WO2015125328A1 - Dispositif de diagnostic d'air expiré - Google Patents

Dispositif de diagnostic d'air expiré Download PDF

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Publication number
WO2015125328A1
WO2015125328A1 PCT/JP2014/074522 JP2014074522W WO2015125328A1 WO 2015125328 A1 WO2015125328 A1 WO 2015125328A1 JP 2014074522 W JP2014074522 W JP 2014074522W WO 2015125328 A1 WO2015125328 A1 WO 2015125328A1
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WIPO (PCT)
Prior art keywords
diagnostic apparatus
breath
intermediate portion
unit
sample gas
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PCT/JP2014/074522
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English (en)
Japanese (ja)
Inventor
茂行 高木
康友 塩見
努 角野
陽 前川
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株式会社 東芝
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Publication of WO2015125328A1 publication Critical patent/WO2015125328A1/fr

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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
    • 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
    • A61B5/082—Evaluation by breath analysis, e.g. determination of the chemical composition of exhaled breath
    • 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
    • G—PHYSICS
    • G01—MEASURING; TESTING
    • G01N—INVESTIGATING OR ANALYSING MATERIALS BY DETERMINING THEIR CHEMICAL OR PHYSICAL PROPERTIES
    • 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
    • G—PHYSICS
    • G01—MEASURING; TESTING
    • G01N—INVESTIGATING OR ANALYSING MATERIALS BY DETERMINING THEIR CHEMICAL OR PHYSICAL PROPERTIES
    • G01N1/00—Sampling; Preparing specimens for investigation
    • G01N1/02—Devices for withdrawing samples
    • G01N1/22—Devices for withdrawing samples in the gaseous state
    • G01N2001/2244—Exhaled gas, e.g. alcohol detecting
    • G—PHYSICS
    • G01—MEASURING; TESTING
    • G01N—INVESTIGATING OR ANALYSING MATERIALS BY DETERMINING THEIR CHEMICAL OR PHYSICAL PROPERTIES
    • G01N21/00—Investigating or analysing materials by the use of optical means, i.e. using sub-millimetre waves, infrared, visible or ultraviolet light
    • G01N21/01—Arrangements or apparatus for facilitating the optical investigation
    • G01N21/03—Cuvette constructions
    • G01N21/031—Multipass arrangements

Definitions

  • Embodiments of the present invention relate to a breath diagnostic device.
  • the gas of breath is measured.
  • the measurement results facilitate disease prevention and early detection.
  • Embodiments of the present invention provide a high precision breath diagnostic device.
  • a breath diagnostic apparatus includes: a supply unit to which a sample gas containing breath is supplied; a cell unit including a space into which the sample gas is introduced from the supply unit; An introduction pipe provided between the cell unit and guiding the sample gas from the supply unit to the space, a light source unit for causing measurement light to enter the space, and a detection unit for detecting the measurement light having passed through the space ,including.
  • the introduction pipe includes an intermediate portion having a bend.
  • FIG. 2A to FIG. 2C are schematic views illustrating a part of the breath diagnostic apparatus according to the embodiment.
  • FIG. 3A and FIG. 3B are schematic views illustrating a part of the breath diagnostic apparatus according to the embodiment.
  • FIG. 4A and FIG. 4B are schematic views illustrating a part of the breath diagnostic apparatus according to the embodiment.
  • FIG. 5A to FIG. 5C are schematic views illustrating a part of the breath diagnostic apparatus according to the embodiment.
  • FIG. 1 is a schematic view illustrating a breath diagnostic apparatus according to the embodiment.
  • the breath diagnostic apparatus 110 includes a supply unit 10i, a cell unit 20, an introduction pipe 15a, a light source unit 30, and a detection unit 40.
  • a discharge unit 10 o and a discharge pipe 15 b are further provided.
  • the sample gas 50 is supplied to the supply unit 10i.
  • the sample gas 50 includes exhalation 50a.
  • the exhalation 50a is exhalation of an animal including, for example, a human.
  • the exhalation 50a contains a substance to be diagnosed. This substance is, for example, acetone.
  • acetone For example, when suffering from diabetes, the concentration of acetone in the exhaled breath 50a is increased as compared to when in health.
  • the breath diagnostic apparatus 110 the health condition is diagnosed by measuring the concentration of a substance (for example, acetone or the like). Examples of the substance will be described later.
  • the sample gas 50 including the breath 50a is blown from the subject into the supply unit 10i.
  • the cell unit 20 includes a space 23s.
  • the sample gas 50 is introduced into the space 23s from the supply unit 10i.
  • the cell unit 20 includes the cell 23.
  • a space 23s is formed in the cell 23.
  • An introduction pipe 15a is provided between the cell 23 (cell unit 20) and the supply unit 10i.
  • An inlet 20 i is provided in the cell unit 20.
  • the inlet pipe 15a is connected to the inlet 20i.
  • the introduction pipe 15a guides the sample gas 50 from the supply unit 10i to the space 23s.
  • the sample gas 50 supplied to the supply unit 10i is introduced into the space 23s via the introduction pipe 15a.
  • the exhaust unit 10 o is provided between the space 23 s and the atmosphere 10 x.
  • the atmosphere 10 x is outside the breath diagnostic apparatus 110.
  • the discharge pipe 15b is provided between the space 23s and the discharge part 10o.
  • the sample gas 50 in the space 23s of the cell unit 20 is introduced into the discharge unit 10o via the discharge pipe 15b.
  • the sample gas 50 is discharged to the atmosphere 10x by the discharge unit 10o.
  • the light source unit 30 causes the measurement light 30L to enter the space 23s.
  • the detection unit 40 detects the measurement light 30L that has passed through the space 23s.
  • the measurement light 30L is absorbed by a substance (for example, acetone or the like) contained in the breath 50a in the sample gas 50.
  • the absorption of the measurement light 30L changes according to the concentration of the substance.
  • the concentration of the target substance can be measured. A diagnosis is made based on this result.
  • the light source unit 30 includes a semiconductor light emitting element 30a and a drive unit 30b.
  • the driving unit 30 b is electrically connected to the semiconductor light emitting element 30 a.
  • the driving unit 30 b supplies power for light emission to the semiconductor light emitting element 30 a.
  • a quantum cascade laser QCL
  • An example of the semiconductor light emitting device 30a will be described later.
  • the measurement light 30L includes a wavelength absorbed by the substance contained in the breath 50a.
  • the measurement light 30L includes infrared light (infrared light).
  • the measurement light 30L is, for example, not less than 0.7 micrometers ( ⁇ m) and not more than 1000 ⁇ m.
  • the measurement light 30L may be, for example, 2.5 ⁇ m to 11 ⁇ m.
  • the cell unit 20 includes a first reflection unit 21 and a second reflection unit 22.
  • the first reflecting portion 21 and the second reflecting portion 22 are reflective to the measurement light 30L.
  • the sample gas 50 introduced from the supply unit 10i is introduced into the space 23s between the first reflection unit 21 and the second reflection unit 22. At least a part of the space 23 s is disposed between the first reflecting portion 21 and the second reflecting portion 22.
  • the measurement light 30L passes through, for example, the space 23s in a state where the sample gas 50 is introduced into the space 23s.
  • the measurement light 30L is reflected by the first reflecting portion 21 and the second reflecting portion 22, and reciprocates between the first reflecting portion 21 and the second reflecting portion 22 (space 23s) a plurality of times.
  • a part of the measurement light 30 L is absorbed by the substance contained in the sample gas 50.
  • the component of the wavelength specific to the substance in the measurement light 30L is absorbed. The degree of absorption depends on the concentration of the substance.
  • the detection unit 40 detects, for example, the measurement light 30L that has passed through the space 23s in a state where the sample gas 50 is introduced into the space 23s.
  • a photodiode or the like is used for the detection unit 40.
  • the detection unit 40 is optional.
  • a processing unit 45 is further provided.
  • the processing unit 45 processes the signal detected by the detection unit 40 and derives a desired result.
  • a housing 10 w is further provided.
  • the cell unit 20, the light source unit 30, the detection unit 40, the introduction pipe 15a, and the discharge pipe 15b are stored in the housing 10w.
  • the first optical component 36 a is provided between the light source unit 30 and the cell unit 20 on the light path of the measurement light 30 ⁇ / b> L.
  • a second optical component 36 b is provided between the cell unit 20 and the detection unit 40 on the optical path.
  • These optical components include, for example, focusing optics.
  • a filter may be used for these optical components.
  • An optical switch may be used for these optical components.
  • the optical components may be provided or omitted as necessary.
  • an intermediate portion 18 a is provided in the introduction pipe 15 a.
  • the middle portion 18 a has a bending portion 17.
  • a plurality of bending portions (a first bending portion 17a, a second bending portion 17b, a third bending portion 17c, and the like) are provided.
  • the intermediate portion 18a creates turbulent flow in the sample gas 50 guided to the intermediate portion 18a.
  • the sample gas 50 guided to the intermediate portion 18 a collides with the wall surface of the bending portion 17. By hitting the wall, turbulence is formed.
  • turbulent flow is formed, the number of times water molecules contained in the sample gas 50 contact the wall increases. Water molecules, for example, adhere to the wall surface. As a result, the amount of water contained in the sample gas 50 is reduced.
  • condensation may occur in the space 23s for measurement if the amount of water in the sample gas 50 including the exhalation 50a is large. For example, water particles adhere to at least one of the surface of the first reflecting portion 21 and the surface of the second reflecting portion 22.
  • the traveling direction of the measurement light 30L is not the desired direction. For example, the effective distance at which the measurement light 30L passes through the space changes. Because of this, measurement results become inaccurate.
  • a multilayer structure may be used for the first reflecting portion 21 and the second reflecting portion 22. This makes it easy to obtain a desired reflectance for the measurement light 30L of infrared light. It has been found that such multilayer structures are susceptible to degradation in high humidity. When the first reflecting portion 21 and the second reflecting portion 22 are degraded, the accuracy of the measurement result is degraded.
  • the intermediate portion 18 a including the bending portion 17 by providing the intermediate portion 18 a including the bending portion 17, the amount of water in the sample gas 50 can be reduced. This can improve the measurement accuracy.
  • the sample gas 50 may contain particles (for example, dust, pollen, etc.).
  • the particles are irradiated with the measurement light 30L. That is, the measurement light 30L is irradiated to particles which are not substances to be measured. As a result, correct measurement results may not be obtained.
  • the intermediate portion 18 a having the bending portion 17 by providing the intermediate portion 18 a having the bending portion 17, the amount of water contained in the sample gas 50 is reduced. Furthermore, the amount of particles can also be reduced. This enables more accurate measurement.
  • the change in the angle in the extension direction of the intermediate portion 18a in the bending portion 17 is 70 degrees or more. Due to the large angle in the extension direction, for example, the sample gas 50 easily collides with the wall surface of the intermediate portion 18a. For example, turbulent flow is likely to occur. Water and particle capture characteristics are improved.
  • a plurality of bending portions 17 may be provided. At this time, the change of the angle in the extension direction of the intermediate portion 18 a in each of at least two of the plurality of bending portions 17 is 70 degrees or more.
  • the introduction pipe 15 a further includes a connection portion 18 b.
  • the connection portion 18 b is provided between the intermediate portion 18 a and the cell portion 20 (space 23 s).
  • the connection 18b extends in a straight line.
  • the flow direction of the sample gas 50 flowing through the connection portion 18b is taken as the extending direction 18d.
  • the length of the connecting portion 18b along the extending direction 18d is equal to or greater than the length of the connecting portion 18b in the cross-sectional direction perpendicular to the extending direction 18d.
  • FIG. 2A to FIG. 2C are schematic views illustrating a part of the breath diagnostic apparatus according to the embodiment. These drawings illustrate the introduction pipe 15a.
  • the intermediate portion 18a is in a loop shape. The number of loops is arbitrary.
  • the intermediate portion 18a includes a plurality of asperities (convex portions 19p and concave portions 19d).
  • the plurality of irregularities are provided on the inner surface of the introduction pipe 15a.
  • the middle portion 18a includes a bellows.
  • a bellows can be used as the intermediate portion 18a.
  • the provision of the plurality of asperities improves, for example, the capture characteristics of water and / or particles.
  • a bellows as a pipe provided between the mouth of a subject and the supply unit 10i.
  • the subject is easy to use by deforming the pipe.
  • the intermediate portion 18a is not necessarily required to be deformed.
  • the removal characteristic of water or the like in the intermediate portion 18a is effectively exhibited.
  • the housing 10w defines the spatial arrangement between the inlet 20i of the cell unit 20 and the supply unit 10i. good. Even if this spatial arrangement is fixed, the removal characteristic of water or the like in the intermediate portion 18a is effectively exhibited.
  • the intermediate portion 18a has a zigzag shape due to the plurality of bending portions 17 (the first bending portion 17a, the second bending portion 17b, and the like). And, a plurality of irregularities are provided. Also in this case, it is possible to provide a breath diagnostic device with high accuracy.
  • the middle portion 18a may have a portion extending in the opposite direction to the direction of gravity. This portion extends in the opposite direction to the gravity, for example, along the direction from the supply unit 10i to the cell unit 20.
  • the particles contained in the sample gas 50 tend to stay in the lower part of the intermediate portion 18a, for example. Particles can be prevented from flowing into the space 23s.
  • water droplets generated on the wall surface of the intermediate portion 18a tend to stay in the lower portion of the intermediate portion 18a. Water can be prevented from flowing into the space 23s.
  • FIG. 3A and FIG. 3B are schematic views illustrating a part of the breath diagnostic apparatus according to the embodiment.
  • These drawings illustrate the introduction pipe 15a.
  • the introduction pipe 15a further includes a wall 19 in addition to the connection 18b.
  • the wall 19 is provided in the space in the connecting portion 18 b.
  • the wall-like body 19 extends in the extending direction of the connecting portion 18 b.
  • the wall-like body 19 is, for example, a straightening vane.
  • the cross-sectional shape of the wall-like body 19 may be, for example, a honeycomb shape.
  • the connection 18 b regulates the flow of the sample gas 50.
  • the cross-sectional area (thickness) of the connection portion 18b gradually increases along the direction from the intermediate portion 18a toward the cell portion 20 (introduction port 20i).
  • the cross-sectional area is the area of the connecting portion 18b when cut by a plane perpendicular to the flowing direction of the sample gas 50 flowing through the connecting portion 18b. Laminar flow can be easily generated also in such a connecting portion 18b. Also in this example, the connection 18 b regulates the flow of the sample gas 50.
  • FIG. 4A and FIG. 4B are schematic views illustrating a part of the breath diagnostic apparatus according to the embodiment.
  • These drawings illustrate the introduction pipe 15a.
  • the introductory piping 15a contains the adsorption part 17p.
  • the adsorption part 17p is provided inside the introduction pipe 15a.
  • the adsorption unit 17 p adsorbs at least a part of water contained in the sample gas 50. This further reduces the water in the sample gas 50 introduced into the space 23s.
  • the adsorption portion 17 p is provided, for example, on at least a part of the inner surface of the introduction pipe 15 a.
  • the suction portion 17 p may be provided in the bending portion 17.
  • At least one of silica gel and zeolite can be used for the adsorption unit 17p. By using these, water can be adsorbed effectively.
  • a control unit (such as a first control unit 17q and a second control unit 17r) is provided.
  • the first control unit 17 q and the second control unit 17 r can change the temperature of the intermediate unit 18 a.
  • the temperature of the intermediate unit 18a may be increased by the first control unit 17q.
  • the temperature of the intermediate portion 18a is increased until the measurement by the breath diagnostic apparatus 110 is completed and the other sample gases 50 are evaluated.
  • the water in the introductory piping 15a can be evaporated and easily discharged to the outside of the apparatus. For example, it becomes easy to remove the water adhering to the inner wall of the introductory piping 15a.
  • the cooling may be performed by the first control unit 17 q and the heating may be performed by the second control unit 17 r. It may heat by the 1st control part 17q, and may cool by the 2nd control part 17r.
  • the above-mentioned adsorption part 17p may be combined with the composition illustrated in Drawing 2 (a), Drawing 2 (b), Drawing 2 (c), Drawing 3 (a), and Drawing 3 (c).
  • the above control unit may be combined with the configuration illustrated in FIG. 2 (a), FIG. 2 (b), FIG. 2 (c), FIG. 3 (a) and FIG. 3 (c).
  • the substance is, for example, carbon dioxide isotope.
  • information on H. pylori can be obtained.
  • the substance is, for example, methane.
  • information on intestinal anaerobic bacteria can be obtained.
  • the substance is, for example, ethanol.
  • information on drinking can be obtained.
  • the substance is, for example, acetaldehyde.
  • information on drinking metabolites and lung cancer can be obtained.
  • the substance is, for example, acetone.
  • information on diabetes can be obtained.
  • the substance is, for example, nitric oxide.
  • information on asthma can be obtained.
  • the substance is, for example, ammonia.
  • information on hepatitis can be obtained.
  • the substance is, for example, nonanal.
  • information on lung cancer can be obtained.
  • the breath 50a contains at least one of carbon dioxide, methane, ethanol, acetaldehyde, acetone, carbon monoxide, ammonia and nonanal.
  • the substance to be measured contained in the breath 50a is optional.
  • FIG. 5A to FIG. 5C are schematic views illustrating a part of the breath diagnostic apparatus according to the embodiment.
  • FIG. 5A is a schematic perspective view.
  • FIG. 5 (b) is a cross-sectional view taken along line A1-A2 of FIG. 5 (a).
  • FIG. 5C is a schematic view illustrating the operation of the light source unit 30.
  • a semiconductor light emitting element 30 a is used as the light source unit 30.
  • a laser is used as the semiconductor light emitting element 30a.
  • a quantum cascade laser is used.
  • the semiconductor light emitting device 30a includes the substrate 35, the laminate 31, the first electrode 34a, the second electrode 34b, and the dielectric layer 32 (first dielectric layer). , And the insulating layer 33 (second dielectric layer).
  • a substrate 35 is provided between the first electrode 34 a and the second electrode 34 b.
  • the substrate 35 includes a first portion 35a, a second portion 35b, and a third portion 35c. These parts are arranged in one plane. This plane intersects (eg, is parallel to) the direction from the first electrode 34a to the second electrode 34b.
  • the third portion 35c is disposed between the first portion 35a and the second portion 35b.
  • the stacked body 31 is provided between the third portion 35c and the first electrode 34a.
  • a dielectric layer 32 is provided between the first portion 35a and the first electrode 34a and between the second portion 35b and the first electrode 34a.
  • An insulating layer 33 is provided between the dielectric layer 32 and the first electrode 34a.
  • the stacked body 31 has a stripe shape.
  • the stacked body 31 functions as a ridge waveguide RG.
  • the two end faces of the ridge waveguide RG become mirror surfaces.
  • the light 31L emitted from the laminate 31 is emitted from the end face (light emitting surface).
  • the light 31L is an infrared laser light.
  • the optical axis 31Lx of the light 31L is along the extending direction of the ridge waveguide RG.
  • the stacked body 31 includes, for example, a first cladding layer 31a, a first guide layer 31b, an active layer 31c, a second guide layer 31d, and a second cladding layer 31e. ,including. These layers are arranged in this order along the direction from the substrate 35 toward the first electrode 34a.
  • Each of the refractive index of the first cladding layer 31a and the refractive index of the second cladding layer 31e is determined by the refractive index of the first guide layer 31b, the refractive index of the active layer 31c, and the refractive index of the second guide layer 31d. Too low.
  • the light 31 L generated in the active layer 31 c is confined in the stack 31.
  • the first guide layer 31 b and the first cladding layer 31 a may be collectively referred to as a cladding layer.
  • the second guide layer 31d and the second cladding layer 31e may be collectively referred to as a cladding layer.
  • the stacked body 31 has a first side 31 sa and a second side 31 sb perpendicular to the optical axis 31 Lx.
  • the distance 31w (width) between the first side surface 31sa and the second side surface 31sb is, for example, 5 ⁇ m or more and 20 ⁇ m or less. Thereby, for example, control of the horizontal lateral mode is facilitated, and output improvement is facilitated. If the distance 31 w is excessively long, high-order modes are likely to occur in the horizontal transverse mode, and it is difficult to increase the output.
  • the refractive index of the dielectric layer 32 is lower than the refractive index of the active layer 31c.
  • the ridge waveguide RG is formed by the dielectric layer 32 along the optical axis 31Lx.
  • the active layer 31c has, for example, a cascade structure.
  • the cascade structure for example, the first regions r1 and the second regions r2 are alternately stacked.
  • the unit structure r3 includes a first region r1 and a second region r2. A plurality of unit structures r3 are provided.
  • first barrier layer BL1 and the first quantum well layer WL1 are provided in the first region r1.
  • the second barrier layer BL2 is provided in the second region.
  • the third barrier layer BL3 and the second quantum well layer WL2 are provided in another first region r1a.
  • a fourth barrier layer BL4 is provided in another second region r2a.
  • an intersubband optical transition of the first quantum well layer WL1 occurs in the first region r1, an intersubband optical transition of the first quantum well layer WL1 occurs. Thereby, for example, light 31La having a wavelength of 3 ⁇ m to 18 ⁇ m is emitted.
  • the energy of carriers c1 (for example, electrons) injected from the first region r1 can be relaxed.
  • the well width WLt is, for example, 5 nm or less.
  • the energy levels are discretely generated, for example, the first sub-band WLa (high level Lu) and the second sub-band WLb (low level Ll).
  • the carriers c1 injected from the first barrier layer BL1 are effectively confined in the first quantum well layer WL1.
  • the carrier c1 transitions from the high level Lu to the low level Ll
  • the light 31La corresponding to the energy difference (the difference between the high level Lu and the low level Ll) is emitted. That is, an optical transition occurs.
  • the quantum well layer may include a plurality of wells with overlapping wave functions.
  • the respective high levels Lu of the plurality of quantum well layers may be identical to each other.
  • the low levels Ll of the plurality of quantum well layers may be the same as one another.
  • intersubband optical transitions occur in either the conduction band or the valence band.
  • recombination of holes and electrons by a pn junction is not necessary.
  • carriers c1 of either holes or electrons cause optical transition to emit light.
  • carriers c1 for example, electrons
  • a barrier layer for example, the first barrier layer BL1
  • the well layer for example, the first quantum well layer WL1 is implanted. This causes an intersubband optical transition.
  • the second region r2 has, for example, a plurality of subbands.
  • the sub band is, for example, a mini band.
  • the energy difference in the subbands is small.
  • the second region r2 for example, light (for example, infrared light having a wavelength of 3 ⁇ m to 18 ⁇ m) is not substantially emitted.
  • the carriers c1 (electrons) of the low level L1 of the first region r1 pass through the second barrier layer BL2, are injected into the second region r2, and are relaxed.
  • the carrier c1 is injected into another cascaded first region r1a. An optical transition occurs in this first region r1a.
  • optical transition occurs in each of the plurality of unit structures r3. This makes it easy to obtain high light output in the entire active layer 31c.
  • the light source unit 30 includes the semiconductor light emitting element 30a.
  • the semiconductor light emitting element 30a emits the measurement light 30L by energy relaxation of electrons in the sub-bands of the plurality of quantum wells (for example, the first quantum well layer WL1 and the second quantum well layer WL2).
  • GaAs is used for the quantum well layers (for example, the first quantum well layer WL1 and the second quantum well layer WL2).
  • Al x Ga 1 -x As (0 ⁇ x ⁇ 1) is used for the barrier layers (eg, the first to fourth barrier layers BL1 to BL4).
  • the barrier layers eg, the first to fourth barrier layers BL1 to BL4.
  • the first cladding layer 31a and the second cladding layer 31e contain, for example, Si as an n-type impurity.
  • the impurity concentration in these layers is, for example, 1 ⁇ 10 18 cm ⁇ 3 or more and 1 ⁇ 10 20 cm ⁇ 3 or less (for example, about 6 ⁇ 10 18 cm ⁇ 3 ).
  • the thickness of each of these layers is, for example, 0.5 ⁇ m or more and 2 ⁇ m or less (for example, about 1 ⁇ m).
  • the first guide layer 31 b and the second guide layer 31 d contain, for example, Si as an n-type impurity.
  • the impurity concentration in these layers is, for example, 1 ⁇ 10 16 cm ⁇ 3 or more and 1 ⁇ 10 17 cm ⁇ 3 or less (for example, about 4 ⁇ 10 16 cm ⁇ 3 ).
  • the thickness of each of these layers is, for example, 2 ⁇ m or more and 5 ⁇ m or less (for example, 3.5 ⁇ m).
  • the distance 31 w (the width of the stack 31, that is, the width of the active layer 31 c) is, for example, 5 ⁇ m or more and 20 ⁇ m or less (for example, about 14 ⁇ m).
  • the length of the ridge waveguide RG is, for example, 1 mm or more and 5 mm or less (for example, about 3 mm).
  • the semiconductor light emitting device 30a (quantum cascade laser) operates at an operating voltage of, for example, 10 V or less.
  • the consumption current is lower than that of a carbon dioxide gas laser device or the like. This enables low power consumption operation.
  • breath diagnosis apparatuses that can be appropriately designed and implemented by those skilled in the art based on the breath diagnosis apparatus described above as the embodiment of the present invention also fall within the scope of the present invention as long as the scope of the present invention is included. Belongs to

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  • Sampling And Sample Adjustment (AREA)

Abstract

La présente invention concerne, dans un mode de réalisation, un dispositif de diagnostic d'air expiré qui possède les éléments suivants : une section d'alimentation à laquelle est fourni un échantillon de gaz contenant de l'air expiré, une section de cellule qui possède un espace dans lequel ledit échantillon de gaz est introduit à partir de la section d'alimentation, un tube d'introduction qui est ménagé entre la section d'alimentation et la section de cellule et qui guide l'échantillon de gaz de la section d'alimentation à l'espace susmentionné, une unité source de lumière qui introduit de la lumière de mesure dans l'espace et une unité de détection qui détecte ladite lumière de mesure après que ladite lumière de gestion a traversé l'espace. Le tube d'introduction possède une section intermédiaire qui a une section incurvée.
PCT/JP2014/074522 2014-02-19 2014-09-17 Dispositif de diagnostic d'air expiré WO2015125328A1 (fr)

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JP2014-030069 2014-02-19
JP2014030069A JP2017072372A (ja) 2014-02-19 2014-02-19 呼気診断装置

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WO2015125328A1 true WO2015125328A1 (fr) 2015-08-27

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Cited By (1)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US9835550B2 (en) 2015-03-18 2017-12-05 Kabushiki Kaisha Toshiba Breath analyzer

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* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
JPH03131316A (ja) * 1989-07-10 1991-06-04 Bai Corp 液滴の分離装置および方法ならびにタービン
JPH06213815A (ja) * 1992-12-03 1994-08-05 Hewlett Packard Co <Hp> 分光分析システムの校正方法
JPH10248826A (ja) * 1997-03-07 1998-09-22 Seitai Kagaku Kenkyusho:Kk 呼気中同位体分析装置
JP3105317U (ja) * 2004-05-18 2004-10-28 啓次 荒倉 高速波型エリミネーター
JP2008070369A (ja) * 2006-09-13 2008-03-27 Autoliv Development Ab 呼気分析装置
JP2010249556A (ja) * 2009-04-13 2010-11-04 Sharp Corp ガス成分検出装置
JP2012170863A (ja) * 2011-02-21 2012-09-10 Fuji Electric Co Ltd 気液分離器
WO2013095284A1 (fr) * 2011-12-22 2013-06-27 Aerocrine Ab Procede et appareil de mesure d'un composant de l'haleine
JP2013239751A (ja) * 2013-08-26 2013-11-28 Toshiba Corp 半導体発光装置

Patent Citations (9)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
JPH03131316A (ja) * 1989-07-10 1991-06-04 Bai Corp 液滴の分離装置および方法ならびにタービン
JPH06213815A (ja) * 1992-12-03 1994-08-05 Hewlett Packard Co <Hp> 分光分析システムの校正方法
JPH10248826A (ja) * 1997-03-07 1998-09-22 Seitai Kagaku Kenkyusho:Kk 呼気中同位体分析装置
JP3105317U (ja) * 2004-05-18 2004-10-28 啓次 荒倉 高速波型エリミネーター
JP2008070369A (ja) * 2006-09-13 2008-03-27 Autoliv Development Ab 呼気分析装置
JP2010249556A (ja) * 2009-04-13 2010-11-04 Sharp Corp ガス成分検出装置
JP2012170863A (ja) * 2011-02-21 2012-09-10 Fuji Electric Co Ltd 気液分離器
WO2013095284A1 (fr) * 2011-12-22 2013-06-27 Aerocrine Ab Procede et appareil de mesure d'un composant de l'haleine
JP2013239751A (ja) * 2013-08-26 2013-11-28 Toshiba Corp 半導体発光装置

Cited By (1)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US9835550B2 (en) 2015-03-18 2017-12-05 Kabushiki Kaisha Toshiba Breath analyzer

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