JP2017192825A - Human health condition detecting device - Google Patents

Abstract

PROBLEM TO BE SOLVED: To provide a human health condition detecting method and device capable of recognizing the feature of being human and determining a human health condition.SOLUTION: The method and device compares signals of body vibration caused by vibration caused by human heart beat, pulmonary respiration, snoozing, or the like, with each other, and performs human health diagnosis on the basis of a result of the comparison. Then, the method and device performs the health diagnosis continually for 24 hours without constraint of the person.SELECTED DRAWING: Figure 5

Description

  The present invention detects a person's health condition by detecting a person's lung respiratory activity and vibration caused by the heartbeat with a vibration sensor in a bed and a bed placed on the floor so that the person's health condition can be detected for 24 hours. The present invention relates to a method and a health condition detection apparatus.

  It is necessary for nursing work to grasp the patient's condition while sleeping in bed, but in order to reduce the burden on the caregiver, the patient's condition is automatically monitored. A notification system is desired. In the conventional system, a method in which a blood pressure monitor is attached to the fingertip or a vibration meter is wound around the waist is used in close contact with the patient's body.

  In this way, the method of restraining the patient and grasping the state is highly reliable in that a signal is always obtained because the sensor is brought into close contact with the body, but the patient is disliked and the spread has been hindered. For this reason, unconstrained type systems have been considered.

  As an unconstrained type, use of a vibration sensor using a piezoelectric element such as a piezo element as the vibration sensor has been studied. For example, a piezoelectric body made of a polymer material, a first electrode holding portion that is disposed on one side of the piezoelectric body and that carries a signal electrode on a first insulator, and a piezoelectric body that is disposed on the other side of the piezoelectric body. And a second electrode carrying part carrying a ground electrode on the second insulator, wherein the signal electrode and the ground electrode overlap each other in the first electrode carrying part and the second electrode carrying part. There is a thing (patent document 1).

  In addition, a piezoelectric body obtained by adding a clay treated with a quaternary ammonium salt or a quaternary ammonium salt to polyvinylidene fluoride, which is a homopolymer of vinylidene fluoride, and then performing polarization treatment without stretching is provided. Yes (Patent Document 2).

  Furthermore, a first polymer piezoelectric body having a first surface and a second surface having a front-back relationship with respect to the first surface and generating a potential by being pressurized, and a first polymer piezoelectric A signal electrode disposed on the second surface side avoiding the outer edge portion of the body and a first ground electrode disposed so as to cover a portion corresponding to the signal electrode on the first surface, and loading a surface load Then, there is a piezoelectric sensor in which the stress generated in the portion where the signal electrode of the first polymer piezoelectric material is disposed is larger than the stress generated in the outer edge portion where the signal electrode is not disposed (Patent Document 3).

  An electrode-integrated shield terminal for transmitting a potential difference generated between a signal electrode and a ground electrode, wherein the signal electrode and the ground electrode are insulated, and the first surface and the first surface have a front-back relationship. A plate-like first insulating layer having a second surface, a film-like first ground electrode formed on the first surface, a signal electrode formed on the second surface side, and a signal A device that generates a potential difference between an electrode and a ground electrode, a signal terminal connected to the signal electrode, and a ground terminal. The electrode is shielded by wrapping the signal terminal and the ground terminal with an insulating layer and the ground electrode. A body-type shield terminal is known (Patent Document 4).

  Detection sensors for detecting a human health condition using such a piezoelectric sensor have been developed. For example, using a PVDF membrane, a respiratory signal, a pulse signal, and a body movement abnormality signal are detected at the same time, and a signal is separated and extracted using a difference in each frequency band and signal intensity, and is compared with an elapsed time using an electronic circuit. An apparatus that performs statistical processing is known (Patent Document 5).

  Also known is a device having a biological vibration sensor means of a biological vibration sensor of a porous polypropylene electret film that detects vibration due to heartbeat of a living body, vibration due to lung respiration, vibration due to body movement and outputs a vibration voltage signal. (Patent Document 6).

  Further, it is constituted by a fluctuation amount detecting means for detecting the physical fluctuation amount of the bed where the subject stays and a biological data detecting means for detecting the biological data of the subject from the fluctuation amount detected by the fluctuation amount detecting means. A biological data detection device is known (Patent Document 7).

  In addition, the first determination means based on the output of the piezoelectric sensor determines the operation information indicating that the user has sat on the toilet seat, and the second determination means detects the biological information such as the user's heartbeat after that. Is known (Patent Document 8).

  Also, a heartbeat / respiration / activity amount for a small animal having a support plate, a plurality of spacers arranged on the support plate, and a vibration transmission plate to which a piezoelectric element sensor is attached and supported on the plurality of spacers A detection device is known (Patent Document 9).

JP 2008-122215 A JP2011-192666A JP 2008-304558 A JP 2008-304223 A JP 2005-253924 A JP 2008-102893 A JP 2004-313495 A JP 2005-110910 A International Publication No. 2007/029326

  The piezoelectric sensors described in Patent Documents 1 to 4 can easily detect various vibration signals generated by humans. Moreover, the shrinkage | contraction resulting from extending | stretching can be suppressed and it can detect with sufficient sensitivity, without receiving the influence of external noise. Further, the electrode-integrated shield terminal that is easy to manufacture can be provided, and various vibration signals generated by humans can be converted into electric signals. However, this type of sensor does not mention a countermeasure when the mounting position of the sensor is shifted due to movement of a person. Further, there is no mention of noise caused by electrostatic pulses caused by friction with bedding or the like due to movement of a person.

  The invention described in Patent Document 5 can detect a pulse or respiratory signal generated by a person with PVDF, detect a difference between a frequency band and a signal intensity, separate a vibration signal into a plurality of signals, and perform statistical processing. Although it is an invention that can be performed, it is particularly aimed at detecting sleep apnea syndrome with respiratory abnormalities, and does not describe a specific configuration of a detection sensor for signal detection as in the present invention.

  The invention described in Patent Document 6 describes a technique for detecting a vibration signal generated in the body, but does not specifically describe how to separate the vibration signal. Perhaps each sensor type has a sensor.

  The invention described in Patent Document 7 detects a vibration signal obtained from a person through a frame of a bed, and does not detect and extract vibration from the body separately from the vibration sensor as in the present invention. Absent.

  In the invention described in Patent Document 8, a piezoelectric sensor is arranged on a toilet seat, and motion information and biological information are accurately obtained from vibration detected by the toilet seat. Is not detected separately from the vibration sensor. The configuration of vibration signal detection is clearly different from the present invention.

  The invention described in Patent Document 9 is such that a small animal is placed on a detection device, and a biological signal from the small animal can be detected with high sensitivity. It is not designed to detect well.

  The present invention has been made in view of such a problem. A vibration signal from a person is separated into a plurality of detection signals using a filtering separation circuit, and these signals are detected with high accuracy for 24 hours. It is an object of the present invention to provide a human health condition determination method and a human health condition determination device that can determine the health condition of the person without restriction.

  In order to solve the above-described problems, the present invention detects a vibration of a body emitted by a person in a predetermined place by a vibration signal sensor unit, and performs a predetermined signal processing on the vibration signal generated by the vibration to obtain a vibration signal. In the human health condition determination method for determining the health condition of a patient based on the obtained vibration signal, the vibration signal sensor unit detects a signal from a human body and performs preprocessing of the detected signal. And filtering the preprocessed signal into a plurality of signals to obtain at least two signals of respiratory vibration, heartbeat vibration, snoring, and body motion signal. Here, snoring includes those that generate sounds such as bruxism, sneezing, and sleeping.

  Further, the vibration signal sensor unit is characterized in that the bottom plate, the cushion member, the vibration sensor main body, and the vibration collecting plate are layered in this order from the bottom. In addition, the sensor body includes a vibration sensor or a vibration sensor, an insulating layer, and upper and / or lower shielding layers.

  The insulating layer may have a thickness of 1 μm or more, or a capacitor constituted by the upper shielding layer, the insulating layer, and the positive electrode layer may have a capacitance of 1 μF or less. The vibration collecting plate may transmit vibration generated in a human body part to the vibration signal sensor unit without being attenuated.

  Further, the hardness of the vibration collecting plate is higher than the hardness of the vibration signal sensor unit. Further, the preprocessing is characterized in that the amplitude of the input vibration signal is limited, the limited output is received to perform a detection operation, the detection output is amplified, and a DC component of the detected signal is removed.

  Further, the vibration signal sensor means detects vibrations of the body emitted by a person in a predetermined place, and performs a predetermined signal processing on the vibration signal generated by the vibration to obtain a vibration signal. Based on the obtained vibration signal, the patient In the human health condition determination apparatus for determining the health condition of the person, a detection means for detecting a signal from the human body by the vibration signal sensor means, a pre-processing means for pre-processing the detected signal, and a pre-processing means for pre-processing Filtering means for filtering the processed signal, separation means for receiving the output of the filtering means and separating it into a plurality of signals, breathing sound, heartbeat vibration, voice, snoring, and body movement from the output of the separation means Signal output means for obtaining at least two of the signals.

  The vibration signal sensor means may be composed of one or more of a vibration sensor main body or a vibration sensor main body and a bottom plate, a cushion member, and a vibration collecting plate that are stacked on top and bottom thereof. Further, the vibration sensor main body includes a vibration sensor or a vibration sensor, an insulating layer, and upper and / or lower shielding layers.

  The insulating layer may have a thickness of 1 μm or more, or a capacitor constituted by the upper shielding layer, the insulating layer, and the positive electrode layer may have a capacitance of 1 μF or less. The vibration collecting plate may transmit vibration generated in a human body part to the vibration signal sensor unit without being attenuated.

  In addition, the preprocessing circuit limits the amplitude of the input vibration signal, a detection circuit or an integration circuit that receives the output of the limitation circuit and performs a detection operation, and amplifies the output of the detection circuit or the integration circuit It is characterized by comprising an amplifier circuit and a DC removal circuit that removes the DC component of the detected signal.

  The detection circuit includes a diode, a resistor, and a capacitor, and receives only an input vibration signal to extract only a heartbeat signal of a person. The detection circuit can be realized not only by such passive elements but also by an active circuit using an operational amplifier or IC.

  Further, the vibration sensor is an electrode terminal embedded type. Further, the vibration signal sensor unit, a signal processing unit that processes a signal detected by the vibration signal sensor unit, and a signal output unit that outputs a signal obtained by the signal processing unit are integrated. And

  Here, the signal output means refers to means for detecting a signal based on human vibration with a vibration sensor, processing a predetermined signal, and outputting the signal to the outside. Further, the thickness of the vibration signal sensor unit is 10 mm or less.

  The material of the vibration collecting plate is a PET plate, a foamed polystyrene plate, a PP plate, an acrylic plate, a cured vinyl chloride plate, a foamed vinyl chloride plate, an aluminum plate, a duralumin plate, a copper plate, an iron plate, or the like. To do.

  In addition, the vibration signal sensor unit detects vibrations of the body emitted by a person in a predetermined place, and performs a predetermined signal processing on the vibration signal from the vibration signal sensor unit to obtain a vibration signal. In the human health condition determination method for determining a patient's health condition based on the above, a signal detected by the vibration signal sensor unit is integrated to obtain a vibration waveform similar to an electrocardiogram.

  In addition, the vibration signal sensor unit detects vibrations of the body emitted by a person in a predetermined place, performs a predetermined signal processing on the vibration signals generated by the vibrations, and obtains a vibration signal. Based on the obtained vibration signal, An apparatus for determining a health condition of a person who determines a health condition is characterized in that an integrating means for integrating the signal detected by the vibration signal sensor unit is provided to obtain a vibration waveform similar to an electrocardiogram.

  Further, in the health condition determination apparatus for determining the presence / absence of a person by counting a pulse group of body movement signals caused by the person's body movement from a vibration of the body emitted by a person at a predetermined place by the vibration sensor, In order to detect only the pulse group of the motion signal, the vibration sensor is covered with an intermediate material for absorbing minute vibrations.

  According to the present invention, it is possible to detect the health state of a person who is a living body for 24 hours without restriction by detecting body vibration caused by vibration of the heart, which is a living body, and vibration due to lung respiration.

It is a figure which shows the example of installation of the apparatus in an Example. It is a block diagram which shows the outline | summary of the apparatus structure in an Example. It is a figure which shows a body motion vibration waveform. It is a figure which shows the structural example of the vibration signal sensor part of this invention. It is a figure which shows the structural example of the vibration sensor main body of this invention. It is explanatory drawing of the example of a connection of the conventional electrode. It is explanatory drawing of the example of a connection of the electrode by this invention. It is an enlarged view of the pressing part by this invention. It is a figure which shows the amplitude waveform of the vibration sensor main body when there is no vibration collection board. It is a figure which shows the amplitude waveform of a vibration sensor when a veneer board-4 mm is used for a vibration collection board. It is a figure which shows the amplitude waveform of a vibration sensor main body when veneer board -2mm is used for a vibration collection board. It is a figure which shows the amplitude waveform of a vibration sensor main body when using PET board-1mm for a vibration collection board. It is a figure which shows the amplitude waveform of a vibration sensor main body when PET board -0.5mm is used for a vibration collection board. It is a figure which shows the amplitude waveform of a vibration sensor main body when a hard vinyl chloride board -0.7mm is used for a vibration collection board. It is a figure which shows the amplitude waveform of a vibration sensor main body when a low foaming vinyl chloride board -1mm is used for a vibration collection board. It is a figure which shows the amplitude waveform of a vibration sensor main body at the time of using low foaming vinyl chloride board -1mm2 sheet for a vibration collection board. It is a figure which shows the amplitude waveform of a vibration sensor main body when using aluminum plate-1mm for a vibration collection board. It is a figure which shows the structure of a vibration taking-out port. It is a figure which shows the detailed structure of a vibration taking-out port. It is a figure which shows the example of arrangement | positioning of a vibration sensor. It is a figure which shows the example of arrangement | positioning of a vibration sensor. It is a figure which shows the state which connects one or four vibration sensors. It is a figure which shows the example which connected the four vibration sensors in parallel. It is a figure which shows the example which connected the four vibration sensors in series. It is a figure which shows the normal state of an electrocardiogram waveform. It is a figure which shows the example of an electrocardiogram waveform. It is a figure which shows the heartbeat vibration output waveform extracted with the vibration sensor of this invention. It is a figure which shows the waveform similar to the monitor waveform in a general electrocardiogram. It is a figure which shows a heart rate. It is explanatory drawing of a heartbeat and a peak. It is explanatory drawing of the setting method of a threshold value. It is a figure which shows the example of whole structure of the input process part of this invention. It is a figure which shows the output waveform of a preamplifier. It is a figure which shows the example which isolate | separates a vibration signal into a several signal. It is a figure which shows an example of the circuit of this invention. It is a figure which shows the other example of the circuit of this invention. It is a figure which shows the other example of the circuit of this invention. It is a figure which shows the waveform which integrated the vibration signal, the waveform which detected both waves, and the waveform which detected half wave.

  Here, a description will first be given of a case where the vibration sensor is arranged in a non-contact manner on the patient and applied to a device that detects the presence / absence of the patient from the vibration sensor. FIG. 1 is a diagram illustrating an installation example of an apparatus in the embodiment. In the bed 11 where it is necessary to detect the presence or absence of a person, the vibration signal sensor means 10 is installed above or below the bed pad 13 or the mattress 12. In the bedding laid on the floor, the vibration signal sensor means 10 is installed above and below the mattress 14. The vibration signal sensor means 10 detects the vibration of the body emitted by the person 15 existing on the bed 11 or the mattress 14, and the presence or absence of the person is determined based on the presence or absence of the body vibration.

  Extracting the pulsation vibration caused by the pulsation of the heart from the body vibration, and the pulsation vibration exceeds the predetermined existence duration, the person 15 is present on the bed 11 or the mattress 14, and the pulsation It is determined that the person 15 is absent when the state without vibration exceeds a predetermined absence continuation time or more. By extracting the pulmonary respiration vibration resulting from pulmonary respiration from the body vibration and the pulmonary respiration vibration exceeds the predetermined existence duration, the person 15 is present on the bed 11 or the mattress 14, and the pulmonary respiration beat When the state where there is no dynamic vibration exceeds a predetermined absence continuation time or more, it is determined that the person 15 is absent.

  The person 15 is present on the bed 11 or the mattress 14 when both the pulsation vibration caused by the heart beat from the body vibration and the pulmonary breathing vibration caused by the pulmonary respiration exceed the predetermined existence duration. The presence of both pulsation vibration and pulmonary breathing vibration exceeds the predetermined absence duration, and the person 15 is absent. Exceeds the predetermined existence duration, the person 15 is present on the bed 11 or the mattress 14, and the state where there is no heel vibration exceeds the predetermined absence duration, the person 15 is absent. It is determined that

  Extracting the pulsation vibration caused by the pulsation of the heart from the body vibration, and the pulsation vibration exceeds the predetermined existence duration, the person 15 is present on the bed 11 or the mattress 14, and the pulsation It is determined that the person 15 is absent when the state without vibration exceeds a predetermined absence continuation time or more. By extracting the pulmonary respiration vibration resulting from pulmonary respiration from the body vibration and the pulmonary respiration vibration exceeds the predetermined existence duration, the person 15 is present on the bed 11 or the mattress 14, and the pulmonary respiration beat When the state where there is no dynamic vibration exceeds a predetermined absence continuation time or more, it is determined that the person 15 is absent.

  FIG. 2 is a block diagram showing an outline of the apparatus configuration in the embodiment. In this block, the vibration sensor 101 which is the vibration sensor means 100 detects a human body vibration as a body vibration electrical signal 102. Here, the vibration sensor 101 is the same as the vibration sensor 30 described later. The body vibration electrical signal 102 is amplified by a differential signal amplification amplifier 110. The pulsating filter means 120 extracts the pulsating vibration electric signal 123 of the pulsating vibration caused by the pulsation of the human heart based on the body vibration electric signal 102.

  The pulmonary respiratory vibration filter means 121 includes a low-pass filter that passes a frequency band equal to or lower than the cut-off frequency set to 1 Hz in the frequency component of the body vibration electrical signal. In this case, the pulmonary respiratory vibration filter means 121 extracts the pulmonary respiratory vibration electrical signal 124 of the pulmonary respiratory vibration caused by the human lung breathing.

  Further, the wrinkle vibration filter means 122 extracts a wobble vibration electric signal 125 of wrinkle vibration caused by a human wrinkle. Further, the body motion vibration filter means 152 extracts a body motion vibration electrical signal 151 caused by a human body motion. As can be seen from the above description, in the present invention, the human vibrational electrical signal is separated by a filter according to the type of vibration, each separated signal is compared with a predetermined threshold value, and the person is based on the comparison result. It is characterized in that the presence / absence of the existence is determined.

  In FIG. 2, 260 is a reference sensor means for outputting a reference value of body motion vibration, and 261 is a storage device for storing various data calculated by the CPU 142. As the storage device 261, for example, a semiconductor storage device or a hard disk device (HDD) is used.

  In this type of filter means, the pulsation filter means 120, the lung respiratory vibration filter means 121, the sputum vibration filter means 122, and the body motion vibration filter means 152 are a low-pass filter (LPF) constituted by a capacitor, a resistor, an operational amplifier, or the like. A high-pass filter (HPF) analog filter or an analog signal that is the body vibration electrical signal 102 is converted into a digital signal by an A / D converter and converted into a digital signal for calculation processing by a CPU (central processing unit). It is possible to configure either one or both of digital filters that perform filtering.

  The digital filter can be configured by an A / D converter and a CPU dedicated to the filter processing unit, but can be processed by the A / D converter 141 and the CPU 142 of the presence / absence determination unit 140. In the presence / absence determination means (also referred to as leaving bed / entrance determination means) 140, when the extracted pulsating vibration electrical signal 123 is an analog signal, the data is digitized using the A / D converter 141, and the CPU 142. The threshold voltage which is the reference for the comparison judgment of the absence / existence is compared.

  Then, based on the comparison result, when the time during which the pulsating vibration electric signal 123 has been detected exceeds the predetermined existence duration, the person can It is determined that it is present in the vicinity of a vibration signal sensor means such as body motion. Further, the time during which the pulsating vibration electric signal 123 is detected is compared with a predetermined existence duration. Then, when the time during which the pulsating vibration electrical signal continues in the state of no detection exceeds a predetermined non-existence duration time, the CPU 142 in the presence / absence determination unit 140 determines that the person is the vibration signal sensor unit 100. It is determined that it is absent in the vicinity of (same as the vibration signal sensor means 10 in FIG. 1).

  Here, the reason why the presence / absence of a person is different is different only by the body motion vibration electrical signal for the following reason. This is because body motion vibrations detect the behavior of a person getting up from the bed or sleeping on the bed, and the behavior is not as frequent as pulsation or breathing. If the body vibration group is at least twice within a predetermined time, it can be determined that the person is getting up from bed or sleeping. Conversely, if the body motion vibration group is less than once within a predetermined time, it can be determined that the person who got up has gone out as it is.

  Note that the body motion vibration has a very large amplitude of the detection signal as compared with the case where a signal such as a pulsation is detected. For example, while the pulsation vibration signal is several tens of mV, the magnitude is 10V. In other words, it is about 1000 times larger than other body vibrations.

  As described above, since the present invention detects four types of vibration using one vibration sensor 101, these four vibration signals are mixed in the output of one amplifier. Therefore, in order to obtain only the body motion signal, the body motion vibration detection means 150 uses an absorber that can absorb weak signals such as pulsation and respiration and prevent signal transmission in the reference vibration sensor 260. By using a vibration sensor configured as described above and using a sensor that does not take in weak signals such as pulsation and respiration, only body vibration can be obtained.

  The magnitude of the body motion signal is 100 times, 1000 times or more larger than other biological signals. By inserting an intermediate material such as a cushion between a person and a vibration sensor, the intermediate material can mechanically absorb these weak biological signals. However, since the body motion signal has a large signal value, only the body motion signal cannot be absorbed.

  As a result, only the body motion signal could be extracted by the vibration sensor in which these intermediate materials were inserted. As the intermediate material, soft organic material, inorganic material fiber, and air layer can be used.

  On the other hand, when a body motion signal and other biological signals are extracted simultaneously by one vibration sensor, the body motion signal is dispersed in a wide frequency band, so that the pulsation and respiration signals are spread over this wide frequency band. A frequency band other than the frequency band in which a biological signal such as can be obtained can be approximately regarded as a body motion signal.

  The body motion signal detection means 150 outputs a body motion vibration electrical signal using the output of the reference sensor means 260. Then, only body motion vibration is detected from the body vibration electrical signal 102. The detected body motion vibration signal is input to the negative input of the differential signal amplification amplifier 110. On the other hand, the body vibration electrical signal 102 is inputted as it is to the positive input of the differential signal amplification amplifier 110. Therefore, the differential signal amplification amplifier 110 outputs the body vibration electrical signal 102 ′ from which the body motion vibration signal is removed.

  The body vibration electrical signal 102 'is input to the pulsation filter means 120, the lung respiration vibration filter means 121, and the sputum vibration filter means 122, and the respective vibration signals are selected. As a result, the pulsation filter means 120 outputs only the pulsatile vibration electrical signal 123, the pulmonary respiratory vibration filter means 121 outputs only the pulmonary respiratory vibration electrical signal 124, and the hemorrhoid vibration filter means 122 outputs the pulsatile vibration electrical signal 124. Only the signal 125 is output.

  On the other hand, the output of the body motion vibration detection means 150 enters the body motion vibration filter means 152, and the body motion vibration filter means 152 outputs only the body motion vibration electrical signal 151.

  FIG. 3 is a diagram showing a body motion vibration waveform. The vertical axis is voltage (V), and the horizontal axis is time and is composed of vibration groups. The horizontal axis is shown at 1 second intervals. As shown in the figure, the amplitude of the body motion vibration waveform is as large as ± 4 to ± 4.5 V, and it can be seen that it is pulsed. The body motion vibration is larger than other vibrations such as pulsation vibration, lung respiration vibration, and hemorrhoid vibration (all outputs are as small as 10 mV).

  The body motion vibration filter unit 152 is configured by an analog or digital filter, converts the input body motion vibration signal into a signal having an optimum amplitude, outputs the signal, and inputs the signal to the presence / absence determination unit 140. As described above, since the body motion vibration signal is pulsed, the pulse signal can be obtained when the body motion vibration filter means 152 differentiates the output. This pulse signal enters the presence / absence determination means 140 as a body vibration electric signal 151.

  The presence / absence determination means 140 gives the pulse signal 151 to the CPU 142. The CPU 142 counts the number of input pulse groups within a predetermined time. If the number of pulse groups is two or more as a result of counting, it is determined that there is a person, and if the number of pulse groups is one or less, it is determined that there is no person.

  Next, a method for detecting a pulsation vibration signal, a lung respiration vibration signal, and a sputum vibration signal will be described. The differential vibration amplification amplifier 110 amplifies the differential signal until the output of the differential signal becomes V order. Each vibration electrical signal extracted in this way can be separated into each vibration signal by the filter means.

  Now, the reporting unit 270 makes a report by lighting an LED or sounding a buzzer based on the presence / absence determination signal 143 from the presence / absence determination unit 140. Or report to the nurse call device or to the outside through the communication line.

  The storage device 261 stores various data created by the CPU 142. For example, the outputs of the pulsation filter unit 120, the lung respiratory vibration filter unit 121, the sputum vibration filter unit 122, and the body motion vibration filter unit 152 are stored in time series.

  Next, the operation of the vibration signal sensor means (10 or 100) used in the present invention will be described. FIG. 4 shows a configuration example of the vibration signal sensor means of the present invention. The vibration signal sensor means 10 (or 100) comprises layers in the order of the bottom plate 26, the cushion member 25, the vibration sensor main body 21, and the vibration collecting plate 27 from the bottom. As the vibration sensor main body 21, a piezo element is preferably used, but other sensors may be used.

  The vibration sensor body 21 needs to cover the entire sensor body 21 with an upper shielding layer (electromagnetic shielding film) and a lower shielding layer (electromagnetic shielding film) in order to eliminate various external noises, particularly electromagnetic noise. It was. Specifically, as shown in FIG. 5, the lower shielding layer (lower electromagnetic shielding film) 32, the vibration sensor 30 (negative electrode layer 51, vibration sensor material (PDF) 53, and positive electrode layer 52 are formed from the bottom. Structure), insulating layer (insulating sheet) 33, upper shielding layer (upper electromagnetic shielding film) 34 in this order. As shown in FIG. 5, the vibration sensor main body 21 includes an upper shielding layer 34, an insulating sheet 33, a vibration sensor 30 and a lower shielding layer 32. An electromagnetic shielding film) and a lower shielding layer (electromagnetic shielding film) cover the vibration sensor 30. However, in the case where the negative electrode line 38 can also serve as the lower shielding layer 32, the lower shielding layer is not necessary.

  In FIG. 5, 37 is a positive (plus) electrode line connected to the positive electrode layer, and 38 is a negative (minus) electrode line connected to the negative electrode layer. The lower shielding layer 32 and the upper shielding layer 34 are set to the same potential, and the vibration sensor 30 is shielded from electromagnetic noise from outside, moisture, air, light, mechanical vibration from the bed periphery, and the like. Here, the vibration sensor main body 21 includes a vibration sensor 30, a lower shielding layer 32, an upper shielding layer 34, and an insulating sheet (insulating layer) 33 as shown in FIG.

  The insulating layer 33 ensures insulation between the positive electrode layer 52 and the upper shielding layer 34. When reading vibrations of 1 Hz or less such as cardiopulmonary vibration, a sufficient output value is obtained regardless of the thickness of the insulating layer. Although it was obtained, the output value decreased in response to the increase in frequency, and no vibration was output in the case of vibrations having a frequency in the vicinity of 100 to 500 Hz, such as a habit or sleep signal. Aside from protecting external noise from affecting the positive electrode layer 52, a signal having a frequency in the vicinity of 100 to 500 Hz, such as a trap or a sleep signal, leaks to the upper shielding layer 34 through the capacitance. Estimated. In order to prevent this, when the thickness of the insulating layer 33 was set to 10 to 100 μm, it was possible to receive a vibration signal caused by a voice such as a habit or sleep. In other words, it was found that the capacitance formed by the upper shielding layer 34, the insulating layer 33, and the positive electrode layer 52 needs to be less than 1/10 of the capacitance of the vibration sensor 30. Further, the resistance value R such as the resistance of the vibration sensor material (PVDF) 53 and the resistance between the positive electrode layer 52 and the vibration sensor material 53, the upper shielding layer 34, the insulating layer 33, and the positive electrode layer 52. When the time constant (1 / (C × R)) determined by the product C × R of the capacitance C of the capacitor between the two is reduced, sound components such as snare and sleep are vibrations in the vicinity of 100 Hz to 500 Hz. Cannot output.

  Therefore, in order to output this audio signal, the thickness of the insulating layer needs to be at least 1 μm or more even if the area of the sensor body and the relative dielectric constant of the insulating layer are converted, but it is 10 μm to 100 μm or more. It is preferable. Further, it has been found that the capacitance of the capacitor composed of the upper shielding layer 34, the insulating layer 33, and the positive electrode layer 52 needs to be at least 1 μF or less, and preferably 0.1 μF or less. . The positive electrode line 37 and the negative electrode line 38 use shield lines, and the shield electrode portions have the same potential as the upper shielding layer 34 and the lower shielding layer 32.

  The vibration collecting plate 27 transmits the body vibration to the vibration sensor main body 21 without attenuating the body vibration. The inventor used a veneer plate on the vibration sensor main body 21 and confirmed that a sufficiently large vibration signal could be obtained even when the distance between the vibration sensor main body 21 and the heart as a vibration source was large. Because veneer boards are made of wood and have problems with durability and reproducibility, alternative materials for veneers are those that have a high Young's modulus and are easy to transmit vibration, such as plastic boards (eg, PET boards, foamed polystyrene boards). PP plates, acrylic plates, cured vinyl chloride plates, foamed vinyl chloride plates, etc.) and metal plates (for example, aluminum plates, duralumin plates, copper plates, iron plates, etc.) can be used. The measurement waveforms of each material are shown below.

  FIG. 6 is a diagram showing a vibration waveform of the vibration sensor main body 21 when the vibration collecting plate 27 is not provided. The horizontal axis is time (seconds), and the vertical axis is amplitude (V). The vibration amplitude of the vibration sensor main body 21 when there is no vibration collecting plate 27 is about ± 1V. FIG. 7 shows the vibration amplitude when a veneer plate—4 mm is used as the vibration collecting plate. As can be seen from this figure, the positive direction is 3V or more, the negative direction is about -1V, and the amplitude is amplified to about 3 times that when there is no vibration collecting plate. FIG. 8 shows the amplitude when the veneer plate is 2 mm. It can be seen that the vibration amplitude is almost the same as when the veneer plate is shown in FIG.

  FIG. 9 is a diagram showing a vibration waveform of the vibration sensor main body 21 in the case of a PET plate—1 mm. The amplitude is 3 V in the positive direction, and it can be seen that a waveform with sufficient amplitude is obtained. FIG. 10 shows a vibration waveform when the PET plate is 0.5 mm. The amplitude is + 2V, which is smaller than that in the case of 1 mm thickness in FIG. FIG. 11 is a diagram showing a vibration amplitude waveform in the case of a hard vinyl chloride plate—0.7 mm. The amplitude is about 2V.

  FIG. 12 shows the amplitude in the case of the low foam PVC plate-1 mm plate, and FIG. 13 shows the amplitude in the case of the low foam PVC plate-2 mm. The amplitude of the 2 mm plate is 2.2 V, which exceeds the amplitude of 2 V of the 1 mm plate. FIG. 14 shows the amplitude in the case of an aluminum plate—1 mm. Its amplitude is about 1.5V.

  An embodiment will be described regarding the structure of the positive electrode lead wire 37 and the negative electrode lead wire 38 described above. FIG. 15 is a view showing the structure of the outlet. As shown in the figure, a negative electrode layer 51, a positive electrode layer 52, and electrode terminals are connected to each other in an electrode terminal embedded type in which the connection between the negative electrode layer 51, the positive electrode layer 52, and the electrode terminal is formed in the plane of the sensor body (PVDF) 53. The embodiment of FIG. 15 shows a state in which three sets of electrode terminals 112 to 114 are provided. In the figure, the states of the fault plane A, the fault plane B, and the fault plane C are shown together. In the tomographic plane A, 34 is an upper shielding layer, 33 is an insulating layer, 53 is a vibration sensor material (PVDC), 51 is a negative electrode layer, and 52 is a positive electrode layer.

  FIG. 5A shows a configuration of a conventional signal connection unit. A vibration sensor material (PVDF) 53 is sandwiched between the positive electrode layer 52 and the negative electrode layer 51. There are conductive films on both surfaces of the vibration sensor 30, and a voltage generated by vibration is generated between the two films. In order to draw out this voltage, two ears 59 and 59 'are provided, and a positive electrode line 37 and a negative electrode line 38 (not shown) are caulked and connected by an eyelet terminal 49 (not shown). However, in the method of putting out the ear, the mechanical strength of the base of the ear is low, and there is a problem that the ear is cut during use and the signal is cut off.

  Therefore, instead of attaching a lead wire to the ear, the main body of the vibration sensor 30 is joined, and as shown in FIG. 5B, the vibration sensor 30 is pressed by the pressing member 46 and connected to the extraction electrode 45. Take. For this purpose, a flat knitted copper wire is bonded to the conductive film on both sides of the vibration sensor 30 with a conductive adhesive, drawn out of the frame of the vibration sensor 30, and a positive electrode line 37 and a negative electrode (not shown) made of shield wires are formed on the conductive film. The wire 38 was soldered. Further, the upper pressing member 46 helps to maintain the strength of the adhesive surface between the conductive coating and the flat knitted copper wire.

  FIG. 5C shows an enlarged view, a cross-sectional view, and a top view of the pressing portion. When the pressing member 46 is pressed, the vibration sensor 30 is pressed between the pressing member 46, and both sides of the vibration sensor 30 are pressed against the pressing member 46, whereby the vibration sensor output is extracted from the extraction electrode 45.

  Next, an embodiment of the structure of the positive electrode line 37 and the negative electrode line 38 will be described. As shown in FIG. 15, the electrode terminal embedded type in which the connection of the negative electrode layer 51, the positive electrode layer 52 and the electrode terminal is formed in the plane of the vibration sensor material 53 is characterized. In FIG. 15, 112 to 114 and three sets of electrode terminals are described. The extraction electrodes are provided in three directions because it is necessary to freely select the electrode extraction direction based on the arrangement position of the vibration signal sensor unit 10 and the signal processing unit. Of course, if the positional relationship between the vibration signal sensor unit 10 and the signal processing unit is constant, it is obvious that the vibration signal sensor unit 10 and the signal processing unit may be limited to one direction or two directions.

  Next, the extraction electrode will be described. As shown in FIG. 15, the tomographic plane A where there is no extraction electrode, the tomographic plane B directly above the extraction electrode, and the tomographic plane C at the edge of the vibration sensor are shown. In the figure, 51 is a negative electrode layer, 52 is a positive electrode layer, 53 is a vibration sensor material (PVDF), 33 is an insulating layer, and 34 is an upper shielding layer. In addition, the negative electrode layer 51, the positive electrode layer 52, and the vibration sensor material 53 shown in this figure indicate the vibration sensor 30 shown in FIG.

  More specifically, FIG. 16 shows details of the connection portion between the positive extraction electrode and the negative extraction electrode. In the positive extraction electrode 58, the upper shielding layer 55, the insulating layer 54, the negative electrode layer 51, and the lower shielding layer 56 are cut, and the positive extraction electrode 58 is caulked with the positive electrode layer 52 using the eyelet terminal 49 or the like, The connection electrode was embedded and connected in the vibration sensor main body (vibration sensor material 53). The positive electrode layer 52 and the vibration sensor material 53 are originally large in area, and even if an external force is applied to the caulking portion, they are subjected to stress as a whole, so that sufficient strength against cutting of the positive electrode layer 52 can be maintained. It was.

  In the negative extraction electrode 57, only the positive electrode layer 52 is cut, and the negative extraction electrode 57 is caulked with the negative electrode layer 51 using the eyelet terminal 49 or the like, and the connection electrode is embedded in the vibration sensor material 53 and connected. . Since the negative electrode layer 51, the vibration sensor material (PVDF) 53, the upper and lower shielding layers 55 and 56, and the insulating layer 54 are originally large in area, even if an external force is applied to the caulking portion, the negative electrode layer 51 is subjected to stress as a whole. It was possible to maintain a sufficient strength against the cutting of the layer 51.

  FIG. 17 is a diagram illustrating a connection relationship between the sensor unit and the apparatus main body. The same components as those in FIG. 4 are denoted by the same reference numerals. In the figure, 30 is a vibration sensor. Reference numeral 41 denotes a connection unit for connecting to the apparatus main body. The connection portion 41 is a portion for connecting the vibration sensor 30 and the apparatus main body 130, and the connection portion 41 is an electrode terminal embedded type as described above, and its periphery is covered with silicon rubber. The apparatus main body 130 inputs the output of the vibration sensor 30 and amplifies it to a predetermined amplitude, and obtains vibrations such as predetermined pulsation, breathing, sputum, and body movement from the output of the vibration sensor 30, and the human health condition And is integrated as shown in the figure, and has a feature that manufacture is facilitated in realizing the present invention.

  Since the connection portion is an electrode terminal embedded type, the connection portion is not disconnected due to aging fatigue as compared with the lead wire type shown in FIG. 5A. Specifically, a highly reliable connection can be achieved by making the vibration sensor 30 and the lead wire embedded in the electrode terminal. In this case, it is preferable that the connection part 41 is an electrode terminal embedded type. In this case, the electrode connection part can be reliably connected by using the eyelet terminal 49 to connect the embedded electrode terminal and the thin coaxial cable 40. The output of the vibration sensor 30 enters the apparatus main body 130.

  Next, a first example of the shape of the vibration sensor 30 (see FIG. 5) will be described. In order to receive sounds from the human body such as heartbeat, breathing, and sleep, it is necessary to place sensors near the source of these signals. In the first embodiment, a range of 40 to 5 cm in the direction along the spine of the patient and 80 to 10 cm in a direction perpendicular to the spine so as to cover the entire heart and lungs (value close to the width of the bed) is covered. There is a need to. In order to realize this with one vibration sensor 30, a 4 cm × 9 cm sheet was used. As a result, it was possible to realize a biosensor capable of sufficiently following changes in body posture due to the patient turning over.

  FIG. 18 is a diagram illustrating an arrangement example of the vibration sensor 30. (A) has shown the example which has arrange | positioned the narrow vibration sensor 30 near the patient's heart. In this arrangement, the vibration sensor 30 is so narrow that when the patient turns over, the vibration sensor 30 protrudes from the heart position, making it impossible to obtain heartbeat vibration. Therefore, as shown in (B), when the vibration sensor 30 is a vibration sensor 30 ′ having a sufficient area according to the patient's body, the patient's body position can be sufficiently tracked even in an unconstrained state. .

  As described above, the vibration sensor 30 and the apparatus main body 130 can be reliably connected by using the eyelet terminal for the electrode connecting portion 41. Furthermore, according to the present invention, the vibration sensor 30 can be in a parallel connection system or a serial connection system. The electrode connecting portion 41 is covered with a material such as silicon rubber or resin in order to prevent deterioration due to seismic resistance and aging.

  FIG. 19 is a diagram showing a state where four vibration sensors 30 are connected. (A) shows one vibration sensor, and (B) shows four vibration sensors. Reference numeral 30 denotes a vibration sensor, 45 denotes a take-out electrode, and 46 denotes a pressing member. From such a configuration, connection can be made.

  FIG. 20 shows an example in which four vibration sensors 30 are connected in parallel. The positive electrode layers 52 of the four vibration sensors 30 from the vibration sensor 30-1 to the vibration sensor 30-4 are connected to each other in order to always take a heartbeat signal regardless of the posture of the patient and the sleeping position. The negative electrode layers 51 are connected to each other, and four vibration sensors 30 are connected in parallel. Then, signals are extracted from the positive electrode extraction terminal 43 and the negative electrode extraction terminal 44. This state of the takeout terminal can be regarded as a single vibration sensor, and is used when the signal detected by the vibration sensor is weak. That is, according to this method, a signal having a stable amplitude can be extracted.

  FIG. 21 shows an example in which four vibration sensors 30 are connected in series. In this example, the negative electrode layer 51 and the negative electrode of the vibration sensor 30-1 are connected to the positive electrode layer 52 of the vibration sensor 30-2, and the negative electrode layer 51 of the vibration sensor 30-2 is connected to the adjacent vibration sensor 30-3. This is connected to the positive electrode layer 52 and connected to the negative electrode layer 51 of the vibration sensor 30-3 and the positive electrode layer 52 of the adjacent vibration sensor 30-4, and the vibration sensors 30 are connected in series. Reference numerals 42 and 42 'denote vibration signal extraction electrodes.

  In this example, a method using a signal between the positive electrode layer 52 of the vibration sensor 30-1 and the negative electrode layer 51 of the last vibration sensor 30-4, a method in which the so-called vibration sensors 30 are coupled in series. is there. In this case, since the outputs of the vibration sensors are connected in series, the outputs of the vibration sensors are added, and a heartbeat signal can be as large as 4 V, for example. In this case, the order of series connection is not particularly limited. For example, it may be connected to No. 3, No. 4, No. 1, No. 2, etc. In addition, in the state shown in FIG. 20, there is a method of checking the signal of each vibration sensor 30 and selecting the vibration sensor having the largest heartbeat signal.

  When the vibration collecting plate 27 (see FIG. 4) is not used, it is necessary to bring a vibration sensor directly under the heart. When performing this experiment, when a 2 mm thick veneer plate was placed on the vibration sensor, a strong signal could be received as long as the heart was on the veneer plate. Although the detailed reason is unknown, it was found that this veneer plate collects the heart beat with the largest amplitude of the vibration beat.

  Therefore, when a board made of various materials was tested instead of the veneer board, these materials were also capable of collecting signals. Specifically, a plastic plate (for example, a PET plate, a foamed plastic plate, an acrylic plate, a cured vinyl chloride plate, a foamed vinyl chloride plate, etc.) and a metal plate (for example, an aluminum plate, a duralumin plate, a copper plate, an iron plate, etc.).

  As for the shape of the vibration collecting plate, it is indispensable that the edge is polished in order to prevent the patient or caregiver from being injured during handling. It is not desirable to simply cut off the plate material. For the same reason, each side needs to be chamfered. It is desirable to round the four corners. For example, 2-50 mmR is desirable.

  The thickness of the vibration collecting plate 27 of the vibration signal sensor means is required not to cause plastic deformation when a person gets on. Although it is determined by the relationship with the Young's modulus, it determines the minimum thickness. Generally, 0.2 mm or more is required. Furthermore, if the patient senses the vibration signal sensor means from above the mattress, the sleeping comfort is impaired, so the maximum is 10 mm or less, preferably 5 mm or less. In these cases, it was found that the rigidity of the vibration collecting plate is preferably slightly harder than that of the vibration sensor body. The cushion member 25 removes vibration when the nurse walks near the patient's bed, and is disposed at the lower part of the sensor body 21.

  Next, the configuration of an input circuit that receives the output of the vibration sensor and processes signals such as heartbeat, respiration, and sputum will be described. Here, an example of an electrocardiogram waveform is taken. First, the similarity between the electrocardiogram and the heartbeat vibration waveform obtained by the vibration sensor of the present invention will be described. An electrocardiogram is an electrical pulse that occurs in the human body, and a heartbeat vibration is a change in weight associated with blood entering or exiting the heart or a vibration during contraction and expansion of the heart. Since the vibration is due to the contraction and expansion of the heart due to the pulse, a similarity is typically obtained.

  FIG. 22 is a diagram showing a normal state of the electrocardiogram waveform. As shown in the figure, it is composed of P wave, T wave, U wave, and QRS wave. The name of each part is shown in the figure. Next, how to count heart rate is described. In the case of the waveform shown in FIG. 23, attention is paid to the waveform recorded by overlapping the R wave of the electrocardiogram with a thick line (line every 5 mm) of the recording paper. From there, the number of thick squares is examined before the next R wave appears.

The heart rate can be calculated as 300 / thick squares. In the example of FIG. 23, the large cell is 4, and the heart rate is 300/4 = 75. In order to count the heart rate more accurately, there is a method in which an actual measurement value (mm) of the RR interval is obtained and 1500 is divided by the distance.
1500 ÷ obtained at the measured R−R interval. For example, when the actual measurement value (mm) of the RR interval is obtained,
1500/25 = 60.

  FIG. 24 is a diagram showing a heartbeat vibration output waveform extracted by the vibration sensor of the present invention. This output is a waveform obtained by processing the signal output from the piezoelectric sensor with the above-described heartbeat vibration filter. Therefore, it is a waveform of only heartbeat vibration.

  The output signal from the piezoelectric sensor is output in proportion to the differential component with respect to the time of the pressure to be pressurized. Therefore, a waveform of the pressurized pressure is obtained by integrating with respect to time. The present inventor has estimated a time when the pressurization pressure becomes zero, and found a method of performing integral calculation from that time, and can obtain a stable heartbeat vibration as shown in FIG. It became possible to obtain a waveform similar to the monitor waveform of (see FIG. 25). FIG. 24 shows the waveform of the pulsating vibration electric signal 123. In FIG. 25, the solid line is the extraction result after the integration process, and the broken line is the waveform of the pulsating vibration electric signal 123 obtained from the vibration signal sensor. The horizontal axis is time (seconds), and the vertical axis is signal amount.

  In addition, since the interval between the time when there is no pressurizing pressure and the time when there is no pressurizing pressure is the interval between heartbeats, the time when the pressurizing pressure disappears is used to detect the heartbeat (60 The heart rate) can be easily obtained from the second / heartbeat interval (seconds). FIG. 26 shows the heart rate. The horizontal axis represents the order of heartbeats, and the vertical axis represents the heart rate (times / minute). Since the fluctuation of the heartbeat vibration can be used for detection of the excited state, detection of the end stage, and detection of the stress intensity, it is possible to know the patient's state in more detail and to perform care and nursing appropriately.

  FIG. 27 is an explanatory diagram of the heartbeat and peak, and shows the first two beats of the waveform of the pulsating vibration electric signal 123 shown in FIG. 24 in an enlarged manner. The horizontal axis is time (seconds), and the vertical axis is signal amount. Schematic representation of heart activity releases blood in the heart through the aorta before it flows through the aorta. At this time, the heart becomes light and the pressure is lost. At that time, since the pressure gradually decreases, the amplitude of the heartbeat vibration obtained by the filtering process greatly fluctuates from the plus side to zero, and when the whole blood flows out, the amplitude of the heartbeat vibration is zero (C Point).

  Next, when blood flows into the heart from the vena cava, the blood accumulates in the heart and becomes heavier, so that the amplitude of the heartbeat vibration swings from the equilibrium position (point C) to the plus side and reaches the maximum amplitude (point A). It is important to perform the integration process from the point where the amplitude becomes zero (C point).

  The point at which the integration process is started (point C) may be obtained with reference to point A that shows the maximum value in amplitude. The maximum value (point A) is extracted as a location having an amplitude larger than a certain threshold value (value B). The point (C point) at which the signal goes negative for the first time from that point is obtained, the amplitude at that point is set to 0, and the subsequent amplitudes are added. The result is the extracted waveform after the integration process of FIG. This threshold value (B value) may be set in advance, or may be obtained from the signal level according to the patient and according to the environment. The method for obtaining the threshold value may be selected from the amplitude range in which the number of appearances is substantially constant from the amplitude-appearance number relationship graph of the signal in FIG.

FIG. 28 is an explanatory diagram of a threshold setting method. The horizontal axis is the threshold voltage (V), and the vertical axis is the number of peaks. When the integration value (sum) from C1 to C2 does not become zero, it means that the equilibrium state is shifted because the lung respiratory vibration is not completely separated. There is no big problem because it is reset and added as zero, but when the deviation is large,
offset = sum / (number of data of (C2-C1))
Is a deviation from the equilibrium state, and if the value is added after correcting the value of the DC component at the time of the next integration, the similarity to the electrocardiogram can be increased.

  In order to obtain the exact time of the peak (point A), this part is approximated by a quadratic expression with respect to time, and the symmetry axis is the time to be obtained (peak time). From this time table, the heartbeat interval can be accurately calculated and displayed in real time. Also, by recording this table in a storage medium, the heartbeat interval can be accurately calculated later. The heart rate for 1 minute can be calculated with the interval time of this heart rate, and the heart rate at each time is shown in FIG.

  When a light emitter such as an LED is turned on at the peak time (An), the heartbeat of the patient can be seen with the eyes. If this signal is placed where caregivers and nurses can monitor, many patients can be monitored at one time, and it can be determined that some abnormalities are indicated when the flashing is intense or slow. It is possible to perform a quick process. In this case, the color of the illuminant such as the LED can be changed from that for displaying the heartbeat, and can be displayed side by side with the heartbeat display.

  Moreover, when this apparatus is installed in the bed of the newborn, the family can also check the state of the newborn by looking at the light emitter from the window.

  FIG. 29 is a circuit diagram showing an embodiment of the signal processing system of the present invention. A signal from the vibration sensor 30 (see FIG. 5) is input from the input terminal 61 to the preamplifier 62, and the preamplifier 62 reduces external noise. The output of the preamplifier 62 is input to the filter 63. FIG. 30 is a diagram showing an output waveform of the preamplifier 62. The horizontal axis shows time in 1 second intervals. The vertical axis represents voltage (V). In this waveform, heartbeat sound and breathing sound overlap, and in addition to this repetitive waveform, there are sounds that appear irregularly (for example, vibrations associated with body movements, sleep, wrinkles, bruxism, caregiver movements, etc.) .

  The filter 63 separates the input vibration signal into heartbeat, respiration, sputum, and body motion signals. As shown in FIG. 31, the separated vibration signal is output by separating the signal inputted from the input terminal 61 into breathing sound, heartbeat vibration, voice, and other signals. The separated vibration signal is input to the detection circuit 64 and converted into a clean signal for each vibration by the detection circuit 64. The operation of the detection circuit will be described later.

  If a DC component is superimposed on the output of the detection circuit 64, the output of the amplifier is saturated and an accurate signal cannot be extracted, so that the DC component is removed by the subsequent DC component removal circuit 65. The vibration signal from which the DC component has been removed enters the waveform shaping circuit 66, is subjected to waveform shaping, and is taken out from the output terminal 67. The extracted signal is displayed on a display device (not shown). The observer can view the displayed signal and can use it for image diagnosis.

  As shown in FIG. 31, according to the present invention, signals such as heartbeat, respiration, sputum, and body movement can be separated and extracted. In the present invention, the health condition can be compared and determined by comparing at least two types of waveforms among these signals. This is because if there are two types of signals, they can be compared with each other. Of course, the health condition can be compared and determined using three or more types of signals.

  FIG. 32 shows an example of the circuit of the present invention. The vibration signal detected by the vibration sensor 30 is amplified A times by the amplification amplifier 70. The amplified signal is input to the subsequent antialiasing filter circuit 71, and only the low-frequency component is extracted. The antialiasing filter circuit 71 is an RC filter as is apparent from the figure.

  The signal passed through the anti-aliasing filter circuit 71 is impedance-converted by the buffer amplifier 72 and then input to the AD converter 73. The AD converter 73 converts the input vibration into digital data. The converted digital signal enters the MPU 74. The MPU 74 takes in the digital data and performs predetermined signal processing. As the contents of the signal processing, the magnitude of the input signal is specified, and it is determined whether or not the signal component is normally output from the relationship with the frequency. The determination result is sent to a nurse center, for example, and the patient's pulsation signal is observed to check whether the result is normal. If the beat signal is normal, leave it alone. If the pulsation signal is abnormal, go to the patient and examine the patient.

  FIG. 33 is a diagram showing another example of the circuit of the present invention. A signal from the vibration sensor 30 enters the amplitude limiting circuit 81. The amplitude limiting circuit 81 limits the amplitude of noise superimposed on the input signal. In the figure, two diodes are connected with opposite polarities. Since the forward voltage of the diode is about 0.6V, in the case of the circuit shown in the figure, the noise superimposed on the input is limited to ± 0.6V or less.

  The output of the amplitude limiting circuit 81 enters the DC voltage blocking circuit 83 via the buffer amplifier 82 and removes the DC voltage. Specifically, as shown in the figure, the output of the buffer amplifier 82 is cut by the capacitor of the DC voltage blocking circuit 83. The vibration signal from which the DC component has been removed by the DC voltage blocking circuit 83 is output from the amplification amplifier 85 via the buffer amplifier 84.

  FIG. 34 is a diagram showing another example of the circuit of the present invention. The vibration signal of the vibration sensor 30 enters the amplification amplifier 91 and is amplified A times. The signal amplified by A times enters the respiratory signal band removing HPF circuit unit 92, the respiratory signal band is removed, and the heartbeat vibration component passes. The heartbeat vibration component enters the detection circuit 94 that passes through the buffer amplifier 93, and the detection circuit 94 extracts only the heartbeat vibration component.

  The detection circuit 94 includes a diode D, a resistor R, and a capacitor C as shown in the figure. According to the experiment of the present inventor, as shown in the figure, the half-wave rectifier circuit using one diode D was the best detection circuit 94 for extracting the heartbeat signal. FIG. 35 shows a comparison of a waveform obtained by integrating vibration signals, a waveform obtained by detecting both waves, and a waveform obtained by half-wave detection. In the figure, f1 is an integrated waveform, f2 is a both-wave detection waveform, and f3 is a half-wave detection waveform. The horizontal axis is time, and the vertical axis is amplitude.

  Since the output of the vibration sensor is a differential waveform, the integrated waveform is a pressure waveform. The double-wave waveform f2 was originally a negative signal as indicated by an arrow, but double-wave rectified so that it is folded and appears on the positive side. In this regard, the half-end rectified waveform f3 shows peaks at a predetermined interval, and by processing these peaks, the heartbeat can be accurately detected. Therefore, the detection circuit unit 94 of FIG. 34 can accurately extract the heartbeat.

  The outline of the operation of the half-wave rectifier circuit 94 is as follows. First, when a voltage is applied via the diode D, a current is charged to the capacitor C from the voltage. When the voltage is no longer applied, the electric charge charged in the capacitor C with the time constant of R and C is discharged, and the output becomes almost zero. Since the voltage is applied again in the next period, the capacitor C is charged. By repeating such an operation, in the case of the half-end rectifier circuit, the waveform f3 is output with a peak waveform at a constant period as shown in FIG. 35, so that the heartbeat signal can be accurately captured.

  The output of the detection circuit 94 is impedance-converted by the buffer amplifier 95 and then enters the DC component removal HPF circuit unit 96 to remove the DC component. The pulsation signal from which the DC component has been removed enters the waveform shaping LPF circuit section 98 via the buffer amplifier 97, and waveform shaping is performed. The waveform shaping LPF circuit unit 98 enters the buffer amplifier 99 and is output from the terminal to the outside. Specifically, after entering the AD converter 73 as shown in FIG. 32 and converted into digital data, the MPU 74 is entered, and the determination process is performed using the read data.

  As described above, according to the present invention, the target measurement object is separated from the output of the vibration sensor, the determination process is performed for each object, and the physical condition of the patient can be determined.

  The above-described device of the present invention integrates the vibration signal sensor means 100 including the vibration sensor main body, the signal processing unit, and the signal output unit into one component, thereby making the device lightweight and compact and easy to design. . For example, in FIG. 2, vibration signal sensor means 100, reference sensor means 260, body motion vibration detection means 150, differential signal amplification amplifier 110, pulsation filter means 120, lung respiratory vibration filter means 121, sputum vibration filter means 122 The body motion vibration filter means 152, the presence / absence determination means 140, the storage device 261, and the notification means 270 can be integrated together, and free combinations can be made.

  In the human health condition determination method and apparatus according to the present invention, in addition to the original human health checkup, the presence or absence of a human health checkup is detected in a chair, seat chair, or vehicle seat on which a person sits. Can also be used. Furthermore, it can be similarly applied to animal pets.

  10 vibration sensor means, 11 bed, 12 mattress, 13 bed pad, 14 mattress, 15 persons, 21 vibration sensor body, 25 cushion member, 26 bottom plate, 27 vibration collection plate, 30, 30 'vibration sensor, 32 for lower electromagnetic shield Film (lower shielding layer), 33 Insulating sheet (insulating layer), 34 Upper electromagnetic shielding film (upper shielding layer), 37 Positive (plus) electrode wire, 38 Negative (minus) electrode wire, 40 Thin coaxial cable, 41 Connection part, 42, 42 'Extraction electrode, 43 Positive electrode extraction terminal, 44 Negative electrode extraction terminal, 45 Extraction electrode, 46 Upper pressing member, 48 Holding member, 49 Eyelet terminal, 51 Negative electrode layer, 52 Positive electrode layer, 53 Vibration sensor material (PVDF), 54 insulation layer, 55 upper shielding layer, 56 Lower shielding layer, 57 Negative electrode extraction terminal, 58 Positive electrode extraction terminal, 59, 59 'ear, 61 input terminal, 62 preamplifier, 63 filter, 64 detection circuit, 65 DC component removal circuit, 66 waveform shaping circuit, 67 output terminal , 70 Amplifying amplifier, 71 Anti-aliasing filter circuit, 72 Buffer amplifier, 73 AD converter, 74 MPU, 81 Input amplitude limiting circuit, 82 Buffer amplifier, 83 DC voltage blocking circuit, 84 Buffer amplifier, 85 Amplifying amplifier, 91 Amplifying amplifier, 92 Respiratory signal band removal HPF circuit section, 93 buffer amplifier, 94 detection circuit section, 95 buffer amplifier, 96 DC component removal HPF circuit section, 97 buffer amplifier, 98 waveform shaping LPF circuit section, 99 buffer amplifier, 100 vibration sensor Means, 1 01 vibration sensor, 102, 102 'body vibration electric signal, 110 differential signal amplification amplifier, 120 pulsation filter means, 121 lung respiratory vibration filter means, 122 sputum vibration filter means, 123 pulsation vibration electric signal, 124 lung Respiratory vibration electrical signal, 125 鼾 Vibration electrical signal, 130 Device main body, 140 Presence absence determination means (leaving / leaving floor determination means), 141 A / D converter, 142 CPU, 143 Presence absence determination signal, 150 Body motion vibration Detection means, 151 body motion vibration electrical signal, 152 body motion vibration filter means, 260 reference sensor means, 261 storage device, 270 notification means

Claims (9)

The vibration signal sensor means detects vibrations of the body emitted by a person in a predetermined location, and performs a predetermined signal processing on the vibration signals generated by the vibrations to obtain vibration signals. Based on the obtained vibration signals, the patient's health In a human health condition determination apparatus for determining a condition
Detecting means for detecting a signal from the human body by the vibration signal sensor means; preprocessing means for preprocessing the detected signal; filtering means for filtering the signal preprocessed by the preprocessing means; Separation means for receiving the output of the filtering means and separating it into a plurality of signals; and signal output means for obtaining at least two signals of respiratory sound, heartbeat vibration, voice, snoring, and body motion signal from the output of the separation means. Have
The vibration signal sensor means is composed of one or more of a vibration sensor main body or a vibration sensor main body and a bottom plate formed by laminating the vibration sensor main body, a cushion member, and a vibration collecting plate.
The vibration sensor body includes a vibration sensor, an insulating layer, and an upper and / or lower shielding layer,
The insulating layer has a thickness of 1 μm or more, or a capacitor composed of an upper shielding layer, the insulating layer, and the positive electrode layer of the vibration sensor has a capacitance of 1 μF or less. Health condition judging device.  2. The human health condition determination apparatus according to claim 1, wherein the vibration collecting plate transmits vibration generated in a human body part to the vibration sensor without being attenuated.  The human health condition determination apparatus according to claim 2, wherein a hardness of the vibration collecting plate is higher than a hardness of the vibration sensor main body.  The preprocessing means includes a limiting circuit that limits the amplitude of the input vibration signal, a detection circuit or an integration circuit that receives the output of the limiting circuit and performs a detection operation, and an amplification circuit that amplifies the output of the detection circuit or the integration circuit 4. A human health condition determination apparatus according to claim 1, further comprising: a DC removal circuit that removes a DC component of the detected signal. 5.  5. The human health condition determination apparatus according to claim 4, wherein the detection circuit includes a diode, a resistor, and a capacitor, and extracts only a human heartbeat signal in response to an input vibration signal.  6. The human health condition determination apparatus according to claim 1, wherein the vibration sensor is an electrode terminal embedded type.  The vibration signal sensor means, a signal processing section for processing a signal detected by the vibration signal sensor means, and the signal output means for outputting a signal obtained by the signal processing section are integrated. The human health condition determination apparatus according to any one of claims 1 to 6.  The human health condition determination apparatus according to any one of claims 1 to 7, wherein the vibration signal sensor means has a thickness of 10 mm or less.  As a material of the vibration collecting plate, a PET plate, a PEN plate, a carbon plate, a foamed polystyrene plate, a PP plate, an acrylic plate, a cured vinyl chloride plate, a foamed vinyl chloride plate, an aluminum plate, a duralumin plate, a copper plate, and an iron plate are used. The health condition determination apparatus according to any one of claims 1 to 8, characterized by:

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