WO2012165182A1 - 生体ガス検知装置及び生体ガス検知方法 - Google Patents
生体ガス検知装置及び生体ガス検知方法 Download PDFInfo
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- WO2012165182A1 WO2012165182A1 PCT/JP2012/062876 JP2012062876W WO2012165182A1 WO 2012165182 A1 WO2012165182 A1 WO 2012165182A1 JP 2012062876 W JP2012062876 W JP 2012062876W WO 2012165182 A1 WO2012165182 A1 WO 2012165182A1
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- G—PHYSICS
- G01—MEASURING; TESTING
- G01N—INVESTIGATING OR ANALYSING MATERIALS BY DETERMINING THEIR CHEMICAL OR PHYSICAL PROPERTIES
- G01N27/00—Investigating or analysing materials by the use of electric, electrochemical, or magnetic means
- G01N27/02—Investigating or analysing materials by the use of electric, electrochemical, or magnetic means by investigating impedance
- G01N27/04—Investigating or analysing materials by the use of electric, electrochemical, or magnetic means by investigating impedance by investigating resistance
- G01N27/12—Investigating or analysing materials by the use of electric, electrochemical, or magnetic means by investigating impedance by investigating resistance of a solid body in dependence upon absorption of a fluid; of a solid body in dependence upon reaction with a fluid, for detecting components in the fluid
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- G—PHYSICS
- G01—MEASURING; TESTING
- G01N—INVESTIGATING OR ANALYSING MATERIALS BY DETERMINING THEIR CHEMICAL OR PHYSICAL PROPERTIES
- G01N33/00—Investigating or analysing materials by specific methods not covered by groups G01N1/00 - G01N31/00
- G01N33/0004—Gaseous mixtures, e.g. polluted air
- G01N33/0009—General constructional details of gas analysers, e.g. portable test equipment
- G01N33/0027—General constructional details of gas analysers, e.g. portable test equipment concerning the detector
- G01N33/0031—General constructional details of gas analysers, e.g. portable test equipment concerning the detector comprising two or more sensors, e.g. a sensor array
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- G—PHYSICS
- G01—MEASURING; TESTING
- G01N—INVESTIGATING OR ANALYSING MATERIALS BY DETERMINING THEIR CHEMICAL OR PHYSICAL PROPERTIES
- G01N33/00—Investigating or analysing materials by specific methods not covered by groups G01N1/00 - G01N31/00
- G01N33/48—Biological material, e.g. blood, urine; Haemocytometers
- G01N33/483—Physical analysis of biological material
- G01N33/497—Physical analysis of biological material of gaseous biological material, e.g. breath
Definitions
- the present invention relates to an apparatus for detecting a desired specific component in a biological gas using a gas sensor without separation and calculating the concentration thereof.
- the present invention also relates to a method for detecting a desired specific component in a biological gas in which an interference gas component coexists, using a gas sensor without separation, and calculating the concentration thereof.
- Patent Literature 1 and Patent Literature 2 disclose techniques for detecting diabetes and measuring the degree of burning of body fat by measuring the concentration of acetone contained in exhaled gas.
- Patent Document 3 discloses a technique for detecting abnormal growth of intestinal anaerobic bacteria and indigestion syndrome by measuring hydrogen contained in exhaled gas.
- Patent Document 4 and Patent Document 5 include not only a single gas component in the exhaled gas but also a plurality of types of gas detection elements such as acetone, nitric oxide, carbon dioxide, hydrogen, and ammonia. A method for detecting a plurality of types of gases therein and performing a complex health examination is disclosed.
- JP 2002-31615 A JP 2001-349888 A JP 2006-75447 A JP 2009-257772 A JP 2010-26746 A JP-A-5-203598
- the present invention solves the above-mentioned problems and easily detects a desired specific component in a biological gas emitted from a living body using a small number of gas sensors without separation even if an interference gas coexists. It is an object of the present invention to provide an apparatus and method that can calculate the concentration and thereby check the health status and diet results anytime, anywhere.
- the biological gas detection device of the present invention is Sensor unit including multiple types of gas sensors, Control unit of the sensor unit, Including data recorder and data analyzer,
- the data recording unit includes a database on the characteristics of the sensitivity of the gas sensor with respect to a single desired gas component contained in the biological gas, a single interference gas component, and a mixed gas thereof
- the data analysis unit is a biological gas detection device, wherein the concentration of the desired gas component is calculated based on the sensitivity of the gas sensor and the database output at the time of detection of the biological gas.
- the biological gas detection method of the present invention comprises: Sensor unit including multiple types of gas sensors, Control unit of the sensor unit, A biogas detection method performed by a biogas detection device including a data recording unit and a data analysis unit,
- the data recording unit includes a database on the characteristics of the sensitivity of the gas sensor with respect to a single desired gas component contained in the biological gas, a single interference gas component, and a mixed gas thereof
- the bioanalyzing method is characterized in that the data analysis unit calculates the desired gas component concentration based on the sensitivity of the gas sensor output in the biogas detection and the database.
- the embodiment of the present invention in the measurement of a biogas component emitted from a living body, separation of the biogas component is not required, and a plurality of types of gas sensors are used, and a desired specific biogas component is present even in the presence of interference gas. And a method for calculating the concentration by detecting the desired specific biological gas in consideration of the influence of interference gas components, and anyone can easily and anywhere from the biological gas It is possible to check the health status and diet results.
- FIG. 1 is a schematic view showing a biological gas detection device according to one embodiment of the present invention.
- FIG. 2 is a graph (database) showing changes in sensitivity of the gas sensor A when the acetone concentration is changed in the example.
- FIG. 3 is a graph (database) showing changes in sensitivity of the gas sensor A when the acetone concentration is changed in the presence of ethanol in the example.
- FIG. 4 is a graph (database) showing a change in sensitivity of the gas sensor B when the ethanol concentration is changed in the example.
- FIG. 5 is a configuration example of the exhalation gas detection device in the embodiment.
- FIG. 6 is a list showing the types of simulated exhaled gas and sensor sensitivity measurement results in the example.
- FIG. 7 is a diagram illustrating a change in sensitivity of the gas sensor A when the acetone concentration in the pseudo expiration gas is changed in the example.
- FIG. 8 is a diagram illustrating a change in sensitivity of the gas sensor B when the acetone concentration in the pseudo expiration gas is changed in the example.
- FIG. 9 is a diagram illustrating the sensitivity ratio between the gas sensor A and the gas sensor B when the acetone concentration in the pseudo-exhalation gas is changed in the example.
- FIG. 10 is a flowchart of an acetone concentration calculation method in the first embodiment.
- FIG. 11 is a list showing measurement results of actual breath gas types and sensor sensitivity in the examples.
- FIG. 12 shows an implementation result of the method for calculating the acetone concentration in Example 1.
- FIG. 13 is a flowchart of an acetone concentration calculation method in the second embodiment.
- FIG. 14 shows an implementation result of the acetone concentration calculation method in Example 2.
- a desired specific component in a biological gas emitted from a living body can be easily detected using a small number of types of gas sensors without separation even if an interference gas coexists. Is calculated.
- the gas emitted from the living body means a component discharged from the living body through various biochemical pathways in the living body.
- Specific examples of discharge to the outside of the body include discharge from the lungs into the breath by breathing, discharge from the gastrointestinal tract and the like through the esophagus and mouth, and the like.
- the gas or gas component to be discharged is not necessarily limited to a gas that is a normal temperature and pressure condition (for example, 1 atm, 25 ° C.), and is simultaneously discharged to the outside of the living body described above. It means to include other gas components and components discharged in a gas state together with moisture.
- Such biological gas components include inorganic gas components and organic gas components. Examples of the inorganic gas component include hydrogen, ammonia, and nitric oxide.
- the organic gas component examples include acetone, aldehyde, alcohol, and the like.
- the biogas component whose concentration is to be detected is calculated as a desired specific component (or desired gas component).
- the desired specific component is described as acetone.
- the coexisting gas component other than the desired component is described as the interference gas.
- the interference gas here means not only the gas component that strongly interferes with the detection / concentration calculation of the desired gas component in the detection apparatus and detection method of the embodiment of the present invention, but also the component that interferes weakly or not at all. It also means including gas components that do not interfere. This is because the interference action / phenomenon depends on the type of sensor used, the type of biological gas, the existing concentration, the detection condition (for example, temperature), and the like.
- the apparatus / method of the embodiment of the present invention is characterized in that even if the interference gas described above coexists, the concentration is calculated by simple detection using a small number of types of gas sensors without separation.
- without separation means that at least a desired gas component is separated from other gas components, and interference action (and its possibility) is removed, and all gas components are separated from each other. Not what you want.
- a small number of types of gas sensors are used on the premise of the presence of interference. That is, in the embodiment of the present invention, it is not necessary to use as many specific / selective gas sensors as the number of biological gas components for each gas component contained in the biological gas.
- the gas sensor that can be used in the embodiment of the present invention is a sensor that can appropriately select an appropriate sensor from gas sensors of various specifications that are generally known.
- a general-purpose gas sensor can be used in the embodiment of the present invention.
- the gas sensor that can be used in the embodiment of the present invention is based on the type and concentration range of the components to be detected (desired gas components, interference gas components, other gas components such as moisture), detection limits, detection conditions, etc. It is possible to appropriately select an optimal sensor from the already known sensors, or to modify the already known sensor to be used as the optimal sensor. For example, among the gas components that may be contained in exhaled breath, acetone is the desired gas component, and alcohol, hydrogen, and the like are considered as possible interfering gas components. Is preferred.
- the gas component contained in the exhaled breath often has a low concentration, and it is preferable to use a semiconductor gas sensor having a high detection capability for the gas component to be detected.
- “high detection ability” means that the concentration can be identified even when the concentration of the gas component to be detected is low.
- At least two types of sensors are used even if two or more types of coherent gas components coexist with a desired gas component.
- These two types of sensors may be gas sensors.
- the selection of such a sensor is not particularly limited, but among these at least two types of sensors, the first sensor mainly has a high detection ability for a desired gas component, It is preferable to select a sensor that has a detection capability for at least an interfering gas component and that exhibits gas sensitivity characteristics different from those of the first sensor. By such selection, as described below, an algorithm for detecting a desired gas component and calculating its concentration can be found more easily.
- the apparatus according to the embodiment of the present invention will be specifically described below.
- FIG. 1 is a schematic view showing an embodiment of the biological gas detection device of the present invention.
- the sensor unit 3 is provided with a gas sensor A and a gas sensor B, and the sensors A and B are controlled by the control unit 4. Further, the control unit 4 is connected to the data recording unit 5 and the data analysis unit 6.
- the gas sensor A is a gas sensor having a relatively high detectability with respect to a desired specific gas component
- the gas sensor B has a detectability with respect to at least an interference gas component, and has a gas sensitivity characteristic different from that of the gas sensor A.
- It is a gas sensor shown.
- the gas sensor has substantially the same detection ability with respect to a desired gas component and an interference gas component.
- the present invention is not limited to this number, and the number of gas sensors is two or more. Also good.
- the biological gas components 8, 9, and 10 are detected simultaneously or separately by the gas sensors A and B, and data is output.
- the output data is displayed on the sensor unit or output from the sensor unit for further recording and analysis as described below.
- the gas sensors A and B are controlled by the control unit 4.
- the detection operation by the gas sensors A and B and the output data therefrom are controlled by the control unit 4.
- the control unit 4 further sends the output data to the data recording unit 5 for recording.
- the output data may be output directly to the data recording unit 5 without going through the control unit 4.
- the recorded data is analyzed by the data analysis unit 6, and the concentration of the interference gas component is calculated as necessary, including the concentration of a desired specific gas component.
- the data analysis unit 6 calculates the sensitivity of each of the gas sensors A and B with respect to the measurement target gas, and calculates the concentration of the gas.
- the sensitivity of the gas sensor is calculated as, for example, the ratio of R to Rair (R / Rair) where Rir is the resistance of the gas sensor in the air and R is the resistance of the gas sensor when the measurement target gas is sprayed.
- R / Rair is defined as sensitivity and used for convenience.
- the sensitivity calculation method is not limited to this method, and depending on the method, the magnitude comparison condition with the threshold value in the density calculation algorithm described below may be reversed.
- the resistance value and sensitivity (R / Rair) value of the sensor decrease as the reducing gas concentration increases.
- the gas sensor A and the gas sensor B are both semiconductor gas sensors using an n-type semiconductor.
- the gas sensor of the present invention is not limited to the gas sensor having such characteristics, and the resistance value and the sensitivity value of the sensor may increase as the reducing gas concentration increases.
- the gas concentration calculation method uses, for example, a database showing the relationship between sensitivity and concentration recorded in advance from the sensitivity of the obtained gas sensor (FIGS. 2 to 4).
- the database to be used is not limited to the one showing the relationship between the sensitivity and the concentration.
- the sensitivity of each sensor, the sum of the sensitivity between the sensors, the ratio of the sensitivity between the sensors, or the relationship between them and the concentration, Etc. may be shown.
- the database recorded in advance may be recorded in any of the control unit 4, the recording unit 5, or the data analysis unit 6.
- the database includes sensitivity behaviors of the sensors A and B with respect to a desired gas component, an interference gas component, and a mixed gas of the desired gas component and the interference gas component. Specifically, the relationship between the concentration of each single gas of the interference gas component or the desired gas component and each sensor sensitivity, the influence of the mixing ratio of the interference gas component on the sensor sensitivity for the desired gas component, and the like. Further, such a database may contain other parameters derived from these sensitivity behaviors. Specifically, the sensitivities of the gas sensors A and B when the biological gas is exposed to the gas sensors A and B are ⁇ and ⁇ .
- a database showing the relationship between ⁇ , ⁇ , and E is created in advance, and some or all of these values are used to generate interference gas components (gas component B, gas component C).
- the algorithm for calculating / estimating the concentration of the desired gas component (gas component A) in consideration of the influence of () is prepared and created.
- the data analysis unit 6 finds the algorithm by referring to a database created based on the values of ⁇ , ⁇ , E for the biological gas actually obtained by measurement, and considers the influence of the interference gas component, The concentration of the desired gas component is calculated.
- FIG. 1 shows an example in which three types of gases, gas component A, gas component B, and gas component C, are included as biological gases.
- the desired gas component is A
- the interference gas components are B and C.
- the actual biogas components are not three types, but include a great variety of gas components.
- the case where the biogas components are three types will be described.
- the sensitivity of the gas sensor A and the gas sensor B changes.
- the sensitivity change of the gas sensor A is largely due to the influence of the gas component A.
- the gas component B, The influence of C cannot be ignored.
- the concentration of the desired gas component is calculated.
- the concentration is very low so that it can be considered that no desired gas component is present. Or, it is judged that there was a problem during the measurement.
- the concentration of the desired gas component is calculated based on the sensitivity of the gas sensor A and the database.
- the sensitivity of the gas sensor B is not more than a predetermined second threshold value and the sensitivity ratio between the gas sensor A and the gas sensor B is larger than the predetermined third threshold value, the sensitivity of the gas sensor A is Based on the database, the concentration of the desired gas component is calculated.
- the sensitivity of the gas sensor B is not more than a predetermined second threshold value and the sensitivity ratio between the gas sensor A and the gas sensor B is not more than the predetermined third threshold value, the sensitivity of the gas sensor B and the database Then, the concentration of the interference gas component is calculated, and the concentration of the desired gas component is calculated based on the interference gas component concentration, the sensitivity of the gas sensor A, and the database.
- the algorithm may be simplified as follows.
- the concentration of the desired gas component is calculated based on the sensitivity of the gas sensor A and the database.
- the sensitivity of the gas sensor B is not more than a predetermined fourth threshold value and the sensitivity of the gas sensor A is not more than a predetermined fifth threshold value, the sensitivity of the gas sensor A and the database are used. The concentration of the desired gas component is calculated.
- the sensitivity of the gas sensor B is a value equal to or lower than the predetermined fourth threshold and the sensitivity of the gas sensor A is greater than the predetermined fifth threshold, the sensitivity of the gas sensor B interferes with the database.
- the concentration of the gas component is calculated, and the concentration of the desired gas component is calculated based on the interference gas component concentration, the sensitivity of the gas sensor A, and the database.
- FIG. 5 schematically shows an embodiment in which a sensor block 17 including a sensor unit 13 is further provided in the apparatus of the embodiment of the present invention described above, and was used in the examples described below.
- an exhalation air inlet 19 and a pump 20 biological gas introduction unit
- the pump 20 is not always necessary, and may be provided when gas replacement in the sensor unit is desired to be performed particularly quickly.
- the biological gases 22, 23, and 24 are introduced into the sensor unit 13 from the exhalation air inlet 19, and each component of the biological gas is detected by the gas sensors A and B and affects each sensor sensitivity. As a result, a desired gas component of the biological gas can be detected accurately and quickly, and its concentration can be calculated.
- exhalation is assumed as a biological gas, and acetone contained in exhalation is used as a desired gas component. Further, ethanol and hydrogen contained in exhaled air are used as interference gas components.
- the gas sensors A and B used in the examples were semiconductor gas sensors manufactured by FIS Co., Ltd. In the measurement, each sensor was exposed to the atmosphere for 3 minutes and read as Rair, and the measurement gas described below was similarly exposed by gently flowing over the sensor for 10 seconds to read the resistance value R.
- Preparation 2 Creation of a database of acetone concentration in the presence of ethanol
- the sensitivity of the gas sensor A with respect to the acetone concentration below is measured, and a database of the sensitivity and acetone concentration of the gas sensor A in the presence of ethanol is created.
- An example of the measurement result is shown in FIG.
- FIG. 6 shows the 11 types of simulated exhaled gas used here, the sensitivity of gas sensors A and B, the ratio of the sensitivity of gas sensor A and the sensitivity of gas sensor B, and the sum of the sensitivity of gas sensor A and the sensitivity of gas sensor B.
- Summarized. 7 to 9 show the measurement results of FIG. 6 plotted on a graph.
- Example 1 Based on the above measurement data, an acetone concentration calculation algorithm was created as follows (FIG. 10).
- FIG. 11 shows the measurement results of 11 types of exhaled gas and sensor sensitivity.
- FIG. 11 also shows the results of measuring the concentrations of acetone, hydrogen, and ethanol using a gas chromatography apparatus using the same exhaled gas in order to verify the validity of the algorithm.
- exhaled gas from subjects who did not drink was used.
- No. 8 to No. 11 the measurement was performed using the breath gas of the subject after drinking.
- the sensor sensitivity measurement used the apparatus typically shown in FIG.
- Exhalation air was blown into an exhalation air inlet 19 provided in the sensor block 17 including the sensor unit 13 to bring the gas sensors A and B provided in the sensor unit 13 into contact with each other.
- the pump 20 is not always necessary, and can be used for quick exchange of exhalation.
- FIG. 12 shows the result of distributing the 11 types of exhaled gas based on the acetone concentration estimation algorithm (FIG. 10) according to Example 1 of the present invention.
- the exhaled gas of No. 4 has a concentration that is very low so that it can be considered that acetone in the exhalation is not present or is being measured. It is judged that there was a problem.
- the concentration is very low at 0.034 ppm, which can be said to be almost consistent with the determination result.
- the sensitivity of the gas sensor B is 0.5 or less, it is determined that ethanol or high-concentration hydrogen exists. And since the sensitivity ratio of a gas sensor is 0.6 or less, it is judged that ethanol exists. From these, the sensitivity of the gas sensor B is applied to the database of the ethanol concentration in the state where the interference gas component does not exist in FIG. 4 to calculate the ethanol concentration. Then, the estimated ethanol concentration is applied to a database showing the relationship of acetone concentration in the presence of ethanol in FIG.
- the acetone concentration is calculated as 0.964 ppm, and this concentration is very close to 0.843 ppm as a result of measuring the acetone concentration of the exhaled breath with a gas chromatography apparatus.
- Example 2 ⁇ Simplified acetone concentration calculation algorithm>
- the gas sensor A is a gas sensor having a particularly high detection capability for acetone
- the acetone concentration calculation algorithm may be simplified as follows (FIG. 13).
- FIG. 14 shows the result of distributing the 11 types of exhaled gas of FIG. 11 based on the simplified acetone concentration estimation algorithm (FIG. 13) according to Example 2 of the present invention. Except for the exhalation of No. 5, it is the same distribution result as the result of applying the non-simplified acetone concentration calculation algorithm (FIG. 12), and even if the algorithm is simplified, it has a certain validity. I understand.
- the device of the embodiment of the present invention is built in the mobile phone or directly connected to the mobile phone via a microUSB or the like, and functions of power supply, data recording unit, and data analysis unit to the device of the embodiment of the present invention are provided. It can also be provided on the mobile phone side. It is also possible to display the measurement result on a display on the mobile phone. With such a configuration, the device according to the embodiment of the present invention can be easily used anytime and anywhere, and the health condition and diet results can be confirmed.
- the apparatus according to the embodiment of the present invention can be provided with a communication function such as Bluetooth or wireless LAN. With this configuration, it is possible to display the measurement results on a mobile phone or a personal computer by communicating the health status and diet results obtained by the apparatus according to the embodiment of the present invention with the mobile phone, for example. Become.
- the breath diagnosis apparatus can be configured using the apparatus according to the embodiment of the present invention.
- the relationship between a predetermined value of the concentration of a desired gas component in exhaled breath and the occurrence of a specific disease is found, and the value is stored in the apparatus according to the embodiment of the present invention.
- a warning is issued if the desired gas component concentration is greater than the value.
- the user can easily and easily know the specific disease onset.
- Modification 5 Further, in Modification 4 above, some or all of the functions of the data recording unit and the data analysis unit in the configuration according to the embodiment of the present invention can be provided in a medical institution server on the network. .
- the sensor sensitivity data according to the embodiment of the present invention can be transferred to a medical institution server on the network in real time if necessary, and the data can be recorded or analyzed on the server. It becomes. Based on this result, it is possible to receive a breath diagnosis by an expert such as a doctor of the medical institution. If necessary, the mobile phone can be notified (or displayed) of the result, and a bidirectional health management system, health advice system, diet management system, diet effect confirmation system, breath diagnosis system, etc. can be constructed.
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Abstract
Description
複数種類のガスセンサを含むセンサユニット、
前記センサユニットの制御部、
データ記録部及び
データ解析部を含み、
前記データ記録部は、前記生体ガスに含まれる所望ガス成分の単体、干渉ガス成分の単体及びそれらの混合ガスに対する前記ガスセンサの感度の特性についてのデータベースを含み、
前記データ解析部は、前記生体ガス検知の際に出力される前記ガスセンサの感度と前記データベースとに基づいて前記所望ガス成分の濃度を算出することを特徴とする、生体ガス検知装置である。
複数種類のガスセンサを含むセンサユニット、
前記センサユニットの制御部、
データ記録部及び
データ解析部を含む生体ガス検知装置により行われる生体ガス検知方法であり、
前記データ記録部は、前記生体ガスに含まれる所望ガス成分の単体、干渉ガス成分の単体及びそれらの混合ガスに対する前記ガスセンサの感度の特性についてのデータベースを含み、
前記データ解析部は、前記生体ガス検知の際に出力される前記ガスセンサの感度と前記データベースとに基づいて前記所望ガス成分濃度を算出することを特徴とする、生体ガス検知方法である。
アセトン濃度を0.1、1、10、50[ppm]と変化させた際における、ガスセンサAの感度を測定し、干渉ガス成分が存在しないアセトン純ガスを用いた際のガスセンサAの感度とアセトン濃度のデータベースを作成する。測定結果の例を図2に示す。
アセトン0.1、1、10、50[ppm]のいずれかと、エタノール0、0.1、1、10、150[ppm]のいずれかとを混合したアセトンとエタノールの混合ガス存在下において、エタノール存在下でのアセトン濃度に対するガスセンサAの感度を測定し、エタノールが存在する状態でのガスセンサAの感度とアセトン濃度のデータベースを作成する。測定結果の例を図3に示す。
エタノール濃度を0.1、1、10、150[ppm]と変化させた際における、ガスセンサBの感度を測定し、干渉ガス成分が存在しないエタノール純ガスを用いた際のガスセンサBの感度とエタノール濃度のデータベースを作成する。測定結果の例を図4に示す。
ガスセンサA、ガスセンサBを用いて、アセトン、水素、エタノールを混合した擬似呼気ガス中におけるアセトン濃度測定の実験を行い、実験結果から干渉ガス成分(水素、エタノール)の影響を考慮したアセトン濃度を算出するアルゴリズムを作成した。図6には、ここで用いた擬似呼気ガスの11種類と、それらに対するガスセンサA及びBの感度、ガスセンサAの感度とガスセンサBの感度の比及びガスセンサAの感度とガスセンサBの感度の和をまとめた。また、図7~図9は図6の測定結果をグラフ上にプロットしたものを示す。ここで、ガスセンサAとガスセンサBの感度比をEとして表し、E=ガスセンサAの感度/ガスセンサBの感度とする。
<アセトン濃度算出アルゴリズム>
以上の測定データに基づき、次のようにアセトン濃度算出アルゴリズムを作成した(図10)。
(I)ガスセンサBの感度が0.5より大きい時:エタノール、または高濃度の水素はほとんど存在しないと判断し、ガスセンサAの感度を図2より作成されるエタノール非存在下のガスセンサAの感度とアセトン濃度の関係性を示すデータベースに当てはめて、アセトン濃度を算出する。
(i)センサの感度比Eが0.6より大きい時:アセトンは10ppm以下で、水素が高濃度にあると判断する。また、水素はガスセンサAの感度への影響は小さいので、水素の影響は無視して、ガスセンサAの感度を図2より作成されるエタノール非存在下のガスセンサAの感度とアセトン濃度の関係性を示すデータベースに当てはめて、アセトン濃度を算出する。
作成したアセトン濃度推定アルゴリズム(図10)をもちいて、実際の呼気ガス中のアセトン濃度の算出を行った。図11は、測定を行った11種類の呼気ガスの種類とセンサ感度の測定結果である。図11には、アルゴリズムの正当性の検証のために、同じ呼気ガスを用いてガスクロマトグラフィ装置による、アセトン、水素、エタノールの濃度測定結果も合わせて示されている。番号1~番号7においては、飲酒をしていない被験者の呼気ガスを用いた。番号8~番号11では、飲酒をした後の被験者の呼気ガスを用いて測定を行った。センサ感度測定は図5で模式的に示す装置を用いた。センサユニット13を含むセンサブロック17に設けられた呼気吹き込み口19に呼気を吹き込んで、センサユニット13に設けられたガスセンサA及びBと呼気を接触させた。ここでポンプ20は必ずしも必要ではなく、呼気の迅速な交換を行う場合に使用することができる。
<簡略化アセトン濃度算出アルゴリズム>
ガスセンサAがアセトンに対して特に高い検知能を有するガスセンサである場合、前記アセトン濃度算出アルゴリズムは、次のように簡略化してもよい(図13)。
(I)ガスセンサAの感度が0.08以下の時:エタノールが一定濃度以上存在するが、ガスセンサAの感度への影響は小さいと判断し、エタノールの影響は無視する。また、水素はガスセンサAの感度への影響は小さいので、水素の影響も無視し、ガスセンサAの感度を図2より作成されるエタノール非存在下のガスセンサAの感度とアセトン濃度の関係性を示すデータベースに当てはめて、アセトン濃度を算出する。
本発明の実施形態の装置は、携帯電話に内蔵するか又はmicroUSB等を介して携帯電話に直接接続し、本発明の実施形態の装置への電力供給、データ記録部、データ解析部の機能を携帯電話側に設けるようにすることも可能である。また測定結果を携帯電話上のディスプレイに表示できるようにすることも可能である。かかる構成により、本発明の実施形態に係る装置をいつでもどこでも簡便に使用でき、健康状態やダイエットの成果を確認することができる。
また本発明の実施形態の装置に、Bluetooth、無線LAN等の通信機能を設けることも可能である。かかる構成により、本発明の実施形態に係る装置で得られた健康状態やダイエットの成果を、例えば携帯電話と通信を行うことにより、携帯電話やパソコンで測定結果の表示などを行うことが可能となる。
また、前記変形例1、2において、データ記録部やデータ解析部の機能の一部または全てを、ネットワーク上のサーバなどに具備させることも可能である。この構成により、本発明の実施形態によるセンサ感度のデータを、必要ならばリアルタイムで、ネットワーク上のサーバなどに転送し、サーバ上で当該データを記録させ又はデータを解析させることが可能となり、必要ならば結果を携帯電話に通知(又は表示)させることで、健康管理、健康アドバイス、ダイエット管理、ダイエット効果確認サービスなどのシステムが可能となる。
また、本発明の実施形態による装置を用いて、呼気診断装置を構成することができる。例えば呼気中の所望のガス成分の濃度の所定の値と特定の疾患発病との関連を見出しておき、本発明の実施形態に係る装置内にその値を記憶させておき、使用者が呼気を本装置で測定した際に、当該所望のガス成分濃度が当該値より大きい場合に警告を発するようにする。これにより、使用者が簡便かつ容易に特定の疾患発病を知ることができるようになる。
さらに上の変形例4において、本発明の実施形態に係る構成のうちデータ記録部やデータ解析部の機能の一部または全てを、ネットワーク上の医療機関のサーバなどに具備させることも可能である。この構成により、本発明の実施形態によるセンサ感度のデータを、必要ならばリアルタイムで、ネットワーク上の医療機関のサーバなどに転送し、サーバ上で当該データを記録させ又はデータを解析させることが可能となる。この結果に基づき当該医療機関の医師などの専門家による呼気診断を受けることが可能となる。必要ならば結果を携帯電話に通知(又は表示)させることができ、双方向の健康管理システム、健康アドバイスシステム、ダイエット管理システム、ダイエット効果確認システム、呼気診断システムなどの構築が可能となる。
2…ガスセンサB
3…センサユニット
4…制御部
5…データ記録部
6…データ解析部
7…生体ガス
8…ガス成分A
9…ガス成分B
10…ガス成分C
11…ガスセンサA
12…ガスセンサB
13…センサユニット
14…制御部
15…データ記録部
16…データ解析部
17…センサブロック
19…吸気吹き込み口
20…ポンプ
21…擬似呼気ガス
22…アセトン
23…水素
24…エタノール
Claims (18)
- 生体ガス検知装置であり、
複数種類のガスセンサを含むセンサユニット、
前記センサユニットの制御部、
データ記録部及び
データ解析部を含み、
前記データ記録部は、前記生体ガスに含まれる所望ガス成分の単体、干渉ガス成分の単体及びそれらの混合ガスに対する前記ガスセンサの感度の特性についてのデータベースを含み、
前記データ解析部は、前記生体ガス検知の際に出力される前記ガスセンサの感度と前記データベースとに基づいて前記所望ガス成分の濃度を算出することを特徴とする、生体ガス検知装置。 - 請求項1に記載の生体ガス検知装置であって、
前記ガスセンサは二種類であり、第1のガスセンサは所望ガス成分に対して相対的に高い検知能を有する半導体式ガスセンサであり、第2のガスセンサは少なくとも干渉ガス成分に対して検知能を有し、第1のガスセンサとは異なる感ガス特性を示す半導体式ガスセンサである、ことを特徴とする生体ガス検知装置。 - 請求項1乃至2のいずれかに記載の生体ガス検知装置であって、
前記第2のガスセンサは所望ガス成分と干渉ガス成分とにほぼ同等の検知能を有する半導体式ガスセンサである、ことを特徴とする生体ガス検知装置。 - 請求項1乃至3のいずれかに記載の生体ガス検知装置であって、
前記第1のガスセンサの感度と前記第2のガスセンサの感度との和が、予め定めた第1の閾値より大きい値であれば、所望ガス成分は存在しないとも見做し得るほど非常に低い濃度であった、もしくは測定中に問題があったとする、ことを特徴とする生体ガス検知装置。 - 請求項1乃至4のいずれかに記載の生体ガス検知装置であって、
前記第2のガスセンサの感度が予め定めた第2の閾値より大きい値であれば、前記第1のガスセンサの感度と前記データベースに基づき所望ガス成分の濃度を算出する、ことを特徴とする生体ガス検知装置。 - 請求項1乃至5のいずれかに記載の生体ガス検知装置であって、
前記第2のガスセンサの感度が予め定めた第2の閾値以下の値であり、かつ前記第1のガスセンサと前記第2のガスセンサの感度比が予め定めた第3の閾値より大きい値であれば、前記第1のガスセンサの感度と前記データベースに基づき所望ガス成分の濃度を算出する、ことを特徴とする生体ガス検知装置。 - 請求項1乃至6のいずれかに記載の生体ガス検知装置であって、
前記第2のガスセンサの感度が予め定めた第2の閾値以下の値であり、かつ前記第1のガスセンサと前記第2のガスセンサの感度比が予め定めた第3の閾値以下であれば、前記第2のガスセンサの感度と前記データベースから干渉ガス成分の濃度を算出し、当該干渉ガス成分濃度、前記第1のガスセンサの感度及び前記データベースに基づき所望ガス成分の濃度を算出する、ことを特徴とする生体ガス検知装置。 - 請求項1乃至3のいずれかに記載の生体ガス検知装置であって、
前記第2のガスセンサの感度が予め定めた第4の閾値より大きい値であれば、前記第1のガスセンサの感度と前記データベースに基づき所望ガス成分の濃度を算出する、ことを特徴とする生体ガス検知装置。 - 請求項1乃至3のいずれかに記載の生体ガス検知装置であって、
前記第2のガスセンサの感度が予め定めた第4の閾値以下の値であり、かつ前記第1のガスセンサの感度が予め定めた第5の閾値以下の値であれば、前記第1のガスセンサの感度と前記データベースに基づき所望ガス成分の濃度を算出する、ことを特徴とする生体ガス検知装置。 - 請求項1乃至3のいずれかに記載の生体ガス検知装置であって、
前記第2のガスセンサの感度が予め定めた第4の閾値以下の値であり、かつ前記第1のガスセンサの感度が予め定めた第5の閾値より大きい値であれば、前記第2のガスセンサの感度と前記データベースから干渉ガス成分の濃度を算出し、当該干渉ガス成分濃度、前記第1のガスセンサの感度及び前記データベースに基づき所望ガス成分の濃度を算出する、ことを特徴とする生体ガス検知装置。 - 請求項1乃至10のいずれかに記載の生体ガス検知装置であって、
前記所望ガス成分がアセトンである、ことを特徴とする生体ガス検知装置。 - 請求項1乃至10のいずれかに記載の生体ガス検知装置であって、
前記干渉ガス成分の主要ガス成分がエタノールと水素であり、そのうち少なくとも1種類が前記所望ガス成分の干渉ガスである、ことを特徴とする生体ガス検知装置。 - 請求項1乃至12のいずれかに記載の生体ガス検知装置であって、前記生体ガスを前記センサユニットに導入する生体ガス導入ユニットをさらに備える、ことを特徴とする生体ガス検知装置。
- 請求項1乃至13のいずれかに記載の生体ガス検知装置であって、前記算出された前記所望ガス成分と干渉ガス成分のうち、少なくとも1種類のガス成分の濃度を表示するための表示ユニットをさらに備える、ことを特徴とする生体ガス検知装置。
- 請求項1乃至14のいずれかに記載の生体ガス検知装置であって、前記算出された前記所望ガス成分と干渉ガス成分のうち、少なくとも1種類のガス成分の濃度情報を、当該生体ガス検知装置から送信するための通信ユニットをさらに備える、ことを特徴とする生体ガス検知装置。
- 干渉ガスを含む生体ガス中の所望ガス成分の濃度を、前記成分を分離することなく検出して算出する生体ガス検知装置により行う生体ガス検知方法であり、
前記生体ガス検知装置は、
複数種類のガスセンサを含むセンサユニット、
前記センサユニットの制御部、
データ記録部及び
データ解析部を含み、
前記データ記録部は、前記生体ガスに含まれる所望ガス成分の単体、干渉ガス成分の単体及びそれらの混合ガスに対する前記ガスセンサの感度の特性についてのデータベースを含み、
前記データ解析部は、前記生体ガス検知の際に出力される前記ガスセンサの感度と前記データベースとに基づいて前記所望ガス成分の濃度を算出することを特徴とする、生体ガス検知方法。 - 請求項16に記載の生体ガス検知方法であり、
前記ガスセンサが、少なくとも2種類のガスセンサであって、第1のガスセンサは所望ガス成分に対して相対的に高い検知能を有する半導体式ガスセンサであり、第2のガスセンサは少なくとも干渉ガス成分に対して検知能を有し、第1のガスセンサとは異なる感ガス特性を示す半導体式ガスセンサであり、
これらを用いて少なくとも、
(i)前記所望ガス成分の単体の濃度に対する前記第1のガスセンサの感度の関係、
(ii)前記所望ガス成分に所定量の前記干渉ガス成分を加えた際の混合ガスの濃度に対する前記第1のガスセンサの感度の関係、及び
(iii)干渉ガス成分の単体の濃度に対する前記第2のガスセンサの感度の関係を取得してそれぞれのセンサについての感度特性のデータベースとし、
前記生体ガスを前記2種類のガスセンサで測定してそれぞれのセンサ感度を取得し、
前記第1のガスセンサの感度と前記第2のガスセンサの感度との和が、予め定めた第1の閾値より大きい値であれば、所望ガス成分は存在しないとも見做し得るほど非常に低い濃度であった、もしくは測定中に問題があったとし、
前記第2のガスセンサの感度が予め定めた第2の閾値より大きい値であれば、前記第1のガスセンサの感度と前記データベースに基づき所望ガス成分の濃度を算出し、
前記第2のガスセンサの感度が予め定めた第2の閾値以下の値であり、かつ前記第1のガスセンサと前記第2のガスセンサの感度比が予め定めた第3の閾値より大きい値であれば、前記第1のガスセンサの感度と前記データベースに基づき所望ガス成分の濃度を算出し、
前記第2のガスセンサの感度が予め定めた第2の閾値以下の値であり、かつ前記第1のガスセンサと前記第2のガスセンサの感度比が予め定めた第3の閾値以下であれば、前記第2のガスセンサの感度と前記データベースから干渉ガス成分の濃度を算出し、当該干渉ガス成分濃度、前記第1のガスセンサの感度及び前記データベースに基づき所望ガス成分の濃度を算出する、ことを特徴とする生体ガス検知方法。 - 請求項16に記載の生体ガス検知方法であり、
前記ガスセンサが、少なくとも2種類のガスセンサであって、第1のガスセンサは所望ガス成分に対して相対的に高い検知能を有する半導体式ガスセンサであり、第2のガスセンサは少なくとも干渉ガス成分に対して検知能を有し、第1のガスセンサとは異なる感ガス特性を示す半導体式ガスセンサであり、
これらを用いて少なくとも、
(i)前記所望ガス成分の単体の濃度に対する前記第1のガスセンサの感度の関係、
(ii)前記所望ガス成分に所定量の前記干渉ガス成分を加えた際の混合ガスの濃度に対する前記第1のガスセンサの感度の関係、及び
(iii)干渉ガス成分の単体の濃度に対する前記第2のガスセンサの感度の関係を取得してそれぞれのセンサについての感度特性のデータベースとし、前記生体ガスを前記2種類のガスセンサで測定してそれぞれのセンサ感度を取得し、
前記第2のガスセンサの感度が予め定めた第4の閾値より大きい値であれば、前記第1のガスセンサの感度と前記データベースに基づき所望ガス成分の濃度を算出し、
前記第2のガスセンサの感度が予め定めた第4の閾値以下の値であり、かつ前記第1のガスセンサの感度が予め定めた第5の閾値以下の値であれば、前記第1のガスセンサの感度と前記データベースに基づき所望ガス成分の濃度を算出し、
前記第2のガスセンサの感度が予め定めた第4の閾値以下の値であり、かつ前記第1のガスセンサの感度が予め定めた第5の閾値より大きい値であれば、前記第2のガスセンサの感度と前記データベースから干渉ガス成分の濃度を算出し、当該干渉ガス成分濃度、前記第1のガスセンサの感度及び前記データベースに基づき所望ガス成分の濃度を算出する、ことを特徴とする生体ガス検知方法。
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DE102015210622A1 (de) | 2014-06-11 | 2015-12-17 | Figaro Engineering Inc | Biological gas detection device, method, and program |
WO2017038889A1 (ja) * | 2015-08-31 | 2017-03-09 | 新コスモス電機株式会社 | ガス分析システム、及び、ガス分析方法 |
JP2017223557A (ja) * | 2016-06-15 | 2017-12-21 | 富士電機株式会社 | ガスセンサ |
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JP2019078752A (ja) * | 2017-10-20 | 2019-05-23 | 新コスモス電機株式会社 | ガス検知方法およびガス検知器 |
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JP2019117069A (ja) * | 2017-12-26 | 2019-07-18 | 株式会社Nttドコモ | 生体情報処理装置、生体情報処理システム、生体情報処理方法及びプログラム |
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Also Published As
Publication number | Publication date |
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CN103518130B (zh) | 2016-05-18 |
CN103518130A (zh) | 2014-01-15 |
US9410912B2 (en) | 2016-08-09 |
EP2634567A1 (en) | 2013-09-04 |
JPWO2012165182A1 (ja) | 2015-02-23 |
EP2634567A4 (en) | 2015-03-11 |
JP5818888B2 (ja) | 2015-11-18 |
US20130283889A1 (en) | 2013-10-31 |
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