- 238000001802 infusion Methods 0.000 title claims abstract description 46
- 239000007788 liquid Substances 0.000 claims description 53
- 238000001514 detection method Methods 0.000 claims description 21
- 238000005265 energy consumption Methods 0.000 claims description 8
- 238000006073 displacement reaction Methods 0.000 claims description 2
- 239000000126 substance Substances 0.000 abstract description 48
- 239000003814 drug Substances 0.000 abstract description 23
- 229940079593 drug Drugs 0.000 abstract description 18
- 239000010409 thin film Substances 0.000 abstract description 12
- 230000007423 decrease Effects 0.000 abstract description 10
- 239000000243 solution Substances 0.000 description 45
- 238000012545 processing Methods 0.000 description 12
- 238000000034 method Methods 0.000 description 10
- 238000005086 pumping Methods 0.000 description 6
- 238000010586 diagram Methods 0.000 description 4
- 238000002347 injection Methods 0.000 description 3
- 239000007924 injection Substances 0.000 description 3
- 239000008155 medical solution Substances 0.000 description 3
- 230000004308 accommodation Effects 0.000 description 2
- 239000012530 fluid Substances 0.000 description 2
- 239000000463 material Substances 0.000 description 2
- 230000001105 regulatory effect Effects 0.000 description 2
- XUIMIQQOPSSXEZ-UHFFFAOYSA-N Silicon Chemical compound [Si] XUIMIQQOPSSXEZ-UHFFFAOYSA-N 0.000 description 1
- 238000013459 approach Methods 0.000 description 1
- 230000037237 body shape Effects 0.000 description 1
- 239000002775 capsule Substances 0.000 description 1
- 239000000470 constituent Substances 0.000 description 1
- 230000008602 contraction Effects 0.000 description 1
- 230000001276 controlling effect Effects 0.000 description 1
- 238000012937 correction Methods 0.000 description 1
- 230000003247 decreasing effect Effects 0.000 description 1
- 230000005611 electricity Effects 0.000 description 1
- 238000000465 moulding Methods 0.000 description 1
- 229920005989 resin Polymers 0.000 description 1
- 239000011347 resin Substances 0.000 description 1
- 239000004065 semiconductor Substances 0.000 description 1
- 229910052710 silicon Inorganic materials 0.000 description 1
- 239000010703 silicon Substances 0.000 description 1
- 229920003002 synthetic resin Polymers 0.000 description 1
- 239000000057 synthetic resin Substances 0.000 description 1
Landscapes
- Infusion, Injection, And Reservoir Apparatuses (AREA)
Abstract
(57)【要約】
【課題】 バルーン式の流量低下やポンプ式の圧力変動
を解消し、任意の流量を確実に確保するとともに薬液の
圧力変動に起因する不具合を回避した新規の輸液装置を
提供し、さらには、小型、軽量化が可能で、エネルギー
消費も少ない輸液装置を実現する。
【解決手段】 流路部材２２には、薬液加圧容器に接続
された輸液チューブに接続される流入口２２ａから流出
口２２ｅまで伸びる薬液の流路が形成され、これに沿っ
て弁体部２２ｂと、薄壁２１ｃの内面に接する薄膜部２
２ｃと、薄壁２１ｄの内面に接する薄膜部２２ｄとが形
成される。弁体部２２ｂの外面側は上記の可動部材２３
の下端に当接し、可動部材２３の移動に伴って上下に移
動し、弁体部２２ｂの近傍の流路断面積を増減させる。
薄膜部２２ｃ，２２ｄは圧力センサ２７，２８が薬液圧
力を正確に検出するに充分な可撓性を備える。
PROBLEM TO BE SOLVED: To provide a new infusion device which eliminates a balloon-type flow rate decrease and a pump-type pressure fluctuation to surely secure an arbitrary flow rate and avoids problems caused by a pressure fluctuation of a chemical solution. Furthermore, an infusion device that can be reduced in size and weight and consumes less energy is realized. SOLUTION: In a flow path member 22, a flow path of a drug solution is formed extending from an inlet 22a connected to an infusion tube connected to a drug pressurized container to an outlet 22e, and a valve body 22b is formed along the flow path. And the thin film portion 2 in contact with the inner surface of the thin wall 21c
2c and a thin film portion 22d in contact with the inner surface of the thin wall 21d are formed. The outer surface side of the valve element portion 22b is
And moves up and down with the movement of the movable member 23 to increase or decrease the flow path cross-sectional area near the valve body 22b.
The thin film portions 22c and 22d have sufficient flexibility so that the pressure sensors 27 and 28 can accurately detect the chemical pressure.
Description
【０００１】[0001]
【発明の属する技術分野】本発明は輸液装置に係り、特
に、薬液を患者の体内に送り込むための医療用の輸液装
置に好適な技術に関する。BACKGROUND OF THE INVENTION 1. Field of the Invention The present invention relates to an infusion device, and more particularly to a technique suitable for a medical infusion device for sending a drug solution into a patient.
【０００２】[0002]
【従来の技術】従来、患者の体内に薬液を送り込むため
には、薬液バッグを患者の上方に吊して、薬液バッグか
ら輸液チューブを介して薬液を落下させて送り込む点滴
法が多く用いられている。この点滴法においては、薬液
をシリンダの内部にて滴下させてその滴下速度を調節す
ることにより薬液の供給速度を制御する場合が多い。し
かしながら、この点滴法では、時間の経過とともに薬液
の供給速度が変化する場合があるため、薬液の供給速度
を検出するための種々の手段が考案されている。2. Description of the Related Art Conventionally, in order to feed a drug solution into a patient's body, a drip method in which a drug solution bag is hung above a patient, and the drug solution is dropped from the drug solution bag via an infusion tube and fed is often used. I have. In this drip method, the supply rate of the chemical solution is often controlled by dropping the chemical solution inside the cylinder and adjusting the dropping speed. However, in this drip method, since the supply speed of the chemical solution may change with the passage of time, various means for detecting the supply speed of the chemical solution have been devised.
【０００３】薬液の供給速度を検出するための方法とし
ては、上記の薬液バッグに接続されたシリンダ内にて落
下する薬滴の滴下速度を検出する方法や落下する薬滴の
重量を計測する方法などがある。[0003] As a method for detecting the supply speed of the chemical liquid, there are a method of detecting the drop speed of the chemical droplet falling in the cylinder connected to the above-described chemical bag and a method of measuring the weight of the chemical droplet falling. and so on.
【０００４】上記の点滴法では、患者に対して薬液バッ
グを所定高さに吊さなければならず、また、薬液の流量
制御が困難であることから、薬液を機械的に送り出す輸
液ポンプを内蔵した各種の輸液装置が開発されている。
これらの輸液装置には種々のものがあるが、薬液注入を
簡易に行うことができるとともに携帯が可能なものとし
ては複雑な構造のものを用いることができないため、輸
液装置の構造にも自ずから制約が課せられる。In the above-described infusion method, a medical solution bag must be hung at a predetermined height with respect to a patient, and since it is difficult to control the flow rate of the medical solution, an infusion pump for mechanically sending the medical solution is incorporated. Various infusion devices have been developed.
Although there are various types of these infusion devices, it is not possible to use a device having a complicated structure that can easily inject a drug solution and be portable, so the structure of the infusion device is naturally restricted. Is imposed.
【０００５】[0005]
【発明が解決しようとする課題】輸液装置として最も簡
単なものはバルーン式と呼ばれるものであり、弾性樹脂
からなるバルーン内に薬液を注入しておき、バルーンの
収縮力によって細い輸液チューブ内に薬液を送り出すよ
うになっている。この輸液装置は極めて簡単な構造であ
るとともに動力が不要で、しかも携帯に支障のない大き
さに形成できる反面、バルーンの容積に限界があり、薬
液の注入量を多くすることができないとともに、バルー
ンの収縮に従って薬液圧力が低下していき、薬液の流量
が徐々に低下してしまい、しかも、注入速度を任意に変
えることができないという問題点がある。The simplest infusion device is a so-called balloon type in which a drug solution is injected into a balloon made of an elastic resin, and the drug solution is injected into a thin infusion tube by the contraction force of the balloon. Is sent out. This infusion device has a very simple structure and requires no power, and can be formed in a size that does not hinder carrying. However, the volume of the balloon is limited, and the injection amount of the drug solution cannot be increased. However, there is a problem that the pressure of the chemical solution decreases as the pressure decreases, the flow rate of the chemical solution gradually decreases, and the injection speed cannot be arbitrarily changed.
【０００６】一方、携帯の可能な輸液装置として小型ポ
ンプを内蔵した輸液装置もある。この種の輸液装置にお
いては、ポンプにより薬液を吐出させるために薬液の供
給速度をほぼ一定に保つことができる反面、ポンピング
動作によって輸液チューブ内の薬液に加わる圧力が周期
的に変動し、極端な場合には薬液に負圧がかかることも
あることから、輸液チューブ内において減圧に起因して
気泡が発生するという問題点がある。気泡が発生し、こ
れが患者に注入されると患者に重大な障害を与えてしま
う恐れがある。また、機械的な運動機構があるため構造
が複雑になり小型化が難しく故障の確率も高い。[0006] On the other hand, there is also an infusion device incorporating a small pump as a portable infusion device. In this type of infusion device, the supply rate of the drug solution can be kept almost constant in order to discharge the drug solution by the pump, but the pressure applied to the drug solution in the infusion tube periodically fluctuates due to the pumping operation, and extreme In such a case, a negative pressure may be applied to the liquid medicine, so that there is a problem that air bubbles are generated in the infusion tube due to the reduced pressure. Bubbles can form and can seriously injure the patient when injected into the patient. In addition, since there is a mechanical movement mechanism, the structure becomes complicated, miniaturization is difficult, and the probability of failure is high.
【０００７】そこで本発明は上記問題点を解決するもの
であり、その課題は、バルーン式の流量低下やポンプ式
の圧力変動を解消し、任意の流量を確実に確保するとと
もに薬液の圧力変動に起因する不具合を回避した新規の
輸液装置を提供することにあり、さらには、小型、軽量
化が可能で、エネルギー消費も少ない輸液装置を実現す
ることにある。Accordingly, the present invention has been made to solve the above-mentioned problems, and has as its object to eliminate a balloon-type flow rate reduction and a pump-type pressure fluctuation to ensure an arbitrary flow rate and to reduce the pressure fluctuation of a chemical solution. It is an object of the present invention to provide a new infusion device which avoids the trouble caused by the infusion device, and to realize an infusion device which can be reduced in size and weight and consumes less energy.
【０００８】[0008]
【課題を解決するための手段】上記課題を解決するため
に本発明が講じた手段は、液体を加圧するための液体加
圧部と、該液体加圧部から前記液体の供給を受けて前記
液体の流量を流路断面積の変化により調節するための流
量調節部と、該流量調節部における前記液体の流量に対
応する検出値を取得する流量検出手段と、該流量検出手
段により検出された前記検出値に応じて前記流量調節部
を駆動する流量制御手段とを備えた輸液装置である。Means taken by the present invention to solve the above-mentioned problems include a liquid pressurizing section for pressurizing a liquid, and a liquid pressurizing section receiving the supply of the liquid from the liquid pressurizing section. A flow rate adjustment unit for adjusting the flow rate of the liquid by a change in the flow path cross-sectional area, a flow rate detection unit that obtains a detection value corresponding to the flow rate of the liquid in the flow rate adjustment unit, and the flow rate detection unit detects the flow rate; A flow control unit that drives the flow rate adjusting unit according to the detection value.
【０００９】この手段によれば、液体加圧部から供給さ
れる液体を流量調節部による流路断面積の変化により流
量調節しているので、液体加圧部の加圧力が変動しても
任意の流量をほぼ一定に保持して供給することができる
から、液体の加圧力の制御を必要としないとともに、ポ
ンピング動作を必要としないため、液体の圧力変動を抑
制することができ、液体中の気泡の発生や逆流を防止す
ることができ、また、大きな動力を必要としないため、
小型、軽量化が可能になるとともに、消費エネルギーを
低減することができる。さらに、流路断面積によって流
量を制御するために微量な液体供給も可能になる。According to this means, since the flow rate of the liquid supplied from the liquid pressurizing section is adjusted by the change of the cross-sectional area of the flow path by the flow rate adjusting section, even if the pressurizing force of the liquid pressurizing section fluctuates. Can be supplied while maintaining the flow rate of the liquid substantially constant, so that the control of the pressure of the liquid is not required, and the pumping operation is not required. Because it can prevent the generation of bubbles and backflow, and does not require large power,
The size and weight can be reduced, and the energy consumption can be reduced. Further, a small amount of liquid can be supplied because the flow rate is controlled by the flow path cross-sectional area.
【００１０】ここで、前記流量検出手段は、前記液体の
流路における大断面部と小断面部との圧力差を検出する
ものである場合がある。Here, the flow rate detecting means may detect a pressure difference between a large cross section and a small cross section in the liquid flow path.
【００１１】この手段によれば、絞り式流量計の原理を
用いて検出した圧力差に基づいて液体の流量に対応する
量を求めることができる。ここで、圧力センサとしては
小型かつ軽量の半導体センサなどの高精度な検出器を用
いることができるため、装置の小型化及び軽量化を図り
つつ、微量な液体供給を容易に行うことができる。According to this means, an amount corresponding to the flow rate of the liquid can be obtained based on the pressure difference detected using the principle of the throttle type flow meter. Here, since a highly accurate detector such as a small and light semiconductor sensor can be used as the pressure sensor, it is possible to easily supply a small amount of liquid while reducing the size and weight of the device.
【００１２】また、前記流量検出手段は、前記液体の流
圧を検出するものである場合がある。In some cases, the flow rate detecting means detects a flow pressure of the liquid.
【００１３】この手段によれば、液体の流圧を検出する
ことにより、任意の場所一ヶ所にて検出ができるので、
装置をさらに小型化することが可能になる。According to this means, by detecting the flow pressure of the liquid, it is possible to detect at any one place,
The device can be further miniaturized.
【００１４】この場合には、前記流量検出手段は、前記
流量調節部における前記液体の流路内にて可動に構成さ
れた流量調整体の受ける圧力を検出し、前記流量調節部
は前記流量調整体の位置によって流路断面積を変えて前
記液体の流量を調節するように構成されていることが好
ましい。[0014] In this case, the flow rate detecting means detects a pressure received by a flow rate adjusting member movable in the flow path of the liquid in the flow rate adjusting section. It is preferable that the flow rate of the liquid is adjusted by changing the cross-sectional area of the flow path depending on the position of the body.
【００１５】この手段によれば、流量調整体の受ける圧
力に基づいて流量を検出するとともに流量調整体の位置
により流路断面積を変えて流量調節を行うため、流量検
出部と流量調節部とを一体化することができるから、さ
らなる小型化を図ることができる。According to this means, since the flow rate is detected based on the pressure received by the flow rate adjusting body and the flow rate is adjusted by changing the cross-sectional area of the flow passage depending on the position of the flow rate adjusting body, the flow rate detecting section and the flow rate adjusting section are provided. Can be integrated, further downsizing can be achieved.
【００１６】さらに、前記流量調節部は、前記液体の流
路内において可動に構成された流量調整体の位置によっ
て流路断面積を変えて前記液体の流量を調節するように
構成され、前記流量調整体の位置は、駆動部分の摩擦力
によってエネルギー消費無しで保持されるように構成さ
れていることが好ましい。Further, the flow rate adjusting section is configured to adjust a flow rate of the liquid by changing a flow path cross-sectional area according to a position of a flow rate adjuster movable in the liquid flow path. Preferably, the position of the adjusting body is configured to be held without energy consumption by the frictional force of the drive part.
【００１７】この手段によれば、流量調整体の位置が駆
動部分の摩擦力によってエネルギー消費無しで保持され
るように構成されているので、流量調節の不要な場合に
は流量調節のエネルギーをほとんどなくすことができる
ため、装置の消費エネルギーを低減することができる。According to this means, since the position of the flow rate adjusting body is held by the frictional force of the driving portion without energy consumption, when the flow rate adjustment is unnecessary, almost all of the energy of the flow rate adjustment is reduced. Since it can be eliminated, the energy consumption of the device can be reduced.
【００１８】この場合において、前記流量調整体を微動
させるための駆動機構と、前記流量調整体の微動変位若
しくは位置を検出する検出手段とを備えていることが望
ましい。ここで、流量調整体は流路と一体に構成されて
おり、構成素材の可撓性により流量調整体が変位するよ
うになっていることが好ましい。特に、流路を構成する
部材を着脱自在に構成し、容易に交換、清掃ができるよ
うに構成することが好ましい。In this case, it is desirable that a drive mechanism for finely moving the flow rate adjusting element and a detecting means for detecting a fine movement displacement or position of the flow rate adjusting element be provided. Here, it is preferable that the flow regulating body is formed integrally with the flow path, and the flow regulating body is displaced by the flexibility of the constituent material. In particular, it is preferable that the members constituting the flow path are configured to be detachable and configured to be easily replaced and cleaned.
【００１９】上記各手段においては、前記流量制御手段
は、前記流量の許容できる変動幅を実質的に示す許容変
動幅を設定し、前記流量検出手段により検出された検出
値の変化量が前記許容変動幅に対応する量となった時点
で前記流量調節部による流量調節を間欠的に行うように
構成されていることが望ましい。In each of the above means, the flow rate control means sets an allowable variation width which substantially indicates an allowable variation range of the flow rate, and the amount of change in the detection value detected by the flow rate detection means is the allowable variation range. It is desirable that the flow rate adjustment unit be configured to intermittently adjust the flow rate when the flow rate reaches the amount corresponding to the fluctuation range.
【００２０】この手段によれば、流量検出手段の検出値
の変化量が許容変動幅に対応する量となった時点で間欠
的に流量調節を行うため、流量調節部の消費エネルギー
を低減することができる。このようにすると、上記のよ
うに流量調整体の位置がエネルギー消費無しで保持され
るように構成されている場合には特に効果的である。According to this means, since the flow rate is adjusted intermittently when the amount of change in the detection value of the flow rate detection means becomes an amount corresponding to the allowable fluctuation range, the energy consumption of the flow rate control unit can be reduced. Can be. This is particularly effective in the case where the position of the flow rate adjusting member is held without energy consumption as described above.
【００２１】[0021]
【発明の実施の形態】次に、添付図面を参照して本発明
に係る実施形態について説明する。図６は本実施形態の
全体構成を示す概略構成図である。この実施形態では、
薬液を充填して所定の圧力に加圧する薬液加圧容器１０
（液体加圧部を構成する。）と、薬液加圧容器１０に輸
液チューブ４１を介して接続され、薬液の流量を制御す
るための流量制御機構２０（流量調節部と、流量検出手
段の主要部とを構成する。）と、流量制御機構２０に電
気ケーブル４２，４３を介して電気的に接続され、流量
制御機構２０を制御するための機構制御装置３０（流量
制御手段を構成する。）と、流量制御機構２０に対して
接続された輸液チューブ４４と、輸液チューブ４４の先
端部に設けられた気泡検出器４５とから構成されてい
る。Next, an embodiment according to the present invention will be described with reference to the accompanying drawings. FIG. 6 is a schematic configuration diagram showing the overall configuration of the present embodiment. In this embodiment,
Chemical pressurized container 10 for filling with a chemical and pressurizing to a predetermined pressure
(Constituting a liquid pressurizing unit) and a flow control mechanism 20 (a flow adjusting unit and a main part of a flow detecting unit) connected to the chemical pressurizing container 10 via an infusion tube 41 to control the flow rate of the chemical. And a mechanism controller 30 (which constitutes a flow control means) which is electrically connected to the flow control mechanism 20 via electric cables 42 and 43 and controls the flow control mechanism 20. And an infusion tube 44 connected to the flow control mechanism 20, and an air bubble detector 45 provided at the distal end of the infusion tube 44.
【００２２】ここで、気泡検出器４５は輸液チューブ４
４内の気泡を光学的に検出し、気泡が検出されると機構
制御装置３０に信号を送って薬液の供給を停止させるよ
うになっている。Here, the bubble detector 45 is connected to the infusion tube 4
The air bubbles in 4 are optically detected, and when the air bubbles are detected, a signal is sent to the mechanism control device 30 to stop the supply of the chemical solution.
【００２３】図２に示すように、薬液加圧容器１０は、
箱状の容器本体１１と、容器本体１１を閉鎖する蓋体１
２とを備え、これらの内部に、断面コ字型の枠板１３
と、枠板１３の内部に配置された下加圧板１４と、蓋体
１２の内面状に固定された上加圧板１５と、枠板１３に
架設され、下加圧板１４を押圧するループ状のゴム帯１
６と、下加圧板１４と上加圧板１５との間に挟持され
た、薬液を収納した薬液嚢１７とが収容されている。As shown in FIG. 2, the chemical pressurized container 10
Box-shaped container body 11 and lid 1 for closing container body 11
2 and a frame plate 13 having a U-shaped cross section
A lower pressing plate 14 disposed inside the frame plate 13; an upper pressing plate 15 fixed to the inner surface of the lid 12; and a loop-like structure that is mounted on the frame plate 13 and presses the lower pressing plate 14. Rubber band 1
6 and a liquid medicine sac 17 which holds a liquid medicine and is sandwiched between the lower pressure plate 14 and the upper pressure plate 15.
【００２４】ゴム帯１６は下加圧板１４の下面に当接し
て下加圧板１４を上方に加圧し、上加圧板１５との間に
挟持された薬液嚢１７を圧縮するため、薬液嚢１７に充
填された薬液はゴム帯１６の弾性力によって加圧されて
上記輸液チューブ４１に接続された排出口１７ａから押
し出される。上加圧板１５の下面には近接センサ１５ａ
が取り付けられ、また、下加圧板１４の上面には検出部
１４ａが固定されている。近接センサ１５ａは、検出部
１４ａが至近距離に近づくと上記機構制御装置３０に信
号を送出し、上記機構制御装置３０が薬液残量の少なく
なったことを知らせる警報を発するようになっている。The rubber band 16 comes into contact with the lower surface of the lower pressing plate 14 to press the lower pressing plate 14 upward and to compress the liquid capsule 17 sandwiched between the lower pressing plate 14 and the upper pressing plate 15. The filled drug solution is pressurized by the elastic force of the rubber band 16 and is pushed out from the outlet 17a connected to the infusion tube 41. A proximity sensor 15a is provided on the lower surface of the upper pressure plate 15.
And a detection unit 14 a is fixed to the upper surface of the lower pressure plate 14. The proximity sensor 15a sends a signal to the mechanism control device 30 when the detection unit 14a approaches a close distance, and issues an alarm informing the mechanism control device 30 that the remaining amount of the chemical solution is low.
【００２５】輸液チューブ４１は上記の流量制御機構２
０に接続されている。流量制御機構２０の内部構造を示
したものが図１である。流量制御機能２０は、内部に流
路収容部２１ａを備えた収容ケース２１と、流路収容部
２１ａ内に収容された流路部材２２とからなる。収容ケ
ース２１の流路収容部２１ａは図示しない開口部を備え
ており、流路部材２２を図の紙面と直交する方向に挿入
することにより図示のように流路収容部２１ａ内に流路
部材２２を嵌合させることができ、必要に応じて流路部
材２２を適宜に着脱させ、交換、清掃などができるよう
になっている。The infusion tube 41 is connected to the flow control mechanism 2 described above.
Connected to 0. FIG. 1 shows the internal structure of the flow control mechanism 20. The flow rate control function 20 includes a housing case 21 having a flow path housing 21a therein, and a flow path member 22 housed in the flow path housing 21a. The flow passage accommodating portion 21a of the accommodating case 21 has an opening (not shown), and the flow passage member 22 is inserted in a direction orthogonal to the plane of FIG. 22 can be fitted, and the flow path member 22 can be appropriately attached and detached as necessary, and can be replaced and cleaned.
【００２６】収容ケース２１の機構収容部２１ｂ内に
は、移動自在に配置された可動部材２３と、可動部材２
３に接触して可動部材２３を図示上下方向に移動させる
ための超音波リニアモータ２４とが収容されている。超
音波リニアモータ２４は、可動部材２３に接触する弾性
体２４ａと、弾性体２４ａに接合された２つの圧電アク
チュエータ２４ｂと、弾性体２４ａを支持する支持体２
４ｃと、支持体２４ｃを可動部材２３の側に付勢するた
めのコイルスプリング２４ｄとから構成されている。弾
性体２４ａと圧電アクチュエータ２４ｂとはいわゆるπ
形超音波リニアモータを構成する。A movable member 23 movably disposed in a mechanism accommodating portion 21b of the accommodating case 21 includes a movable member 2b.
3 and an ultrasonic linear motor 24 for moving the movable member 23 in the vertical direction in the figure. The ultrasonic linear motor 24 includes an elastic body 24a in contact with the movable member 23, two piezoelectric actuators 24b joined to the elastic body 24a, and a support 2 supporting the elastic body 24a.
4c and a coil spring 24d for urging the support 24c toward the movable member 23. The elastic body 24a and the piezoelectric actuator 24b have a so-called π
A supersonic linear motor is constructed.
【００２７】圧電アクチュエータ２４ｂに通電すると弾
性体２４ａの２つの脚部が周期的に変形し、可動部材２
３を図示上下のいずれかの方向に摩擦力によってたぐり
寄せるようにして移動させる。圧電アクチュエータ２４
ｂに通電されていない場合には、コイルスプリング２４
ｄの付勢力によって静止状態の弾性体２４ａが可動部材
２３に接触し、その接触摩擦力により可動部材２３の位
置を保持するようになっている。When electricity is supplied to the piezoelectric actuator 24b, the two legs of the elastic body 24a are periodically deformed, and the movable member 2
3 is moved in such a manner as to be approached by a frictional force in any of the upper and lower directions in the figure. Piezoelectric actuator 24
b is not energized, the coil spring 24
The elastic body 24a in a stationary state comes into contact with the movable member 23 by the urging force d, and the position of the movable member 23 is held by the contact frictional force.
【００２８】収容ケース２１には、上記機構収容部２１
ｂの下流側に流路収容部２１ａに臨む薄壁２１ｃ，２１
ｄが形成されており、この薄壁２１ｃ，２１ｄの内側に
それぞれ圧力センサ２７，２８が被着されている。圧力
センサ２７，２８は薄壁２１ｃ，２１ｄの変形に応じた
出力信号をそれぞれ出力するように構成されており、た
とえば、周知のシリコンダイヤフラム型の圧力センサを
用いることができる。The accommodation case 21 includes the mechanism accommodation section 21.
b, the thin walls 21c and 21 facing the flow channel accommodating portion 21a
d are formed, and pressure sensors 27 and 28 are attached to the insides of the thin walls 21c and 21d, respectively. The pressure sensors 27 and 28 are configured to output output signals corresponding to the deformation of the thin walls 21c and 21d, respectively. For example, a well-known silicon diaphragm type pressure sensor can be used.
【００２９】流路収容部２１ａ内に収容された流路部材
２２は耐薬品性を備えた合成樹脂などの成形によって一
体に構成されている。流路部材２２には、上記の輸液チ
ューブ４１に接続される流入口２２ａから上記輸液チュ
ーブ４４に接続される流出口２２ｅまで伸びる薬液の流
路が形成されており、この流路に沿って、可撓性の高い
薄膜部の中心に構成された弁体部２２ｂ（流量調整体を
構成する。）と、大きな断面積の流路部に臨み、上述の
薄壁２１ｃの内面に接するように配置された薄膜部２２
ｃと、上記の薄壁２１ｄの内面に接するように、オリフ
ィス状に狭められた流路に臨むように配置された薄膜部
２２ｄとが形成されている。The channel member 22 accommodated in the channel accommodating portion 21a is integrally formed by molding a synthetic resin or the like having chemical resistance. The flow path member 22 is formed with a flow path of a drug solution extending from the inflow port 22a connected to the infusion tube 41 to the outflow port 22e connected to the infusion tube 44, and along this flow path, The valve body portion 22b (constituting a flow rate adjusting member) formed at the center of the highly flexible thin film portion and the flow path portion having a large cross-sectional area are arranged so as to be in contact with the inner surface of the thin wall 21c. Thin film part 22
c and a thin film portion 22d arranged so as to be in contact with the inner surface of the thin wall 21d so as to face the flow path narrowed in an orifice shape.
【００３０】弁体部２２ｂの外面側は上記の可動部材２
３の下端に当接しており、可動部材２３の上下方向の移
動に伴って上下に移動し、弁体部２２ｂの近傍の流路の
断面積を増減させることができるように構成されてい
る。薄膜部２２ｃ，２２ｄは、上記薄壁２１ｃ，２１ｄ
に被着された圧力センサ２７，２８が流路中の薬液の圧
力を正確に検出するに充分な可撓性を備えるように薄く
形成されている。The outer surface of the valve body 22b is
3, and moves up and down with the vertical movement of the movable member 23, so that the cross-sectional area of the flow path near the valve body 22b can be increased or decreased. The thin film portions 22c, 22d are formed by the thin walls 21c, 21d.
The pressure sensors 27 and 28 are formed thin so as to have sufficient flexibility to accurately detect the pressure of the chemical solution in the flow path.
【００３１】図４は機構制御装置３０の概略構成を示す
ブロック図である。機構制御装置３０は、上記の圧力セ
ンサ２７，２８の検出値を受け取り、両者の検出値か
ら、薄膜部２０ｃの臨む大きな断面積を有する流路部
と、薄膜部２０ｄの臨む小さな断面積を有する流路部と
の圧力差を求め、この圧力差から流路部材２２内を通過
する薬液の流量を算出する中央処理部３１と、この中央
処理部３１に対して薬液の流量設定値を入力するための
流量設定部３２と、薬液の流量変動に対する許容変動幅
を入力するための許容幅設定部３３とから構成される。
中央処理部３１は、 Ｑ＝εα（π／４）ｄ2 （２Δｐ／ρ１ ）1/2 …（１） の式に基づいた処理、すなわち、演算処理やルックアッ
プテーブルの参照などの処理を行って、上記圧力差Δｐ
から検出流量Ｑを求める。上記（１）式において、εは
薬液の膨張補正係数（非圧縮性流体ではε＝１）、αは
流量係数、ｄは上記薄膜部２２ｄの流路部の断面を円形
断面に換算した場合の円形断面の直径、ρ１ は上記薄
膜部２２ｃの流路部における薬液密度を表す。流量係数
αは、直径ｄと薄膜部２２ｃの流路部の断面を円形断面
に換算した場合の円形断面の直径Ｄとの比β＝ｄ／Ｄを
用いると、 α＝Ｃ／（１−β4 ）1/2 …（２） で表される。なお、Ｃは流出係数である。FIG. 4 is a block diagram showing a schematic configuration of the mechanism control device 30. The mechanism control device 30 receives the detected values of the pressure sensors 27 and 28 and, based on the detected values of both, has a flow path portion having a large cross-sectional area facing the thin film portion 20c and a small cross-sectional area facing the thin film portion 20d. A central processing unit 31 for obtaining a pressure difference from the flow path unit and calculating a flow rate of the chemical solution passing through the flow path member 22 from the pressure difference, and inputs a set flow rate of the chemical solution to the central processing unit 31. Setting unit 32 for inputting an allowable variation width for the variation in the flow rate of the chemical solution.
The central processing unit 31 performs processing based on the equation of Q = εα (π / 4) d 2 (2Δp / ρ1) 1/2 (1), that is, processing such as arithmetic processing and lookup table lookup. And the pressure difference Δp
From the detected flow rate Q. In the above formula (1), ε is the expansion correction coefficient of the chemical solution (ε = 1 for an incompressible fluid), α is the flow coefficient, and d is the value obtained when the cross section of the flow channel of the thin film portion 22d is converted into a circular cross section. The diameter of the circular cross section, ρ1, represents the density of the chemical solution in the flow channel portion of the thin film portion 22c. The flow coefficient α can be obtained by using the ratio β = d / D of the diameter d and the diameter D of the circular cross section when the cross section of the flow path portion of the thin film portion 22c is converted into a circular cross section, α = C / (1−β 4 ) 1/2 … (2) Note that C is an outflow coefficient.
【００３２】上記のようにして求められた薬液の検出流
量Ｑは、上記流量設定部３２にて設定された設定流量Ｑ
０ と比較され、検出流量Ｑと設定流量Ｑ０ との関係
に応じて超音波リニアモータ２４に駆動信号を送出す
る。このようなフィードバック制御の具体的な方法に
は、周知のＰＩＤ制御などの種々の方法を適宜に用いる
ことができる。The detected flow rate Q of the chemical solution obtained as described above is the set flow rate Q set by the flow rate setting section 32.
0, and sends a drive signal to the ultrasonic linear motor 24 in accordance with the relationship between the detected flow rate Q and the set flow rate Q0. As a specific method of such feedback control, various methods such as well-known PID control can be appropriately used.
【００３３】ここで、上記のようにして圧力センサ２
７，２８からの検出値に基づいて中央処理部３１から常
時駆動信号を超音波リニアモータ２４に送出し、連続的
に流量制御を行ってもよいが、本実施形態では、主な電
力消費部位である流量制御機構２０（特に超音波リニア
モータ２４）の消費電力を低減するために、上記のフィ
ードバック制御を間欠的に行うようにしている。すなわ
ち、上記の設定流量Ｑ０と検出流量Ｑとの流量差ΔＱを
常時求めながら、流量差ΔＱが上記の許容幅設定部３３
にて設定された薬液流量の許容変動幅ΔＱＳ よりも小
さい場合には制御を行わず、中央処理部３１は駆動信号
を超音波リニアモータ２４に対して送出しない。流量差
ΔＱが許容変動幅ΔＱＳ を越えると、中央処理部３１
は超音波リニアモータ２４に駆動信号を送出し、可動部
材２３を移動させて流量を調節する。流量調節が或る程
度収束して検出流量Ｑが安定すると中央処理部３１は超
音波リニアモータ２４への駆動信号の送出を停止し、可
動部材２３はコイルスプリング２４ｄの付勢力によって
その位置を保持する。そして、再び流量差ΔＱがΔＱＳ
を越えるまで待機する。Here, as described above, the pressure sensor 2
The central processing unit 31 may constantly transmit a drive signal to the ultrasonic linear motor 24 based on the detection values from the detection units 7 and 28 to continuously control the flow rate. In order to reduce the power consumption of the flow control mechanism 20 (particularly, the ultrasonic linear motor 24), the above-described feedback control is intermittently performed. That is, the flow rate difference ΔQ is constantly calculated while the flow rate difference ΔQ between the set flow rate Q0 and the detected flow rate Q is set to the allowable width setting unit 33.
When the variation is smaller than the permissible variation width ΔQS of the chemical liquid flow rate set in the above, the control is not performed, and the central processing unit 31 does not send the drive signal to the ultrasonic linear motor 24. When the flow rate difference ΔQ exceeds the allowable variation width ΔQS, the central processing unit 31
Sends a drive signal to the ultrasonic linear motor 24 and moves the movable member 23 to adjust the flow rate. When the flow rate adjustment converges to some extent and the detected flow rate Q becomes stable, the central processing unit 31 stops sending the drive signal to the ultrasonic linear motor 24, and the movable member 23 holds its position by the urging force of the coil spring 24d. I do. Then, the flow rate difference ΔQ again becomes ΔQS
Wait until it exceeds.
【００３４】図５には、上記の間欠的な制御時における
本実施形態の流量差ΔＱと、上記薬液加圧容器１０内の
薬液の供給圧力Ｐ０ との経時変化を示す。本実施形態
では、薬液加圧容器１０による薬液の供給圧力Ｐ０ は
時間の経過とともに徐々に低下していくため、上記のよ
うに一旦流量を制御してもその後流量制御を停止してい
ると供給圧力Ｐ０ の低下に伴って徐々に検出流量Ｑも
低下していく。検出流量Ｑの低下が上記の許容変動幅Δ
ＱＳ を越えると、上述のように流量制御が行われて再
び流量差ΔＱが０になり、その後、再び流量差ΔＱが発
生するというように繰り返す。FIG. 5 shows a change with time of the flow rate difference ΔQ of the present embodiment and the supply pressure P0 of the chemical in the chemical pressurized container 10 during the intermittent control. In the present embodiment, since the supply pressure P0 of the chemical solution by the chemical solution pressurizing container 10 gradually decreases with the passage of time, even if the flow rate is once controlled as described above, the supply is stopped if the flow rate control is stopped. The detected flow rate Q gradually decreases as the pressure P0 decreases. The decrease in the detected flow rate Q is caused by the above-mentioned allowable fluctuation range Δ
When QS is exceeded, the flow rate control is performed as described above, the flow rate difference ΔQ becomes zero again, and thereafter, the flow rate difference ΔQ is generated again.
【００３５】仮に、薬液流量差と薬液の供給圧力差とが
ほぼ比例しているとすると、図示のように許容変動幅Δ
ＱＳ に対応する許容圧力差ΔＰＳ が存在し、供給圧
力Ｐ０ が許容圧力差ΔＰＳ だけ低下する毎に繰り返
し流量制御が行われることになる。Assuming that the difference between the flow rate of the chemical solution and the difference between the supply pressures of the chemical solution is approximately proportional, as shown in FIG.
There is an allowable pressure difference ΔPS corresponding to QS, and the flow control is repeatedly performed each time the supply pressure P0 decreases by the allowable pressure difference ΔPS.
【００３６】上記実施形態では、中央処理部３１にて流
量差ΔＱを求め、これを許容変動幅と比較することによ
り間欠的に流量制御を行っているが、圧力センサ２７な
どにより流量制御機構２０内の薬液圧力を検出し、薬液
圧力の変化が一定値（例えば、上記のΔＰＳ ）に達し
たときに流量制御を行ってもよい。In the above-described embodiment, the flow rate difference ΔQ is determined by the central processing unit 31 and the flow rate control is performed intermittently by comparing this with the allowable variation range. The flow rate control may be performed by detecting the pressure of the liquid medicine inside the chamber and when the change in the pressure of the liquid medicine reaches a constant value (for example, ΔPS).
【００３７】以上説明した本実施形態によれば、薬液加
圧容器１０から押し出された薬液には流量制御機構２０
内において流量制御が施されるため、薬液加圧容器１０
の供給圧力が変化しても所要の流量が確保される。した
がって、常にほぼ一定速度で薬液を患者に注入すること
ができる。ここで、輸液ポンプのようにポンピングを要
しないため、薬液圧力が流路内においてポンピングに伴
って上下に変動することがなく、安定した状態で患者に
供給できる。したがって、気泡の発生も抑制される。ま
た、ポンピング動作を必要とせず、流量制御のみを行う
ため、消費電力を小さくすることができるとともに流量
制御機構の剛性も低減できるため、小型化、軽量化が可
能であり、しかも、微量の薬液注入においても高精度に
流量を制御することが可能になる。According to the above-described embodiment, the chemical liquid pushed out from the chemical liquid pressurizing container 10 is provided with the flow control mechanism 20.
Since the flow rate control is performed in the inside,
The required flow rate is ensured even if the supply pressure of the gas changes. Therefore, the medicinal solution can always be injected into the patient at a substantially constant speed. Here, since pumping is not required unlike an infusion pump, the drug solution pressure can be supplied to the patient in a stable state without fluctuating up and down due to pumping in the flow path. Therefore, generation of bubbles is also suppressed. In addition, since only the flow rate control is performed without the need for a pumping operation, power consumption can be reduced, and the rigidity of the flow rate control mechanism can be reduced, so that the size and weight can be reduced. It is possible to control the flow rate with high precision even during injection.
【００３８】本実施形態では、薬液加圧容器１０の加圧
力が大きく変動しても薬液の流量制御に影響を与えにく
いため、薬液加圧容器１０の加圧機構を極めて簡単な構
造とすることが可能になった。特に、何らエネルギーを
消費しない機構で薬液を加圧できるので、消費電力を大
幅に低減することができる。In this embodiment, even if the pressure of the chemical solution pressurizing container 10 fluctuates greatly, it does not easily affect the control of the flow rate of the chemical solution, so that the pressurizing mechanism of the chemical solution pressurizing container 10 has an extremely simple structure. Is now possible. In particular, since the chemical solution can be pressurized by a mechanism that does not consume any energy, power consumption can be significantly reduced.
【００３９】本実施形態ではさらに、流量制御を間欠的
に行っているため、流量制御のために消費するエネルギ
ーも大きく低減することができた。特に、流量制御を休
止している期間において、弁体部２２ｂが摩擦力によっ
て保持されている可動部材２３により支持されているの
で、何らエネルギーを消費するこなく次の流量制御まで
待機することができる。このようにして、本実施形態の
輸液装置は、携帯しても長時間患者に薬液を送り続ける
ことができ、従来にない実用的な携帯型輸液装置を構成
することができる。In this embodiment, since the flow control is performed intermittently, the energy consumed for the flow control can be greatly reduced. In particular, during the period when the flow control is paused, the valve body portion 22b is supported by the movable member 23 held by the frictional force, so that it is possible to wait for the next flow control without consuming any energy. it can. In this manner, the infusion device of the present embodiment can continue to send a drug solution to a patient for a long time even if it is carried, and a practical portable infusion device that has never been available can be configured.
【００４０】次に、図３を参照して本発明に係る別の実
施形態について説明する。この実施形態では、上記の実
施形態と同じ薬液加圧容器１０を備えるとともに、上記
の実施形態とほぼ同様の機構制御装置を備えている。本
実施形態の流量制御機構５０は、図３に示すように、収
容ケース５１と、収容ケース５１の流路収容部５１ａに
収容された流路部材５２とを有する。収容ケース５１に
は上述と同様の可動部材５３、超音波リニアモータ５４
とを収容した機構収容部５１ｂが形成されている。Next, another embodiment according to the present invention will be described with reference to FIG. In the present embodiment, the same chemical solution pressurized container 10 as in the above embodiment is provided, and a mechanism control device substantially similar to that in the above embodiment is provided. As shown in FIG. 3, the flow control mechanism 50 of the present embodiment includes a storage case 51 and a flow path member 52 stored in a flow path storage section 51 a of the storage case 51. A movable member 53 and an ultrasonic linear motor 54 similar to those described above are
And a mechanism accommodating portion 51b accommodating these.
【００４１】流路部材５２には、上記輸液チューブ４１
に接続される流入口５２ａから輸液チューブ４４に接続
される流出口５２ｅまで伸びる流路に沿って、円錐面状
に形成された弁路部５２ｂと、上記機構収容部５１ｂと
の間に形成された薄い壁面の中央に一体に設けられた係
合弁体部５２ｃと、係合弁体部５２ｃから上記弁路部５
２ｂに向けて伸びる弁軸部５２ｄ（流量調整体を構成す
る。）とが形成されている。The infusion tube 41 is provided in the flow path member 52.
Along the flow path extending from the inflow port 52a connected to the infusion tube 44 to the outflow port 52e connected to the infusion tube 44, a valve path 52b formed in a conical surface and the mechanism accommodating section 51b are formed. An engaging valve body 52c integrally provided at the center of the thin wall surface;
A valve stem 52d (constituting a flow rate adjusting member) extending toward 2b is formed.
【００４２】係合弁体部５２ｃは機構収容部５１ｂの側
において可動部材５３の下端に取付けられた係合部５５
に係合している。可動部材５３の係合部５５の上部には
圧電体などからなる力センサ５６が可動部材５３と一体
化されている。可動部材５３は上下に移動自在に保持さ
れているが、可動部材５３の移動方向に沿った機構収容
部５１ｂの内面上にはリニアスケール５７が配設されて
おり、また、可動部材５３の上端部に対向する機構収容
部５１ｂの内面には近接センサ５８が取り付けられてい
る。The engagement valve body 52c is provided with an engagement portion 55 attached to the lower end of the movable member 53 on the side of the mechanism housing portion 51b.
Is engaged. A force sensor 56 made of a piezoelectric material or the like is integrated with the movable member 53 above the engagement portion 55 of the movable member 53. The movable member 53 is held movably up and down, but a linear scale 57 is disposed on the inner surface of the mechanism accommodating portion 51b along the moving direction of the movable member 53. A proximity sensor 58 is attached to the inner surface of the mechanism housing part 51b facing the part.
【００４３】なお、本実施形態においては、上記収容ケ
ース５１及び流路部材５２の外形は係合弁体部５２ｃ及
び弁軸部５２ｄを中心とする円筒形状に形成されてお
り、弁路部５２ｂ、係合弁体部５２ｃ、弁軸部５２ｄ及
びその周囲もまた、ほぼ回転体形状（平面図形を一つの
回転軸を中心に回転させた場合の回転軌跡を占める立体
形状）に形成されている。In this embodiment, the outer shape of the housing case 51 and the flow path member 52 is formed in a cylindrical shape centering on the engagement valve body 52c and the valve shaft 52d, and the valve passage 52b, The engagement valve body 52c, the valve shaft 52d, and the periphery thereof are also formed in a substantially rotating body shape (a three-dimensional shape that occupies a rotation trajectory when a plane figure is rotated around one rotation axis).
【００４４】この実施形態では、超音波リニアモータ５
４を駆動させて可動部材５３を上下に移動させることに
より弁軸部５２ｄを上下に移動させて薬液の流量を調節
することができるようになっている。ここで、弁軸部５
２ｄは薬液の流通によって応力を受けるが、この応力は
力センサ５６によって検出される。また、弁軸部５２ｄ
の上下方向の位置はリニアスケール５７によって検出さ
れる。In this embodiment, the ultrasonic linear motor 5
4, the movable member 53 is moved up and down, so that the valve shaft 52d is moved up and down to adjust the flow rate of the chemical solution. Here, the valve stem 5
2d receives a stress due to the flow of the chemical solution, and this stress is detected by the force sensor 56. Also, the valve stem 52d
Are detected by the linear scale 57.
【００４５】この実施形態における流量制御は面積式流
量計の原理を利用したものである。面積式流量計におい
ては、テーパ管の中に配置されたフロートの位置によっ
て流量を知ることができる。検出流量Ｑは、 Ｑ＝Ｃ（Ａ−ａ）｛Ｗｆ ／（ａρ０ ）｝1/2 …（３） で表される。ここで、Ｃは実験的に定められる流出係
数、Ａはテーパ管の断面積、ａはフロートの最大断面
積、Ｗｆ はフロートの重量、ρ０ は流体密度であ
る。この（３）式の関係は、テーパ管を上記弁路部５２
ｂとし、フロートを上記弁軸部５２ｄとし、さらに、フ
ロートの重量を力センサ５６により検出される検出値と
見なすことによって、本実施形態の場合にも同様に成立
する。The flow rate control in this embodiment utilizes the principle of the area type flow meter. In the area type flow meter, the flow rate can be known from the position of the float arranged in the tapered pipe. The detected flow rate Q is expressed as follows: Q = C (A−a) ｛Wf / (aρ0)｝ 1/2 (3) Here, C is the outflow coefficient determined experimentally, A is the cross-sectional area of the tapered pipe, a is the maximum cross-sectional area of the float, Wf is the weight of the float, and ρ0 is the fluid density. The relationship of this equation (3) is that the tapered pipe is
b, the float is used as the valve shaft portion 52d, and the weight of the float is regarded as a detection value detected by the force sensor 56, so that the present embodiment is similarly established.
【００４６】この場合、超音波リニアモータ５４が動作
していないときには、可動部材５３が超音波リニアモー
タ５４からの付勢力によって保持されているので弁軸部
５２ｄが上下に移動しないため、力センサ５６の検出値
をそのまま上記のフロートの重量Ｗｆ と見なして考え
れば、リニアスケール５７によって弁軸部５２ｄの位置
を算出し、その位置における弁路部５２ｂの断面積をＡ
とし、弁軸部５２ｄの断面積をａとすれば、（３）式に
より検出流量Ｑが求められる。In this case, when the ultrasonic linear motor 54 is not operating, since the movable member 53 is held by the urging force from the ultrasonic linear motor 54, the valve shaft 52d does not move up and down. Considering the detected value of 56 as it is as the float weight Wf, the position of the valve shaft 52d is calculated by the linear scale 57, and the sectional area of the valve passage 52b at that position is calculated as A.
Assuming that the sectional area of the valve stem 52d is a, the detected flow rate Q is obtained by the equation (3).
【００４７】検出流量Ｑが設定流量Ｑ０ と異なってい
る場合には、超音波リニアモータ５４を動作させて可動
部材５３を移動させ、弁軸部５２ｄを上下に移動させ、
断面積Ａを変えればよい。そのときのＷｆ とＡを常に
検出して再計算し、最終的に検出流量Ｑが設定流量Ｑ０
とほぼ一致するまで調節する。If the detected flow rate Q is different from the set flow rate Q0, the ultrasonic linear motor 54 is operated to move the movable member 53 and move the valve stem 52d up and down.
The sectional area A may be changed. Wf and A at that time are always detected and recalculated, and finally the detected flow rate Q becomes equal to the set flow rate Q0.
Adjust until it almost matches.
【００４８】この実施形態においても、上記の実施形態
と同様に間欠的に流量制御を行うことによって消費電力
を低減することができる。Also in this embodiment, power consumption can be reduced by intermittently controlling the flow rate as in the above-described embodiment.
【００４９】本実施形態によれば、薬液の流量調節部と
流量検出部とが一体に構成されているので、構造がきわ
めて簡単になるため、さらに小型化及び軽量化を図るこ
とが可能になる。According to the present embodiment, since the flow rate adjusting section and the flow rate detecting section for the chemical solution are integrally formed, the structure becomes extremely simple, so that the size and weight can be further reduced. .
【００５０】[0050]
【発明の効果】以上説明したように本発明によれば、液
体加圧部から供給される液体を流量調節部による流路断
面積の変化により流量調節しているので、液体加圧部の
加圧力が変動しても流量をほぼ一定に保持して供給する
ことができるから、液体の加圧力の制御を必要としない
とともに、ポンピング動作を必要としないため、液体の
圧力変動を抑制することができ、液体中の気泡の発生や
逆流を防止することができ、また、大きな動力を必要と
しないため、小型、軽量化が可能になるとともに、消費
エネルギーを低減することができる。さらに、流路断面
積によって流量を制御するために微量な液体供給も可能
になる。As described above, according to the present invention, the flow rate of the liquid supplied from the liquid pressurizing section is adjusted by changing the flow path cross-sectional area by the flow rate adjusting section. Even if the pressure fluctuates, the flow rate can be maintained at a substantially constant level, so that it is not necessary to control the pressure of the liquid and it is not necessary to perform a pumping operation. Thus, the generation and backflow of bubbles in the liquid can be prevented, and since large power is not required, the size and weight can be reduced, and the energy consumption can be reduced. Further, a small amount of liquid can be supplied because the flow rate is controlled by the flow path cross-sectional area.
【図１】本発明に係る輸液装置の実施形態の流量制御機
構を示す概略断面図である。FIG. 1 is a schematic sectional view showing a flow control mechanism of an embodiment of an infusion device according to the present invention.
【図２】同実施形態における薬液加圧容器の構造を示す
概略断面図である。FIG. 2 is a schematic cross-sectional view showing a structure of a chemical liquid pressurizing container in the same embodiment.
【図３】上記実施形態とは異なる流量制御機構を示す概
略断面図である。FIG. 3 is a schematic sectional view showing a flow control mechanism different from the above embodiment.
【図４】上記実施形態における機構制御装置を示す概略
構成図である。FIG. 4 is a schematic configuration diagram showing a mechanism control device in the embodiment.
【図５】上記実施形態の間欠的な制御動作に伴う流量差
及び供給圧力の変動を示すグラフである。FIG. 5 is a graph showing a change in flow rate and a change in supply pressure due to an intermittent control operation of the embodiment.
【図６】上記実施形態の全体構成を示す概略構成図であ
る。FIG. 6 is a schematic configuration diagram showing the overall configuration of the embodiment.
１０ 薬液加圧容器 １７ 薬液嚢 ２０，５０ 流量制御機構 ２１，５１ 収容ケース ２２，５２ 流路部材 ２２ｂ 弁体部 ２３，５３ 可動部材 ２４，５４ 超音波リニアモータ ２７，２８ 圧力センサ ３０ 機構制御装置 ３１ 中央処理部 ３２ 流量設定部 ３３ 許容幅設定部 ５２ｂ 弁路部 ５２ｃ 係合弁体部 ５２ｄ 弁軸部 ５６ 力センサ ５７ リニアスケール DESCRIPTION OF SYMBOLS 10 Chemical liquid pressurized container 17 Chemical liquid bag 20, 50 Flow control mechanism 21, 51 Storage case 22, 52 Flow path member 22b Valve body part 23, 53 Movable member 24, 54 Ultrasonic linear motor 27, 28 Pressure sensor 30 Mechanism control device 31 Central processing unit 32 Flow rate setting unit 33 Allowable width setting unit 52b Valve path unit 52c Engaging valve body unit 52d Valve shaft unit 56 Force sensor 57 Linear scale
Claims (7)
液体加圧部から前記液体の供給を受けて前記液体の流量
を流路断面積の変化により調節するための流量調節部
と、該流量調節部における前記液体の流量に対応する検
出値を取得する流量検出手段と、該流量検出手段により
検出された前記検出値に応じて前記流量調節部を駆動す
る流量制御手段とを備えた輸液装置。1. A liquid pressurizing unit for pressurizing a liquid, and a flow rate adjusting unit for receiving a supply of the liquid from the liquid pressurizing unit and adjusting a flow rate of the liquid by changing a cross-sectional area of the flow path. A flow rate detection unit that acquires a detection value corresponding to the flow rate of the liquid in the flow rate adjustment unit; and a flow rate control unit that drives the flow rate adjustment unit in accordance with the detection value detected by the flow rate detection unit. Infusion device.
は、前記液体の流路における大断面部と小断面部との圧
力差を検出するものである輸液装置。2. The infusion device according to claim 1, wherein the flow rate detecting means detects a pressure difference between a large cross section and a small cross section in the flow path of the liquid.
は、前記液体の流圧を検出するものである輸液装置。3. The infusion device according to claim 1, wherein said flow rate detecting means detects a flow pressure of said liquid.
は、前記流量調節部における前記液体の流路内にて可動
に構成された流量調整体の受ける圧力を検出し、前記流
量調節部は前記流量調整体の位置によって流路断面積を
変えて前記液体の流量を調節するように構成されている
輸液装置。4. The flow rate detection unit according to claim 3, wherein the flow rate detection unit detects a pressure received by a flow rate adjustment body movable in the flow path of the liquid in the flow rate adjustment unit, and the flow rate adjustment unit is configured to detect the pressure. An infusion device configured to adjust the flow rate of the liquid by changing the cross-sectional area of the flow path depending on the position of the flow rate adjusting body.
前記液体の流路内において可動に構成された流量調整体
の位置によって流路断面積を変えて前記液体の流量を調
節するように構成され、前記流量調整体の位置は、駆動
部分の摩擦力によってエネルギー消費無しで保持される
ように構成されている輸液装置。5. The flow control device according to claim 1, wherein
The flow rate of the liquid is adjusted by changing the cross-sectional area of the flow path according to the position of the flow rate adjuster movably configured in the flow path of the liquid, and the position of the flow rate adjuster is determined by a frictional force of a driving portion. An infusion device configured to be held without energy consumption by.
動させるための駆動機構と、前記流量調整体の微動変位
若しくは位置を検出する検出手段とを備えている輸液装
置。6. The infusion device according to claim 5, further comprising: a drive mechanism for finely moving the flow rate adjusting body; and a detecting means for detecting a fine movement displacement or a position of the flow rate adjusting body.
項において、前記流量制御手段は、前記流量の許容でき
る変動幅を実質的に示す許容変動幅を設定し、前記流量
検出手段により検出された検出値の変化量が前記許容変
動幅に対応する量となった時点で前記流量調節部による
流量調節を間欠的に行うように構成されている輸液装
置。7. One of claims 1 to 6
In the item, the flow rate control means sets an allowable variation width that substantially indicates an allowable variation width of the flow rate, and a change amount of a detection value detected by the flow rate detection means is an amount corresponding to the allowable variation width. An infusion device configured to intermittently adjust the flow rate by the flow rate adjusting unit at the time when the infusion device is set.
Priority Applications (1)
| Application Number | Priority Date | Filing Date | Title |
|---|---|---|---|
| JP9297606A JPH11128344A (en) | 1997-10-29 | 1997-10-29 | Infusion device |
Applications Claiming Priority (1)
| Application Number | Priority Date | Filing Date | Title |
|---|---|---|---|
| JP9297606A JPH11128344A (en) | 1997-10-29 | 1997-10-29 | Infusion device |
Publications (1)
| Publication Number | Publication Date |
|---|---|
| JPH11128344A true JPH11128344A (en) | 1999-05-18 |
Family
ID=17848741
Family Applications (1)
| Application Number | Title | Priority Date | Filing Date |
|---|---|---|---|
| JP9297606A Withdrawn JPH11128344A (en) | 1997-10-29 | 1997-10-29 | Infusion device |
Country Status (1)
| Country | Link |
|---|---|
| JP (1) | JPH11128344A (en) |
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