JP2016022293A - Device and method for monitoring biological information, and program for the same - Google Patents

Abstract

PROBLEM TO BE SOLVED: To provide an art for properly extracting respiratory information.SOLUTION: A device for monitoring biological information is provided that includes: a peak detection circuit 7 receiving information on potential difference from a biological signal measurement device 200 measuring potential difference between two electrodes 2a, 2b placed at the chest of a user and detecting at least an S-wave peak and a T-wave peak of electrocardiogram from information on the potential difference; an interface device acquiring information on the positions of two electrodes at the chest of the user; a selection circuit selecting one of the S-wave peak and the T-wave peak on the basis of the information on the positions of the two electrodes; an envelope curve processing circuit 8 extracting respiration information on respiration of the user from time-oriented information on the S-wave peak or the T-wave peak selected by the selection circuit; and a respiratory information output circuit 9 outputting the respiratory information extracted by the envelope curve processing circuit 8.SELECTED DRAWING: Figure 9

Description

  The present application relates to a technique for extracting respiration. More specifically, the present application relates to a technique for measuring the impedance of a living body using a plurality of electrodes attached to a user's body and extracting information related to respiration.

  In recent years, a method of measuring and recording a user's physical condition electrically and mechanically for a long time is becoming widespread. Basic electrical information representing the physical state of the user includes an electroencephalogram (EEG) related to the brain and an electrocardiogram (ECG) related to the motion of the heart. Of these, the electrocardiogram is acquired as basic biological information (vital sign) at a hospital, for example. The electrocardiogram can also be obtained by using a portable electrocardiograph called a Holter-type electrocardiograph when a cardiac disease is suspected. By using a Holter type electrocardiograph, it is possible to record an electrocardiogram at a place other than a hospital such as a home for a long time, for example, 24 hours. In recent years, miniaturization of this Holter type electrocardiograph has progressed, and a user can measure an electrocardiogram more easily.

  By recording an electrocardiogram over a long period of time using a Holter-type electrocardiograph, it is possible to discover symptoms such as arrhythmia that cannot be detected by a short examination in a hospital. However, in addition to the electrocardiogram, there are examination items (cases) that become apparent if the examination can be performed for a long time. For example, sleep apnea syndrome. Sleep apnea syndrome is a respiratory disease that is closely associated with arrhythmia.

  Sleep apnea syndrome cannot be assessed by electrocardiogram alone, and information on breathing is also required. Currently, evaluation of sleep apnea syndrome requires an overnight polysomnography test that simultaneously measures ECG, respiration, and brain waves. This examination had to be carried out while staying in the hospital, which was a burden for both the hospital and the patient. For this reason, at the stage where the possibility of a disease is suspected, it is not realistic to perform such a heavy test.

  If information on respiratory diseases, specifically information on respiratory rate, can be obtained with the convenience of acquiring an electrocardiogram using a Holter-type electrocardiograph, early detection of the disease and rapid diagnosis It is thought to lead to

  In the past, when it was desired to measure respiration simply, a medical device called a pulse oximeter has been mainly used. This is a measuring device for examining arterial oxygen saturation. Arterial oxygen saturation is measured by attaching a sensor called a probe to the fingertip. This measuring device has a red light source (LED), emits red light from the LED, and measures the transmitted light of the finger with a sensor, thereby measuring the oxygen content in the artery inside the finger. Measure in real time. As described above, when both electrocardiogram and respiration information are required, an electrode for an electrocardiograph must be attached to the chest, and a pulse oximeter probe must be attached to the fingertip.

  Up to now, efforts have been made to simultaneously acquire electrocardiogram and respiration information with a single device and separate respiration information from data acquired using the electrocardiogram information. One approach is the impedance method. In the impedance method, a current is passed through the user's body, and an impedance change due to an electrocardiogram or respiration is measured with an electrode placed on the chest. For example, Non-Patent Document 1 discloses a method of extracting respiratory information from chest impedance at low current (10 nA).

  Before explaining the concept of the method described in Non-Patent Document 1, basic components of electrocardiogram will be explained. FIG. 1 shows the basic components of one cycle of the electrocardiogram. The electrocardiogram has peaks of P wave, Q wave, R wave, S wave, and T wave. Each wave portion of the QRS represents ventricular excitement.

  2A to 2C show the concept of the method described in Non-Patent Document 1. FIG. At the time of measurement, four electrodes are mounted in the middle of the chest (see FIG. 2 (a)). In FIG. 2A, the potential is measured with two inner electrodes out of the four electrodes, excluding the ground. A low current (10 nA) is passed between the two outer electrodes. FIG. 2 (b) shows the chest impedance measured from the potential. In Non-Patent Document 1, the T-wave envelope of the electrocardiogram-derived component is used as respiratory information.

  Non-Patent Document 1 measures chest impedance by attaching four electrodes to the middle of the chest. In the experiment of Non-Patent Document 1, the subject was asked to perform a four-phase breathing method of “normal breath”, “deep breath”, “apnea”, and “normal breath”. For normal breathing, subjects were instructed to take 15 breaths with a period of 3 seconds. For deep breaths, subjects were instructed to take 8 breaths with a period of 5 seconds. For apnea, subjects were instructed to hold their breath for 30 seconds.

  FIG.2 (c) shows the extraction result of respiration. The period in the envelope is correlated with actual breathing. Also, since the amplitude during apnea is very small and the amplitude during deep breathing is greater than the amplitude during normal breathing, the extracted breathing information represents actual breathing.

Jeffry Bonar Fernando et. Al, "Estimation of respiratory signal from thoracic impedance cardiography in low electrical current", International Conference of the IEEE Engineering in Medicine and Biology Society, p.3829-3832 (2013)

  In the above-described conventional technique, it is necessary to improve the technique for more correctly extracting respiration.

  One non-limiting exemplary embodiment of the present application is that even if the user incorrectly attaches the electrode, even if the electrode cannot be attached to the specified position for various reasons, A technique capable of measuring biological information related to respiration is provided.

  In order to solve the above problems, a biological information monitoring apparatus according to one aspect of the present invention receives information on a potential difference from a measurement device that measures a potential difference between two electrodes arranged on a chest of a user, and information on the potential difference To at least a detection circuit for detecting an S-wave peak and a T-wave peak of electrocardiogram, an interface device for acquiring information on the positions of the two electrodes in the chest of the user, and information on the positions of the two electrodes. A selection circuit for selecting one of the S wave peak and the T wave peak based on the time series information of the S wave peak or the T wave peak selected by the selection circuit, and A processing circuit for extracting respiration information; and an output circuit for outputting the respiration information extracted by the processing circuit.

  The general and specific aspects described above can be implemented using a system, apparatus, method and computer program, or can be implemented using a combination of system, apparatus, method and computer program.

  According to the biological information monitoring apparatus according to one aspect of the present invention, even when the user incorrectly attaches the electrode, even when the electrode cannot be attached to the designated position due to various circumstances, Biological information related to respiration can be measured.

It is a figure which shows the basic component of 1 period of electrocardiogram. (A)-(c) is a figure which shows the concept of the method described in the nonpatent literature 1. FIG. (A) is a figure which shows the electrode group with which the right chest was mounted | worn, (b) is a figure which shows the waveform of the measured chest impedance, (c) was calculated | required using the measured chest impedance. It is a figure which shows the result of having extracted respiration information from the envelope of a T wave peak. (A) is a figure which shows the electrode group with which the right chest was mounted | worn, (b) is a figure which shows the waveform of the measured chest impedance, (c) is the same chest impedance measured in FIG. It is a figure which shows the extraction result of the respiration information in the case of applying the envelope of the S wave peak calculated | required using. (A) is a diagram showing an arrangement example when the electrode group is arranged in the center of the chest, (b) is a diagram showing a waveform of the chest impedance measured using the electrode arranged in the center of the chest, (C)-(g) is a figure which shows the envelope of P wave, Q wave, R wave, S wave, and T wave, respectively. (A) is a diagram showing an arrangement example when an electrode group is arranged on the right chest, (b) is a diagram showing a waveform of a chest impedance measured using an electrode placed on the right side of the chest, (C)-(g) is a figure which shows the envelope of P wave, Q wave, R wave, S wave, and T wave, respectively. (A) is a diagram showing an arrangement example when an electrode group is arranged on the left chest, (b) is a diagram showing a waveform of a chest impedance measured using an electrode placed on the left side of the chest, (C)-(g) is a figure which shows the envelope of P wave, Q wave, R wave, S wave, and T wave, respectively. (A) is a figure which shows the schematic circuit structure of 2 terminal method, (b) is a figure which shows the schematic circuit structure of 4 terminal method. 1 is a diagram illustrating a configuration of a biological information monitoring system 100 according to an exemplary embodiment. It is a flowchart which shows the whole process flow of the biometric information monitoring system 100 by example embodiment. It is a flowchart which shows the process flow in which the detection circuit 7 selects any one of P wave, Q wave, R wave, S wave, and T wave which are electrocardiogram peaks. 1 is a diagram illustrating a configuration of a biological information monitoring system 102 according to an exemplary embodiment. It is a figure which shows typically the amplitude Amp and width D of an electrocardiogram peak. It is a flowchart which shows the whole processing flow of the biometric information monitoring system 102 by example embodiment. It is a figure which shows the structure of the biometric information monitoring system 104 by example embodiment. It is a flowchart which shows the whole processing flow of the biometric information monitoring system 104 of exemplary embodiment. It is a figure which shows the structure of the biometric information monitoring system 110 by the modification of exemplary Embodiment 1. FIG.

  The inventors of the present application have found that the technique of Non-Patent Document 1 described above can acquire respiratory information more accurately.

  For example, suppose that it is desired to acquire respiratory information of a certain user using a monitoring device. Even if the user receives an instruction to wear the electrode in the middle of the chest, the user may wear the electrode in the wrong mounting position. Moreover, the user may not be able to wear the electrode in the middle of the chest due to circumstances such as a wound in the middle of the chest. If the electrode is not mounted at the planned position, breathing may not be extracted correctly.

(Experimental findings)
The present inventors conducted various experiments in order to correctly extract respiration information. And it came to make this invention based on the knowledge obtained from the result of the experiment. Below, the knowledge obtained by experiment is demonstrated first.

  FIG. 3A shows an electrode group attached to the right breast. The subject's heart is on the left side of the chest.

  FIG. 3B shows a waveform of the measured chest impedance. At the time of measurement, the subject was instructed to repeat breathing with a period of 4 seconds for 32 seconds. FIG. 3B also shows a T-wave envelope.

  FIG. 3C shows the result of extracting respiratory information from the envelope of the T wave peak obtained from the measured chest impedance. If the period between the broken lines represents one respiration cycle and respiration information is correctly extracted, one peak should be observed. However, multiple peaks are observed in many respiratory cycles.

  The present inventors examined the reason. As a possible reason, it is presumed that the amplitude of the T wave is very small. This is considered to be due to the fact that since the electrode position is away from the heart, the electrocardiographic component in impedance is generally smaller than when it is worn in the middle of the chest. That is, since the amplitude of the T wave approaches the noise level of the sensor, the peak value is easily buried in the noise.

  FIG. 4A shows an electrode group mounted on the right breast. FIG. 4B shows a waveform of the measured chest impedance. The experimental conditions are the same as the experimental conditions related to FIG. Unlike FIG. 3B, an S-wave envelope is shown in FIG. 4B.

  FIG. 4C shows the extraction result of the respiratory information when the envelope of the S wave peak is applied to the envelope of the S wave peak obtained from the same chest impedance measured in FIG. There is only one peak per cycle, representing actual breathing.

  Next, the inventors of the present application investigated how accurately the peak envelope of the P wave, Q wave, R wave, S wave, and T wave represents actual respiration depending on the difference in electrode position. The subject was instructed to breathe for a period of 4 seconds for 32 seconds while changing to three electrode positions (middle of chest, right side, left side). It is assumed that the subject's heart is on the left side of the chest.

  FIG. 5A, FIG. 6A, and FIG. 7A show examples of arrangement when electrode groups are arranged at the center of the chest, the right breast, and the left breast, respectively.

  FIG. 5B shows a waveform of the chest impedance measured using the electrode arranged at the center of the chest. FIG. 5C to FIG. 5G show the envelopes of the P wave, Q wave, R wave, S wave, and T wave, respectively. It is determined that the envelope of the T wave in FIG. 5 (g) represents the most actual respiration. Among P waves, Q waves, R waves, S waves, and T waves, R waves, S waves, and T waves have large peak amplitudes. Since the width of the T wave peak is larger than the widths of the other two peaks, it is considered that the correct peak value is sampled more stably.

  FIG. 6B shows a waveform of the chest impedance measured using the electrode arranged on the right side of the chest. FIG. 6C to FIG. 6G show envelopes of P wave, Q wave, R wave, S wave, and T wave, respectively. It is determined that the envelope of the S wave in FIG. 6 (f) represents the most actual breathing. When the electrode position is on the right side of the chest, the electrocardiographic component in the impedance is generally smaller than when it is worn in the middle of the chest. That is, the amplitude of the T wave is also very small. Since the amplitude of the T wave approaches the noise level of the sensor, the peak value is likely to be buried in the noise. Among the P wave, Q wave, R wave, S wave, and T wave, the R wave and S wave have the largest peak amplitude. Since the width of the S wave peak is larger than the width of the R wave peak, it is considered that the correct peak value is sampled more stably.

  FIG. 7B shows a waveform of the chest impedance measured using an electrode arranged on the left side of the chest. FIGS. 7C to 7G show envelopes of P wave, Q wave, R wave, S wave, and T wave, respectively. It is determined that the envelope of the T wave in FIG. 7G represents the most actual respiration. Among the P wave, Q wave, R wave, S wave, and T wave, the Q wave, R wave, S wave, and T wave have the largest peak amplitude. Since the width of the T wave peak is larger than the width of the other three peaks, the correct peak value is considered to be sampled more stably.

  As a result of the above-described experiment, the inventors of the present application have obtained the knowledge that the component that reflects the respiratory information changes depending on where the electrode group is disposed on the chest of the user.

  The outline of one embodiment of the present invention is as follows.

  The biological information monitoring device according to one aspect of the present invention receives information on a potential difference from a measurement device that measures a potential difference between two electrodes arranged on a chest of a user, and at least S of an electrocardiogram is obtained from the information on the potential difference. A detection circuit for detecting a wave peak and a T wave peak, an interface device for acquiring information on the positions of the two electrodes in the chest of the user, and the S wave peak and the information based on the information on the positions of the two electrodes. A selection circuit that selects one of the T wave peaks, and a processing circuit that extracts respiration information related to the user's respiration from the time series information of the S wave peak or the T wave peak selected by the selection circuit; And an output circuit for outputting the respiration information extracted by the processing circuit.

  The interface device acquires information on positions of the two electrodes input from the outside.

  The interface device further acquires information on the position of the heart of the user input from the outside.

  The selection circuit selects one of the S wave peak and the T wave peak depending on whether or not the two electrodes are arranged on the chest opposite to the position of the user's heart.

  The selection circuit selects the S wave peak when the two electrodes are arranged on the chest opposite to the position of the user's heart.

  The selection circuit selects the T-wave peak when the two electrodes are not disposed on the chest opposite to the position of the user's heart.

  The processing circuit generates an envelope of the S wave peak or the T wave peak from time-series information of the S wave peak or the T wave peak selected by the selection circuit, and uses the envelope The respiration information relating to the respiration of the user is extracted by using.

  A biological information monitoring device according to another aspect of the present invention receives information on a potential difference from a measuring device that measures a potential difference between two electrodes arranged on a chest of a user, and is included in an electrocardiogram from the information on the potential difference. A detection circuit that detects a plurality of peaks, an attribute extraction circuit that extracts attribute information of each peak detected within a predetermined period, and a predetermined condition from the plurality of peaks with reference to the attribute information of each peak A selection circuit that selects a matching peak group, a processing circuit that extracts respiration information related to the user's respiration from time series information of the peak group selected by the selection circuit, and a processing circuit that extracts the respiration information. An output circuit for outputting the respiration information, and the attribute information includes information on the amplitude of each peak, information on the width, or the plurality of peaks. Is information about the envelope of the peaks having a common characteristic with respect to waveforms of.

  The attribute extraction circuit extracts information regarding the amplitude and width of each peak as the attribute information.

  The selection circuit refers to the attribute information of each peak and selects a peak group having an amplitude equal to or greater than a first threshold and a maximum width.

  The processing circuit generates an envelope from time-series information of the peak group selected by the selection circuit, and extracts respiration information related to the user's breathing using the envelope.

  The biological information monitoring apparatus further includes a signal generation circuit that generates a signal for instructing the user to have a predetermined respiratory cycle T2 within a predetermined time T1 from the start of the measurement of the potential difference, and the attribute extraction circuit includes: Each peak detected within the predetermined period is classified into one of a P wave, a Q wave, an R wave, an S wave, and a T wave, and the P wave, the Q wave, the R wave, the S wave, Each envelope corresponding to the T wave is generated, the selection circuit specifies an envelope having the highest correlation with the respiratory cycle T2, and the processing circuit is information on the envelope specified by the selection circuit And using the envelope, extract respiration information related to the user's respiration.

  According to another aspect of the present invention, there is provided a method for monitoring biological information, in which (a) information on a potential difference is received from a measuring device that measures a potential difference between two electrodes arranged on a user's chest, and (b) At least the S-wave peak and the T-wave peak of the electrocardiogram are detected from the information on the potential difference, (c) information on the positions of the two electrodes in the chest of the user is obtained, and (d) the positions of the two electrodes One of the S wave peak and the T wave peak is selected based on the information of (e), from the time-series information of the S wave peak or the T wave peak selected by (d), Respiratory information relating to the user's respiration is extracted, and (f) the respiration information extracted in (e) is output.

  According to another aspect of the present invention, there is provided a method for monitoring biological information, in which (a) information on a potential difference is received from a measuring device that measures a potential difference between two electrodes arranged on a user's chest, and (b) Detecting a plurality of peaks included in the electrocardiogram from the information on the potential difference, and (c) attribute information of each peak detected within a predetermined period, the information on the amplitude of each peak, the information on the width, or the plurality And extracting attribute information that is information related to an envelope of a peak group having a common characteristic with respect to the waveform among the peaks of the plurality of peaks, and (d) referring to the attribute information of each peak to obtain a predetermined condition from the plurality of peaks A matching peak group is selected, and (e) respiration information related to the user's breathing is extracted from the time-series information of the peak group selected by (d), (f Outputting the respiratory information extracted by the (e).

  A computer program according to still another aspect of the present invention is a computer program executed by a computer provided in a biological information monitoring apparatus, and the computer program is arranged in the computer and (a) on the chest of the user. Receiving information on the potential difference from the measuring device that measures the potential difference between the two electrodes, and (b) detecting at least an S wave peak and a T wave peak of the electrocardiogram from the information on the potential difference, and (c) Information on the position of the two electrodes on the chest of the user is acquired; (d) one of the S wave peak and the T wave peak is selected based on the information on the position of the two electrodes; From the time-series information of the S wave peak or the T wave peak selected by d), the user's call Is extracted respiration information about, and outputs the breathing information extracted by (f) said (e).

  A computer program according to still another aspect of the present invention is a computer program executed by a computer provided in a biological information monitoring apparatus, and the computer program is arranged in the computer and (a) on the chest of the user. And (b) detecting a plurality of peaks included in the electrocardiogram from the information regarding the potential difference, and (c) detecting within a predetermined period. In addition, the attribute information of each peak is extracted, the information regarding the amplitude of each peak, the information regarding the width, or the information regarding the envelope of the peak group having the characteristics common to the waveform among the plurality of peaks. (D) referring to the attribute information of each peak, a predetermined condition is obtained from the plurality of peaks. And (e) extracting respiration information related to the user's respiration from the time-series information of the peak group selected in (d), and (f) (e) The respiration information extracted by the step is output.

  Hereinafter, prior to the description of the embodiment, a configuration for measuring chest impedance will be described. FIG. 8A is a diagram illustrating a schematic circuit configuration of the two-terminal method, and FIG. 8B is a diagram illustrating a schematic circuit configuration of the four-terminal method. Z represents the impedance of the object to be measured, and R1 to R4 represent the contact impedance between the electrode and the skin. “◯” on the drawing corresponds to an electrode.

  In the two-terminal method of FIG. 8A, Z + R1 + R2 is measured. On the other hand, in the four-terminal method of FIG. 8B, only Z is measured. Therefore, when measuring the chest impedance, the 4-terminal method is used when it is desired to eliminate the influence of the contact impedance between the electrode and the skin. That is, it can be said that the impedance measured by the four-terminal method is more accurate than that measured by the two-terminal method.

  Changes in chest impedance depend on heart activity (heartbeat) and lung activity (breathing). The reason why the impedance changes due to the heart activity (heartbeat) is that when the heart performs mechanical activities such as contraction and expansion, the cardiomyocytes are electrically excited (depolarized) and reverted (repolarized). is there. This electrical change in cardiomyocytes causes a change in impedance. On the other hand, the reason why the impedance changes due to lung activity (respiration) is as follows. That is, during inspiration, air is taken into the alveoli, making it difficult for current to flow. As a result, the impedance is increased. On the other hand, at the time of exhalation, air is discharged, and the current easily flows. As a result, the impedance is lowered. When the impedance is measured with electrodes attached to both hands, a change due to heartbeat and a change due to breathing appear in the impedance between both hands.

  In the embodiments described below, the chest opposite to the position of the user's heart will be described as the right chest. When the position of the user's heart is on the right chest, the chest opposite to the position of the user's heart is the left chest.

  There is also a view that the human heart is located approximately in the center of the body. Based on this view, the “position of the user's heart” in this specification refers to the position on the side where the ventricle (typically the left ventricle) that delivers blood to the aorta is present. This is because, by developing the ventricular muscle, contraction and expansion of the muscle can be obtained strongly as an electrocardiogram.

  Hereinafter, embodiments according to the present disclosure will be described with reference to the accompanying drawings. In each of the following embodiments, a configuration for measuring an electrocardiogram mainly by the above-described two-terminal method will be described. However, it is also possible to measure the electrocardiogram by the 4-terminal method. For reference, FIG. 17 also illustrates a configuration for measuring an electrocardiogram by the 4-terminal method. The configuration corresponds to the configuration of the first embodiment, but the same applies to the second and third embodiments.

(Embodiment 1)
(Biological information monitoring system configuration)
FIG. 9 shows a configuration of the biological information monitoring system 100 according to the present embodiment.

  The biological information monitoring system 100 includes a data storage device 6, a biological signal measuring device 200, and a biological information monitoring device 300.

  The biological signal measuring device 200 includes electrodes 2 a and 2 b and a potential measuring circuit 5. The realization form as the hardware of the biological signal measuring device 200 is, for example, a potential sensor with electrodes attached to the chest of the user 1. In the present specification, the electrodes 2a and 2b are described as components of the biological signal measurement device 200, but may not be components of the biological signal measurement device 200.

  The potential measurement circuit 5 acquires information on the potential difference using the electrodes 2a and 2b. The information regarding the potential difference may be a value indicating a potential difference between the two electrodes, or may be an impedance value. In the latter example, the impedance value may be measured using a potential difference between the two electrodes in a state where a power source is provided and electrically connected to the two electrodes and a potential is applied to the electrodes. The impedance value is obtained by dividing the potential measured at the two electrodes by the applied current value.

  Electrodes 2a and 2b are placed on the user's chest. For example, the user's chest is divided into a first region and a second region by the chest centerline. In the present specification, it is assumed that the positions of the electrodes 2a and 2b are provided in the first region, the second region, or the region near the center line of the chest. For example, the first region is the so-called left chest, the second region is the so-called right chest, and the region near the center line is almost in the middle of the chest.

  In the present specification, the electrode position may be described in relation to the user's heart position. For example, the expression “electrodes 2a and 2b are arranged in a region opposite to the heart” means that when the heart is located in the first region, electrodes 2a and 2b are opposite to the first region. It is arranged in the second region. The “first region” at this time is typically the left breast, but may be the right breast depending on the user.

  In addition, an earth electrode (for example, FIG. 2A to FIG. 7A) is additionally provided, and a potential difference between the electrode 2a and the earth and a potential difference between the electrode 2b and the earth are obtained, and these differences are obtained as a potential difference. May be.

  The potential measurement circuit 5 acquires the measured potential difference or impedance value as information about the potential difference. This information is sent to the biological information monitoring apparatus 300.

  The biological information monitoring device 300 includes a peak detection circuit 7, an envelope processing circuit 8, a respiration information output circuit 9, a peak selection circuit 10, and an interface device 11.

  The peak detection circuit 7 (hereinafter referred to as “detection circuit 7”) receives information on the potential difference acquired by the biological signal measuring device 200, for example, information on the potential difference of the chest. Based on the information, the detection circuit 7 detects P wave, Q wave, R wave, S wave, and T wave, which are ECG peaks. In this example, a P wave, a Q wave, an R wave, an S wave, and a T wave are listed, but it is sufficient that at least a T wave or an S wave can be acquired.

  Note that the P wave, Q wave, R wave, S wave, and T wave themselves mean peaks, but in this specification, for example, an S wave is used to more directly indicate a peak. Sometimes expressed as a peak or a T wave peak.

  Hereinafter, an example of a method for detecting the S wave peak and the T wave peak will be described. The S wave peak and the T wave peak are obtained as the minimum value or the maximum value in the waveform example shown in FIG. It should be noted that the waveform shown in FIG. 1 can be reversed when, for example, the electrodes 2a and 2b are replaced, and in that case, the minimum value or the maximum value needs to be replaced and read.

  An example of the detection method of the S wave peak is as follows.

Example S-1:
The detection circuit 7 calculates the minimum value of the peak below a predetermined threshold (for example, the value of the broken line A in FIG. 1) in one cycle of the electrocardiogram from the information regarding the potential difference acquired by the biological signal measuring device 200. Detect as wave peak.

Example S-2:
The detection circuit 7 detects an R wave within one cycle of the electrocardiogram from information on the potential difference acquired by the biological signal measuring device 200, and detects a minimum value after the R wave as an S wave peak. The detection circuit 7 can specify a waveform having a peak equal to or greater than a predetermined threshold (for example, the value of the broken line B in FIG. 1) as an R wave.

  An example of a T-wave peak detection method is as follows.

Example T-1:
The detection circuit 7 detects the local maximum value after the S wave peak detected by any of the above-described methods as the T wave peak from the information regarding the potential difference acquired by the biological signal measuring device 200.

Example T-2:
The detection circuit 7 detects an R wave within one cycle of the electrocardiogram from information on the potential difference acquired by the biological signal measuring device 200, and detects a maximum value after the R wave as a T wave peak. The detection circuit 7 can specify a waveform having a peak equal to or greater than a predetermined threshold (for example, the value of the broken line B in FIG. 1) as an R wave.

  It should be noted that other detection methods for S waves are also conceivable.

Example S-3:
The detection circuit 7 detects an R wave and a T wave within one cycle of the electrocardiogram from information on the potential difference acquired by the biological signal measuring device 200, and the R wave and the T wave that exist between the R wave and the T wave. A peak having a polarity opposite to that of the wave may be detected as an S wave peak.

  An implementation form of the detection circuit 7 as hardware may be a potential sensor, or may be a PC, a smartphone, or a tablet. A CPU (processor; the same applies hereinafter) of a PC, smartphone, or tablet receives information on a potential difference transmitted by wire or wireless from the potential measurement circuit 5 by executing installed software (computer program). S wave peak, T wave peak, etc. are detected by information processing based on software.

  The envelope processing circuit 8 (hereinafter referred to as “processing circuit 8”) extracts respiration information related to the user's respiration from time-series information of S wave peaks or T wave peaks detected by the detection circuit 7. To do. More specifically, the processing circuit 8 generates an envelope by interpolating between S wave peaks or between T wave peaks with a spline curve. The generated S-wave peak or T-wave peak envelope is used as respiration information. Whether the S-wave peak or the T-wave peak is used to generate the envelope depends on the result of selection by the peak selection circuit 10 described later.

  Note that the processing circuit 8 may extract respiratory information by another method. For example, when the S wave peak and the T wave peak are periodically obtained, the electrode temporarily floats due to the movement of the user, and a specific peak may disappear. In that case, the processing circuit 8 specifies the time corresponding to each of the S wave peak or the T wave peak, calculates a representative value instead of the peak value using the measured values before and after that time, A respiratory component curve may be calculated from the representative value. As a representative value, for example, an average value of S wave peaks or T wave peaks so far may be used.

  An implementation form of the processing circuit 8 as hardware may be a potential sensor, or may be a PC, a smartphone, or a tablet. The CPU of the PC, smartphone, or tablet may extract respiratory information (envelope) by information processing based on software by executing installed software (computer program).

  The respiration information output circuit 9 (hereinafter referred to as “output circuit 9”) outputs the respiration information generated by the processing circuit 8. The form of output may be, for example, visual output on a screen or the like, or may be wired or wireless transmission. In the latter example, respiratory information can be stored in the data storage device 6.

  The implementation form of the output circuit 9 as hardware is a display device, a communication circuit, and a communication interface.

  The peak selection circuit 10 (hereinafter, referred to as “selection circuit 10”) is a P wave, Q wave, R wave, which is an electrocardiographic peak, depending on the electrode position with respect to the heart of the user acquired by the interface device 11 described later. Select either S wave or T wave. In the present embodiment, the S wave is selected when the electrodes 2a and 2b are arranged on the chest opposite to the position of the heart, and the T wave is selected for other relationships.

  The implementation form of the selection circuit 10 as hardware may be a potential sensor, or may be a PC, a smartphone, or a tablet. The CPUs of PCs, smartphones, and tablets can select S-wave or T-wave by executing installed software (computer program) and performing information processing based on software according to the electrode position relative to the position of the user's heart. That's fine.

  The interface device 11 (hereinafter referred to as “I / F device 11”) acquires information on the positions of the electrodes 2a and 2b on the chest of the user. The I / F device 11 can also acquire information on the position of the user's heart. The electrode position and the heart position may be specified by any of the left chest, the right chest, and the middle of the chest, for example.

  Generally, it is said that the position of a person's heart is the left chest. Therefore, the I / F device 11 does not always need to acquire information on the position of the user's heart. Only when the biological information monitoring system 100 is used by a user whose heart position is on the right chest, the I / F device 11 needs to acquire information on the user's heart position. When the I / F device 11 does not acquire heart position information, the biological information monitoring apparatus 300 can perform processing assuming that the user's heart position is the left breast. In this case, the I / F device 11 only needs to acquire information on the positions of the electrodes 2a and 2b on the chest of the user.

  The I / F device 11 may be an input device such as a touch screen, a keyboard, or a mouse, or may be a terminal provided in the biological information monitoring device 300 for connecting an external device. The latter example is an Ethernet (registered trademark) terminal for connecting the biological information monitoring apparatus 300 to a network, for example. If an input device such as a keyboard or a mouse is not a constituent element of the biological information monitoring device 300, the I / F device 11 may be a USB terminal or a PS / 2 terminal, for example.

  When the I / F device 11 is realized as a communication terminal, the I / F device 11 and the output circuit 9 can be unified.

  The data storage device 6 is, for example, a recording medium and / or a recording device including a recording medium, and stores the respiratory information transmitted from the output circuit 9. As the recording medium, a semiconductor recording medium, a magnetic recording medium, an optical recording medium, and the like can be considered.

(Overall processing flow)
FIG. 10 shows an overall processing flow of the biological information monitoring system 100 of the present embodiment.

<Step S101>
The I / F device 11 of the biological signal measuring device 200 receives information specifying at least the positions of the electrodes 2a and 2b from the user. The positions of the electrodes 2a and 2b are specified by, for example, whether the positions of the electrodes 2a and 2b are the middle of the chest, the right breast, or the left breast. The I / F device 11 may further receive information specifying whether the position of the heart is the left chest or the right chest from the user. Inputs relating to the position of the heart are “right” and “left”. Inputs relating to the electrode position are “middle”, “right” and “left”.

<Step S102>
The selection circuit 10 selects one of the P wave, Q wave, R wave, S wave, and T wave, which is an electrocardiographic peak, according to the electrode position with respect to the heart of the user detected in step S101. As described above, in the present embodiment, the S wave is selected when the electrodes 2a and 2b are arranged on the chest opposite to the position of the heart, and the T wave is selected in other cases. select.

<Step S103>
The potential measurement circuit 5 measures the potential difference between the two electrodes 2a and 2b arranged on the chest of the user, and generates information regarding the potential difference. This step S103 may be performed before step S101, or may be performed between steps S101 and S102.

<Step S104>
The detection circuit 7 detects an electrocardiogram peak from the information regarding the potential difference generated in step S103. Depending on the electrocardiographic peak detection method, in order to detect an S wave peak or a T wave peak, it is necessary to first detect an R wave peak or the like. The detection circuit 7 performs the peak detection operation.

<Step S105>
The processing circuit 8 extracts the S wave peak or T wave peak selected in step S102 from the time series of the electrocardiographic peaks detected in step S104, and generates respiratory information. More specifically, the processing circuit 8 generates an envelope by interpolating between the electrocardiographic peaks of each S wave peak or each T wave peak with a spline curve. The generated envelope is respiratory information.

<Step S106>
The output circuit 9 outputs the respiration information created in step S105. As an output form, it may be displayed on a screen or recorded on a recording medium.

  Next, processing for selecting any one of the P wave, Q wave, R wave, S wave, and T wave, which is an electrocardiographic peak, according to the electrode position of the user with respect to the heart according to step S102 described above will be described in detail.

  FIG. 11 shows a processing flow in which the detection circuit 7 selects any one of the P wave, Q wave, R wave, S wave, and T wave that are ECG peaks.

<Step S1021>
The selection circuit 10 determines whether or not the user's heart is on the left side of the chest by the user's input via the I / F device 11. By default, the heart is on the left of the chest. If the heart is on the left side of the chest, processing proceeds to step S1022. If not, that is, if it is input that the user's heart is on the right side of the chest, the process proceeds to step S1023.

<Step S1022>
If it is determined in step S1021 that the heart is on the left side of the chest, the selection circuit 10 determines whether the electrode position is on the right side of the chest. That is, the selection circuit 10 determines whether or not the electrode position is on the opposite side of the heart position. If the electrode position is on the right side of the chest, the process proceeds to step S1024. Otherwise, the process proceeds to step S1025.

<Step S1023>
If it is determined in step S1021 that the heart is on the right side of the chest, the selection circuit 10 determines whether the electrode position is on the left side of the chest. That is, the selection circuit 10 determines whether or not the electrode position is on the opposite side of the heart position. If the electrode position is on the left side of the chest, the process proceeds to step S1026. Otherwise, the process proceeds to step S1027.

<Step S1024>
If it is determined in step S1022 that the electrode position is on the right side of the chest, the detection circuit 7 selects the S wave peak and ends the process.

<Step S1025>
If it is determined in step S1022 that the electrode position is in the middle or left side of the chest, the detection circuit 7 selects the T wave peak and ends the process.

<Step S1026>
If it is determined in step S1023 that the electrode position is on the left side of the chest, the detection circuit 7 selects the S wave peak and ends the process.

<Step S1027>
If it is determined in step S1023 that the electrode position is in the middle or right side of the chest, the detection circuit 7 selects the T wave peak and ends the process.

  By the above-described processing, the detection circuit 7 selects the S wave peak or the T wave peak. Thereby, in step S105 of FIG. 10, respiratory information is generated from the peak group (peak time series) corresponding to the selection result.

(Embodiment 2)
The biological information monitoring apparatus according to the present embodiment can select a peak group including appropriate respiration information without acquiring electrode position information from the user. The biological information monitoring apparatus selects a peak group using the amplitude and width of each peak (P wave, Q wave, R wave, S wave, T wave) of the electrocardiogram.

(Biological information monitoring system configuration)
FIG. 12 shows a configuration of the biological information monitoring system 102 according to the present embodiment. The biological information monitoring system 102 includes a data storage device 6, a biological signal measuring device 200, and a biological information monitoring device 302. The configurations and operations of the data storage device 6 and the biological signal measurement device 200 are the same as those in the first embodiment. Therefore, the same reference numerals are given and description thereof is omitted.

  The biological information monitoring apparatus 302 includes a detection circuit 7, a processing circuit 8, an output circuit 9, a selection circuit 10, and a peak attribute extraction circuit 12.

  Among these, the configuration and operation of the peak attribute extraction circuit 12 (hereinafter referred to as “extraction circuit 12”) will be described in detail below. Since the configurations and operations of the detection circuit 7, the processing circuit 8, the output circuit 9, and the selection circuit 10 have been described in relation to the biological information monitoring apparatus 300 of the first embodiment, description thereof will be omitted. Of these components, when the operation is changed or added in connection with the introduction of the extraction circuit 12, the operation will be described as appropriate.

  The extraction circuit 12 extracts attribute information of each peak detected within a predetermined period. In the present embodiment, the attribute information is intended to be information related to the amplitude of each peak and information related to the width.

  Hereinafter, the operation of the extraction circuit 12 according to the present embodiment will be described.

  The extraction circuit 12 acquires information on the amplitude and width of each peak detected by the detection circuit 7 as attribute information. In the present embodiment, the detection circuit 7 may detect not only a T wave peak or an S wave peak but also, for example, a P wave, a Q wave, and an R wave.

  FIG. 13 schematically shows the peak amplitude Amp and the width D. FIG. The extraction circuit 12 acquires information on the amplitude Amp and the width D for each detected peak.

  The realization form of the extraction circuit 12 as hardware may be a potential sensor, or may be a PC, a smartphone, or a tablet. The CPUs of PCs, smartphones, and tablets receive wave peak information detected by the detection circuit 7 and transmitted by wire or wireless by executing installed software (computer program). And CPU acquires the above-mentioned attribute information by information processing based on software.

  The selection circuit 10 selects one of the P wave, Q wave, R wave, S wave, and T wave using the attribute information of each wave extracted by the extraction circuit 12. This will be described more specifically. First, the selection circuit 10 holds a predetermined threshold Amp_th1 and a width D_th1 prepared in advance. Using the attribute information of each wave extracted by the extraction circuit 12, the selection circuit 10 compares the obtained amplitude and width of each wave with the predetermined threshold Amp_th1 and the width D, and the amplitude is equal to or greater than the predetermined threshold Amp_th1. The peak with the widest width is selected. The reason why the peak having the widest width is selected is that a peak having a wide width can be detected more stably.

  The processing circuit 8 acquires time-series information of the peak group selected by the selection circuit 10 and generates an envelope by interpolating between adjacent peaks with a spline curve. The generated envelope is used as respiration information.

  As another method for generating respiratory information, the method using the representative value described in the first embodiment may be used.

(Overall processing flow)
FIG. 14 shows an overall processing flow of the biological information monitoring system 102 according to the present embodiment.

<Step S201>
The potential measuring circuit 5 measures a potential difference from the two electrodes 2a and 2b arranged on the chest of the user.

<Step S202>
The detection circuit 7 detects P wave, Q wave, R wave, S wave, and T wave, which are each peak of electrocardiogram within a predetermined time T1 from the start of measurement. The predetermined time T1 is a time sufficiently including a plurality of beat periods. By continuously detecting each peak over a plurality of pulsation cycles, the detection accuracy can be further increased.

<Step S203>
The extraction circuit 12 acquires the amplitude Amp (FIG. 13) of each peak of the electrocardiogram detected within the time T1. In each peak, there may be two or more cases within time T1. In that case, the extraction circuit 12 may take an average value thereof.

  Among the peaks detected within T1, there may be a peak (outlier) that is affected by the waveform disturbance. In order to exclude outliers in the calculation of the average value, the average value and the standard deviation are obtained once. Only values of amplitudes that are separated by a standard deviation (eg, 3 × standard deviation) multiplied by a predetermined coefficient are extracted based on the obtained average value. Recalculate the average value from the extracted amplitude values.

<Step S204>
The extraction circuit 12 acquires the width D (FIG. 13) of each peak of the electrocardiogram detected within T1. In each peak, there may be two or more cases within time T1. In that case, the extraction circuit 12 may take an average value thereof. In each peak, when there are two or more within T1, the average value is taken.

  Among the peaks detected within T1, there may be a peak (outlier) that is affected by the waveform disturbance. In order to exclude outliers in the calculation of the average value, the average value and the standard deviation are obtained once. Based on the obtained average value, only a value having a width separated by a standard deviation (for example, 3 × standard deviation) multiplied by a predetermined coefficient is extracted. Recalculate the average value from the extracted width values.

<Step S205>
The selection circuit 10 selects a peak whose amplitude acquired in step S203 is greater than or equal to a predetermined threshold Amp_th1. This peak is one of a P wave, a Q wave, an R wave, an S wave, and a T wave that are electrocardiographic peaks.

<Step S206>
The selection circuit 10 further selects the peak having the largest width acquired in step S204 from the peaks selected in step S205. Information for specifying the selected peak is transmitted from the selection circuit 10 to the processing circuit 8.

<Step S207>
The processing circuit 8 identifies the peak group selected in step S206 from the chest potential difference measured in step S201.

<Step S208>
The processing circuit 8 generates respiratory information from the time-series information of the peaks identified in step S207. More specifically, an envelope is generated by interpolating between peaks with a spline curve. The generated envelope is used as respiration information.
<Step S209>
The output circuit 9 outputs the respiration information created in step S208. As an output form, it may be displayed on a screen or recorded on a recording medium.

  As described above, according to the processing of the present embodiment, it is possible to select a peak group including appropriate respiration information without acquiring information on the position of the electrode from the user.

(Embodiment 3)
The biological information monitoring apparatus according to the present embodiment can also select a peak group including appropriate respiration information without acquiring electrode position information from the user. The biological information monitoring apparatus instructs the user of a predetermined respiration cycle T2 within a predetermined time T1 from the start of measurement, and envelopes each peak (P wave, Q wave, R wave, S wave, T wave) within the time T1. Generate a line. The biological information monitoring apparatus selects a peak having the largest correlation between the envelope and the respiratory cycle T2.

(Biological information monitoring system configuration)
FIG. 15 shows the configuration of the biological information monitoring system 104 according to this embodiment. The biological information monitoring system 104 includes a data storage device 6, a biological signal measuring device 200, and a biological information monitoring device 304. The configurations and operations of the data storage device 6 and the biological signal measurement device 200 are the same as those in the first embodiment. Therefore, the same reference numerals are given and description thereof is omitted.

  The biological information monitoring device 304 includes a detection circuit 7, a processing circuit 8, an output circuit 9, a selection circuit 10, a peak attribute extraction circuit 13, and an instruction signal generation circuit 14.

  Among these, the configurations and operations of the peak attribute extraction circuit 13 and the instruction signal generation circuit 14 will be described in detail below. Since the configurations and operations of the detection circuit 7, the processing circuit 8, the output circuit 9, and the selection circuit 10 have been mainly described in relation to the biological information monitoring apparatus 300 of the first embodiment, the description thereof is omitted. Of these components, when the operation is changed or added in connection with the introduction of the extraction circuit 13, the operation will be described as appropriate.

  A peak attribute extraction circuit 13 (hereinafter referred to as “extraction circuit 13”) extracts attribute information of each peak detected within a predetermined period T1. In the present embodiment, the attribute information is intended for envelope information generated using the amplitude of each peak.

  More specifically, the extraction circuit 13 divides the plurality of peaks detected by the detection circuit 7 into peak groups having characteristics common to each other with respect to the waveform. In short, the “peak group having characteristics common to waveforms” is, for example, a T-wave peak group and an S-wave peak group. That is, this process corresponds to an operation of classifying the plurality of peaks detected by the detection circuit 7 into P wave, Q wave, R wave, S wave, and T wave, respectively.

  The extraction circuit 13 generates an envelope of each peak (P wave, Q wave, R wave, S wave, T wave) included in the time T1. The extraction circuit 13 generates an envelope of each peak by interpolating between the peaks with a spline curve. The extraction circuit 13 sends the envelope information of each peak to the selection circuit 10.

  The realization form of the extraction circuit 13 as hardware may be a potential sensor, or may be a PC, a smartphone, or a tablet. The CPUs of PCs, smartphones, and tablets receive wave peak information detected by the detection circuit 7 and transmitted by wire or wireless by executing installed software (computer program). And CPU acquires the above-mentioned attribute information by information processing based on software.

  Since the extraction circuit 13 generates an envelope for each peak, the processing circuit 8 no longer needs to obtain an envelope. The processing circuit 8 may receive the envelope information that is the selected peak from the selection circuit 10 and extract the respiratory information based on the envelope. As a method for generating respiration information, the method using the representative value described in the first embodiment may be used.

  The instruction signal generation circuit 14 generates a signal (instruction signal) for instructing the user of a predetermined respiratory cycle T2. The respiratory cycle T2 is a time required when a series of operations of inhaling and exhaling is defined as one cycle. An example of the instruction signal is an audio signal for presenting a voice “please breathe” or “puff out” to the user via a speaker. Another example of the instruction signal is an image signal for presenting a text or an image “please breathe” or “please breathe” to the user via a display (not shown).

  The instruction signal generation circuit 14 determines in advance a period T1 in which audio and / or video is presented based on the instruction signal, and generates an instruction signal during the period T1. The beginning of the period T1 is, for example, the start of electrocardiogram measurement using the electrodes 2a and 2b. In the present embodiment, the time T1 is a time that sufficiently includes a plurality of respiratory cycles T2.

  The selection circuit 10 calculates the correlation between the envelope of each peak (P wave, Q wave, R wave, S wave, T wave) generated by the extraction circuit 13 and the respiratory cycle T2, and the envelope is the respiratory cycle T2. And select the peak with the highest correlation. In this embodiment, selection of a peak is synonymous with selection of an envelope. As a correlation calculation method, Fourier transform is applied to the envelope, and the frequency characteristic of the envelope is obtained. It is determined whether or not the frequency at which the peak appears in the frequency characteristic matches the frequency of the respiratory cycle T2. The correlation may be calculated based on the peak detection rate. "Peak detection rate" is the probability that only one peak will be present correctly in the envelope in one respiratory cycle.

(Overall processing flow)
FIG. 16 shows an overall processing flow of the biological information monitoring system 104 of the present embodiment.

<Step S301>
The potential measuring circuit 5 measures a potential difference from the two electrodes 2a and 2b arranged on the chest of the user.

<Step S302>
The instruction signal generation circuit 14 instructs the user about a predetermined respiratory cycle T2 within a predetermined time T1 from the start of measurement. As an instruction method, voices of “suck” and “suck” are output to the user through the speaker. The instruction may be displayed on a display screen.

<Step S303>
The detection circuit 7 detects P wave, Q wave, R wave, S wave, and T wave, which are each peak of electrocardiogram within T1. The predetermined time T1 is a time sufficiently including a plurality of respiratory cycles T2. By continuously detecting each peak over a plurality of respiratory cycles T2, it is possible to increase the detection accuracy.

<Step S304>
The extraction circuit 13 generates an envelope of each peak (P wave, Q wave, R wave, S wave, T wave) within T1. More specifically, an envelope is generated by interpolating between peaks with a spline curve.

<Step S305>
The selection circuit 10 calculates the correlation between the envelope of each peak (P wave, Q wave, R wave, S wave, T wave) generated by the extraction circuit 13 and the respiratory cycle T2. As a method of calculating the correlation, a Fourier transform is applied to the envelope to obtain a frequency characteristic. It is determined whether or not the frequency at which the peak appears in the frequency characteristic matches the frequency of the respiratory cycle T2. The correlation may be calculated based on the peak detection rate.

<Step S306>
The selection circuit 10 selects the peak having the highest correlation calculated in step S305.

<Step S307>
The processing circuit 8 receives information about the envelope of the peak selected in step S306 from the selection circuit 10.

<Step S308>
The processing circuit 8 generates respiration information from the envelope information received in step S307.

<Step S309>
The output circuit 9 outputs the respiration information created in step S308. As an output form, it may be displayed on a screen or recorded on a recording medium.

  The exemplary embodiments according to the present disclosure have been described above.

  Each of the above embodiments is a configuration example in which electrocardiogram is measured by the two-terminal method. However, it is also possible to measure the electrocardiogram by the 4-terminal method.

  For example, FIG. 17 shows a configuration of the biological information monitoring system 110 according to a modification of the first embodiment. The biological information monitoring system 110 measures the chest impedance of the user 1 by the 4-terminal method.

  The biological information monitoring system 110 includes a data storage device 6, a biological signal measuring device 202, and a biological information monitoring device 300.

  The biological information monitoring system 110 is different from the configuration of the biological information monitoring system 100 with respect to the configuration of the biological signal measuring device. Only the configuration related to the difference will be described below.

  The biological signal measuring apparatus 202 measures the potential using the four electrodes 2a, 2b, 3a, and 3c. The electrodes 2a and 2b are potential measurement electrodes. The electrodes 3a and 3b are current application electrodes.

  The potential measurement electrodes 2a and 2b and the current application electrodes 3a and 3b are installed at positions that satisfy the measurement conditions of the four-terminal method. In other words, the potential measuring electrodes 2a and 2b are installed, for example, within a range through which a current flowing from the current applying electrode 3a to the current applying electrode 3b passes. More specifically, the potential measuring electrodes 2a and 2b are provided so as to be sandwiched between the current applying electrodes 3a and 3b.

  The potential measurement circuit 5 includes a current source 5a and an impedance measurement circuit 5b.

  The current source 5a supplies a current to the current application electrodes 3a and 3b arranged on the chest of the user. The current source 5a is, for example, a built-in battery (not shown) and a circuit provided for supplying current from the battery. Note that the current source 5a may be configured in a manner that does not include a built-in battery.

  In the present specification, the current value applied by the current source 5a is set to a value (for example, several nA to several hundred μA) smaller than the current value (for example, 350 μA) used for conventional electrocardiographic measurement. This is because the biological signal measuring apparatus 202 assumes that the capacity of the battery (not shown) must be reduced due to downsizing and the like. By measuring the impedance with a current value lower than the conventionally applied current value, the driving time of the biological signal measuring device 202 can be extended. As described above, in the present embodiment, the current source 5a applies a current having a value smaller than 350 μA.

  In the present specification, the current source 5a applies a sine wave alternating current, and the current value is ± 10 nA.

  The impedance measurement circuit 5b measures the value of the chest impedance of the user at a plurality of times using the potential difference between the first potential measurement electrode unit 2a and the second potential measurement electrode unit 2b. Specifically, the impedance measurement circuit 5b measures a potential difference between the potential measurement electrodes 2a and 2b. The impedance measurement circuit 5b divides the measured potential difference value by the current value applied from the current source 5a, and acquires the division result as a chest impedance value. The chest impedance value is sent to the detection circuit 7 as information on the potential difference.

  Hereinafter, the processing performed in the biological information monitoring apparatus 300 is as described above. The operation of the biological information monitoring system 110 is also performed as shown in FIG.

  According to the biological information monitoring system according to the present disclosure, even if the user puts the electrode in the wrong position, even if the electrode cannot be attached to the designated position due to various circumstances, Information can be measured. As a result, the user can easily perform respiration monitoring at home and can measure respiration information even if the electrode positions are different. The present invention can be applied to fields such as confirmation of health conditions at home and the like, and grasping of dynamic load conditions during sports. It is also possible to simplify the measurement in the hospital.

2a, 2b Electrode 5 Potential measurement circuit 6 Data storage device 7 Peak detection circuit (detection circuit)
8 Envelope processing circuit (processing circuit)
9 Respiration information output circuit (output circuit)
10 Peak selection circuit (selection circuit)
11 I / F device 12, 13 Peak attribute extraction circuit (extraction circuit)
14 Instruction signal generation circuit 100, 102, 104 Biological information monitoring system 200 Biological signal measuring device 300, 302, 304 Biological information monitoring device

Claims (16)

A detection circuit that receives information on the potential difference from a measurement device that measures the potential difference between the two electrodes arranged on the chest of the user, and detects at least the S wave peak and the T wave peak of the electrocardiogram from the information on the potential difference;
An interface device for obtaining information on the positions of the two electrodes on the chest of the user;
A selection circuit that selects one of the S-wave peak and the T-wave peak based on the position information of the two electrodes;
A processing circuit that extracts respiration information related to the user's respiration from time-series information of the S wave peak or the T wave peak selected by the selection circuit;
A biological information monitoring apparatus comprising: an output circuit that outputs the respiratory information extracted by the processing circuit.   The biological information monitoring device according to claim 1, wherein the interface device acquires information on positions of the two electrodes input from the outside.   The biological information monitoring device according to claim 2, wherein the interface device further acquires information on a position of the heart of the user input from the outside.   The selection circuit selects one of the S wave peak and the T wave peak depending on whether or not the two electrodes are arranged on a chest opposite to the position of the heart of the user. 4. The biological information monitoring device according to any one of items 1 to 3.   The biological information monitoring apparatus according to claim 4, wherein the selection circuit selects the S wave peak when the two electrodes are disposed on a chest opposite to the position of the heart of the user. .   The biological information monitoring apparatus according to claim 4, wherein the selection circuit selects the T-wave peak when the two electrodes are not arranged on the chest opposite to the position of the user's heart. .   The processing circuit generates an envelope of the S wave peak or the T wave peak from time-series information of the S wave peak or the T wave peak selected by the selection circuit, and uses the envelope The biological information monitoring apparatus according to any one of claims 1 to 6, wherein respiration information relating to respiration of the user is extracted. A detection circuit that receives information on a potential difference from a measurement device that measures a potential difference between two electrodes arranged on the chest of the user, and detects a plurality of peaks included in the electrocardiogram from the information on the potential difference;
An attribute extraction circuit for extracting attribute information of each peak detected within a predetermined period;
A selection circuit that refers to the attribute information of each peak and selects a peak group that matches a predetermined condition from the plurality of peaks;
A processing circuit that extracts respiration information related to the user's respiration from time-series information of the peak group selected by the selection circuit;
An output circuit for outputting the respiration information extracted by the processing circuit,
The said attribute information is a biological information monitoring apparatus which is the information regarding the amplitude of each said peak, the information regarding a width | variety, or the information regarding the envelope of the peak group which has the characteristic common regarding a waveform among these peaks.   The biological information monitoring apparatus according to claim 8, wherein the attribute extraction circuit extracts information regarding the amplitude and width of each peak as the attribute information.   The biological information monitoring apparatus according to claim 9, wherein the selection circuit selects a peak group having an amplitude equal to or greater than a first threshold and a maximum width with reference to the attribute information of each peak.   The said processing circuit produces | generates an envelope from the time series information of the said peak group selected by the said selection circuit, The respiratory information regarding the said user's respiration is extracted using the said envelope. The biological information monitoring apparatus according to 1. A signal generation circuit for generating a signal for instructing the user of a predetermined respiratory cycle T2 within a predetermined time T1 from the start of the measurement of the potential difference;
The attribute extraction circuit classifies each peak detected within the predetermined period as one of a P wave, a Q wave, an R wave, an S wave, and a T wave, and the P wave, the Q wave, and the R wave. Each envelope corresponding to the wave, the S wave, and the T wave,
The selection circuit specifies an envelope having the highest correlation with the respiratory cycle T2,
The biological information monitoring apparatus according to claim 8, wherein the processing circuit receives information on the envelope specified by the selection circuit, and extracts respiration information related to the user's respiration using the envelope. (A) receiving information on a potential difference from a measuring device that measures a potential difference between two electrodes arranged on the chest of the user;
(B) detecting at least an S-wave peak and a T-wave peak of electrocardiogram from the information on the potential difference;
(C) obtaining information on the position of the two electrodes on the chest of the user;
(D) selecting one of the S wave peak and the T wave peak based on the position information of the two electrodes;
(E) extracting respiration information related to the user's respiration from the time-series information of the S wave peak or the T wave peak selected by (d);
(F) outputting the respiratory information extracted by (e);
A method for monitoring biological information. (A) receiving information on a potential difference from a measuring device that measures a potential difference between two electrodes arranged on the chest of the user;
(B) detecting a plurality of peaks included in the electrocardiogram from the information on the potential difference,
(C) Attribute information of each peak detected within a predetermined period, which is information about amplitude of each peak, information about width, or an envelope of a peak group having characteristics common to waveforms among the plurality of peaks Extract attribute information that is information about the line,
(D) Referring to the attribute information of each peak, select a peak group that matches a predetermined condition from the plurality of peaks,
(E) Extracting respiratory information related to the user's breathing from the time-series information of the peak group selected by (d),
(F) outputting the respiratory information extracted by (e);
A method for monitoring biological information. A computer program executed by a computer provided in the biological information monitoring device,
The computer program is stored in the computer.
(A) receiving information on a potential difference from a measuring device that measures a potential difference between two electrodes arranged on the chest of the user;
(B) From the information regarding the potential difference, at least the S wave peak and the T wave peak of the electrocardiogram are detected,
(C) obtaining information on the position of the two electrodes on the chest of the user;
(D) One of the S wave peak and the T wave peak is selected based on the information on the positions of the two electrodes,
(E) extracting respiratory information related to the user's breathing from the time-series information of the S wave peak or the T wave peak selected by (d);
(F) outputting the respiratory information extracted by (e);
Computer program. A computer program executed by a computer provided in the biological information monitoring device,
The computer program is stored in the computer.
(A) receiving information on a potential difference from a measuring device that measures a potential difference between two electrodes arranged on the chest of the user;
(B) detecting a plurality of peaks included in the electrocardiogram from the information on the potential difference,
(C) Attribute information of each peak detected within a predetermined period, which is information about amplitude of each peak, information about width, or an envelope of a peak group having characteristics common to waveforms among the plurality of peaks Extract attribute information that is information about the line,
(D) With reference to the attribute information of each peak, a peak group that matches a predetermined condition is selected from the plurality of peaks,
(E) extracting respiration information related to the user's respiration from the time-series information of the peak group selected by (d),
(F) outputting the respiratory information extracted by (e);
Computer program.

Images