JPH0334724B2 - - Google Patents
Info
- Publication number
- JPH0334724B2 JPH0334724B2 JP62048565A JP4856587A JPH0334724B2 JP H0334724 B2 JPH0334724 B2 JP H0334724B2 JP 62048565 A JP62048565 A JP 62048565A JP 4856587 A JP4856587 A JP 4856587A JP H0334724 B2 JPH0334724 B2 JP H0334724B2
- Authority
- JP
- Japan
- Prior art keywords
- heating element
- injection needle
- blood
- sensor function
- core material
- 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
- 238000010438 heat treatment Methods 0.000 claims description 59
- 239000007924 injection Substances 0.000 claims description 29
- 238000002347 injection Methods 0.000 claims description 29
- 239000011162 core material Substances 0.000 claims description 17
- 238000005259 measurement Methods 0.000 claims description 15
- 229910052751 metal Inorganic materials 0.000 claims description 15
- 239000002184 metal Substances 0.000 claims description 15
- WABPQHHGFIMREM-UHFFFAOYSA-N lead(0) Chemical compound [Pb] WABPQHHGFIMREM-UHFFFAOYSA-N 0.000 claims description 12
- 239000011248 coating agent Substances 0.000 claims description 9
- 238000000576 coating method Methods 0.000 claims description 9
- 239000000919 ceramic Substances 0.000 claims description 6
- 238000007740 vapor deposition Methods 0.000 claims description 5
- 229920003002 synthetic resin Polymers 0.000 claims description 3
- 239000000057 synthetic resin Substances 0.000 claims description 3
- 239000010409 thin film Substances 0.000 claims 1
- 239000008280 blood Substances 0.000 description 27
- 210000004369 blood Anatomy 0.000 description 27
- 239000012530 fluid Substances 0.000 description 6
- 238000010586 diagram Methods 0.000 description 5
- 230000002093 peripheral effect Effects 0.000 description 5
- 229910001220 stainless steel Inorganic materials 0.000 description 5
- 239000010935 stainless steel Substances 0.000 description 5
- HTTJABKRGRZYRN-UHFFFAOYSA-N Heparin Chemical compound OC1C(NC(=O)C)C(O)OC(COS(O)(=O)=O)C1OC1C(OS(O)(=O)=O)C(O)C(OC2C(C(OS(O)(=O)=O)C(OC3C(C(O)C(O)C(O3)C(O)=O)OS(O)(=O)=O)C(CO)O2)NS(O)(=O)=O)C(C(O)=O)O1 HTTJABKRGRZYRN-UHFFFAOYSA-N 0.000 description 3
- 210000004204 blood vessel Anatomy 0.000 description 3
- 230000007423 decrease Effects 0.000 description 3
- 229960002897 heparin Drugs 0.000 description 3
- 229920000669 heparin Polymers 0.000 description 3
- BASFCYQUMIYNBI-UHFFFAOYSA-N platinum Chemical compound [Pt] BASFCYQUMIYNBI-UHFFFAOYSA-N 0.000 description 3
- 238000004804 winding Methods 0.000 description 3
- 239000002473 artificial blood Substances 0.000 description 2
- 238000010241 blood sampling Methods 0.000 description 2
- 238000000502 dialysis Methods 0.000 description 2
- 230000000694 effects Effects 0.000 description 2
- 230000020169 heat generation Effects 0.000 description 2
- 238000004519 manufacturing process Methods 0.000 description 2
- 229920005989 resin Polymers 0.000 description 2
- 239000011347 resin Substances 0.000 description 2
- 206010061876 Obstruction Diseases 0.000 description 1
- 239000003146 anticoagulant agent Substances 0.000 description 1
- 229940127219 anticoagulant drug Drugs 0.000 description 1
- 230000017531 blood circulation Effects 0.000 description 1
- 230000023555 blood coagulation Effects 0.000 description 1
- 210000004958 brain cell Anatomy 0.000 description 1
- 238000004364 calculation method Methods 0.000 description 1
- 230000002490 cerebral effect Effects 0.000 description 1
- 239000004020 conductor Substances 0.000 description 1
- 238000007796 conventional method Methods 0.000 description 1
- 239000003814 drug Substances 0.000 description 1
- 239000003822 epoxy resin Substances 0.000 description 1
- 239000011888 foil Substances 0.000 description 1
- 238000005534 hematocrit Methods 0.000 description 1
- 238000000338 in vitro Methods 0.000 description 1
- 238000001727 in vivo Methods 0.000 description 1
- 210000003734 kidney Anatomy 0.000 description 1
- 150000002739 metals Chemical class 0.000 description 1
- 239000000203 mixture Substances 0.000 description 1
- 230000017074 necrotic cell death Effects 0.000 description 1
- 239000002504 physiological saline solution Substances 0.000 description 1
- 229920000647 polyepoxide Polymers 0.000 description 1
- XLYOFNOQVPJJNP-UHFFFAOYSA-N water Substances O XLYOFNOQVPJJNP-UHFFFAOYSA-N 0.000 description 1
Landscapes
- Measurement Of The Respiration, Hearing Ability, Form, And Blood Characteristics Of Living Organisms (AREA)
Description
【発明の詳細な説明】
（産業上の利利用分野）
本発明は、センサー機能が付いた注射針、主と
して血液の粘性を検知することができるセンサー
機能をもつた注射針に関する。DETAILED DESCRIPTION OF THE INVENTION (Field of Industrial Application) The present invention relates to an injection needle with a sensor function, and mainly to an injection needle with a sensor function that can detect the viscosity of blood.
（従来の技術）
医療等の分野において、患者の血液粘度の変化
を知ることは重要である。(Prior Art) In fields such as medicine, it is important to know changes in a patient's blood viscosity.
例えば、脳閉塞患者の血液は、特に患者が高齢
であると、朝と夜とでヘマトクリツトの量が変化
し、これによつて血液の見かけ上の粘度が変化す
る。血液の粘度が上がると、血管中を流れる血液
の流速が落ち、ある粘度を超えると血液の流れが
止まつてしまつて、その先の脳細胞が壊死してし
まう。 For example, in the blood of a cerebral obstruction patient, especially if the patient is elderly, the amount of hematocrit changes between morning and night, and this changes the apparent viscosity of the blood. When the viscosity of blood increases, the speed of blood flowing through the blood vessels decreases, and when the viscosity exceeds a certain level, the blood flow stops, leading to necrosis of brain cells beyond that point.
このため、ある粘度を超えた場合には生理食塩
水を注入して粘度を下げなければならない。又、
腎透析の場合にも、血液粘度が上がらないように
ヘパリン（血液凝固防止剤）を血液中に注入しな
ければならない。 Therefore, if the viscosity exceeds a certain level, physiological saline must be injected to lower the viscosity. or,
Even in the case of kidney dialysis, heparin (an anti-coagulant) must be injected into the blood to prevent blood viscosity from increasing.
以上のように、患者の血液粘度の変化を知るこ
とは医療上重要であり、現在は医者が経験的に判
断するが、あるいは多量のサンプルを採血して粘
度計測を行つている。 As described above, it is medically important to know changes in a patient's blood viscosity, and currently doctors make judgments based on experience, or viscosity measurements are performed by drawing a large amount of blood samples.
（発明が解決しようとする問題点）
しかしながら、医者による経験的な判断は、必
ずしも確実であるとは言い難く、また、従来の粘
度計測では多量の採血を要するという問題があ
る。(Problems to be Solved by the Invention) However, empirical judgments made by doctors are not necessarily reliable, and conventional viscosity measurement requires a large amount of blood to be collected.
本発明の目的は、以上のような問題点を解決し
不要な採血をなくすと共に、確実に血液粘度を計
測することができるようにすることにある。 An object of the present invention is to solve the above-mentioned problems, eliminate unnecessary blood sampling, and enable reliable measurement of blood viscosity.
（問題点を解決するための手段）
上記目的を達成するための本発明センサー機能
付き注射針は、少なくとも、細管状の芯材と、こ
の芯材の回りに設けた発熱体と、この発熱体に電
流を導入する電流導入用リード線と、前記発熱体
に印加されている電圧を測定するための電圧測定
用リード線と、前記発熱体の回りに設けた外管と
で構成することにより、前記発熱体に印加されて
いる電圧と電流を測定可能にした。(Means for Solving the Problems) A hypodermic needle with a sensor function of the present invention for achieving the above object includes at least a thin tube-shaped core material, a heating element provided around the core material, and a heating element provided around the core material. By comprising a current introduction lead wire for introducing current into the heating element, a voltage measurement lead wire for measuring the voltage applied to the heating element, and an outer tube provided around the heating element, The voltage and current applied to the heating element can be measured.
（作用効果）
一般に流体の粘度は熱伝達率の関数として与え
られ、熱伝達率は発熱体から流体へ熱量及び熱が
移動するときの発熱体表面における温度差の関数
として次の次式で与えられる。(Effect) Generally, the viscosity of a fluid is given as a function of the heat transfer coefficient, and the heat transfer coefficient is given by the following equation as a function of the amount of heat and the temperature difference on the surface of the heating element when heat is transferred from the heating element to the fluid. It will be done.
α＝Ｑ／Ｆ・Δθ ここでα：熱伝達率 Ｑ：発熱量 Ｆ：発熱体表面積、 Δθ：温度差（θs−θ∞） θs：発熱体表面温度 θ∞：流体の温度 また発熱量Ｑは Ｑ＝Rw・iw2 ここで、Rw：発熱体電気抵抗、 iw：発熱体加熱電流 であらわされ、上式は以下のごとくなる。 α=Q/F・Δθ Where α: Heat transfer coefficient Q: Calorific value F: Heating element surface area, Δθ: Temperature difference (θs−θ∞) θs: Heating element surface temperature θ∞: Fluid temperature Also, calorific value Q is Q=Rw・iw 2where , Rw: heating element electrical resistance, iw: heating element heating current, and the above equation becomes as follows.
α＝Rw・iw2／Ｆ・（θs−θ∞）
従つてこの式より、流体中に配置される発熱体
の温度を測定し、その温度の変化を測定すること
によつて熱伝達率の変化が計測可能となる。 α=Rw・iw 2 /F・(θs−θ∞) Therefore, from this equation, we can calculate the heat transfer coefficient by measuring the temperature of the heating element placed in the fluid and measuring the change in temperature. Changes can be measured.
一般の流体においては、動粘性率ν、熱伝導率
λ、温度伝導率ａ、体積膨張率β及び流速ｕ、熱
伝達率ａが変化するが、血液の場合ははその成分
組成の大部分が水であるため、λ、ａ、βは実質
的に一定とみなせる。またin vitro系ではｕ＝
０、またはin vivo系では時間平均をとることに
よつてｕ＝一定と、それぞれみなせるため、αの
変化はνの変化と１対１の対応関係にあるといえ
る。 In general fluids, the kinematic viscosity ν, thermal conductivity λ, temperature conductivity a, volumetric expansion coefficient β, flow velocity u, and heat transfer coefficient a change, but in the case of blood, most of its component composition changes. Since it is water, λ, a, and β can be considered to be substantially constant. In addition, in the in vitro system, u=
0, or in an in vivo system, it can be assumed that u=constant by taking the time average, so it can be said that the change in α has a one-to-one correspondence with the change in ν.
本発明は微小血液循環系の影響する血液粘度も
しくは血液凝固を熱伝達率の変化を測定できる機
能を備えた注射針を提供するものである。 The present invention provides an injection needle having the function of measuring blood viscosity or blood coagulation, which is influenced by the microcirculatory system, and changes in heat transfer coefficient.
本発明のセンサー素子機能付き注射針は前記構
成によるとおり、注射針の回りに発熱体を配置し
たので、その電流と電圧から、発熱体の温度変化
を知ることができ、注射針内表面もしくは外表面
における熱伝達率の変化を知り、注射針の内部に
取り込まれた、もしくは内部を流動する、もしく
は注射針の外表面近傍の静止もしくは流動する血
液の粘度変化の事実を検知する。熱伝達率、すわ
ち、発熱体の温度と粘度の関係は１対１の関係に
ある。すなわち、粘度が高いと熱伝達率が相対的
に減少し、発熱体自体の温度が減少するため、熱
伝達率と逆数関係にある上記温度差θs−θ∞か
ら、粘度変化（θs−θ∞と比例関係にある）が検
出できる。 As described above, the injection needle with sensor element function of the present invention has a heating element arranged around the injection needle, so it is possible to know the temperature change of the heating element from the current and voltage. It detects changes in the viscosity of blood drawn into or flowing inside the injection needle, or of stationary or flowing blood near the outer surface of the injection needle, by knowing the change in heat transfer coefficient at the surface. The heat transfer coefficient, that is, the relationship between the temperature and viscosity of the heating element is a one-to-one relationship. In other words, when the viscosity is high, the heat transfer coefficient decreases relatively, and the temperature of the heating element itself decreases. Therefore, from the above temperature difference θs - θ∞, which has a reciprocal relationship with the heat transfer coefficient, the viscosity change (θs - θ∞ ) can be detected.
本発明センサー機能付き注射針は上記の構成と
したので、次のような作用効果を奏する。 Since the injection needle with sensor function of the present invention has the above-described configuration, it has the following effects.
すなわち、細管状の芯材の回りに設けた発熱体
に電流導入用リード線によつて通電してこれを発
熱させ、この発熱体に印加されている電圧を電圧
測定用リード線を通じて測定し、その電圧値と前
記電流値とから発熱体の発熱量を計測することが
できる。 That is, a heating element provided around a tubular core material is energized through a current introduction lead wire to generate heat, and the voltage applied to this heating element is measured through a voltage measurement lead wire. The amount of heat generated by the heating element can be measured from the voltage value and the current value.
そこで、注射針の芯材を構成している細管内周
面及び、又は外管の外周面を血液と熱的に接触さ
せて、この熱的接触面の温度差及び前記発熱量の
変化を計測すれば熱伝達率の変化を計測でき、結
果として血液の粘度の変化を計測することができ
る。 Therefore, the inner peripheral surface of the thin tube and/or the outer peripheral surface of the outer tube, which constitute the core material of the injection needle, are brought into thermal contact with the blood, and the temperature difference at this thermal contact surface and the change in the calorific value are measured. By doing so, changes in heat transfer coefficient can be measured, and as a result, changes in blood viscosity can be measured.
（実施例）
以下、図示の実施例について説明する。第１図
は本発明にかかるセンサー機能付き注射針の一実
施例を示す一部省略拡大断面図、第２図は同上使
用状態の一例を示すブロツク図である。(Example) The illustrated example will be described below. FIG. 1 is a partially omitted enlarged sectional view showing an embodiment of the sensor-equipped injection needle according to the present invention, and FIG. 2 is a block diagram showing an example of the same in use.
本注射針１は第１図に示すように、細管状の芯
材２と、この芯材２の回りに設けた導電体よりな
る発熱体３と、この発熱体３に電流を導入する電
流導入用リード線４及び前記発熱体に印加されて
いる電圧を測定するための電圧測定用リード線５
と、前記発熱体の回りに設けた外管６とを備えて
いる。 As shown in FIG. 1, the present injection needle 1 includes a thin tube-shaped core material 2, a heating element 3 made of a conductor provided around the core material 2, and a current introduction for introducing current into the heating element 3. and a voltage measurement lead wire 5 for measuring the voltage applied to the heating element.
and an outer tube 6 provided around the heating element.
芯材２は金属製細管、例えばステンレス製細管
で構成してあり、上部には注射器先端７との嵌合
部分２ａが形成されている。 The core material 2 is constituted by a metal thin tube, for example, a stainless steel thin tube, and has a fitting portion 2a with a syringe tip 7 formed at its upper portion.
８は芯材２の外周面に形成した絶縁被膜であつ
て、例えばセラミツク蒸着、合成樹脂膜等で形成
してあり、この絶縁被膜８を介して前記発熱体３
が設けてある。 Reference numeral 8 denotes an insulating coating formed on the outer circumferential surface of the core material 2, and is made of, for example, ceramic vapor deposition or a synthetic resin film.
is provided.
前記外管６は金属製細管、例えばステンレス製
細管で構成してあり、前記発熱体３の回りに絶縁
被膜９（セラミツク、合成樹脂等）を介して設け
てある。絶縁被膜９として間隙に樹脂を充填する
と、空気に比べて熱伝導率が大きくなつて内外面
の温度が小なくなるという利点がある。 The outer tube 6 is made of a metal thin tube, for example, a stainless steel thin tube, and is provided around the heating element 3 with an insulating coating 9 (ceramic, synthetic resin, etc.) interposed therebetween. Filling the gap with resin as the insulating coating 9 has the advantage that the thermal conductivity is higher than that of air and the temperature of the inner and outer surfaces is lower.
前記発熱体３の形成方法は、適宜の手段を採用
し得、例えば金属細線を芯材２に巻き付けること
によつて形成することができる。 The heating element 3 can be formed by any suitable means, for example, by winding a thin metal wire around the core material 2.
この場合、リード線の引き出しを容易にするた
め、第３図に示すように予め２つ折りした細線１
０を第４図に示すように芯材２の回りに巻き付け
るとよい。これらの図において、４ａ，４ｂが電
流導入用リード線、５ａ，５ｂが電圧測定用リー
ド線である。電流導入用リード線４ａ，４ｂは第
２図に示す電流源４０に接続されており、電圧測
定用リード線５ａ，５ｂは、電圧測定装置５０に
接続されている。 In this case, in order to make it easier to draw out the lead wire, as shown in Figure 3, the thin wire 1 is folded in half in advance.
0 is preferably wrapped around the core material 2 as shown in FIG. In these figures, 4a and 4b are lead wires for introducing current, and 5a and 5b are lead wires for voltage measurement. The current introduction lead wires 4a, 4b are connected to a current source 40 shown in FIG. 2, and the voltage measurement lead wires 5a, 5b are connected to a voltage measuring device 50.
第２図において、６０は前記電流源４０及び電
圧測定装置５０の制御を司る制御装置であり、こ
れら電流源４０、電圧測定装置５０、制御装置６
０はそれぞれGP−IB（ゼネラル・パーパス・イ
ンターフエイス・バス）制御系で接続されてい
る。 In FIG. 2, 60 is a control device that controls the current source 40 and voltage measuring device 50, and these current source 40, voltage measuring device 50, and control device 6
0 are connected to each other by a GP-IB (General Purpose Interface Bus) control system.
以上のような注射針の製法の一例について第５
図を参照して説明すると、先ずステレス製の極細
管２の外周面にセラミツク層８を蒸着する。 Regarding an example of the manufacturing method of the above-mentioned injection needle, Section 5
To explain with reference to the drawings, first, a ceramic layer 8 is vapor-deposited on the outer peripheral surface of an ultra-thin tube 2 made of stainless steel.
次いで、このセラミツク層８の外周面に発熱体
として直径0.1mm程度の白金線１０を巻き付けた
ものをステンレス製の外管６中に挿入する（第５
図はこの状態を示している）。 Next, a platinum wire 10 with a diameter of about 0.1 mm is wound around the outer peripheral surface of the ceramic layer 8 as a heating element and inserted into the stainless steel outer tube 6 (fifth
The figure shows this situation).
そして前記セラミツク層８と外管６との間に形
成されたパイプ状空隙１２の一端を図示しない真
空ポンプに連結して吸引１１し、他端からエポキ
シ系樹脂９を供給して前記パイプ状空隙１２に該
樹脂を充填し、白金線１０を固定すると同時に白
金線１０と外管６とを電気的に絶縁する。その
後、Ｃ−Ｃ線で切断し、２本の注射針を同時に作
成する。 Then, one end of the pipe-shaped gap 12 formed between the ceramic layer 8 and the outer tube 6 is connected to a vacuum pump (not shown) to perform suction 11, and epoxy resin 9 is supplied from the other end to form the pipe-shaped gap. 12 is filled with the resin to fix the platinum wire 10 and at the same time electrically insulate the platinum wire 10 and the outer tube 6. Then, cut along the C-C line to create two injection needles at the same time.
＜使用例 １＞
さて、以上のような注射針１は、例えば第２図
に示すように注射器７に取り付け、血液との熱的
接触状態が得られるようにする。そして、例えば
この注射器で採血する際に、あるいは予め前記電
流導入用リード線４を通じて発熱体３に電流を供
給して発熱体３を発熱させ、前記電圧測定用リー
ド線５を介して電圧測定装置５０で発熱体３に印
加されている電圧を測定する。<Usage Example 1> Now, the injection needle 1 as described above is attached to a syringe 7, for example, as shown in FIG. 2, so as to be in thermal contact with blood. For example, when drawing blood with this syringe, or by supplying current to the heating element 3 through the current introduction lead wire 4 in advance to cause the heating element 3 to generate heat, the voltage measurement device is connected to the voltage measurement device through the voltage measurement lead wire 5. At 50, the voltage applied to the heating element 3 is measured.
その測定結果に基づいて、制御装置６０がその
時の発熱体３に供給されている電流値との関係で
発熱体３の発熱量Ｗを算出し、更に、この発熱量
Ｗ及び前記熱的境界面における温度差に基づいて
発熱体３と血液との間における熱伝達率を算出
し、この熱伝達率に基づいて粘度を算出する。 Based on the measurement results, the control device 60 calculates the heat generation amount W of the heating element 3 in relation to the current value being supplied to the heating element 3 at that time, and further calculates the heat generation amount W and the thermal boundary surface. The heat transfer coefficient between the heating element 3 and the blood is calculated based on the temperature difference in the blood, and the viscosity is calculated based on this heat transfer coefficient.
従つての場合には、採血と同時に血液粘度も計
測することができる。しかも、本注射針によれ
ば、従来と異なり、現に人体を流れている血液の
粘度を測定することができる。 In this case, blood viscosity can also be measured at the same time as blood sampling. Moreover, according to the present injection needle, unlike conventional methods, it is possible to measure the viscosity of blood actually flowing through the human body.
なお、前記熱伝達率を算出する式を掲げれば次
のとおりである。すなわち、第７図に示すような
発熱体３′、非発熱体７０，７１からなる３層構
造の円柱座標系を考ええると、熱伝達率αは
α＝Wd2／4Δθs｛１−〔d1／d2〕2｝
Ｗ：円管状発熱体３′の発熱量（実測可能）
d1：発熱体３′の内径（既知）
d2：発熱体３′の外径（既知）
Δθs：流体との接触面７２における温度差であ
つて、
Δθs＝θs−θ∞
θ∞：流体温度（実測可能）
θs：非発熱体７１の表面温度であつて、
θs＝θwWd2／8λ3（d3−d2）｛１−〔d1／d2〕2｝
d3：非発熱体７１の外径（既知）
λ3：非発熱体７１の熱伝導率（既知）
θs：発熱体の平均温度（実測可能）
として算出できる。 The formula for calculating the heat transfer coefficient is as follows. That is, if we consider a cylindrical coordinate system with a three-layer structure consisting of a heating element 3' and non-heating elements 70 and 71 as shown in FIG. 7, the heat transfer coefficient α is α=Wd 2 /4Δθs {1−[d 1 / d 2 ] 2 } W: Calorific value of the circular tubular heating element 3' (can be measured) d 1 : Inner diameter of the heating element 3' (known) d 2 : Outer diameter of the heating element 3' (known) Δθs: Fluid The difference in temperature at the contact surface 72 with -d 2 ) {1-[d 1 /d 2 ] 2 } d 3 : Outer diameter of non-heating element 71 (known) λ 3 : Thermal conductivity of non-heating element 71 (known) θs: Average temperature of heating element (Actually measurable) It can be calculated as
＜実施例 ２＞
第６図に示すように、本注射針１を腎透析等に
おいて血液のパイパスとして用いる人工血管２０
に取り付け、前述したようにして血液粘度を測定
する。更に、この場合には、予め血液粘度の許容
値を設定しておき、該許容値を超えた場合には、
注射器７の図示しない駆動装置を作動させ、自動
的にヘパリンを人工血管２０中に注入するように
する。すなわち、本注射針１は粘度測定センサー
としての役割と、ヘパリン注入手段としての役割
を同時に果たすことができる。<Example 2> As shown in FIG. 6, an artificial blood vessel 20 in which the present injection needle 1 is used as a blood bypass in renal dialysis etc.
and measure blood viscosity as described above. Furthermore, in this case, a permissible value for blood viscosity is set in advance, and if the permissible value is exceeded,
A drive device (not shown) of the syringe 7 is activated to automatically inject heparin into the artificial blood vessel 20. That is, the injection needle 1 can simultaneously serve as a viscosity measurement sensor and a heparin injection means.
以上本発明の実施例について説明したが、本発
明は上記実施例に限るものではなく、適宜変形実
施可能である。例えば、
芯材２はステンレスに限らず、他の金属を採
用し得る。 Although the embodiments of the present invention have been described above, the present invention is not limited to the above embodiments, and can be modified as appropriate. For example, the core material 2 is not limited to stainless steel, and other metals may be used.
発熱体として金属細線を用いた場合におい
て、絶縁被膜８は必ずしも必要ではなく、代わ
りに金属細線に絶縁被膜を形成してもよい。 In the case where a thin metal wire is used as the heating element, the insulating coating 8 is not necessarily required, and an insulating coating may be formed on the thin metal wire instead.
発熱体として金属細線を用いた場合、第３，
４図に示したように二重巻きとする必要はな
く、単一巻きとしてもよい。 When a thin metal wire is used as a heating element, the third
It is not necessary to use double winding as shown in Fig. 4, but single winding may be used.
発熱体は、金属細線に限るものではなく、セ
ンサー層８の外周面に金属箔を巻き付けてもよ
く、金属蒸着によつて形成してもよい。 The heating element is not limited to a thin metal wire, and may be formed by wrapping metal foil around the outer peripheral surface of the sensor layer 8 or by metal vapor deposition.
発熱体を金属蒸着によつて形成する場合に、
第３，４図に示したようなパターンその他任意
のパターンを形成することができる。 When forming a heating element by metal vapor deposition,
Any pattern other than the patterns shown in FIGS. 3 and 4 can be formed.
発熱体は、注射針先端部分にのみ形成しても
よい。 The heating element may be formed only at the tip of the injection needle.
上記〜を適宜組合せることもできる。 The above ~ can also be combined as appropriate.
第１図は本発明にかかるセンサー機能付き注射
針の一実施例を示す一部省略拡大断面図、第２図
は同上使用状態の一例を示すブロツク図、第３図
及び第４図は発熱体の形成例の説明図、第５図は
本注射針の製造例の説明図、第６図は第２図とは
異なる使用例の説明図、第７図は熱伝達率算出法
の参考図である。
１……注射率、２……芯材、３……発熱体、４
……電流導入用リード線、５………電圧測定用リ
ード線、６……外管。
FIG. 1 is a partially omitted enlarged cross-sectional view showing an embodiment of the sensor function-equipped injection needle according to the present invention, FIG. 2 is a block diagram showing an example of the same usage state, and FIGS. 3 and 4 are heating elements. Figure 5 is an explanatory diagram of a manufacturing example of this injection needle, Figure 6 is an explanatory diagram of a usage example different from Figure 2, and Figure 7 is a reference diagram of a heat transfer coefficient calculation method. be. 1... Injection rate, 2... Core material, 3... Heating element, 4
... Lead wire for current introduction, 5 ... Lead wire for voltage measurement, 6 ... Outer tube.
Claims (1)
りに設けた発熱体と、この発熱体に電流を導入す
る電流導入用リード線と、前記発熱体に印加され
ている電圧を測定するための電圧測定用リード線
と、前記発熱体の回りに設けた外管とで構成し、
前記発熱体に印加されている電圧と電流を測定可
能にしたセンサー機能付き注射針。 ２ 前記芯材を金属製細管とし、前記発熱体は絶
縁被膜を介して設けた特許請求の範囲第１項記載
のセンサー機能付き注射針。 ３ 前記外管を金属製細管とし、これを前記発熱
体の回りに絶縁被膜を介して設けた特許請求の範
囲第１項又は第２項記載のセンサー機能付き注射
針。 ４ 前記絶縁被膜は合成樹脂薄膜とした特許請求
の範囲第２項又は第３項の記載のセンサー機能付
き注射針。 ５ 前記絶縁被膜はセラミツク蒸着で形成した特
許請求の範囲第２項又は第３項記載のセンサー機
能付き注射針。 ６ 前記発熱体は、金属細線として芯材に巻き付
けた特許請求の範囲第１項乃至第５項のうちの何
れか一項に記載のセンサー機能付き注射針。 ７ 前記発熱体は、金属蒸着にて形成した特許請
求の範囲第１項乃至第５項のうち何れか一項に記
載のセンサー機能付き注射針。[Scope of Claims] 1. At least a thin tube-shaped core material, a heating element provided around the core material, a current introduction lead wire for introducing current into the heating element, and an electric current applied to the heating element. It is composed of a voltage measurement lead wire for measuring the voltage at the heating element, and an outer tube provided around the heating element,
An injection needle with a sensor function that can measure the voltage and current applied to the heating element. 2. An injection needle with a sensor function according to claim 1, wherein the core material is a metal thin tube, and the heating element is provided with an insulating coating interposed therebetween. 3. The injection needle with a sensor function according to claim 1 or 2, wherein the outer tube is a metal thin tube, and this is provided around the heating element with an insulating coating interposed therebetween. 4. The injection needle with a sensor function according to claim 2 or 3, wherein the insulating coating is a synthetic resin thin film. 5. The injection needle with a sensor function according to claim 2 or 3, wherein the insulating coating is formed by ceramic vapor deposition. 6. The injection needle with a sensor function according to any one of claims 1 to 5, wherein the heating element is a thin metal wire wound around a core material. 7. The injection needle with a sensor function according to any one of claims 1 to 5, wherein the heating element is formed by metal vapor deposition.
Priority Applications (1)
| Application Number | Priority Date | Filing Date | Title |
|---|---|---|---|
| JP62048565A JPS63214240A (en) | 1987-03-03 | 1987-03-03 | Syringe needle having sensor function |
Applications Claiming Priority (1)
| Application Number | Priority Date | Filing Date | Title |
|---|---|---|---|
| JP62048565A JPS63214240A (en) | 1987-03-03 | 1987-03-03 | Syringe needle having sensor function |
Publications (2)
| Publication Number | Publication Date |
|---|---|
| JPS63214240A JPS63214240A (en) | 1988-09-06 |
| JPH0334724B2 true JPH0334724B2 (en) | 1991-05-23 |
Family
ID=12806915
Family Applications (1)
| Application Number | Title | Priority Date | Filing Date |
|---|---|---|---|
| JP62048565A Granted JPS63214240A (en) | 1987-03-03 | 1987-03-03 | Syringe needle having sensor function |
Country Status (1)
| Country | Link |
|---|---|
| JP (1) | JPS63214240A (en) |
Families Citing this family (2)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| JP4576222B2 (en) * | 2004-12-17 | 2010-11-04 | 日機装株式会社 | In vivo characteristic sensor and biological information monitoring system |
| JP4576627B2 (en) * | 2005-07-05 | 2010-11-10 | 独立行政法人産業技術総合研究所 | Puncture device integrated biosensor |
-
1987
- 1987-03-03 JP JP62048565A patent/JPS63214240A/en active Granted
Also Published As
| Publication number | Publication date |
|---|---|
| JPS63214240A (en) | 1988-09-06 |
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