METHOD AND APPARATUS FOR INTELLIGENT FLOW SENSORS

Abstract

A single sensor capable of detecting both airflow in spirometry and the full range of sound frequencies needed to track clinically relevant breath sounds is provided. The airflow sensor includes a movable flap with one or more integrated strain gauges for measuring displacement and vibration. The airflow sensor is inherently bidirectional. The sensor is an elastic flap airflow sensor that is capable of detecting data needed for both spirometry and auscultation measurements. The sensor is sterilizable and designed for the measurement of human respiratory airflow. The sterilizable sensor is also suitable for non-medical fluid flow metering applications. Additional devices such as sensors for the ambient level of various chemicals, sensors for temperature, sensors for humidity and microphones, may be affixed to the flap. When the strain gauge is placed in a conventional Wheatstone bridge configuration, the sensor can provide the airflow measurements needed for medical spirometry.

Claims

1. A fluid flow sensing system comprising: a housing having a chamber that is sized and dimensioned to allow fluid to pass therethrough; a flap provided within the chamber, wherein the fluid causes the flap to move when the fluid passes thereover; a sensor coupled to the flap for generating an output signal when the flap moves, wherein: the sensor is configured to sense a displacement of the movable flap and a vibration of the movable flap, the displacement of the movable flap is representative of a flow rate associated with the fluid and the vibration of said movable flap is representative of a frequency associated with the fluid; and a determining unit that is configured to receive the output signal of the sensor and in response thereto, determine flow rate data associated with the fluid and determine frequency data associated with the fluid.

2. The system of claim 1 wherein the fluid comprises air, the flow rate is an air flow rate and the frequency is a sound.

3. The system of claim 1 wherein the sensor is a piezoresistive sensor.

4. The system of claim 3 wherein the piezoresistive sensor comprises first and second piezoresistive circuits and the first and second piezoresistive circuits are substantially perpendicular to each other.

5. The system of claim 4 wherein the first and second piezoresistive circuits have a resistance of about 120 ohms.

6. The system of claim 1 wherein the sensor is a strain gauge.

7. The system of claim 1 wherein the determining unit further comprises: a voltage conversion unit for receiving the output signal of the sensor and converting said the output signal into a voltage output signal; and an amplification unit for receiving the voltage output signal and generating an amplified voltage output signal.

8. The system of claim 2 wherein the determining unit further comprises: a voltage conversion unit for receiving the output signal of the sensor and converting the output signal into a voltage output signal; an amplification unit for receiving the voltage output signal and generating an amplified voltage output signal; an air flow rate determining unit for receiving the amplified voltage output signal and determining in response thereto the air flow rate data based at least in part upon the output signal of said sensor; and a sound determining unit for receiving the amplified voltage output signal and generating in response thereto the sound data signal representative of the sound.

9. The system of claim 8 wherein the air flow rate determining unit further comprises: a converter for converting the amplified voltage output signal into a digital output signal; and a calculation unit for determining the air flow rate of the air based upon the digital output signal.

10. The system of claim 9 wherein the calculation unit includes a calibration curve that correlates the digital output signal to an air flow rate.

11. The system of claim 8 wherein the sound determining unit comprises: a sound processing unit for generating the sound data signal in response to the amplified voltage output signal, and a frequency conversion unit for receiving the sound data signal and in response thereto converting the signal into a frequency signal.

12. The system of claim 11 wherein the sound processing unit includes a sound card.

13. The system of claim 11 wherein the frequency conversion unit includes a fast fourier transform module.

14. The system of claim 1 wherein the output signal of the sensor has a direct current electrical component that represents the flow rate associated with the fluid and a high frequency alternating current component that represents the frequency associated with the fluid.

15. A method for determining a flow rate and a frequency of a fluid, the method comprising: providing a sensor coupled to a flap, wherein the sensor is configured to generate an output signal in response to detecting movement of the flap moves; providing a flow of fluid across the sensor; sensing a displacement of the flap with the sensor, said displacement being representative of a flow rate associated with the fluid flow; sensing a vibration of the flap with the sensor, the vibration being representative of a frequency associated with the fluid flow; generating the output signal from the sensor; and determining from the output signal the flow rate and frequency associated with the fluid flow from the sensed displacements and the sensed vibrations respectively.

16. The method of claim 15 wherein the steps of sensing both a displacement and a vibration of said flap occur simultaneously using the sensor.

17. The method of claim 15 wherein: the fluid comprises air; the flow rate is an air flow rate; the frequency is a sound; and the determining step further comprises: determining the air flow rate based at least in part upon said output signal of the sensor, and generating the sound representative of the sound associated with the air based at least in part upon said output signal of the sensor.

18. The method of claim 17 wherein the determining step further comprises: converting the output signal into a voltage output signal; generating an amplified voltage output signal from the voltage output signal; determining the flow rate based on the amplified voltage output signal; and determining the frequency based on the amplified voltage output signal.

19. The method of claim 18 wherein: determining the flow rate further comprises converting the amplified voltage output signal into a digital output signal, and determining the airflow rate based upon the digital output signal; and determining the frequency further comprises: generating a frequency data signal based on the amplified voltage signal; and converting the frequency data signal into a frequency waveform.

Description

BRIEF DESCRIPTION OF THE DRAWINGS

[0023] The accompanying drawings, which are incorporated in and constitute part of this specification, illustrate embodiments of the invention and together with the description, serve to explain the principles of the invention. The embodiments illustrated herein are presently preferred, it being understood, however, that the invention is not limited to the precise arrangements and instrumentalities shown, wherein:

[0024] FIG. 1 is a graphical depiction of a conventional spirometry flow-volume loop;

[0025] FIG. 2A is a schematic view of a conventional Fleisch-type pneumotachometer;

[0026] FIG. 2B is a schematic view of a conventional Lilly-type pneumotachometer;

[0027] FIG. 2C is a schematic view of a conventional device for performing FOT or IOS techniques;

[0028] FIG. 3 is a general block diagram view of a system for measuring airflow and breath sounds according to the techniques of the present invention;

[0029] FIG. 4A is a schematic depiction of an exemplary airflow sensor according to an exemplary embodiment of the present invention;

[0030] FIG. 4B is a graphical depiction of an exemplary mode analysis examining the effect of Young's modulus on the frequency of a first vibrational mode of an exemplary sensor and according to the teachings of the present invention;

[0031] FIG. 4C is a graphical depiction of the effects of a tapered design during bending of an exemplary flap used in the system of FIG. 3 according to the teachings of the present invention;

[0032] FIG. 4D illustrates an exemplary sensor mounted on a tapered surface according to an exemplary embodiment of the present invention;

[0033] FIG. 4E illustrates an exemplary pair of symmetric sensors mounted on a tapered surface according to an exemplary embodiment of the present invention;

[0034] FIG. 5 is a perspective view of a device that captures spirometry data and breath sounds simultaneously according to the teachings of the present invention;

[0035] FIG. 6A is a schematic depiction of an exemplary FOT or IOS device that employs a piezoresistive airflow sensor and a pressure sensor according to the teachings of the present invention;

[0036] FIG. 6B is a schematic depiction of another exemplary FOT or IOS device that employs only the piezoresistive airflow sensor according to the teachings of the present invention;

[0037] FIGS. 7A-7C are a schematic block diagram of a system where the airflow measuring device of the present invention is used to gather and analyze spirometry data and breath sounds simultaneously;

[0038] FIG. 8A illustrates an exemplary three dimensional plot representing auscultation data gathered using the airflow measuring device of the present invention;

[0039] FIG. 8B illustrates an exemplary spirogram representing spirometry data gathered using the airflow measuring device of the present invention;

[0040] FIG. 8C illustrates expiratory and inspiratory recordings from a sound card according to an exemplary embodiment of the present invention;

[0041] FIGS. 9A-9B is a graphical depiction showing a comparison between data gathered using an airflow sensor according to the teachings of the present invention and simultaneous data gathered using a conventional Pulmonary Waveform Generator (PWG); and

[0042] FIG. 10 is a flowchart of steps illustrating an exemplary method of simultaneously gathering spirometry and auscultation data using the airflow sensor of the present invention according to an exemplary embodiment of the present invention.

DETAILED DESCRIPTION

[0043] Present invention provides an airflow sensor that is capable of measuring bidirectional airflow of a patient, as well as clinically relevant breath sounds associated therewith. Breath sounds include sounds that are associated with inhalation and exhalation of humans and/or animals. Specifically, the airflow sensor used according to the teachings of the present invention is capable of simultaneously detecting auscultation data and airflow data. The airflow sensor generates an output signal in response to the presence of airflow. The generated output signal is representative of both the airflow data including airflow rate, and the breath sound data associated therewith.

[0044] According to various embodiments of the present invention, a single sensor is provided for sensing both the airflow in spirometry and the full range of sound frequencies needed to track clinically relevant breath sounds in auscultation. Any suitable type of sensor can be used provided it is capable of sensing both airflow and breath sounds while simultaneously providing an appropriate output signal that is representative of or can be correlated to the patient's airflow and breath sounds. Examples of sensors suitable for this purpose include strain gauges and piezoresistive or piezoelectric sensors. According to a preferred embodiment, the present invention employs a thin film sensor mounted in an airflow chamber. The thin film sensor may be a piezoresistive sensor that is sensitive to bending. An amplified signal output from the sensor consists of a direct current (DC) electrical component that measures airflow (spirometry) and a high frequency alternating current (AC) audio component that is representative of sound from the lungs (auscultation) during the inhalation and exhalation cycles of respiration.

[0045] Particular implementations of the present invention may provide one or more of the advantages provided herein. The airflow sensor described in the present application not only overcomes the above-listed limitations of conventional spirometers but also provides the simultaneous, direct sensing or detection of sound from the airway. The piezoresistive airflow sensor of the present invention may also be used in connection with the conventional FOT or IOS instrumentation to replace the pneumotachometer airflow sensors. Thus, it is possible to produce FOT or IOS instruments at lower cost. Replacing the pneumotachometer of the conventional FOT or IOS instrumentation with the piezoresistive airflow sensor of the present invention results in a more stable, portable, easier to use and easier to maintain FOT or IOS device. The simpler design and greater stability in the FOT or IOS device afforded by the present invention allows the FOT or IOS device to enter the mainstream of clinical medicine.

[0046] FIG. 3 is a schematic block diagram of a system 300 for generally measuring, collecting, analyzing, processing and/or gathering airflow and sound data. If configured for task-appropriate data analysis, the system 300 may be used for any of spirometry, FOT or IOS. The system 300 includes the sensor 304 of the present invention. The sensor 304 is connected to a source of airflow 302 to be analyzed. The airflow can be provided, for example, by a patient. The sensor 304 may be provided in a mouthpiece that allows measuring characteristics of the air flowing in and out of the lungs of the source of airflow 302. The readings of the sensor 304 may be sent to a computing device or system 306 for further analysis. The computing device 306 may include one or more processors, one or more storage devices, or one or more filters or other associated processing circuitry, and a display device. The various components of the computing device 306 can be located in a single location or can be distributed throughout the system 300. The illustrated computing device processes the output signal generated by the sensor 304 and is capable of determining the airflow rate and breath sounds associated with the source 302.

[0047] FIG. 4A is a general schematic depiction of an exemplary sensor 304 according to one embodiment of the present invention. Specifically, FIG. 4A illustrates a piezoresistive sensor 402 that has two orthogonal piezoresistive circuits 404, 406 for measuring both sound and spirometry data. The resistance of both circuits may be about 120 ohms. The inner circuit 404 may be sensitive to spirometry data while the outer circuit 406 may be sensitive to high frequency sounds. The sensor 304 of the present invention may be sensitive to sounds with frequencies between about 1 Hz and about 1000 Hz. Preferably, the sensor 304 of the present invention is sensitive to sounds with frequencies between about 35 Hz and about 1000 Hz. A plurality of pads 408 are provided at a lower end of the sensor 402 for connecting the sensor 402 to other system circuitry. The piezoresistive sensor 402 illustrated in FIG. 4A is provided for illustrative purposes only and should not be construed in a limiting sense. The sensor 304 of the present invention may also employ a single piezoresistive circuit that is sensitive to both spirometry data and high frequency sounds.

[0048] The sensor 402 used in the present invention may consist of a grid of metallic wire bonded to polyimide or polymer films such as polyethylene terephthalate (PET), nylon, polypropylene or polyethylene. The metallic wire may be made of constantan, i.e. a copper-nickel alloy consisting of about 55% copper and 45% nickel. Constantan has a resistivity that is constant over a wide range of temperatures. Alternatively, the metallic wire may be made of gold, chromium, aluminum, etc. Aluminum or steel has much less flexibility than constantan.

[0049] The piezoresistive sensor 402 may be constructed by deposition techniques, for example, vacuum deposition, electroplating, and printing procedures familiar in the semiconducting fabrication field. FIG. 4A illustrates an exemplary pattern of constantan deposited on polyimide for measuring strain in two perpendicular directions. As provided above, the sensor 402 of the present invention may be formed by depositing constantan in polyimide in a single direction. The metallic wire may be deposited on polyimide using E-beam or sputtering deposition techniques. Photolithography mask, shadow masks, and electrophotographic imaging may be used in conjunction with E-beam deposition techniques in manufacturing the strain gauge. Optionally, various coatings may be applied to the strain gauge for protecting the circuit from oxidation or water aging.

[0050] Conventionally, a polyimide-backed strain gauge is used to measure the strain of a carrier medium such as a piece of aluminum, or steel, to which the polyimide flap is glued. When the carrier medium is strained, the length of the grid changes, which causes a change in the electrical resistance. A Wheatstone bridge may used to monitor the change in resistance and produce an output voltage proportional to the strain in the carrier medium.

[0051] Contrary to the conventional strain gauges where the gauge is glued directly onto the carrier medium, in producing the airflow sensor of the present invention, the sensor is attached to the carrier medium at one end. Thus, the sensor becomes integrated with a bendable flap. In the present invention, the polyimide flap itself is the target of the measurement.

[0052] According to various embodiments of the present invention, Kapton may be used as the carrier medium for the sensor. Kapton is a polyimide film that remains stable in a wide range of temperatures, i.e. from 269 to +400 C. (452 to 752 F.). FIG. 4B illustrates a mode analysis examining the effect of Young's modulus on the frequency of the first vibration mode of the sensor using a one dimensional model. FIG. 4B further illustrates the thickness of a backing required to obtain a 1.5 cm deflection. For a given pressure, stiff materials, such as steel, need to be very thin. For such materials the frequency of the first vibration mode is high. Softer materials, such as rubber, have a lower frequency but are generally thicker. Thicker materials are desirable since a larger signal is observed from the sensor. The present inventors have realized that a reasonable compromise between the two extremes is found where the two curves intersect on FIG. 4B. The intersection point illustrates the properties of Kapton.

[0053] Kapton is a polymer that has a glass transition temperature of greater than 350 C., a coefficient of thermal expansion of 1210.sup.6/ C., and a RMS surface roughness of approximately 30 nm for the film. Kapton polyimide films have low shrinkage properties, i.e. a 75 m thick foil shrinks approximately 0.04% after about 2 hours at about 200 C. The film has a relatively low humidity expansion coefficient of 910.sup.6/% RH, a water permeability of 4 g/m.sub.2/day, oxygen permeability of 4 cm.sub.3/m.sub.2/day, and water absorption of 2.4%. The bulk modulus of Kapton E is 780 Kpsi.

[0054] However, the use of Kapton in accordance with the present invention is for illustrative purposes only and should not be construed in a limiting sense.

[0055] According to various embodiments of the present invention, the flap 450 may be a tapered surface. FIG. 4C graphically depicts the performance of the flap with and without a taper. Specifically, the graphical lines illustrate how the side profiles of the flaps bend under pressure. A positive taper can be used in connection with the present invention. A flap with a positive taper has a fixed end that is thicker than the free end. A flap with a negative taper has a free end that is thicker than the fixed end. During bending, the maximum curvature that is proportional to change in resistance occurs at the fixed end. As illustrated in FIG. 4C, larger signals are generated using a flap with a positive taper rather than using a flap with no taper.

[0056] FIG. 4D illustrates an exemplary sensor 402 mounted on or affixed to a tapered surface 414 of the flap 450 according to an embodiment of the present invention. The flap 450 formed according to FIG. 4D may be used in a device to detect and/or capture spirometry data and breath sounds simultaneously. Such an exemplary device is illustrated in FIG. 5. The flap 450 may also be used in connection with FOT or IOS devices, as illustrated in FIGS. 6A-6B.

[0057] FIG. 4E illustrates an alternative exemplary sensor, in particular a symmetric sensor 460. In this sensor, substrate 462 is coated with metal 464 on both sides of the flap. Coating 468 may then be applied to provide further structural integrity and protection for the deposited metal. Ideally, this sensor is completely balanced, positionally, on the flap substrate, i.e. the metal is deposited symmetrically with regard to side-to-side and front-to-back dimensions. Pads 466 are provided for electrical connection to the sensor. The metal of this sensor may be deposited by any of a number of techniques such as sputtering, e-beam, and thermal evaporation. Symmetric sensors may be more reliable than non-symmetrical sensors, for example where elastic stretching of the flap occurs in response to air pressure, whereby measurement by a single sensor, placed on one side of the flap may be distorted. This is particularly so where multiple axes of stretching and bending of the flap are caused by the airflow. This is so in both the case of using either a single sensor or array of sensors on one side of the flap. Greater accuracy may therefore result with a symmetrical sensor in which the signal from the piezoresistive element(s) on the up-wind side, which are subject to both bending stretch and longitudinal stretch, are compared with signals from a piezoresistive element(s) on the opposite side of the flap, which may not be subject to each and every stretching component. Alternatively, or in combination, the sensed signals from the back-side sensor(s) may at least be used to compensate for such stretching through comparative signal analysis.

[0058] FIG. 5 illustrates an exemplary airflow sensing device 500 that captures spirometry data and breath sounds simultaneously. The device 500 includes an airflow chamber 502 attached to a mouthpiece 504. The airflow chamber 502 is illustrated as a rectangular chamber in FIG. 5 for illustrative purposes only. Those of ordinary skill in the art will readily recognize that the airflow chamber 502 may have any suitable shape, length or size, including but not limited to a circular chamber. The flap 450 includes a thin film sensor 402 and is provided within the airflow chamber 502. As illustrated, the flap 450 is mounted to a wall of the chamber and extends outwardly therefrom into the chamber 502. The flap 450 is positioned so as to be transverse or perpendicular to the direction of airflow, indicated by arrow A.

[0059] As illustrated in FIG. 4D, the flap 450 can have a positive or a negative taper. Specifically, the airflow sensing device 500 simultaneously measures the airflow by measuring the displacement of the flap 450 and the sound by measuring the vibration of the flap 450. The device 500 may be used in diagnosing and monitoring lung diseases or conditions that are associated with changes in spirometry values and characterized by abnormal lung sounds.

[0060] According to an exemplary embodiment, the device 500 may be used by a patient to analyze the spirometry and auscultation data. The patient breaths into device 500 through the mouthpiece 504. The inhalation or the exhalation of the patient creates an airflow in the direction A illustrated with the arrow in FIG. 5. The airflow displaces and vibrates the flap 450 in the airflow chamber 502. The displacement and the vibration of the flap 450 are sensed by the sensor (not shown) provided on the flap 450. The sensor generates an output signal that represents data associated with the displacement and the vibration of the flap 450. The data associated with the displacement of the flap 450 is used to measure airflow characteristics for spirometry analysis. The data associated with the vibration of the flap 450 is used to measure breath sound characteristics for auscultation analysis. The processing of the output signal is illustrated in FIGS. 7A-7C and is discussed below.

[0061] As indicated above, the flap 450 of the present invention may also be used in connection with FOT or IOS devices, as illustrated in FIGS. 6A-6B. FIG. 6A illustrates an airflow sensing device 602 for FOT or IOS applications. The sensing device 602 includes an exemplary piezoresistive sensor 304 according to an embodiment of the present invention. The piezoresistive sensor is coupled to the flap 450 and is similar to the flap 450 illustrated in FIGS. 4D and 5. The piezoresistive sensor 304 replaces the pneumotachometer 216 and the flow transducer 224. Pressure transducer 604 may employ different technology than pressure transducer 226 of the conventional FOT or IOS device 206.

[0062] The piezoresistive sensor 304 of the present invention functions as one branch of the Wheatstone bridge from which the voltage output feeds into an analogue-digital converter incorporated into the digital signal processor 228. The digital signal processor 228 may also include the Wheatstone bridge and amplifiers. The piezoresistive sensor-based FOT or IOS device 602 is capable of the full range of measurements that can be performed with the conventional FOT or IOS device 206. In addition, according to various embodiments of the present invention, the piezoresistive sensor-based FOT or IOS device 602 is capable of measuring impulse frequencies greater than 50 Hz, for example frequencies up to 1000 Hz. The piezoresistive sensor-based FOT or IOS may measure impulse frequencies between about 1 Hz and about 1000 Hz. More preferably, the piezoresistive sensor-based FOT or IOS may measure frequencies of between about 35 Hz and about 1000 Hz. The piezoresistive sensor-based FOT or IOS device 602 is less expensive to build and maintain, more rugged and portable, easier to clean, and simpler to operate than the conventional FOT or IOS device 206.

[0063] According to an illustrative example, the FOT or IOS device 602 may be used by a patient for collecting data for FOT or IOS applications. The patient may breath through the mouthpiece 218 provided at one end of the FOT or IOS device 602. The breathing generates airflow in the direction of the arrow A, as illustrated in FIG. 6A. The flap 450 including the sensor 304 of the present invention is provided in a direction substantially perpendicular to the direction of the airflow. The airflow causes the flap 450 to move and vibrate. The sensor 304 provided on the flap 450 senses the movement, i.e. displacement, and vibration of the flap 450. The sensor 304 generates an output signal that is representative of the displacement data and the vibration data of the flap 450. The displacement data is correlated with the airflow characteristics, such as airflow rate, of the airflow. The vibration data is correlated with the breath sound characteristics associated with the airflow. The output signal of the sensor 304 is then sent to digital signal processor 228 and a computer 232 for further processing. The processing of the output signal is discussed below in connection with FIGS. 7A-7C. FOT or IOS device 602 also includes a pressure sensor 604 that collects pressure data generated by the airflow. The pressure data is also sent to the computer 232 for processing. The pressure data collected by the pressure sensor 604 may be used for calculating impedance of the respiratory flow.

[0064] According to various embodiments of the present invention, the sensor 304 of the present invention may be used to measure the response of the airway to perturbations other than the series of short pressure pulses used in IOS and continuous waves in FOT.

[0065] The sensing device 606 illustrated in FIG. 6B is a simpler version of the device 602 illustrated in FIG. 6A in that it does not include the pressure sensor 604. The piezoresistive sensor 304 of the FOT or IOS device 606 may detect airflow velocity and, therefore, differences in pressure. Accordingly, the impedance of the respiratory flow may be calculated using the data from the piezoresistive sensor 304 provided in the FOT or IOS device 606. In the sensing device 606, the pressure may be measured using the sensor 304. That way, the sensing device 606 is capable and adapted to measure the impedance inside the airway 610, for example at a central point of the airway 610. The measurement of impedance is more accurate when the measurement is taken at a location closer to the air source. Accordingly, the sensing device 606 of FIG. 6B may provide better and more accurate measurements compared to the device 206 illustrated in FIG. 2C.

[0066] The FOT or IOS device 606 can be used for the calculation of impedance of the spontaneous breathing and the superimposed impulse signal. Using the FOT or IOS device 606, it is possible to determine the phase, frequency, and signal strength at two physical points, i.e. the sensor 304 and the loudspeaker 230. The sensor and/or the flap 450 may contain additional elements such as additional parallel and/or perpendicular strain gauge sensor 402. The additional elements of the sensor 304 may detect additional data streams from detectors such as flexible membrane pressure sensors. According to an illustrative example, the FOT or IOS device 606 may be used by a patient for collecting data for FOT or IOS applications. The patient may breath through the mouthpiece 218 provided at one end of the FOT or IOS device 606. The breathing generates airflow in the direction of the arrow A, as illustrated in FIG. 6B. The flap 450 including the sensor 304 of the present invention is provided in a direction substantially perpendicular to the direction of the airflow. The airflow causes the flap 450 to move and vibrate. The sensor 304 provided on the flap 450 senses the movement, i.e. displacement, and vibration of the flap 450. The sensor 304 generates an output signal that is representative of the displacement data and the vibration data of the flap 450. The displacement data is correlated with the airflow characteristics, such as airflow rate, of the airflow. The vibration data is correlated with the breath sound characteristics associated with the airflow. The sensor 304 of the FOT or IOS device 606 may also sense a pressure differential caused by the airflow. Therefore, the output signal of FOT or IOS device 606 may also represent the pressure data associated with the airflow. The output signal of the sensor 304 is sent to digital signal processor 228 and a computer 232 for further processing. The processing of the output signal is discussed below in connection with FIGS. 7A-7C.

[0067] According to various embodiments of the present invention, the piezoresistive circuits 404 and 406 may be used in combination for phase calibration allowing quadrature detection. Semiconductor pressure sensors may also be incorporated in the base of the sensor 304 that may be used for reference.

[0068] FIG. 7A illustrates an exemplary sensing system 700 where the sensor 304 of the present invention is used to gather and analyze spirometry data and sound data associated with the airflow simultaneously. The sensor 304 outputs a signal x 730 that represents two sets of data simultaneously, i.e. the spirometry data x1 (732) and the sound data associated with the airflow x2 (734). The output x of the sensor 304 is sent to a voltage conversion unit 702. According to an embodiment of the present invention, the voltage conversion unit 702 may be a Wheatstone bridge. The output of the voltage conversion unit 702 is then sent to an amplification unit 704, such as an amplifier. The output of the amplifier represents two sets of converted and amplified data, i.e. the spirometry data x1 (732) and the sound data associated with the airflow x2 (734).

[0069] The spirometry data x1 (732), i.e. the displacement of the flap 450 carrying the sensor 304, may be provided to an airflow rate determining unit 706. The output x3 (736) of the airflow rate determining unit 706 represents the airflow data, i.e. the spirometry data. The sound data x2, i.e. the vibration of the flap 450 carrying the sensor 304, may be provided to a sound determining unit 708. The output x4 of the sound determining unit 708 represents the sound data, i.e. the auscultation data. The airflow determining unit 706 and the sound determining unit 708 may be a part of a determining unit 710. The determining unit 710 may include a processor 714 for performing various computations and analysis using the output x of the sensor 304. The determining unit 710 may also include a memory 712 for storing the airflow data, the sound data and/or the results of the analysis performed on the airflow data and/or the sound data. The determining unit can include other circuitry or components as would be obvious to one of ordinary skill in the art.

[0070] FIG. 7B illustrates the airflow rate determining unit 706 of FIG. 7A. The airflow rate determining unit 706 includes an analog-to-digital converter (ADC) 716. The spirometry data x1, typically an analog signal, is input to the ADC 716. The output of the ADC 176 is a DC voltage that may be coupled to a calculation unit 718. The calculation unit 718 correlates the input data signal with a pre-determined calibration curve to determine the airflow rate. The calculation unit 718 generates graphical representations of the input data and/or the results of correlating the input data with the pre-determined calibration curve. These results can be displayed on an associated display device (not shown), or can be stored in memory 712.

[0071] FIG. 7C illustrates the sound determining unit 708 of FIG. 7A. The sound determining unit 708 includes a sound processing unit 720. According to various embodiments of the present invention, the sound processing unit 720 may be a sound card. The sound data x2 is input to the sound processing unit 720. The output of the sound processing unit 720 is a sound data signal representative of the sound generated by the source of the airflow (i.e., the patient). The sound data signal is then passed through a frequency conversion unit 722. The frequency conversion unit 722 may apply Fast Fourier Transform (FFT) technique to the sound data signal. The output from the frequency conversion unit 722 may be used to determine peak frequencies that are representative of medical conditions. Accordingly, using the output of the frequency conversion unit 722, it is possible to determine whether a patient has a medical condition, such as asthma and the like.

[0072] The output of the airflow rate determining unit 706 and the sound determining unit 708 (736 and 738 respectively) may be visually represented. FIGS. 8A-8C illustrate various way of visually representing the spirometry data and the sound data detected and/or measured using the airflow measuring device 500 of the present invention. An adult male is used as a subject to collect the data illustrated in FIGS. 8A and 8B. FIG. 8A illustrates the auscultation data and FIG. 8B illustrates the spirometry data, both simultaneously measured using a single airflow sensor.

[0073] FIG. 8A illustrates a three dimensional plot 902 of frequency, time and auscultation data of an adult male subject. A Fast Fourier Transform may be performed on the auscultation intensity data. The airflow sensor of the present invention is a bidirectional sensor, i.e. the sensor of the present invention may measure both the inhalation and exhalation data. Accordingly, both the inhalation data 903 and the exhalation data 905 are represented on the three dimensional plot 902 of FIG. 8A.

[0074] FIG. 8B illustrates the spirogram 904 of the adult male subject. The data illustrated on FIG. 8B may be collected using the same airflow sensor used to detect the data illustrated on FIG. 8A. It is also possible to record the breath sound data at the output of a sound card. FIG. 8C illustrates expiratory and inspiratory recordings 906 from the sound card.

[0075] The airflow sensor of the present invention is tested with various applications. The American Thoracic Society publishes spirometry waveforms for the purpose of spirometer calibration and validation of accuracy. These waveforms are fed from a computer into a pulmonary waveform generator (PWG) consisting of a computer-directed servo-controlled pump which generates airflow according to those patterns, which a spirometer can then be tested for its ability to track. FIGS. 9A and 9B compare the standard pulmonary waveform #11 output of a PWG with the recording by the airflow sensor of the present invention. In FIGS. 9A-9B, the data 950 gathered using an exemplary airflow sensor of the present invention are compared to the standard pulmonary waveform #11 data 960 of the PWG.

[0076] FIG. 9A illustrates the response of the airflow sensor according to the present invention versus the observed and calibrated PWG curve. The PWG curve is characterized by two initial humps followed by a decay. As illustrated in FIG. 9A, the sensor of the present invention provides data that match well with the output of the PWG.

[0077] FIG. 9B shows a comparison of peak expiratory flow (PEF).sup.1/2 from the PWG data set versus the maximum voltages obtained from the airflow sensor of the present invention. As illustrated, a linear correlation is observed.

[0078] A flowchart 800 of steps illustrating an exemplary method of simultaneously gathering spirometry and auscultation data using the airflow sensor of the present invention is provided in FIG. 10. The method includes collecting displacement data using a sensor according to the present invention (step 802). The displacement data relates to the displacement of the flap including the sensor caused by the airflow generated by a source. The displacement data may be used to measure the airflow rate of the source, such as a patient. The displacement data may be used as the spirometry data. According to various embodiments of the present invention, the displacement data is sent to an airflow rate determining unit (step 804). The airflow rate determining unit may include an analog-to-digital converter.

[0079] The method further includes collecting vibration data using the same sensor of the present invention (step 806). The vibration data relates to the vibration of the flap including the airflow sensor caused by the airflow generated by the source. The vibration data may be used to measure the sound of the source. The vibration data may be used as the auscultation data. The vibration data is sent to a sound processing unit (step 808). The sound processing unit may include a sound card. Accordingly, the method collects two sets of data, i.e. displacement data and vibration data, using the same sensor.

[0080] The use of a thin film flexible polymeric in the present invention allows modal vibrations to be used as a mechanism for representing sound. Any physical object subjected to a force that allows slippage, whether it be a flute subjected to airflow slipping across its mouthpiece or a violin with a bow slipping over a string, will have resonance modal vibrations that are activated when the applied force meets specific physical conditions. When specific air velocities are achieved with the elastic flap sensor of the present invention, resonance conditions are satisfied and the timing, frequency and energy of the resulting sonic vibrations can be quantified if the data set is converted by such analytic modalities as Fast Fourier Transform algorithms.

[0081] Accordingly, in step 810 of the flowchart 800 of FIG. 10, a Fast Fourier Transform or other algorithms may be applied to the analog sound data signal representing the vibration data in order to decompose the sequence of values collected by the airflow sensor into components of different frequencies for further analysis (step 810). The result of the Fast Fourier Transform and/or the raw data collected by the airflow sensor is sent to a determining unit for further analysis (step 812) and visual representation (step 816). If additional data are collected by other sensors (step 814), such as chemical sensors or thermal sensors, used in conjunction with the airflow sensor of the present invention, the additional data may also be sent to the determining unit to be analyzed along with the displacement and vibration data (step 812). When the collected data are analyzed using the determining unit, the data may be visually displayed, saved, or sent to other devices (step 816).

[0082] The present invention provides a new class of airflow sensors, in which the indicator of airflow is the elastic deformation of a flexible flap. The flexible flap does not require additional appendages for controlling vibration. The elimination of additional appendages prevents trapping of respiratory secretions and results in a device that is easy to clean and disinfect. The primary intended use of the airflow sensor according to the present invention is medical measurement of human respiratory airflow and breathing sounds for diagnostic and therapeutic purposes. However, the primary intended use should not be construed as limiting. Multiple embodiments are envisioned in which the flap can accommodate a plurality of other physical and chemical sensors.

[0083] The present invention is not limited to medical applications. An exemplary non-medical use of the present invention may be the measurement of airflow across the various surfaces of aircraft in flight. The airflow sensors of the present invention may be used to measure airflow with the particular advantage that the elastic flap devices of the present invention are very sensitive under stall conditions. Unlike pitot tubes, flaps built into the wings and bodies of commercial jet aircraft do not plug up with ice.

[0084] Another exemplary non-medical implementation of the present invention is a device mounted at the top of a mast of a sailboat that measures the wind speed, direction, and sound. The device may have a strain gauge in a tube. As wind goes through the tube, the sensor is bent, giving a change in resistance. The gauge may be connected to a cable capable of 360 degree rotation. A Wheatstone bridge may be used to monitor the change in resistance. The measurements of the strain gauge may be conveyed to a computing device. Using the sound card of the computing device, the user may hear low frequency sound indicative of adverse sail flapping, which could tell the user that a stall condition has occurred.

[0085] Other potential non-medical applications include monitoring air flow and vibrations in acoustical wind instruments from pipe organs to saxophones. Both medical and industrial embodiments of the airflow sensor can be modular, allowing cleaning and disinfection of the sensor.

[0086] While the invention has been shown and described with reference to specific preferred embodiments, it should be understood by those skilled in the art that various changes in form and detail may be made therein without departing from the spirit and scope of the invention as defined by the following claims.