JPH0347855B2 - - Google Patents
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- Publication number
- JPH0347855B2 JPH0347855B2 JP57197514A JP19751482A JPH0347855B2 JP H0347855 B2 JPH0347855 B2 JP H0347855B2 JP 57197514 A JP57197514 A JP 57197514A JP 19751482 A JP19751482 A JP 19751482A JP H0347855 B2 JPH0347855 B2 JP H0347855B2
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- Prior art keywords
- sample gas
- skin
- sampling
- gas sampling
- sample
- 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
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- Other Investigation Or Analysis Of Materials By Electrical Means (AREA)
- Investigating Or Analysing Biological Materials (AREA)
- Sampling And Sample Adjustment (AREA)
- Measurement Of The Respiration, Hearing Ability, Form, And Blood Characteristics Of Living Organisms (AREA)
Description
【発明の詳細な説明】
〔発明の利用分野〕
本発明は大気圧イオン化質量分析計等の試料ガ
ス採取装置の改良に係り、特に、この種装置にお
いて人間の生体皮膚から発生する微量の揮発性有
機物質からなる試料ガスを効率的に採取するのに
好適な試料ガス採取装置に関する。[Detailed Description of the Invention] [Field of Application of the Invention] The present invention relates to the improvement of sample gas sampling devices such as atmospheric pressure ionization mass spectrometers, and in particular, the present invention relates to the improvement of sample gas sampling devices such as atmospheric pressure ionization mass spectrometers. The present invention relates to a sample gas collection device suitable for efficiently collecting sample gas made of organic substances.
人体において血液中に含まれる揮発性物質は種
種の人体の機能との関連をもつており、それらを
計測することは人体機能の解明、さらには病気の
診断において重要である。この揮発性物質を血液
を試料とせず、皮膚を透過することによつて揮発
してくるガスを試料とすることは血液を試料とし
た場合の問題点を解決できるので極めて有効であ
る。すなわち、血液の分析では血液を採取するた
めに検体に負担がかかり、同一検体に対する連続
測定ができないこと、また、血液を採取し、測定
器に導入するまでの間に生体外反応が起こり、生
体内におけると同様の測定ができないことの大き
な二つの問題点がある。皮膚から発生するガスを
試料とするならばこの二つの問題は解決される。
しかしながら、血液中に含まれる代謝による揮発
性有機物は極めて微量であり、これが皮膚を透過
してくるので、更に微量となる。この微量の揮発
性有機物ガスを少しでも多く採取することは測定
上重要である。
Volatile substances contained in blood in the human body are related to various functions of the human body, and measuring them is important in elucidating human body functions and furthermore in diagnosing diseases. It is extremely effective to use a gas that evaporates by permeating the skin as a sample for this volatile substance instead of using blood as a sample because it can solve the problems that arise when blood is used as a sample. In other words, in blood analysis, collecting the blood puts a strain on the specimen, making it impossible to perform continuous measurements on the same specimen.Also, in vitro reactions occur between the time the blood is collected and the time it is introduced into the measuring instrument, leading to There are two major problems in that measurements cannot be made in the same way as in the body. These two problems can be solved if gas generated from the skin is used as a sample.
However, the volatile organic substances contained in the blood due to metabolism are extremely small, and as they permeate through the skin, the amount becomes even smaller. It is important for measurement to collect as much of this trace amount of volatile organic gas as possible.
そのために、従来の皮膚から血液ガスを採取す
る装置はガス採取容器の皮膚に接する面に多数の
穴のあいた金属板をとりつけ、この穴のあいた金
属板にヒータを接しさせて電気的に皮膚を加熱す
るようにしたものである。 To this end, conventional devices for collecting blood gas from the skin include a metal plate with many holes attached to the surface of the gas collection container that contacts the skin, and a heater is placed in contact with the metal plate with holes to electrically collect the skin. It is designed to be heated.
１） P.Rolfe；“Fetal and Neonatal
Physiological Measuremtnts”，Pitman
Medical Limited，London，1980，pp.385〜
449.
２） P.Rolfe；“Non−Invasive Physiolgical
Measurements”，Academic Press，London，
New York，San Francisco，1979，pp.333〜
344.
しかしながら、このような構成ではガス採取容
器の皮膚に接する面積のうちで実際にガスを採取
している有効面積が少なく、単位時間当りのガス
採取量が極めて少ないと言う欠点があつた。この
装置の本来の目的は血液ガスのうちの主成分であ
る酸素、炭酸ガス、麻酔ガス（N2O）を採取す
ることにあり、したがつて、発生ガス量が多いた
め有効面積が少なくとも問題とはならなかつた。
しかし、採取目的物質が生体代謝による揮発性有
機物ガスになると極めて微量となるために、この
ような試料ガスを採取するための有効面積を大き
くすることが重要になる。1) P.Rolfe; “Fetal and Neonatal
Physiological Measuremtnts”，Pitman
Medical Limited, London, 1980, pp.385~
449. 2) P. Rolfe; “Non-Invasive Physiolgical
Measurements”, Academic Press, London,
New York, San Francisco, 1979, pp.333~
344. However, this configuration had the disadvantage that the effective area of the gas sampling container in contact with the skin, where gas was actually collected, was small, and the amount of gas collected per unit time was extremely small. The original purpose of this device is to collect oxygen, carbon dioxide gas, and anesthetic gas (N 2 O), which are the main components of blood gas, so the effective area is at least a problem due to the large amount of gas generated. It didn't happen.
However, when the target substance to be collected becomes volatile organic gas due to biological metabolism, the amount is extremely small, so it is important to increase the effective area for collecting such sample gas.
したがつて、本発明の目的は生体皮膚から発生
する微量の揮発性有機物からなる試料ガスを効率
的に採取できる試料ガス採取装置を提供すること
にある。
SUMMARY OF THE INVENTION Accordingly, an object of the present invention is to provide a sample gas sampling device that can efficiently sample a sample gas consisting of a small amount of volatile organic matter generated from the skin of a living body.
上記目的を達成するために本発明においては、
キヤリアガスを導入するための導入口と、生体皮
膚に密着させてこの生体皮膚から発生する揮発性
有機物からなる試料ガスを採取するための開口
と、採取された試料ガスをキヤリアガスと共に導
出するための導出口とからなる試料ガス採取手段
と、生体皮膚を加熱することによつて揮発性有機
物ガスの発生を促進するための生体皮膚から離間
して設けられた加熱手段とによつて試料ガス採取
装置を構成したことを特徴としている。
In order to achieve the above object, in the present invention,
An inlet for introducing the carrier gas, an opening for bringing the sample gas in close contact with the skin of a living body to collect a sample gas consisting of volatile organic matter generated from the skin, and a guide for leading out the sample gas together with the carrier gas. A sample gas sampling device is constructed by a sample gas sampling means consisting of an outlet and a heating means provided at a distance from the living body's skin to promote generation of volatile organic gas by heating the living body's skin. It is characterized by its composition.
かかる本発明の特徴的な構成によつて、試料ガ
ス採取手段の開口によつて覆われる生体皮膚の全
表面積が試料ガスの採取に対する有効面積とする
ことができるために生体皮膚から発生する微量な
揮発性有機物からなる試料ガスを効率的に採取で
きるようになる。その採取効率は従来装置に比較
して５〜10倍であつた。 With this characteristic configuration of the present invention, the entire surface area of the living body's skin covered by the opening of the sample gas sampling means can be used as an effective area for sampling the sample gas. It becomes possible to efficiently collect sample gas consisting of volatile organic substances. The sampling efficiency was 5 to 10 times higher than that of conventional equipment.
以下、本発明を図を用いて詳細に説明する。 Hereinafter, the present invention will be explained in detail using the drawings.
第１図は本発明による試料ガス採取装置を大気
圧イオン質量分析計と結合した時の基本構成を示
したものである。 FIG. 1 shows the basic configuration of a sample gas sampling device according to the present invention combined with an atmospheric pressure ion mass spectrometer.
同図において、キヤリアガスとしての純窒素は
ボンベ（図示せず）より供給されるが、この窒素
ガスは保護弁１、流量調整ニードルバルブ３、モ
レキユラーシーブトラツプ４、試料ガス採取容器
６を経由して、生体皮膚５より発生した揮発性有
機物からなる試料ガスとともに大気圧イオン化質
量分析計のイオン源９に導入される。このキヤリ
アガスは大気圧イオン化質量分析計の一次イオン
として必要なものである。すなわち、大気圧イオ
ン化質量分析計では１気圧のイオン源９にキヤリ
アガスと微量の試料ガスが導入されるが、この時
まずコロナ放電または放射線による一次イオ化が
起こる。この時生ずる一次イオンの組成は試料ガ
スが微量（ppm〜ppt）のためにほとんどがキヤ
リアガスイオンである。次に二次イオン化として
このキヤリアガスイオンは大気圧イオン化質量分
析計の分析部１０へ導入されるあいだに中性分子
と衝突し、キヤリアガスよりもイオン化ポテンシ
アルの低い物質をイオン化する。１気圧のイオン
源９では平均自由行程が短かく通常イオン源９の
内部で１個のイオン105〜106回の衝突をくり返
す。したがつて微量の試料ガスでもほぼ100％が
この衝突に関与し、イオン化される。通常、キヤ
リアガスとしては窒素、アルゴン、ヘリウム、酸
素、空気が用いられこれらは目的物質である有機
物よりもイオン化がポテンシアルが高いために電
荷交換反応は速やかに進行し、逆反応は起こられ
ない。また、通常は試料ガスに多量の水が含まれ
ている場合が多いが、この時はキヤリアガスイオ
ンから水または水のクラスタイオンが生成され、
これらのイオンがリアクタントイオンとなつてプ
ロトン移動反応を起こし、目的有機物をイオン化
する。生体皮膚５は鐘型をしたガラス製試料ガス
採取容器６と密着され、光の方向及び広がりを制
御するシエード８を備えた赤外線ランプ７で42〜
43℃に加熱される。試料ガス採取容器６は内径が
約30mm、内容積が約25mlであり、赤外線ランプ８
としては200〜300Wのものが用いられ、生体皮膚
５から20〜40cmの距離に設置されている。大気圧
イオン化質量分析計のイオン源９はロータリポン
プ１２とイオン源９に隣接して設けられた分析部
１０（10paおよび10-3paの真空室部よりなる）
とへのガス流入により、１気圧よりわずかに圧力
が低く維持されており、試料ガス採取容器６の内
部もイオン源９の圧力とほぼ同じため、生体皮膚
５は破線で示されるようにわずかに内方へ吸引さ
れて、揮発性有機物ガスをより発生しやすいよう
になつている。試料ガス採取容器６の内部圧力は
ニードルバルブ３，１１、流量計２、および保護
弁１で制御される。ニードルバルブ３，１１をと
もに閉じた状態で流量計２が示す値V1とニード
ルバルブ３，１１ともに開けた時に流量計２が示
す値V2との差（V1−V2）が試料ガス採取容器６
に送られるキヤリアガスの流量である。生体皮膚
５が適度に吸引されるようにニードルバルブ３，，
１１で試料ガス採取容器６内の圧力を調整する。
試料ガス採取容器６内の圧力は0.8気圧以上、キ
ヤリアガスの流量は100ml／分〜１／分が良い。
保護弁１は保護弁１の前後の圧力差が大きくなつ
た時にその弁が開き、キヤリアガスが流れる。通
常の試料ガスの採取時は数回／秒の開閉を行なつ
ているが、イオン源９側の吸引の操作ミスなどで
試料ガス採取容器６内の圧力が下がりすぎた場合
には保護弁１は開いたままの状態となる。これに
より、生体皮膚５が吸引されすぎるのを保護す
る。なお、窒素ガスからなるキヤリアガス中に含
まれる微量の不純物はモレキユラーシーブトラツ
プ４で除去される。 In the figure, pure nitrogen as a carrier gas is supplied from a cylinder (not shown). The gas is then introduced into the ion source 9 of the atmospheric pressure ionization mass spectrometer along with a sample gas consisting of volatile organic substances generated from the biological skin 5 . This carrier gas is necessary as primary ions in the atmospheric pressure ionization mass spectrometer. That is, in an atmospheric pressure ionization mass spectrometer, a carrier gas and a small amount of sample gas are introduced into the ion source 9 at 1 atmosphere, and at this time, primary ionization occurs due to corona discharge or radiation. The composition of the primary ions generated at this time is mostly carrier gas ions because the sample gas is in a trace amount (ppm to ppt). Next, as secondary ionization, the carrier gas ions collide with neutral molecules while being introduced into the analysis section 10 of the atmospheric pressure ionization mass spectrometer, ionizing substances with a lower ionization potential than the carrier gas. In the ion source 9 at 1 atmosphere, the mean free path is short, and normally one ion collides 10 5 to 10 6 times inside the ion source 9 . Therefore, even if there is only a small amount of sample gas, almost 100% of it will be involved in this collision and will be ionized. Generally, nitrogen, argon, helium, oxygen, and air are used as the carrier gas, and since these have a higher ionization potential than the target organic substance, the charge exchange reaction proceeds quickly and no reverse reaction occurs. In addition, the sample gas usually contains a large amount of water, but in this case water or water cluster ions are generated from the carrier gas ions.
These ions become reactant ions, cause a proton transfer reaction, and ionize the target organic substance. The biological skin 5 is brought into close contact with a bell-shaped glass sample gas sampling container 6, and an infrared lamp 7 equipped with a shade 8 that controls the direction and spread of light is used to heat the sample gas from 42 to 42.
Heated to 43℃. The sample gas sampling container 6 has an inner diameter of approximately 30 mm and an internal volume of approximately 25 ml, and is equipped with an infrared lamp 8.
A power source of 200 to 300 W is used, and is installed at a distance of 20 to 40 cm from the living body's skin 5. The ion source 9 of the atmospheric pressure ionization mass spectrometer has a rotary pump 12 and an analysis section 10 (consisting of 10 pa and 10 -3 pa vacuum chambers) provided adjacent to the ion source 9.
The pressure inside the sample gas collection container 6 is almost the same as that of the ion source 9, so the pressure on the living body's skin 5 is slightly lower than 1 atm, as shown by the broken line. They are drawn inward and are more likely to generate volatile organic gases. The internal pressure of the sample gas sampling container 6 is controlled by needle valves 3 and 11, a flow meter 2, and a protection valve 1. The difference (V 1 - V 2 ) between the value V 1 indicated by the flow meter 2 when both the needle valves 3 and 11 are closed and the value V 2 indicated by the flow meter 2 when both the needle valves 3 and 11 are opened is the sample gas. Collection container 6
is the flow rate of carrier gas sent to Needle valves 3, so that the biological skin 5 is appropriately suctioned.
At step 11, the pressure inside the sample gas sampling container 6 is adjusted.
The pressure inside the sample gas sampling container 6 is preferably 0.8 atmospheres or more, and the flow rate of the carrier gas is preferably 100 ml/min to 1/min.
The protection valve 1 opens when the pressure difference before and after the protection valve 1 becomes large, and the carrier gas flows. During normal sample gas collection, the valve is opened and closed several times per second, but if the pressure inside the sample gas collection container 6 drops too much due to an error in suction operation on the ion source 9 side, the protective valve 1 remains open. This protects the biological skin 5 from being sucked too much. Note that trace impurities contained in the carrier gas consisting of nitrogen gas are removed by the molecular sieve trap 4.
本実施例では次の効果が得られる。従来装置で
は採取容器の生体皮膚との接触部に皮膚加熱用の
多数の穴のあいた金属板が設置されているため揮
発性有機物ガスの発生のための有効面積が少な
く、生体皮膚との全接触面積に対し、穴面積は10
〜20％程度であつた。これに対して、本実施例で
は試料ガス採取容器６で覆われる生体皮膚５の全
表面が有効面積であるので従来装置の数倍以上の
効率で試料ガスが採取できる。また、従来装置で
有効面積を大きくするために穴面積を大きくする
と加熱による生体皮膚の表面温度が均一でなくな
り、穴の中央部付近は温度が低くなつて結果的に
有効面積が小さくなる。そこで、穴の中央部の温
度を上げるために金属板の温度を上げると生体皮
膚を火傷させる。これに対して、本実施例では試
料ガス採取容器６で覆われている生体皮膚５は離
間して設けられた赤外線ランプ７によつて容器６
を通して赤外線が均一に照射されているため生体
皮膚５の全表面が均一に加熱される。そのため、
生体皮膚５に火傷させることは生じない。 This embodiment provides the following effects. In conventional devices, a metal plate with many holes for skin heating is installed at the part of the collection container that comes into contact with the living body's skin, so the effective area for generating volatile organic gases is small, and the entire contact area with the living body's skin is reduced. Compared to the area, the hole area is 10
It was about ~20%. In contrast, in this embodiment, the entire surface of the biological skin 5 covered by the sample gas collection container 6 is the effective area, so the sample gas can be collected with an efficiency several times higher than that of the conventional device. Furthermore, if the hole area is increased in order to increase the effective area in the conventional device, the surface temperature of the biological skin due to heating becomes uneven, and the temperature near the center of the hole becomes lower, resulting in a smaller effective area. Therefore, if the temperature of the metal plate is increased to raise the temperature in the center of the hole, the skin of the living body will be burned. On the other hand, in this embodiment, the living body skin 5 covered with the sample gas sampling container 6 is exposed to the container 6 by an infrared lamp 7 provided at a distance.
Since the infrared rays are uniformly irradiated through the body, the entire surface of the living body's skin 5 is heated uniformly. Therefore,
The living body's skin 5 will not be burned.
さらに本実施例では試料ガス採取装置が大気圧
イオン化質量分析計と直接に結合されているため
に、オンライン測定が可能であり、検体の大量処
理および連続測定が可能である。 Furthermore, in this embodiment, since the sample gas sampling device is directly coupled to the atmospheric pressure ionization mass spectrometer, on-line measurement is possible, and mass processing and continuous measurement of specimens is possible.
第２図は本発明による試料ガス採取装置を試料
ガス採取ボンベと結合した時の基本構成を示した
ものである。第１図の実施例と異なるところは試
料ガス採取装置が直接、大気圧イオン化質量分析
計に結合されずに、試料ガス採取ボンベ１５を介
在させて、オフライン的に大気圧イオン化質量分
析計に結合されることである。この試料ガス採取
ボンベ１５は内容積が２〜３のガラス製のもの
でニードルバルブ１４，１６が具備されている。
試料ガス採取ボンベ１５はあらかじめ1pa以下の
圧力に減圧されており、結合器１３で鐘型試料ガ
ス採取容器６と結合される。生体皮膚５からの試
料ガスの採取操作は第１図の実施例と同様であ
り、第２図のニードルバルブ１４が第１図のニー
ドルバルブ１１に相当している。試料ガス採取ボ
ンベ１５へのキヤリアガスと生体皮膚５からの試
料ガスとの採取完了時点は流量計２で検出する。
すなわち、あらかじめキヤリアガスを流し、ニー
ドルバルブ３を閉じた状態で流量計２が示す値f1
にニードルバルブ３，１４を開けて試料ガスの採
取を行なつている時の流量計２が示す値f2が一致
した時が試料ガスの採取完了時点である。試料ガ
スの採取時のキヤリアガスの流量は一定（200〜
500ml／分）となるようにニードルバルブ１４で
調整する。試料ガスの採取完了時点に近づくと２
〜３秒で値f2は値f1に復帰するので試料ガスの採
取時のキヤリアガスの流量はほとんど一定とみな
せる。試料ガスの採取完了した試料ガス採取ボン
ベ１５は第１図で示した大気圧イオン化質量分析
計のイオン源９に結合されるがニードルバルブ１
６側がイオン源９に、そしてニードルバルブ１４
側が高純度窒素ガスボンベに結合され、バルブ１
４，１６が開けられて窒素ガスを200ml／分程度
流すことにより試料ガス採取ボンベ１５の中の試
料ガスをイオン源９に送出する。 FIG. 2 shows the basic configuration of the sample gas sampling device according to the present invention when combined with a sample gas sampling cylinder. The difference from the embodiment shown in FIG. 1 is that the sample gas sampling device is not directly coupled to the atmospheric pressure ionization mass spectrometer, but is coupled offline to the atmospheric pressure ionization mass spectrometer via a sample gas sampling cylinder 15. It is to be done. This sample gas sampling cylinder 15 is made of glass and has an internal volume of 2 to 3, and is equipped with needle valves 14 and 16.
The sample gas sampling cylinder 15 has been previously evacuated to a pressure of 1 Pa or less, and is connected to the bell-shaped sample gas sampling container 6 by a coupler 13 . The operation for collecting sample gas from the biological skin 5 is similar to that in the embodiment shown in FIG. 1, and the needle valve 14 in FIG. 2 corresponds to the needle valve 11 in FIG. The flow meter 2 detects the time when the carrier gas and the sample gas from the living body skin 5 are completely collected into the sample gas collection cylinder 15.
That is, the value f 1 indicated by the flow meter 2 with the carrier gas flowing in advance and the needle valve 3 closed.
The time when the value f 2 indicated by the flowmeter 2 when sampling the sample gas by opening the needle valves 3 and 14 coincides with each other is the point in time when the sampling of the sample gas is completed. The flow rate of the carrier gas when sampling the sample gas is constant (200~
500ml/min) using the needle valve 14. 2 when approaching the completion of sampling the sample gas.
Since the value f 2 returns to the value f 1 in ~3 seconds, the flow rate of the carrier gas at the time of sampling the sample gas can be considered to be almost constant. The sample gas sampling cylinder 15 from which sample gas has been sampled is connected to the ion source 9 of the atmospheric pressure ionization mass spectrometer shown in FIG.
6 side to the ion source 9 and the needle valve 14
side is connected to a high purity nitrogen gas cylinder, valve 1
4 and 16 are opened and nitrogen gas flows at a rate of about 200 ml/min, thereby sending the sample gas in the sample gas sampling cylinder 15 to the ion source 9.
本実施例における効果は試料ガスの採取効率に
関しては第１図の実施例と同じであるが、オフラ
イン的な試料採取方法であるので、さらに次の効
果が得られる。検体が大気圧イオン化質量分析計
が設置されている場所に来ることができない時、
すなわち、各地の病院、診療所で試料ガスの採取
を行なう場合は試料ガス採取装置のみを試料ガス
の採取場所に設置することで試料ガスの採取が行
なえる。したがつて、本実施例によれば大型の大
気圧イオン化質量分析計を試料ガスの採取場所に
設置しなくても試料ガスを採取できるので病人等
を遠隔地から移動させる必要が全くない。 The effects of this embodiment are the same as those of the embodiment shown in FIG. 1 in terms of sampling efficiency of sample gas, but since it is an off-line sampling method, the following effects can be obtained. When the specimen cannot come to the location where the atmospheric pressure ionization mass spectrometer is installed,
That is, when sample gas is to be sampled at hospitals and clinics in various locations, the sample gas can be sampled by installing only the sample gas sampling device at the sample gas sampling location. Therefore, according to this embodiment, the sample gas can be collected without installing a large atmospheric pressure ionization mass spectrometer at the sample gas collection location, so there is no need to move the sick person from a remote location.
第３図は本発明による試料ガス採取装置によつ
て人間の腕から採取された微量の揮発性有機物か
らなる試料ガスの測定結果を示したものである。
同図から明らかなように、質量数が18（アンモニ
ア），45（アセトアルデヒド），47（エタノール），
59（アセトン）の揮発性有機物が観測されている。
これらの揮発性有機物は生体代謝物として種々の
病気と因果関係があり、その測定は重要である。
なお、質量数が19，37，55，73の物質は水のクラ
スタイオンH3O+，H+（H2O）2，H+（H2O）3，H+
（H2O）4である。このように本実施例によれば生
体学上重要な生体代謝による微量の揮発性有機物
ガスを非観血的に検出できる効果が得られる。 FIG. 3 shows the measurement results of a sample gas consisting of a trace amount of volatile organic matter collected from a human arm by the sample gas sampling device according to the present invention.
As is clear from the figure, the mass numbers are 18 (ammonia), 45 (acetaldehyde), 47 (ethanol),
Volatile organic matter of 59 (acetone) has been observed.
These volatile organic substances are causally related to various diseases as biological metabolites, and their measurement is important.
In addition, substances with mass numbers of 19, 37, 55, and 73 are water cluster ions H 3 O + , H + (H 2 O) 2 , H + (H 2 O) 3 , H +
(H 2 O) 4 . As described above, according to this embodiment, it is possible to non-invasively detect trace amounts of volatile organic gases caused by biologically important biological metabolism.
以上述べたように本発明によれば、試料ガス採
取容器で覆われる生体皮膚の全表面積が試料ガス
の採取に対する有効な表面積とすることができる
ので、生体学上重要な生体代謝による微量の揮発
性有機物ガスを有効に採取できる効果が得られ
る。従来装置では血液中の主揮発性成分である
CO2，N2，O2を採取するためのものであるため、
試料ガスの採取のための有効面積は少なくても問
題とはならなかつた。しかし、生体皮膚から発生
する代謝による揮発性有機物ガスは極めてその量
が少なく、少しでも効率的に採取することは重要
な課題である。本発明では従来装置に比較して５
〜10倍の試料ガスの採取効率を有している。
As described above, according to the present invention, the entire surface area of the living body's skin covered by the sample gas collection container can be used as an effective surface area for sample gas collection, so that trace amounts of volatilization due to biologically important biological metabolism can be reduced. The effect of effectively collecting organic gases can be obtained. In conventional devices, it is the main volatile component in blood.
Because it is for collecting CO 2 , N 2 , and O 2 ,
Although the effective area for sample gas sampling was small, it did not pose a problem. However, the amount of volatile organic gases generated from living body skin due to metabolism is extremely small, and it is an important issue to collect them as efficiently as possible. In the present invention, compared to the conventional device, the
It has ~10 times the sampling efficiency of sample gas.
第１図は本発明による試料ガス採取装置を大気
圧イオン化質量分析計に結合した時の基本構成
図、第２図は本発明による試料ガス採取装置を試
料ガス採取ボンベに結合した時の基本構成図、第
３図は本発明による試料ガス採取装置を用いて採
取した試料ガスを大気圧イオン化質量分析計によ
つて測定したマススペクトル図である。
１……保護弁、２……流量計、３，１１，１
４，１６……ニードルバルブ、４……モレキユラ
ーシーブトラツプ、５……生体皮膚、６……試料
ガス採取容器、７……赤外線ランプ、８……赤外
線の方向、広がりを制御するシエード、９……大
気圧イオン化質量分析計のイオン源、１０……大
気圧イオン化質量分析計の分析部、１２……ロー
タリポンプ、１３……結合器、１５……試料ボン
ベ採取ボンベ。
Fig. 1 is a basic configuration diagram when a sample gas sampling device according to the present invention is coupled to an atmospheric pressure ionization mass spectrometer, and Fig. 2 is a basic configuration diagram when a sample gas sampling device according to the present invention is coupled to a sample gas sampling cylinder. 3 are mass spectrograms obtained by measuring a sample gas sampled using the sample gas sampling device according to the present invention using an atmospheric pressure ionization mass spectrometer. 1...Protection valve, 2...Flowmeter, 3, 11, 1
4, 16... Needle valve, 4... Molecular sieve trap, 5... Biological skin, 6... Sample gas collection container, 7... Infrared lamp, 8... Shade that controls the direction and spread of infrared rays. , 9... Ion source of atmospheric pressure ionization mass spectrometer, 10... Analysis section of atmospheric pressure ionization mass spectrometer, 12... Rotary pump, 13... Combiner, 15... Sample cylinder collection cylinder.
Claims (1)
体皮膚に密着させて上記生体皮膚から発生する揮
発性有機物からなる試料ガスを採取するための開
口と、上記採取された試料ガスを上記キヤリアガ
スと共に導出するための導出口とからなる試料ガ
ス採取手段と、上記生体皮膚から離間して設けら
れた加熱手段とを有し、上記試料ガス採取手段が
上記導出口を介して大気圧イオン化質量分析計の
イオン源に接続されていることを特徴とする試料
ガス採取測定装置。 ２ 上記試料ガス採取手段が鐘形ガラス容器から
なることを特徴とする特許請求の範囲第１項記載
の試料ガス採取測定装置。 ３ 上記加熱手段が赤外線ランプからなることを
特徴とする特許請求の範囲第１項記載の試料ガス
採取測定装置。 ４ 上記試料ガス採取手段が上記試料ガスを採取
中、負圧に維持されていることを特徴とする特許
請求の範囲第１項記載の試料ガス採取測定装置。[Scope of Claims] 1. An inlet for introducing a carrier gas, an opening for collecting a sample gas consisting of volatile organic matter generated from the skin of the living body by bringing it into close contact with the skin of the living body, and the sample gas collected above. and a heating means provided at a distance from the biological skin, and the sample gas sampling means includes an outlet for introducing the carrier gas together with the carrier gas, and a heating means provided at a distance from the biological skin, and the sample gas collecting means is heated to atmospheric pressure through the outlet. A sample gas sampling and measuring device, characterized in that it is connected to an ion source of an ionization mass spectrometer. 2. The sample gas sampling and measuring device according to claim 1, wherein the sample gas sampling means comprises a bell-shaped glass container. 3. The sample gas sampling and measuring device according to claim 1, wherein the heating means comprises an infrared lamp. 4. The sample gas sampling and measuring device according to claim 1, wherein the sample gas sampling means is maintained at a negative pressure while sampling the sample gas.
Priority Applications (1)
| Application Number | Priority Date | Filing Date | Title |
|---|---|---|---|
| JP57197514A JPS5988141A (en) | 1982-11-12 | 1982-11-12 | Sample gas sampling measurement device |
Applications Claiming Priority (1)
| Application Number | Priority Date | Filing Date | Title |
|---|---|---|---|
| JP57197514A JPS5988141A (en) | 1982-11-12 | 1982-11-12 | Sample gas sampling measurement device |
Publications (2)
| Publication Number | Publication Date |
|---|---|
| JPS5988141A JPS5988141A (en) | 1984-05-22 |
| JPH0347855B2 true JPH0347855B2 (en) | 1991-07-22 |
Family
ID=16375728
Family Applications (1)
| Application Number | Title | Priority Date | Filing Date |
|---|---|---|---|
| JP57197514A Granted JPS5988141A (en) | 1982-11-12 | 1982-11-12 | Sample gas sampling measurement device |
Country Status (1)
| Country | Link |
|---|---|
| JP (1) | JPS5988141A (en) |
Cited By (3)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| WO2002054041A1 (en) * | 2000-12-27 | 2002-07-11 | Japan Science And Technology Corporation | Skin permeable gas collector and skin permeable gas measuring apparatus |
| JP2010148692A (en) * | 2008-12-25 | 2010-07-08 | National Cardiovascular Center | Method and apparatus for detecting surface gas |
| JP2010281698A (en) * | 2009-06-04 | 2010-12-16 | Toyota Central R&D Labs Inc | Skin gas detection device |
Families Citing this family (5)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| JP2533709Y2 (en) * | 1988-02-05 | 1997-04-23 | 東京瓦斯 株式会社 | Gasification sampling equipment for low temperature liquefied gas |
| GB0416239D0 (en) * | 2004-07-21 | 2004-08-25 | Givaudan Sa | Method to identify or evaluate compounds useful in the field of fragrances and aromas |
| JP4669456B2 (en) * | 2006-09-01 | 2011-04-13 | 花王株式会社 | Volatile substance collection device and method |
| DE102009016512B4 (en) * | 2009-04-08 | 2011-05-12 | Forschungszentrum Jülich GmbH | Method and apparatus for performing a quantitative spatially resolved local and distributional analysis of chemical elements and in situ characterization of the ablated surface regions |
| MX2011012540A (en) | 2009-05-27 | 2012-04-02 | Medimass Kft | System and method for identification of biological tissues. |
Family Cites Families (2)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| JPS5631206U (en) * | 1979-08-17 | 1981-03-26 | ||
| DE3018863A1 (en) * | 1980-05-16 | 1981-11-26 | Hellige Gmbh, 7800 Freiburg | HEATED MEASURING METER FOR PHYSIOLOGICAL MEASUREMENTS WITH A BUILT-IN TEMPERATURE-CONTROLLED SWITCH |
-
1982
- 1982-11-12 JP JP57197514A patent/JPS5988141A/en active Granted
Cited By (3)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| WO2002054041A1 (en) * | 2000-12-27 | 2002-07-11 | Japan Science And Technology Corporation | Skin permeable gas collector and skin permeable gas measuring apparatus |
| JP2010148692A (en) * | 2008-12-25 | 2010-07-08 | National Cardiovascular Center | Method and apparatus for detecting surface gas |
| JP2010281698A (en) * | 2009-06-04 | 2010-12-16 | Toyota Central R&D Labs Inc | Skin gas detection device |
Also Published As
| Publication number | Publication date |
|---|---|
| JPS5988141A (en) | 1984-05-22 |
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