JP2015040770A - Exhaled-gas sampling analyzer and portable type exhaled-gas analyzer - Google Patents

Abstract

PROBLEM TO BE SOLVED: To provide a small-sized exhaled-gas sampling analyzer capable of removing moisture from exhaled-gas without requiring power consumption, and without impeding flow of the exhaled-gas, and to provide a portable type exhaled-gas analyzer using the same.SOLUTION: An exhaled-gas sampling analyzer 1A has a sampling path 10 for introducing and sampling exhaled-gas therethrough, an adiabatic change part 30 for cooling exhaled-gas introduced from the sampling path by adiabatic change, a separation part 31 for separating moisture from cooled exhaled-gas, and an analysis part 32 for analyzing exhaled-gas from which moisture is separated.

Description

  The present invention relates to a breath gas collection and analysis device, a portable breath gas analysis device, and the like.

  In humans, nutrients taken from food react with oxygen taken by breathing to produce chemical energy and carbon dioxide. Therefore, if the amount of oxygen that reacts with nutrients and the amount of carbon dioxide that accompanies it can be grasped, the amount of energy consumption can be determined. Generally, the heat energy held per gram of each nutrient is said to be 4 kcal for carbohydrates, 9 kcal for fats and 4 kcal for proteins. Carbohydrates and fats are eventually broken down into carbon dioxide and water, and proteins are broken down into urinary nitrogen, so measure the concentration and volume of breathing oxygen and carbon dioxide and the amount of urinary nitrogen. Find energy consumption. Since it is known in advance that the oxygen concentration in the atmosphere is about 21% and the carbon dioxide concentration is about 0.03%, how much the oxygen concentration in the exhalation is reduced compared to that in the atmosphere, and the carbon dioxide concentration is We will analyze how much it has increased. These are called breath gas analysis methods and have already been put into practical use.

  Furthermore, research on the components of biogas in the exhaled gas has progressed, and it has been found that it is possible to know how much fat has been burned by detecting acetone in the exhaled gas. For example, Patent Document 1 proposes an exercise device that detects the concentration of acetone in expired air and indicates an appropriate exercise intensity.

  In addition, as an example of non-invasive disease diagnosis in the future, studies have been made to diagnose various cancers from biological gas components in exhaled gas. It is still at the stage where clinical support for the specific component in the exhaled gas is correlated with which cancer, and future research results are awaited. For example, acetoin 1-butanol in exhaled breath is lung cancer, acetone is diabetes or obesity, ethane or pentane is bronchial asthma or pulmonary hypertension, nitric oxide is asthma, ammonia is cerebral liver disease, hydrogen is dyspepsia syndrome or lactose intolerance, Studies have shown that methane is associated with gut microbiota, trimethylamine is associated with liver failure, methyl mercaptan and hydrogen sulfide are associated with periodontal disease, and toluene is associated with thinner poisoning.

  Expiratory gas is generated by gas exchange with blood in the alveoli, and the temperature of the expiratory gas is about 37 ° C., which is close to the deep body temperature, and the relative humidity is almost 100%. When the exhaled gas having a relative humidity of 100% is directly analyzed by the sensor, if many water molecules are adsorbed on the sensor surface, the adsorption of molecules on the sensor surface of other gas components in the exhaled gas may be hindered. For this reason, it is necessary to have a configuration in which moisture is detected in the expired gas and then detected by the sensor. Patent Documents 2 to 5 disclose techniques for removing moisture contained in exhaled gas.

JP 2010-268864 A JP 11-160301 A JP 2010-046107 A JP 2009-047593 A Japanese Patent Laid-Open No. 7-103974

  In Patent Document 2, exhaled gas is cooled by a dehumidifier, but a specific structure for cooling the exhaled gas is not disclosed. In the cooling methods of Patent Documents 3 to 5, it may take electric power to cool the exhaled gas, obstruct the flow of the exhaled gas, or increase the size of the apparatus. For example, the Beltier element used in Patent Document 3 requires electric power. When moisture is adsorbed on a porous material such as silica as in Patent Document 4, the flow of exhaled gas is inhibited. In Patent Document 5, exhalation gas is allowed to pass through a thin tube passing through the refrigerant, and the exhalation gas is cooled to condense moisture. However, the drawing of the thin tube, the refrigerant machine, etc., increase the size of the apparatus.

  Some aspects of the present invention are a small expiratory gas sampling / analyzing apparatus capable of removing moisture from expiratory gas without requiring power consumption and without disturbing the flow of expiratory gas, and portable expiratory air using the same. An object is to provide a gas analyzer.

(1) One aspect of the present invention is
A sampling channel for introducing and collecting exhaled gas;
An adiabatic change part that cools the exhaled gas introduced from the sampling channel by an adiabatic change;
A separation unit for separating moisture from the cooled exhaled gas;
An analysis unit for analyzing the exhaled gas from which moisture has been separated;
The present invention relates to a breath gas collection and analysis apparatus characterized by comprising:

  In one embodiment of the present invention, the collected exhaled gas is cooled by an adiabatic change. Adiabatic work is performed by the adiabatic change, and the temperature of the exhaled gas is decreased by an amount corresponding to the adiabatic work. The adiabatic change with cooling is adiabatic expansion. The exhaled gas can be adiabatically compressed in advance, and then the exhaled gas can be adiabatically expanded at once. In this way, since the exhaled gas can be adiabatically changed only by changing the volume without supplying heat, no power is required, the flow of exhaled gas is not hindered, and the apparatus is not enlarged. Since the cooled exhaled gas is separated into moisture by the separation unit and guided to the analysis unit, adhesion of moisture to the analysis unit is prevented.

  (2) In one mode of the present invention, the heat insulation change part can be constituted by a turbine having a housing and a plurality of turbine blades rotatably supported in the housing.

  In this way, the exhaled gas is compressed between the turbine blades and discharged from between the turbine blades, thereby being adiabatically expanded and cooled at once. Moreover, since the turbine blade is rotated by the energy of the exhaled gas, no power is required and the flow of the exhaled gas is not hindered.

  (3) In one aspect of the present invention, the turbine is a radiant flow turbine in which the exhaled gas is introduced from a radial direction of the turbine blade and discharges the exhaled gas along the axial direction of the turbine blade. Can do.

  The radial flow turbine can reduce the axial length as compared with an axial flow turbine that takes in exhalation gas from one axial end of the turbine blade and discharges exhalation gas from the other axial end of the turbine blade. Suitable for downsizing of equipment.

  (4) In one aspect of the present invention, the housing has a flow path for guiding and guiding the exhaled gas toward the radial direction of the turbine blade, and the cross-sectional area of the flow path is upstream of the exhaled gas. It can be made smaller as it goes downstream.

  In this way, the expiratory gas can be gradually compressed by the flow path formed in the housing before the expiratory gas is led out to a narrow space between the turbine blades. Thereby, exhaled gas is compressed at a stretch in the narrow space between turbine blades, and it can control that the temperature of exhaled gas rises.

  (5) In the aspect of the invention, the separation unit may include a moisture adsorption unit disposed at a position facing the discharge end from which the expiration gas is discharged from the turbine in the axial direction.

  If it carries out like this, the expiration gas discharge | released along the axial direction from the radial flow turbine will contact a water | moisture-content adsorption | suction part, and a water | moisture content will be removed from an expiration gas.

(6) In one aspect of the present invention,
A first exhaust path for exhausting exhaled gas in the sampling path to the outside by the expiratory pressure;
A valve for opening and closing a part of the first discharge path;
A valve drive unit for opening and closing the valve;
When the valve is closed, a second discharge path that discharges exhaled gas in the sampling path to the outside by the expiratory pressure;
Further comprising
The adiabatic change part, the separation part, and the analysis part may be disposed in the second discharge path.

  If the valve is opened, the exhaled gas introduced into the sampling path by the expiratory pressure is discharged to the outside via the first discharge path by the expiratory pressure. In addition, if the valve is opened, it is possible to inhale through the sampling channel and the first discharge channel. Therefore, it is allowed to breathe normally (inhalation and exhalation) while wearing the exhalation gas collection and analysis device even during daily life and exercise. When the valve is closed, the exhaled gas in the collection channel is introduced into the second exhaust channel different from the first exhaust channel by the expiratory pressure, and is analyzed by the analysis unit via the adiabatic change unit and the separation unit.

  (7) In 1 aspect of this invention, the said collection path can contain the mouthpiece which can be attached or detached with respect to the main body in which the said heat insulation change part, the said separation part, and the said analysis part are provided.

  If the mouthpiece is used as a consumable item, hygiene and safety are ensured.

(8) Another aspect of the present invention is:
The breath gas collection and analysis apparatus according to any one of (1) to (7),
Glasses-type display device connected to the exhalation gas collection analyzer for displaying the analysis results;
The present invention relates to a portable expiratory gas analyzer.

  According to another aspect of the present invention, breathing gas is analyzed hand-free by holding the sampling path (or mouthpiece) of the breath gas collecting and analyzing apparatus in the mouth and wearing a glasses-type display device on the head. And the analysis result can be confirmed. The glasses-type display device may display a procedure for collecting exhalation, and instruct the start of exhalation on the screen.

1 is a schematic explanatory diagram of an exhaled gas sampling / analyzing apparatus according to a first embodiment of the present invention. It is a PV diagram explaining the principle of operation in the heat insulation change part shown in FIG. It is a schematic sectional drawing of the turbine which is an example of an adiabatic change part. It is a perspective view of a turbine blade. FIG. 5A is a plan view of the separation portion, and FIG. 5B is a vv cross-sectional view of FIG. 5A. It is a schematic sectional drawing of the expiration gas collection | recovery analyzer provided with the valve which is 2nd Embodiment of this invention. 7A and 7B are diagrams illustrating a semiconductor sensor. It is an equivalent circuit diagram of a semiconductor sensor. It is a figure which shows the relationship between the resistance ratio of a semiconductor sensor, and gas concentration. 10A and 10B are diagrams illustrating an example of a QCM sensor. FIGS. 11A and 11B are diagrams showing different examples of the QCM sensor. 12A and 12B are diagrams showing a circuit example of the QCM sensor and its frequency response characteristics. It is a figure which shows the calibration curve of the frequency change rate of QCM sensor, and gas concentration. It is a figure for demonstrating the detection principle of a SERS sensor. It is a figure which shows the analytical curve of acetone. It is a figure which shows the flow from the intake of three macronutrients (a carbohydrate, lipid, protein) to storage. It is a figure explaining the mechanism of fat burning when exercising. It is a figure explaining the time transition of the utilization factor of carbohydrate and fat in aerobic exercise. It is a figure which shows a portable expiratory gas analyzer. It is a control system block diagram of a portable expiratory gas analyzer. It is an operation | movement flowchart of a portable breathing gas analyzer.

  Hereinafter, preferred embodiments of the present invention will be described in detail. The present embodiment described below does not unduly limit the contents of the present invention described in the claims, and all the configurations described in the present embodiment are indispensable as means for solving the present invention. Not necessarily.

1. First Embodiment (Exhalation Gas Collection and Analysis Device)
FIG. 1 is a cross-sectional view of the exhaled gas collection / analysis apparatus 1A. In FIG. 1, an exhalation gas collection / analysis apparatus 1A includes a collection path 10 through which exhaled gas is collected by the exhalation pressure, and a main body (housing) 20A through which the exhalation gas in the collection path 10 passes. The collection path 10 may be integrated with the main body 20A, but may be a mouthpiece that is detachable from the main body 20A. The opening end 11 side of the collection path 10 is held, and exhaled gas is introduced into the collection path 10 and collected.

  The main body 20A communicating with the collection channel 10 has a discharge port 21 at the downstream end of the exhalation gas passage passing through the main body 20A. Exhaled gas in the main body 20 </ b> A is discharged from the discharge port 21. In the main body 20A, an adiabatic change part 30, a separation part 31, and an analysis part 32 are sequentially arranged from the upstream side of the expiration gas passage passing through the main body 20A. The adiabatic change unit 30 cools the exhaled gas introduced from the sampling channel 10 by adiabatic change. The separation unit 31 separates moisture from the cooled exhaled gas. The analysis unit 32 analyzes the exhaled gas from which moisture has been separated.

  FIG. 2 is a PV diagram for explaining the operating principle in the adiabatic change section 30. In the adiabatic change in thermodynamics, the gas and the surroundings are insulated from each other, and internal heat generation due to friction does not occur, so the change amount dq of the heat quantity q is dq = 0.

If the internal energy is u, the amount of change is du, the pressure is p, the volume is v, the amount of change is dv, the constant volume specific heat is cv, the constant pressure specific heat is cp, and the absolute temperature is T, ,
dq = du + pdv = cvdT + pdv = 0 Equation (1)
Is established.

Differentiating both sides of the ideal gas equation of state pv = RT,
pdv + vdp = RdT (2)
It becomes. However, R is a gas constant.

Transforming equation (2) using R = cp−cv,
dT = (pdv + vdp) / R = (pdv + vdp) / (cp−cv) (3)
It becomes.

When formula (1) is transformed using formula (3),
cv · (pdv + vdp) / (cp−cv) + pdv = 0 Equation (4)
It becomes.

When the equation (4) is transformed using the specific heat ratio (adiabatic index) κ = cp / cv,
(Pdv + vdp) + (κ−1) pdv = κpdv + vdp = 0 Equation (5)
It becomes.

When equation (5) is transformed,
κdv / v + dp / p = 0 Equation (6)
It becomes. Integrating both sides of equation (6), since the ^{κInv + Inp = In (v κ} p) = constant,
pv ^κ = const (constant) (7)
Is established.

Pv ^κ = const in the equation (7) means an adiabatic change when the volume changes from the state 1 (pressure p1, temperature T1)) to the state 2 (pressure p2, temperature T2) shown in FIG. This adiabatic change, insulation work w ₁₂ of FIG. 2 are performed. Since the adiabatic change from state 1 (pressure p1, temperature T1)) to state 2 (pressure p2, temperature T2) shown in FIG. 2 is adiabatic expansion, the amount of gas (expired gas) corresponding to the adiabatic work is increased. The temperature decreases from temperature T1 to temperature T2 (T2 <T1). The adiabatic change in Expression (7) is distinguished from the isothermal change in which pv = const shown in FIG. 2, and a cooling action occurs.

  As an example of the adiabatic change portion 30 shown in FIG. 1, the turbine 40 shown in FIG. 3 can be cited. The turbine 40 includes a housing 41 and a plurality of turbine blades 43. The housing 41 is provided with a rotatable shaft 42 via a bearing (not shown), and a plurality of turbine blades 43 are fixed to the shaft. In addition, since the expiration gas is a temperature of about body temperature, the housing 41 and the plurality of turbine blades 43 can be molded from a resin having low heat resistance.

  A turbine 40 shown in FIG. 3 is a radiant flow turbine in which exhaled gas is introduced from the radial direction A of the turbine blade and the exhaled gas is discharged along the axial direction B of the turbine blade. The radial flow turbine of the present embodiment is advantageous in that the length in the axial direction B can be shortened as compared with the axial flow turbine, and it is suitable for downsizing of the apparatus. The adiabatic change section 30 may be constituted by an axial flow turbine. However, since the axial flow turbine takes in the exhaled gas from one axial end of the turbine blade and releases the exhaled gas from the other axial end of the turbine blade, multistage turbine blades are provided along the axial direction B. As a result, the length in the axial direction B is increased.

  In the radial turbine 40, the interval between the turbine blades 43, 43 adjacent in the circumferential direction is wide on the upstream side 43A of the exhaled gas and narrows on the downstream side 43B. In this way, the exhaled gas is compressed between the turbine blades 43 and discharged outward from between the turbine blades 43 to be adiabatically expanded and cooled at once. Moreover, since the turbine 40 is rotated by the energy of the expiratory gas, no power is required and the flow of the expiratory gas is not hindered.

  As shown in FIG. 3, the housing 41 has a flow path 41 </ b> A for introducing and guiding exhaled gas from the radial direction A of the turbine blade 43. The flow path 41 </ b> A has a length that substantially goes around the periphery of the turbine blade 43, and one end in the circumferential direction of the flow path 41 </ b> A communicates with the sampling path 10. The flow path 41A can make the cross-sectional area of the said turbine blade said flow path small as it goes to the downstream rather than the upstream of the said expiration gas.

  In this way, the expiratory gas can be gradually compressed by the flow path 41 </ b> A formed in the housing 41 before the expiratory gas is introduced into the narrow space between the turbine blades 43. As a result, the exhaled gas is compressed at once in a narrow space between the turbine blades 43, and the temperature of the exhaled gas can be prevented from rising.

  Separation part 31 can be constituted by a moisture adsorbing part arranged at a position facing discharge end part 41 </ b> B from which exhaled gas is discharged from turbine 40 in the axial direction B. As shown in FIGS. 5A and 5B, the moisture adsorbing part 31 has a surface area of one surface of the base plate 51 increased by forming a concave / convex pattern 52 on one surface of the base plate 51.

  The exhaled gas discharged along the axial direction B from the discharge end portion 41B of the radiant flow turbine 40 comes into contact with the moisture adsorption unit 31, and the flow direction is changed. At this time, the exhaled gas cooled and liquefied comes into contact with the concavo-convex pattern 52 of the moisture adsorption unit 31. At that time, moisture is condensed and adsorbed on the concave / convex pattern 52, and moisture is separated from the exhaled gas. A drain hole 22A penetrating the bottom wall 22 of the main body 20A is provided, and the plug 22B can be removed to appropriately release moisture to the outside.

  Expiratory gas is generated by gas exchange with blood in the alveoli, and the temperature of the expiratory gas is about 37 ° C., which is close to the deep body temperature, and the relative humidity is almost 100%. The exhaled gas having a relative humidity of 100% passes through the adiabatic change section 30 and the separation section 31 to remove moisture. Therefore, in the analysis part 32 located downstream from the separation part 31, it is prevented that many water molecules adsorb | suck to a sensor surface. As a result, gas components other than water molecules in the exhaled gas are easily adsorbed on the sensor surface.

2. Second Embodiment (Exhalation Gas Collection / Analysis Device with Valve)
FIG. 6 is a cross-sectional view of the exhaled gas collection / analysis apparatus 1B. In FIG. 6, an exhalation gas collection / analysis apparatus 1B includes a collection path 10 through which exhalation gas is collected by the exhalation pressure, a first discharge path 23 that discharges the exhalation gas in the collection path 10 to the outside by the exhalation pressure, A valve 24 that opens and closes the discharge path 23, a valve drive unit 25 that drives the valve 24 to open and close, and a second discharge path 26 that discharges exhaled gas in the collection path 10 to the outside by expiratory pressure when the valve 24 is closed. Have. In the present embodiment, the adiabatic change part 30, the separation part 31, and the analysis part 32 are provided in the second discharge path 26.

  The first and second discharge paths 23 and 26 are provided in the housing 20B that constitutes the main body. The collection path 10 can be a mouthpiece that is detachable from the housing 20B. The mouthpiece 10 is provided with a filter 10A. The filter 10A prevents saliva and the like from entering the inside.

  When the valve 24 is opened, the first discharge path 23 discharges the expiratory gas in the mouthpiece 10 to the outside by the expiratory pressure as indicated by the solid line arrow in FIG. When the valve 24 provided in the first discharge path 23 is opened by the drive unit 25, the inside of the housing 20B communicates with the outside air. Therefore, when the valve 24 is opened, it is possible to breathe (inhale and exhale) via the mouthpiece 10 and the first discharge path 23. Therefore, even during daily life and exercise, it is allowed to breathe normally (inhalation and exhalation) while wearing the exhalation gas collecting / analyzing apparatus 1B. Further, if the valve 24 is opened, dead space exhalation can be discharged to the outside.

  When the valve 24 is closed, the second discharge path 26 discharges the expiratory gas in the mouthpiece 10 to the outside by the expiratory pressure as indicated by the dotted arrow in FIG. The second exhaust path 26 is provided with an analysis unit 32 that analyzes exhaled gas. Therefore, since the exhaled gas can be analyzed only when the valve 24 is closed, if the valve 24 is opened during dead space exhalation and the valve 24 is closed during the end exhalation, the analysis unit 32 analyzes only the end exhalation gas. it can. Moreover, in order to introduce the end exhalation into the second discharge channel 26, it is only necessary to close the valve 24, and a suction pump or the like is not necessary.

  Also in FIG. 6, as in FIG. 1, the adiabatic change part 30 and the separation part 31 are provided upstream of the analysis part 32. Therefore, water molecules in exhaled gas are prevented from adhering to the sensor surface of the analysis unit 32. In addition, since the 2nd discharge path 26 is provided with the heat insulation change part 30, flow path resistance is larger than the 1st discharge path 23. FIG. Therefore, when the valve 24 is opened, the exhaled gas hardly flows into the second exhaust path 26.

3. Analysis unit 3.1. Semiconductor Sensor As the analysis unit 32 shown in FIGS. 1 and 6, a semiconductor sensor 50 shown in FIGS. 7A and 7B can be cited. On the surface 51A of the substrate 51 of the semiconductor sensor 50, as shown in FIG. 7A, gas sensitive material plates 52A to 52D and two electrodes 53A and 53B connected to the gas sensitive material plates 52A to 52D, Have As shown in FIG. 7B, the back surface 51B of the substrate 51 includes a heater 54 and electrodes 55A and 55B connected thereto. The gas sensitive material plates 52A to 52D include tin oxide SnO ₂ , antimony-added tin oxide Sb: SnO ₂ , zinc oxide ZnO, tungsten oxide WO ₃ , indium tin oxide, titanium oxide TiO ₂ , niobium-added titanium oxide Nb: TiO _{2 and the} like, and these composite materials and other additives can be included.

FIG. 8 is an equivalent circuit diagram of the semiconductor sensor 50. When reducing gas is exposed to the gas sensitive material plates 52A to 52D heated by the heater 54, the oxygen adsorbed on the surfaces of the gas sensitive material plates 52A to 52D is reduced, the potential barrier is lowered, and electrons move. It becomes easy. Thereby, the sensor resistances R _{L1 to} R _{L4 of the} gas sensitive material plates 52A to 52D are reduced. FIG. 9 shows the correlation between gas concentration and (R _S / R ₀ ) between the initial sensor resistance R ₀ of a semiconductor sensor using a gas sensitive material plate and the sensor resistance R _S during gas analysis. ing. The rate of change of R _S / R ₀ depending on the gas concentration varies depending on the gas type. The characteristics of FIG. 9 vary depending on the gas sensitive material plate. Therefore, by detecting the output voltages V _{OUT1 to} V _OUT4 (see FIG. 8) corresponding to the sensor resistance ratios (R _S / R ₀ ) of the plurality of gas sensitive material plates 52A to 52D shown in FIG. The gas type and gas concentration can be detected by a linear discriminant method, a principal component analysis method, or the like.

3.2. Quartz Crystal Microbalance (QCM) Sensor The QCM sensor 60 includes electrodes 62A and 62B disposed on both sides of the crystal resonator 61 as shown in FIGS. 10 (A), (B) or FIGS. 11 (A), (B). The lead wires 63A and 63B arranged and connected to the electrodes 62A and 62B are fixed to the substrate 64. In FIG. 10B, the lead wires 63A and 63B are arranged in parallel to the substrate 64, while in FIG. 11B, the lead wires 63A and 63B are arranged perpendicular to the substrate 64. In FIGS. 11A and 11B, the air flow is better, and the skin gas is likely to come into contact with both surfaces of the crystal unit 61.

The frequency of the crystal unit 61 changes according to the mass of the substance on the electrodes 62A and 62B, and the relationship between the amount of change in the frequency and the mass of the attached substance is called the Sauerbrey equation. The frequency increases as the amount of adhering material decreases. A method of measuring the mass change of a substance on the electrode by detecting the frequency change of the crystal resonator using this phenomenon is called a crystal resonator microbalance method (QCM method). Sauerbrey equation, the fundamental frequency F _0, the change amount of the frequency [Delta] F, mass change amount Delta] m, the density of the crystal [rho, the shear stress of the crystal mu, and the area of the electrode is A,
ΔF = −2F ₀ ² · Δm / A / (ρμ) ^(1/2) (8)
It can be expressed. On the surfaces of the electrodes 62A and 62B, the frequency decreases when the amount of adhered substances increases, and the frequency increases when the amount of adhered substances decreases. Thus, since the frequency changes when the analyte is adsorbed, it is possible to know how much the analyte has been adsorbed by detecting the frequency change ΔF.

  12A and 12B show a circuit example of the QCM sensor and its frequency response. Although it is a general circuit composed of a C-MOS inverter, resistor, and capacitor, it is not limited to this circuit. In order to make it easy to adsorb a specific component of exhaled gas, a polymer may be formed thinly on the electrode surface of the QCM sensor. By selecting a polymer that responds as shown in the frequency response graph of FIG. 12 (B) as the response curve of the analyte with respect to the polymer, obtaining the amount of frequency change, and obtaining a calibration curve in advance as shown in FIG. The concentration of the desired component can be known from the frequency change amount. Note that the frequency response graph is not limited to the one that responds cleanly as shown in the figure, so if a polymer is selected in advance, a good response can be obtained for the target component gas. FIG. 13 shows an example of the amount of frequency change with respect to three types of gas when a polymer is applied to a QCM sensor (quartz crystal oscillator) by spin coating.

3.3. SERS Sensor As shown in FIG. 14, in the SERS sensor 70, a sensor substrate 71 is arranged facing a flow path into which skin gas is introduced, and excitation light (frequency ν) from the light source is irradiated to the sensor substrate 71. . Most of the excitation light is scattered as Rayleigh scattered light, and the frequency ν or wavelength of the Rayleigh scattered light does not change with respect to the incident light. A part of the excitation light is scattered as Raman scattered light, and the frequency (ν−ν ′ and ν + ν ′) or wavelength of the Raman scattered light reflects the frequency ν ′ (molecular vibration) of the molecule of skin gas. . That is, the Raman scattered light is light reflecting the skin gas molecules to be examined. The vibration energy of skin gas molecules may be added to the vibration energy or light energy of Raman scattered light. Such a frequency shift (ν ′) is called a Raman shift.

  In the region where incident light is incident on the metal nanoparticles 72 formed on the sensor substrate 71 shown in FIG. 14, an enhanced electric field 73 is formed in the gap between the adjacent metal nanoparticles 72. In particular, when the incident light is irradiated onto the metal nanoparticles 72 smaller than the wavelength of the incident light, the electric field of the incident light acts on free electrons existing on the surface of the metal nanoparticles 72 to cause resonance. Thereby, electric dipoles due to free electrons are excited in the metal nanoparticles 72, and an enhanced electric field 73 stronger than the electric field of incident light is formed. This is also called Localized Surface Plasmon Resonance (LSPR). This phenomenon is a phenomenon peculiar to electrical conductors such as metal nanoparticles 72 having a size of 1 to 500 nm smaller than the wavelength of incident light.

  In FIG. 14, when the sensor substrate 71 is irradiated with incident light, surface enhanced Raman scattering (SERS) occurs. That is, when the skin gas molecule 74 enters the enhanced electric field 73, the Raman scattered light by the target molecule 74 is enhanced by the enhanced electric field 73, and the signal intensity of the Raman scattered light increases. In such surface-enhanced Raman scattering, the analysis sensitivity can be increased even if the amount of the target molecule 74 is very small.

  FIG. 15 shows an example of a calibration curve for acetone. For example, a sample gas having a different concentration of acetone is prepared by the analysis unit 32 formed by the SERS sensor shown in FIG. 14, and acetone detection is performed for each sample. Acetone signal intensity is obtained for a strong peak, and a correlation graph between acetone concentration and signal intensity is created. From the graph, a calibration curve of acetone concentration and acetone signal intensity is obtained as shown in FIG.

4). FIG. 16 shows the flow from intake to storage of the three major nutrients (carbohydrate, lipid, protein) that are the main energy sources. Carbohydrates, lipids, and proteins taken in the diet are digested in the stomach and further digested and absorbed in the small intestine. The absorbed nutrients circulate in the blood in different forms, such as carbohydrates for glucose, lipids for fatty acids and glycerol, and proteins for amino acids. Some of the necessary parts burn, but the extra ones are changed to glucose for liver glycogen and muscle glycogen, fatty acid and glycerol for fat via neutral fat, and amino acid for protein, respectively. Stored and consumed via reverse flow as needed. The energy when the three macronutrients are burned corresponds to 4 kcal / g for carbohydrates, 9 kcal / g for lipids, and 4 kcal / g for proteins. However, since lipid contains water when stored in white adipocytes, it corresponds to an energy of 7.2 kcal / g.

  FIG. 17 shows a diagram for explaining the mechanism of fat burning when exercising. Exercise results in adrenaline, activation of hormone-sensitive lipase in white fat cells, promotion of triglyceride breakdown, and fatty acids and glycerol. Since fatty acids cannot be circulated in the blood, they bind to albumin to become free fatty acids and circulate in the blood. A part of it is supplied to the myocardium and skeletal muscle and decomposed by β-oxidation to produce acetyl-CoA while producing NADH2 + and FADH2, and ATP is produced via the TCA circuit (commonly called citric acid circuit). Eventually, it becomes carbon dioxide (CO2) and water (H2O). In skeletal muscle, glycogen is mainly consumed as energy, and free fatty acid consumption is small. In the myocardium, about 70% of the total energy is consumed as free fatty acids.

  On the other hand, most of the free fatty acids bind to carnitine and become acylcarnitine, which is supplied to the liver. It becomes acyl-CoA in the liver, β-oxidized in the liver mitochondria, and becomes acetyl-CoA. Furthermore, acetyl-CoA is changed to acetoacetic acid, and further β-hydroxybutyric acid (3-hydroxybutyric acid) and acetone. Acetoacetic acid, β-hydroxybutyric acid, and acetone are collectively referred to as a ketone body, and only acetone becomes a gas that circulates in the blood and is released from breath and skin. Looking at the rate of fat burning, the proportion in the liver is higher than in skeletal muscle and heart, and there is a correlation between fat burning and acetone. Therefore, the amount of fat burning can be known by measuring the amount of acetone in the breath gas and the amount of acetone in the skin gas.

  FIG. 18 is a diagram for explaining the temporal transition of carbohydrate and fat utilization rates in aerobic exercise. In the first step, ATP is synthesized by metabolism of glycogen in muscle. In the second step, the use of blood glucose begins with a decrease in muscle glycogen. Next, adipose tissue fat is released into the blood as free fatty acids. Finally, using both as fuels, ATP is synthesized by oxidation metabolism.

  It is said that fat burning becomes active after 15-20 minutes after the start of exercise. Fat burning is not actively performed at any exercise intensity, but fat burning is active in a region where the exercise intensity is relatively light. As the exercise intensity increases, anaerobic exercise results, and the amount of fat burning decreases. Instead, glycogen is mainly consumed.

  In general, it is known that the fat burning rate (the amount of fat burning per unit time) becomes maximum depending on the sex, age, exercise habits, and the like. The fat burning rate is maximized when the exercise intensity is about 40% for an ordinary person and when the exercise intensity is about 50% for an athlete. Therefore, in order to efficiently burn fat, it is necessary to appropriately manage exercise intensity for each individual. Specifically, the exercise intensity that maximizes the fat burning rate is measured for each individual, and the exercise intensity is indicated by numerical values that can be easily managed during exercise such as heart rate and pulse rate. Is effective. The exercise intensity at which the fat burning rate is maximized for each individual changes with exercise habits and age, and regular measurement increases the effect of fat burning.

  Furthermore, if the exercise is performed for a certain period of time according to the appropriate exercise intensity and the effect can be confirmed, the motivation to continue the exercise increases, and a continuous effect can be expected. Measuring the amount of fat burning during exercise has the following two meanings: 1) indicate the appropriate exercise intensity that maximizes the fat burning rate, and 2) confirm the effect of exercise with the appropriate exercise intensity. is there.

The three major nutrients are sugars, lipids, and proteins, and the composition ratios of carbon atoms, oxygen atoms, hydrogen atoms, etc. are different. Therefore, during internal breathing, the ratio of consumed O ₂ and produced CO ₂ differs depending on which nutrient is decomposed. When nutrients, which are whole body cells, are mainly metabolized, the proportion should be reflected in respiration. This is expressed by a respiratory quotient RQ (Respiratory Quotient), which is expressed by the following equation.

Respiratory quotient RQ = (CO ₂ emission per unit time) / (O ₂ consumption per unit time)
Formula (8)
Lipids have very few oxygen atoms in the fatty acids themselves, so they must consume a lot of oxygen when they break down. Since the amount of CO ₂ produced is small for O ₂ consumption, the respiratory quotient is 0.70, the smallest among the three major nutrients. Fat has the lowest oxygen content, so the heat per weight is 9.3 kcal / g, the largest among the three major nutrients. It is a nutrient suitable for preserving energy, and lipid is also stored subcutaneously by overeating.

The proportion of glucose atoms that are representative of saccharides is C ₆ H ₁₂ O ₆ . Since it contains a lot of oxygen atoms, it can be decomposed even if the amount of oxygen consumption is small. The respiratory quotient is 1.00, the largest among the three major nutrients. Conversely, the oxygen content is high, so the heat per weight is 4.1 kcal / g, the smallest among the three major nutrients.

Proteins have an atomic ratio between lipid and carbohydrate, a respiratory quotient of 0.85, and a calorific value of 5.3 kcal / g. Theoretically, the respiratory quotient RQ can be 1 or more, but actually the respiratory quotient R
The condition that Q exceeds 1 is limited. On the other hand, when the respiratory quotient RQ is 0.7, it indicates fat utilization, and when the respiratory quotient RQ is 0.7 or less, it indicates that the product is ketogenic in a starved state. Very recently, it may be considered that the respiratory quotient RQ is substantially constant at rest, and it is known that the variation of the individual respiratory quotient is also in the range of 0.78 to 0.87.

The energy produced when the three nutrients are oxidized is as follows.
1) When carbohydrates are oxidized
_{C 6 H 12 O 6 + 6O} 2 → 6CO 2 + 6H 2 O + 36ATP (657kcal)
_{[RQ = 6CO 2 / 6O 2} = 1.0]
2) If the fat is oxidized _{C 55 H 102 O 6 + 77.5O2} → 55CO 2 + 51H 2 + 429ATP (7,833kcal)
[RQ = 55CO ₂ /77.5O ₂ = 0.71]
3) When protein is oxidized
C ₁₀₀ H ₁₅₉ O ₃₂ S _0.7 + 105.3O ₂ →
_{13CON 2 H 4 (urea) +} 87CO 2 + 52.8H 2 O + 0.7H 2 SO 4 + 27ATP
(4,948 kcal) [RQ = 87 CO ₂ /105.3O ₂ = 0.83]
4) When a ketone body is produced from fat
0.176 g (lipid) +0.437 LO ₂ → 1 g (ketone body) +0.11 LCO ₂ + 0.129H ₂ O + 2,039 kcal
_{[RQ = 0.111LCO 2 /0.437LO 2 =} 0.25]
Fat burning rate (g / min) = oxygen uptake (L / min) × heat amount per liter of oxygen (kcal / L) × burning ratio of lipid (%) × weight corresponding to heat amount of lipid (g / kcal)

Here, the oxygen intake (L / min) is a value measured by the expiration gas analyzer. The amount of heat per liter of oxygen (kcal / L) is obtained by converting the respiratory quotient RQ value measured by the breath gas analyzer into the amount of heat per liter of oxygen shown in the table. Lipid burning ratio (%) is the ratio of carbohydrate to lipid in burning to respiratory quotient. The weight corresponding to the calorific value of lipid is 0.1097 (g / kcal) because 7,833 kcal of energy is generated when fat C ₅₅ H ₁₀₂ O ₆ (859.395 g / mol) is burned.

  A correlation between the fat burning rate obtained in this way and the amount of acetone released from the skin per minute is taken in advance, and the fat burning rate is calculated from the measured acetone amount in the breath gas per minute.

4). Portable Expiratory Gas Analyzer FIG. 19 shows a portable expiratory gas analyzer 100 using the expiratory gas collection / analyzer 1 (1A or 1B) shown in FIG. 1 or FIG. The portable breath gas analyzer 100 includes the breath gas collection analyzer 1 (1A or 1B) shown in FIG. 1 or 6 and a glasses-type display device 110. The exhalation gas sampling / analysis apparatus 1 is fixed to, for example, the front end of the support unit 120, and the other end of the support unit 120 is locked to a user's ear or the like. The expired gas collection / analysis apparatus 1 and the glasses-type display apparatus 110 can be connected by, for example, a cable disposed in the support unit 120.

  The eyeglass-type display device 110 is also called a head mounted display, and has been actively developed in recent years. There are mainly three display methods, and the video transmission display method or the optical transmission display method is more suitable than the non-transmission display method for the purpose of exercise. This is because the non-transparent display system cannot be seen outside when attached. The video transmissive display system is equipped with not only a display device but also a video camera, and when it is attached, you can not see the outside directly, but the outside is reflected on the display, so users can safely Can move. In the optical transmission type display system, the display device is made of a half mirror and the outside can be seen. Some have a display device on one eye only. When an optical multilayer half mirror is used, it is possible to see through the outside while displaying only necessary information on the surface of the display plate.

  FIG. 20 is a control system block diagram of the portable breath gas analyzer 100 provided with the breath gas collection analyzer 1B shown in FIG. In the bus line of the CPU 130, in addition to the breath gas analysis unit 32 provided in the breath gas collection analyzer 1, the drive unit 25 that drives the valve 24, and the glasses-type display device 110, the input unit 140 and the heart rate sensor 150. , GPS 160 and timer 170 are connected. The heart rate sensor 150 detects the heart rate during exercise. When walking or jogging, if you know the relationship between running speed (km / h) and heart rate in advance, you can know the walking speed from the heart rate, and calculate calories burned from the time you continued walking and jogging. Is possible. A pulse sensor may be used instead of the heart rate sensor. By having the GPS 160, data such as walking speed, walking distance, and time can be accurately obtained, so that the calories consumed can also be accurately calculated.

Here, a person's exhalation gas is composed of several hundreds or more kinds of gas components, and it is possible to obtain information correlating with a human health condition such as illness or stress from the components and amounts thereof. The main components of the atmosphere are N ₂ is about 78%, O ₂ is about 21%, argon is 0.93%, and CO ₂ is 0.03%. N ₂ is about 78%, O ₂ is about 16%, CO ₂ is 4%, and water vapor, ammonia, acetone, isoprene, ethanol, propanol, pentanol, methanol, H ₂ , sulfur compounds, and the like. Here, exhaled gas means mainly end-expired gas exchanged in the alveoli, including some dead space gas (gases that do not contribute to alveolar gas exchange such as oral cavity and esophagus) that are mixed during collection. However, it reflects the gas components contained in the blood. Therefore, it is desirable to reduce the ratio of dead space gas as much as possible when collecting exhaled gas. In general, the ratio of dead space ventilation VD to tidal volume VT of a healthy adult is said to be VD ÷ VT = 150 mL ÷ 500 mL = 0.3 in the case of normal breathing. The dead space ventilation VD varies depending on the age and sex, and is about 90 to 180 mL.

  Therefore, it is preferable to display the sampling timing of the expiration gas on the glasses-type display device 110. FIG. 21 shows an operation flowchart of the portable breath gas analyzer 100 including a display operation on the glasses-type display device 110.

  First, personal information such as the subject's sex, age, weight, resting heart rate (pulse rate, etc.) is input (step 1), and then the input information is registered (recorded) in a storage device in the device (step). 2) Setting exhalation gas collection conditions (collection time, interval, display method, dead space gas discharge time, etc.) (step 3) For example, heart rate 120 (times / min), exercise time for one time 60 minutes , 30 minutes before exercise, 60 minutes after exercise, 10 minutes between exhalation gas sampling time, and 6 seconds for inhaling exhalation gas. The sample is collected and exercised at a heart rate of 120 (times / minute) for 60 minutes, and exhaled gas is collected every 10 minutes for 60 minutes after the exercise.

  Next, when an exercise start is input from the input unit 140, the determination in step 4 is YES. With this as a trigger, the heart rate (pulse rate) by the heart rate sensor (pulse sensor) 150 is measured and displayed on the glasses-type display device 110 (step 5). This value is used to determine whether the current exercise load is appropriate. If it is instructed to be higher than the heart rate (pulse rate), the exercise intensity is lowered, and conversely if instructed to be lower than the heart rate (pulse rate), the exercise intensity is Make adjustments so that This adjustment is performed as needed by looking at the displayed value of the heart rate (pulse rate).

  When, for example, 10 minutes have elapsed since the start of exercise for 30 minutes, “It is time to collect expiratory gas” is displayed on the glasses-type display device 110 (step 6), and preparation is made while continuing the exercise. Next, an expiration gas collection procedure is displayed on the glasses-type display device 110 (step 7). First, since “please exhale in XX seconds” is displayed on the glasses-type display device 110, exhale in the supported OO seconds. The time (seconds) counted from the start of sweeping is counted down by the timer 170 and displayed on the glasses-type display device 110.

  After expiration of the first period after the start of exhalation, a person's exhalation takes some time to reach the true exhalation gas that is exchanged in the lungs because there is gas in the mouth and airway gas During the second period, the analysis unit 32 analyzes the expired gas component. Therefore, when the start of the second period is detected from the output of the timer 170, the valve 24 is closed by the drive unit 25 and the analysis of the exhaled gas is started.

  When the expiration gas collection and analysis are completed, “Δ collection gas expired” is displayed on the glasses-type display device 110 (step 8), and the valve 24 is opened by the drive unit 25. Subject continues to exercise further. Meanwhile, in the breath gas analyzer 100, the CPU 130 calculates the fat burning amount from the acetone concentration in the breath gas (step 9), and displays “the fat burning amount is OO” on the glasses-type display device 110 (step). 10). By this display, the current amount of fat burning can be known, and the effect of exercise can be actually confirmed.

  As long as the expiration gas sampling is not finished (NO in Step 11) or the exercise continues (NO in Step 13), the expiration gas collection etc. (Steps 4 to 20) are repeated every 10 minutes, and finally When the exhalation gas sampling is completed (Yes in step 11), the total fat combustion amount analyzed so far is displayed on the glasses-type display device 110 (step 12). Is displayed. Further, when the exercise is completed (YES in step 13), “Exercise program is completed” is displayed on the glasses-type display device 110, and all the operations are completed (step 14).

  Those skilled in the art will readily appreciate that many variations are possible without substantially departing from the novel features and advantages of the present invention. Accordingly, all such modifications are intended to be included in the scope of the present invention. For example, a term described with a different term having a broader meaning or the same meaning at least once in the specification or the drawings can be replaced with the different term in any part of the specification or the drawings.

  1, 1A, 1B Expiratory gas sampling and analysis device, 10 sampling path (mouthpiece), 20A, 20B main body, 23 first discharge path, 24 valve, 25 drive unit, 26 second discharge path, 30 heat insulation change section, 31 separation Part (moisture adsorption part), 32 analysis part, 40 turbine, 41 housing, 41A flow path, 42 shaft, 43 turbine blade, 100 portable breath gas analyzer, 110 glasses-type display device

Claims (8)

A sampling channel for introducing and collecting exhaled gas;
An adiabatic change part that cools the exhaled gas introduced from the sampling channel by an adiabatic change;
A separation unit for separating moisture from the cooled exhaled gas;
An analysis unit for analyzing the exhaled gas from which moisture has been separated;
A breathing gas collection and analysis device characterized by comprising: In claim 1,
The adiabatic change part is:
A housing;
A plurality of turbine blades rotatably supported in the housing;
A breathing gas collecting and analyzing apparatus, characterized by being a turbine having In claim 2,
The expiratory gas collection and analysis apparatus, wherein the expiratory gas is introduced from the radial direction of the turbine blade and is a radial flow turbine that discharges the expiratory gas along the axial direction of the turbine blade. In claim 3,
The housing has a flow path for guiding and guiding the exhaled gas toward a radial direction of the turbine blade;
An expiratory gas collection and analysis apparatus characterized in that the cross-sectional area of the flow path decreases from the upstream side to the downstream side of the expiratory gas. In claim 3 or 4,
The exhalation gas collecting / analyzing apparatus according to claim 1, wherein the separation unit includes a moisture adsorbing unit disposed at a position facing the discharge end portion from which the exhalation gas is discharged from the turbine in the axial direction. In any one of Claims 1 thru | or 5,
A first exhaust path for exhausting exhaled gas in the sampling path to the outside by the expiratory pressure;
A valve for opening and closing a part of the first discharge path;
A valve drive unit for opening and closing the valve;
When the valve is closed, a second discharge path that discharges exhaled gas in the sampling path to the outside by the expiratory pressure;
Further comprising
The adiabatic gas collection and analysis apparatus, wherein the adiabatic change part, the separation part, and the analysis part are arranged in the second discharge path. In any one of Claims 1 thru | or 6,
The breathing gas collection and analysis apparatus, wherein the collection path includes a mouthpiece that is detachable from a main body on which the adiabatic change section, the separation section and the analysis section are provided. An exhalation gas collection and analysis apparatus according to any one of claims 1 to 7,
A glasses-type display device connected to the breath gas collection analyzer and displaying a breath collection procedure;
A portable breath gas analyzer characterized by comprising: