Abstract:
The oxygen and carbon dioxide content of expired respiratory gas is determined by measuring the mass and volume of the expired breath. From the composition of the inspired gas which may either be assumed or measured, the mass of the inspired volume may be determined, and since the inspired and expired breaths contain the same mass of nitrogen, the oxygen and carbon dioxide content of the expired breath may be determined. Measurements of temperature and humidity may be required to account for temperature and humidity changes between the inhalation and the exhalation or the inhaled gas may be adjusted in temperature and humidity to equalize the inhaled and exhaled temperature and humidity conditions. The mass and volume of the expiration and the volume mass of the inhalations are determined by an ultrasonic transit time system and a gas density sensor.

Description:
CROSS REFERENCE TO RELATED APPLICATIONS 
     This application is a continuation of U.S. patent application Ser. No. 09/674,897, filed Nov. 7, 2000 now U.S. Pat. No. 6,277,645, which is a 371 of PCT/US99/17553, filed Aug. 3, 1999, which claims the benefit of U.S. Provisional Patent Application Serial No. 60/095,092, filed Aug. 3, 1998. 
    
    
     FIELD OF THE INVENTION 
     This invention relates to a method and apparatus for indirect calorimetry employing respiratory gas analysis and more particularly to a method and system which determines the oxygen and/or carbon dioxide content of the expired gas using measurements of mass and volume of the expired gas and mass and volume of the inspired gas as measured by transit time of ultrasonic pulses passed through the gas. 
     BACKGROUND OF THE INVENTION 
     I have a number of patents on respiratory calorimeters. Some of these operate by integrating the flow volume of a number of inhalations and exhalations over a period of time and by subtracting the CO 2  volume in the exhalation from the integral of the exhaled volume by scrubbing the CO 2  and then subtracting the exhaled flow volume less the CO 2  volume from the inhaled flow volume to determine oxygen consumption during the period. I also have a pending application that measures both inspired and expired volume and either O 2  or CO 2  content to determine oxygen consumption. The carbon dioxide scrubber is bulky and requires replenishment after a number of uses. Carbon dioxide or oxygen analyzers are also relatively expensive. 
     It has previously been proposed to determine the mass of a gas flowing through a conduit by determining the transit time of ultrasonic pulses passed through the gas in a direction having a component along the axis of flow so as to determine the flow rate of the gas, and additionally determining the density of the gas. U.S. Pat. No. 2,911,825 discloses such a system in which the acoustic impedance of the gas is measured to determine the density. U.S. Pat. No. 5,214,966 similarly employs the transit time of ultrasonic pulses to determine the flow rate and determines the density of the flowing gas through measurement of the velocity of sound through the gas. U.S. Pat. No. 5,645,071 uses the transit time of ultrasonic pulses to determine the flow rate and additionally makes temperature measurements which, with the flow rate, allow the determination of mass of the flowing gas. This latter patent also suggests the application of this device to pulmonary function diagnostics and discloses an additional gas analyzing sensor for determining the carbon dioxide and/or oxygen content of the flowing gas on an on-line, real time basis. 
     It would be desirable to provide a method of analysis which allows the determination of oxygen consumption, carbon dioxide production and related and derived respiratory factors without the need for any gas analyzers, such as O 2  and CO 2  analyzers. This would result in a low cost, high precision instrument suitable for a wide range of health care applications. 
     SUMMARY OF THE INVENTION 
     Accordingly, the present invention is directed toward a method and apparatus for analyzing respiratory gases to determine oxygen consumption for indirect calorimetry purposes as well as CO 2  production and related respiratory factors, by measuring the mass and flow volume of expired gas without the need for additional analysis of the oxygen or CO 2  content of the expired gas, through use of measurements of the inhaled gas. In its simplest form, in which the constituents of the inhaled gas are known with sufficient precision, as is the case when the subject is breathing ambient air, and the temperature and humidity of the inspired and expired gases are the same as a result of passage through an artificial nose or the like, or are measured or assumed, the O 2  and CO 2  contents of the exhaled gases may be determined from measurements of the inhaled and exhaled flow volumes and the mass of the exhaled gases. Alternatively, the mass of the inhaled gas will also be measured. The measurements are preferably made by a subject breathing through the apparatus of the present invention for five to ten minutes with the measurements of the inhalations and exhalations being integrated over those periods. 
     To understand the method of the present invention and the system for implementing it, assume that the subject is breathing ambient air which has a composition of 79% nitrogen, 21% oxygen and 0.03% CO 2 . By measuring the flow volume of the inhalations over the test period, the inhaled mass may be determined. Assuming that the exhalations are at the same humidity and temperature as the inhalations, from measurements of the integrated mass and flow volume of the exhalations the CO 2  and O 2  contents of the exhalations may be determined since the nitrogen content of the inhalations and exhalations will be the same, leaving only two unknowns, and after equalization for the differential in volumes between the inhaled gas the exhaled gas, the mass of the exhaled gas will vary linearly as a function of its CO 2  and O 2  content. The determination of the O 2  and CO 2  content of the expired volume is possible because CO 2  has a substantially higher density than O 2  and moles of O 2  and CO 2  occupy the same volume so that substitution of CO 2  in the exhaled gas for O 2  in the inhaled gas changes the gas mass but not the volume. 
     The system of the present invention preferably makes the flow measurements of the inhaled and exhaled volumes with known ultrasonic pulse transit time techniques and determines gas density with measurements such as acoustic impedance, speed of sound, or temperature. The same apparatus can measure the masses and flow volumes of the inhaled and exhaled gases. 
    
    
     BRIEF DESCRIPTION OF THE DRAWINGS 
     The invention will be further described in conjunction with the accompanying drawings, in which: 
     FIG. 1 is a perspective drawing of a preferred embodiment of the invention, being used by a subject to allow determination of the subject&#39;s respiratory parameters; 
     FIG. 2 is a cross sectional view of the flow tube forming part of the preferred embodiment of the invention, illustrating the associated electronics in block form; 
     FIG. 3 is a schematic drawing of an alternative embodiment of the invention; and 
     FIG. 4 is a drawing of an ultrasonic transducer capable of measuring the acoustic impedance of the flowing gas. 
    
    
     DETAILED DESCRIPTION OF THE PREFERRED EMBODIMENTS 
     Referring to FIG. 1, a preferred embodiment of the invention comprises a calorimeter, generally indicated at  10 , having a mask  12  formed at one end which is adapted to engage the face of a user  14  so as to cover the nose and mouth. The mask connects via a conduit  16  to a test body  18  incorporating a flow tube  20 . One end of the flow tube  20  connects to the ambient air. As the user  14  inhales during a breathing test, which may last from two to ten minutes, ambient air is drawn in, passes through the flow tube  20  and to the user  14  through the mask  12 . As the user exhales, air moves from the mask  12 , through the conduit  16 , through the flow tube  20 , to the ambient air. In alternative embodiments of the invention, the source and sink for the respiratory gases may be conditioned air as used in forced respiratory apparatus. 
     A cable  22  connects to the test body  18  and carries electrical signals between the test body and a computation unit  24 . The computation unit preferably includes a display  26  which may be switched to display the various results of the test and instructions to the user such as “start test” and “stop test.” The flow tube  20  and the mask  12  are preferably formed as a disposable unit so that they may be replaced between uses for hygienic purposes. The balance of the system including the test body  18  and computation unit  24  are preferably reusable. The breath under test only passes through the disposable portions of the system. 
     FIG. 2 illustrates the disposable flow tube  18  in cross section. The flow tube and its associated components are of the type illustrated in U.S. Pat. No. 2,911,825 which is operative to calculate the flow rate of the inhaled and exhaled respiratory gases through the tube  18  and to calculate the density of the gases via a determination of the acoustic impedance of the flowing gases. As illustrated in FIG. 2, the left end of the flow tube  18  connects to the atmosphere so that ambient air is drawn into the flow tube when the user inhales and exhaled air is returned to the ambient. The right hand end of the flow tube connects to the mask  12 . Thus, inhalations pass through the tube to the right and exhalations pass through the tube  18  to the left. 
     A pair of piezoelectric crystals  30  and  32  are mounted on opposite sides of the flow tube  18  at an angle to the central axis of the flow tube so that they face one another and ultrasonic pulses may be sent from the crystal  30  to the crystal  32  in the direction of the arrow  34 . Similarly, a pair of crystals  36  and  38  are supported on opposite sides of the tube so that they face one another, at an angle to the central axis of the tube, in the direction of the arrow  40 . Electrical connections are made from each of the crystals to an electronic control and computation circuit  42  which may be generally of the type illustrated in FIG. 1 of U.S. Pat. No. 2,911,825. 
     Additionally, another piezoelectric crystal transducer  52  is mounted in a wall of the flow tube  18  so as to contact the gases flowing through the tube. Signals from the transducer  30  are also provided to the computation and control unit  42 . Essentially, the control unit controls the crystals  30  and  36  to transmit ultrasonic pulses to the crystals  32  and  38  respectively. The circuitry for generating the pulses and to receive the detected pulses is contained in the unit  42 . Since the time of flight of these pulses between the transmitting and receiving crystals is a function of their separation and the rate of flow of gases through the tube, the flow rate may be calculated as a function of the difference between the transit times of the pulses between the two sets of crystals. 
     The transducer  52  forms one part of a resonance circuit controlled by an oscillator in the unit  42 . The frequency of the oscillator is adjusted until the transducer  30  is tuned to series resonance and the voltage drop across the transducer  52  is measured by circuitry contained in the unit  42 . This voltage is a measure of the acoustic impedance of the fluid. The density of the fluid is equal to the acoustic impedance divided by the wave propagation velocity through the fluid as fully explained in U.S. Pat. No. 2,869,357. Thus, the computation unit receives signals proportional to the flow rate of gases through the flow tube and the density of those gases and the mass can be calculated. Since the interior diameter of the flow tube  18  is known, the flow volume may be calculated. 
     The computation unit  42  thus measures the flow volume of the inhalations, the flow volume of the exhalations, and the mass of the exhaled volume. 
     The unit may incorporate a conventional artificial nose  60  which passes both the inhalations and exhalations and accumulates moisture from the exhalations and generally equalizes the temperature and humidity of the inhalations and exhalations. Alternatively, these temperatures and humidities may be measured or they may be conditioned by active elements such as a thermistor and humidifier. 
     Assuming that the temperature and humidity of the inhalations and exhalations are equal, the O 2  and CO 2  composition of the exhalation may easily be computed. The mass of the exhalations is first equalized on the basis of the flow volumes of the inhalations and exhalations. The mass of nitrogen in the inhalations is computed and that mass is subtracted from the mass of the exhaled gas. The remaining mass composed of O 2  and CO 2  and the mass will vary linearly depending on the proportions of those components so they can be computed or determined from a look-up table. The remaining mass is linearly related to the percentages of CO 2  and O 2  in the exhalation. 
     FIG. 2 illustrates the flow tube and associated circuitry of a second embodiment of the invention which uses the method and apparatus disclosed in U.S. Pat. No. 5,214,966 for the determination of the flow velocity and the sound velocity of the respiratory gases passing through the flow tube. The mass of the flowing gas may be calculated using the flow velocity and the sound velocity in the manner set forth in that patent. The flow tube  80  of the second embodiment of the invention is U-shaped with two legs  82  and  84  extending parallel to one another and at right angles to a central connecting section  86 . The leg  82  connects the central section  86  to a source and sink for respiratory gases which is preferably the ambient air. The leg  84  connects the other end of the section  86  to the mask  12  illustrated in FIG. 1 or another respiratory connector such a mouthpiece. 
     A first ultrasonic transducer  88  is disposed in the wall of the tube  80  at one end of the connecting section  86  in direct opposition to a second ultrasonic transducer  90  which is disposed at the opposite end so that the two face one another. Each of the two transducers  88  and  90  is formed with a piezoelectric crystal acting as both a transmitter and receiver of ultrasonic pulses. The transducer  90 , which is illustrated in detail in FIG. 4, is especially designed for measuring the density of the gases flowing through the flow tube  80 . As illustrated in FIG. 2, the transducer  90  consists of a piezoelectric transducer  92 , a first block  94  of a material having an acoustic impedance Z 0  and a length X 0 , and a second block  96  having an acoustic impedance Z 1  and a length X 1 . The two blocks  94  and  96  are disposed in such a manner that an ultrasonic pulse transmitted from the crystal  92  will transverse the two blocks  94 ,  96  before reaching the gas. The first block  94  being disposed between and in contact with the crystal  92  and the second block  96 , and the second block  96  is disposed between and in contact with the first block  94  and the gas flowing through the tube  80 . The two transducers  88  and  90  are connected to a computation and control unit  100  which contains control and computation electronics. The unit  100  includes sing-around electronic circuitry of a well known type and includes a microprocessor that calculates the flow velocity of gases passing through the section  86  of the flow tube  80 . 
     Simultaneously, the signals from the crystal  90  are used to determine the density of the gas flowing through the section  86  based on the reflection of pulses generated by the transducer  92  from the interface between the crystals  94  and  96 , the interface between the crystal  96  and the flowing gas, and the amplitude of those reflections. This is all done in the manner described in U.S. Pat. No. 5,214,966 and will not be repeated. Again, the mass of the exhalations may be calculated from the integrated flow volume density measurements. The flow volume of the inhalation may also be computed and used along with the exhaled volume to analyze the mass reading. The normalized mass will be a function of its complementary O 2  and CO 2  constituents. 
     In another embodiment only the expired mass and volume are measured. The expired O 2  concentration [O 2 ] e  and the expired CO 2  concentration [CO 2 ] e  are calculated from the expired mass and volume, and, knowing the inspired O 2  concentration [O 2 ] i , then V o     2    is calculated by the following formula:          V     O   2       =         1   -       [     O   2     ]     e     -       [     CO   2     ]     e         1   -       [     O   2     ]     i         ×     (         [     O   2     ]     i     -       [     O   2     ]     e       )                   Ve   ×   k                            
     where k is a non-adiabatic correction constant to compensate for the non-ideal nature of the gases, determinable from the van der Waals equation. 
     The expired volume Ve is a summation of partial volumes attributable to each of the constituent gas making up the expired volume. Since the inhaled oxygen concentration is known or determinable independent of the present invention, the volume of oxygen in the exhalant is related to the exhalant mass change associated with the molar concentrations of oxygen and carbon dioxide relative to inhalant gas. CO 2  volume is calculated as: 
     
       
           V   CO     2     =[CO   2 ] e   ×Ve   
       
     
     Where Ve is the total expiration volume.