JP2005160644A - Respiratory data acquisition system - Google Patents

Abstract

<P>PROBLEM TO BE SOLVED: To acquire quantitative data related to apnea in a daily life. <P>SOLUTION: This respiratory data acquisition system includes a respiratory data acquisition device worn on the face and acquiring and storing respiratory data, and an analytical display device receiving the transfer of the respiratory data from the respiratory data acquisition device 10 detached from the face after finishing the acquisition of the respiratory data and analyzing and displaying the respiratory data. The respiratory data acquisition device 10 is stuck on the skin of the palate fitted to grasp an air flow 2 of the nasal respiration and an air flow 4 of the oral respiration, with a pad 20 to be worn, detects respiratory sounds by a respiratory sound sensor 40 mounted on the pad 20 to be worn, and acquires and stores the respiratory sound data by a data acquisition part incorporated in left/right circuit packages 24a and 24b attached to the pad 20 to be worn. <P>COPYRIGHT: (C)2005,JPO&NCIPI

Description

  The present invention relates to a respiratory data collection system, and more particularly to a respiratory data collection system that collects changes in respiratory sounds related to apnea.

  A person may repeat apnea intermittently during sleep, resulting in various symptoms such as somnolence during the day. These are called sleep disordered breathing. Apnea refers to stopping airflow for 10 seconds or more, and sleep sleep disorder is accompanied by 30 or more apneas during sleep of 7 hours or more, or 5 or more times per hour of sleep. Those with apnea are defined as sleep apnea syndrome.

  For the diagnosis of sleep respiratory disorder, electroencephalogram measurement, electrooculogram measurement, electromyogram measurement, and the like are performed. In addition, apnea determination is performed based on the presence of nasal airflow and mouth airflow. Various methods are used to determine the presence of nasal airflow and mouth airflow. For example, a thermistor is fixed to the nose or mouth and the presence or absence of breathing or breathing is measured from the temperature change due to the airflow. The carbon dioxide in the breath is sampled from the nasal cavity and the concentration is measured to determine the presence or absence of breathing. There is one that qualitatively measures the sound of airflow during breathing and determines the presence or absence of breathing.

For the diagnosis of sleep disordered breathing, measure the respiratory movement by winding elastic strings that change the resistance value when stretched around the chest and abdomen, and measure the intraabdominal pressure by placing a balloon in the esophagus Respiratory effort is evaluated, and various measurements and evaluations are performed over a long period of time, such as measuring the oxygen concentration of blood from the absorption spectrum of Hb and HbO _{2 in} the bloodstream using a so-called oximeter. Based on these comprehensive evaluations, it is determined whether or not the patient has sleep apnea syndrome, the degree of sleep disordered breathing, the cause of the disorder, and the treatment based on the determination.

Honma Nihonomi, Sleep Apnea Syndrome, Koseido Publishing, February 1, 2002, 1st Edition, 4th Edition, p48-57

  As described above, the examination for sleep disordered breathing in the hospital is performed not only for the measurement of apnea but also for the purpose of elucidating the cause and performing treatment suitable for the measurement, and various measurements and evaluations are performed. For example, in addition to confirming breathing with a mask covering the mouth and nose, an inspection device such as an electrocardiograph, an oximeter, a pulse meter, an electroencephalograph, etc. is attached, and a large-scale inspection requiring at least one night is required.

  As described above, in the prior art, there is only a large-scale examination of a sleep disordered breathing in a medical institution such as a hospital, and the sleep disordered breathing cannot be easily quantitatively monitored in daily life.

  An object of the present invention is to solve the problems of the prior art and to provide a respiratory data collection system that can collect quantitative data related to apnea in daily life.

  In order to achieve the above object, a respiratory data collection system according to the present invention is removed from the face after the collection of respiratory sound data and the respiratory data collection device that collects and stores the respiratory data by attaching to the face. A respiratory data collection system including an analysis display device for analyzing and displaying the respiratory data upon receipt of the respiratory data transferred from the respiratory data collection device, wherein the respiratory data collection device is attached near the nostril of the face or near the mouth A removable attachment pad that is attached, a respiratory sound sensor that is attached to the attachment pad and detects a breathing sound, and a data collection unit that is attached to the attachment pad and collects and stores data detected by the respiratory sound sensor; The analysis display device includes a display for displaying at least one of the respiratory sound data or the analysis result of the respiratory sound data.

  The deposition pad has an output port for transferring data to the analysis display device, and the analysis display device has an insertion section for receiving the deposition pad removed from the face after the collection of respiratory sound data is completed, And an input port that is detachably connected to the output port of the deposition pad.

  The analysis display device includes an output unit that outputs at least one output data of the respiratory sound data or the analysis result of the respiratory sound data based on the data received from the respiratory data collection device. It is preferable to have at least one of writing means for writing the output data to the portable memory or transmission means for transmitting the output data to the outside through a communication line.

  The respiratory sound sensor detects the air flow through the nostril and the air flow from the mouth through the upper airway, and the data collection unit detects the nasal respiratory sound and the mouth based on the data detected by the respiratory sound sensor. The analysis and display device displays at least one of the data on the occurrence status of the nasal breathing sound and the mouth breathing, or the association data between the occurrence status and the lifestyle habits. Is preferred.

  Moreover, it is preferable that the respiratory sound collecting device includes an attaching / detaching means for detachably attaching the respiratory sound sensor to the deposition pad.

  Further, the deposition pad has a deposition portion having a shape along the outer surface of the palate between the nostril and the mouth, and the respiratory sound sensor is a pyroelectric polymer film provided on the deposition portion. A pyroelectric polymer film attached to a thin metal plate and coated with a flexible resin is preferable.

  Further, in the respiratory data collection system according to the present invention, the deposition pad is provided with a beam portion in which a conductive wire is embedded in a flexible resin and the outer shape can be changed. It is preferable that the signal terminal is connected to the data collection unit via a conductive wire.

  In the respiratory data collection system according to the present invention, the deposition pad has a beam portion having a bifurcated shape in which a conductive elastic wire is embedded in a flexible resin and the outer shape can be inserted into both nostrils. The respiratory sound sensor is attached to both nostrils, held at the tip of the beam portion, and using the elasticity of the conductive elastic wire material of the beam portion to press each bifurcated tip against the inner wall of each nostril. It is preferable.

  In addition, the data collection unit identifies the magnitude of the mouth breathing sound that passes through the mouth and the magnitude of the nasal breathing sound that passes through the nostrils based on a cue signal indicating whether the subject's breathing is mouth breathing or nose breathing. It is preferable to have a breathing sound discriminating means for obtaining an identification level to be detected and a breathing sound discriminating means for discriminating the breathing sound into a nasal breathing sound or a mouth breathing sound based on the obtained discrimination level.

  In addition, the data collection unit includes a pitch measurement unit that measures a respiratory pitch based on a signal detected by the respiratory sound sensor, a pitch notification unit that displays and notifies a pitch corresponding to the measured respiratory pitch, and a displayed notification. Re-measurement signal receiving means for receiving a re-measurement instruction signal output by the subject based on the pitch, and when receiving the re-measurement instruction signal, the re-measurement pitch signal is measured again and the re-measurement instruction signal is not received within a predetermined time. In some cases, it is preferable to have initial reference respiration data setting means for setting the respiration data at that time as initial reference respiration data. Further, it is preferable that the pitch notification means gradually weakens the display intensity as the measurement time elapses and induces the person to be measured to sleep.

  The data collection unit sequentially calculates the latest average respiratory pitch based on the latest measured respiratory pitch data and pitch measuring means for measuring the respiratory pitch based on the signal detected by the respiratory sound sensor. Average pitch calculation means, and the average pitch calculation means obtains the standard deviation of a plurality of average breath pitches so far, determines the normal range of the breath pitch based on the obtained standard deviation, and measures the latest When data out of the normal range is included in the plurality of respiration pitch data, it is preferable to exclude this and recalculate the latest average respiration pitch.

  In addition, the data collection unit includes an estimation unit that estimates the respiratory pitch, and a sleep unit that sleeps the circuit operation until a timing necessary for the next respiratory sound detection after the detection of the respiratory sound based on the estimated respiratory pitch. It is preferable.

  Further, the data collection unit has no signal from the respiratory sound sensor, a signal presence / absence determining means for determining the presence / absence of a signal from the respiratory sound sensor, an end signal receiving means for receiving a measurement end signal output by the measurement subject, When it is determined that the respiratory data collection device has been removed, the data processing is terminated based on the deletion means for deleting the last apnea data and the determination result of the signal presence / absence determination means or the acquisition of the measurement end signal. And terminating means.

  In addition, the respiratory sound data collection system according to the present invention includes a respiratory data collection device that collects respiratory data by attaching to the face, and an analysis that analyzes and displays the respiratory data upon receiving the respiratory data transferred from the respiratory data collection device A respiratory data collection system including a display device, wherein the respiratory data collection device is attached to a part of the face so as to be detachably attached, and a respiratory sound that is attached to the deposition pad and detects a respiratory sound The analysis display device includes: a sensor; and a transmission unit that is provided on the deposition pad and modulates data detected by the respiratory sound sensor into a signal in a non-audible frequency band and transmits the signal to an external reception unit. Receiving means for receiving a signal in the non-audible frequency band transmitted by the means and demodulating it into respiratory sound data, and at least one of the demodulated respiratory sound data or the analysis result of the respiratory sound data Characterized in that it comprises a display that, a.

  According to at least one of the above-described configurations, a removable attachment pad that attaches near the nostril or mouth of the face is provided, a respiratory sound sensor is attached to the attachment pad, and respiratory sound data is collected and recorded. Install the data collection unit. Therefore, it is possible to complete the acquisition, collection, and recording of respiratory sound data during the data collection period such as during sleep with a load that only attaches the deposition pad. Can be collected.

  The analysis display device receives the respiration data from the respiration collection device removed from the face after the collection of the respiration sound data, analyzes the respiration data, and displays the respiration sound data or the analysis result thereof. In other words, the data collection record and the analysis display of the result are separated, no special processing is required for data output during the data collection period such as during sleep, and data transfer is performed when collecting respiratory sounds. No need for codes. Therefore, the burden of deposition can be reduced, and breathing data can be easily collected in daily life and the results can be viewed.

  In addition, according to at least one of the above-described configurations, the deposition pad has an output port for data transfer, and an input port is provided in the insertion portion of the analysis display device. Therefore, the breathing data can be easily transferred by inserting the deposition pad into the insertion portion and connecting the output port and the input port.

  In addition, according to at least one of the above-described configurations, the analysis display device displays the transferred breathing sound data or the analysis result on the display, and writes and outputs it to the portable memory, or externally through a communication line. Send to. As described above, in addition to knowing respiration data and the like on the display, those data can be further used via a portable memory or a communication line. For example, the data can be analyzed in detail by another data analysis device, and can be provided to the judgment of a doctor or the like in a medical institution. Therefore, respiration data that can be easily collected in daily life can be used more effectively.

  In addition, with at least one of the above-described configurations, the respiratory sound sensor captures both the air flow through the nostril and the air flow from the mouth through the upper airway. Therefore, it is not necessary to provide a sensor for nasal breathing sound and a mouth breathing sound sensor separately, and the load of sensor attachment can be reduced. And a data collection part classify | categorizes and memorize | stores a nasal breathing sound and a mouth breath from these data. The analysis display device displays data on the occurrence status, for example, the number of times and the ratio. Or the data which linked | related the occurrence condition and lifestyle were displayed. Therefore, it is possible to easily know the frequency of mouth breathing related to sleep disordered breathing, and to know the association with lifestyle habits, which can be used to improve lifestyle habits.

  Moreover, the attachment / detachment means which attaches a breathing sound sensor to an attachment pad so that attachment or detachment is possible by at least one of the said structures is provided. Therefore, only the respiratory sound sensor can be removed and replaced, or cleaning, cleaning, and the like can be easily performed.

  Further, according to at least one of the above structures, a pyroelectric polymer film attached to a thin metal plate and coated with a flexible resin is used as a respiratory sound sensor, and this is the outer surface of the palate between the nostril and the mouth. It is provided in the adherend part of the shape along Therefore, the entire breathing sound sensor and its mounting portion can be made compact and lightweight, and it is flexible, so that the burden of deposition can be reduced and breathing data can be easily collected in daily life.

  In addition, with at least one of the above-described configurations, the respiratory sound sensor is held at the tip of the flexible resin beam portion in which the conductive wire is embedded, and the whole is attached to the deposition pad. The conductive wire serves as a core material for changing the outer shape of the beam portion along the outer surface of the face, for example, and also serves as a signal line of the respiratory sound sensor. Therefore, since the signal line or the like is not exposed to the outside and is flexible as a whole, the burden of deposition can be reduced, and respiratory data can be easily collected in daily life.

  Further, by at least one of the above-described configurations, the beam portion has a bifurcated shape that can be inserted into both nostrils, and the beam portion has a conductive wire material having elasticity and flexibility as a core material, so that the elasticity of the conductive wire material is utilized. The breathing sound sensor at the tip of the beam portion can be attached by being pressed against the inner walls of both nostrils. In other words, nasal septum pinching or nostril attachment can be performed, and the need for fixing to the face can be reduced, for example, due to the adhesiveness of the pad. Even when the person to be measured is sensitive to the adhesive material or when it is difficult to apply the adhesive material with a beard or the like, it is possible to reduce the burden and fix the deposition pad and the respiratory sound sensor to the face.

  In addition, according to at least one of the above-described configurations, the discrimination level between the nasal breathing sound and the mouth breathing sound is obtained based on a signal indicating whether the breathing performed by the measurement subject is mouth breathing or nasal breathing. Since it is generally known that snoring is related to sleep disordered breathing and snoring is related to the frequency of mouth breathing, it is preferable to identify the snoring. The level of the nasal breathing sound and mouth breathing sound is almost determined once the position of the breathing sound sensor is determined, so the nasal breathing sound level and the mouth breathing sound level are determined according to the cue signal. By comparing these, the magnitude of the signal level that distinguishes the nasal breathing sound and the mouth breathing sound can be obtained. The signal to be measured may be output by the person to be measured and acquired by the data collection unit, or may be output by the data collection unit and the person to be measured may perform mouth breathing or nasal breathing according to the signal. Once the identification level is obtained, it is then possible to automatically determine whether it is nasal breathing or mouth breathing according to the identification level. Therefore, data on nasal breathing or mouth breathing can be easily collected without increasing the burden on the subject.

  In addition, the respiratory sound pitch is measured by at least one of the above-described configurations, and notification is displayed at the same pitch as the measured respiratory sound pitch. The notification display may be sound, sound, light, vibration, or the like. Then, the person being measured can judge whether or not his breathing pitch and the breathing pitch judged by the breathing sound data collecting device match each other by this notification display. Put out. By receiving this remeasurement instruction signal, the breathing sound pitch measurement can be performed again. Thereby, noise in measurement, data processing, etc. can be removed. Since the person to be measured makes this determination when he / she is awake, if the remeasurement instruction is not output for a certain period of time, the breathing data such as the breathing pitch at that time is considered to be normal breathing data of the person to be measured. . Therefore, if this is set as the initial reference respiration data, then the change in the respiration sound data can be automatically measured based on the initial reference respiration data.

  In addition, due to at least one of the above-described configurations, the respiration pitch notification display gradually weakens the display intensity as the measurement time elapses. For example, the notification display is blinking light and gradually darkens with time. As a result, the person to be measured is guided and easily sleeps. Therefore, the burden can be reduced and breathing data can be easily collected in daily life.

  Further, the average pitch is sequentially calculated for the measurement of the respiratory pitch by at least one of the above-described configurations. And the standard deviation is calculated | required about the calculated | required average pitch, and a normal respiration pitch range is set by it. Since the average pitch changes sequentially with time, the normal breathing pitch range also changes sequentially. Then, data out of the normal range of the respiratory pitch is excluded and the average respiratory pitch is recalculated. In this way, temporary breathing disturbance can be excluded, and noise in breathing sound measurement and data processing can be removed.

  In addition, at least one of the above-described configurations estimates the respiratory pitch, and sleeps the circuit operation during a period that is not used for respiratory sound detection based on the estimated respiratory pitch. This reduces the power consumption of the respiratory data collection device and allows the use of smaller batteries.

  In addition, with at least one of the above-described configurations, the end of the data processing is performed based on the presence or absence of a response from the respiratory sound sensor or the end signal of the measurement subject without requiring a special end processing procedure. When it is determined that there is no response from the breathing sound sensor and the breathing data collection device is removed, the last apnea data is deleted to ensure data reliability. As described above, since the burden of termination processing on the measurement subject can be reduced, it is possible to easily collect respiratory data in daily life.

  Moreover, the data detected by the respiratory sound sensor is converted into a signal that cannot be detected by hearing by at least one of the above configurations, and transmitted to an external receiving device. Therefore, a data collection unit is not required for the deposition pad, and further reduction in size and weight can be achieved. Respiration data can be easily collected in daily life with less burden.

  Hereinafter, embodiments of the present invention will be described in detail with reference to the drawings. In the following description, the material and dimensions of each element are examples, and the time for measurement is also an example. In the following description, the attachment pad to which the breathing sound sensor or the like is attached will mainly be described as being attached to the palate between the nostril and the mouth. A string of a formula or the like may be attached to the deposition pad, or a string attached to the deposition pad may be turned around the head to assist the deposition.

  First, an overview of the respiratory data collection system will be described, and then the components will be described in detail. The breathing data collection system includes a breathing data collection device that collects and stores breathing sounds by attaching to the face of a measurement subject during sleep, and an analysis display device that is placed on a desk, for example. Consists of. As will be described later, the analysis display device has an insertion unit for receiving the respiratory data collection device. When the measurement subject wakes up, the breathing data collection device is removed from the face, and this is inserted into the analysis display device, whereby the respiratory data is collected. Respiratory data during sleep stored in the collection device is transferred to the analysis display device. The analysis display device has a display for displaying respiration data.

  Next, in the respiratory data collection system having such a configuration, a respiratory data collection device will be described. FIG. 1 is a diagram illustrating a state in which a respiratory data collection device 10 is attached and attached to the skin of the palate between the nostril of the face and the mouth. The palate between the nostril and the mouth is a position suitable for capturing both the sound or vibration due to the airflow 2 of nasal breathing and the sound or vibration due to the airflow 4 of mouth breathing. Therefore, it is not necessary to prepare separate sensors for detecting nasal breathing and for detecting mouth breathing and attach them separately.

  FIG. 2 is an exploded view of the respiratory data collection device 10. The breathing data collection device 10 includes a deposition pad 20 having a generally butterfly-shaped wing, and a breathing sound sensor 40 having a bridge shape so that the airflow from the nose and the airflow from the mouth flow between them. A pair of hooks 22a and 22b for detachably attaching the breathing sound sensor 40 to the deposition pad 20 are configured. By attaching and detaching the hooks 22a and 22b, for example, the breathing sound sensor 40 is exchanged according to the person to be measured, or the breathing sound sensor 40 is exchanged with another when the breathing sound sensor 40 is defective, or the like. The breathing sound sensor 40 can be freely attached and detached from the wearing pad 20.

  The deposition pad 20 has a function of attaching and holding the breathing sound sensor 40, a function of storing a circuit block for collecting, processing and storing the breathing sound data detected by the breathing sound sensor 40, and all elements necessary for these. This is a member having a function of fixing the position as a unit to the skin surface. The deposition pad 20 includes plastic resin left and right circuit packages 24a and 24b, a pad plate 26 made of a plastic resin thin plate for holding the left and right circuit packages 24a and 24b, and a plastic resin airflow provided on the pad plate 26. A bank member 30 is included.

  The pad plate 26 is a thin plate having a substantially butterfly-shaped wing. The left and right circuit packages 24a and 24b are arranged at both ends of the pad plate 26 so as to be separated from each other. The air current bank member 30 is arranged at a position that enters the gap space of the bridge shape. In addition, a pair of holes 28a and 28b into which the pair of hooks 22a and 22b are fitted are provided at positions outside the arrangement positions of the left and right circuit packages 24a and 24b. As shown in FIG. 3, a pair of adhesive sheets 36 a and 36 b are attached to both ends of the back surface of the pad plate 26. The adhesive sheets 36a and 36b have a function of pressing and adhering the adherend pad 20 to the face skin surface and fixing the position thereof. Instead of the adhesive sheets 36a, 36b, an adhesive gel may be applied.

  The airflow bank member 30 has a function of narrowing the flow of the respiratory airflow in cooperation with the bridge shape of the respiratory sound sensor 40 so that the respiratory sound sensor 40 can efficiently detect the respiratory sound. It is a member having a similar cross-sectional shape. As shown in FIG. 2, it is preferable that the pad plate 26 is disposed at a position near the nostril, and the direction in which the wing cross section gradually narrows is directed to the nostril side.

  The left and right circuit packages 24a and 24b are plastic resin packages that house circuit components therein. An LED (Light Emission Diode) 32 is attached to one circuit package 24b. As will be described later, the LED 32 detects a breathing sound by the breathing sound sensor 40, processes the breathing sound data, blinks light at the same pitch as the breathing pitch calculated and notifies the subject to measure the pitch. Means. The other circuit package 24a is provided with an input / output port 34 for data transfer and charging. The input / output port 34 is preferably embedded without protruding from the outer periphery of the circuit package 24a. For example, a female jack can be used.

  The respiratory sound sensor 40 is an element having a function of detecting a respiratory sound, and a condenser microphone 50 that is a detector, and a bridge type microphone that concentrates the airflow 2 from the nostril and the airflow 4 from the mouth on the condenser microphone 50. The holding frame 42 is included. The microphone holding frame 42 is made of plastic resin, and the condenser microphone 50 is attached to the bridge-shaped ceiling portion with the sound collection surface facing the inside of the bridge, and the roots of the both sides of the bridge-shaped shape are outward. Holes 44a and 44b are provided in which the pair of hooks 22a and 22b are fitted.

  FIG. 4 shows an exploded view of the respiratory sound sensor 40 as viewed from the back side. The condenser microphone 50 has a cylindrical shape, and the bottom surface on one side thereof is a sound collection surface. The dimensions are, for example, about 7 mm in diameter and about 2-3 mm in height. A hole 49 is provided in the bridge-shaped ceiling portion of the microphone holding frame 42, and the outer periphery of the cylindrical portion of the capacitor microphone 50 is fitted into the hole 49 and is fixed with an adhesive or the like. The microphone holding frame 42 is provided with a positive electrode 46 and a negative electrode 48 corresponding to the positions of the holes into which the pair of hooks 22a and 22b are fitted. The positive electrode 46 is connected to the output terminal of the sound collecting surface of the capacitor microphone 50, and the negative electrode is connected to the ground of the capacitor microphone 50, for example, its casing.

  Next, an analysis display device constituting the respiratory data collection system will be described. FIG. 5 is a diagram showing an analysis display device 60 that receives data stored in the respiratory data collection device 10 and displays the contents thereof. The analysis display device 60 includes a rectangular parallelepiped housing, and an insertion recess 62 that can be inserted with the respiratory data collection device 10 in an upright posture is provided on the top surface of the housing. In the insertion recess 62, an input / output port 64 for data transfer and charging is arranged at a position corresponding to the input / output port 34 provided in the circuit package 24a of the respiratory data collection device 10.

  FIG. 5 shows a state in which a male input / output port 64 is provided in the insertion recess 62 corresponding to the female input / output port 34. By inserting the female input / output port 34 of the respiratory data collection device 10 into the male input / output port 64 of the insertion recess 62 in a detachable manner, data transfer from the respiratory data collection device 10 to the analysis display device 60 is performed. The respiration data collection device 10 is charged from the analysis display device 60. Therefore, the breathing data collection device 10 is normally left inserted in the analysis display device 60, and when breathing sounds are collected, the breathing data collection device 10 is detached from the analysis display device 60 and attached to the measurement subject, and the breathing data is collected. When the collection is completed, for example, when the measurement person wakes up, it is preferable that the data collection device 10 is removed from the face and inserted into the analysis display device 60.

  A display 66 and operation buttons 68 are further arranged on the upper surface of the analysis display device 60. The display 66 is a display element that displays respiration data and the like using characters and characters. For example, a liquid crystal panel or the like can be used. The operation button 68 is a button for switching display contents on the display 66. The operation button 68 can be a push button, a touch button, or a roll-type switching button. The functions of the display 66 and the operation buttons will be described later. A battery box cover 70 and an insertion slot 72 for the memory card 80 are provided on the front surface of the analysis display device 60.

  FIG. 6 is a block diagram of a collecting device circuit 90 that is a circuit portion of the respiratory data collecting device 10 and a display device circuit 110 that is a circuit portion of the analysis display device 60. The collecting device circuit 90 is housed in the left and right circuit packages 24a and 24b, and the display device circuit 110 is housed inside the housing. The collector circuit 90 and the display device circuit 110 are connected by a cable, and data communication and charging power supply are performed. First, the configuration of the collecting device circuit 90 will be described, and then the configuration of the display device circuit 110 will be described.

  The collector circuit 90 receives an amplifier (AMP) 92 that receives and amplifies the signal detected by the respiratory sound sensor 40, a band-pass filter (BPF) 94 that performs band-filter processing on the amplified signal, and an analog signal after the processing A / D converter 96 for converting the signal into a digital signal is connected in series and then connected to CPU 98.

  The CPU 98 is an arithmetic processing unit having a function of processing the received digital signal. Specifically, when the measurement subject is awake, a teaching function that sets the initial value of the respiratory data, and monitoring the respiratory pitch and apnea during the measurement subject's sleep based on the set initial value It has a running function. Details thereof will be described later.

  The LED 32 has a function of outputting the breathing pitch calculated at the time of teaching by blinking light to inform the measurement subject.

  The flash memory 100 is a semiconductor memory that stores respiration data subjected to data processing by the teaching function and running function of the CPU 98. The storage capacity is desirably a capacity capable of storing respiration data of at least about 10 hours. As the flash memory 100, for example, a commercially available product of about 32 MB can be used.

  The secondary battery 106 is a power supply for the entire collector circuit 90, and is boosted to a predetermined voltage level by the DC converter 108 and supplied to each element. As the secondary battery 106, a small rechargeable button battery or the like can be used. Further, a switch 104 may be provided as necessary.

  In the display device circuit 110, the display control unit 114 is a circuit having a function of controlling the operation of the entire display device circuit 110. Specifically, it has a function of receiving data from the collector circuit 90 at the input / output port 64, performing data analysis processing such as aggregation on the received data, and storing the data in the memory together with the transferred data. In addition, it has a function of performing image processing or the like on the transferred data or analysis result data and outputting it to the display 66. Further, it has a function of outputting the received data and analysis result data to the memory card 80 via the memory interface 116. In addition, the charging control unit 120 is controlled to supply the primary battery power as charging power to the secondary battery 106 of the collector circuit 90 via the input / output port 64.

  The memory card 80 is a small portable storage medium, and for example, a commercially available 32 MB flash memory card can be used. The primary battery 118 is a power source for the entire display device circuit 110 and also has a function as a charging power source for the secondary battery 106 of the collector circuit 90 as described above. As such a primary battery, a commercially available AA battery or AA battery can be used.

  Next, the data processing function of the CPU 98 will be described using a flowchart. First, the teaching function and then the running function will be described. Such a function can be realized by software, specifically, by executing a respiratory data collection program. Each STEP in the following flowchart corresponds to each processing procedure of the respiratory data collection program. In the following description, the symbols in FIGS. 1-6 are used for each element.

  FIG. 7 is a flowchart showing the entire teaching process. In the teaching process, the respiratory data collection device 10 is attached to the measurement subject, and when the measurement subject lies on a bed or the like for sleep and is still awake, Perform initial settings. As described with reference to FIG. 5, since the respiration data collection device 10 is inserted into the analysis display device 60 and charged in the non-use state, the respiration data collection device 10 is first removed from the analysis display device 60 when teaching. This removal is detected, and the initialization process (S10) starts. Specifically, initial values of hardware and software are set, and an internal timer is started. Then, the adhesive sheets 36a and 36b on the back surface of the deposition pad 20 of the respiratory data collection device 10 are firmly pressed onto the skin of the palate portion between the measurement subject's nostril and mouth. In this state, the person to be measured lies on the bed.

  Next, it is determined whether it is a nose breathing instruction (S12). Specifically, the signal of the person to be measured is detected by the condenser microphone 50. The person to be measured gives a signal as to whether to perform nasal breathing or mouth breathing according to a predetermined identification method. For example, “Hana” and “Kuchi” may be signaled, and “Ton” and “Tonton” may be signaled. Alternatively, a notification means such as an audio speaker or a piezoelectric buzzer is provided on the side of the respiratory data collection device 10 so that, for example, a signal such as “please breathe in the nose” or an intermittent sound of the buzzer is output, and the measurement is performed accordingly A person may perform nasal breathing or mouth breathing.

  If it is determined whether the measurement subject's instruction is a nasal breathing instruction or a mouth breathing instruction, the determination is temporarily stored, and in either case, the process proceeds to the breathing sound acquisition step (S14). The breathing sound acquisition step is a step of processing so that the signal detected by the condenser microphone 50 can be used as a breathing sound. That is, after the step of S12, it is assumed that all the sounds detected by the condenser microphone 50 are treated as breathing sounds, but there is noise if the raw signals remain as they are, and in the breathing sounds, the call state and the sucking state May be difficult to distinguish. Therefore, before performing data processing, in the breathing sound acquisition process, it is necessary to process the raw sound, make it less susceptible to noise, make it easier to distinguish the sound, and acquire this as a breathing sound Become.

  FIG. 8 shows an internal flowchart of the breathing sound acquisition step (S14). First, it is determined whether 10 msec has elapsed (S40). If 10 msec has not elapsed, the process returns to the beginning, and if 10 msec elapses, the process proceeds to the data preprocessing step (S42). Therefore, here, data preprocessing is performed every 10 msec. That is, 10 msec corresponds to the sampling time.

  The data preprocessing step (S42) is a process for making the detected signal easy to use as a breathing sound, and is converted into a digital signal by the A / D converter 96, for example, differential processing is performed to detect a signal change. In order to make it easy to add and reduce the influence of noise, and to make it easy to add, processing such as absolute value processing is performed before that.

  FIG. 9 shows the raw signal 130 detected by the condenser microphone 50 in nasal breathing, with the horizontal axis representing time and the vertical axis representing voltage. FIG. 10 shows the raw signal 134 in mouth breathing with the horizontal axis and the vertical axis as in FIG. 9 and 10, call signals 132 and 136 are shown together with suction signals 131 and 135. In these data, the suction signal has a lower level than the call signal, and the nasal breathing has a lower level than the mouth breathing. The difference between these levels can be used to distinguish between nasal breathing and mouth breathing, and between breathing signals and call signals. In these raw signals 130 and 134, the direct current levels of the signals are different, but are shifted to positions where they are easy to see. Note that this difference in DC level can be removed by performing a differentiation process on the raw signals 130 and 134.

  Returning again to FIG. 8, it is determined whether 100 msec has elapsed (S44). If 100 msec has not elapsed, the process returns to the beginning, and if 100 msec has elapsed, the process proceeds to an addition process (S46) every 100 msec. Therefore, here, addition processing is performed on the data after data preprocessing every 100 msec. The data after the addition processing every 100 msec is used as breathing sound data for subsequent data processing.

  FIG. 11 compares the signal 133 after differentiation of the nasal respiration with the signal 138 after adding the absolute value of the signal after differentiation and processing every 100 msec in the same manner as in FIG. It is shown for ease. Thus, in order to compare the magnitude of the signal, that is, the magnitude of the breathing sound, the absolute value processing is performed rather than the comparison of the peak value of the differentiated signal 133, and this is added every certain time width. It can be seen that the influence of the transient noise of the signal after differentiation can be reduced. A signal 138 in FIG. 11 is respiratory sound data.

  In this way, when the respiratory sound data is acquired in the respiratory sound acquisition step (S14), the rest is used to set the respiratory level (S22) and the respiratory pitch for distinguishing between nasal breathing and mouth breathing. Data processing for performing the setting (S30) will be advanced. In performing these processes, it is possible to proceed only with the calculation process, but using the confirmation by the person being measured (S16) can reduce erroneous processes in the data process. Therefore, although confirmation by the measurement subject (S16) is not necessarily an essential process, the contents of the process will be described with reference to the flowchart of FIG.

  FIG. 12 is an internal flowchart of the confirmation process (S16) by the measurement subject. When breathing sound acquisition, that is, addition data every 100 msec is obtained, provisional breathing determination (S50) is performed using the acquired data. More specifically, a temporarily determined threshold value is used and compared with the acquired respiratory sound data. Then, it is determined whether or not there is provisional breathing (S52). When the breathing sound data exceeds the temporary threshold value, it is determined that temporary breathing is present, and the process proceeds to the LEDon process (S54). When the respiratory sound data is equal to or lower than the temporary threshold value, it is not determined that temporary breathing is present. ) In the LEDon process (S54), the LED 32 is turned on, and in the LEDoff process (S54), the LED 32 is turned off. Therefore, the LED 32 is lit while the temporary threshold value is exceeded, and the LED 32 is turned off when the threshold value is below the temporary threshold value. Therefore, the LED 32 indicates the respiratory sound data obtained as a result of the arithmetic processing in the respiratory sound acquisition step. Repeats lighting and extinguishing with changes. That is, the LED 32 is repeatedly turned on and off at a pitch corresponding to the breathing pitch obtained in the breathing sound processing step. That is, the LED 32 corresponds to pitch notifying means for notifying the calculated pitch.

  The person to be measured can easily determine whether or not the pitch of the nasal breathing etc. that he / she is performing matches with the blinking of the LED 32, so if the pitch does not match, the retry is performed according to a predetermined rule. Give instructions. For example, “Retry” sound is output. Therefore, it is determined whether there is a retry instruction (S58). When it is determined that there is a retry instruction, the process returns to the beginning of the breathing sound acquisition step and the breathing sound acquisition step (S14) is performed again. If it is not determined that there is a retry instruction even after a certain amount of time has elapsed, the measured person can assume that the breathing pitch of the breathing sound data acquired in the breathing sound acquisition process is the same as his / her breathing pitch. Data processing can be performed using the respiratory sound data acquired in the sound acquisition process.

  In this way, by making the person to be measured know and confirm the pitch corresponding to the calculated breathing pitch, it is possible to prevent erroneous calculation due to noise or the like in the calculation in teaching.

  In addition to using the notification light from the LED 32, the pitch notification means may provide a sounding body in the respiratory data collection device 10 to notify the breathing pitch by sound or voice, or provide a vibrating body to notify the breathing pitch by vibration. .

  Moreover, since the confirmation by the measurement subject is after the breathing sound acquisition step, the measurement subject may go to sleep as it is if the nasal breathing instruction and the mouth breathing instruction are completed. Therefore, the brightness of the notification light is gradually weakened over time. This is shown in FIG. FIG. 13A shows respiratory sound data, and FIG. 13B shows the presence of temporary breathing as the H level and the absence of temporary breathing as the L level. The LED 32 is turned on at the H level and turned off at the L level. FIGS. 13C to 13F show how the LED 32 is turned on / off with the passage of time when the breathing sound continues stably as shown in FIG. 13A. As (d)-(e) elapses, the lighting period is gradually shortened and finally the light is completely turned off in (f). By doing in this way, a to-be-measured person can be induced to sleep.

  Returning to FIG. 7 again, after the confirmation by the measurement subject (S16), when highly reliable breathing sound data is acquired in the breathing sound acquisition step (S14), it is next determined whether or not 20 seconds have passed (S18). To do. If 20 seconds have not elapsed, the process returns to the beginning, and if 20 seconds have elapsed, the process proceeds to the MAX value detection step (S20), and here, respiratory sound data for 20 seconds is acquired. The reason for setting 20 seconds is that the respiratory pitch during sleep or rest is usually 4-6 seconds, so we wanted to calculate a quantitative respiratory pitch with 5 breaths as one unit. It does not matter if the time is set properly.

  In the MAX value detection step (S20), in order to determine a signal level that can distinguish between nasal breathing and mouth breathing, the maximum value of breathing sound data during 20 seconds of nasal breathing and 20 seconds of mouth breathing are performed. It is the process of calculating | requiring the maximum value of the respiratory sound data in between. For example, when it is determined in S12 that the instruction is nasal breathing, the MAX value detected in the MAX value detecting step (S20) is the MAX value in nasal breathing. When the nasal breathing instruction is not determined, the detected MAX value is the MAX value in mouth breathing.

  Next, respiration level setting (S22) is performed based on the detected MAX value. For example, the MAX value in nasal breathing is multiplied by an appropriate coefficient, which is set as the respiratory level of nasal breathing. Also in mouth breathing, the detected MAX value is multiplied by an appropriate coefficient and set as the breathing level of nasal breathing. The set breathing level is used as a reference for automatically distinguishing the acquired breathing sound data from nasal breathing or mouth breathing in the running process. For example, if the MAX value for nasal breathing is 5 mV, the MAX value for mouth breathing is 50 mV, and the coefficient is 0.3, the breathing level for nasal breathing is set to 1.5 mV, and the breathing level for mouth breathing is set to 15 mV. .

  Next, it is determined whether or not respiration is detected (S24). The determination is made by setting an appropriate signal level equal to or higher than the noise level, and if it is less than that level, it is determined that no respiration is detected, and the process returns to the beginning of the respiratory sound acquisition step (S14). If it is determined that respiration is detected, the process proceeds to a respiration pitch acquisition step (S26).

  FIG. 14 is an internal flowchart of the breathing pitch acquisition process. First, the respiratory level is subtracted from the respiratory sound data (S60). That is, using the set respiration level as a threshold value, a point that crosses the threshold value, a so-called zero cross point, is obtained, and the interval between the zero cross points is treated as a respiration pitch. The respiration level subtraction process is performed for a period of 20 sec with respect to respiration sound data every 100 msec.

  In the interpolation processing step (S62), because of noise, zero cross points are frequently detected in the subtraction process every 100 msec. Therefore, the zero cross points that occur at too short intervals are ignored as noise, and the ignored section. Are interpolated to form a smoothly connected breathing curve. Based on the data after the interpolation processing, zero cross point detection (S64) is performed to obtain a breathing pitch.

  FIG. 15 shows the state of data processing in the breathing pitch acquisition process. Here, as the breathing sound data, the signal 138 in FIG. 11 is used. FIG. 15A is a diagram showing the MAX value 140 of the signal 138 and the respiration level 142, and corresponds to the processes of steps S20, S22, and S60. FIG. 15B shows the signal 144 after the interpolation process (S64), and FIG. 15C shows the zero-cross points 146a to 146f from the positive direction to the negative direction. Correspond.

  Returning to FIG. 7 again, it is determined whether or not the number of zero cross points in the 20 sec interval is within a predetermined range (S28). This is to check whether it is in the normal range of the breathing pitch at rest, and when it is too far away, it is returned to the beginning of the breathing sound acquisition step (14) as a malfunction. With the predetermined range, for example, the number of zero cross points can be 3-7. In the case of FIG. 15C, the number is six, so that it is determined to be within the predetermined range.

  If it is determined that the number of zero cross points is within the predetermined range, the process proceeds to an initial breathing pitch setting step (S30). Specifically, the intervals between the detected zero-cross points are calculated, and the average value of these is set as the initial breathing pitch. In the case of FIG. 15C, when the average interval of the zero cross points is 3.5 sec, this value is set as the initial breathing pitch in mouth breathing.

  Thus, when it is determined whether the instruction is a nasal breathing instruction or mouth breathing instruction in S12, the respiration level is set in S22, and the initial respiration pitch is set in S30, these are collectively set and registered as initial reference respiration data. In the above example, (nasal breathing-1.5 mV-3.5 sec) is registered.

  When setting registration for either nasal breathing or mouth breathing is thus performed, it is determined whether or not the settings for nasal breathing and the settings for mouth breathing have been completed (S34). If only one of the settings has been made yet, the process returns to step S12 to execute the steps up to S32 and the other setting is performed. Teaching ends when setting registration is completed for both.

  Next, the running process will be described. In the running process, since the person to be measured has already gone to sleep, only the sound detected by the condenser microphone 50 is used to identify nasal breathing or mouth breathing, monitor changes in breathing pitch, and monitor apnea. FIG. 16 is a flowchart of the entire running process.

  First, initialization (S70) is performed. Next, it is determined whether or not there is an end instruction (S72). Specifically, the signal of the person to be measured is detected by the condenser microphone 50. When the subject wakes up from sleep and tries to end the collection of breathing sound data, he gives a signal for an end instruction according to a predetermined rule. For example, the voice of “End” is output. Therefore, in the running process, the end instruction is monitored, and the end process (S88) is not performed until the end instruction is received, and the breathing sound acquisition is continued. The content of the breathing sound acquisition step (S74) is the same as that described with reference to FIGS. Based on the acquired respiratory sound data, the respiratory pitch monitoring and the apnea monitoring are performed in parallel.

  That is, after the breathing sound acquisition step (74), the determination as to whether 20 seconds have elapsed (S76) and the determination as to whether 1 second have elapsed (S80) are performed in parallel. The content of the process of S76 is the same as the content of S18 of the teaching process, and the content of the process of S80 differs only in that the set time is 1 sec. Therefore, respiratory pitch monitoring (S78) is performed every 20 seconds, and apnea monitoring (S82) is performed every 1 second.

  FIG. 17 is an internal flowchart of the breathing pitch monitoring step (S78). First, the MAX value detection (S90) of the respiratory sound data in the 20 sec period is performed. This content is the same as the processing content of S20 of the teaching process. Next, a process of distinguishing between nasal breathing and mouth breathing (S92) is performed. That is, the respiratory level in the nasal breathing and the breathing level in the mouth breathing that are registered for registration are compared with the detected MAX value, and the acquired breathing sound data is distinguished from nasal breathing or mouth breathing. For example, if the detected MAX value is 5 mV, in the case of the above example, it is smaller than 15 mV, which is the breathing level for mouth breathing, and larger than 1.5 mV, which is the breathing level for nasal breathing. Is attributed to nasal breathing.

  Next, respiratory pitch acquisition (S94) is performed. This process is the same as the content of the breathing pitch process of FIGS. And it is judged whether it is a predetermined range (S96). This process is also the same as the content of the process in S28 of the teaching process. When it is determined that the number of detected zero-cross points is within a predetermined range, a breathing pitch calculation (S98) is performed. Specifically, the interval between the detected zero-cross points is calculated, and the average value thereof is used as the breathing pitch.

  Then, it is determined whether or not the calculated respiration pitch is within a normal range (S100). When the breathing pitch is calculated for the first time, the initial breathing pitch that has been set and registered is set as the center value, an appropriate range is determined, and the range is set as the normal range. After the respiration pitch is calculated several times, the moving average is obtained, set as the center value, and a range of about three times the standard deviation is set on both sides thereof, and the range is set as the normal range. The moving average is an average of the latest data and the immediately preceding data, which is repeated over time, and the change in the average value over time becomes smooth. In this way, it is determined whether or not it is within the normal range, data out of the normal range is excluded as an abnormal value, and the latest average breathing pitch is calculated again.

  When the latest average breathing pitch is calculated in this way, this is replaced with the previous average breathing pitch and the breathing pitch is updated (S102). In this way, the respiratory pitch is monitored.

  FIG. 18 is an internal flowchart of the apnea monitoring step (S82). First, it is determined whether or not there is breathing (S110). Specifically, the value of the breathing level in the nasal breathing or the breathing level in the mouth breathing that is registered for registration is compared with the acquired breathing sound data. In the above example, the acquired respiratory sound data is compared with 1.5 mV.

  When it is determined that there is breathing, it is determined whether or not an apnea period has already been set (S112). The setting of the apnea period is performed when the time without breathing exceeds 10 seconds. Therefore, if it is determined that the apnea period is set, it is determined that the breath is present after the apnea has continued for 10 seconds or more, and the apnea is resolved. In this case, for the previous apnea period, the apnea time length, apnea start time, etc. are set as apnea information (S114) and updated in addition to the previous apnea information (S116). ). If it is not determined in S112 that the apnea period is set, the breathing state continues, so the process returns to the breathing sound acquisition step (S74) and the apnea monitoring is continued.

  If it is not determined in step S110 that breathing is present, apnea has started, and measurement of apnea time is started (S118). And it is judged whether it is apnea (S120). This determination can be made based on the definition of apnea based on whether or not the apnea time has exceeded 10 seconds. When it is determined that apnea is performed, an apnea period is set (S122). This is repeated every 1 sec to perform apnea monitoring.

  Returning to FIG. 16 again, following the apnea monitoring step (S82), it is determined whether or not the sensor is attached (S84). For example, when no breathing is detected for more than 7 minutes, it is considered that the breathing data collection device 10 is usually removed from the face except in the case of an accident. In this way, it can be determined whether or not the sensor is attached only.

  In the above example, if it is determined that the sensor has been removed after 7 minutes, for example, there may be no apnea for 7 minutes, so the last apnea period setting is deleted ( S86). Thus, after increasing the reliability of the data, the process proceeds to the end process (S88). That is, even when the measurement subject forgets to give an end instruction and leaves it alone, the process can proceed to the end process (S88). In addition, when it is not determined that the sensor is removed, that is, when 7 minutes have not elapsed, it is determined whether or not the sensor is inserted into the analysis display device 60 (S85). When the breathing data collection device 10 is inserted into the analysis display device 60, this is a time when the measurement subject forgets to give an end instruction but intends to remove the attachment voluntarily and end the measurement. In step S86, the process proceeds to end processing (S88). In other words, if it is determined that the sensor has been removed, either spontaneously or for some other reason, the last apnea period setting performed is deleted, and the termination process is performed. When it is not determined to be inserted into the analysis display device 60, the process returns to S72 and the apnea monitoring is continued.

  The end process (S88) is performed when it is determined that there is an end instruction in S72 and after the process process of S86 is performed although no end instruction is given. That is, the termination process is a process performed when data collection is terminated due to the measurement subject's intention or the like. At this time, as described with reference to FIG. 5, the breathing data collection device 10 that has been detached is inserted into the insertion recess 62 of the analysis display device 60, and this termination is detected and the termination process (S 88) is started. To do. FIG. 19 is an internal flowchart of the end processing step (S88). First, a measurement STOP process (S130) is performed. Next, memory backup (S132) and charging start (S134) are performed via the input / output ports 34 and 64. The memory backup step (S132) is a step of transferring respiratory data from the respiratory data collection device 10 to the analysis display device 60. The order of step S132 and step S134 may be reversed or may be performed simultaneously. Thereafter, the sleep process (S136) of the CPU 98 of the respiratory data collection device 10 is performed, and all the running steps are ended here.

  When the running process is completed, the data transferred to the analysis display device 60 is analyzed by the analysis display device 60 as described above, and the analysis result is stored in the memory of the display control unit 114 together with the transferred data. And so on. Next, data can be displayed on the display 66 by operating the operation button 68 of the analysis display device 60. FIGS. 20 to 26 are diagrams showing how various data are displayed on the display 66 by the operation of the operation button 68.

  FIG. 22 is a diagram showing the initial screen of the display 66 and the arrangement of the operation buttons 68. The initial screen shows that three types of display can be selected: A: total, B: pickup, and C: individual. The operation button 68 includes three button groups: a SEL button for selecting three types of display, a NEXT button for changing the month and day, a power ON / OFF, and an ENT button for confirming or reselecting the selection. .

  FIG. 21 shows a state of the display screen when the cursor is set to A: on the display screen by the SEL button, the selection is confirmed by the ENT button, and A: total is selected. Similarly, FIG. 22 shows that B: Pickup is selected, and (a) shows the first three items displayed among the six items that can be displayed by the pickup, and (b) shows the next 3 items by operating the NEXT button. Shows how items are displayed. FIG. 23 shows C: Individual, (a) shows the display of the first two items, and (b) shows the display of the second two items.

  FIG. 24 shows that the initial screen of the display 66 can further display two types of D: history total and E: history pickup. FIG. 25 is a diagram showing an example in which, when D: history total is selected, FIGS. 26A and 26B select E: history pickup and display each item.

  The analysis display device 60 can further write data transferred from the respiratory data collection device 10 via the input / output ports 34 and 64 and analysis result data to the memory card 80. FIG. 27 shows a state in which the data transferred to the memory card 80 is subjected to more detailed data analysis using a personal computer (PC) 150 which is an analysis display device having more functions than the analysis display device 60. FIG. The PC 150 includes an adapter 152 for performing data input / output from the memory card 80. As the adapter 152, a PCMCIA card adapter or the like can be used. The PC 150 that has received the data from the memory card 80 via the adapter 152 performs more detailed data analysis using appropriate data analysis software, and via external communication such as e-mail via a communication line such as the Internet line 154. The data and the like can be further transmitted to an organization, etc., and judgments and instructions can be asked.

  As described above, the respiration data collected by the respiration data collection device 10 can be effectively used in various ways using an analysis display device having a data transfer function, a data analysis function, a data transmission function, and the like. In the above, an example of (respiration data collection device 10 -analysis display device 60 -memory card 80 -PC 150 -external transmission) has been described. However, other usage forms, for example, input of the respiration data collection device 10 removed from the face are described. A usage form such as directly connecting the output port 34 and an appropriate input / output adapter of the PC 150 by a signal jack may be used.

  28 and 29 are display examples of data analyzed by the PC 150. FIG. FIG. 28 is a screen showing the analysis result of the number of occurrences per day, the respiration waveform, the nasal breathing and mouth breathing, the occurrence status such as the ratio based on the number, the number of apneas per day, the apnea accumulation time, the apnea frequency, etc. Are summarized. This data can be used as a judgment material for going to a doctor or as a judgment material for necessity of treatment. FIG. 29 is a screen showing the results of lifestyle history analysis. As an expression of daily health, physical condition before sleep, awakening refreshment, drinking, smoking, etc. are apnea data, nasal breathing and mouth breathing occurrence data. It is related and summarized. By keeping a history of health conditions in this way, lifestyle habits can be specifically checked.

  A pyroelectric polymer film can be used for detection of respiratory sounds. Since the pyroelectric polymer film is a so-called piezo film, vibrations such as airflow movement are transmitted to the film surface, and an electric signal generated thereby is detected. Since the pyroelectric polymer film is thin and lightweight, the burden on the subject can be reduced. An example of a respiratory sound sensor using a pyroelectric polymer film based on the respiratory sound sensor 40 described in FIG. 4 will be described below. Elements similar to those in FIG. 4 are denoted by the same reference numerals, and detailed description thereof is omitted.

  FIG. 30 is an exploded view of the respiratory sound sensor 200 when the pyroelectric polymer film 210 is attached to the opening surface of the cylinder 212 whose bottom surface is blocked, and this is used as a respiratory sound detector. Here, the breathing sound sensor 40 described with reference to FIG. 4 is different from the respiratory sound sensor 40 in the microphone holding frame 42 in which the pyroelectric polymer film 210 is pasted in the hole 49 into which the condenser microphone is fitted. This is where 212 is fitted and fixed. The thickness of the pyroelectric polymer film 210 may be about 20-40 μm, for example. The cylinder 212 can have a diameter of about 12 mm and a height of about 1 mm.

  FIG. 31 shows a respiratory sound sensor 220 in which the ceiling portion of the bridge-shaped support frame 224 is made slightly thicker, a recess 226 having a rectangular opening is formed therein, and a pyroelectric polymer film 222 is attached to the opening. FIG. That is, since the air chamber sealed by the recess 226 provided in the support frame 224 and the pyroelectric polymer film 222 is formed, it is easy to detect the movement of the airflow flowing on the surface of the pyroelectric polymer film 222.

  FIG. 32 is a diagram showing a respiratory sound sensor 220 in which a pyroelectric polymer film 222 is attached to the inner surface side of a thin metal plate 234 bent into a bridge shape. The metal thin plate 234 is preferably a metal material having a spring property. For example, a stainless thin plate having a thickness of about 0.2 mm can be used. After attaching the pyroelectric polymer film 222 to the metal thin plate 234, it is preferable to coat the surface with a more flexible resin. As the coating resin, for example, a silicon resin can be used. Since the metal thin plate 234 has a bridge shape, has a spring property, and the coating resin is also flexible, it is attached to the pad plate 26 described with reference to FIG. 2 with a pair of hooks 22a and 22b. Even if it is bent according to the shape of the face of the person being measured, it can be followed sufficiently while changing the shape. Therefore, it is possible to improve the fit when the person to be measured is attached.

  FIG. 33 is a diagram showing a state in which the pyroelectric polymer film 260 is wound into a cylindrical shape, thereby forming a respiratory sound sensor 240 that detects respiratory sounds. FIG. 34 is an exploded view thereof. The respiratory sound sensor 240 includes left and right circuit packages 242a and 242b and a connecting pipe 244 that connects the left and right circuit packages 242a and 242b. The pyroelectric polymer film 260 is wound into a round cylinder so as to be fixed at both ends of the connection tube 244. Thereafter, it is preferable to coat the surface with a resin having flexibility. Silicon resin can be used as the coating resin. The size of the connecting tube 144 is such that the length of the portion between the left and right circuit packages is about 12 mm, and the pyroelectric polymer film 260 is attached at the portions of about 1 mm at both ends. The diameter of the attachment parts at both ends is about 2-3 mm, the diameter between the attachment parts is about 0.2 mm smaller than that, and the space between the outer shape and the pyroelectric polymer film 260 is a sealed air chamber.

  One end of each of the pair of plug-in signal plugs 246a and 246b is inserted into both ends of the connection pipe 244. Each of the other end portions of the pair of plug-in signal plugs 246a and 246b has a plug shape, and is inserted into connection ports 250a and 250b provided in the left and right circuit packages 242a and 242b, respectively. The pair of plug-in plugs 246a and 246b are plugs that can transmit electrical signals, receive respiratory sound signals from the pyroelectric polymer film 260, and transmit them to the collector circuit 90 built in the left and right circuit packages 242a and 242b. The left and right circuit packages 242a and 242b have a function of transmitting signals.

  FIG. 35 is a view showing a respiratory sound sensor 270 provided with arms 274a and 274b having flexibility on both sides of the connecting pipe 244. FIG. The material of the arm portions 274a and 274b is preferably a plastic resin rich in flexibility. For example, silicon rubber or the like can be used. Insertion signal plugs 278a and 278b are provided at the ends of the arm portions 274a and 274b. Conductive wires 276a and 276b that also serve as signal lines are arranged along the arm portions 274a and 274b. The conductive wires 276a and 276b may be disposed along the outer periphery of the arm portions 274a and 274b, and may be coated with a flexible resin from above, or embedded in the arm portions 274a and 274b. The conductive wires 276a and 276b have a function of a support or a core when the arms 274a and 274b are deformed according to the shape of the face of the measurement subject. As the conductive wires 276a and 276b, metal wires rich in elasticity and flexibility, for example, copper wires having a diameter of about 1 mm can be used. With this configuration, it is easy to change the shape of the breathing sound sensor 270 in accordance with the shape of the face of the person to be measured as shown by the arrow in FIG. Thus, the fitting feeling is improved.

  FIG. 36 shows the state of signals detected by the pyroelectric polymer film in nasal breathing, with the horizontal axis representing time and the vertical axis representing voltage. FIG. 37 shows the state of detection signals in mouth breathing, with the horizontal axis and vertical axis similar to FIG. Compared with FIGS. 9 and 10 for the condenser microphone, in the case of the pyroelectric polymer film, the direction of deflection of the film differs between expiration and inspiration, and the sign of the detection voltage changes accordingly. Understand. Therefore, data preprocessing when acquiring respiratory sounds can be simplified compared to condenser microphones.

  By locating the breathing sound sensor in the nostril, detection of nasal breathing and detection of mouth breathing can be performed by the same sensor. In other words, mouth breathing causes the mouth to shake and the throat to ring, causing the bones of the head to vibrate or the muscles to vibrate. Therefore, by pressing the breathing sound sensor against the inner wall of the nostril, the same sensor can detect the airflow due to nasal breathing and the vibration of the inner wall of the nostril such as the nasal septum due to mouth breathing.

  FIGS. 38 and 39 show a breathing data collection device 300 in which a bifurcated beam portion 304 is attached to the deposition pad 302 and condenser microphones 306a and 306b are attached to the tips of the attachment pad 302, and the beam portion 304 is inserted into the nostril. It is a figure which shows a mode that condenser microphone 306a, 306b is hold | maintained so that a nostril may be spread outward. FIG. 40 is an exploded view of the respiratory data collection device 300. The beam portion 304 is made of a flexible plastic resin, and a conductive wire 308 that also serves as a signal line of the capacitor microphones 306a and 306b is embedded therein. As the conductive wire 308, a metal wire rich in elasticity and flexibility, for example, a copper wire having a diameter of about 1 mm can be used. One end of the conductive wire 308 is connected to the capacitor microphones 306a and 306b, and the other end is connected to the plug-in signal plugs 310a and 310b. Corresponding to these plug-in signal plugs 310 a and 310 b, connection ports 312 a and 312 b are provided on the deposition pad 302. In this manner, the attachment pad 302 and the beam portion 304 can be attached and detached by the plug-in signal plugs 310a and 310b and the connection ports 312a and 312b, and when combined, the condenser microphones 306a and 306b A collector circuit built in the landing pad 302 is connected. Further, when the beam portion 304 inserted into the nostril becomes dirty, the beam portion 304 can be easily cleaned by removing it from the deposition pad 302. The deposition pad 302 is provided with an input / output port 314 and an LED 316.

  FIG. 41 is an enlarged view of the beam portion 304. The beam portion 304 is made of a flexible plastic resin such as silicon rubber, and the embedded conductive wire 308 functions as a core material. Therefore, as shown by an arrow in FIG. The shape can be changed according to the situation. Since the shape can be maintained as it is after the shape is changed, the fitting feeling is improved for the person to be measured.

  42 and 43 are views showing a state in which the condenser microphones 306a and 306b provided at the tip of the bifurcated beam portion 326 are held so as to sandwich the nasal septum. In other words, the condenser microphones 306a and 306b at the tips of the beam portion 326 use the elasticity of the conductive wire 308 of the beam portion 326 so that the sound collection surfaces face each other, and the bifurcated tips are respectively attached to the inner walls of the nostrils. It is attached to both nostrils as if pressing. Other elements are the same as those described in FIGS.

  Thus, since the position of the condenser microphone can be fixed using the nostril, the load for fixing the deposition pad to the palate portion with an adhesive sheet or the like can be reduced. For example, the load of deposition is reduced for a measurement subject with a beard or a measurement subject sensitive to an adhesive member or the like.

  Data detected by the breathing sound sensor can be transmitted as it is to an external receiving device by wireless means. By doing in this way, the electronic circuit part in a respiration data collection device can be decreased, weight reduction and size reduction can be achieved, and the load of deposition can be reduced. In the following description, elements common to those in FIGS. 5 and 6 are denoted by the same reference numerals, and detailed description thereof is omitted.

  FIG. 44 is a diagram illustrating a state in which a signal 352 in an inaudible frequency band is transmitted from the respiratory data collection device 305 to which the measurement subject is attached toward the reception device 360. FIG. 45 is a diagram showing details of the receiving device 360 and the respiratory data collecting device 305. The receiving device 360 includes a parabolic antenna 362, a flexible antenna support 364 having a signal line therein, and an analysis analysis display device 370 connected by the parabolic antenna 362 and a signal line passing through the antenna support 364. The analysis display device 370 has a display 66, operation buttons 68, and a memory card 80 insertion slot 72. The respiration data collection device 350 is provided with a piezoelectric body 354, which emits a signal 352 in an inaudible frequency band when driven.

  FIG. 46 is a block diagram of a collecting device circuit 380 that is a circuit portion of the respiratory data collecting device 350 and a receiving device circuit 390 that is a circuit portion of the receiving device 360. The collecting device circuit 380 is housed in the left and right circuit package of the respiration data collecting device 350, and the receiving device circuit 390 is housed inside the housing of the analysis display device 370.

  The collector circuit 380 receives an amplifier (AMP) 92 that receives and amplifies the signal detected by the respiratory sound sensor 40, a band-pass filter (BPF) 94 that performs band-pass processing on the amplified signal, and a voltage value of the signal. A VCO (Voltage Controlled Oscillator) 382 that generates a frequency-modulated signal in response to the signal, an amplifier 92 that amplifies the modulated signal, and a piezoelectric body 354 that is driven by the amplified signal and emits a signal in an inaudible frequency band. Including. As the piezoelectric body 354, a commercially available piezoelectric buzzer or the like can be used.

  The receiver circuit 390 includes a microphone 392 that receives a modulation signal radiated from the piezoelectric body 354, an amplifier 92, a bandpass filter 94, and a control unit 394. The control unit 394 has a function of demodulating the received modulation signal as respiratory sound data. In addition, the demodulated respiratory sound data is subjected to data analysis processing such as tabulation and stored in the memory together with the demodulated data. Further, the demodulated data and analysis result data are subjected to image processing or the like and output to the display 66. Further, it has a function of outputting the received data and analysis result data to the memory card 80 via the memory interface 116.

  FIG. 47 is a diagram for explaining how the respiratory signal is modulated and demodulated in the collector circuit 380 and the receiver circuit 390. In these figures, the horizontal axis represents time and the vertical axis represents voltage, and the scale of the horizontal axis in FIG. 47 (a) is about 1/2 of the scale of the horizontal axis of (b)-(e). It is shortened.

  FIG. 47A shows a respiration signal 400 detected by the respiration sound sensor 40. In this case, the signal detected by the pyroelectric polymer film is taken as an example. FIG. 47B shows a modulation signal 402 that is frequency-modulated according to the voltage value of the respiratory signal 400 at each time. That is, frequency modulation is performed in which the frequency is increased when the voltage value of the respiration signal 400 is large and the frequency is decreased when the voltage value is small. This modulation can be performed by the function of the modulation VCO 382. The piezoelectric body 354 is driven by the modulation signal, and a sound wave corresponding to the piezoelectric body 354 is emitted into the air. Here, the modulation frequency band and the characteristics of the piezoelectric body 354 are set so that the radiated sound wave is in an inaudible frequency band. In this way, it is possible to prevent disturbing the sleep of the non-measuring person by the emitted sound wave.

  FIG. 47 (c) is a diagram showing the received signal 404 received by the microphone 392. Basically, the waveform is the same as that in FIG. 47 (d) shows a pulse signal 406 obtained by shaping the received signal 404 into a rectangular wave, and FIG. 47 (e) shows a demodulated signal 408 obtained by converting the frequency of the pulse signal 406 into a voltage value and returning it to respiratory data. Show. These demodulation processes can be performed by the function of the control unit 394.

  In this way, the respiratory data is demodulated in real time in the receiver circuit 390. The demodulated respiratory data is temporarily stored in the memory or the like of the control unit 394, and data analysis is performed after the data for one day is collected. By operating the operation button 68, the respiratory sound data and the analysis result are displayed on the display 66. Can be displayed. Further, the data can be written into the memory card 80.

  About the circuit operation | movement of a respiration data collection device, it can be set as sleep mode during the period which is not required for detection of a respiration sound, and its data processing. For example, as can be seen from FIGS. 9 and 10 which are raw data of respiratory sounds, and FIGS. 11 and 15 showing the process of data processing of these, the respiratory sounds repeatedly appear with a periodicity of the respiratory pitch. That is, periods in which no breathing sound is detected also appear periodically. The time required to process the respiratory sound data is much faster than the length of time to detect the respiratory sound, so the circuit part including the respiratory sound sensor of the respiratory data collection device is almost the time to detect the respiratory sound. It only needs to work. Accordingly, in other periods, it is possible to set a sleep mode in which only necessary portions such as a clock are operated and the operations of the remaining circuit portions are stopped.

  The timing for entering the sleep mode is to estimate the breathing pitch, automatically enter the sleep mode according to the estimated breathing pitch, and cancel the sleep mode. As an estimated value of the breathing pitch, an initial reference breathing pitch obtained by the teaching process or an average breathing pitch that is sequentially updated in the running process can be used. The setting of the sleep period in which only a necessary part such as a clock is operated can be set with a margin period before and after the period required for detection of respiratory sounds and data processing. The margin period is set in anticipation of changes in the respiratory pitch, and can be determined based on, for example, the standard deviation of the average respiratory pitch.

As an example, an average breathing pitch is set to 3.5 sec, its standard deviation is set to 0.2 sec, and a time required for detection of nasal breathing sound or mouth breathing sound and data processing is set to 1.2 sec. The case margin period, twice the standard deviation prior to detection, if set standard deviations after detection, the estimated time at which the breath sound appears as T _0, can set the timing related to the sleep mode as follows .

The release start time of the sleep mode is a time (T ₀ −2 × 0.2 sec = T ₀ −0.4 sec). From here, 1.8 sec up to (T ₀ +1.2 sec + 0.2 sec = T ₀ +1.4 sec) is used for respiratory sound detection and data processing. Then, the _(T 0 + _1.4sec) sleep mode starts from, 1.7sec until the next sleep mode release start time _{(3.5sec + T 0 -0.4sec = T} 0 + 3.1sec) becomes the sleep period . Assuming that the power consumption in the sleep mode is much lower than the power consumption during operation, the power consumption of the entire respiratory data collection device is 1.8 / 3.5 = 0.51 compared to the case where the sleep mode is not adopted. Can be reduced.

  Among the margin periods, the margin period after detection of the breathing sound is set to a predetermined threshold value for the breathing sound level, and when it falls below that threshold, the margin period ends, that is, the sleep period starts. You can also

It is a figure which shows a mode that the respiratory data collection device in embodiment which concerns on this invention is affixed on the skin of a palate part. It is an exploded view of the respiration data collection device in an embodiment concerning the present invention. It is a reverse view of the pad board in embodiment which concerns on this invention. It is the exploded view which looked at the respiration sound sensor in the embodiment concerning the present invention from the back. It is a figure which shows the display apparatus which receives the data memorize | stored in the respiration data collection device in embodiment which concerns on this invention, and displays the content. It is a block diagram about a collection device circuit and a display device circuit in an embodiment concerning the present invention. It is a flowchart which shows the whole teaching process in embodiment which concerns on this invention. It is an internal flowchart of the respiratory sound acquisition process in embodiment which concerns on this invention. In embodiment which concerns on this invention, it is a figure which shows the raw signal of the condenser microphone in nasal respiration, and the signal after this differentiation. In embodiment which concerns on this invention, it is a figure which shows the raw signal and differential signal of a capacitor | condenser microphone in mouth respiration. In embodiment which concerns on this invention, it is a figure which shows the signal after carrying out the addition process for every 100 msec what performed the absolute value process of the post-differentiation signal of mouth breathing, and the signal after differentiation. It is an internal flowchart of the confirmation process by the to-be-measured person in embodiment which concerns on this invention. In embodiment which concerns on this invention, it is a figure which shows a mode that the brightness of notification light is gradually weakened with progress of time. It is an internal flowchart of the respiration pitch acquisition process in embodiment which concerns on this invention. It is a figure which shows the mode of the data processing of the respiration pitch acquisition process in embodiment which concerns on this invention. It is a flowchart of the whole running process in embodiment which concerns on this invention. It is an internal flowchart of the respiration pitch monitoring process in embodiment which concerns on this invention. It is an internal flowchart of the apnea monitoring process in embodiment which concerns on this invention. It is an internal flowchart of the completion | finish process process in embodiment which concerns on this invention. In an embodiment concerning the present invention, it is a figure showing an example of data displayed on a display by operation of an operation button. In an embodiment concerning the present invention, it is a figure showing an example of data displayed on a display by operation of an operation button. In an embodiment concerning the present invention, it is a figure showing an example of data displayed on a display by operation of an operation button. In an embodiment concerning the present invention, it is a figure showing an example of data displayed on a display by operation of an operation button. In an embodiment concerning the present invention, it is a figure showing an example of data displayed on a display by operation of an operation button. In an embodiment concerning the present invention, it is a figure showing an example of data displayed on a display by operation of an operation button. In an embodiment concerning the present invention, it is a figure showing an example of data displayed on a display by operation of an operation button. In an embodiment concerning the present invention, it is a figure showing signs that data transferred to a memory card is analyzed in more detail using PC. In embodiment which concerns on this invention, it is a figure which shows the screen of the analysis result of the daily occurrence number. In embodiment which concerns on this invention, it is a figure which shows the screen of the analysis result of a lifestyle history. It is an exploded view of the respiratory sound sensor of other embodiment. It is an exploded view of the respiratory sound sensor of other embodiment. It is a figure which shows the respiratory sound sensor of other embodiment. It is a figure which shows the respiratory sound sensor of other embodiment. It is an exploded view of the respiratory sound sensor of other embodiment. It is an exploded view of the respiratory sound sensor of other embodiment. In other embodiment, it is a figure which shows the mode of the signal which the pyroelectric polymer film detected in nasal respiration. In other embodiment, it is a figure which shows the mode of the signal which the pyroelectric polymer film detected in mouth respiration. It is a figure which shows the respiratory data collection apparatus of other embodiment. It is a figure which shows the respiratory data collection apparatus of other embodiment. It is an exploded view of the respiration data collection device of other embodiments. It is an enlarged view of the beam part in other embodiment. It is a figure which shows the respiratory data collection apparatus of other embodiment. It is a figure which shows the respiratory data collection apparatus of other embodiment. It is a figure which shows the respiratory data collection apparatus of other embodiment. It is detail drawing of the respiration data collection device of other embodiments. FIG. 5 is a block diagram of a collector circuit and a receiver circuit in another embodiment. In other embodiment, it is a figure explaining the mode of a modulation | alteration and demodulation of a respiration signal.

Explanation of symbols

  2,4 Airflow 10,300,305,350 Respiratory Data Collection Device, 20,302 Deposited Pad, 22a, 22b Hook, 24a, 24b, 242a, 242b Circuit Package, 26 Pad Board, 30 Airflow Bank Member, 34, 64,314 Input / output port, 36a, 36b Adhesive sheet, 40, 200, 220, 240, 270 Respiratory sound sensor, 42 Microphone holding frame, 50, 306a, 306b Condenser microphone, 60, 370 Analysis display device, 66 Display, 68 Operation button, 72 insertion slot, 80 memory card, 90, 380 collecting device circuit, 98 CPU, 100 flash memory, 110 display device circuit, 114 display control unit, 116 memory interface, 144,244 connecting pipe, 150 PC, 210, 2 2,260 Pyroelectric polymer film, 224 Support frame, 234 Metal thin plate, 276a, 276b, 308 Conductive wire, 304, 326 Beam part, 360 receiver, 354 piezoelectric body, 382 VCO for modulation, 390 receiver circuit 392 Microphone, 394 control unit.

Claims (15)

Respiratory data is analyzed by receiving respiratory data from a respiratory data collection device that attaches to the face and collects and stores respiratory data and a respiratory data collection device that is removed from the face after the collection of respiratory sound data. A respiratory data collection system including an analysis display device for displaying,
Respiratory data collection device
A detachable deposition pad that deposits near the nostril or mouth of the face;
A respiratory sound sensor that is attached to the deposition pad and detects respiratory sounds;
A data collection unit that is attached to the deposition pad and collects and stores data detected by the respiratory sound sensor;
With
The analysis display device comprises a display for displaying at least one of respiratory sound data or analysis result of the respiratory sound data. The respiratory data collection system according to claim 1,
The deposition pad has an output port for transferring data to the analysis display device,
The analysis display device
An insertion portion for receiving the deposition pad removed from the face after the collection of respiratory sound data is completed;
An input port provided in the insertion portion and detachably connected to the output port of the deposition pad;
A respiratory data collection system comprising: The respiratory data system of claim 1, wherein
The analysis display device includes an output unit that outputs at least one output data of the respiratory sound data or the analysis result of the respiratory sound data based on the data transferred from the respiratory data collection device,
The output unit includes at least one of a writing unit that writes output data to a portable memory, or a transmission unit that transmits output data to the outside through a communication line. The respiratory data collection system according to claim 1,
The breathing sound sensor detects the flow of air through the nostrils and the flow of air from the mouth through the upper airway,
Based on the data detected by the breathing sound sensor, the data collection unit stores the nasal breathing sound and the mouth breathing and stores them,
The analysis display device displays at least one of the data on the occurrence status of each of the nasal breathing sound and the mouth breath, or the association data between the occurrence status and the lifestyle habits. The respiratory data collection system according to claim 1,
The breathing sound collection apparatus includes a breathing data collection system comprising attachment / detachment means for detachably attaching the breathing sound sensor to the deposition pad. The respiratory data collection system according to claim 1,
The deposition pad has a deposition portion shaped along the outer surface of the palate between the nostril and the mouth,
The respiratory sound sensor is a pyroelectric polymer film provided on a deposition portion, and is a pyroelectric polymer film attached to a thin metal plate and coated with a flexible resin. Respiratory data collection system. The respiratory data collection system according to claim 1,
To the deposition pad, a conductive wire is embedded in a flexible resin and a beam part whose outer shape can be changed is attached.
The respiratory sound collecting system, wherein the respiratory sound sensor is held at the tip of the beam portion, and a signal terminal thereof is connected to the data collecting unit via a conductive wire. The respiratory data collection system according to claim 1,
A beam portion having a bifurcated shape in which a conductive elastic wire is embedded in a flexible resin and an outer shape can be inserted into both nostrils is attached to the deposition pad,
The breathing sound sensor is held at the tip of the beam part, and is attached to both nostrils by using the elasticity of the conductive elastic wire of the beam part so that each bifurcated tip is pressed against the inner wall of each nostril. Respiratory data collection system. The respiratory data collection system according to claim 1,
The data collection department
A breathing sound for obtaining an identification level for discriminating between the magnitude of mouth breathing sound passing through the mouth and the magnitude of nasal breathing sound passing through the nostrils, based on a signal indicating whether the subject's breathing is mouth breathing or nose breathing An identification means;
A breathing sound distinguishing means for distinguishing a breathing sound into a nasal breathing sound or a mouth breathing sound based on the determined discrimination level;
A respiratory data collection system comprising: The respiratory data collection system according to claim 1,
The data collection department
Pitch measuring means for measuring a respiratory pitch based on a signal detected by the respiratory sound sensor;
Pitch notification means for displaying and notifying the pitch corresponding to the measured breathing pitch;
A remeasurement signal receiving means for receiving a remeasurement instruction signal output by the person to be measured based on the displayed notification pitch;
When receiving a remeasurement instruction signal, measure the respiration pitch again. ,
A respiratory data collection system comprising: The respiratory data collection system according to claim 10,
The pitch information means gradually weakens the display intensity as the measurement time elapses and induces the person to be measured to sleep. The respiratory data collection system according to claim 1,
The data collection department
Pitch measuring means for measuring a respiratory pitch based on a signal detected by the respiratory sound sensor;
An average pitch calculating means for sequentially calculating the latest average respiratory pitch based on the data of the plurality of respiratory pitches measured the latest;
The average pitch calculation means calculates the standard deviation of the plurality of average breathing pitches so far, determines a normal range of the breathing pitch based on the obtained standard deviation, and determines the plurality of breathing pitches measured most recently. A respiratory data collection system characterized in that, when data out of the normal range is included in data, the latest average respiratory pitch is recalculated by excluding this data. The respiratory data collection system according to claim 1,
The data collection department
An estimation means for estimating a respiratory pitch;
Sleep means for causing the circuit operation to sleep after the detection of the breathing sound until the timing required for the next breathing sound detection based on the estimated breathing pitch;
A respiratory data collection system comprising: The respiratory data collection system according to claim 1,
The data collection department
A signal presence / absence determining means for determining the presence / absence of a signal from the respiratory sound sensor;
An end signal receiving means for receiving a measurement end signal output by the measured person;
When there is no signal from the breathing sound sensor and it is determined that the breathing data collection device has been removed, deletion means for deleting the last apnea data;
Ending means for ending data processing based on the determination result of the signal presence / absence determining means or acquisition of the measurement end signal;
A respiratory data collection system comprising: A respiratory data collection system comprising: a respiratory data collection device that attaches to a face and collects respiratory data; and an analysis display device that analyzes and displays respiratory data in response to the transfer of respiratory data from the respiratory data collection device,
Respiratory data collection device
An attachment pad that is detachably attached to a part of the face;
A respiratory sound sensor that is attached to the deposition pad and detects respiratory sounds;
Transmitting means provided on the deposition pad, modulating the data detected by the respiratory sound sensor into a signal in a non-audible frequency band, and transmitting the signal to an external receiving means;
With
The analysis display device
Receiving means for receiving a signal in a non-audible frequency band transmitted by the transmitting means, and demodulating the respiratory sound data;
A display for displaying at least one of the demodulated respiratory sound data or the analysis result of the respiratory sound data;
A respiratory sound data collection system comprising:

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