JP2012035055A - Respiration training apparatus and respiration training system - Google Patents

Abstract

PROBLEM TO BE SOLVED: To enable training of breathing efficiently using bioelectrical impedances.SOLUTION: A living body determination apparatus 1 includes a bioelectrical impedance determinination part 200 for determining the bioelectrical impedance of a specified region in a human subject. A CPU 170 controls the bioelectrical impedance determinination part 200 to determinine a first bioelectrical impedance Za at the upper body trunk of the human subject and a second bioelectrical impedance Zb at the middle body trunk. Besides, the CPU 170 defines, in mutually orthogonally crossed two axes, one axis to be the first bioelectrical impedance Za and the other axis to be the second bioelectrical impedance Zb, to generate display data of a Lissajous figure showing change over time in the measurement values of the first bioelectrical impedance Za and the second bioelectrical impedance Zb.

Description

  The present invention relates to an apparatus and system for training breathing.

  Various devices that measure bioelectric impedance and estimate the state of a living body based on the measurement result are known. As one of such devices, Patent Document 1 discloses a technique for estimating vital capacity based on trunk impedance.

  Breathing is the only biological data (blood pressure, body temperature, skin temperature, electroencephalogram, pulse wave, etc.) that can be self-controlled. Therefore, breathing, such as yoga, pilates, qigong, chiropractic, etc. There are many health laws to enhance. Breathing can be broadly divided into chest breathing and abdominal breathing.

Japanese Patent Laying-Open No. 2007-50127 (see paragraph 0020)

By the way, when breathing is trained, it is desirable to be able to grasp whether or not chest breathing and abdominal breathing are correctly performed and the magnitude of those breaths. However, in the prior art, it has not been possible to know from the bioelectrical impedance whether the subject's breathing is chest or abdominal.
An object of the present invention is to provide a breathing training apparatus and a breathing training system that can efficiently train breathing using bioelectrical impedance.

  The present invention will be described below. In addition, in order to make an understanding of this invention easy, the code | symbol etc. of an accompanying drawing are attached in parenthesis, However, This invention is not limited to the aspect of illustration by it.

  In order to solve the above-described problems, a respiratory training device (1) according to the present invention includes a first bioelectrical impedance (Za) of an upper trunk that includes a lung of a subject and does not include an abdomen, and a trunk that includes the abdomen of the subject. The bioelectrical impedance measuring unit (170, 200) that measures the second bioelectrical impedance (Zb) in the middle, and one of the two axes orthogonal to each other is the first bioelectrical impedance and the other is the second A display for generating display data of a Lissajous figure (FIGS. 32 to 35 and FIGS. 37 to 39) showing bioelectrical impedance and a change with time of the measured value of the first bioelectrical impedance and the measured value of the second bioelectrical impedance A data generation unit (170).

  Note that the two axes orthogonal to each other are, for example, the X axis and the Y axis. However, the present invention is not limited to this. For example, the X axis and the Y axis may be two axes inclined by 45 degrees. Further, the Lissajous figure may indicate, for example, one breathing state as shown in FIGS. 32 and 33, or a plurality of breathing states continuously as shown in FIGS. 34 and 35. May be shown. The respiratory training apparatus may include a display unit that displays a Lissajous figure, or may include an output unit that outputs display data of the Lissajous figure to an external display device.

  For example, in the case of thoracic respiration, as shown in FIG. 10, the first bioelectrical impedance Za and the second bioelectrical impedance Zb change in an increasing direction during inspiration, and the first bioelectrical impedance Za and the second living body during exhalation. Both the electrical impedances Zb change in a decreasing direction. Therefore, when the ratio of the chest type respiration in the respiration of the subject is extremely high, the locus of the Lissajous figure becomes an inclined straight line as shown in FIGS. 32 and 34, for example. Also, if the chest breathing is shallow, the locus of the Lissajous figure becomes small, and if the chest breathing is deep, the locus of the Lissajous figure becomes large.

  On the other hand, in the case of abdominal breathing, as shown in FIG. 9, both the first bioelectrical impedance Za and the second bioelectrical impedance Zb change in an increasing direction during inspiration, and the first bioelectrical impedance Za decreases during exhalation. While changing in the direction, the second bioelectrical impedance Zb changes in the increasing direction. Therefore, when the subject's breathing includes abdominal breathing, the locus of the Lissajous figure is bent as shown in FIGS. 33 and 35, for example.

  Note that the Lissajous figure shown in FIG. 33 is a case where the ratio of the chest breathing and the abdominal breathing to one breath is 50%. In this case, the locus of the Lissajous figure has a boomerang shape ("<" shape), and the shape of the locus is almost symmetrical vertically. However, if the proportion of the abdominal breathing is lower than that of the chest breathing, the locus of the Lissajous figure has a larger proportion of the straight line portion corresponding to the trajectory in the case of the chest breathing (the straight line portion rising to the right in FIG. 33). Thus, the proportion of the bent portion (the straight downward portion in FIG. 33) is reduced. On the contrary, if the proportion of the abdominal breathing is higher than that of the chest breathing, the locus of the Lissajous figure is the proportion of the straight line portion corresponding to the locus in the case of the chest breathing (the straight line portion rising to the right in FIG. 33). It becomes smaller, and the proportion of the bent portion (the straight downward portion in FIG. 33) increases. In this way, when the subject's breathing includes abdominal breathing, the trajectory of the Lissajous figure varies in bending shape depending on the ratio of chest breathing and abdominal breathing.

  Theoretically, when the rate of abdominal breathing is 100%, the locus of the Lissajous figure is a straight line inclined in the opposite direction to the locus of chest breathing. However, for example, even when the abdomen is recessed or inflated with the breath stopped and no chest breathing performed, the lungs contract and expand with the diaphragm above and below, Except when the diaphragm does not function at all due to disease or the like, chest breathing is always included when the subject breathes. Therefore, in fact, no matter how high the abdominal breathing rate is, the Lissajous figure trajectory always includes a straight line portion corresponding to the trajectory in the case of chest breathing, resulting in a bent shape. . Further, as shown in FIG. 33, a bending indicating how much a bent portion (approximate straight line LN2) is bent with respect to a straight line portion (approximate straight line LN1) corresponding to the locus in the case of chest breathing. The angle AG decreases when the abdominal breathing is shallow, and increases when the abdominal breathing is deep. Also, in the case of abdominal breathing, the trajectory of the Lissajous figure becomes smaller when breathing is shallow, and the trajectory of the Lissajous figure becomes larger when breathing is deep.

  Thus, the shape of the locus of the Lissajous figure is different between the chest breathing and the abdominal breathing. Further, the size and shape of the locus of the Lissajous figure changes depending on the magnitude (depth) of chest-type breathing and abdominal-type breathing. Therefore, the subject can look at the Lissajous figure to determine whether their current breathing is chest or abdominal breathing, or whether their current breathing is more of the chest or abdominal breathing. Can be grasped. In addition, the magnitude of chest breathing and abdominal breathing can be grasped from the Lissajous figure.

  In addition, when the subject performs exercises for chest breathing, the subject may respire consciously so that the locus of the Lissajous figure becomes an inclined straight line and the size thereof increases. Further, when abdominal breathing exercises are performed, breathing may be performed with an awareness that the locus of the Lissajous figure is bent and the size and bending angle AG are increased. If breathing training can be performed while looking at the Lissajous figure in this way, the training can be advanced while confirming whether or not chest breathing and abdominal breathing are correctly performed and their sizes as needed.

  In addition to chest-type breathing and abdominal-type breathing, there is a breathing method (hereinafter referred to as draw-in breathing) in which exhalation and inspiration are performed while maintaining a state in which the abdomen is recessed. In the case of draw-in respiration, as shown in FIG. 30, both the first bioelectrical impedance Za and the second bioelectrical impedance Zb change in an increasing direction during inspiration, and the first bioelectrical impedance Za and the second bioelectrical impedance Zb during exhalation. Both change in a decreasing direction. This change is the same as for chest breathing. This is because in the case of draw-in breathing, exhalation and inhalation are performed by chest breathing while maintaining a state where the abdomen is recessed. However, in the case of draw-in breathing, since the abdomen is pressed to dent the abdomen, the amplitude reference level of the second bioelectrical impedance Zb in the middle trunk as shown in FIG. Also gets higher. For this reason, when comparing the Lissajous figures in the case of draw-in breathing and chest breathing, as shown in FIG. 45, the trajectories of both are linear, but the other bioelectric impedance Zb is assigned to the other. The locus is shifted in the axial direction (X-axis direction in FIG. 45).

  Therefore, the subject can grasp whether or not his / her respiration is a draw-in respiration by looking at the Lissajous figure. In the case of draw-in breathing, the trajectory of the Lissajous figure becomes smaller if the breathing is shallow, and the trajectory of the Lissajous figure becomes larger if the breathing is deep. Therefore, the magnitude of the draw-in breath can also be grasped from the Lissajous figure. Also, in the case of draw-in breathing, training can be carried out while confirming whether or not the draw-in breathing is correctly performed and the size thereof by performing training while looking at the Lissajous figure.

  If the Lissajous figure can be displayed as described above, the subject can correct his / her current breathing type and size as well as chest, abdominal and draw-in breathing while training breathing. It is possible to grasp whether or not. In addition, it is possible to objectively grasp the type and size of respiration, or whether chest respiration, abdominal respiration, and draw-in respiration are correctly performed based on the measured value of bioelectrical impedance. Therefore, it becomes possible to train respiration efficiently.

Moreover, if the breathing can be efficiently trained, the respiratory muscles can be effectively trained. In particular, the transverse abdominal muscles included in the respiratory muscles are trunk muscles that greatly affect not only breathing but also motor function. In addition, draw-in breathing can strengthen not only the respiratory muscles but also the inner muscles of the trunk, such as the spine standing muscles. Therefore, breathing exercises are effective not only for improving respiratory function, but also for strengthening motor function, improving / preventing back pain, and dieting. Also, for example, breathing exercises such as taking deep breaths (deep abdominal breathing) or making exhalation longer than inspiration can lead to a more relaxed state by increasing the function of parasympathetic nerves. It also has the effect of improving mental and physical health.
Furthermore, according to the present invention, it is only necessary to measure the first bioelectrical impedance Za and the second bioelectrical impedance Zb and to display a Lissajous figure showing a change with time of both, which will be described in the first embodiment described later. As described above, since it is not necessary to perform complicated respiration analysis processing, the control configuration of the breathing exercise apparatus can be simplified.

  Respiratory training includes, for example, rehabilitation performed for the purpose of recovering reduced respiratory function in patients with respiratory diseases, training performed for the purpose of strengthening motor functions by athletes, and respiratory function and physical and mental health for healthy individuals. Training that is performed for the purpose of improving the state, training that is performed by a healthy person for the purpose of improving respiratory function that has decreased due to smoking, lifestyle-related diseases, lack of exercise, aging, and the like.

  In addition, for example, in inductance-type respiratory plethysmography, a measurement band with a coil is wrapped around both the subject's thorax (sword-shaped projection) and abdomen (umbilical portion), and the change in the inductance of the coil results in the surroundings of the chest during breathing. The chest change rate Rrc (%) corresponding to the diameter change and the abdominal change rate Rabd (%) corresponding to the change in the peripheral diameter of the abdomen during breathing are measured. Among such inductance-type respiratory plethysmographs, for example, there is one that displays a Lissajous figure according to the Konno-Mead Diagram with the X axis as the abdominal change rate Rabd and the Y axis as the chest change rate Rrc.

  However, in the case of inductance-type respiratory plethysmography, measurement bands must be worn on the subject's chest and abdomen. In addition, when the subject is conscious of measurement or is nervous during measurement, the chest change rate Rrc and the abdomen change rate Rabd vary greatly. For this reason, a relatively reliable measurement result can be obtained during sleep, but there are many cases in which a highly reliable measurement result cannot be obtained when measurement is performed while the subject is awake.

  On the other hand, in the case of measurement by bioelectrical impedance, for example, if the limb induction eight electrode method is used, current electrodes and voltage electrodes may be disposed on both palms and soles, and current electrodes and voltages are applied to the trunk of the subject. Since there is no need to affix electrodes, there are few restrictions. In the case of bioelectric impedance, for example, in the case of the first bioelectric impedance Za at the upper part of the trunk, about 80% of the measured values are due to the inflow / outflow of air to the lungs, and the remaining 20% are due to respiratory muscles, etc. It is. Therefore, as compared with the case of inductance-type respiratory plethysmography, it is possible to reduce the influence of the subject being aware of the measurement or being nervous during the measurement, and obtain a more reliable measurement result. In addition to this, it is possible to measure with high sensitivity information directly related to breathing, such as air in and out of the lungs and vertical movement of the diaphragm.

For this reason, the Lissajous figure based on bioelectrical impedance reflects information directly related to breathing, such as air in / out of the lungs and the vertical movement of the diaphragm, with higher sensitivity than the Lissajous figure based on the inductance-type respiratory plethysmography. It will be. Further, as described above, the Lissajous figure obtained by inductance-type respiratory plethysmography has, for example, the X axis as the abdomen change rate Rabd and the Y axis as the chest change rate Rrc. In this case, the trajectory for one breath is a straight line that rises to the right in both cases of chest breathing and abdominal breathing. In addition, when the angle between the linear trajectory rising to the right and the X-axis is taken as the inclination angle of the trajectory, the inclination angle of the trajectory increases as the ratio of chest respiration increases and approaches 90 degrees. The higher the ratio is, the smaller the inclination angle of the trajectory approaches 0 degrees. In other words, in the case of a Lissajous figure based on inductance-type respiratory plethysmography, the shape of the trajectory is not different as in the present invention because the inclination of the trajectory changes only in the case of chest respiration and abdominal respiration. It is difficult to grasp the type of breathing from the figure.
The same applies to the case where a Lissajous figure conforming to the Konno-Mead Diagram is displayed using the chest circumference Rib and abdominal circumference Ab measured by respi tracing.

  As an aspect of the respiratory training device (1) according to the present invention, the bioelectrical impedance measuring unit (170, 200) includes a first bioelectrical impedance Za in the upper trunk portion that includes the upper part of the subject's lung and does not include the abdomen, and the subject. The second bioelectrical impedance Zb of the middle trunk including the middle lower part and the abdomen of the lungs may be measured.

  For example, in order to measure the first bioelectrical impedance Za of the upper trunk that includes the lung and does not include the abdomen, a current electrode or a voltage electrode may be attached to the right lung and the left lung of the trunk surface of the subject. It is done. Further, in order to measure the second bioelectrical impedance Zb in the middle of the trunk including the abdomen, it is conceivable to paste the current electrode and the voltage electrode on the part of the subject's groove and the navel. However, such a method requires time and effort to attach the current electrode and the voltage electrode to the subject. If the limb-guided eight-electrode method is used, the first bioelectric impedance Za of the upper trunk including the upper part of the subject's lung and not including the abdomen is arranged by arranging current electrodes and voltage electrodes on both palms and soles. Then, the second bioelectric impedance Zb of the middle trunk including the middle lower part and the abdomen of the subject's lung can be measured. For this reason, it is not necessary to affix a current electrode or a voltage electrode on a test subject's trunk. In the measurement between both palms, the bioelectrical impedance of the left and right upper limbs is measured in addition to the lungs, but if the left and right upper limbs are not moved, the bioelectrical impedance of that part does not change. It doesn't matter so much in grasping the size and the size.

  As aspects of the respiratory training device (1) according to the present invention, the first bioelectrical impedance (ZaR) on the right side of the upper trunk including the subject's right lung and not including the abdomen, and the body including the subject's left lung and not including the abdomen A bioelectrical impedance measuring unit (170, 200) that measures the second bioelectrical impedance (ZaL) on the left side of the trunk and the third bioelectrical impedance (Zb) in the middle of the trunk including the abdomen of the subject are orthogonal to each other. Of the two axes, one axis is the first bioelectrical impedance and the other axis is the third bioelectrical impedance, and the first bioelectrical impedance measurement value and the third bioelectrical impedance measurement value change over time The display data of one Lissajous figure (FIG. 40: for right lung) is generated, one axis is the second bioelectric impedance, and the other axis is the third bioelectric impedance. A display data generation unit (170) that generates display data of a second Lissajous figure (FIG. 40: for the left lung) indicating a change with time of the measured value of the second bioelectrical impedance and the measured value of the third bioelectrical impedance. ).

  Even if it is this structure, there exists an effect similar to the respiratory training apparatus mentioned above. In addition, since it is possible to display the first Lissajous figure for the right lung and the second Lissajous figure for the left lung, it is possible to grasp the type of breathing and the size thereof for each left and right lung. Also, by comparing the two Lissajous figures, it is possible to easily grasp the difference in ventilation capacity between the left and right lungs. Furthermore, by displaying two Lissajous figures for the right lung and the left lung, it becomes possible to perform breathing training for each of the left and right lungs. In the case of a healthy person, there is almost no difference in ventilation capacity between the left and right lungs. For example, a person with a disease in one lung has a large difference in ventilation capacity between the left and right lungs. Also, those who have experienced lung disease in the past may have differences in ventilation capacity between the left and right lungs. For example, if you want to increase the ventilation capacity of the left lung, such as when the ventilation capacity of the left lung is lower than the right lung, turn the left arm behind the right shoulder and push the left elbow back with the right hand to the left lung. By giving a load and breathing while maintaining this state, the ventilation ability of the left lung can be intensively trained.

As an aspect of the respiratory training device (1) according to the present invention, the bioelectrical impedance measuring unit (170, 200) includes the upper part of the right lung of the subject and the first bioelectrical impedance (ZaR) on the right side of the upper trunk without including the abdomen. ), A second bioelectric impedance (ZaL) on the left side of the upper trunk that includes the upper part of the left lung of the subject and does not include the abdomen, and a third bioelectrical impedance (ZaL) of the middle part of the trunk including the middle lower part and the abdomen of the subject's lung. Zb) may be measured.
In this case as well, the current and voltage electrodes are arranged on both palms and soles using the limb-guided eight-electrode method, so that the first bioelectrical impedance ZaR on the upper right side of the trunk and the left side of the upper left side of the trunk Since the second bioelectrical impedance ZaL and the third bioelectrical impedance Zb in the middle of the trunk can be measured, there is no need to attach a current electrode or a voltage electrode to the trunk of the subject.

As an aspect of the breathing exercise apparatus (1) according to the present invention, the display data generation unit (170) includes the display data of the first Lissajous figure and the display data of the first Lissajous figure so that the first Lissajous figure and the second Lissajous figure are displayed in an overlapping manner. Display data of the second Lissajous figure may be generated.
In this case, since the first Lissajous figure for the right lung and the second Lissajous figure for the left lung can be displayed in an overlapping manner, the difference in ventilation capacity between the left and right lungs can be easily grasped.

As an aspect of the breathing exercise apparatus (1) according to the present invention, the display data generation unit (170) is configured to display the first Lissajous figure so that the display form of the first Lissajous figure and the second Lissajous figure is different. Display data and display data of the second Lissajous figure may be generated.
In this case, for example, even if the first Lissajous figure for the right lung and the second Lissajous figure for the left lung are displayed in an overlapping manner, the right lung and the left lung due to the difference in the display mode of the trajectory (for example, color and line type). Two Lissajous figures for the lung can be easily distinguished.

As an aspect of the breathing exercise apparatus (1) according to the present invention, the respiratory training device (1) further includes a trajectory analysis unit (170) for detecting a difference between the trajectory of the first Lissajous figure and the trajectory of the second Lissajous figure, and a display data generation unit (170). The display data of the first Lissajous figure and the display data of the second Lissajous figure may be generated so that the difference is displayed with emphasis.
Even in this way, it is possible to easily grasp the difference in ventilation capacity between the left and right lungs.

As an aspect of the respiratory training device (1) according to the present invention, the first centering value (Za0) indicating the amplitude reference level of the measurement value of the first bioelectrical impedance and the amplitude reference level of the measurement value of the second bioelectrical impedance are set. And a centering value generation unit (170) that generates a second centering value (Zb0) to be displayed. The display data generation unit (170) has a Lissajous position on the Lissajous figure determined by the first centering value and the second centering value. The display data of the Lissajous figure may be generated so as to be the center of the display area (160A) for displaying the figure.
In this case, since the Lissajous figure can be displayed at the center of the display area, the Lissajous figure can be easily seen.

  As an aspect of the respiratory training device (1) according to the present invention, the first centering value (Za0) indicating the amplitude reference level of the measurement value of the first bioelectrical impedance and the amplitude reference level of the measurement value of the second bioelectrical impedance are set. A centering value generation unit (170) that generates a second centering value (Zb0) to be displayed, and the display data generation unit (170) performs a first centering value as a process performed when generating display data of the Lissajous figure. A first centering process for centering the Lissajous figure in one axial direction based on the second centering process and a second centering process for centering the Lissajous figure in the other axial direction based on the second centering value. The frequency of performing the process may be less than the frequency of performing the first centering process.

  When comparing the Lissajous figures in the case of draw-in respiration and chest respiration, as shown in FIG. 45, both trajectories are linearly inclined, but the other axial direction to which the second bioelectric impedance Zb is assigned. The position of the locus is shifted in the X-axis direction in FIG. Here, if centering is frequently performed, the Lissajous figure is always displayed in the center of the display area, so that it becomes impossible to distinguish the draw-in breath and the chest-type breath from the Lissajous figure. According to the above-described aspect, for example, the first centering process is performed every breath, while the second centering process is performed only once for the first time and is not performed later. Since the frequency of performing the centering process is reduced, the position of the locus of the Lissajous figure is shifted in the other axial direction in the case of the draw-in breathing and the case of the chest breathing. This makes it possible to distinguish between draw-in breathing and chest breathing from the Lissajous figure. Moreover, the power consumption of the breathing exercise apparatus can be reduced by the amount that the frequency of performing the second centering process is reduced. Moreover, although the frequency is low, the second centering process is also performed, so that the Lissajous figure can be displayed at the center of the display area for easy viewing.

As an aspect of the respiratory training device (1) according to the present invention, a first amplitude value indicating the amplitude of the measured value of the first bioelectrical impedance and a second amplitude value indicating the amplitude of the measured value of the second bioelectrical impedance are provided. An amplitude value specifying unit (170) for specifying is further provided, and the display data generating unit (170) adjusts the biaxial range using the first amplitude value and the second amplitude value, and generates display data of the Lissajous figure. May be.
In this case, it is possible to display the Lissajous figure with a size just right for the display area for displaying the Lissajous figure by adjusting the range of the two axes. A Lissajous figure can also be displayed at the center of the display area. This makes it easy to see the Lissajous figure.

As an aspect of the respiratory training device (1) according to the present invention, a first amplitude value indicating the amplitude of the measured value of the first bioelectrical impedance and a second amplitude value indicating the amplitude of the measured value of the second bioelectrical impedance are provided. An amplitude value specifying unit (170) for specifying is further provided, and the display data generating unit (170) adjusts the range of one axis using the first amplitude value as processing to be performed when generating the display data of the Lissajous figure. Frequency of performing the first range adjustment processing and the second range adjustment processing of adjusting the range of the other axis using the second amplitude value, and the frequency of performing the second range adjustment processing is the frequency of performing the first range adjustment processing You may make it become less.
Also in this case, it becomes possible to distinguish between draw-in breathing and chest breathing from the Lissajous figure. Moreover, the power consumption of the breathing exercise apparatus can be reduced by the amount that the frequency of performing the second range adjustment process is reduced. In addition, although the frequency is low, the second range adjustment process is also performed, so that the Lissajous figure can be displayed in a size that is just right with respect to the display area for displaying the Lissajous figure for easy viewing.

As a mode of the breathing training apparatus (1) according to the present invention, the display data generation unit (170) is configured to display the Lissajous figure so that the display mode of the locus of the Lissajous figure is different between the latest one breath and the other past breaths. Display data may be generated.
For example, as shown in FIG. 34 and FIG. 35, in the case of a Lissajous figure that continuously shows the state of breathing a plurality of times, if the trajectory display mode is the same, it is difficult to grasp the latest trajectory for one breath. If it is the above-mentioned aspect, the latest locus | trajectory for one breath can be easily grasped | ascertained from the difference in a display aspect (for example, a color, a line type, etc.).

As a mode of the breathing exercise apparatus (1) according to the present invention, the display data generation unit (170) generates the display data of the Lissajous figure so that the display mode of the locus of the Lissajous figure changes according to the elapsed time. Good.
For example, if the color of the trajectory becomes lighter as the elapsed time increases, the new trajectory becomes darker because the color of the new trajectory becomes darker, so that a new trajectory such as the latest trajectory for one breath can be easily grasped.

As an aspect of the breathing exercise apparatus (1) according to the present invention, the display data generation unit (170) generates display data of a Lissajous figure and performs breathing guidance according to the target breathing type and the breathing magnitude. Display data for the Lissajous figure may be generated.
In this case, in addition to the Lissajous figure indicating the breathing state of the subject, it is possible to display a Lissajous figure for breathing guidance indicating the target breathing state. Therefore, the subject can perform breathing training while comparing both Lissajous figures. In this case, the subject can acquire the target breath by consciously breathing so that the locus of the Lissajous figure indicating the state of his / her breathing matches the locus of the Lissajous figure for breathing guidance. . Thus, by using the Lissajous figure for breathing guidance, the subject's breathing can be effectively taught.

  Note that the display data generation unit (170) may generate display data of both so that a Lissajous figure indicating the breathing state of the subject and a Lissajous figure for breathing guidance are displayed in an overlapping manner. In this way, the difference from the target breath can be easily grasped. Further, the display data generation unit (170) may generate both display data so that the display form of the Lissajous figure showing the breathing state of the subject and the Lissajous figure for breathing guidance are different in display mode. Good. In this way, for example, even if the Lissajous figure indicating the breathing state of the subject and the Lissajous figure for breathing guidance are displayed in an overlapping manner, both of them can be easily displayed due to the difference in the display mode of the trajectory (for example, color and line type). Can be distinguished.

As an aspect of the breathing exercise apparatus (1) according to the present invention, an inclination angle calculation unit (170) that calculates an inclination angle of a locus of a Lissajous figure, and an inclination angle calculated by the inclination angle calculation unit is a predetermined reference inclination angle. And a ventilation capacity determination unit (170) that determines whether the lung ventilation capacity is good or bad.
In this case, the quality of the lung ventilation ability can be easily determined from the locus of the Lissajous figure. Note that the inclination angle of the locus of the Lissajous figure varies depending on the posture at the time of measurement, such as standing, sitting, and the supine position, so the reference inclination angle also differs depending on the posture at the time of measurement.

As an aspect of the breathing training apparatus (1) according to the present invention, based on the measured value of the first bioelectrical impedance and the measured value of the second bioelectrical impedance, the breathing depth in one breath is extracted for each breath of the subject. And a graph generation unit (170) that generates display data of a graph indicating a temporal change in the breathing depth extracted by the breathing depth extraction unit, and the time axis of the graph is nonlinear However, when the predetermined time width is one section, the time axis range is different in the latest one section and the oldest section, and the latest one section has higher time resolution than the oldest section. It may be made to become.
For example, the exercise time for breathing is often a relatively long time of 10 minutes to several tens of minutes. For this reason, when trying to display the entire graph from the start of measurement to the present, the graph must be compressed in the time axis direction. At this time, if the entire graph is uniformly compressed, the time resolution is reduced uniformly over the entire measurement section, and it becomes difficult to grasp details about the magnitude of the most recent breath. According to the above-described aspect, the time axis of the graph to be displayed can be made non-linear, and the time resolution of the latest one section can be made higher than the oldest one section, so that the details of the most recent breathing can be easily grasped. can do.

As an aspect of the breathing training apparatus (1) according to the present invention, a training menu for training breathing and a clear condition for clearing the class are stored for each class determined according to the breathing ability. See the storage unit (120), the breathing ability detection unit (170) that detects the breathing ability of the subject based on the measurement value of the first bioelectrical impedance and the measurement value of the second bioelectrical impedance, and the storage unit Then, the class corresponding to the breathing ability detected by the breathing ability detection unit is specified, and the process for training the subject's breathing is performed based on the training menu corresponding to the specified class, and the clear corresponding to the specified class is performed. When the condition is satisfied, a training management unit (170) that shifts the class of the subject to the next class higher than the class may be further provided.
In this case, the subject can perform breathing training based on a training menu corresponding to his / her breathing ability. In addition, the training menu is prepared for each class, and by having the game characteristics of proceeding to the next class while clearing each class, it is possible to perform breathing training while having fun, so subjects for breathing training You can also increase your motivation.

As an aspect of the respiratory training device (1) according to the present invention, whether the subject's breathing is abdominal breathing or chest breathing based on the measured value of the first bioelectrical impedance and the measured value of the second bioelectrical impedance. And an analysis unit (170) that obtains discrimination information that can discriminate whether or not. In this case, there is an advantage that the type of breathing of the subject (abdominal breathing or chest breathing) can be accurately determined.
In addition, instead of the analysis unit, a determination unit that determines whether the subject's respiration is abdominal respiration or chest respiration based on the first bioelectrical impedance measurement value and the second bioelectrical impedance measurement value (170) may be provided.

  As an aspect of the respiratory training device (1) according to the present invention, the first centering value (Za0) indicating the amplitude reference level of the first bioelectrical impedance measurement value and the amplitude reference level of the second bioelectrical impedance measurement value A first centering value generator (170) for generating a second centering value (Zb0) indicating the first relative value (ΔZa), which is a relative value of the measured value of the first bioelectrical impedance to the first centering value A relative value calculation unit (170); and a second relative value calculation unit (170) for obtaining a second relative value (ΔZb) that is a relative value of the measurement value of the second bioelectrical impedance to the second centering value. The analysis unit may obtain the discrimination information based on the first relative value and the second relative value.

In this aspect, the analysis unit obtains discrimination information that can discriminate whether the subject's breathing is abdominal breathing or chest breathing based on the first relative value and the second relative value. Type can be accurately identified in real time. More specifically, the discrimination information indicates the ratio (ΔRib / ΔAb) between the change in the circumference of the subject's chest and the change in the circumference of the abdomen. In the present invention, there is a correlation between the ratio (ΔRib / ΔAb) between the change in the circumference of the subject's chest and the change in the circumference of the abdomen and the first relative value and the second relative value described above. And the analysis unit executes a calculation process according to the regression information representing the relationship between the determination information and the first relative value and the second relative value, thereby determining the determination corresponding to the first relative value and the second relative value. Ask for information. Then, the type of breathing of the subject can be estimated from the obtained discrimination information. The regression equation is expressed in the following form.
ΔRib / ΔAb = (a × ΔZb−ΔZa) / ΔZa + b
ΔRib: change in the circumference of the subject's chest, ΔAb: change in the circumference of the subject's abdomen, ΔRib / ΔAb: discrimination information, ΔZa: first relative value, ΔZb: second relative value, a, b: constant.

  In this aspect, when the value of ΔRib / ΔAb exceeds a predetermined threshold, it is estimated that the subject's breathing is chest-type breathing, whereas when the value is equal to or smaller than the predetermined threshold, it is estimated to be abdominal breathing. For this reason, there is an advantage that it is possible to accurately determine whether the subject's breathing is chest breathing or abdominal breathing from the value of ΔRib / ΔAb obtained by the analysis unit.

As an aspect of the breathing training apparatus (1) according to the present invention, the analysis unit (170) determines whether the subject's breathing is based on the measured value of the first bioelectrical impedance and the measured value of the second bioelectrical impedance. Distinguishing information that can discriminate whether the breathing method is breathing or breathing while maintaining a state where the abdomen is dented, may be obtained. In this mode, whether the subject's breathing is abdominal breathing or chest breathing, and whether it is draw-in breathing (a breathing method that exhales and inhales while keeping the abdomen recessed) Can be determined.
Also in this case, whether the subject's breathing is abdominal breathing or chest breathing based on the measured value of the first bioelectrical impedance and the measured value of the second bioelectrical impedance instead of the analysis unit. Alternatively, a determination unit (170) may be provided that determines whether the breathing method performs exhalation and inhalation while maintaining a state in which the abdomen is recessed.

  In this aspect, when the value of ΔRib / ΔAb is equal to or less than a predetermined threshold, the subject's breathing is abdominal breathing, the value of ΔRib / ΔAb exceeds the predetermined threshold, and the second generated by the centering value generation unit If the centering value is larger than the second centering value during the subject's chest breathing by a predetermined value or more, the subject's breathing is a draw-in breath, the value of ΔRib / ΔAb exceeds a predetermined threshold, and the centering value generator generates If the second centering value is less than the sum of the second centering value and the predetermined value during the subject's chest breathing, the subject's breathing is estimated to be chest breathing. For this reason, from the value of ΔRib / ΔAb obtained by the analysis unit, it can be accurately determined whether the subject's breathing is chest breathing, abdominal breathing, or draw-in breathing.

  As an aspect of the respiratory training device (1) according to the present invention, the respiratory training device (1) further includes a zero cross timing extraction unit (170) that extracts a zero cross timing at which the measured value of the first bioelectrical impedance is equal to the first centering value. The impedance measuring unit measures the first bioelectrical impedance and the second bioelectrical impedance every time the sampling timing is reached at a predetermined cycle, and the centering value generating unit is configured to measure the first bioelectrical power at each of the predetermined number of sampling timings. While generating the first centering value based on the measured impedance value, the second centering value may be generated based on the measured value of the second bioelectrical impedance at the zero cross timing extracted by the zero cross timing extraction unit.

Here, when the subject performs breathing consisting of inspiration and expiration, the first bioelectrical impedance of the upper trunk and the second bioelectrical impedance of the middle trunk change according to the breathing. The lungs expand and contract in the same way during abdominal breathing, chest breathing, and draw-in breathing, and the amount of air contained in lung tissue increases during inspiration, so the bioelectrical impedance of the lungs changes in the increasing direction, and lungs during exhalation As the amount of air contained in the tissue decreases, the bioelectrical impedance of the lung changes in a decreasing direction. That is, regardless of whether the subject's breathing is abdominal breathing, chest breathing, or draw-in breathing, the first bioelectrical impedance that includes the lungs and does not include the abdomen changes in an increasing direction during inspiration, while in exhalation. It changes in the decreasing direction.
In abdominal breathing, the visceral tissue rises in the direction of pushing up the diaphragm by the action of the abdominal skeletal muscle during exhalation, so the bioelectrical impedance of the abdomen changes in the increasing direction. That is, in the expiration of abdominal breathing, the increase in the bioelectrical impedance of the abdomen cancels the decrease in the bioelectrical impedance of the lungs. On the other hand, this is not the case with chest breathing and draw-in breathing. Therefore, when the subject's breathing is abdominal breathing, a change in the second bioelectric impedance including the abdomen is different from the above-described change in the first bioelectric impedance.

  Regardless of whether the subject's breathing is chest breathing, abdominal breathing or draw-in breathing, the waveform indicating the change in the first bioelectrical impedance is substantially sinusoidal. Even if the waveform indicating the change in the first bioelectrical impedance is disturbed due to the influence of body movement or the like, the first centering value corresponding to that is extracted (information resulting from respiration from the waveform indicating the change in the first bioelectrical impedance). The centering value generation unit generates the first centering value based on the measured value of the first bioelectrical impedance at each of the predetermined number of sampling timings. More specifically, for each sampling timing, the centering value generator generates a plurality of sampling timings within a centering period starting from a time point that is a predetermined time length before the sampling timing and ending with the sampling timing. A moving average process using the measured value of the first bioelectric impedance in each is performed, and based on the result, the first centering value at the sampling timing is obtained. Thereby, even if the waveform indicating the change in the first bioelectrical impedance is disturbed due to the influence of body movement or the like, the first centering value corresponding to the waveform can be generated with high accuracy. The time length of the centering period is variably set according to the breathing rate of the subject at the sampling timing. Here, the “moving average process” includes not only an unweighted average process but also an average process with a weight. For example, the averaging process may be performed after weighting according to the difference in frequency at each sampling timing.

  On the other hand, the change in the second bioelectric impedance due to the abdominal breathing has a different form (non-sinusoidal) from the change in the first bioelectrical impedance. Even if the moving average processing using the measurement value of the second bioelectric impedance at each sampling timing is performed, information derived from respiration is obtained from the amplitude reference level, that is, the waveform indicating the change in the second bioelectric impedance. It is difficult to accurately obtain an amplitude reference level for extraction.

  Therefore, in the above aspect, the centering value generation unit generates the second centering value at the sampling timing based on the measurement value of the second bioelectrical impedance at the zero cross timing extracted by the zero cross timing extraction unit. Specifically, for each sampling timing, the centering value generation unit determines whether or not the sampling timing is a zero-cross timing. If the sampling timing is the zero-cross timing, the second bioelectric at the sampling timing is determined. Based on the measured impedance value, the second centering value at the sampling timing is generated. On the other hand, if the sampling timing is not zero cross timing, the second centering value generated at the sampling timing immediately before the sampling timing is The second centering value at the timing is adopted. Thereby, the amplitude reference level of the measured value of the second bioelectrical impedance can be obtained with high accuracy.

  As an aspect of the breathing training apparatus (1) according to the present invention, a breathing depth extraction unit (170) that extracts a breathing depth in one breath for each breath of the subject, and an analysis unit for each breath of the subject. An abdominal level calculation unit (170) for obtaining an abdominal level indicating the proportion of the abdominal breathing in the one breath based on the determined discrimination information, and the breathing depth and abdominal formula in the one breath for each breath of the subject You may further provide the alerting | reporting part (170,160) which alert | reports each magnitude | size and margin of abdominal respiration and chest respiration in the said 1 respiration based on a level. More specifically, it further includes a normalization unit (170) that normalizes the respiration depth extracted by the respiration depth extraction unit, and the notification unit indicates the respiration depth and the amount of air that enters and exits the lung in one breath. The tidal volume corresponding to the breathing depth normalized by the normalization unit is obtained by executing the arithmetic processing according to the second regression equation indicating the relationship with the tidal volume, and the obtained tidal volume Based on the amount and the abdominal level, the magnitude and margin of each of the subject's abdominal respiration and chest respiration are determined and notified.

  In this aspect, the notification unit notifies the subject of the magnitude and margin of each of the abdominal breathing and the chest breathing in one breath for each breath of the subject. Recognize the strengths and weaknesses of utilizing muscles and abdominal respiratory muscles. This makes it possible to ensure motivation for respiratory muscle training such as abdominal breathing for activating one's weakness while making the subject aware of his strength. In addition, according to this aspect, it is possible to grasp the margin of the subject's breathing ability even if the subject does not perform the maximum breathing, such as a spiro, which is preferable from the viewpoint of ensuring the safety of the subject. is there.

  In order to solve the above-described problem, the respiratory training device (300) according to the present invention is the first upper trunk that includes the lungs of the subject and does not include the abdomen, as measured by the bioelectrical impedance measuring device (200 ′). The input unit (320) for inputting the bioelectrical impedance (Za) and the second bioelectrical impedance (Zb) of the trunk including the abdomen of the subject, and one of the two axes orthogonal to each other is the first axis A display data generation unit that generates display data of a Lissajous figure indicating changes over time in the measured value of the first bioelectrical impedance and the measured value of the second bioelectrical impedance, with the bioelectrical impedance being the second bioelectrical impedance on the other axis (360).

  As an aspect of the respiratory training device (300) according to the present invention, the first bioelectric impedance (ZaR) on the right side of the upper trunk, which includes the right lung of the subject and does not include the abdomen, measured by the bioelectrical impedance measuring device (200 ′). And a second bioelectrical impedance (ZaL) on the upper left side of the trunk that includes the left lung of the subject and does not include the abdomen, and a third bioelectrical impedance (Zb) in the middle of the trunk that includes the abdomen of the subject (320) and one of the two orthogonal axes is the first bioelectrical impedance and the other axis is the third bioelectrical impedance, and the measured value of the first bioelectrical impedance and the measurement of the third bioelectrical impedance The display data of the first Lissajous figure showing the change over time of the value is generated, one axis is the second bioelectrical impedance, and the other axis is the third living body. A display data generation unit (360) that generates display data of a second Lissajous figure that represents electrical impedance and represents a time-dependent change in the measured value of the second bioelectrical impedance and the measured value of the third bioelectrical impedance. Good.

  Also in the breathing training apparatus having the above configuration, the Lissajous figure can be utilized as biofeedback information for training breathing, and therefore it is possible to train breathing efficiently. Note that the breathing training apparatus may be, for example, a game machine, a personal computer, or a portable electronic device (for example, a mobile phone).

  In order to solve the above-described problem, the respiratory training system (5) according to the present invention includes the first bioelectric impedance (Za) of the upper trunk including the lungs of the subject and not including the abdomen, and the abdomen of the subject. The bioelectrical impedance measuring unit (200 ′, 360) that measures the second bioelectrical impedance (Zb) in the middle of the trunk, and one of the two axes orthogonal to each other is the first bioelectrical impedance and the other axis Is a second bioelectrical impedance, and a Lissajous graphic generation unit (300, 360) for generating a Lissajous graphic indicating a change over time of the measured value of the first bioelectrical impedance and the measured value of the second bioelectrical impedance, and Lissajous graphic generation And a display unit (400) for displaying the Lissajous figure generated by the unit.

  As aspects of the breathing training system (5) according to the present invention, the first bioelectric impedance (ZaR) on the upper right side of the trunk including the right lung of the subject and not including the abdomen, and the body including the left lung of the subject and not including the abdomen A bioelectrical impedance measuring unit (200 ′, 360) that measures the second bioelectrical impedance (ZaL) on the left side of the trunk and the third bioelectrical impedance (Zb) in the middle of the trunk including the abdomen of the subject, and orthogonal to each other Of these two axes, one axis is the first bioelectrical impedance and the other axis is the third bioelectrical impedance, and the measured value of the first bioelectrical impedance and the measured value of the third bioelectrical impedance are shown over time. A first Lissajous figure is generated, and one axis is a second bioelectrical impedance and the other axis is a third bioelectrical impedance. A Lissajous figure generating unit (300, 360) for generating a second Lissajous figure indicating a change over time in the measured value of the air impedance and the measured value of the third bioelectrical impedance; the first Lissajous figure generated by the Lissajous figure generating unit; And a display unit (400) for displaying the second Lissajous figure.

  Also in the breathing training system having the above configuration, the Lissajous figure can be utilized as biofeedback information for training breathing, so that breathing can be efficiently trained. Note that the breathing exercise system may be configured using, for example, a game machine, a personal computer, a portable electronic device, or the like.

It is a block diagram shown about the electrical constitution of the biometric device of the embodiment concerning the present invention. It is a perspective view which shows the example of an external appearance of a biometric apparatus. It is explanatory drawing which shows electrode arrangement | positioning of a biometric apparatus. It is explanatory drawing for demonstrating selection of a current electrode and selection of a voltage electrode. It is a flowchart which shows the operation | movement content of a biometric apparatus. It is a schematic diagram which shows the outline of the structure | tissue which comprises a trunk. It is a circuit diagram which shows the equivalent circuit of the bioelectrical impedance of a trunk. It is explanatory drawing explaining the relationship between respiration and the change of bioelectrical impedance. It is a figure which shows the change of the bioelectrical impedance in abdominal respiration. It is a figure which shows the change of the bioelectrical impedance in chest type respiration. It is a figure which shows the circumference change of the chest and abdomen accompanying abdominal respiration. It is a figure which shows the circumference diameter change of the chest and abdomen accompanying chest type respiration. It is a correlation diagram showing the relationship between the ratio between the change in the circumference of the chest and the change in the circumference of the abdomen, and the first relative value and the second relative value. It is a flowchart which shows an example of the processing content of a respiration analysis process. It is a flowchart which shows the processing content of a 1st centering process. It is a flowchart which shows the processing content of a respiration timing extraction process. It is a flowchart which shows the processing content of a respiration timing extraction process. It is a flowchart which shows the processing content of a breathing speed discrimination | determination flag setting process. It is a flowchart which shows the processing content of a 1st centering value extraction process. It is a schematic diagram for demonstrating notionally the production | generation method of a 2nd centering value. It is a flowchart which shows the processing content of a 2nd relative value calculation process. It is a figure which shows the time-dependent change of the 1st relative value and 2nd relative value in abdominal respiration. It is a flowchart which shows the processing content of (DELTA) Rib / (DELTA) Ab estimation calculation processing. It is a flowchart which shows the processing content of (DELTA) Rib / (DELTA) Ab estimation calculation processing. It is a figure which shows the calculation result of (DELTA) Rib / (DELTA) Ab estimation calculation processing. It is a figure which shows the display mode in a display part. It is a flowchart which shows the processing content of the respiration depth extraction process. It is a flowchart which shows the processing content of a respiration level display process. It is a correlation diagram which shows the relationship between respiration depth and a tidal volume. It is a graph which shows the time change of the bioelectrical impedance of a trunk upper part and a trunk trunk. It is a flowchart which shows the processing content of a respiration classification discrimination | determination process. It is a figure which shows the Lissajous figure for one breath obtained at the time of chest type breathing. It is a figure which shows the Lissajous figure for 1 breath obtained at the time of abdominal breathing. It is a figure which shows the Lissajous figure for several times of breaths obtained at the time of chest type breathing. It is a figure which shows the Lissajous figure for several times of breaths obtained at the time of abdominal breathing. It is a flowchart which shows the processing content of a Lissajous figure display process. It is a figure for demonstrating the change of the Lissajous figure from chest type breathing to abdominal type breathing. It is a figure which shows a Lissajous figure at the time of switching X axis and Y axis. It is a figure for demonstrating the change from the chest type | mold breathing to abdominal type | mold breathing in the Lissajous figure at the time of switching an X-axis and a Y-axis. It is a figure which shows the case where two Lissajous figures (for 1 breath) for right lung and left lung are displayed superimposed. It is a figure which shows the case where the difference of two Lissajous figures for right lung and left lung is highlighted. It is a figure which shows the case where the average value of two Lissajous figures for right lung and left lung is plotted. It is a schematic diagram (the 1) for demonstrating the method of centering the display position of a Lissajous figure. It is a schematic diagram (2) for demonstrating the method of centering the display position of a Lissajous figure. It is a figure which shows the Lissajous figure in the case of draw-in respiration and the case of chest respiration. It is a figure which shows a Lissajous figure at the time of changing the color of the color of a locus | trajectory with the latest one breath and other past breaths. It is FIG. (1) for demonstrating the assist display by a Lissajous figure. It is FIG. (2) for demonstrating the assist display by a Lissajous figure. It is FIG. (1) for demonstrating the method to determine the quality of the ventilation capability of a lung. It is FIG. (2) for demonstrating the method to determine the quality of the ventilation capability of a lung. It is FIG. (3) for demonstrating the method to determine the quality of the ventilation capability of a lung. It is a graph which shows the time change of a respiration level. It is a figure for demonstrating the display mode of assist information. It is a figure which shows an example of the display mode of assist information. It is a figure which shows an example of the display mode which alert | reports the magnitude | size of respiration. It is a figure which shows the structure of the biometric system using a home game machine. It is a block diagram which shows the structure of a game machine. It is a figure which shows the data structure of a training menu management table. It is a flowchart which shows the processing content of a breathing exercise management process.

<1. First Embodiment>
<1-1: Configuration of Biometric Apparatus>
FIG. 1 is a block diagram showing a configuration of a biometric apparatus 1 according to an embodiment of the present invention. This living body measuring apparatus 1 measures the state of a living body, but a part of its function serves as a breath determining apparatus that determines the type of breathing, the degree of chest breathing, and the degree of abdominal breathing. Bear.
The biometric apparatus 1 includes a management unit 100 that measures body weight and manages the operation of the entire apparatus, and a bioelectrical impedance measurement unit 200 that measures bioelectrical impedance of each part of the subject. The management unit 100 includes a weight scale 110, a first storage unit 120, a second storage unit 130, a sound processing unit 140, a speaker 145, an input unit 150, and a display unit 160. These components are connected to a CPU (Central Processing Unit) 170 via a bus. The CPU 170 functions as a control center that controls the entire apparatus. The CPU 170 operates by receiving a clock signal from a clock signal generation circuit (not shown). Further, when a power switch (not shown) is turned on to each component, power is supplied from the power supply circuit.

  The weight scale 110 measures the weight of the subject, and outputs the measured weight data to the CPU 170 via the bus. The first storage unit 120 is a non-volatile memory, and is composed of, for example, a ROM (Read Only Memory). The first storage unit 120 stores a control program for controlling the entire apparatus. CPU 170 executes a predetermined calculation according to the control program.

  The second storage unit 130 is a volatile memory, and includes, for example, a DRAM (Dynamic Random Access Memory) or the like. The second storage unit 130 functions as a work area of the CPU 170, and stores data when the CPU 170 executes a predetermined calculation. In addition, the audio processing unit 140 amplifies an audio signal obtained by DA converting audio data under the control of the CPU 170 and outputs the amplified audio signal to the speaker 145. The speaker 145 converts the amplified audio signal into vibration and emits the sound. Thus, advice information such as guidance on the breathing method can be notified to the subject by sound.

  The input unit 150 includes various switches, and when a subject operates the switches, information such as height, age, and sex is input. The display unit 160 displays a measurement result such as weight and type of breath, a function for notifying advice information such as a rhythm and a pattern of exhalation and inspiration for leading to abdominal breathing, or a message prompting the subject to input various information. It has the function to do. The display unit 160 is configured by, for example, a liquid crystal display device.

Next, the bioelectrical impedance measuring unit 200 measures the bioelectrical impedance of the subject (human body). The bioelectrical impedance measurement unit 200 includes an alternating current output circuit 210, a reference current detection circuit 220, a potential difference detection circuit 230, an A / D converter 240, and electrode switching circuits 251 and 252.
The alternating current output circuit 210 is a means for generating a reference current Iref. The alternating current output circuit 210 generates the reference current Iref so that the effective value of the reference current Iref becomes a predetermined value. The reference current detection circuit 220 detects the magnitude of the reference current Iref flowing through the object to be measured and outputs it as current data Di to the CPU 170 and energizes the subject with the reference current Iref. In this case, the electrode switching circuit 252 selects two of the current electrodes X1 to X4 and supplies current.
Further, the potential difference detection circuit 230 detects a potential difference between two voltage electrodes selected from the voltage electrodes Y1 to Y4 and generates a potential difference signal ΔV. The A / D converter 240 converts the potential difference signal ΔV from an analog signal to a digital signal and outputs it to the CPU 170 as voltage data Dv. The CPU 170 calculates a bioelectric impedance Z (= Dv / Di) based on the voltage data Dv and the current data Di.

The first storage unit 120 can store various data in advance. For example, a correlation equation or a correlation table for calculating body fat fat percentage and muscle mass using the bioelectrical impedance of each part as a variable is stored.
The CPU 170 calculates body weight, bioelectrical impedance (for example, upper limb bioelectrical impedance, lower limb bioelectrical impedance, trunk bioelectrical impedance) of various parts of the subject, and various input / output, measurement, calculation, and the like. Control. Based on bioelectrical impedance, etc., visceral fat / subcutaneous fat, visceral fat mass, subcutaneous fat percentage, subcutaneous fat mass, whole body fat percentage, fat percentage of each part of body (upper limb fat percentage, lower limb fat percentage, body Stem fat percentage etc.) can also be calculated.

  In FIG. 2, the example of an external appearance of the biometric apparatus 1 is shown. The biometric device 1 has an L-shape and includes a columnar casing 30 on the pedestal 20. The pedestal 20 is provided with a current electrode X1 and a voltage electrode Y1 for the left foot, and a current electrode X2 and a voltage electrode Y2 for the right foot. A display unit 160 is provided on the upper portion of the housing unit 30. The display unit 160 is configured with a touch panel and also functions as the input unit 150. Further, left and right electrode portions 30 </ b> L and right hand electrode portions 30 </ b> R are provided on the left and right side surfaces of the housing portion 30.

  FIG. 3 is an enlarged view in which the upper part of the housing part 30 is enlarged. As shown in this figure, the left-hand electrode portion 30L includes a current electrode X3 and a voltage electrode Y3, and the right-hand electrode portion 30R includes a current electrode X4 and a voltage electrode Y4. The subject performs measurement by standing on the pedestal 30 and holding the electrode part 30L and the electrode part 30R with the left and right hands lowered.

  The electrode switching circuits 251 and 252 select eight electrodes to be worn on both hands and both feet under the control of the CPU 170. By appropriately selecting these eight electrodes, it is possible to measure the bioelectrical impedance Z at a predetermined part of the human body. For example, as shown in FIG. 4A, the reference current Iref is supplied between the current electrode X1 for the left foot and the current electrode X3 for the left hand, and the voltage electrode Y1 for the left foot and the voltage electrode Y3 for the left hand If the potential difference is measured between them, the bioelectrical impedance of the whole body can be measured. Note that the bioelectric impedance of the whole body can be measured even if the reference current Iref is passed between the current electrodes X2 and X4 and the potential difference between the voltage electrodes Y2 and Y4 is measured. Furthermore, as shown in FIG. 4 (K), both palms may be short-circuited, both feet may be short-circuited, and the bioelectric impedance from both palms to both feet may be measured as the bioelectric impedance of the whole body.

  Further, as shown in FIG. 4B, the reference current Iref is supplied between the right foot current electrode X2 and the right hand current electrode X4, and the right foot voltage electrode Y2 and the left foot voltage electrode Y1 are connected. If the potential difference is measured between them, the bioelectrical impedance Z of the right lower limb can be measured. Further, as shown in FIG. 4C, the reference current Iref is supplied between the left foot current electrode X1 and the left hand current electrode X3, and the left foot voltage electrode Y1 and the right foot voltage electrode Y2 are connected. If the potential difference is measured between them, the bioelectrical impedance Z of the left lower limb can be measured.

  Further, as shown in FIG. 4D, the reference current Iref is supplied between the right-hand current electrode X4 and the right-foot current electrode X2, and the right-hand voltage electrode Y4 and the left-hand voltage electrode Y3 are connected. By measuring the potential difference between them, the bioelectrical impedance Z of the upper right limb (upper trunk) can be measured. However, the present invention is not limited thereto, and the reference current Iref is supplied between the left-hand current electrode X3 and the right-hand current electrode X4, and the potential difference between the right-hand voltage electrode Y4 and the right-foot voltage electrode Y2 is determined. The bioelectric impedance Z of the upper right limb (upper trunk) can also be measured by measuring.

  Further, as shown in FIG. 4E, the reference current Iref is supplied between the left-hand current electrode X3 and the left-foot current electrode X1, and the right-hand voltage electrode Y4 and the left-hand voltage electrode Y3 are connected. If the potential difference is measured between them, the bioelectrical impedance Z of the left upper limb (upper trunk) can be measured. However, the reference current Iref is supplied between the left-hand current electrode X3 and the right-hand current electrode X4, and the potential difference between the left-hand voltage electrode Y3 and the left-foot voltage electrode Y1 is not limited thereto. The bioelectrical impedance Z of the left upper limb (upper trunk) can also be measured by measuring.

  Further, as shown in FIG. 4F, the reference current Iref is supplied between the right-hand current electrode X4 and the left-hand current electrode X3, and the right-hand voltage electrode Y4 and the left-hand voltage electrode Y3 are connected. If the potential difference is measured between the two, the bioelectric impedance Z between both palms can be measured. Here, when the trunk is divided into the upper trunk and the middle trunk, the bioelectrical impedance between the left upper limb, the upper right limb, and the palm includes the upper trunk. For this reason, it is also possible to handle the bioelectric impedance between the left upper limb, the upper right limb, and the palm as the bioelectric impedance of the upper trunk.

  Further, as shown in FIG. 4G, the reference current Iref is supplied between the left hand current electrode X3 and the left foot current electrode X1, and the right hand voltage electrode Y4 and the right foot voltage electrode Y2 are connected. If the potential difference is measured between the two, the bioelectrical impedance in the middle of the trunk can be measured. Further, as shown in FIG. 4H, the reference current Iref is supplied between the right-hand current electrode X4 and the right-foot current electrode X2, and the left-hand voltage electrode Y3 and the left-foot voltage electrode Y1 are connected. If the potential difference is measured between the two, the bioelectrical impedance in the middle of the trunk can be measured. Further, as shown in FIG. 4 (I), the reference current Iref is supplied between the current electrode X4 for the right hand and the current electrode X1 for the left foot, and the voltage electrode Y3 for the left hand and the voltage electrode Y2 for the right foot By measuring the potential difference between the two, it is possible to measure the bioelectrical impedance that crosses the middle part of the trunk diagonally. As shown in FIG. 4J, the reference current Iref is supplied between the current electrode X2 for the right foot and the current electrode X3 for the left hand, and between the voltage electrode Y4 for the right hand and the voltage electrode Y1 for the left foot. By measuring the potential difference, bioelectrical impedance that crosses the middle of the trunk diagonally can be measured.

  The method for measuring the bioelectrical impedance Zx of the trunk is not limited to the above-described method, and an electrode for supplying a reference current Iref and an electrode for detecting a potential difference are appropriately selected from the electrodes of both hands and feet. Thus, the bioelectrical impedance Z of each part of the human body such as the hand, foot, or whole body is measured, and the bioelectrical impedance Z of the middle trunk is calculated by adding and subtracting the measurement results. Further, the bioelectrical impedance Zx of the trunk can be measured even if the earlobe of the head is used as a substitute for any of the limbs in addition to the limbs. In addition, it goes without saying that a contact electrode is provided on the trunk.

<1-2: Operation of Biometric Device>
FIG. 5 is a flowchart showing the operation of the biometric apparatus 1. First, when a power switch (not shown) in the input unit 150 is turned on, power is supplied to each part of the electric system from a power supply unit (not shown), and body identification information including height (height, gender, age) is displayed on the display unit 160. Etc.) is displayed (step S1).
Subsequently, when height, sex, age, and the like are input from the input unit 150, the weight is measured by the weight scale 110, and the CPU 170 acquires the weight (step S2).

  After step S2, CPU 170 executes a breath analysis process (step S3). In this processing, the CPU 170 obtains discrimination information that can discriminate whether the subject's breathing is abdominal breathing or chest breathing. Details of this will be described later. After step S3, the CPU 170 executes a respiration level display process for displaying the magnitude and margin of each of abdominal respiration and chest respiration in one respiration for each respiration of the subject (step S4). This detailed content will also be described later.

<1-3: Principle of respiratory analysis>
Next, the principle of respiratory analysis will be described. FIG. 6 is a schematic diagram showing an outline of the tissue of the trunk. As shown in FIG. 6, the trunk tissue is divided into upper and lower portions by a diaphragm. In the upper part, lungs and thoracic skeletal muscles such as internal and external intercostals are formed. On the other hand, a visceral tissue and abdominal skeletal muscles including internal and external oblique / lateral abdominal muscles and rectus abdominis muscles are formed in the lower part.
In both abdominal breathing and chest breathing, the diaphragm rises and the lungs are compressed during expiration, and the diaphragm descends and the lungs expand and expand during inspiration. A feature of abdominal breathing that does not exist in chest breathing is that the diaphragm is moved up and down along with the visceral tissues by expansion and contraction of abdominal respiratory muscles such as the rectus abdominis, internal and external oblique and transverse abdominal muscles.

  Here, the first bioelectric impedance Za of the upper trunk and the second bioelectric impedance Zb of the middle trunk can be represented by an equivalent circuit shown in FIG. As shown in FIG. 7, the first bioelectrical impedance Za is a serial connection of the bioelectrical impedance Z1 of the thoracic skeletal muscle and the parallel impedance of the bioelectrical impedance Z2 of the lung and the bioelectrical impedance Z3 of the upper limb skeletal muscle. Will be. Here, the parallel impedance of Z1 and Z2 corresponds to the bioelectrical impedance of the upper lobe of the lung.

  Further, as shown in FIG. 7, the second bioelectric impedance Zb includes the bioelectrical impedance Z4 of the thoracic skeletal muscle, the parallel impedance of the bioelectrical impedance Z5 of the lung, the bioelectrical impedance Z6 of the abdominal skeletal muscle, and The parallel impedance of the bioelectric impedance Z7 of the visceral tissue is connected in series. Here, the parallel impedance of Z4 and Z5 corresponds to the bioelectrical impedance of the middle and lower lobe of the lung. Further, the bioelectric impedance of the diaphragm can be considered to be included in the bioelectric impedance Z7 typified by visceral tissue.

  Next, with reference to FIG. 8, the relationship between respiration and changes in bioelectrical impedance will be described. Changes in the first bioelectric impedance Za linked to respiration are thought to be mainly due to changes in electrical characteristics (electrical conductivity, 1 / volume resistivity) due to the entry and exit of highly insulating air into and from the lungs. It is done. That is, in exhalation (exhalation), the amount of air contained in the lung tissue decreases, so that the bioelectric impedance Z2 of the lung changes in a decreasing direction (ΔZlu <0). On the other hand, in the inspiration (inhalation), the amount of air increases, so that the bioelectric impedance Z2 of the lung changes in the increasing direction (ΔZlu> 0).

  In the breathing method (thoracic breathing) that expands the thorax with the chest type, the expansion and contraction of the respiratory skeletal muscles such as the internal and external intercostal muscles and the expansion and contraction of the lungs act in the same direction, so if the lung bioelectrical impedance Z2 increases, the chest The bioelectrical impedance Z1 of the skeletal muscle also increases, and if the bioelectrical impedance Z2 of the lung decreases, the bioelectrical impedance Z1 of the thoracic skeletal muscle also decreases. On the other hand, since abdominal breathing is a breathing method in which changes in the rib cage are hardly seen, the bioelectrical impedance Z1 of the thoracic skeletal muscle hardly changes, and the bioelectrical impedance Z2 of the lung changes greatly with respiration. The first bioelectric impedance Za includes the bioelectrical impedance Z3 of the upper limb skeletal muscle, but the upper limb skeletal muscle is not a muscle that directly contributes to respiration. In the present embodiment, the subject stands on the pedestal portion 20 of the measuring apparatus shown in FIG. 2 and grasps 30L and 30R in a state where the left and right arms are lowered, so the upper limb skeletal muscle (Z3) is measured during the measurement. Rarely moves. As shown in FIGS. 9 and 10, the first bioelectrical impedance Za changes in an increasing direction in inspiration and the first in exhalation, regardless of whether the subject's breathing is chest breathing or abdominal breathing. The bioelectrical impedance Za changes in a decreasing direction.

  On the other hand, the change of the second bioelectric impedance Zb linked to respiration is linked to the movement of the diaphragm. As described above, in both cases of abdominal breathing and chest breathing, the diaphragm rises during expiration and falls during inspiration. A feature of abdominal breathing is that the diaphragm is moved up and down together with the visceral tissue by expansion and contraction of the abdominal respiratory muscles. More specifically, only during expiration of abdominal breathing, the bioelectrical impedance of the parallel part of the visceral tissue and the abdominal skeletal muscle increases by tensioning the abdominal muscles and pushing up the diaphragm along with the visceral tissue ( ΔZst> 0). At this time, the bioelectrical impedance of the lung tissue decreases (ΔZlu <0). For this reason, it acts so that the increase in the bioelectric impedance in the upper part from the diaphragm cancels the increase in the bioelectric impedance in the lower part from the diaphragm. Thus, the movements of the abdominal skeletal muscle and the visceral tissue below the diaphragm differ between the chest breathing and the abdominal breathing.

  As shown in FIG. 9, when the subject's breathing is abdominal breathing, the second bioelectrical impedance Zb changes in an increasing direction during inhalation, while in exhalation, a decrease in the bioelectrical impedance from the diaphragm to the lower part is performed from the diaphragm to the lower part. Since the increase in bioelectrical impedance acts to cancel out, the second bioelectrical impedance Zb changes in the increasing direction. Also, as shown in FIG. 10, when the subject's breathing is chest breathing, the second bioelectrical impedance Zb changes in an increasing direction during inspiration, as in the change in the first bioelectrical impedance Za described above, In exhalation, the second bioelectrical impedance Zb changes in a decreasing direction.

  Next, with reference to FIG. 11 and FIG. 12, the relationship between the breathing of the subject and the peripheral diameter Rib of the subject's chest and the peripheral diameter Ab of the abdomen will be described. First, it is assumed that the subject's breathing is abdominal breathing. FIG. 11 is a diagram showing a result of capturing time-series changes in the peripheral diameter of each of the chest and abdomen in conjunction with the subject's abdominal breathing with Respitrace (manufactured by A.M.I., USA). As can be understood from FIG. 11, when the subject's breathing is abdominal breathing, the peripheral diameter Ab of the abdomen changes according to the breathing, while the peripheral diameter Rib of the chest hardly changes. Therefore, in the case of abdominal breathing, the change in the circumference of the subject's chest circumference Rib (the relative value of Rib (measurement value) relative to the Rib reference value indicating the reference level of the Rib measurement value) ΔRib and the circumference of the subject's abdomen ΔRib / ΔAb indicating the ratio of Ab change (relative value of Ab (measured value) to Ab reference value indicating the reference level of the measured value of Ab) ΔAb is less than “1”. The response trace information includes the peak value or absolute value of the bottom value relative to the reference value of the measurement value (0-P), and the sum of the absolute value of the peak value and the bottom value (PP). It is detected by either. Here, since the determination of the type of breathing is performed for each breath of the subject, the information on the response trace is detected in the form of PP.

  Next, it is assumed that the subject's breathing is chest breathing. FIG. 12 is a diagram showing a result of capturing time-series changes in the peripheral diameter of each of the chest and abdomen in conjunction with the subject's chest breathing with Respitrace (manufactured by A.M.I., USA). When the subject's breathing is thoracic breathing, the change in the peripheral diameter Rib of the chest corresponding to the respiration is larger than the change in the peripheral diameter Ab of the abdomen, and thus the above-described ΔRib / ΔAb exceeds “1”. Condition. Here, ΔRib / ΔAb can be regarded as discrimination information that can discriminate whether the subject's breathing is abdominal breathing or chest breathing.

  In the present embodiment, the ratio (= ΔRib / ΔAb) of the change ΔRib in the circumference of the chest of the subject and the change ΔAb in the circumference of the abdomen, and the relative value of the measured value of the first bioelectrical impedance Za to the first centering value Za0. It is found that there is a correlation between the first relative value ΔZa that is a value and the second relative value ΔZb of the measured value of the second bioelectrical impedance Zb with respect to the second centering value Zb0, and represents the correlation Using the equation, the value of ΔRib / ΔAb corresponding to the first relative value ΔZa and the second relative value ΔZb is obtained. The type of breathing (whether chest breathing or abdominal breathing) of the subject can be estimated from the obtained ΔRib / ΔAb value. Although the detailed contents will be described later, the “first centering value Za0” indicates an amplitude reference level for extracting information resulting from respiration from a waveform indicating a change in the first bioelectrical impedance Za. The “second centering value Zb0” indicates an amplitude reference level for extracting information resulting from respiration from a waveform indicating a change in the second bioelectric impedance Zb.

FIG. 13 is a correlation diagram showing the relationship between ΔRib / ΔAb and ΔZb / ΔZa obtained from the measurement data of a plurality of subjects. As can be understood from FIG. 13, a high correlation of correlation coefficient R = 0.651 and P <0.01 is obtained between ΔRib / ΔAb and ΔZb / ΔZa, and the following regression equation (1 ) Holds.
ΔRib / ΔAb = a0 × ΔZb / ΔZa + b0 (1)
a0: regression coefficient, b0: constant.

The regression equation (1) can be modified as follows.
ΔRib / ΔAb = (a0 × ΔZb−ΔZa) / ΔZa + b1 (2)
b1: Constant (= b0 + 1).

  Here, the change in the first bioelectric impedance Za accompanying respiration can be regarded as a change in the bioelectric impedance (parallel impedance of Z1 and Z2) of the upper lobe of the lung. On the other hand, changes in the second bioelectrical impedance Zb include changes in the bioelectrical impedance (parallel impedance of Z4 and Z5) of the middle and lower lobes of the lung, and changes in the bioelectrical impedance of the abdomen (parallel impedance of Z6 and Z7). Can be seen as the sum of If the change of the bioelectric impedance of the upper lobe of the lung and the change of the bioelectric impedance of the middle and lower lobe of the lung are considered to be changes of the bioelectric impedance of the same part (chest), the second bioelectric impedance The difference between the change in Zb and the change in the first bioelectric impedance Za corresponds to the change in the bioelectric impedance of the abdomen. Then, the above equation (2) can be regarded as an equation representing the relationship between ΔRib / ΔAb and the ratio between the change in the bioelectrical impedance of the abdomen and the change in the bioelectrical impedance of the chest. In the above equation (2), a0 can be regarded as a correction coefficient for correcting a difference in measurement sensitivity between the upper lobe portion and the middle lower lobe portion of the lung.

<1-4: Respiration analysis processing>
Next, the breath analysis process executed by the CPU 170 will be described. FIG. 14 is a flowchart for explaining specific contents of the breath analysis process. In the present embodiment, it is set so that 10 breath analysis processes are executed for one normal breath (= one inspiration + 1 exhalation). Here, the time required for one normal breath is regarded as 4 seconds, and the CPU 170 executes the breath analysis process every 0.4 seconds. Hereinafter, the timing for executing the breath analysis process (timing every 0.4 seconds) is referred to as sampling timing. This is only an example, and the timing for executing the breath analysis process can be arbitrarily set.

  As shown in FIG. 14, first, the CPU 170 determines whether or not the sampling timing has been reached (step S10), and proceeds to step S20 if the result of step S10 is affirmative. Here, assuming the case where the nth (n ≧ 1) sampling timing has been reached, the specific contents of each step after step S20 will be described. Prior to specific description of each step after step S20, first, an outline of the contents of each step will be briefly described. In step S20 after step S10, the CPU 170 measures the first bioelectric impedance Za of the upper trunk. In step S30 after step S20, the CPU 170 measures the second bioelectric impedance Zb of the middle trunk. In step S40 after step S30, the CPU 170 performs a smoothing process on each of the first bioelectric impedance Za measured in step S20 and the second bioelectric impedance Zb measured in step S30. In step S50 after step S40, the CPU 170 generates a first centering value Za0 indicating the amplitude reference level of the measured value of the first bioelectrical impedance Za. In step S60 after step S50, the CPU 170 calculates a first relative value ΔZa that is a relative value of the measured value of the first bioelectrical impedance Za with respect to the first centering value Za0. In step S70 after step S60, the CPU 170 generates a second centering value Zb0 indicating the amplitude reference level of the measurement value of the second bioelectrical impedance Zb, and uses the generated second centering value Zb0 to generate the second centering value Zb0. A second relative value ΔZb that is a relative value of the measured value of the bioelectrical impedance Zb with respect to the second centering value Zb0 is calculated. In step S80 after step S70, the CPU 170 executes a calculation process according to the regression equation (2) to obtain a value of ΔRib / ΔAb corresponding to the first relative value ΔZa and the second relative value ΔZb. Condition. Hereinafter, the specific contents of each step will be described in order.

  In step S20, the CPU 170 measures the first bioelectric impedance Za of the upper trunk. For example, the CPU 170 controls the electrode switching circuit 252 so as to select the current electrode X3 for the left hand and the current electrode X4 for the right hand, and selects the voltage electrode Y2 for the right foot and the voltage electrode Y4 for the right hand. Thus, the electrode switching circuit 251 is controlled. The CPU 170 outputs current data Di indicating the magnitude of the reference current Iref flowing between the right hand and the left hand, and voltage data Dv indicating the potential difference between the right foot voltage electrode Y2 and the right hand voltage electrode Y4. The first bioelectric impedance Za of the upper right limb (upper trunk) is measured. Here, the measured value of the first bioelectrical impedance at the nth (n ≧ 1) sampling timing is expressed as Za (n) ′.

  After step S20, the CPU 170 measures the second bioelectric impedance Zb of the middle trunk (step S30). For example, the CPU 170 controls the electrode switching circuit 252 so as to select the current electrode X1 for the left foot and the current electrode X4 for the right hand, and selects the voltage electrode Y3 for the left hand and the voltage electrode Y2 for the right foot. Thus, the electrode switching circuit 251 is controlled. The CPU 170 outputs current data Di indicating the magnitude of the reference current Iref flowing between the left foot and the right hand, and voltage data Dv indicating the potential difference between the left hand voltage electrode Y3 and the right foot voltage electrode Y2. Then, the second bioelectric impedance Zb in the middle of the trunk is measured. Here, the measured value of the second bioelectrical impedance at the nth sampling timing is expressed as Zb (n) ′.

  After step S30, the CPU 170 performs a smoothing process on each of the first bioelectrical impedance Za (n) ′ measured in step S20 and the second bioelectrical impedance Zb (n) ′ measured in step S30 (step S30). S40). First, the smoothing process of the first bioelectric impedance Za (n) ′ will be specifically described. The CPU 170 measures the measured value Za (n-2) ′ of the first bioelectrical impedance at the (n−2) th sampling timing and the measured value Za (n−) of the first bioelectrical impedance at the (n−1) th sampling timing. 1) ′ and a moving average process using the measured value Za (n) ′ of the first bioelectrical impedance at the nth sampling timing. And the process result is employ | adopted as a measured value of the 1st bioelectrical impedance in the nth sampling timing (smoothing process). Here, the measured value of the first bioelectrical impedance at the nth sampling timing after the smoothing process is performed is denoted as Za (n).

  Next, the smoothing process of the second bioelectrical impedance Zb (n) ′ will be specifically described. The CPU 170 measures the second measured value Zb (n-2) ′ of the second bioelectrical impedance at the (n−2) th sampling timing and the measured value Zb (n−) of the second bioelectrical impedance at the (n−1) th sampling timing. 1) ′ and a moving average process using the measured value Zb (n) ′ of the second bioelectrical impedance at the n-th sampling timing are performed. And the process result is employ | adopted as a measured value of the 2nd bioelectrical impedance in the nth sampling timing (smoothing process). Here, the measured value of the second bioelectrical impedance at the nth sampling timing after the smoothing process is performed is denoted as Zb (n).

  After step S40, the CPU 170 executes a first centering process for generating a first centering value Za0 indicating the amplitude reference level of the measured value of the first bioelectrical impedance Za (step S50). Here, the first centering value at the nth sampling timing is expressed as Za0 (n). In the present embodiment, the CPU 170 starts the time point a predetermined time before the n-th sampling timing as the start point and the n-th sampling timing as the end point in each of the plurality of sampling timings in the centering period. Based on the measured value of the 1 bioelectrical impedance Za, the first centering value Za0 (n) at the nth sampling timing is generated. The time length of the centering period is variably set according to the breathing speed of the subject at the nth sampling timing. The specific contents will be described in detail below.

  FIG. 15 is a flowchart showing specific contents of the first centering process. As shown in FIG. 15, first, the CPU 170 executes an MA10 extraction process for extracting MA10 indicating the amplitude reference level of the measurement value of the first bioelectrical impedance Za at each of the ten sampling timings (step S51). More specifically, the CPU 170 obtains the measured values (Za (n-9) to Za (n)) of the first bioelectric impedance Za at each of the n-9th to nth sampling timings. The moving average processing is performed, and the processing result is extracted as MA10 (n) at the nth sampling timing ([Za (n−9) + Za (n−8) +... + Za (n)] / 10 → MA10 (n)).

  After step S51, the CPU 170 executes MA20 extraction processing for extracting MA20 indicating the amplitude reference level of the measurement value of the first bioelectrical impedance Za at each of the 20 sampling timings (step S52). More specifically, the CPU 170 obtains measured values (Za (n-19) to Za (n)) of the first bioelectric impedance Za at each of the n-19th to nth 20 sampling timings. The moving average processing is performed, and the processing result is extracted as MA20 (n) at the nth sampling timing ([Za (n−19) + Za (n−18) +... + Za (n)] / 20 → MA20 (n)).

  After step S52, the CPU 170 executes MAX10 extraction processing for extracting the maximum value as MAX10 among the measured values of the first bioelectrical impedance Za at each of the ten sampling timings (step S53). More specifically, the CPU 170 calculates the maximum value among the measured values of the first bioelectrical impedance Za at each of the n-9th to nth sampling timings at the nth sampling timing. That is, it is extracted as MAX10 (n).

  After step S53, the CPU 170 executes a MIN10 extraction process for extracting the minimum value of the measured values of the first bioelectric impedance Za at each of the ten sampling timings as MIN10 (step S54). More specifically, the CPU 170 obtains the minimum value among the measured values of the first bioelectrical impedance Za at each of the n-9th to nth sampling timings at the nth sampling timing. That is, it is extracted as MIN10 (n).

  After step S54, the CPU 170 performs a moving average process on the average value of MAX10 and MIN10 at each of the 20 sampling timings (the average value at the nth sampling timing is expressed as AV10 (n)). A median calculation process for calculating the result as a median is executed (step S55). More specifically, the CPU 170 performs a moving average process on average values (AV10 (n-19) to AV10 (n)) at each of the n-19th to nth 20 sampling timings, The processing result is extracted as the median value CNT20 (n) at the nth sampling timing ([AV10 (n−19) + AV10 (n−18) +... + AV10 (n)] / 20 → CNT20 (n) ). Although the description is omitted here, the median value CNT20 (n) is used to extract an abnormal waveform that is not suitable for processing due to artifacts (distortion of data waveform) caused by body movements or the like.

After step S55, the CPU 170 executes a breathing timing extraction process for extracting the breathing timing of the subject at the nth sampling timing (step S56). Hereinafter, specific contents of the breathing timing extraction process will be described with reference to FIGS. 16 and 17. 16 and 17 are flowcharts showing specific contents of the breathing timing extraction process. As shown in FIG. 16, first, the CPU 170 executes a differential coefficient extraction process for extracting the differential coefficient dZa (n) of the first bioelectric impedance Za at the nth sampling timing (step S201). More specifically, the CPU 170 extracts the differential coefficient dZa (n) by executing arithmetic processing according to the following equation (3).
[Za (n) −Za (n−2)] / 1.2 = dZa (n) (3)

  Next, the CPU 170 determines whether or not the absolute value of the differential coefficient dZa (n) extracted in step S201 is smaller than 0.1 (step S202). If the result of step S202 is affirmative, the CPU 170 sets the polarity determination flag F0 (n) of the differential coefficient dZa (n) to “0” and proceeds to step S204. The polarity determination flag F0 (n) being “0” means that the value of the first bioelectrical impedance Za is a maximum value (peak value) or a minimum value (bottom value) at the n-th sampling timing. means.

  On the other hand, when the result of step S202 is negative, the CPU 170 determines whether or not the value of the differential coefficient dZa (n) is greater than 0 (step S203). If the result of step S203 is affirmative, the CPU 170 sets the polarity determination flag F0 (n) to “+1” and proceeds to step S204. The polarity determination flag F0 (n) being “+1” means that the change direction of the first bioelectrical impedance Za is on the positive side at the nth sampling timing. If the result of step S203 is negative, the CPU 170 sets the polarity determination flag F0 (n) to “−1” and proceeds to step S204. The polarity determination flag F0 (n) being “−1” means that the direction of change of the first bioelectrical impedance Za is negative on the nth sampling timing.

  In step S204, the CPU 170 makes the absolute value of the polarity determination flag F0 (n) at the nth sampling timing equal to the absolute value of the polarity determination flag F0 (n-1) at the (n-1) th sampling timing. In addition, it is determined whether the value of F0 (n-1) is not equal to the value of F0 (n). If the result of step S204 is affirmative, the CPU 170 sets F0 (n) to “0” and proceeds to the next step S206 (see FIG. 17). If the result of step S204 is negative, the CPU 170 proceeds to the next step S206 while maintaining the value of F0 (n) set immediately before step S204.

The description of the specific content of the breathing timing extraction process will be continued with reference to FIG. The CPU 170 determines whether or not the polarity determination flag F0 (n) at the nth sampling timing is “0” (step S206). If the result of step S206 is negative, the CPU 170 sets the peak / bottom determination flag F1 (n) to “0” and proceeds to step S209. The peak / bottom determination flag F1 (n) being “0” means that the measured value Za (n) of the first biopotential impedance at the nth sampling timing is not a peak value or a bottom value. .
On the other hand, when the result of step S206 is affirmative, the CPU 170 determines whether or not the sum of the polarity determination flags F0 at each of the three sampling timings is greater than “+1” (step S207). More specifically, the CPU 170 determines that the sum of the polarity determination flags (F0 (n-2) to F0 (n)) at each of the (n-2) th sampling timing to the nth sampling timing is "+1". It is judged whether it is larger than.

  If the result of step S207 is affirmative, the CPU 170 sets the peak / bottom determination flag F1 (n) to “+1”, and proceeds to step S209. The peak / bottom discrimination flag F1 (n) being “+1” means that the measured value Za (n) of the first bioelectrical impedance at the nth sampling timing is a peak value (maximum value). To do.

  If the result of step S207 is negative, the CPU 170 determines whether or not the sum of the polarity determination flags F0 at each of the three sampling timings is smaller than “−1” (step S208). More specifically, the CPU 170 determines that the sum of the polarity determination flags (F0 (n-2) to F0 (n)) at each of the (n-2) th sampling timing to the nth sampling timing is "-1". Or less.

  If the result of step S208 is affirmative, the CPU 170 sets the peak / bottom determination flag F1 (n) to “−1”, and proceeds to step S209. The peak / bottom discrimination flag F1 (n) being “−1” means that the measured value Za (n) of the first bioelectrical impedance at the nth sampling timing is a bottom value (minimum value). To do. On the other hand, if the result of step S208 is negative, the CPU 170 sets the peak / bottom discrimination flag F1 (n) to “0” and proceeds to step S209.

  In step S209, the CPU 170 determines whether or not the peak / bottom determination flag F1 (n) is “+1”. When the result of step S209 is negative, the CPU 170 adds 1 to the sampling counter value N (n−1) at the immediately preceding n−1th sampling timing (step S210), while the result of step S209 is positive. If so, the CPU 170 initializes the sampling counter value N (step S211). Here, as can be understood from FIGS. 9 and 10, a waveform showing a change in the first bioelectrical impedance Za accompanying respiration regardless of whether the subject's respiration is chest respiration or abdominal respiration. Is substantially sinusoidal, the sampling counter value N is initialized (sampling counter value = 0) every time the measured value of the first bioelectrical impedance Za reaches the peak value, and until the next peak value is reached. The number of sampling timings is sequentially counted. This completes the breathing timing extraction process in step S56 of FIG.

  Returning to FIG. 15 again, the description will be continued. When the above-described respiration timing extraction process ends, the CPU 170 sets a respiration speed determination flag for determining whether the subject's respiration is fast or slow respiration (step S57). Hereinafter, specific contents of the breathing speed determination flag setting process executed by the CPU 170 in step S57 will be described with reference to FIG. FIG. 18 is a flowchart showing specific contents of the breathing speed determination flag setting process. As shown in FIG. 18, first, the CPU 170 determines whether or not the polarity determination flag F0 (n) is “0” (step S301). When the result of step S301 is negative, the CPU 170 determines that the breathing speed determination flag Fma (n) at the nth sampling timing is the breathing speed determination flag Fma (n−1) at the immediately preceding n−1th sampling timing. ) And the process ends.

  If the result of step S301 is affirmative, the CPU 170 determines whether or not the peak / bottom determination flag F1 (n) is “+1” (step S302). If the result of step S302 is affirmative, the CPU 170 determines whether or not the sampling counter value N (n−1) at the immediately preceding n−1th sampling timing is greater than “10” (step S303). . Here, if the breathing speed of the subject is slow, the time length from when the measured value of the first bioelectrical impedance Za reaches the peak value until it reaches the next peak value becomes longer, and the next peak value is reached. The sampling counter value N immediately before reaching also increases. In the present embodiment, when the CPU 170 determines that the measured value of the first bioelectrical impedance Za has reached the peak value at the nth sampling timing, the sampling counter at the n−1th sampling timing immediately before the measured value. It is determined whether or not the value is greater than “10”, and if it is determined that the sampling counter value is greater than “10”, it is determined that the subject's breathing is slow breathing. Specifically, if the result of step S303 is affirmative, the CPU 170 sets the breathing speed determination flag Fma (n) to “20” and ends the process. The breathing speed determination flag Fma (n) being “20” means that the subject's breathing is slow breathing. If the result of step S303 is negative, the CPU 170 determines that the subject's breathing is fast breathing, sets the breathing speed discrimination flag Fma (n) to “10”, and ends the process. The breathing speed determination flag Fma (n) being “10” means that the subject's breathing is fast breathing.

  On the other hand, when the result of step S302 is negative, the CPU 170 determines whether or not the peak / bottom determination flag F1 (n) is “−1” (step S304). When the result of step S304 is negative, the CPU 170 determines that the respiration speed determination flag Fma (n) at the nth sampling timing is the respiration speed determination flag Fma (n−1) at the immediately preceding n−1th sampling timing. ) And the process ends. If the result of step S304 is affirmative, the CPU 170 determines whether or not the sampling counter value N (n−1) at the immediately preceding (n−1) th sampling timing is greater than “5” (step S305). . In the present embodiment, when the sampling counter value N (n−1) immediately before reaching the bottom value is larger than “5”, the CPU 170 determines that the subject's breathing is slow breathing, while the bottom When the sampling counter value N (n−1) immediately before reaching the value is smaller than “5”, it is determined that the subject's breathing is fast breathing. Specifically, if the result of step S305 is affirmative, CPU 170 sets the respiration speed determination flag Fma (n) to “20” and ends the process, while the result of step S305 is negative. Indicates that the breathing speed determination flag Fma (n) is set to “10” and the process is terminated. This completes the breathing speed determination flag setting process in step S57 of FIG.

  Returning to FIG. 15 again, the description will be continued. When the above-described breathing speed determination flag setting process ends, the CPU 170 extracts the first centering value Za0 (n) at the nth sampling timing (step S58). Hereinafter, specific contents of the first centering value extraction process executed by the CPU 170 in step S58 will be described with reference to FIG. FIG. 19 is a flowchart showing specific contents of the first centering value extraction process. As shown in FIG. 19, first, the CPU 170 determines whether or not the respiration speed determination flag Fma (n) is “10” (step S401). In other words, the CPU 170 determines whether or not the subject's breathing at the n-th sampling timing is fast breathing.

  In this embodiment, based on the measured value of the first bioelectrical impedance Za at each of a plurality of sampling timings within a centering period that is variably set according to the breathing rate of the subject, the first at the nth sampling timing. A centering value Za0 (n) is generated. If the result of step S401 is affirmative, that is, if the subject's breathing at the n-th sampling timing is a fast breath, the time length required for one fast breath (here, approximately 4.0 seconds) is centered. Set as period. That is, when the subject's breathing is fast breathing, a period from the n-9th sampling as the start point and the nth sampling timing as the end point is set as the centering period, and the n-9th to A first centering value Za0 (n) is generated based on the result of the moving average process using the measurement value of the first bioelectrical impedance at each of the nth sampling timings. More specifically, when the result of step S401 is affirmative, the CPU 170 determines the first centering value Za0 (n) at the nth sampling timing based on MA10 (n) obtained in step S51 of FIG. Is generated (step S402). More specifically, the CPU 170 has a first centering value Za0 (n-2) at the (n-2) th sampling timing, a first centering value Za0 (n-1) at the (n-1) th sampling timing, The moving average processing is performed using MA10 (n), and the processing result is adopted as the first centering value Za0 (n) at the nth sampling timing ([Za0 (n−2) + Za0 (n−1). ) + MA10 (n)] / 3 → Za0 (n)).

  On the other hand, if the result of step S401 is negative, that is, if the subject's breathing at the n-th sampling timing is a slow breath, the length of time required for that slow breath (here, approximately 8.0) Second) is set as the centering period. That is, when the subject's breathing is slow breathing, the period from the n-19th sampling as the start point and the nth sampling timing as the end point is set as the centering period. A first centering value Za0 (n) is generated based on the result of the moving average process using the measurement value of the first bioelectrical impedance at each of the nth sampling timings. More specifically, if the result of step S401 is negative, the CPU 170 determines the first centering value Za0 (n) at the nth sampling timing based on MA20 (n) obtained in step S52 of FIG. Is generated (step S403). More specifically, the CPU 170 performs moving average processing using Za0 (n-2), Za0 (n-1), and MA20 (n), and the processing result is obtained at the nth sampling timing. Adopted as the first centering value Za0 (n) ([Za0 (n−2) + Za0 (n−1) + MA20 (n)] / 3 → Za0 (n)). This completes the first centering process in step S50 of FIG.

  As described above, the waveform indicating the change in the first bioelectrical impedance Za is substantially sinusoidal regardless of whether the subject's breathing is chest breathing or abdominal breathing. Even if the waveform indicating the change in the first bioelectric impedance Za is disturbed due to the influence of body movement or the like, the CPU 170 obtains the first centering value Za0 according to the first waveform at each of the predetermined number of sampling timings. A first centering value Za0 is generated based on the measured value of the bioelectric impedance Za. More specifically, for each sampling timing, the CPU 170 starts at a time point that is a predetermined time length before the sampling timing and starts at the sampling timing in each of a plurality of sampling timings within the centering period with the sampling timing as an end point. Since the moving average process using the measurement value of one bioelectrical impedance is performed and the first centering value Za0 at the sampling timing is obtained based on the result, the change in the first bioelectrical impedance Za due to the influence of body movement or the like Even if the waveform indicating is disturbed, the first centering value Za0 corresponding to the waveform can be generated with high accuracy. The time length of the centering period corresponding to each sampling timing is variably set according to the breathing rate of the subject at the sampling timing.

  Returning to FIG. 14, the description will be continued. As illustrated in FIG. 14, when the first centering process in step S50 is completed, the CPU 170 performs a first relative that is a relative value of the first bioelectrical impedance measurement value Za (n) with respect to the first centering value Za0 (n). A first relative value calculation process for calculating the value ΔZa (n) is executed (step S60). More specifically, the CPU 170 obtains the difference between the first bioelectrical impedance measurement value Za (n) obtained in step S40 and the first centering value Za0 (n) obtained in step S50. The difference value is employed as the first relative value ΔZa (n) at the nth sampling timing.

  After step S60, the CPU 170 generates a second centering value Zb0 indicating the amplitude reference level of the measurement value of the second bioelectrical impedance Zb, and uses the generated second centering value Zb0 to generate the second bioelectrical impedance Zb. A second relative value ΔZb, which is a relative value of the measured value to the second centering value Zb0, is calculated (step S70).

  Here, as described above, the change in the second bioelectrical impedance Zb in the exhalation of abdominal breathing is different from the change in the first bioelectrical impedance Za, and thus is similar to the case of obtaining the first centering value Za0. In addition, even if the moving average process using the measurement value of the second bioelectric impedance Zb at each of the predetermined number of sampling timings is performed, the amplitude reference level, that is, the waveform indicating the change of the second bioelectric impedance Zb is used. The amplitude reference level (second centering value Zb0) for extracting information resulting from respiration cannot be obtained with high accuracy.

  Therefore, in the present embodiment, as shown in FIG. 20, the zero cross timing at which the measured value of the first bioelectric impedance Za is equal to the first centering value Za0 is extracted, and the second bioelectric impedance Zb at the zero cross timing is extracted. The second centering value Zb0 is generated based on the measured value. Thereby, the amplitude reference level of the measured value of the second bioelectrical impedance Zb can be extracted with high accuracy. FIG. 20 is a diagram for conceptually explaining a method of generating the second centering value Zb0. Hereinafter, specific contents of the second relative value calculation process executed by the CPU 170 in step S70 will be described with reference to FIG.

  FIG. 21 is a flowchart showing specific contents of the second relative value calculation process. As shown in FIG. 21, the CPU 170 extracts the minimum value from the first relative values ΔZa at each of the five sampling timings (step S71). More specifically, the CPU 170 determines the absolute value | ΔZa | (| ΔZa (n−4) | to | ΔZa (n) of the first relative value ΔZa at each of the (n−4) th to n-th sampling timings. The minimum value of |) is extracted as the cross-point determination value ΔMIN5 (n) at the n-th sampling timing.

  After step S71, the CPU 170 determines whether or not the cross point determination value at the immediately preceding sampling timing is equal to the cross point determination value extracted at step S71 and the immediately preceding sampling timing is zero cross timing ( Step S72). More specifically, the CPU 170 determines that the cross point determination values ΔMIN5 (n−1) and ΔMIN5 (n) at the (n−1) th sampling timing are equal and the crosspoint at the (n−1) th sampling timing. It is determined whether or not the determination flag F2 (n−1) is set to “+1”. When the cross point determination flag F2 (n-1) is set to "+1", the (n-1) th sampling timing is regarded as the zero cross timing. The initial value (default value) of the cross point determination flag F2, that is, the value of the cross point determination flag F2 (1) at the first sampling timing is set to “0”.

  If the result of step S72 is affirmative, the CPU 170 determines that the nth sampling timing is not the zero cross timing, sets the cross point determination flag F2 (n) to “0”, and proceeds to step S74. If the result of step S72 is negative, the CPU 170 determines whether or not the absolute value of the first relative value ΔZa (n) at the nth sampling timing is 0.3 or less (step S73). If the result of step S73 is negative, the CPU 170 determines that the nth sampling timing is not the zero cross timing, sets the cross point determination flag F2 (n) to “0”, and proceeds to step S74. If the result of step S73 is affirmative, the CPU 170 determines that the nth sampling timing is zero cross timing, sets the cross point determination flag F2 (n) to “+1”, and proceeds to step S74.

  Next, the CPU 170 determines whether or not the cross point determination flag F2 (n) at the nth sampling timing is “+1” (step S74). If the result of step S74 is affirmative, the CPU 170 extracts the second centering value Zb0 (step S75). More specifically, the CPU 170 obtains the second centering value Zb0 (n-2) at the (n-2) th sampling timing and the second centering value Zb0 (n-1) at the (n-1) th sampling timing. The moving average process is performed using the measured value Zb (n) of the second bioelectrical impedance at the nth sampling timing, and the processing result is obtained as the second centering value Zb0 (n) at the nth sampling timing. ([Zb0 (n-2) + Zb0 (n-1) + Zb (n)] / 3 → Zb0 (n)). On the other hand, if the result of step S74 is negative, the CPU 170 changes the second centering value Zb0 (n−1) at the immediately preceding n−1th sampling timing to the second centering value Zb0 ( n) (Zb0 (n−1) → Zb0 (n)).

  Then, the CPU 170 calculates a second relative value ΔZb (n) at the nth sampling timing (step S76). More specifically, the CPU 170 calculates the difference between the second bioelectrical impedance measurement value Zb (n) and the second centering value Zb0 (n) as the second relative value ΔZb (n at the nth sampling timing. ) Is adopted. This completes the second relative value calculation process in step S70 of FIG.

  For example, when the subject's breathing is abdominal breathing and the first bioelectrical impedance Za and the second bioelectrical impedance Zb change as shown in FIG. 9, the first time relative value ΔZa and the second relative value ΔZb change over time. The waveform showing is as shown in FIG. The waveform showing the temporal change of the first relative value ΔZa is based on the first centering value Za0, which is the amplitude reference level of the measured value of the first bioelectrical impedance Za, as the zero reference, and the second relative value ΔZb is elapsed with time. The waveform indicating the change in the state is based on the second centering value Zb0, which is the amplitude reference level of the measurement value of the second bioelectric impedance Zb, as a zero reference. By superimposing both waveforms, it is possible to determine the waveforms of the first relative value ΔZa and the second relative value ΔZb in inhalation and the waveforms of the first relative value ΔZa and the second relative value ΔZb in expiration. . In the present embodiment, the CPU 170 determines whether the subject's breathing is inspiration or expiration based on the value of the first relative value ΔZa. More specifically, the CPU 170 determines that it is inspiration when the first relative value ΔZa is a positive value, and determines that it is expiration when the first relative value ΔZa is a negative value. Further, the coefficient of the regression equation (2) described above may be corrected based on the difference in the amplitude and integral value of each waveform of the first relative value ΔZa and the second relative value ΔZb in the intake air. Thereby, the measurement accuracy is improved.

  Returning to FIG. 14 again, the description will be continued. As shown in FIG. 14, when the second relative value calculation process in step S70 is completed, the CPU 170 estimates ΔRib / ΔAb corresponding to the first relative value ΔZa (n) and the second relative value ΔZb (n). / ΔAb estimation calculation processing is executed (step S80). The specific contents of the ΔRib / ΔAb estimation calculation process executed by the CPU 170 in step S80 will be described below with reference to FIGS. 23 and 24 are flowcharts showing specific contents of the ΔRib / ΔAb estimation calculation process. As shown in FIG. 23, first, the CPU 170 determines whether or not the value of the first relative value ΔZa (n) at the n-th sampling timing is “0” or more (step S81).

  If the result of step S81 is negative, the CPU 170 determines that the subject's breath is exhalation, and performs an estimation calculation of ΔRib / ΔAb (n) at the nth sampling timing (step S82). More specifically, the CPU 170 executes arithmetic processing according to the above-described regression equation (2), whereby ΔRib / ΔAb (corresponding to the first relative value ΔZa (n) and the second relative value ΔZb (n). n). On the other hand, if the result of step S81 is affirmative, the CPU 170 determines that the subject's breathing is inspiration, and sets the value of ΔRib / ΔAb (n) at the nth sampling timing to an initial value. In this embodiment, when the result of step S81 is positive, the CPU 170 sets the value of ΔRib / ΔAb (n) at the n-th sampling timing to “1.0” which is an initial value.

  Next, the CPU 170 determines whether or not the value of ΔRib / ΔAb (n) is −2.5 or more and 4.5 or less (step S83). If the result of step S83 is negative, the CPU 170 sets the value of ΔRib / ΔAb to the initial value “1.0” and proceeds to step S84. If the result of step S83 is affirmative, the CPU 170 proceeds to step S84 as it is.

  In step S84, the CPU 170 determines the difference (| ΔRib / ΔAb (n) between the absolute value of ΔRib / ΔAb (n) and the absolute value of ΔRib / ΔAb (n−1) at the immediately preceding (n−1) th sampling timing. ) | − | ΔRib / ΔAb (n−1) |) is determined as to whether it is greater than 0.3. When the result of step S84 is negative, the CPU 170 obtains the average of ΔRib / ΔAb (n−1) and ΔRib / ΔAb at the immediately preceding (n−1) -th sampling timing, and calculates the obtained average value. Adopted as ΔRib / ΔAb (n) at the n-th sampling timing ([ΔRib / ΔAb (n−1) + ΔRib / ΔAb (n)] / 2 → ΔRib / ΔAb (n)) and the next step S85 (FIG. 24). On the other hand, if the result of step S84 is affirmative, the CPU 170 sets the value of ΔRib / ΔAb (n) at the n-th sampling timing to the initial value “1.0” and proceeds to the next step S85.

  With reference to FIG. 24, the description of the specific contents of the ΔRib / ΔAb estimation calculation process will be continued. As shown in FIG. 24, in step S85, the CPU 170 determines whether or not the first relative value ΔZa (n) at the nth sampling timing is smaller than “0”. If the result of step S85 is affirmative, the CPU 170 determines that the subject's breathing is exhalation, and adds 1 to the count value Ni of the previous integration count. More specifically, the CPU 170 counts the number of integrations at the nth sampling timing by adding a value obtained by adding 1 to the count value Ni (n−1) of the number of integrations at the immediately preceding n−1th sampling timing. The value Ni (n) is adopted.

  On the other hand, if the result of step S85 is negative, the CPU 170 determines that the subject's breathing is inspiration, and initializes the count value Ni of the number of integrations to “0”. That is, in this case, the count value Ni (n) of the number of integrations at the nth sampling timing is set to “0”.

  Subsequently, as illustrated in FIG. 24, the CPU 170 determines again whether or not the first relative value ΔZa (n) is smaller than “0” (step S86). If the result of step S86 is affirmative, the CPU 170 calculates the sum of ΔRib / ΔAb integral value (ΣΔRib / ΔAb (n−1)) and ΔRib / ΔAb (n) at the immediately preceding (n−1) th sampling timing. Is obtained, and the integrated value (ΣΔRib / ΔAb (n)) of ΔRib / ΔAb at the n-th sampling timing is obtained, and the process proceeds to the next step S87. On the other hand, if the result of step S86 is negative, that is, if it is determined that the subject's breathing state is inhalation, the CPU 170 sets the peak / bottom determination flag F1 (n) to “+1” and then continues. The process proceeds to step S87.

  Next, the CPU 170 determines whether or not the count value Ni (n) of the number of integrations at the nth sampling timing is zero (step S87). If the result of step S87 is negative, the CPU 170 obtains the integrated value [ΣΔRib / ΔAb (n)] of ΔRib / ΔAb at the nth sampling timing, and the count value Ni (n of the number of integrations at the nth sampling timing). ) To obtain an average value of ΔRib / ΔAb. On the other hand, when the result of step S87 is affirmative, the CPU 170 determines the average value of [Delta] Rib / [Delta] Ab at the immediately preceding (n-1) th sampling timing ([[Sigma] [Delta] Rib / [Delta] Ab (n-1)] / Ni (n-1)). Is adopted as the average value of ΔRib / ΔAb at the nth sampling timing. This completes the ΔRib / ΔAb estimation calculation process, and the breath analysis process at the nth sampling timing ends.

  When the subject's breathing is abdominal breathing and the first relative value ΔZa and the second relative value ΔZb change as shown in FIG. 22, the above average value of ΔRib / ΔAb ([ΣΔRib / ΔAb] / Ni) is As shown in FIG. In FIG. 25, when the value (average value) of ΔRib / ΔAb in exhalation is 1.0 or less, the subject's breathing is estimated to be abdominal breathing. Respiration is estimated to be chest respiration.

  As described above, in the present embodiment, when the CPU 170 executes the breath analysis process, ΔRib / ΔAb corresponding to the first relative value ΔZa and the second relative value ΔZb at the sampling timing is calculated for each sampling timing. Therefore, there is an advantage that the type of breathing (abdominal breathing or chest breathing) of the subject can be accurately determined in real time.

<1-5: Respiration level display process>
Next, a respiration level display process executed by the CPU 170 will be described. In the present embodiment, the CPU 170 executes a breathing level display process for displaying (notifying) the size and margin of each abdominal breathing and chest breathing in one breath for each breath of the subject. More specifically, for each breath of the subject, the CPU 170 determines the chest breathing in the one breath and the breathing analysis indicating the depth of the breath in the one breath and the result of the breath analysis process in the one breath. Control is performed so that the magnitude and margin of each abdominal breath are displayed on the display unit 160. As shown in FIG. 26, in the present embodiment, in addition to the magnitude and margin of each of the chest breathing and the abdominal breathing in one breath, the abdominal level indicating the proportion of the abdominal breathing in the one breath is displayed on the display unit. The display is controlled to be displayed at 160. The first bar graph BG1 shown in FIG. 26 is for displaying the magnitude and margin of each of the chest breathing and the abdominal breathing. On the other hand, the second bar graph BG2 shown in FIG. 26 is for displaying the subject's abdominal level. Details of these will be described later.

  Prior to specific description of the respiration level display process, a respiration depth extraction process executed by the CPU 170 will be described with reference to FIG. FIG. 27 is a flowchart showing specific contents of the breathing depth extraction process executed by the CPU 170. As will be described later, the breathing depth (breathing depth) of the subject extracted by this breathing depth extraction process is used for the breathing level display process.

  As shown in FIG. 27, first, the CPU 170 determines whether or not the sampling timing has been reached (step S501), and if the result of step S501 is affirmative, the process proceeds to the next step S502. In step S502, the CPU 170 determines whether or not the subject's breathing is inspiration. Specifically, the CPU 170 determines that it is inspiration when the value of the first relative value ΔZa at the sampling timing is a positive value, and determines that it is expiration when the value is a negative value. That's it. If the CPU 170 determines that it is inhalation, it sets the inhalation determination flag F3 to “1”, whereas if it determines that it is expiration, it sets the inspiration determination flag F3 to “0”. In the initial state, the intake determination flag F3 is set to “1” (that is, the default value of F3 is set to 1).

  If the result of step S502 is positive, the CPU 170 executes a peak hold process (step S503). More specifically, the CPU 170 holds the maximum value as the peak value ΔZa (MAX) among the first relative values ΔZa at each of a plurality of sampling timings during intake. On the other hand, if the result of step S502 is negative, the CPU 170 executes bottom hold processing (step S504). More specifically, the CPU 170 holds the minimum value among the first relative values ΔZa at each of a plurality of sampling timings during expiration as the bottom value ΔZa (MIN).

  Next, the CPU 170 determines whether or not the sampling timing is a zero cross timing (step S505). More specifically, the CPU 170 determines whether or not the sampling timing is the zero cross timing by determining whether or not the cross point determination flag F2 at the sampling timing is “+1”. It is. If the result of step S505 is negative, the respiration depth extraction process at the sampling timing ends. On the other hand, when the result of step S505 is positive, the CPU 170 determines whether or not the differential coefficient dZa of the first bioelectric impedance Za at the sampling timing is positive (> 0) (step S506). In other words, the CPU 170 determines whether or not the sampling timing is a timing for changing from expiration to inspiration.

  If the result of step S506 is affirmative, the CPU 170 determines that the sampling timing is a timing at which the expiration changes from inspiration to inspiration, and the peak value ΔZa (MAX) and bottom value ΔZa (MIN) held at that time are determined. ) And the absolute value are extracted as the breathing depth ΔZap-p in the immediately preceding one breath (step S507). Thereafter, the CPU 170 executes an intake flag setting process (step S508). More specifically, the CPU 170 sets the intake determination flag F3 to “1”. Then, the CPU 170 initializes the peak hold process (step S509). More specifically, the CPU 170 sets (initializes) the peak value ΔZa (MAX) held in step S503 to “0”, and ends the respiration depth extraction process at the sampling timing.

  On the other hand, if the result of step S506 is negative, the CPU 170 determines that the sampling timing is a timing at which the sampling changes from inspiration to expiration, and executes an expiration flag setting process (step S510). More specifically, the CPU 170 sets the intake determination flag F3 to “0”. Then, the CPU 170 initializes the bottom hold process (step S511). More specifically, the CPU 170 sets (initializes) the bottom value ΔZa (MIN) held in step S504 to “0”, and ends the respiration depth extraction process at the sampling timing.

  Next, the specific contents of the respiration level display process executed by the CPU 170 will be described with reference to FIG. FIG. 28 is a flowchart showing specific contents of the respiration level display process. As shown in FIG. 28, the CPU 170 normalizes the breathing depth in the immediately preceding one breath (step S601). Here, “normalize the breathing depth” is a value obtained by removing the influence of individual differences such as the physique among subjects from the value of the breathing depth immediately before one breath extracted by the above-described breathing depth extraction process. It means to correct. Specifically, in step S601, the CPU 170 sets the breathing depth ΔZap-p in the immediately preceding one breath to the second centering value Zb0 in the one breath (specifically, in each of a plurality of sampling timings in the one breath. A value obtained by dividing by 100 after being divided by the average value of the second centering value Zb0) is employed as a normalized value of breathing depth% ΔZa (= (ΔZap−p / Zb0) × 100).

  Next, the CPU 170 determines the number of stages of the first bar graph BG1 to be colored and displayed according to the value of the normalized value% ΔZa of the respiration depth obtained in step S601 (hereinafter referred to as “first display stage number”). Is determined (step S602). More specifically, the CPU 170 obtains a normalized value% ΔTV of the tidal volume corresponding to the normalized value% ΔZa of the breathing depth obtained in step S601, and according to the obtained value of% ΔTV, The number of display stages is determined. Here, “tidal volume” indicates the amount of air that enters and exits the lung in one breath of the subject and is expressed as ΔTV. “Normalizing the tidal volume” means correcting the tidal volume value ΔTV (measured value) measured by a spiro etc. to a value that removes the influence of individual differences such as physique between subjects. It means to do. In the present embodiment, when normalizing the tidal volume ΔTV, the value (actually measured value) VC of the subject's vital capacity measured by a spiro or the like is divided by the standard VC indicating the standard vital capacity. Coefficient% VC (= actual VC / standard VC) is used. Specifically, the normalized value% ΔTV (= ΔTV /% VC) of the tidal volume is obtained by dividing the measured value (actually measured value) of the tidal volume ΔTV by the above-described coefficient% VC. . For example, male standard vital capacity VCmale (ml) is expressed by (27.63-0.112 × age) × height (cm), and female standard vital capacity VCfemale (ml) is (21.78-0. 101 × age) × height (cm).

FIG. 29 shows tidal ventilation when 20 people in both men and women measure each tidal volume ΔTV three times (small ventilation, medium ventilation, and large ventilation once). It is a correlation diagram which shows the relationship between the normalized value% ΔTV of the quantity and the normalized value% ΔZa of the respiratory depth. As shown in FIG. 29, the normalized value% ΔTV of the tidal volume and the normalized value% ΔZa of the respiratory depth have a high correlation coefficient r = 0.75, and the following regression equation (4) Is established.
% ΔZa = c0 ×% ΔTV (4)
c0: regression coefficient.

  The CPU 170 obtains a normalized value% ΔTV of the tidal volume corresponding to the normalized value% ΔZa of the respiration depth obtained in step S601 by executing arithmetic processing according to the regression equation (4). Then, the CPU 170 determines the first display step number according to the obtained normalized value% ΔTV of the tidal volume. In the present embodiment, the maximum value of the number of first display steps is set to “10”, which is a combination of the five chest methods and the five belly methods (see FIG. 26).

  As shown in FIG. 29, in this embodiment, when the value of the normalized value% ΔTV of the tidal volume is equal to or greater than the first predetermined value α1, the breathing level of the subject is regarded as “maximum”. In this case, the CPU 170 determines the first display step number to be “10” which is the maximum value. Further, when the value of the normalized tidal volume value% ΔTV is equal to or larger than the second predetermined value α2 (<α1) and is lower than the first predetermined value α1, the respiration level of the subject is “large”. (See FIG. 29). In this case, the CPU 170 determines the first display step number as “8”. Further, when the normalized value% ΔTV of the tidal volume is equal to or larger than the third predetermined value α3 (<α2) and is lower than the second predetermined value α2, the subject's respiratory level is regarded as “medium”. (See FIG. 29). In this case, the CPU 170 determines the first display step number as “6”. When the value of the tidal volume normalized value% ΔTV is equal to or larger than the fourth predetermined value α4 (<α3) and lower than the third predetermined value α3, the subject's breathing level is “small”. Considered (see FIG. 29). In this case, the CPU 170 determines the first display step number as “4”. In addition, when the value of the normalized value% ΔTV of the tidal volume is lower than the fourth predetermined value α4, the subject's breathing level is regarded as an essential level at rest (see FIG. 29). In this case, the CPU 170 determines the number of first display steps as “2”.

  Returning to FIG. 28 again, the description will be continued. As shown in FIG. 28, when the stage number determination process in step S602 ends, the CPU 170 determines the abdominal level in the immediately preceding one breath (step S603). Specifically, CPU 170 determines the numerical value of the abdominal level according to the value (average value) of ΔRib / ΔAb in the immediately preceding one breath. The numerical value of the abdominal level is represented by a value from 0 to 100. The closer the value is to 0, the smaller the level of abdominal breathing (the proportion of the abdominal breathing in the subject's breathing is smaller). The degree of breathing is large (the proportion of abdominal breathing in the subject's breathing is large).

  As shown in FIG. 28, after step S603, the CPU 170 executes a stage number division process for dividing the first display stage number determined in step S602 into an abdominal type and a chest type (step S604). More specifically, the CPU 170 executes the stage number division process based on the first display stage number determined in step S602 and the abdominal level determined in step S603. Here, the description will be continued assuming that the first display stage number indicating the entire respiration level is “6” while the abdominal level is “70”. If the abdominal level is “70”, the ratio between the abdominal breathing and the chest breathing is considered to be 7: 3, so the first display stage number “6” Divided into 4 stages in the abdomen. That is, as shown in FIG. 26, the number of display stages of BG1 of the first bar graph indicating the magnitude of chest breathing is “2”, and the number of display stages of the first bar graph BG1 indicating the magnitude of abdominal breathing is “ 4 ".

  As shown in FIG. 28, after step S604, the CPU 170 determines a margin level according to the breathing rate of the subject (step S605). Now, it is assumed that the last breath is a rest breath and the time length required for the breath is 4 seconds or more. In the present embodiment, the number of steps of the first bar graph BG1 corresponding to the essential respiratory level according to the breathing rate of the subject is determined in advance, and corresponds to the essential respiratory level according to the respiratory rate during rest breathing. The number of steps of the first bar graph BG1 is set to “2”. The CPU 170 assigns the stage number “2” to the breast type and the abdominal type one by one. As described in step S604 above, here, the number of display stages of the first bar graph BG1 indicating the magnitude of the chest breathing is “2”, and the display of the first bar graph BG1 indicating the magnitude of the abdominal breathing is displayed. Since the number of stages is set to “4”, there is a margin for one stage for chest breathing and a margin for three stages for abdominal breathing.

  In this case, if the number of display steps of the first bar graph BG1 indicating the magnitude of abdominal breathing is “1” or more, it means that the subject's abdominal breathing magnitude meets the required level, If the number of display steps is “2”, it means that the subject's abdominal breathing level satisfies the “small” level exceeding the required level, and if the display step number is “3”. Means that the “medium” level above is met, and if the number of display stages is “4”, it means that the “large” level is met, If the number of display steps is “5”, it means that the magnitude of the subject's abdominal breathing satisfies the “maximum” level. As described above, since the number of display steps of the first bar graph BG1 indicating the magnitude of abdominal breathing is set to “4”, the magnitude of the subject's abdominal breathing is “large”. It can be seen that there is a sufficient margin with respect to the required level (the number of display stages “1”). The same applies to thoracic breathing. Here, since the number of display steps of the first bar graph BG1 indicating the magnitude of thoracic breathing is set to “2”, the magnitude of thoracic breathing of the subject is It can be seen that the level of “small” is satisfied and exceeds the required level (number of display steps “1”).

  As the subject's breathing rate increases, the number of stages of the first bar graph BG1 corresponding to the mandatory breathing level corresponding to the breathing rate increases. The corresponding number of stages also increases. For example, if the time length required for one breath is 3 seconds or more and less than 4 seconds, the number of stages of the first bar graph BG1 corresponding to the required breathing level is set to “4”, and the number of stages “4” is assigned in two stages for the chest type and the abdominal type. Correspondingly, the respective margin levels of chest and abdominal breathing change.

  After step S605, the CPU 170 displays the magnitude and margin of each of the subject's chest breathing and abdominal breathing as a first bar graph BG1, while displaying the subject's abdominal level as a second bar graph BG2. (Step S606). As shown in FIG. 26, the CPU 170 corresponds to the essential levels of the abdominal breathing and the chest breathing among the number of stages of the first bar graph BG1 to be colored and displayed (two breast stages, four abdominal stages). Since the number of steps and the number of steps corresponding to the margin are displayed in different colors, the subject can easily grasp the size and margin of each of his abdominal breathing and chest breathing.

  Further, as shown in FIG. 26, the number of steps of the abdominal level displayed in the second bar graph BG2 is set to “5”, and 5 is set according to the numerical value of the abdominal level determined in the above-described step S603. Any one of the two stages is selectively colored. Specifically, the CPU 170 performs control so that only the first step is colored when the abdominal level value is 0 to 20, and only the second step is displayed when the abdominal level value is 21 to 40. If the numerical value of the abdominal level is 41 to 60, control is performed so that only the third step is displayed in color. If the numerical value of the abdominal level is 61 to 80, only the fourth step is controlled. Control is performed so that the display is colored. When the numerical value of the abdominal level is 81 to 100, control is performed so that only the fifth stage is displayed in color. As described above, since it is assumed here that the abdomen level is “70”, as shown in FIG. 26, the CPU 170 color-displays only the fourth stage of the second bar graph BG2. It is a condition to control to.

  As described above, in this embodiment, the CPU 170 controls the display unit 160 to display the size and margin of abdominal breathing and chest breathing in one breath for each breath of the subject. Thus, the subject can recognize the strengths and weaknesses of utilizing his chest respiratory muscles and abdominal respiratory muscles. This makes it possible to ensure motivation for respiratory muscle training such as abdominal breathing for activating one's weakness while making the subject aware of his strength. In addition, according to the present embodiment, it is preferable from the viewpoint of ensuring the safety of the subject because the subject can grasp the margin of the breathing ability of the subject without performing the maximum breathing, such as a spiro. There is.

<2. Second Embodiment>
In addition to chest and abdominal breathing, there is a draw-in breath that exhales and inhales while maintaining a depressed state. Draw-in breathing can effectively train inner trunk muscles that are not often used in everyday life (for example, the transverse abdominal muscles and the spine upright muscles). Strengthening the inner muscle not only enhances breathing function, but also strengthens the muscles that support the spine, making it easier for the muscles of the trunk to exert their power, leading to enhancement of motor functions and the like. For example, draw-in breathing has been incorporated into athlete training for the purpose of improving motor function. In physical therapy and rehabilitation, draw-in breathing is used to improve low back pain and prevent low back pain. Draw-in breathing is also effective for dieting.

  If the biometric apparatus 1 described in the first embodiment is applied, it is possible to determine whether the subject's breathing is a chest breathing or abdominal breathing, as well as a draw-in breathing. Hereinafter, the case of determining draw-in breathing will be described. Since the hardware configuration of the biometric apparatus is basically the same as that described in the first embodiment, the same reference numerals as those in the first embodiment are used and description thereof is omitted.

  FIG. 30 is a graph showing temporal changes of the first bioelectric impedance Za at the upper trunk and the second bioelectric impedance Zb at the middle trunk. As shown in the figure, in the case of draw-in respiration, both the first bioelectrical impedance Za and the second bioelectrical impedance Zb change in an increasing direction in inspiration, and in the exhalation, the first bioelectrical impedance Za and the second bioelectrical impedance Zb are Both change in a decreasing direction. This change is the same as for chest breathing. This is because in the case of draw-in breathing, exhalation and inhalation are performed by chest breathing while maintaining a state where the abdomen is recessed. However, in the case of draw-in respiration, since force is applied to the abdomen to dent the abdomen, the amplitude reference level of the second bioelectrical impedance Zb in the middle of the trunk is higher than in the case of chest respiration.

  As described above, since the amplitude reference level of the second bioelectrical impedance Zb is different between the case of the draw-in respiration and the case of the chest respiration, it is possible to determine the draw-in respiration using this. That is, after performing the respiration analysis process described in the first embodiment (FIG. 14), the second bioelectric impedance is determined when it is determined that the respiration is chest respiration because the average value of ΔRib / ΔAb exceeds 1.0. When the amplitude reference level of Zb (second centering value Zb0) is higher than the amplitude reference level of the second bioelectrical impedance Zb in the case of chest-type respiration, this may be determined as draw-in respiration.

  However, the amplitude reference level of the second bioelectrical impedance Zb in the case of thoracic breathing differs for each subject. Therefore, in order to determine draw-in respiration by the above-described method, it is necessary to measure in advance the amplitude reference level of the second bioelectrical impedance Zb in the case of chest respiration and store it in the second storage unit 130. . In addition, the above-described predetermined value needs to be stored in the first storage unit 120 in advance.

  For this reason, the biometric apparatus 1 (CPU 170) according to the present embodiment notifies, for example, a message for instructing the subject to perform chest-type breathing, and obtains a number of times acquired during the period in which the subject is performing chest-type breathing. The average value of the second centering value Zb0 is calculated and stored in the second storage unit 130 as the amplitude reference level of the second bioelectrical impedance Zb in the case of chest breathing. Hereinafter, the amplitude reference level of the second bioelectrical impedance Zb stored in the second storage unit 130 in this way in the case of thoracic respiration is denoted as Zb1. On the other hand, the predetermined values stored in the first storage unit 120 are the amplitude reference level of the second bioelectrical impedance Zb in the case of chest respiration and the second living body in the case of draw-in respiration collected from a large number of subjects in advance. The value can be set based on the difference between the electrical impedance Zb and the amplitude reference level. Hereinafter, the predetermined value stored in the first storage unit 120 is expressed as ΔZb1.

FIG. 31 is a flowchart showing the processing content of the breathing type determination processing.
The processing shown in the figure is executed after performing the breath analysis processing described in the first embodiment. That is, also in the present embodiment, the CPU 170 performs the respiration analysis processing shown in FIG. 14, and measures the first bioelectric impedance Za (step S20) and the second bioelectric impedance Zb (steps) at each sampling timing. S30), smoothing processing (step S40), first centering processing (step S50), first relative value calculation processing (step S60), second relative value calculation processing (step S70), and ΔRib / ΔAb estimation. Arithmetic processing (step S80) is executed.

  Thereafter, the CPU 170 starts the respiration type determination process. First, the average value ([ΣΔRib / ΔAb] / Ni) of ΔRib / ΔAb obtained by the ΔRib / ΔAb estimation calculation process (step S80) is 1.0 or less. It is determined whether or not (step S701). If the result of step S701 is affirmative, the CPU 170 determines that the subject's breathing is abdominal breathing (step S702).

  On the other hand, if the result of step S701 is negative, the CPU 170 reads out the amplitude reference level Zb1 of the second bioelectrical impedance Zb in the case of chest-type breathing from the second storage unit 130 and the predetermined value ΔZb1 as the first storage unit. Read from 120 (step S703). Note that the predetermined value ΔZb1 stored in the first storage unit 120 is set as a standard value, and this standard value is used as a pre-input height, age, gender (step S1 in FIG. 5) or a pre-measured weight ( You may correct | amend by the calculation using step S2) of FIG.

  Thereafter, the CPU 170 uses the second centering value Zb0 generated in the process of calculating the second relative value ΔZb in the second relative value calculation process (step S70) as the second bioelectrical impedance Zb in the case of chest breathing. It is determined whether or not the value is equal to or greater than the sum of the amplitude reference level Zb1 and the predetermined value ΔZb1 (step S704). The second centering value Zb0 used in step S704 may be, for example, the average value of the second centering value Zb0 in the immediately preceding one breath or the average value of the second centering value Zb0 in the immediately preceding multiple sampling periods. Good. When the result of step S704 is affirmative, the CPU 170 determines that the subject's breathing is draw-in breathing (step S705). If the result of step S704 is negative, the CPU 170 determines that the subject's breathing is chest breathing (step S706).

  As described above, according to the present embodiment, it is possible to accurately determine in real time whether the subject's breathing is abdominal breathing, chest breathing or draw-in breathing. Note that the biometric apparatus 1 may determine only whether or not it is draw-in respiration, instead of determining draw-in respiration in addition to chest respiration and abdominal respiration.

  Zb1 (the amplitude reference level of the second bioelectrical impedance Zb in the case of chest breathing) stored in the second storage unit 130 is a plurality of second values acquired during the period in which the subject is performing chest breathing. It is not limited to the average value of the centering value Zb0. For example, it may be one second centering value Zb0 acquired at an arbitrary timing during a period in which the subject is performing chest breathing. In addition, the CPU 170 does not add a predetermined value ΔZb1 to Zb1 read from the second storage unit 130, but multiplies a predetermined coefficient (for example, 1.035) larger than 1.0 to add the value (Zb1 + ΔZb1). A threshold value corresponding to may be calculated. As in the case of the predetermined value ΔZb1, the coefficient in this case is also the amplitude reference level of the second bioelectrical impedance Zb in the case of chest-type respiration collected in advance from a large number of subjects, and the second bioelectricity in the case of draw-in respiration. The value can be set based on the difference between the impedance Zb and the amplitude reference level. Further, the threshold value calculated in this way is stored in the second storage unit 130 instead of Zb1, and the second centering value Zb0 is read from the second storage unit 130 in step S704 of the above-described respiration type determination process. It may be determined whether or not it is equal to or greater than the threshold value.

  Moreover, since the respiration depth extraction process and respiration level display process which were demonstrated by 1st Embodiment are performed irrespective of a test subject's respiration type, it is performed also when a test subject is performing the draw-in respiration. Accordingly, the first bar graph BG1 and the second bar graph BG2 shown in FIG. 26 are also displayed in the case of draw-in respiration. Therefore, the subject can confirm the magnitude of the draw-in breath that he / she is performing by looking at the level meter indicating the magnitude of the chest-type breathing in the first bar graph BG1.

The biometric apparatus 1 may determine draw-in respiration by the following method.
[Method 1] As shown in FIG. 30, in the case of draw-in respiration, only the amplitude reference level of the second bioelectric impedance Zb in the middle of the trunk is shifted upward in comparison with the case of chest respiration or abdominal respiration. Therefore, the CPU 170 has a first centering value Za0 indicating the amplitude reference level of the first bioelectrical impedance Za in the upper trunk and a second centering value Zb0 indicating the amplitude reference level of the second bioelectrical impedance Zb in the middle of the trunk. When only the second centering value Zb0 increases by a predetermined value (for example, 0.5Ω) or more, it is determined that it is a draw-in respiration.

[Method 2] As shown in FIG. 30, in the case of draw-in respiration, the amplitude value (maximum value-minimum value) of the first bioelectric impedance Za and the second bioelectricity are compared with those in the case of chest respiration or abdominal respiration. The amplitude value (maximum value−minimum value) of the impedance Zb becomes smaller. Therefore, in order to be able to determine whether or not it is a draw-in breath from these amplitude values, a threshold value is determined for the amplitude value and stored in the first storage unit 120. Then, the CPU 170 monitors the amplitude value of the first bioelectrical impedance Za and the amplitude value of the second bioelectrical impedance Zb, both amplitude values are equal to or less than a threshold value (for example, 1.8Ω), and described above. When only the second centering value Zb0 is increased by a predetermined value or more by [Method 1], it is determined that it is a draw-in breath. The first storage unit 120 may store two threshold values for the first bioelectric impedance Za and the second bioelectric impedance Zb, or may store one threshold value shared by both. Also good.

[Method 3] In the case of draw-in respiration, the measurement waveform of the first bioelectrical impedance Za and the measurement waveform of the second bioelectrical impedance Zb show the same characteristics as those in the case of chest respiration. That is, in inspiration, both the first bioelectrical impedance Za and the second bioelectrical impedance Zb change in an increasing direction, and in expiration, both the first bioelectrical impedance Za and the second bioelectrical impedance Zb change in a decreasing direction. Therefore, the CPU 170 monitors the measurement waveform of the first bioelectrical impedance Za and the measurement waveform of the second bioelectrical impedance Zb, both of the measurement waveforms exhibit the same characteristics as in the case of chest type respiration, and When only the second centering value Zb0 is increased by a predetermined value or more by the [Method 1], it is determined that the breath is a draw-in breath.

<3. Third Embodiment>
For example, by displaying a Lissajous figure obtained from the waveform of the first bioelectrical impedance Za and the waveform of the second bioelectrical impedance Zb in one respiration for each respiration of the subject, the current respiration is a chest respiration It can also be set as the aspect which alert | reports to a test subject which of the dependence of abdominal respiration is high. Here, when the subject's breathing is chest breathing, as shown in FIG. 10, both the first bioelectrical impedance Za and the second bioelectrical impedance Zb change in an increasing direction during inhalation, and the first bioelectrical impedance during exhalation. Both Za and the second bioelectric impedance Zb change in a decreasing direction. Therefore, the Lissajous figure for one breath in this case is, for example, as shown in FIG. That is, when the ratio of chest-type breathing to one breath is extremely high, a Lissajous figure that draws a substantially linear locus is obtained.

  On the other hand, when the subject's breathing is abdominal breathing, as shown in FIG. 9, both the first bioelectrical impedance Za and the second bioelectrical impedance Zb change in an increasing direction during inspiration, and the first bioelectrical impedance Za during exhalation. Changes in the decreasing direction, while the second bioelectrical impedance Zb changes in the increasing direction. Therefore, the Lissajous figure in this case is as shown in FIG. 33, for example. That is, when the subject's breathing includes abdominal breathing, a Lissajous figure that draws a locus of a bent shape, such as a “Boomerang” type, is obtained.

  In this aspect, by displaying a Lissajous figure indicating the state of one breath immediately before the subject, the subject can easily recognize whether his or her breathing is chest or abdominal breathing. And in this aspect, since it is not necessary to perform the above-mentioned respiration analysis processing, there exists a remarkable effect that a subject's respiration type can be presumed with simple composition. In addition, for example, the subject can bring the respiration closer to the chest-type respiration by respiring while conscious of bringing the Lissajous figure form closer to a straight line. That is, the display of the Lissajous figure can be used as biofeedback information for breathing exercise training.

  Here, as shown in FIG. 32 and FIG. 33, the aspect of displaying the Lissajous figure indicating the state of one breath immediately before the subject has been described. It is also possible to display a Lissajous figure based on each data (first bioelectric impedance Za, second bioelectric impedance Zb) of multiple breaths. When the proportion of chest breathing in the subject's breathing is high (when the chest breathing dependency is high), for example, a Lissajous figure as shown in FIG. 34 is obtained, while the subject breathing includes abdominal breathing. In this case, for example, a Lissajous figure as shown in FIG. 35 is obtained. Further, for example, a Lissajous figure obtained from the waveform of the first relative value ΔZa and the waveform of the second relative value ΔZb in each breath may be displayed for each breath of the subject.

  The case where a Lissajous figure is displayed will be described in detail below. Since the hardware configuration of the biometric apparatus is basically the same as that described in the first embodiment, the same reference numerals as those in the first embodiment are used and description thereof is omitted.

<3-1: Display of Lissajous figure>
FIG. 36 is a flowchart showing the contents of the Lissajous figure display process.
In the flowchart shown in the figure, the processing from step S801 to S804 is the same as the processing from step S10 to S40 of the respiratory analysis processing (FIG. 14) described in the first embodiment. That is, also in this embodiment, when the sampling timing is reached (step S801: YES), the CPU 170 controls the bioelectrical impedance measuring unit 200 to measure the first bioelectrical impedance Za and the second bioelectrical impedance Zb (step S801). S802, S803). Further, the CPU 170 performs a smoothing process on the measured value of the first bioelectric impedance Za and the measured value of the second bioelectric impedance Zb (step S804).

  Thereafter, the CPU 170 generates display data of a Lissajous figure having, for example, the X axis as the second bioelectric impedance Zb and the Y axis as the first bioelectric impedance Za (step S805). Here, the second storage unit 130 is provided with a Lissajous figure drawing area. This Lissajous figure drawing area is a storage area for temporarily storing display data of the Lissajous figure displayed on the display unit 160. When generating the display data of the Lissajous figure, the CPU 170 uses the measured value (X coordinate value) of the second bioelectrical impedance Zb and the measured value (Y coordinate value) of the first bioelectrical impedance Za in the Lissajous figure drawing area. Plot dots at fixed positions and update the locus of the Lissajous figure. Further, the CPU 170 reads the display data of the Lissajous figure from the Lissajous figure drawing area, outputs it to the display unit 160, and displays the Lissajous figure on the display unit 160 (Step S806). Since the processing shown in the figure is performed at every sampling timing, the locus of the Lissajous figure is updated at every sampling timing in step S805. The display of the Lissajous figure is also updated at every sampling timing.

  Therefore, when the subject is breathing, the Lissajous figure is displayed on the display unit 160 in real time. For example, when the proportion of chest breathing is extremely high, the Lissajous figure shown in FIGS. 32 and 34 is displayed. When the subject's breathing includes abdominal breathing, the Lissajous figure shown in FIGS. 33 and 35 is displayed. In addition, when the subject's breathing gradually changes from the chest type to the abdominal type, for example, as shown in FIG. Elongates and changes to a bent shape.

  As shown in FIG. 32 and FIG. 34, when the proportion of chest breathing is extremely high, the locus of the Lissajous figure becomes a straight line that rises to the right. Also, if the chest breathing is shallow, the locus of the Lissajous figure becomes small, and if the chest breathing is deep, the locus of the Lissajous figure becomes large.

  On the other hand, as shown in FIGS. 33 and 35, when the subject's breathing includes abdominal breathing, the locus of the Lissajous figure becomes a bent shape. Note that the Lissajous figure shown in FIG. 33 is a case where the ratio of the chest breathing and the abdominal breathing to one breath is 50%. In this case, the locus of the Lissajous figure has a boomerang shape ("<" shape), and the shape of the locus is almost symmetrical vertically. However, if the proportion of abdominal breathing is lower than that of chest breathing, the locus of the Lissajous figure will be larger in the proportion of the straight line that goes up to the right corresponding to the locus of chest breathing, and the part bent from there The proportion of the straight line portion (lower straight line in FIG. 33) is reduced. On the other hand, if the proportion of abdominal breathing is higher than that of chest breathing, the locus of the Lissajous figure becomes smaller in the proportion of the straight line that goes up to the right corresponding to the locus of chest breathing, and then bends from there. The proportion of the part increases. In this way, when the subject's breathing includes abdominal breathing, the trajectory of the Lissajous figure varies in bending shape depending on the ratio of chest breathing and abdominal breathing.

  Theoretically, when the rate of abdominal breathing is 100%, the locus of the Lissajous figure is a straight line that is inclined in the opposite direction to the locus of the chest breathing (in the case of FIG. 33, a straight line that descends to the right). )become. However, for example, even when the abdomen is recessed or inflated with the breath stopped and no chest breathing performed, the lungs contract and expand with the diaphragm above and below, Except when the diaphragm does not function at all due to disease or the like, chest breathing is always included when the subject breathes. Therefore, in fact, no matter how high the proportion of abdominal breathing is, the Lissajous figure's trajectory always includes a straight line that rises to the right, corresponding to the trajectory of chest breathing, and is bent. It becomes a shape. Further, as shown in FIG. 33, how much the bent portion (approximate straight line LN2) is bent with respect to the straight upward part (approximate straight line LN1) corresponding to the trajectory in the case of chest breathing. The bend angle AG is smaller when the abdominal breathing is shallow, and is larger when the abdominal breathing is deep. Also, in the case of abdominal breathing, the trajectory of the Lissajous figure becomes smaller when breathing is shallow, and the trajectory of the Lissajous figure becomes larger when breathing is deep.

  Thus, the shape of the locus of the Lissajous figure is different between the chest breathing and the abdominal breathing. Further, the size and shape of the locus of the Lissajous figure changes depending on the magnitude (depth) of chest-type breathing and abdominal-type breathing. Therefore, the subject can look at the Lissajous figure to determine whether their current breathing is chest or abdominal breathing, or whether their current breathing is more of the chest or abdominal breathing. Can be grasped. In addition, the magnitude of chest breathing and abdominal breathing can be grasped from the Lissajous figure.

  In addition, when the subject performs chest-type breathing training, the subject may breathe consciously so that the locus of the Lissajous figure becomes a straight line that rises to the right and the size thereof increases. Further, when abdominal breathing exercises are performed, breathing may be performed with an awareness that the locus of the Lissajous figure is bent and the size and bending angle AG are increased. If breathing training can be performed while looking at the Lissajous figure in this way, the training can be advanced while confirming whether or not chest breathing and abdominal breathing are correctly performed and their sizes as needed.

  Further, when the subject's breathing is draw-in breathing, as described with reference to FIG. 30 in the second embodiment, both the first bioelectrical impedance Za and the second bioelectrical impedance Zb change in an increasing direction during inspiration, and expiration Then, both the first bioelectrical impedance Za and the second bioelectrical impedance Zb change in a decreasing direction. This change is the same as for chest breathing. This is because in the case of draw-in breathing, exhalation and inhalation are performed by chest breathing while maintaining a state where the abdomen is recessed. However, in the case of draw-in respiration, since force is applied to the abdomen to dent the abdomen, the amplitude reference level of the second bioelectrical impedance Zb is higher than that in the case of chest respiration as shown in FIG. . For this reason, when comparing the Lissajous figures in the case of draw-in breathing and chest breathing, as shown in FIG. 45, both trajectories are linearly rising to the right, but the axis to which the second bioelectric impedance Zb is assigned. The position of the locus is shifted in the direction (X-axis direction in FIG. 45).

  Therefore, the subject can grasp whether or not his / her respiration is a draw-in respiration by looking at the Lissajous figure. In the case of draw-in breathing, the trajectory of the Lissajous figure becomes smaller if the breathing is shallow, and the trajectory of the Lissajous figure becomes larger if the breathing is deep. Therefore, the magnitude of the draw-in breath can also be grasped from the Lissajous figure. Also, in the case of draw-in breathing, training can be carried out while confirming whether or not the draw-in breathing is correctly performed and the size thereof by performing training while looking at the Lissajous figure.

  If the Lissajous figure can be displayed as described above, the subject can correct his / her current breathing type and size as well as chest, abdominal and draw-in breathing while training breathing. It is possible to grasp whether or not. In addition, it is possible to objectively grasp the type and size of respiration, or whether chest respiration, abdominal respiration, and draw-in respiration are correctly performed based on the measured value of bioelectrical impedance. Therefore, it becomes possible to train respiration efficiently.

  In addition, respiratory training (for example, transverse abdominal muscles, diaphragm, internal intercostal muscles, external intercostal muscles, sternocleidomastoid muscles, anterior oblique muscles, mid oblique muscles, posterior oblique muscles) , Straight abdominal muscle, internal oblique muscle, external oblique muscle, etc.) can be effectively trained. In particular, the transverse abdominal muscles included in the respiratory muscles are trunk muscles that greatly affect not only breathing but also motor function. In addition, draw-in breathing can reinforce not only the respiratory muscles but also the inner muscles of the trunk, such as the spine standing muscles. Therefore, breathing exercises are effective not only for improving respiratory function, but also for strengthening motor function, improving / preventing back pain, and dieting. Also, for example, breathing exercises such as taking deep breaths (deep abdominal breathing) or making exhalation longer than inspiration can lead to a more relaxed state by increasing the function of parasympathetic nerves. It also has the effect of improving mental and physical health.

  In addition, the biometric device 1 only needs to measure the first bioelectrical impedance Za and the second bioelectrical impedance Zb and display a Lissajous figure showing the change over time of both, and the respiratory analysis described in the first embodiment Among the processes (FIG. 14), the first centering process (step S50), the first relative value calculation process (step S60), the second relative value calculation process (step S70), and the ΔRib / ΔAb estimation calculation process (step S80) are performed. Since it is not necessary to perform, the control structure of the biometric apparatus 1 can be simplified.

  Respiratory training includes, for example, rehabilitation performed for the purpose of recovering reduced respiratory function in patients with respiratory diseases, training performed for the purpose of strengthening motor functions by athletes, and respiratory function and physical and mental health for healthy individuals. Training that is performed for the purpose of improving the state, training that is performed by a healthy person for the purpose of improving respiratory function that has decreased due to smoking, lifestyle-related diseases, lack of exercise, aging, and the like.

  32 to 35 and FIG. 37 exemplify a Lissajous figure in which the X axis is the second bioelectric impedance Zb and the Y axis is the first bioelectric impedance Za, the Lissajous figure is the X axis and the Y axis. May be replaced. For example, FIG. 38 is a Lissajous figure (in the case of abdominal breathing) in which the X axis is the first bioelectric impedance Za and the Y axis is the second bioelectric impedance Zb, but the X axis and the Y axis may be interchanged. The locus of the Lissajous figure is bent. In the case of the Lissajous figure in which the X axis and the Y axis are interchanged in this way, when the subject's breathing gradually changes from the chest type to the abdominal type, for example, as shown in FIG. From the straight line shape, the lower part gradually expands while bending upward and changes to a bent shape. Further, the Lissajous figure may be obtained by inclining the X axis and the Y axis by 45 degrees as shown in FIG. In short, any Lissajous figure may be used as long as one of the two axes orthogonal to each other is the first bioelectrical impedance Za and the other axis is the second bioelectrical impedance Zb.

<3-2: Display of Lissajous figure for right lung and Lissajous figure for left lung>
A Lissajous figure for the right lung and a Lissajous figure for the left lung may be displayed so that the difference in ventilation capacity between the left and right lungs can be grasped. Here, in order to generate a Lissajous figure for the right lung, the first bioelectrical impedance Za includes the upper right limb shown in FIG. 4D, that is, the trunk including the upper part of the subject's right lung and not including the abdomen. It is necessary to measure the bioelectrical impedance on the upper right side. Moreover, in order to generate a Lissajous figure for the left lung, as the first bioelectrical impedance Za, the upper left trunk shown in FIG. 4E, that is, the upper part of the trunk including the upper part of the subject's left lung and not including the abdomen It is necessary to measure the bioelectrical impedance on the left side. That is, in order to display two Lissajous figures for the right lung and the left lung, 3 of the bioelectrical impedance on the upper right side of the trunk, the bioelectrical impedance on the left side of the upper trunk, and the bioelectrical impedance on the middle part of the trunk. One needs to be measured.

  Hereinafter, in the present specification, when displaying two Lissajous figures for the right lung and the left lung, the bioelectric impedance on the right side of the upper trunk is referred to as a first bioelectric impedance ZaR, and the bioelectricity on the left side of the upper trunk is displayed. The impedance is expressed as a second bioelectric impedance ZaL, and the bioelectric impedance in the middle of the trunk is expressed as a third bioelectric impedance Zb.

  When displaying two Lissajous figures for the right lung and left lung, the CPU 170 appropriately selects the current electrodes X1 to X4 and the voltage electrodes Y1 to Y4 in steps S802 and S803 of the Lissajous figure display process (FIG. 36). While switching, the first bioelectrical impedance ZaR, the second bioelectrical impedance ZaL, and the third bioelectrical impedance Zb are measured. For example, when measuring the first bioelectrical impedance ZaR, the CPU 170 controls the electrode switching circuit 252 so as to select the current electrode X3 for the left hand and the current electrode X4 for the right hand, and the voltage electrode Y2 for the right foot. And the right-hand voltage electrode Y4 are controlled. The CPU 170 outputs current data Di indicating the magnitude of the reference current Iref flowing between the right hand and the left hand, and voltage data Dv indicating the potential difference between the right foot voltage electrode Y2 and the right hand voltage electrode Y4. From the above, the first bioelectric impedance ZaR on the upper right side of the trunk is measured. When measuring the second bioelectrical impedance ZaL, the CPU 170 controls the electrode switching circuit 252 so as to select the current electrode X3 for the left hand and the current electrode X4 for the right hand, and the voltage electrode Y1 for the left foot. And the left-hand voltage electrode Y3 are controlled. The CPU 170 outputs current data Di indicating the magnitude of the reference current Iref flowing between the right hand and the left hand, and voltage data Dv indicating the potential difference between the left foot voltage electrode Y1 and the left hand voltage electrode Y3. From the above, the second bioelectric impedance ZaL on the upper left side of the trunk is measured.

  Next, in step S804, the CPU 170 performs a smoothing process on the measured value of the first bioelectrical impedance ZaR, the measured value of the second bioelectrical impedance ZaL, and the measured value of the third bioelectrical impedance Zb. In step S805, the CPU 170, for example, a right lung Lissajous figure having the X-axis as the third bioelectrical impedance Zb and the Y-axis as the first bioelectrical impedance ZaR, and the X-axis as the third bioelectrical impedance Zb. Display data is generated for a Lissajous figure for the left lung having the Y axis as the second bioelectrical impedance ZaL. In step S806, CPU 170 outputs display data of two Lissajous figures for right lung and left lung to display unit 160.

  In this case, since two Lissajous figures for the right lung and the left lung can be displayed, the type and size of breathing can be grasped for each left and right lung. Also, by comparing the two Lissajous figures, it is possible to easily grasp the difference in ventilation capacity between the left and right lungs. Further, by displaying two Lissajous figures for the right lung and the left lung, it becomes possible to perform breathing training for each of the left and right lungs. In the case of a healthy person, there is almost no difference in ventilation capacity between the left and right lungs. For example, a person with a disease in one lung has a large difference in ventilation capacity between the left and right lungs. Also, those who have experienced lung disease in the past may have differences in ventilation capacity between the left and right lungs. For example, if you want to increase the ventilation capacity of the left lung, such as when the ventilation capacity of the left lung is lower than the right lung, turn the left arm behind the right shoulder and push the left elbow back with the right hand to the left lung. By giving a load and breathing while maintaining this state, the ventilation ability of the left lung can be intensively trained.

  By the way, the two Lissajous figures for the right and left lungs may be displayed side by side. However, in order to make it easier to grasp the difference in the ventilation capacity between the left and right lungs, they are overlapped as shown in FIG. It is good to display. In this case, the CPU 170 only has to draw the Lissajous figure for the right lung and the Lissajous figure for the left lung in the Lissajous figure drawing area. In addition, when two Lissajous figures for the right and left lungs are displayed in a superimposed manner, the Lissajous figure for the right lung and the Lissajous figure for the left lung are displayed so that they can be easily distinguished from each other. It is preferable to change the display mode of the trajectory. For example, when the CPU 170 generates display data of two Lissajous figures for the right lung and the left lung, the locus color is set to blue for the Lissajous figure for the right lung, and the locus for the Lissajous figure for the left lung. The color of can be red. In addition to changing the color of the trajectory, the CPU 170 can change, for example, the thickness of the line indicating the trajectory and the line type (for example, a solid line and a broken line). When two Lissajous figures for the right lung and the left lung are displayed side by side, the display mode of the trajectory of both may be changed.

  In addition, as shown in FIG. 41, the difference between the two Lissajous figures for the right lung and the left lung may be highlighted. In this case, the CPU 170, for example, the Lissajous figure for the right lung determined by the measured value (X coordinate value) of the third bioelectrical impedance Zb and the measured value (Y coordinate value) of the first bioelectrical impedance ZaR at each sampling timing. Coordinates on the Lissajous figure for the left lung determined by the upper coordinates (XR, YR), the measured value (X coordinate value) of the third bioelectrical impedance Zb, and the measured value (Y coordinate value) of the second bioelectrical impedance ZaL Compare with (XL, YL). Then, when the two are different, the CPU 170 generates display data of a bar (straight line) connecting the coordinates (XR, YR) and the coordinates (XL, YL). Thus, if the difference between the two Lissajous figures for the right lung and the left lung can be highlighted and displayed, it becomes easy to grasp the difference in the ventilation capacity between the left and right lungs.

  Note that the CPU 170 may change the color of the bar between the expiration phase and the inspiration phase. In the measurement waveform of the first bioelectric impedance Za shown in FIG. 20, the portion above the first centering value Za0 is the inspiratory phase, and the portion below the first centering value Za0 is the expiration phase. Therefore, for example, when the average value of the first centering value Za0 in the immediately preceding one breath is a straight line portion indicated by a two-dot difference line in FIG. 41, the color of the bar may be changed above and below this straight line. However, in order to change the color of the bar between the expiration phase and the inspiration phase in this way, it is necessary to perform the first centering process described in the first embodiment for the first bioelectric impedance ZaR. Alternatively, the second centering process described in the first embodiment needs to be performed on the second bioelectrical impedance ZaL instead of the first bioelectrical impedance ZaR.

  Further, the CPU 170 compares the coordinates (XR, YR) and the coordinates (XL, YL) at the same sampling timing, and determines whether the color obtained by subtracting the other X coordinate value from one X coordinate value is positive or negative. Or the bar color may be changed depending on whether the solution obtained by subtracting the other Y coordinate value from one Y coordinate value is positive or negative. Further, the CPU 170 may compare the coordinates (XR, YR) and the coordinates (XL, YL) at the same sampling timing, and change the color tone of the bar according to the distance between the two coordinates. For example, the color can be darkened if the distance between the two coordinates is large, and the color can be lightened if the distance between the two coordinates is small. Further, instead of displaying the bar, the CPU 170 may fill the area displaying the bar with a light color.

  Further, the CPU 170 obtains a difference area between the two Lissajous figures for the right lung and the left lung (the area where the bar is displayed in FIG. 41), and how much the ventilation capacity is in the left and right lungs from the size of the difference area. For example, the difference may be classified into five levels and notified to the subject. In this case, the sum of bars (difference lines) may be used instead of the difference area. Further, as shown in FIG. 42, the CPU 170 calculates an intermediate coordinate between the coordinates (XR, YR) and the coordinates (XL, YL) at each sampling timing, and plots a dot at this position. The average value of the two Lissajous figures may be displayed. In addition, when the CPU 170 displays two Lissajous figures for the right lung and the left lung side by side, for example, a portion different from the locus of the left lung Lissajous figure among the locus of the right lung Lissajous figure is thicker. While highlighting with a line, a portion different from the locus of the Lissajous figure for the right lung among the locus of the Lissajous figure for the left lung may be highlighted with a thicker line.

  In addition, for the Lissajous figure for the right lung and the Lissajous figure for the left lung, the X axis and the Y axis can be interchanged, and one of the two axes orthogonal to each other is defined as the first bioelectric impedance ZaR. (Or the second bioelectric impedance ZaL) may be a Lissajous figure having the other axis as the third bioelectric impedance Zb. 40 to 42 show a Lissajous figure in the case of abdominal breathing, but it may be a Lissajous figure in the case of chest breathing or draw-in breathing. Further, only one of the two Lissajous figures for the right lung and the left lung may be displayed. For example, when performing a breathing exercise on the right lung, the subject can operate the input unit 150 to instruct to display only the Lissajous figure for the right lung. In this case, the CPU 170 measures the first bioelectrical impedance ZaR and the third bioelectrical impedance Zb in the Lissajous graphic display process, generates only the Lissajous graphic for the right lung, and displays it on the display unit 160.

<3-3: Centering of display position>
The display position of the Lissajous figure can be centered using the first centering value Za0 and the second centering value Zb0 described in the first embodiment. Hereinafter, a case of a Lissajous figure in which the X axis is the second bioelectric impedance Zb and the Y axis is the first bioelectric impedance Za will be described as an example.

  First, after finishing the smoothing process (step S804) in the Lissajous figure display process shown in FIG. 36, the CPU 170 performs the processes from step S50 to step S70 of the breath analysis process (FIG. 14) described in the first embodiment. The first centering value Za0 and the second centering value Zb0 are extracted. As is clear from FIG. 20, the first centering value Za0 indicates the amplitude reference level of the measurement waveform of the first bioelectrical impedance Za, and the second centering value Zb0 is the measurement of the second bioelectrical impedance Zb. Indicates the amplitude reference level of the waveform.

  Further, when the CPU 170 generates display data of the Lissajous figure in step S805 of the Lissajous figure display process, as shown in FIG. The drawing position of the Lissajous figure drawn in the Lissajous figure drawing area is corrected so that (Zb0, Za0) is positioned at the center of the Lissajous figure display area 160A for displaying the Lissajous figure on the display unit 160. In this way, since the Lissajous figure can be displayed at the center of the Lissajous figure display area 160A, the Lissajous figure can be easily seen.

  Since the first centering value Za0 and the second centering value Zb0 are values obtained by performing the moving average process, even if the display position is centered at each sampling timing, the display position of the Lissajous figure is a short time interval. The problem of sudden changes does not occur. However, if the display position of the Lissajous figure is centered at each sampling timing, the processing load increases. Therefore, for example, for each breath, the display position of the Lissajous figure may be centered using the average value of the first centering value Za0 and the average value of the second centering value Zb0 in the immediately preceding one breath. In addition, for each predetermined measurement interval (for example, 20 seconds), the display position of the Lissajous figure is centered using the average value of the first centering value Za0 and the average value of the second centering value Zb0 in the immediately preceding measurement interval. May be. Thus, the timing for centering the display position of the Lissajous figure can be arbitrarily determined.

  Further, the display position of the Lissajous figure can be centered by adjusting the display range of the X axis and the display range of the Y axis. In this case, for example, for each breath, the CPU 170 detects the maximum value and the minimum value of the measurement value of the first bioelectrical impedance Za, and acquires both as the first amplitude value (maximum value, minimum value). Also, the CPU 170 detects the maximum value and the minimum value for each breath of the measured value of the second bioelectrical impedance Zb, and acquires both as the second amplitude value (maximum value, minimum value). Thereafter, the CPU 170 adjusts the display range of the X axis using the second amplitude value, and adjusts the display range of the Y axis using the first amplitude value.

  For example, when the width of the Lissajous figure display area 160A in the X-axis direction is 10, the CPU 170 has a difference between the maximum value and the minimum value of the second amplitude value of about 8 to 9, and the second amplitude value The size and position of the Lissajous figure drawn in the Lissajous figure drawing area are adjusted so that both the maximum value and the minimum value are displayed in the Lissajous figure display area 160A. Similarly, when the width of the Lissajous figure display area 160A in the Y-axis direction is 10, the CPU 170 has a difference between the maximum value and the minimum value of the first amplitude value of about 8 to 9, and the first amplitude value. The size and position in the Y-axis direction of the Lissajous figure drawn in the Lissajous figure drawing area are adjusted so that both the maximum value and the minimum value are displayed in the Lissajous figure display area 160A.

  In this way, for example, as shown in FIG. 44, the Lissajous figure can be displayed in a size that is just right for the Lissajous figure display area 160A. A Lissajous figure can also be displayed at the center of the Lissajous figure display area 160A. This makes it easy to see the Lissajous figure. Note that the timing for adjusting the display range of the two axes can be arbitrarily determined. However, since it is desirable that the entire trajectory for at least one breath fits in the Lissajous figure display area 160A, the CPU 170 may acquire the first amplitude value and the second amplitude value from the measurement waveform for one breath or more.

  By the way, when comparing the Lissajous figures in the case of the draw-in breathing and the chest breathing, as shown in FIG. 45, both of the loci are linearly rising to the right, but the X is assigned the second bioelectrical impedance Zb. The position of the locus is shifted in the axial direction. Here, if centering is frequently performed, the Lissajous figure is always displayed in the center of the Lissajous figure display area 160A, so that it becomes impossible to distinguish the draw-in breath and the chest-type breath from the Lissajous figure. In order to prevent this, centering in the X-axis direction should not be performed so much.

  That is, for example, if the display position of the Lissajous figure is centered using the first centering value Za0 and the second centering value Zb0, the Lissajous figure is centered in the Y-axis direction based on the first centering value Za0. When the process is the first centering process and the process of performing the centering of the Lissajous figure in the X-axis direction based on the second centering value Zb0 is the second centering process, the CPU 170 determines the frequency of the second centering process as the first centering process. The frequency may be less than the frequency of performing the centering process. If the display position is centered in the Lissajous figure using the first amplitude value and the second amplitude value, the process of adjusting the display range of the Y axis using the first amplitude value is the first range adjustment process. When the process of adjusting the display range of the X axis using the second amplitude value is the second range adjustment process, the CPU 170 determines the frequency of performing the second range adjustment process from the frequency of performing the first range adjustment process. Less.

  In this case, for example, the first centering process (or the first range adjustment process) is performed for each breath, while the second centering process (or the second range adjustment process) is performed only once at the start of measurement or the like. It can be avoided. The first centering process (or the first range adjustment process) may be performed every breath, while the second centering process (or the second range adjustment process) may be performed every 30 breaths. The first centering process (or first range adjustment process) may be performed every 8 seconds, while the second centering process (or second range adjustment process) may be performed every 5 minutes.

  In this way, if the centering in the X-axis direction to which the second bioelectrical impedance Zb is assigned is not performed so much, even if the shape of the Lissajous locus is the same, the case of the draw-in breathing and the case of the chest breathing Then, the display position of the locus is shifted in the X-axis direction. Therefore, it becomes possible to distinguish between draw-in breathing and chest breathing from the Lissajous figure. In addition, the power consumption of the biometric device 1 can be reduced by the amount that the frequency of performing the second centering process and the second range adjustment process is reduced. Further, although the frequency is low, the second centering process and the second range adjustment process are performed, so that the Lissajous figure is displayed in the center of the Lissajous figure display area 160A, or just right for the Lissajous figure display area 160A. Lissajous figures can be displayed in size.

  Note that the second bioelectric impedance Zb in the middle of the trunk is less susceptible to artifacts due to movement of the extremities such as the arms, and the variation range of the measured value is relatively stable, compared to the first bioelectric impedance Za in the upper trunk. is doing. For this reason, even if the centering in the X-axis direction to which the second bioelectric impedance Zb is assigned is not performed so frequently, there is almost no problem that the Lissajous figure does not fit in the Lissajous figure display area 160A.

  Further, in the case of a Lissajous figure in which the X axis is the first bioelectric impedance Za and the Y axis is the second bioelectric impedance Zb, the display position in the Y axis direction should not be centered much. . In short, the centering frequency in the axial direction to which the second bioelectrical impedance Zb is assigned among the two axes orthogonal to each other should be less than the centering frequency in the axial direction to which the first bioelectrical impedance Za is assigned. Good. 43 and 44 show a Lissajous figure in the case of abdominal breathing, but it may be a Lissajous figure in the case of chest breathing or draw-in breathing.

  Further, the first bioelectric impedance Za of the upper trunk has a relatively large variation range compared to the second bioelectric impedance Zb of the middle trunk, but this is largely affected by artifacts due to movement of the extremities such as arms. For this reason, even if this is ignored and the frequency of centering is reduced, it does not matter much. Therefore, centering in the axial direction to which the first bioelectrical impedance Za is assigned is performed at a frequency (for example, every 30 breaths or every 5 minutes) for the axial direction to which the second bioelectrical impedance Zb is assigned. Also good. That is, the centering frequency is the same in the axial direction to which the second bioelectrical impedance Zb is assigned and the axial direction to which the first bioelectrical impedance Za is assigned, and the time interval for centering is set every 30 breaths, every 5 minutes, etc. You may spread it out.

<3-4: Trajectory display processing>
As shown in FIG. 34 and FIG. 35, in the case of a Lissajous figure that continuously shows the state of breathing a plurality of times, it is difficult to grasp the latest one-breath trajectory if the trajectory display mode is the same. Therefore, the display mode of the locus of the Lissajous figure may be changed between the latest one breath and the other past breaths.

  For example, when generating the display data of the Lissajous figure, the CPU 170 may darken the color of the latest one respiratory trajectory and lighten the colors of the other past respiratory trajectories as shown in FIG. it can. Further, the CPU 170 may make the latest one respiration trajectory a solid line, and other past respiration trajectories may be a dotted line. The CPU 170 may change the color of the trajectory between the latest one breath and the other past breaths. For example, the CPU 170 determines whether or not a new one breath has started based on the measurement waveform of the first bioelectric impedance Za and the second bioelectric impedance Zb, and when the new one breath starts, the newly started breath The trajectory color for is changed to red, and the color of the previous respiratory trajectory is changed from red to blue.

  CPU 170 may change the display mode of the locus of the Lissajous figure according to the elapsed time. For example, if the color of the trajectory becomes lighter as the elapsed time increases, the new trajectory becomes darker because the new trajectory is darker. In addition, the Lissajous figure is not limited to that shown in FIG. 46, for example, the X axis and the Y axis are interchanged, or the X axis and the Y axis rotated by an arbitrary angle while maintaining an orthogonal state. It may be. 46 shows a Lissajous figure in the case of abdominal breathing, it may be a Lissajous figure in the case of chest breathing or draw-in breathing.

<3-5: Assist display>
As shown in FIG. 47, a Lissajous figure TL indicating a target breathing state may be superimposed on a Lissajous figure ML indicating a subject's breathing state. Hereinafter, in this chapter, a Lissajous figure indicating the breathing state of the subject is referred to as an actually measured Lissajous figure ML, and a Lissajous figure indicating the target breathing state is referred to as a target Lissajous figure TL.

  The target Lissajous figure TL can be generated by processing a past Lissajous figure ML of the subject, such as a measured Lissajous figure ML indicating the state of one breath immediately before the subject. For example, when the subject is practicing chest-type breathing or draw-in breathing, the CPU 170 increases the size of the measured Lissajous figure ML (straight-up linear trajectory) indicating the state of one breath immediately before by 1.1 times. For example, the display data of the target Lissajous figure TL can be used. When the subject is performing abdominal breathing exercise, the CPU 170 enlarges the size of the measured Lissajous figure ML (bent shape trajectory) indicating the state of one breath immediately before by a predetermined magnification, The display data of the target Lissajous figure TL can be generated by adjusting the size of the angle AG.

  In addition, the CPU 170 displays the target Lissajous figure TL in the Lissajous figure display area 160A, while showing the current breathing state of the subject based on the measured value of the first bioelectric impedance Za and the measured value of the second bioelectric impedance Zb. Display data of the actually measured Lissajous figure ML is generated and displayed on the Lissajous figure display area 160A so as to overlap the target Lissajous figure TL. In this way, the subject can perform breathing training while comparing the measured Lissajous figure ML indicating the current state of breathing with the target Lissajous figure TL indicating the state of target breathing. In addition, the subject can acquire the target respiration by performing respiration while keeping the trajectory of the actually measured Lissajous figure ML coincident with the trajectory of the target Lissajous figure TL.

  In addition, the CPU 170 does not process the past measured Lissajous figure ML to generate the target Lissajous figure TL, but the type of breath (chest breathing, abdominal breathing, draw-in breathing, etc.) to be performed by the subject and its size. A target Lissajous figure TL corresponding to the size can also be generated. For example, when it is determined that a small-sized chest-type breath is performed once and then a middle-sized abdominal breath is performed once as a training menu for training breathing, the CPU 170 Generates and displays a target Lissajous figure TL corresponding to a small-sized chest-type breath and displays it, before the subject completes the first breath and takes the next breath. A target Lissajous figure TL corresponding to the abdominal breathing is generated and displayed. In addition, if the timing which displays target Lissajous figure TL is controlled, a test subject's breathing rhythm can also be instruct | indicated. If the assist display for instructing the subject's breathing is performed using the target Lissajous figure TL in this way, the subject can be effectively instructed on the type and size of breathing, the rhythm of breathing, and the like.

  The CPU 170 may change the display mode (for example, color, line type, etc.) of the trajectory between the measured Lissajous figure ML and the target Lissajous figure TL so that both can be easily distinguished. Further, as shown in FIG. 48, the CPU 170 may display a bar on a portion that is different between the locus of the actually measured Lissajous figure ML and the locus of the target Lissajous figure TL, and highlight the difference between the two. Further, the CPU 170 obtains a difference area between the actually measured Lissajous figure ML and the target Lissajous figure TL (an area where a bar is displayed in FIG. 48), and ranks how much the two differ from the size of the difference area, for example, in five levels. You may divide and alert | report to a test subject. In this case, the sum of bars (difference lines) may be used instead of the difference area.

  Further, it is not always necessary to display the measured Lissajous figure ML and the target Lissajous figure TL in an overlapping manner, and both may be displayed side by side. Further, the measured Lissajous figure ML and the target Lissajous figure TL are not limited to those shown in FIGS. 47 and 48, for example, the X axis and the Y axis are exchanged, or the X axis and the Y axis are maintained in an orthogonal state. The shaft may be rotated by an arbitrary angle.

<3-6: Determination of good or bad lung ventilation>
The quality of the lung ventilation ability can be determined from the inclination angle of the locus of the Lissajous figure. For example, as shown in FIG. 49, in the case of chest breathing, the CPU 170 determines the trajectory for one breath (XY determined by the measured value of the first bioelectric impedance Za and the measured value of the second bioelectric impedance Zb obtained at each sampling timing). The approximate straight line LN is obtained from the coordinate values by the least square method or the like. Next, the CPU 170 calculates an angle α formed by the approximate straight line LN and the X axis, and sets this as the inclination angle α of the locus of the Lissajous figure.

  As shown in FIG. 49, when the X-axis is the second bioelectrical impedance Zb and the Y-axis is the first bioelectrical impedance Za, an ellipse indicating a trajectory for one breath rises as the lung ventilation capacity increases ( (The inclination angle α increases and approaches 90 degrees). Conversely, the lower the ventilation capacity of the lung, the lower the ellipse indicating the trajectory for one breath (the inclination angle α decreases and approaches 0 degrees). Therefore, the CPU 170 compares the inclination angle α with a predetermined reference inclination angle β, and determines that the lung ventilation ability is good when the inclination angle α is equal to or larger than the reference inclination angle β, and the inclination angle α is the reference inclination angle. If it is smaller than β, it can be determined that the lungs have poor ventilation capacity. The reference inclination angle β is a threshold value for determining the quality of the lung ventilation ability, and can be determined based on the inclination angle of the trajectory for one breath collected from a large number of subjects in advance. Further, the value of the reference inclination angle β is stored in the first storage unit 120.

  By doing so, it is possible to easily determine whether the lung ventilation ability is good or not from the locus of the Lissajous figure. Note that the inclination angle of the trajectory for one breath varies depending on the posture at the time of measurement, such as standing, sitting, and supine. Therefore, a plurality of values of the reference inclination angle β may be stored in the first storage unit 120 in association with the posture at the time of measurement. In this case, for example, the posture at the time of measurement may be input from the input unit 150, and the value of the reference inclination angle β corresponding to the input posture may be read from the first storage unit 120 and used. Further, the reference inclination angle β stored in the first storage unit 120 is set as a standard value, and the standard value is used as the height, age, sex (step S1 in FIG. 5) input in advance, and the weight measured in advance. You may correct | amend by the calculation using (step S2 of FIG. 5) etc.

  As shown in FIG. 50, when the Lissajous figure is rotated by the coordinate conversion process so that the straight line indicating the reference inclination angle β is vertical, the ellipse indicating the trajectory for one breath is the same as or perpendicular to the vertical direction. It can be determined that the lung ventilation capacity is good when tilted to the left of the direction, and the lung ventilation capacity is poor when tilted to the right of the vertical direction. In the case of abdominal breathing as shown in FIG. 51, an approximate straight line LN is obtained for the portion surrounded by an ellipse indicated by a solid line in the trajectory for one breath, as in the case of chest breathing. The quality of the lung ventilation ability can be determined. In the case of draw-in respiration, the quality of the lung ventilation ability can be determined in the same manner as in the case of chest respiration.

  Further, the locus of the Lissajous figure used for the determination of the quality of the ventilation ability is not necessarily limited to the locus for one breath, and may be the locus for two breaths or the locus for half breaths. Even if a Lissajous figure with the X axis and Y axis swapped, or a Lissajous figure with the X axis and Y axis rotated by an arbitrary angle while maintaining an orthogonal state, the ventilation of the lungs from the inclination angle of the trajectory The ability can be judged. Further, the value of the reference inclination angle β stored in the first storage unit 120 is set to an arbitrary value, and it is determined whether or not the subject's lung ventilation ability is higher than a predetermined reference ability value. Also good.

<3-7: Time axis compression display of respiratory depth graph>
The CPU 170 can extract the respiration depth (respiration level) indicating the respiration depth for each respiration by performing the respiration depth extraction process (FIG. 27) described in the first embodiment. That is, the CPU 170 can extract the breathing depth for each breath based on the measurement value of the first bioelectric impedance Za and the measurement value of the second bioelectric impedance Zb. In addition, the CPU 170 performs a respiration depth normalization process (FIG. 28: step S601) described in the first embodiment on the extracted respiration depth, and then shows a graph showing the temporal change in the respiration depth (hereinafter, respiration depth). Graph) can be generated and displayed on the display unit 160. For example, the respiration depth graph is as shown in FIG.

  By the way, the subject refers to the breathing depth graph in order to grasp how the magnitude (depth) of breathing has changed due to training. At this time, what is particularly important in grasping the change in the magnitude of the breath is the magnitude of the most recent breath. Since the exercise time for breathing is a relatively long time of 10 minutes to several tens of minutes in many cases, when trying to display the entire graph from the start of measurement to the present time on the display unit 160, the graph is displayed. It must be compressed in the time axis direction. At this time, if the entire graph is uniformly compressed, the time resolution is reduced uniformly over the entire measurement section, and it becomes difficult to grasp details about the magnitude of the most recent breath.

  Therefore, when generating the display data of the respiration depth graph, the CPU 170 compresses the time axis of the graph in a non-linear manner and sets an arbitrary time width as one section, and at least one section at the latest and one section at the start of measurement. And the time axis range is different, and the time resolution is higher in the latest one section than in the first section at the start of measurement. For example, the CPU 170 can increase the time resolution in the most recent measurement section by setting the time axis to a logarithmic scale as shown in FIG. In addition, as shown in FIG. 52C, the CPU 170 divides the entire measurement section from the start of measurement to the present into three sections 1 to 3, so that the latest section 1 has the highest time resolution. The time axis range can be changed for each section. In this way, even if the respiration depth graph is compressed and displayed in the time axis direction, the details of the most recent respiration can be easily grasped.

  In the third embodiment described above, centering of the display position, trajectory display processing, assist display, and quality determination of lung ventilation ability can also be performed for the right lung and left lung Lissajous figures. Further, the CPU 170 calculates the first relative value ΔZa and the second relative value ΔZb by performing the processes from step S10 to step S70 of the breath analysis process (FIG. 14) described in the first embodiment, and calculates the first relative value. The display data of the Lissajous figure may be generated using ΔZa and the second relative value ΔZb. That is, the CPU 170 may generate Lissajous graphic display data in which one of the two axes orthogonal to each other is the first relative value ΔZa and the other axis is the second relative value ΔZb.

  Moreover, this embodiment and 1st, 2nd embodiment can be combined suitably. For example, the biometric apparatus 1 may display and display a Lissajous figure and determine whether the subject's breathing is chest or abdominal breathing. In addition, the biometric apparatus 1 may display the Lissajous figure and the bar graphs BG1 and BG2 shown in FIG. In addition, the biometric apparatus 1 may display and display a Lissajous figure and determine whether the subject's breathing is chest breathing, abdominal breathing, or draw-in breathing.

<4. Modification>
The present invention is not limited to the above-described embodiments, and for example, the following modifications are possible. Also, two or more of the modifications shown below can be combined.

(1) Modification 1
CPU170 can also perform the assist alerting | reporting for instruct | indicating a test subject's respiration. For example, the display unit 160 may display the inspiration / expiration rhythm and pattern and the necessary respiration depth in the form of a third bar graph BG3 shown in FIG. As shown in FIG. 53, the number of stages that can be displayed on the third bar graph BG3 is “6”, and the number is divided into three stages on the inspiratory side and three stages on the expiratory side. Here, the greater the number of steps displayed, the greater the required breathing depth. For example, when the number of display steps on the intake side is “1”, that is, when only the first step on the intake side is displayed in color, the subject is informed that a small amount of intake should be performed. Is. In addition, when the number of display steps on the inhalation side is “2”, that is, when the first and second steps on the inhalation side are displayed in color, moderate inspiration should be performed on the subject. This is to be notified. Furthermore, when the number of display stages on the inhalation side is “3”, that is, when the first to third stages on the inhalation side are colored and displayed, a large amount of inhalation should be performed on the subject. This is to notify that there is.

  On the other hand, when the number of display stages on the expiration side is “1”, that is, when only the first stage on the expiration side is displayed in color, it is notified that a small amount of expiration should be given to the subject. To do. In addition, when the number of exhalation-side display stages is “2”, that is, when the exhalation-side first stage and the second stage are displayed in color, moderate exhalation should be performed on the subject. This is to be notified. Furthermore, when the number of display stages on the exhalation side is “3”, that is, when the first to third stages on the exhalation side are colored and displayed, a large amount of exhalation should be performed on the subject. This is to notify that there is.

  For example, if the subject is instructed to perform medium inspiration twice and then perform medium exhalation twice, the display of the third bar graph BG3 changes as shown in FIG. Condition. Here, if the time required for one breath is 2 seconds, it corresponds to instructing to perform two exhalations and two inspirations at a specified breathing level in 4 seconds. This is only an example, and various assist information (inspiratory / expiratory rhythm, pattern and size) can be notified. For example, assist information for guiding the subject's breathing to abdominal breathing can be notified. Further, instead of the display by the third bar graph BG3, a mode of performing voice assist notification or a mode of combining both may be used.

  By performing the assist notification as described above, it is possible to guide the subject to breathe in consideration of the rhythm, pattern, and depth of breathing. In addition, the subject can check his / her current breathing state by looking at the display of the first bar graph BG1 and the second bar graph BG2. In other words, the display of the first bar graph BG1 and the second bar graph BG2 can be used as biofeedback information for breathing exercise training.

(2) Modification 2
As shown in FIG. 55, a schematic diagram of the lungs indicating the magnitude of respiration may be displayed on the display unit 160. In this case, the area of the colored portion of the lung increases as the respiration increases, and the area of the colored portion of the lung decreases as the respiration decreases. This may be displayed based on the measurement result, or may be displayed as breathing guidance information.
Also, an animation image of a person or animal may be displayed to notify the type of breathing and its size. For example, in the case of small chest breathing, an animation image in which the chest is small and repeats expansion and contraction is displayed. In the case of large chest breathing, an animation image in which the chest is large and repeats expansion and contraction is displayed. In the case of small abdominal breathing, an animation image in which the abdomen is small and repeats expansion and contraction is displayed. In the case of large abdominal breathing, an animation image in which the abdomen is large and repeats expansion and contraction is displayed. In the case of small draw-in breathing, an animated image that repeats expansion and contraction is displayed with the abdomen being small and recessed, and in the case of large draw-in breathing, the chest is also greatly expanded with the abdomen greatly recessed. An animation image that repeats shrinkage is displayed. Such animation images may also be displayed based on the measurement results, or may be displayed as breathing instruction information.
If it does in the above way, a measurement result and guidance information can be reported to a subject more easily.

(3) Modification 3
In each of the above-described embodiments, the limb induction eight-electrode method using both hands and both feet as electrode contacts has been described as an example of a current electrode and a voltage electrode, but the present invention is not limited to this. For example, the bioelectrical impedance of the upper trunk may be measured in combination with the limb induction method with the ear electrode.
In this case, by using the ear electrode, the measurement of the bioelectrical impedance of the upper trunk can be performed by one-arm measurement rather than by both-arm measurement. In the case where an ear electrode is used, a combination with sound notification / stimulation such as voice is effective by incorporating the ear electrode into an earphone or a headphone.
In each of the above-described embodiments, the measurement is performed in the standing position. However, the present invention is not limited to this, and the bioelectrical impedance in the toilet seat may be measured. In this case, electrodes can be secured on the toilet seat and handrail. Furthermore, the bioelectrical impedance may be measured in a pocketable or wearable relaxation posture (chair sitting position, etc.). In this case, an electrode can be secured for a handrail such as a massage chair and a footrest.
Furthermore, respiration measurement during bathing is also possible. In this case, electrodes are provided on the bathtub handrail part, the bottom of the bathtub bottom, and the sole contact side part. Current flow becomes dominant because the trunk is made of physiological saline rather than hot water in the bathtub. Therefore, breathing training can be performed in a relaxed state during bathing.
In addition, a sphygmomanometer that is brought into contact with the sphygmomanometer arm band by hand or the like is added to the biometric device 1 of each of the above-described embodiments, and electrodes are placed on the sphygmomanometer to change breathing or torso muscle tension. May be used as correction information during blood pressure measurement.
It is also desirable that the subject can perform breathing training in a relaxed state. Therefore, during breathing exercises, you can display an idyllic landscape image, play peaceful music, bird calls, waterfall sounds, etc., or adjust the temperature and humidity of the place where breathing exercises are performed It is also important. In addition, breathing exercise training videos may be added to increase training efficiency.

(4) Modification 4
In each of the embodiments described above, the CPU 170 calculates the potential difference between the current data Di indicating the magnitude of the reference current Iref flowing between the right hand and the left hand and the voltage electrode Y2 for the right foot and the voltage electrode Y4 for the right hand. Although the bioelectrical impedance of the upper right limb is measured from the voltage data Dv shown, the measurement method of the first bioelectrical impedance Za of the upper trunk including the upper part of the lung and not including the abdomen is arbitrary. It is. For example, from the current data Di indicating the magnitude of the reference current Iref flowing between the right hand and the left hand and the voltage data Dv indicating the potential difference between the voltage electrode Y1 for the left foot and the voltage electrode Y3 for the left hand, Alternatively, the bioelectric impedance may be measured and used as the first bioelectric impedance Za.
Further, in each of the above-described embodiments, the CPU 170 determines between the current data Di indicating the magnitude of the reference current Iref flowing between the left foot and the right hand, and the voltage electrode Y3 for the left hand and the voltage electrode Y2 for the right foot. The second bioelectric impedance Zb of the middle trunk is measured from the voltage data Dv indicating the potential difference. However, the second bioelectric impedance Zb of the middle trunk including the middle lower part and the abdomen of the lung is not limited thereto. The measuring method is arbitrary. For example, from the current data Di indicating the magnitude of the reference current Iref flowing between the right foot and the left hand and the voltage data Dv indicating the potential difference between the voltage electrode Y4 for the right hand and the voltage electrode Y1 for the left foot, the trunk The bioelectrical impedance that crosses the middle part diagonally may be measured and used as the second bioelectrical impedance Zb.

  In addition, without using the limb-guided eight-electrode method, the current electrode and the voltage electrode are directly attached to the trunk of the subject, the bioelectric impedance of the upper trunk including the lung of the subject and not including the abdomen, and the right lung of the subject The bioelectrical impedance of the upper right side of the trunk without including the abdomen, the bioelectrical impedance of the upper left side of the trunk including the left lung of the subject and not including the abdomen, and the bioelectrical impedance of the middle part of the trunk including the abdomen of the subject are measured. Also good.

  Further, when measuring the first to third bioelectric impedances ZaR, ZaL, Zb in order to display the two Lissajous figures for the right lung and the left lung, the CPU 170 causes the first bioelectric impedance Za on the upper trunk to be displayed. The first bioelectrical impedance ZaR or the second bioelectrical impedance ZaL is used as the second bioelectrical impedance Zb, and the third bioelectrical impedance Zb is used as the second bioelectrical impedance Zb in the middle of the trunk to perform the respiratory analysis processing (first embodiment). Thus, the type of breathing of the subject can be determined for the right lung or the left lung. Similarly, the CPU 170 uses the first bioelectric impedance ZaR or the second bioelectric impedance ZaL as the first bioelectric impedance Za of the upper trunk and the third bioelectric impedance as the second bioelectric impedance Zb of the middle trunk. By performing breathing depth extraction processing and breathing level display processing (first embodiment) using Zb, the first bar graph BG1 and the second bar graph BG2 can be displayed for the right lung or the left lung. .

(5) Modification 5
In the above-described respiration level display processing, the CPU 170 normalizes the respiration depth by dividing the respiration depth ΔZap-p in the immediately preceding one breath by the second centering value Zb0 in the one respiration and multiplying by 100. Although the value% ΔZa (= (ΔZap−p / Zb0) × 100) is adopted, the normalization method of the respiration depth ΔZap−p is arbitrary. In short, what is necessary is just to correct | amend the value of respiration depth (DELTA) Zap-p to the value which remove | eliminated the influence of individual differences, such as a physique, between test subjects. For example, MV is an index indicating the amount of skeletal muscle (development of skeletal muscle), H is an index indicating the length of a subject's height or bioelectrical impedance measurement section, and bioelectrical impedance of a site useful for the development of body skeletal muscle When expressed as Zx, a relationship of MV∝H2 / Zx is established, and instead of the second centering value Zb0, the respiration depth ΔZap-p may be normalized using H2 / Zx. In addition, in the estimation of the index MV, accuracy can be improved by including gender, age, weight, and the like as multivariate terms by multiple regression analysis.

(6) Modification 6
For example, the present invention can be applied to a system using a game machine.
FIG. 56 is a diagram showing a configuration of the biometric system 5 using the home game machine 300. As shown in FIG. As shown in the figure, the biological measurement system 5 includes a biological information input device 200 ′, a game machine 300, a controller 350, and a monitor 400. In addition, the optical disk 500 is inserted into the disk slot of the game machine 300.

  The biological information input device 200 ′ includes a platform 20 ′ on which a subject is placed, a left-hand electrode unit 30 </ b> L, and a right-hand electrode unit 30 </ b> R. This biometric information input device 200 ′ has basically the same configuration as the bioelectrical impedance measuring unit 200 shown in FIG. 1, and has a configuration in which a scale is added. The biological information input device 200 ′ is connected to the controller 350 via a communication cable, measures the bioelectrical impedance and body weight of each part of the subject, and supplies the biological information to the game machine 300 via the controller 350. To do.

  The controller 350 is an input device for inputting operation information and the like. The controller 350 communicates with the game machine 300 by wireless communication such as Bluetooth (registered trademark), and transmits operation information input by the subject and biometric information output from the biometric information input device 200 ′ to the game machine 300. For example, information such as height, age, and sex can be input by operating the controller 350. The monitor 400 is, for example, a television receiver, and is connected to the game machine 300 via a communication cable. The optical disc 500 stores programs and data for controlling various processes described in the first to third embodiments and the modifications (1) to (5).

  In the figure, the case where the biological information measured by the biological information input device 200 ′ is supplied to the game machine 300 via the controller 350 is illustrated, but the biological information input device 200 ′ stores the biological information. You may supply directly to the game machine 300 by wireless communication. In this case, the biometric information input device 200 ′ includes a wireless communication module for performing wireless communication with the game machine 300. Further, the biometric information input device 200 ′ may directly supply the biometric information to the game machine 300 through wired communication. In this case, the biological information input device 200 ′ and the game machine 300 may be directly connected with a communication cable. Further, a left-hand controller 350 provided with a current electrode X3 and a voltage electrode Y3 is provided instead of the left-hand electrode portion 30L, while a current electrode X4 and a voltage electrode Y4 are provided instead of the right-hand electrode portion 30R. Alternatively, a right hand controller 350 may be provided.

FIG. 57 is a block diagram showing a configuration of the game machine 300.
As shown in the figure, the game machine 300 includes a ROM 301, a RAM 302, a hard disk 303, a disk drive 310, a wireless communication module 320, an image processing unit 330, an audio processing unit 340, and a CPU 360. The ROM 301 stores a program that performs basic control of the game machine 300. The RAM 302 is used as a work area for the CPU 360. The hard disk 303 stores programs and data read from the optical disc 500 such as a training menu management table TBL (FIG. 58) described later. The disk drive 310 reads programs and data from the optical disk 500. The program and data are not only provided to the game machine 300 by a recording medium such as the optical disc 500, but may be downloaded from a server or the like via a communication network. In this case, the game machine 300 includes a network communication module.

  The wireless communication module 320 controls wireless communication performed with the controller 350. The wireless communication module 320 is an input unit for inputting the biological information measured by the biological information input device 200 ′ to the game machine 300. The image processing unit 330 generates image data and outputs it to the monitor 400. The audio processing unit 340 generates audio data such as sound effects and audio and outputs the audio data to the monitor 400 (speaker). The CPU 360 controls the entire game machine 300 by executing various programs stored in the ROM 301, the hard disk 303, and the like. For example, the CPU 360 can control the wireless communication module 320 and communicate with the biological information input device 200 ′ via the controller 350. Further, the CPU 360 can instruct the biological information input device 200 'to switch the current electrodes X1 to X4 and the voltage electrodes Y1 to Y4, measure the bioelectrical impedance, measure the weight, and the like.

  Further, the CPU 360 can perform, for example, the breath analysis process described in the first embodiment, and can determine whether the subject's breathing is chest breathing or abdominal breathing. In addition, the CPU 360 performs the respiration depth extraction process and the respiration level display process described in the first embodiment, and the first bar graph BG1 indicating the magnitude of chest respiration and abdominal respiration, and the second indicating abdominal respiration level. The bar graph BG2 can be displayed on the monitor 400. In addition, the CPU 360 can perform the suction type determination process described in the second embodiment to determine whether the subject's breathing is chest breathing, abdominal breathing, or draw-in breathing. Further, the CPU 360 can perform the Lissajous figure display processing described in the third embodiment and display the Lissajous figure on the monitor 400. Further, the CPU 360 can perform processing for training the breathing of the subject using the bar graphs BG1 to BG3, the Lissajous figure, the schematic diagram of the lung, and the like. As described above, the CPU 360 can perform various processes described in the first to third embodiments and the modifications (1) to (5).

FIG. 58 is a diagram showing a data configuration of the training menu management table TBL.
The training menu management table TBL is used for allowing the subject to perform breathing training using a training menu suitable for his / her breathing ability. The training menu management table TBL has a training menu for training breathing and a clear condition for clearing this class and proceeding to the next class for each class (rank) determined according to the breathing ability. It is remembered. For example, in the example shown in the figure, five classes from rank 1 to rank 5 are provided. In addition, 20 training menus are prepared for each class.

  For example, as a specific example of the training menu, training to master chest breathing and abdominal breathing, training to master full breathing that combines chest breathing and abdominal breathing, training to master draw-in breathing, Using exercises to increase the ventilation capacity of the lungs by abdominal breathing and complete breathing, training to increase the ventilation capacity of the left and right lungs, training to increase respiratory function and motor function by draw-in breathing, various poses used in yoga etc. The exercise | movement which reinforces a respiratory function and an exercise | movement function by performing various respiration while giving a load to a respiratory muscle can be illustrated.

  Complete breathing is a breathing method that uses the abdomen, chest, and shoulders to make the best use of the ventilation capacity of the lungs and exhale and inhale. For complete breathing, for example, when inhaling, first inhale while inflating the belly, then inhale while expanding the ribcage with the feeling of protruding the chest forward, and finally inhale while raising the shoulder. As a result, the diaphragm is fully opened. When exhaling, on the contrary, first exhale while lowering the shoulder, then exhale while returning the expanded rib cage, and finally exhale while denting the abdomen.

  The training menu uses, for example, a Lissajous figure showing the subject's breathing (or bar graphs BG1 and BG2 showing the subject's breathing and a schematic diagram of the lungs). Using a Lissajous figure (or a bar graph BG3 showing the state of the target breath or a schematic diagram of the lung) that enables the training while confirming, the subject's target breathing That allows training while confirming the state of the subject, a Lissajous figure showing the subject's breathing state (or bar graphs BG1 and BG2 showing the subject's breathing state, and a schematic diagram of the lungs) and the target breathing Using both the Lissajous figure indicating the state (or the bar graph BG3 indicating the state of the target breath and the schematic diagram of the lungs), the subject should compare his breathing state with the target breathing state. It is included, such as those that allows for the training.

  Further, as specific examples of clear conditions, the magnitude of chest breathing or abdominal breathing is greater than or equal to a predetermined reference value, the lung ventilation capacity is greater than or equal to a predetermined reference value, Examples include what can be done, that the abdominal level is equal to or higher than a predetermined level, and that all 20 training menus have been trained. In the training menu management table TBL, the number of classes may be two or more, and the training menu may be one or more for each class. Moreover, the following can be illustrated as a specific example of classification and training content.

[Rank 1 / Training for patients with moderate to advanced respiratory disease]
Rehabilitation training to train the chest respiratory muscles that perform basic thoracic breathing exercises by thoracic breathing to restore respiratory function that has been reduced by respiratory disease.
[Rank 2: Training for patients with mild respiratory disease]
Rehabilitation training for abdominal respiratory muscles such as the diaphragm to be trained by abdominal breathing to restore respiratory function that has been reduced by respiratory disease.
[Rank 3 / Standard training for healthy people]
Complete breathing combined with chest breathing and abdominal breathing to train both chest and abdominal breathing muscles to further improve respiratory function and reduce respiratory function due to smoking, lifestyle-related diseases, lack of exercise, aging, etc. Training to improve.
[Rank 4 / light load training]
Training to strengthen the inner muscles of the trunk (such as transverse abdominal muscles and standing spine muscles) by draw-in breathing, improve respiratory function, and prevent back pain and exercise function.
[Rank 5 / Medium-level load training for athletes]
Training for strengthening motor functions by combining postures that apply stress to respiratory muscles, such as those used in yoga, and draw-in breathing.

  In addition, the training for patients with respiratory diseases listed as ranks 1 and 2 is based on the premise that the medical guidance at the treatment facility is strictly followed. Depending on the level of the disease, the subject is basically a person whose diaphragm functions to some extent and who can expect improvement in respiratory function by training breathing. Moreover, it is possible to combine loads such as breathing while purging the mouth with respect to ranks 1 to 5. In addition, the combination of breathing method and pose, the time distribution of training, and the like can be arbitrarily determined as appropriate.

FIG. 59 is a flowchart showing the contents of the breathing exercise management process.
The breathing training management process shown in the figure is executed by the CPU 360 when, for example, the subject starts breathing training using the system 5. When starting the respiratory training management process, the CPU 360 first performs a process of detecting the breathing ability of the subject (step S901). For example, the CPU 360 notifies a message instructing the subject to perform chest-type breathing or abdominal-type breathing, and also performs the breath analysis processing and breathing depth extraction processing described in the first embodiment, or the Lissajous described in the third embodiment. The quality of the graphic display process and lung ventilation capacity is determined. Thus, the CPU 360 detects, for example, the magnitude of chest breathing or abdominal breathing, lung ventilation ability, abdominal level, and the like as the subject's breathing ability.

  In order to detect the breathing ability of the subject from normal breathing, the process shown in step S901 may be performed without notifying the subject that the breathing is being measured. In step S901, the first bioelectric impedance Za and the second bioelectric impedance Zb may be measured to detect the breathing ability of the subject, or the first to third bioelectric impedances ZaR, ZaL, and Zb may be detected. Measurement may be made to detect the breathing ability of the subject.

  Next, the CPU 360 refers to the training menu management table TBL, and identifies a class corresponding to the subject's breathing ability detected in step S901 (step S902). Further, the CPU 360 selects a training menu corresponding to the specified class from the training menu management table TBL (step S903). For example, when the class of the subject is rank 3, the CPU 360 refers to the training menu management table TBL shown in FIG. 58 and selects the menus 41 to 60.

  Thereafter, the CPU 360 performs a process for training the subject's breathing using the training menu selected in step S903 (step S904). For example, when the class of the subject is rank 3, the CPU 360 performs a process for training breathing using the menus 41 to 60. In addition, when rank 3 is the above-described standard training for healthy persons, the CPU 360 performs training for mastering complete breathing that combines chest breathing and abdominal breathing based on the training menu, and lungs through complete breathing. Provide training to increase ventilation capacity. In addition, the CPU 360 displays, for example, a Lissajous figure indicating the state of breathing of the subject (or bar graphs BG1 and BG2 indicating the state of breathing of the subject or a schematic diagram of the lung) on the monitor 400, and the state of the subject's own breathing. Training can be performed while confirming. In addition, the CPU 360 displays a Lissajous figure (or a bar graph BG3 indicating a target breathing state or a schematic diagram of the lung) on the monitor 400 indicating the target breathing state, and the subject's target breathing state is displayed. Training can be performed while checking. Further, the CPU 360 displays a Lissajous figure (or bar graphs BG1 and BG2 showing the subject's breathing and a schematic diagram of the lung) showing the subject's breathing, and a Lissajous figure (or Both the bar graph BG3 showing the state of breathing and the schematic diagram of the lung) can be displayed on the monitor 400 so that the subject can practice while comparing his breathing state with the target breathing state. .

  Thereafter, the CPU 360 reads a clear condition corresponding to the current class of the subject from the training menu management table TBL, and determines whether the clear condition is satisfied (step S905). For example, when the current class of the subject is rank 3, the CPU 360 reads the condition C from the training menu management table TBL shown in FIG. 58 and determines whether or not the condition C is satisfied.

  For example, when the condition C is “the magnitude of the abdominal breathing is equal to or greater than a predetermined reference value”, the CPU 360 performs the breath analysis process and the breath depth extraction process described in the first embodiment, and the abdomen of the subject. It is determined whether or not the magnitude of the expression breath is equal to or greater than a reference value. When the condition C is “the lung ventilation capacity is equal to or greater than a predetermined reference value”, the CPU 360 determines whether the lung ventilation capacity is good or not as described in the third embodiment. It is determined whether or not it is greater than or equal to the value. On the other hand, when the condition C is “capable of drawing in”, the CPU 360 performs the breathing type determination process described in the second embodiment, and determines whether or not the subject's breathing is draw-in breathing. Further, when the condition C is “finished all 20 training menus”, the CPU 360 determines that the clear condition is satisfied when all the trainings from the menus 41 to 60 have been completed.

  If the result of step S905 is negative, the process returns to step S904, and breathing training in the current class is continued. On the other hand, when the result of step S905 is affirmative, the CPU 360 ranks up the subject's class to the next class (step S906), and then returns to step S903. For example, when the class of the subject is rank 3, the CPU 360 changes the class of the subject to rank 4 in step S906 and returns to step S903. Thereby, a training menu (menu 61 to menu 80) corresponding to rank 4 is selected from the training menu management table TBL, and a new training is started.

  Note that when the subject operates the controller 350 to instruct the end of exercise, the breathing exercise management process shown in FIG. At this time, the CPU 360 stores rank information indicating the current class of the subject in the hard disk 303, and when the subject performs breathing training next time, the rank information stored in the hard disk 303 is read and processed from step S903. To start.

  As described above, according to this modification, by using the game machine 300, it is possible to easily measure respiration in the home in the same way as measuring body weight and body fat. In addition, breathing training can be done easily at home. Further, according to the present modification, the subject can perform respiration training based on the training menu corresponding to his / her respiration ability, so that respiration can be efficiently trained. In addition, the training menu is prepared for each class, and by having the game characteristics of proceeding to the next class while clearing each class, it is possible to perform breathing training while having fun, so subjects for breathing training You can also increase your motivation.

  In addition, you may perform a breathing exercise management process (FIG. 59) in the biometric apparatus 1 demonstrated by 1st-3rd embodiment. In this case, a program for performing a breathing exercise management process, a breathing exercise management table TBL (FIG. 58), and the like may be stored in the first storage unit 120. Further, instead of the game machine 300, a personal computer or a portable electronic device (for example, a mobile phone) may be used. In the case of a portable electronic device, a head mounted display may be used as a display device. .

(7) Modification 7
The biometric apparatus 1 may not include the display unit 160 and may display a Lissajous figure, bar graphs BG1 to BG3, etc. on an external display device. In addition, the biometric device 1 does not include the bioelectrical impedance measuring unit 200, and the first bioelectrical impedance Za and the second bioelectrical impedance Zb (or first to third) measured by an external bioelectrical impedance measuring device. You may provide the input part which inputs bioelectrical impedance ZaR, ZaL, Zb) by radio | wireless communication or wire communication. In this case, the input unit is, for example, a communication interface such as a wireless communication module, a network communication module, or a USB (Universal Serial Bus) interface.

(8) Modification 8
The present invention is not limited to a device or system having only a breathing training function. For example, the present invention can be applied to various training devices and training systems in which a breathing training function is incorporated in a part thereof, such as a fitness training device.

1 Biological Measuring Device 5 Biological Measuring System 120 First Storage Unit 150 Input Unit 170 CPU
200 Bioelectrical impedance measurement unit 200 ′ Biological information input device Za First bioelectrical impedance (upper trunk)
Zb Second bioelectric impedance (mid-trunk)
300 game machine 320 wireless communication module 360 CPU
400 monitors

Claims (34)

A bioelectrical impedance measuring unit for measuring a first bioelectrical impedance of the upper trunk including the lung of the subject and not including the abdomen, and a second bioelectrical impedance of the middle trunk including the abdomen of the subject;
Of the two axes orthogonal to each other, one axis is the first bioelectrical impedance and the other axis is the second bioelectrical impedance, and the measured value of the first bioelectrical impedance and the measured value of the second bioelectrical impedance A display data generation unit for generating display data of a Lissajous figure showing a change over time of
A breathing training apparatus characterized by that. The bioelectrical impedance measuring unit includes a first bioelectrical impedance of an upper trunk that includes an upper part of the subject's lung and does not include an abdomen, and a second bioelectrical part of the trunk that includes the middle lower part and the abdomen of the subject's lung. Measure impedance and
The respiratory training device according to claim 1. A first bioelectrical impedance on the right side of the upper trunk that includes the right lung of the subject and does not include the abdomen; a second bioelectrical impedance on the left side of the upper trunk that includes the left lung of the subject and does not include the abdomen; A bioelectrical impedance measuring unit for measuring a third bioelectrical impedance of the middle trunk including
Of the two axes orthogonal to each other, one axis is the first bioelectrical impedance and the other axis is the third bioelectrical impedance. The measured value of the first bioelectrical impedance and the measured value of the third bioelectrical impedance Display data of a first Lissajous figure showing a change over time of the first bioelectrical impedance, the one axis as the second bioelectrical impedance, the other axis as the third bioelectrical impedance, and the second bioelectrical impedance A display data generation unit that generates display data of a second Lissajous figure indicating a change over time of the measurement value and the measurement value of the third bioelectrical impedance,
A breathing training apparatus characterized by that. The bioelectrical impedance measurement unit includes a first bioelectrical impedance on the right side of the upper trunk that includes the upper part of the subject's right lung and does not include the abdomen, and an upper left side of the trunk that includes the upper part of the left lung of the subject and does not include the abdomen. Measuring the second bioelectrical impedance of the subject and the third bioelectrical impedance of the middle trunk including the middle and lower abdomen of the subject's lung,
The breathing training apparatus according to claim 3. The display data generation unit generates display data of the first Lissajous figure and display data of the second Lissajous figure so that the first Lissajous figure and the second Lissajous figure are displayed in an overlapping manner.
The respiratory training device according to claim 3 or 4, wherein The display data generation unit generates display data of the first Lissajous figure and display data of the second Lissajous figure so that a display mode of the locus of the first Lissajous figure is different from that of the second Lissajous figure. To
The respiratory training apparatus according to any one of claims 3 to 5, wherein the respiratory training apparatus is characterized. A trajectory analysis unit for detecting a difference between the trajectory of the first Lissajous figure and the trajectory of the second Lissajous figure;
The display data generation unit generates display data of the first Lissajous figure and display data of the second Lissajous figure so that the difference is highlighted and displayed;
The respiratory training apparatus according to any one of claims 3 to 6, wherein the respiratory training apparatus is characterized. A centering value generator for generating a first centering value indicating an amplitude reference level of the measurement value of the first bioelectrical impedance and a second centering value indicating the amplitude reference level of the measurement value of the second bioelectrical impedance; Prepared,
The display data generation unit generates display data of the Lissajous figure so that a position on the Lissajous figure determined by the first centering value and the second centering value is a center of a display area for displaying the Lissajous figure. To
The respiratory training device according to claim 1 or 2, wherein A centering value generator for generating a first centering value indicating an amplitude reference level of the measurement value of the first bioelectrical impedance and a second centering value indicating the amplitude reference level of the measurement value of the second bioelectrical impedance; Prepared,
The display data generation unit, as a process performed when generating the display data of the Lissajous figure, a first centering process for centering the Lissajous figure in the one axial direction based on the first centering value; A second centering process for performing centering in the other axial direction of the Lissajous figure based on a second centering value;
The frequency of performing the second centering process is less than the frequency of performing the first centering process;
The respiratory training device according to claim 1 or 2, wherein An amplitude value specifying unit for specifying a first amplitude value indicating the amplitude of the measurement value of the first bioelectrical impedance and a second amplitude value indicating the amplitude of the measurement value of the second bioelectrical impedance;
The display data generation unit adjusts the range of the two axes using the first amplitude value and the second amplitude value, and generates display data of the Lissajous figure.
The respiratory training device according to any one of claims 1, 2, 8, and 9. An amplitude value specifying unit for specifying a first amplitude value indicating the amplitude of the measurement value of the first bioelectrical impedance and a second amplitude value indicating the amplitude of the measurement value of the second bioelectrical impedance;
The display data generation unit performs a process for generating display data of the Lissajous figure, a first range adjustment process for adjusting a range of the one axis using the first amplitude value, and the second amplitude. A second range adjustment process for adjusting the range of the other axis using a value,
The frequency of performing the second range adjustment process is less than the frequency of performing the first range adjustment process.
The respiratory training device according to any one of claims 1, 2, 8, and 9. The display data generation unit generates the display data of the Lissajous figure so that the display mode of the locus of the Lissajous figure is different between the latest one breath and the other past breaths.
The breathing training apparatus according to any one of claims 1, 2, and 8 to 11. The display data generation unit generates display data of the Lissajous figure so that a display mode of a locus of the Lissajous figure changes according to an elapsed time;
The breathing training apparatus according to any one of claims 1, 2, and 8 to 11. The display data generation unit generates display data of the Lissajous figure, and generates display data of a Lissajous figure for breathing guidance according to a target breathing type and the magnitude of the breathing.
The respiratory training apparatus according to any one of claims 1, 2, and 8 to 13. An inclination angle calculation unit for calculating an inclination angle of the locus of the Lissajous figure;
A ventilation capability determination unit that compares the inclination angle calculated by the inclination angle calculation unit with a predetermined reference inclination angle to determine the quality of the lung ventilation capability;
The respiratory training apparatus according to any one of claims 1, 2, and 8 to 14. A breathing depth extraction unit that extracts a breathing depth in one breath for each breath of the subject, based on the measured value of the first bioelectrical impedance and the measured value of the second bioelectrical impedance;
A graph generation unit that generates display data of a graph indicating temporal changes in the respiration depth extracted by the respiration depth extraction unit;
The time axis of the graph is non-linear, and when the predetermined time width is one section, the range of the time axis is different between the latest one section and the oldest one section, and the latest one section is more The time resolution is higher than the oldest section,
The respiratory training apparatus according to any one of claims 1, 2, and 8 to 15. A storage unit that stores a training menu for training breathing and a clear condition for clearing the class for each class determined according to the ability of breathing,
A breathing ability detector that detects the breathing ability of the subject based on the measured value of the first bioelectrical impedance and the measured value of the second bioelectrical impedance;
Referring to the storage unit, a class corresponding to the breathing ability detected by the breathing ability detection unit is specified, and a process for training breathing of the subject is performed based on the training menu corresponding to the specified class A training management unit that, when the clear condition corresponding to the specified class is established, further shifts the class of the subject to the next class higher than the class,
The breathing exercise apparatus according to any one of claims 1, 2, and 8 to 16. Based on the measured value of the first bioelectrical impedance and the measured value of the second bioelectrical impedance, an analysis unit that obtains discrimination information that can determine whether the subject's breathing is abdominal breathing or chest breathing And further comprising
The breathing exercise apparatus according to any one of claims 1, 2, and 8 to 17. A centering value generator for generating a first centering value indicating an amplitude reference level of the measurement value of the first bioelectrical impedance and a second centering value indicating an amplitude reference level of the measurement value of the second bioelectrical impedance;
A first relative value calculation unit for obtaining a first relative value that is a relative value of the measured value of the first bioelectrical impedance with respect to the first centering value;
A second relative value calculation unit that obtains a second relative value that is a relative value of the measurement value of the second bioelectrical impedance with respect to the second centering value;
The analysis unit obtains the discrimination information based on the first relative value and the second relative value;
The breathing training apparatus according to claim 18. The discrimination information indicates a ratio between a change in the circumference of the chest of the subject and a change in the circumference of the abdomen,
The analysis unit
The discrimination information corresponding to the first relative value and the second relative value by executing a calculation process according to a regression equation representing a relationship between the discrimination information and the first relative value and the second relative value. Seeking
The breathing exercise apparatus according to claim 19. The regression equation is represented in the following form:
The respiratory training device according to claim 20, wherein:
ΔRib / ΔAb = (a × ΔZb−ΔZa) / ΔZa + b
ΔRib: change in the circumference of the subject's chest, ΔAb: change in the circumference of the subject's abdomen, ΔRib / ΔAb: discrimination information, ΔZa: first relative value, ΔZb: second relative value, a, b: constant. If the value of ΔRib / ΔAb exceeds a predetermined threshold, the subject's breathing is chest breathing, whereas if it is less than or equal to the predetermined threshold, it is abdominal breathing,
The breathing training apparatus according to claim 21, wherein: Based on the measured value of the first bioelectrical impedance and the measured value of the second bioelectrical impedance, the analysis unit determines whether the subject's breathing is abdominal breathing, chest breathing, Find discriminating information that can discriminate between breathing and breathing while maintaining a recessed state.
The breathing training apparatus according to claim 18 to 21, wherein Based on the measured value of the first bioelectrical impedance and the measured value of the second bioelectrical impedance, the analysis unit determines whether the subject's breathing is abdominal breathing, chest breathing, Find discriminating information that allows you to discriminate between breathing and breathing while maintaining the indented state,
If the value of ΔRib / ΔAb is less than or equal to a predetermined threshold, the subject's breathing is abdominal breathing,
When the value of ΔRib / ΔAb exceeds the predetermined threshold value and the second centering value generated by the centering value generation unit is greater than the second centering value during the chest breathing of the subject by a predetermined value or more, Breathing of the subject is a breathing method that performs exhalation and inspiration while maintaining a state where the abdomen is recessed,
The value of ΔRib / ΔAb exceeds the predetermined threshold value, and the second centering value generated by the centering value generation unit is an addition value of the second centering value and the predetermined value during chest breathing of the subject. If less, the subject's breathing is chest breathing,
The breathing training apparatus according to claim 21, wherein: A zero cross timing extraction unit for extracting a zero cross timing at which the measured value of the first bioelectrical impedance is equal to the first centering value;
The bioelectrical impedance measuring unit is
Measuring the first bioelectrical impedance and the second bioelectrical impedance each time the sampling timing is reached at a predetermined period;
The centering value generation unit
While generating the first centering value based on the measured value of the first bioelectrical impedance at each of the predetermined number of sampling timings, the second bioelectrical impedance at the zero crossing timing extracted by the zero crossing timing extracting unit Generating the second centering value based on the measured value of
The respiratory training device according to any one of claims 8, 9, and 19 to 24. The centering value generation unit
For each of the sampling timings, the measurement of the first bioelectrical impedance at each of the plurality of sampling timings within a centering period starting from a time point a predetermined time before the sampling timing and ending at the sampling timing A moving average process is performed using the value, and the first centering value at the sampling timing is generated based on the result.
26. The respiratory training apparatus according to claim 25. The time length of the centering period is variably set according to the breathing rate of the subject.
27. The respiratory training apparatus according to claim 26. The centering value generation unit
For each sampling timing, it is determined whether or not the sampling timing is the zero cross timing, and when the sampling timing is the zero cross timing, based on the measurement value of the second bioelectrical impedance at the sampling timing And generating the second centering value at the sampling timing, if the sampling timing is not zero-cross timing, the second centering value generated at the sampling timing immediately before the sampling timing is the second centering value at the sampling timing. 2 Adopted as a centering value
The respiratory training apparatus according to any one of claims 25 to 27, wherein: A breathing depth extraction unit that extracts a breathing depth in the one breath for each breath of the subject;
An abdominal level calculation unit for obtaining an abdominal level indicating the proportion of the abdominal breathing in the one breath based on the discrimination information obtained by the analysis unit for each breath of the subject;
An informing unit for notifying each of the abdominal breathing and the chest breathing in one breath and the margin for each breath of the subject based on the breathing depth and the abdominal level in the one breath; Further comprising
The respiratory training apparatus according to any one of claims 19 to 28, wherein: A normalization unit that normalizes the respiration depth extracted by the respiration depth extraction unit;
The notification unit
Normalized by the normalization unit by executing arithmetic processing according to the second regression equation indicating the relationship between the breathing depth and the tidal volume indicating the amount of air entering and exiting the lung in one breath Obtaining the tidal volume corresponding to the breathing depth;
Based on the determined tidal volume and the abdominal level, the magnitude and margin of each of the subject's abdominal breathing and chest breathing are determined and reported,
30. A respiratory training apparatus according to claim 29. An input unit for inputting the first bioelectric impedance of the upper trunk including the subject's lung and not including the abdomen, and the second bioelectric impedance of the middle trunk including the subject's abdomen measured by the bioelectrical impedance measuring device When,
Of the two axes orthogonal to each other, one axis is the first bioelectrical impedance and the other axis is the second bioelectrical impedance, and the measured value of the first bioelectrical impedance and the measured value of the second bioelectrical impedance A display data generation unit for generating display data of a Lissajous figure showing a change over time of
A breathing training apparatus characterized by that. The first bioelectrical impedance measured by the bioelectrical impedance measuring apparatus on the right side of the upper trunk including the right lung of the subject and not including the abdomen, and the second living body on the left side of the upper trunk including the left lung of the subject and not including the abdomen. An input unit for inputting the electrical impedance and the third bioelectrical impedance of the middle trunk including the abdomen of the subject;
Of the two axes orthogonal to each other, one axis is the first bioelectrical impedance and the other axis is the third bioelectrical impedance. The measured value of the first bioelectrical impedance and the measured value of the third bioelectrical impedance Display data of a first Lissajous figure showing a change over time of the first bioelectrical impedance, the one axis as the second bioelectrical impedance, the other axis as the third bioelectrical impedance, and the second bioelectrical impedance A display data generation unit that generates display data of a second Lissajous figure indicating a change over time of the measurement value and the measurement value of the third bioelectrical impedance,
A breathing training apparatus characterized by that. A bioelectrical impedance measuring unit for measuring a first bioelectrical impedance of the upper trunk including the lung of the subject and not including the abdomen, and a second bioelectrical impedance of the middle trunk including the abdomen of the subject;
Of the two axes orthogonal to each other, one axis is the first bioelectrical impedance and the other axis is the second bioelectrical impedance, and the measured value of the first bioelectrical impedance and the measured value of the second bioelectrical impedance A Lissajous figure generating unit for generating a Lissajous figure showing a change in time of
A display unit for displaying the Lissajous figure generated by the Lissajous figure generation unit,
A respiratory training system characterized by that. A first bioelectrical impedance on the right side of the upper trunk that includes the right lung of the subject and does not include the abdomen; a second bioelectrical impedance on the left side of the upper trunk that includes the left lung of the subject and does not include the abdomen; A bioelectrical impedance measuring unit for measuring a third bioelectrical impedance of the middle trunk including
Of the two axes orthogonal to each other, one axis is the first bioelectrical impedance and the other axis is the third bioelectrical impedance. The measured value of the first bioelectrical impedance and the measured value of the third bioelectrical impedance A first Lissajous figure showing a change over time of the second bioelectrical impedance, the first bioelectrical impedance as the second axis and the third bioelectrical impedance as the other axis, and a measured value of the second bioelectrical impedance, A Lissajous figure generating unit for generating a second Lissajous figure showing a change over time of the measurement value of the third bioelectrical impedance;
A display unit for displaying the first Lissajous figure and the second Lissajous figure generated by the Lissajous figure generation unit;
A respiratory training system characterized by that.

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