WO2015033582A1 - ガス分析装置およびガス分析方法 - Google Patents
ガス分析装置およびガス分析方法 Download PDFInfo
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- WO2015033582A1 WO2015033582A1 PCT/JP2014/004597 JP2014004597W WO2015033582A1 WO 2015033582 A1 WO2015033582 A1 WO 2015033582A1 JP 2014004597 W JP2014004597 W JP 2014004597W WO 2015033582 A1 WO2015033582 A1 WO 2015033582A1
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- MWUXSHHQAYIFBG-UHFFFAOYSA-N Nitric oxide Chemical compound O=[N] MWUXSHHQAYIFBG-UHFFFAOYSA-N 0.000 claims description 42
- CSCPPACGZOOCGX-UHFFFAOYSA-N Acetone Chemical compound CC(C)=O CSCPPACGZOOCGX-UHFFFAOYSA-N 0.000 claims description 39
- GYHFUZHODSMOHU-UHFFFAOYSA-N nonanal Chemical compound CCCCCCCCC=O GYHFUZHODSMOHU-UHFFFAOYSA-N 0.000 claims description 32
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- IKHGUXGNUITLKF-XPULMUKRSA-N acetaldehyde Chemical compound [14CH]([14CH3])=O IKHGUXGNUITLKF-XPULMUKRSA-N 0.000 claims description 10
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Classifications
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- A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
- A61B5/00—Measuring for diagnostic purposes; Identification of persons
- A61B5/08—Detecting, measuring or recording devices for evaluating the respiratory organs
- A61B5/082—Evaluation by breath analysis, e.g. determination of the chemical composition of exhaled breath
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- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
- A61B5/00—Measuring for diagnostic purposes; Identification of persons
- A61B5/0059—Measuring for diagnostic purposes; Identification of persons using light, e.g. diagnosis by transillumination, diascopy, fluorescence
- A61B5/0075—Measuring for diagnostic purposes; Identification of persons using light, e.g. diagnosis by transillumination, diascopy, fluorescence by spectroscopy, i.e. measuring spectra, e.g. Raman spectroscopy, infrared absorption spectroscopy
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- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
- A61B5/00—Measuring for diagnostic purposes; Identification of persons
- A61B5/08—Detecting, measuring or recording devices for evaluating the respiratory organs
- A61B5/097—Devices for facilitating collection of breath or for directing breath into or through measuring devices
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- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
- A61B5/00—Measuring for diagnostic purposes; Identification of persons
- A61B5/44—Detecting, measuring or recording for evaluating the integumentary system, e.g. skin, hair or nails
- A61B5/441—Skin evaluation, e.g. for skin disorder diagnosis
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- A61B5/72—Signal processing specially adapted for physiological signals or for diagnostic purposes
- A61B5/7271—Specific aspects of physiological measurement analysis
- A61B5/7278—Artificial waveform generation or derivation, e.g. synthesising signals from measured signals
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- G01N21/00—Investigating or analysing materials by the use of optical means, i.e. using sub-millimetre waves, infrared, visible or ultraviolet light
- G01N21/17—Systems in which incident light is modified in accordance with the properties of the material investigated
- G01N21/25—Colour; Spectral properties, i.e. comparison of effect of material on the light at two or more different wavelengths or wavelength bands
- G01N21/31—Investigating relative effect of material at wavelengths characteristic of specific elements or molecules, e.g. atomic absorption spectrometry
- G01N21/35—Investigating relative effect of material at wavelengths characteristic of specific elements or molecules, e.g. atomic absorption spectrometry using infrared light
- G01N21/3504—Investigating relative effect of material at wavelengths characteristic of specific elements or molecules, e.g. atomic absorption spectrometry using infrared light for analysing gases, e.g. multi-gas analysis
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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
- G01N33/0036—General constructional details of gas analysers, e.g. portable test equipment concerning the detector specially adapted to detect a particular component
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- G01N33/48—Biological material, e.g. blood, urine; Haemocytometers
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- G01N33/497—Physical analysis of biological material of gaseous biological material, e.g. breath
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- 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
- G01N33/4975—Physical analysis of biological material of gaseous biological material, e.g. breath other than oxygen, carbon dioxide or alcohol, e.g. organic vapours
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- G01N—INVESTIGATING OR ANALYSING MATERIALS BY DETERMINING THEIR CHEMICAL OR PHYSICAL PROPERTIES
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Definitions
- the present invention relates to a gas analyzer and a gas analysis method for analyzing a plurality of gas components contained in a gas.
- Biological gases such as human breath, skin gas, and rectal gas (explosive) contain several hundred kinds of gaseous substances such as volatile organic compounds. Among them, substances that are causally related to diseases are also included, and these substances are quantitatively analyzed using these as markers to apply to biogas diagnosis for diagnosing diseases. Therefore, research for identifying biological gas components derived from diseases and research and development of new measurement / analysis methods have been actively conducted. As one of the methods for easily and rapidly measuring a trace component in a biological gas, there is an absorption spectroscopy using a mid-infrared laser.
- a component concentration is quantified by absorption spectroscopy measurement using a narrow-band mid-infrared laser wavelength-tuned to the absorption spectrum of the component as a light source.
- nitric oxide (NO) in biogas that can distinguish asthma from other chronic coughs can be quantitatively measured using a quantum cascade laser with a wavelength of 5.27 ⁇ m (1898 cm ⁇ 1 ).
- a detection limit of about is realized.
- Lung cancer-derived acetaldehyde can be measured with a detection limit of about 80 ppb using a quantum cascade laser of 5.79 ⁇ m (1727 cm ⁇ 1 ).
- the characteristic absorption bands of functional groups such as aldehydes, ketones, carboxylic acids, and amides that are important as biological products are concentrated in the vicinity of 1600-1800 cm ⁇ 1 , and are also in the vicinity of 800-1400 cm ⁇ 1, which are also called molecular fingerprint regions. In this region, many characteristic absorption spectra unique to the molecule are distributed.
- the effective wavelength tunable region of a mid-infrared laser with a narrowed spectral width is as narrow as several cm ⁇ 1 , making simultaneous measurement of multiple gases difficult.
- Patent Document 1 a combined light combining a near-infrared pump light and a near-infrared signal light from a semiconductor laser for detecting a first gas medium is incident on a PPLN crystal, and a second gas is obtained.
- Patent Document 1 it is difficult to efficiently analyze a gas because a lower detection limit that is different for each gas component, that is, a measurement integration time is not taken into consideration.
- An object of the present invention is to provide an apparatus and method for efficiently measuring a plurality of types of gas components using mid-infrared light of different wavelengths.
- the gas analyzer includes a cell that houses a gas to be measured, a light source that selects mid-infrared light of an arbitrary wavelength and emits the light into the cell, and transmits through the cell.
- the light source has a first light source that emits first infrared light and a wavelength different from the first infrared light.
- a second light source that emits the second infrared light, and a wavelength conversion device that outputs a difference frequency between the first infrared light and the second infrared light.
- the first light source is a laser that emits laser light having a single wavelength
- the second light source is laser light having a different wavelength. It is characterized by being made into the arrayed laser which radiates
- a nonlinear optical crystal that is not a ferroelectric crystal is used as the wavelength conversion device.
- the nonlinear optical crystal is an AgGaS 2 crystal.
- a sixth aspect of the present invention is the gas analyzer according to any one of the first to fifth aspects, wherein the gas component to be measured is selected from two of nitrogen monoxide, nonanal, acetaldehyde, and acetone. It is characterized by having more than seeds.
- the gas component to be measured is ethane, nonanal, acetaldehyde, methylamine, methanol, acetone, and It is characterized by two or more of methane.
- the present invention according to claim 8 is the gas analyzer according to any one of claims 1 to 7, wherein the gas to be measured is exhaled air.
- the gas to be measured is detected as a biological gas such as breath, skin gas, or rectal gas. From the concentration of the gas component, bronchial asthma, lung cancer, lung disease, renal failure, pneumonia, Helicobacter pylori, diabetes, obesity, or gastrointestinal failure is characterized.
- the gas analysis method of the present invention according to claim 10 is a gas for obtaining the concentration of the gas component in the gas to be measured using the light intensity of the wavelength in the mid-infrared region synchronized with the absorption spectrum of the gas component.
- the gas component at least a first gas component and a second gas component are measured, a mid-infrared light having a first wavelength corresponding to the first gas component, and the first gas component, And the measurement integration time of the first wavelength by the mid-infrared light and the measurement integration time of the second wavelength by the mid-infrared light. It is characterized by different times.
- the present invention according to claim 11 is the gas analysis method according to claim 10, wherein the gas to be measured is exhaled air.
- the present invention it is possible to realize an apparatus and method for efficiently measuring a plurality of types of gas components in a gas to be measured using mid-infrared light having a plurality of wavelengths.
- summary of the gas analyzer by one Example of this invention The figure which shows the structure of the light source of the gas analyzer.
- the gas analyzer corresponds to the measurement time setting means for setting the measurement integration time of the mid-infrared light of the wavelength for each gas component to be measured, and the measurement integration time.
- control means for controlling at least one of the emission time of the light source and the detection time of the detector.
- the light source is different from the first infrared light and the first light source that emits the first infrared light. It comprises a second light source that emits second infrared light having a wavelength, and a wavelength conversion device that outputs a difference frequency between the first infrared light and the second infrared light.
- the wavelength of the mid-infrared light output from the wavelength conversion device can be changed by changing the wavelengths of the first infrared light and the second infrared light.
- the first light source is a laser that emits a single-wavelength laser beam
- the second light source is a different wavelength.
- This is an arrayed laser that emits laser light.
- the wavelength of the infrared light emitted from the second light source is changed without changing the wavelength of the infrared light emitted from the first light source.
- the wavelength of infrared light can be changed.
- by using an arrayed laser as the second light source it is possible to change the wavelength of infrared light simply by switching the internal elements.
- the fourth embodiment of the present invention uses a nonlinear optical crystal that is not a ferroelectric crystal as a wavelength conversion device. According to the present embodiment, it is possible to output mid-infrared light having a light transmission region up to a long wavelength of 5 ⁇ m or longer.
- the nonlinear optical crystal is an AgGaS 2 crystal in the gas analyzer according to the fourth embodiment.
- the AgGaS 2 crystal is a high quality crystal among non-linear optical crystals that are not ferroelectric crystals, the quality can be improved.
- a gas component to be measured is selected from nitrogen monoxide, nonanal, acetaldehyde, and acetone. Two or more types. According to the present embodiment, the concentration of these gas components can be measured in an infrared absorption region of approximately 1600 to 1800 cm ⁇ 1 .
- gas components to be measured are ethane, nonanal, acetaldehyde, methylamine, methanol, acetone, And two or more of methane.
- concentration of these gas components can be measured in an infrared absorption region of approximately 2800 to 3000 cm ⁇ 1 .
- the gas to be measured is exhaled. According to the present embodiment, it is possible to provide an exhalation analyzer that measures a plurality of gas components contained in exhaled breath.
- the gas to be measured is a living gas such as breath, skin gas or rectal gas, and is detected. From the concentration of the gas component, bronchial asthma, lung cancer, lung disease, renal failure, pneumonia, H. pylori, diabetes, obesity, or gastrointestinal failure is discriminated. According to the present embodiment, since the gas component capable of discriminating these pathologies has the characteristic absorption band in the mid-infrared absorption region, these pathologies can be discriminated.
- the gas analysis method at least a first gas component and a second gas component are measured as gas components, and the first wavelength component corresponding to the first gas component is measured.
- the measurement integration time is different. According to the present embodiment, it is possible to set the measurement integration time corresponding to the difference in the lower detection limit necessary for pathological diagnosis, and the measurement integration time considering the absorption intensity due to the difference in the absorption region of the gas component and Therefore, the concentration measurement of each gas component can be performed reliably.
- the gas to be measured is exhaled. According to the present embodiment, it is possible to measure a plurality of gas components contained in exhaled breath.
- FIG. 1 is a diagram showing an overall outline of a gas analyzer.
- the gas analyzer 10 includes a light source 20 that selects and emits mid-infrared light having an arbitrary wavelength, a cell 30 that accommodates exhaled air to be analyzed and receives mid-infrared light from the light source 20, and a cell 30.
- the control means 60 may control both the emission time of the light source 20 and the detection time of the detector 40 corresponding to the measurement integration time.
- the light source 20 emits mid-infrared light having a wavelength corresponding to the absorption spectrum of the gas component to be measured.
- the measurement time setting means 50 sets the measurement integration time of mid-infrared light having a wavelength corresponding to each gas component to be measured.
- the control means 60 according to the set measurement integration time, at least one of the emission time of the mid-infrared light emitted from the light source 20 or the detection time of the detector 40 is made different according to each wavelength.
- the gas analyzer 10 uses two or more kinds of gas components contained in the exhaled breath contained in the cell 30 as a measurement target, and outputs mid-infrared light having a wavelength tuned to an absorption spectrum of the gas component to be measured as a light source 20. From the light intensity detected by the detector 40, the concentration measuring means 70 determines the concentration of the gas component.
- FIG. 2 is a diagram showing the configuration of the light source of the gas analyzer according to this embodiment.
- the light source 20 uses a first laser that emits the first laser light as the first light source 21 and a second laser light having a wavelength different from that of the first laser light as the second light source 22.
- a second laser to be emitted and a wavelength conversion device 23 are provided.
- the first laser light is incident on the wavelength conversion device 23 via the mirror 24A and the lens 25A
- the second laser light is incident on the wavelength conversion device 23 via the mirror 24B and the lens 25A.
- the two laser beams incident on the wavelength conversion device 23 are converted into light (difference frequency) corresponding to the difference between the frequencies, and the mid-infrared light generated by the conversion is output to the cell 30 through the lens 26A and the filter 27.
- a distributed feedback semiconductor laser (DFB laser) of continuous wave oscillation operation (CW operation) is used for the first light source (first laser) 21 and the second light source (second laser) 22.
- the DFB laser has been developed as a light source having a narrow line spectrum in the near-infrared region of about 1 ⁇ m to 1.7 ⁇ m and capable of freely selecting an oscillation wavelength.
- the gas analyzer 10 is downsized by configuring the light source 20 using a small semiconductor laser, the gas analyzer 10 can be made portable and used by being carried to various places. Is possible.
- the first light source (first laser) 21 and the second light source (second laser) 22 may be pulse-operated distributed feedback semiconductor lasers (DFB lasers).
- DFB lasers distributed feedback semiconductor lasers
- the efficiency of wavelength conversion can be increased due to its high peak power, and the power of the obtained mid-infrared light is increased accordingly, so a high S / N ratio (signal / Noise ratio) can be measured.
- the detection element of the MCT detector 41 described later can be made one by using a time difference for each pulse.
- the wavelength conversion device 23 uses AgGaS 2 crystal.
- AgGaS 2 crystals can be excited by a DFB laser, and ferroelectric crystals such as LiNbO 3 crystals are opaque in the mid-infrared region of 5 ⁇ m (2000 cm ⁇ 1 ) or more, whereas wavelengths longer than 5 ⁇ m ( ⁇ 13 ⁇ m).
- the first laser 21 is a laser that emits a single wavelength. In this embodiment, the first laser 21 emits a laser beam having a wavelength of 1064 nm.
- the second laser 22 is an array and is a wavelength tunable laser that can emit laser light having a plurality of wavelengths.
- the wavelength of the second laser light emitted from the second laser 22 is changed by switching the elements inside the second laser 22 by a signal from the control unit 60, and the medium red having a different wavelength from the wavelength conversion device 23 is changed. External light (converted light) can be output.
- the second laser 22 has four elements therein so that laser beams having wavelengths of 1325 nm, 1307 nm, 1308 nm, and 1305 nm can be emitted.
- the light source 20 does not use the difference frequency generation as in the present embodiment, but may be configured using, for example, a quantum cascade laser, and a plurality or a single infrared laser diode (infrared LD) is used. It is good also as the structure which was.
- FIG. 3 is a diagram showing the configuration of the cell and the detector of the gas analyzer according to this embodiment.
- a multipath cell 31 is used as the cell 30 according to this embodiment.
- the multipath cell 31 includes an introduction port 33 for introducing exhalation into the multipass cell 31 and an exhaust port 32 for discharging the exhalation from the multipath cell 31.
- the multipath cell 31 is preferably an astigmatism Herriot type multipath cell that can ensure a long optical path length with respect to the cell capacity. By employing an astigmatism Herriot type multi-pass cell, a long optical path length ( ⁇ 210 m) can be obtained, and the sampling amount of breath can be suppressed.
- the multipath cell 31 is not limited to the Herriot type multipath cell, and may be a multipath cell 31 of another type.
- the detector 40 according to the present embodiment includes an MCT detector 41 having sensitivity in the mid-infrared region, a mirror 42, and a beam splitter 43.
- the mid-infrared light output from the wavelength conversion device 23 is a beam.
- One of the mid-infrared light is divided by the splitter 43 and enters the MCT detector 41 through the multi-pass cell 31, and the other mid-infrared light enters the MCT detector 41 through the mirror 42.
- the detector 40 is good also as a structure which can provide a wavelength selection filter and can measure only a specific wavelength.
- the infrared absorption region of the four gas components are distributed from 1600 cm -1 to 1800 cm -1 vicinity, for example, if the nitrogen monoxide (NO) 5.40 ⁇ m (1852cm - any infrared light in a 1), mid-infrared light of 5.72 ⁇ m (1748cm -1) if nonanal, infrared light in a long acetaldehyde 5.70 ⁇ m (1754cm -1), in acetone
- the concentration of each component can be measured by using mid-infrared light of 5.76 ⁇ m (1736 cm ⁇ 1 ).
- FIG. 5 is a diagram showing the emission time of mid-infrared light corresponding to each gas component of the gas analyzer according to the present embodiment.
- the measurement time setting means 50 uses ⁇ seconds for nitric oxide (NO).
- NO nitric oxide
- the emission time is set to ⁇ seconds for nonanal, ⁇ seconds for acetaldehyde, and ⁇ seconds for acetone.
- the angle of the AgGaS 2 crystal of the wavelength conversion device 23 is ⁇ 48.9 deg.
- the first laser 21 emits a first laser beam having a wavelength of 1064 nm
- the second laser 22 emits a second laser beam having a wavelength of 1325 nm.
- the wavelength conversion device 23 generates mid-infrared light having a converted wavelength of 5.40 ⁇ m (1852 cm ⁇ 1 ).
- the generated mid-infrared light having a wavelength of 5.40 ⁇ m is divided by the beam splitter 43, and one mid-infrared light is incident on the MCT detector 41 through the multipass cell 31 into which exhalation is introduced, and the other mid-red light. External light enters the MCT detector 41 via the mirror 42.
- the concentration measuring means 70 determines the concentration of nitric oxide (NO) from the light intensity detected by the MCT detector 41.
- the light source 20 determines the concentration of the nonanal based on a command from the control unit 60 in order to measure the concentration of nonanal.
- the angle of the AgGaS 2 crystal is ⁇ 47.4 deg.
- the wavelength of the laser light emitted from the second laser 22 is switched to 1307 nm.
- the wavelength conversion device 23 generates mid-infrared light having a converted wavelength of 5.72 ⁇ m (1748 cm ⁇ 1 ).
- the generated mid-infrared light having a wavelength of 5.72 ⁇ m is separated by the beam splitter 43, and one mid-infrared light is incident on the MCT detector 41 through the multipath cell 31 into which exhalation is introduced, and the other mid-red light. External light enters the MCT detector 41 via the mirror 42.
- the concentration measurement means 70 obtains the concentration of nonanal from the light intensity detected by the MCT detector 41.
- the measurement integration time set for nonanal reaches ⁇ seconds
- the light source 20 measures the angle of the AgGaS 2 crystal of the wavelength conversion device 23 based on a command from the control unit 60 in order to measure the concentration of acetaldehyde. ⁇ 47.5 deg.
- the wavelength conversion device 23 generates mid-infrared light having a converted wavelength of 5.70 ⁇ m (1754 cm ⁇ 1 ).
- the generated mid-infrared light having a wavelength of 5.70 ⁇ m is divided by the beam splitter 43, one of the mid-infrared light is incident on the MCT detector 41 through the multipass cell 31 into which exhalation has been introduced, and the other mid-red light. External light enters the MCT detector 41 via the mirror 42.
- the concentration measuring means 70 determines the concentration of acetaldehyde from the light intensity detected by the MCT detector 41.
- the light source 20 When the measurement integration time ⁇ seconds set for acetaldehyde is reached, the light source 20 then measures the angle of the AgGaS 2 crystal of the wavelength conversion device 23 based on a command from the control unit 60 in order to measure the concentration of acetone. ⁇ 47.3 deg. And the wavelength of the laser light emitted from the second laser 22 is switched to 1305 nm. Then, the wavelength conversion device 23 generates mid-infrared light having a converted wavelength of 5.76 ⁇ m (1736 cm ⁇ 1 ).
- the generated mid-infrared light having a wavelength of 5.76 ⁇ m is divided by the beam splitter 43, and one mid-infrared light is incident on the MCT detector 41 through the multipath cell 31 into which exhalation is introduced, and the other mid-red light. External light enters the MCT detector 41 via the mirror 42. Then, the concentration measuring means 70 determines the concentration of acetone from the light intensity detected by the MCT detector 41. When the measurement integration time ⁇ seconds set for acetone is reached, the light source 20 stops emitting infrared light from the first laser 21 and the second laser 22 based on a command from the control unit 60.
- the exhaust port 32 is opened and the exhaled air introduced into the multipass cell 31 is discharged.
- the detector 40 detects mid-infrared light after the start of measurement of each gas component or before the end of measurement, such as after switching from measurement of nitric oxide (NO) to nonanal or before switching from measurement of acetaldehyde to acetone. You may control by the control means 60 so that the time slot
- the emission time of the mid infrared light is different for each gas component as shown in FIG. 5, but the emission time of the mid infrared light is the same even if the gas component to be measured is changed.
- the measurement integration time may be adjusted by changing the detection time at the detector 40 by controlling the incident time of the mid-infrared light to the detector 40 with a shutter.
- nitric oxide (NO), nonanal, acetaldehyde, and acetone are simultaneously measured.
- ethane, nonanal, acetaldehyde, methylamine, methanol, acetone, and methane are described.
- Two or more of (CH 4 ) can be the target of simultaneous measurement.
- the infrared absorption region of these gas components is distributed from 2800 cm -1 in the vicinity 3000 cm -1, by utilizing the infrared light in the wavelength in this range, the components Concentration can be measured.
- FIG. 6 is a diagram showing a result of measuring methane (CH 4) using a gas analyzer according to the present embodiment.
- the concentration of methane (CH 4 ) is 4.96 ppm
- the pressure in the multipass cell 31 is 760 torr
- the optical path length of the multipass cell 31 is 76 m
- the measurement increment is 0.014 cm ⁇ 1 .
- the white circle ( ⁇ ) shows the measurement result
- the solid line shows the absorption spectrum calculated based on the HITRAN 2008 database. It can be seen that the two data are almost in the vicinity of the wavelength of 3.39 ⁇ m (2948 cm ⁇ 1 ). .
- the gas component at least the first gas component and the second gas component are measured, the first wavelength corresponding to the first gas component, and the second gas component are corresponded.
- the measurement integration time corresponding to the difference in detection lower limit required for pathological diagnosis by using the second wavelength and making the measurement integration time by the first wavelength different from the measurement integration time by the second wavelength.
- gas components capable of discriminating these pathologies for bronchial asthma, lung cancer, lung disease, renal failure, pneumonia, H. pylori, diabetes, obesity, or gastrointestinal failure are characteristic in the mid-infrared absorption region. Since it has an absorption band, these pathologies can be distinguished.
- the breath analysis apparatus using breath for the biological gas has been described as the gas analysis apparatus.
- the present invention uses a biological gas such as skin gas, rectal gas (radiation), or gas that is discharged from the affected area of an operation. It can also be used for gas analyzers and can diagnose diseases, drugs, doping, virus infections, and the like.
- the present invention can be used outside the medical field.
- an agricultural product gas analyzer that uses gas from plants
- it can be used for disease diagnosis, grasping of the growth state, identification of the production area, or determination of the presence or absence of use of agricultural chemicals.
- It can be used for disease diagnosis as an animal gas analyzer that uses the gas that comes out, and in food management, it can be used as a food gas analyzer that uses the gas that comes from food to determine the place of production or to understand the fermentation maturation state of fermented food
- the victim's breath gas analyzer uses the victim's breath gas as a marker, and can be used to find survivors buried in rubble, etc.
- an indoor airborne gas analyzer it can be used for allergen detection. It can be used for monitoring of exhaust gas from cars and factories.
- the present invention can be used in an apparatus and method for efficiently measuring a plurality of types of gas components in a gas to be measured using mid-infrared light having a plurality of wavelengths.
- the apparatus or method according to the present invention by monitoring the gas component in the biological gas using the apparatus or method according to the present invention, it can be developed as a health care for diagnosing the health condition of a person, which leads to prevention medical care and medical cost control. It becomes possible.
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Abstract
Description
生体ガス中の微量成分を簡易的かつ迅速に計測する手法の一つとして、中赤外レーザーを利用した吸収分光法がある。これは疾患由来の既知の生体ガス成分を検出するために、その成分の吸収スペクトルに波長同調させた狭帯域中赤外レーザーを光源とし、吸収分光計測により成分濃度を定量する手法である。例えば、喘息と他の慢性的な咳とを区別できる生体ガス中の一酸化窒素(NO)は、波長5.27μm(1898cm-1)の量子カスケードレーザーを用いて定量計測することができ、1ppb程度の検出下限が実現されている。また、肺がん由来のアセトアルデヒドは、5.79μm(1727cm-1)の量子カスケードレーザーを利用して80ppb程度の検出下限で計測できる。
疾病由来のガス成分とその赤外吸収領域を図4に示す。生体生産物として重要なアルデヒド、ケトン、カルボン酸、およびアミドなどの官能基の特性吸収帯は1600~1800cm-1近傍に集中しており、また、分子の指紋領域とも呼ばれる800~1400cm-1近傍の領域には分子固有の特徴的な吸収スペクトルが多く分布している。
現在、スペクトル幅が狭帯域化された中赤外レーザーの実効的な波長可変領域は数cm-1と非常に狭く、複数ガスの同時計測が困難となっている。そこで、狭線スペクトルで、かつ中赤外領域において広い波長可変領域を有する光源を利用した、ガス中に含まれる複数ガス成分分析装置の開発が期待されている。
特許文献1には、近赤外ポンプ光と、第1のガス媒質を検出するための半導体レーザーからの近赤外シグナル光とを結合した合波光をPPLN結晶に入射させて、第2のガス媒質を検出するための近赤外または中赤外の差周波光を発生し、試料ガスが封入されたマルチパスセルを通過したシグナル光、差周波光およびポンプ光の合波光から、シグナル光および差周波光のみを同一光軸上に分離した後、このシグナル光および差周波光をMCT検出器に入射させて同時に検出し、MCT検出器からの電気信号に基づいて第1のガス媒質および第2のガス媒質の濃度を解析する方法が提案されている。
請求項2記載の本発明は、請求項1に記載のガス分析装置において、前記光源は、第1の赤外光を出射する第1の光源と、前記第1の赤外光とは異なる波長の第2の赤外光を出射する第2の光源と、前記第1の赤外光と前記第2の赤外光との差周波を出力する波長変換デバイスとからなることを特徴とする。
請求項3記載の本発明は、請求項2記載のガス分析装置において、前記第1の光源を、単一波長のレーザー光を出射するレーザーとし、前記第2の光源を、異なる波長のレーザー光を出射するアレイ化したレーザーとしたことを特徴とする。
請求項4記載の本発明は、請求項2又は請求項3に記載のガス分析装置において、前記波長変換デバイスとして、強誘電体結晶ではない非線形光学結晶を用いたことを特徴とする。
請求項5記載の本発明は、請求項4に記載のガス分析装置において、前記非線形光学結晶を、AgGaS2結晶としたことを特徴とする。
請求項6記載の本発明は、請求項1から請求項5のいずれかに記載のガス分析装置において、測定対象とする前記ガス成分を、一酸化窒素、ノナナール、アセトアルデヒド、およびアセトンのうちの二種以上としたことを特徴とする。
請求項7記載の本発明は、請求項1から請求項5のいずれかに記載のガス分析装置において、測定対象とする前記ガス成分を、エタン、ノナナール、アセトアルデヒド、メチルアミン、メタノール、アセトン、およびメタンのうちの二種以上としたことを特徴とする。
請求項8記載の本発明は、請求項1から請求項7のいずれかに記載のガス分析装置において、測定対象とする前記ガスを、呼気としたことを特徴とする。
請求項9記載の本発明は、請求項1から請求項7のいずれかに記載のガス分析装置において、測定対象とする前記ガスを、呼気、皮膚ガス又は直腸ガス等の生体ガスとし、検出される前記ガス成分の濃度から、気管支喘息、肺癌、肺疾患、腎不全、肺炎、ピロリ菌、糖尿病、肥満、又は胃腸不全を判別することを特徴とする。
請求項10記載の本発明のガス分析方法は、ガス成分の吸収スペクトルに同調させた中赤外領域の波長の光強度を用いて、測定対象とするガス中の前記ガス成分の濃度を求めるガス分析方法であって、前記ガス成分として、少なくとも第1のガス成分と第2のガス成分を測定対象とし、前記第1のガス成分に対応する第1の波長の中赤外光と、前記第2のガス成分に対応する第2の波長の中赤外光とを用い、前記第1の波長の前記中赤外光による測定積算時間と前記第2の波長の前記中赤外光による測定積算時間とを異ならせたことを特徴とする。
請求項11記載の本発明は、請求項10に記載のガス分析方法において、測定対象とする前記ガスを、呼気としたことを特徴とする。
図1は、ガス分析装置の全体概要を示す図である。
ガス分析装置10は、任意の波長の中赤外光を選択して出射する光源20と、分析対象とする呼気を収容して光源20からの中赤外光を入射するセル30と、セル30内を透過した中赤外光を検出する検出器40と、中赤外光の測定積算時間を設定する測定時間設定手段50と、測定積算時間に対応して光源20の出射時間又は検出器40の検出時間の一方を制御する制御手段60と、検出器40で検出した光強度からガス成分の濃度を求める濃度計測手段70とを備えている。なお、制御手段60は、測定積算時間に対応して光源20の出射時間と検出器40の検出時間の両方を制御するものとしても良い。
光源20では、測定対象とするガス成分の吸収スペクトルに対応する波長の中赤外光を出射する。測定時間設定手段50では、測定対象とするそれぞれのガス成分に対応する波長の中赤外光の測定積算時間を設定する。制御手段60では、設定された測定積算時間に従って、光源20から出射する中赤外光の出射時間又は検出器40の検出時間の少なくとも一方をそれぞれの波長に応じて異ならせる。
ガス分析装置10は、セル30に収容された呼気中に含まれる二種以上のガス成分を測定対象とし、測定対象とするガス成分の吸収スペクトルに同調させた波長の中赤外光を光源20からセル30内に出射し、検出器40で検出した光強度から濃度計測手段70においてガス成分の濃度を求める。
本実施例による光源20は、第1の光源21として第1のレーザー光を出射する第1のレーザーと、第2の光源22として第1のレーザー光とは異なる波長の第2のレーザー光を出射する第2のレーザーと、波長変換デバイス23を有している。第1のレーザー光は、ミラー24Aとレンズ25Aを介して波長変換デバイス23に入射し、第2のレーザー光はミラー24Bとレンズ25Aを介して波長変換デバイス23に入射する。波長変換デバイス23に入射した二つのレーザー光は、その周波数の差に相当する光(差周波)に変換され、変換により生じた中赤外光はレンズ26Aおよびフィルター27を介してセル30へ出力される。
ここで、第1の光源(第1のレーザー)21および第2の光源(第2のレーザー)22には、連続波発振動作(CW動作)の分布帰還型半導体レーザー(DFBレーザー)を用いている。DFBレーザーは、およそ1μm~1.7μmの近赤外領域で狭線スペクトルを有し、かつ発振波長が自由に選択可能な光源が開発されている。さらに、小型の半導体レーザーを用いて光源20を構成することによってガス分析装置10が小型化されるので、ガス分析装置10を可搬型とすることができ、様々な場所へ携帯して使用することが可能となる。
なお、第1の光源(第1のレーザー)21および第2の光源(第2のレーザー)22には、パルス動作型の分布帰還型半導体レーザー(DFBレーザー)を用いてもよい。パルス動作型のDFBレーザーを用いることで、その高いピークパワーにより波長変換の効率を上げることができ、それに伴い、得られる中赤外光のパワーも高くなるため、高いS/N比(シグナル/ノイズ比)で計測が可能になる。また、パルス動作にした場合、パルス毎の時間差を利用することで、後述するMCT検出器41の検出素子を1つにすることができる。
また、波長変換デバイス23には、AgGaS2結晶を用いている。AgGaS2結晶はDFBレーザーにより励起が可能であり、LiNbO3結晶などの強誘電体結晶が5μm(2000cm-1)以上の中赤外領域では不透明であるのに対し、5μmよりも長波長(~13μm)の光透過領域を有する。
第1のレーザー21は単一波長を出射するレーザーであり、本実施例においては、1064nmの波長のレーザー光を出射する。第2のレーザー22はアレイ化されており、複数の波長のレーザー光を出射することができる波長可変型レーザーである。従って、制御部60からの信号により第2のレーザー22内部の素子を切り替えることによって、第2のレーザー22から出射する第2のレーザー光の波長を変え、波長変換デバイス23から波長の異なる中赤外光(変換光)を出力させることができる。本実施例においては、第2のレーザー22は、1325nm、1307nm、1308nm、および1305nmの波長のレーザー光を出射することができるように四つの素子を内部に有している。
なお、光源20は本実施例のように差周波発生を利用するものでなくとも、例えば、量子カスケードレーザーを用いた構成としても良く、複数又は単体の赤外レーザーダイオード(赤外LD)を用いた構成としても良い。
本実施例によるセル30には、マルチパスセル31を用いる。マルチパスセル31は、呼気をマルチパスセル31内に導入するための導入口33と、マルチパスセル31から呼気を排出するための排気口32を備えている。
ここで、マルチパスセル31には、セル容量に対して光路長を長く確保できる非点収差Herriot式マルチパスセルを用いることが好ましい。非点収差Herriot式マルチパスセルを採用することで、長い光路長(~210m)が得られ、呼気のサンプリング量を抑えることが可能となる。ただし、Herriot式マルチパスセルに限定されるものではなく、他方式のマルチパスセル31としても良い。
また、本実施例による検出器40は、中赤外領域に感度を有するMCT検出器41と、ミラー42と、ビームスプリッタ43とからなり、波長変換デバイス23から出力された中赤外光はビームスプリッタ43で分けられ、一方の中赤外光はマルチパスセル31を通ってMCT検出器41に入射し、他方の中赤外光はミラー42を介してMCT検出器41に入射する。
なお、検出器40は、波長選択フィルターを設け、特定の波長のみを計測できる構成としても良い。
図4に示すように、上記四つのガス成分の赤外吸収領域は、1600cm-1から1800cm-1近傍に分布しており、例えば、一酸化窒素(NO)であれば5.40μm(1852cm-1)の中赤外光を、ノナナールであれば5.72μm(1748cm-1)の中赤外光を、アセトアルデヒドであれば5.70μm(1754cm-1)の中赤外光を、アセトンであれば5.76μm(1736cm-1)の中赤外光を利用することで、各成分の濃度を計測することができる。
また、図5は、本実施例によるガス分析装置の各ガス成分に対応する中赤外光の出射時間を示す図であり、測定時間設定手段50で、一酸化窒素(NO)にはα秒、ノナナールにはβ秒、アセトアルデヒドにはγ秒、アセトンにはζ秒の出射時間を設定している。
測定が開始されると、まず一酸化窒素(NO)の濃度を測定するために、制御部60からの指令に基づいて、波長変換デバイス23のAgGaS2結晶の角度は~48.9deg.に調整され、第1のレーザー21からは波長1064nmの第1のレーザー光が、第2のレーザー22からは波長1325nmの第2のレーザー光が出射される。すると、波長変換デバイス23では変換された波長5.40μm(1852cm-1)の中赤外光が発生する。発生した波長5.40μmの中赤外光はビームスプリッタ43で分けられ、一方の中赤外光は呼気が導入されたマルチパスセル31を通ってMCT検出器41に入射し、他方の中赤外光はミラー42を介してMCT検出器41に入射する。そして、MCT検出器41で検出した光強度から濃度計測手段70において一酸化窒素(NO)の濃度が求められる。
一酸化窒素(NO)に対して設定された測定積算時間α秒に達すると、次にノナナールの濃度を測定するために、光源20は制御部60からの指令に基づいて、波長変換デバイス23のAgGaS2結晶の角度を~47.4deg.に変化させるとともに、第2のレーザー22から出射するレーザー光の波長を1307nmに切り替える。すると、波長変換デバイス23では変換された波長5.72μm(1748cm-1)の中赤外光が発生する。発生した波長5.72μmの中赤外光はビームスプリッタ43で分けられ、一方の中赤外光は呼気が導入されたマルチパスセル31を通ってMCT検出器41に入射し、他方の中赤外光はミラー42を介してMCT検出器41に入射する。そして、MCT検出器41で検出した光強度から濃度計測手段70においてノナナールの濃度が求められる。
ノナナールに対して設定された測定積算時間β秒に達すると、次にアセトアルデヒドの濃度を測定するために、光源20は制御部60からの指令に基づいて、波長変換デバイス23のAgGaS2結晶の角度を~47.5deg.に変化させるとともに、第2のレーザー22から出射するレーザー光の波長を1308nmに切り替える。すると、波長変換デバイス23では変換された波長5.70μm(1754cm-1)の中赤外光が発生する。発生した波長5.70μmの中赤外光はビームスプリッタ43で分けられ、一方の中赤外光は呼気が導入されたマルチパスセル31を通ってMCT検出器41に入射し、他方の中赤外光はミラー42を介してMCT検出器41に入射する。そして、MCT検出器41で検出した光強度から濃度計測手段70においてアセトアルデヒドの濃度が求められる。
アセトアルデヒドに対して設定された測定積算時間γ秒に達すると、次にアセトンの濃度を測定するために、光源20は制御部60からの指令に基づいて、波長変換デバイス23のAgGaS2結晶の角度を~47.3deg.に変化させるとともに、第2のレーザー22から出射するレーザー光の波長を1305nmに切り替える。すると、波長変換デバイス23では変換された波長5.76μm(1736cm-1)の中赤外光が発生する。発生した波長5.76μmの中赤外光はビームスプリッタ43で分けられ、一方の中赤外光は呼気が導入されたマルチパスセル31を通ってMCT検出器41に入射し、他方の中赤外光はミラー42を介してMCT検出器41に入射する。そして、MCT検出器41で検出した光強度から濃度計測手段70においてアセトンの濃度が求められる。アセトンに対して設定された測定積算時間ζ秒に達すると光源20は制御部60からの指令に基づいて、第1のレーザー21および第2のレーザー22からの赤外光の出射を止める。
以上のようにして計測対象ガス成分について全ての計測を終了した後、排気口32を開放してマルチパスセル31内に導入した呼気を排出させる。
なお、一酸化窒素(NO)からノナナールの測定に切り替えた後や、アセトアルデヒドからアセトンに測定を切り替える前など各ガス成分の測定開始後又は測定終了前に、検出器40が中赤外光を検出しない時間帯を設けるように制御手段60で制御しても良い。
メタン(CH4)の濃度は4.96ppm、マルチパスセル31内の圧力は760torr、マルチパスセル31の光路長は76m、測定刻みは0.014cm-1である。
白丸(○)は測定結果を、実線はHITRAN2008データベースをもとに算出した吸収スペクトルを示しており、波長3.39μm(2948cm-1)近傍において、両者のデータはほぼ一致していることが分かる。
20 光源
21 第1の光源(第1のレーザー)
22 第2の光源(第2のレーザー)
23 波長変換デバイス
24A ミラー
24B ミラー
25A レンズ
26A レンズ
27 フィルター
30 セル
31 マルチパスセル
32 排気口
33 導入口
40 検出器
41 MCT検出器
42 ミラー
43 ビームスプリッタ
50 測定時間設定手段
60 制御手段
70 濃度計測手段
Claims (11)
- 測定対象とするガスを収容するセルと、
任意の波長の中赤外光を選択して前記セル内に出射する光源と、
前記セル内を透過した前記中赤外光を検出する検出器とを備え、
前記ガスに含まれる二種以上のガス成分を測定対象とし、測定対象とする前記ガス成分の吸収スペクトルに同調させた波長の中赤外光を前記光源から出射し、前記検出器で検出した光強度から前記ガス成分の濃度を求めるガス分析装置であって、
測定対象とするそれぞれの前記ガス成分に対する前記波長の前記中赤外光の測定積算時間を設定する測定時間設定手段と、
前記測定積算時間に対応して前記光源の出射時間又は前記検出器の検出時間の少なくとも一方を制御する制御手段とを有することを特徴とするガス分析装置。 - 前記光源は、第1の赤外光を出射する第1の光源と、前記第1の赤外光とは異なる波長の第2の赤外光を出射する第2の光源と、前記第1の赤外光と前記第2の赤外光との差周波を出力する波長変換デバイスとからなることを特徴とする請求項1に記載のガス分析装置。
- 前記第1の光源を、単一波長のレーザー光を出射するレーザーとし、前記第2の光源を、異なる波長のレーザー光を出射するアレイ化したレーザーとしたことを特徴とする請求項2に記載のガス分析装置。
- 前記波長変換デバイスとして、強誘電体結晶ではない非線形光学結晶を用いたことを特徴とする請求項2又は請求項3に記載のガス分析装置。
- 前記非線形光学結晶を、AgGaS2結晶としたことを特徴とする請求項4に記載のガス分析装置。
- 測定対象とする前記ガス成分を、一酸化窒素、ノナナール、アセトアルデヒド、およびアセトンのうちの二種以上としたことを特徴とする請求項1から請求項5のいずれかに記載のガス分析装置。
- 測定対象とする前記ガス成分を、エタン、ノナナール、アセトアルデヒド、メチルアミン、メタノール、アセトン、およびメタンのうちの二種以上としたことを特徴とする請求項1から請求項5のいずれかに記載のガス分析装置。
- 測定対象とする前記ガスを、呼気としたことを特徴とする請求項1から請求項7のいずれかに記載のガス分析装置。
- 測定対象とする前記ガスを、呼気、皮膚ガス又は直腸ガス等の生体ガスとし、検出される前記ガス成分の前記濃度から、気管支喘息、肺癌、肺疾患、腎不全、肺炎、ピロリ菌、糖尿病、肥満、又は胃腸不全を判別することを特徴とする請求項1から請求項7のいずれかに記載のガス分析装置。
- ガス成分の吸収スペクトルに同調させた中赤外領域の波長の光強度を用いて、測定対象とするガス中の前記ガス成分の濃度を計測するガス分析方法であって、
前記ガス成分として、少なくとも第1のガス成分と第2のガス成分を測定対象とし、
前記第1のガス成分に対応する第1の波長の中赤外光と、前記第2のガス成分に対応する第2の波長の中赤外光とを用い、
前記第1の波長の前記中赤外光による測定積算時間と前記第2の波長の前記中赤外光による測定積算時間とを異ならせたことを特徴とするガス分析方法。 - 測定対象とする前記ガスを、呼気としたことを特徴とする請求項10に記載のガス分析方法。
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