JP2000107154A - Device for detecting apnea - Google Patents

Abstract

PROBLEM TO BE SOLVED: To detect breathing without attaching a detection directly to the body and warn of apnea by measuring reliably movements of the body of a subject including breathing. SOLUTION: This detector is equipped with a detection mat 2 having a pressure sensitive pipe 21, a pressure measuring means 4 that measures pressure inside the pressure sensitive pipe 21 at every prescribed time with a pressure sensor 41 and a monitor display 3 having an apnea detecting means 5 that receives signals from the pressure measuring means 4 and detects apnea from a pressure change in the pressure sensitive pipe 21. In this case, by laying a subject 100 on this detection mat 2 through a mattress 101 or the like, breathing can be detected without attaching any cord and any sensor, and body movements including breathing of the subject 100 can be measured reliably and the subject can be warned against apnea.

Description

DETAILED DESCRIPTION OF THE INVENTION

[0001]

BACKGROUND OF THE INVENTION 1. Field of the Invention The present invention relates to an apnea detecting apparatus, and more particularly to a sudden neonatal death syndrome (S) occurring during sleep.
(IDS) and apnea syndrome in adult apnea syndrome, etc. are detected by monitoring respiration to notify the apnea state, and during artificial respiration, disconnection of the respiratory circuit and obstruction of the airway are detected. The present invention relates to an apnea detecting device.

[0002]

[Background Art] In recent years, sudden death syndrome (hereinafter abbreviated as SIDS) is the leading cause of neonatal death in Western countries, and lifestyle changes in Europe and the United States affected the increase in SIDS in Japan as well. Is given. SIDS is
The cause is still unknown medically, and the knowledge of prediction and prevention is insufficient and it is a very important problem. Moreover, it is a shocking disease in which a newly born baby suddenly dies. For this reason, especially in the era of low birth rates due to the low birth rate in recent years, the breathing of newborns at home is
There is a need for an apnea detection device as home monitoring that can monitor time and know a state of not breathing, that is, an apnea state.

[0003] In addition, by installing an apnea detection device in a nursery school outside a home or in a neonatal room at a maternity hospital, a newborn baby can be safely left in a place other than the home. It is expected that it will be needed at facilities and the like. In addition, this home monitoring is also required for those who experience apnea due to immaturity or chronic lung disease, those who are at home with oxygen or artificial ventilation, or those who have tracheostomy. You.

[0004] Such home monitoring includes:
A high-performance and expensive apnea detection device that uses a heart rate monitor or the like used in a hospital or the like may be used, but it is not fully operable at a general level, and is usually used in a home or a nursery school. Since it is mainly used by housewives, nurses, etc., it must be an apnea detection device that is easy to operate and has no trouble.

[0005] By the way, various apnea detecting devices have been developed as home monitoring, but to name a few examples, as a first conventional example, a retractable abdominal band is used as a detecting unit and breathing is performed. A variable resistance apnea determining device (Japanese Patent Laid-Open No. 6-63031) that detects respiration by utilizing the fact that the resistance value of a variable resistor incorporated inside a belly band changes due to the vertical movement of the abdomen accompanying the is there. This utilizes the fact that the belly band attached to the body expands and contracts due to the vertical movement of the abdomen during sleep of the subject, and the resistance value of the variable resistor incorporated therein changes.
Then, a constant voltage is applied to the variable resistor, and the current flowing therethrough is continuously measured to detect respiration and determine the apnea state.

As a second conventional example, a sound detection type apnea detecting apparatus which detects a respiration by measuring a sound generated in an airway or the like along with the respiration by using a microphone as a detection unit (Japanese Patent Application Laid-Open No. Sho 63/1988). 158040). In this method, sound generated in the respiratory tract or the like from the neck or upper chest of the subject along with breathing is measured by a microphone attached to the body to detect breathing and determine an apnea state. At this time, the microphone is attached to the body of the subject with an adhesive tape.

Further, as a third conventional example, a capsule which is a detection unit wound around the abdomen is compressed when breathing, and the pressure change in the capsule is detected by a pressure gauge. Pneumatic capsule type that detects breathing by measuring
No. 2042).

[0008]

However, in these conventional devices for home monitoring, since the detection section must be attached to the body of the subject, the detection sensitivity is reduced depending on the attachment position, and respiration cannot be detected. There is a problem in that when pasted with an adhesive tape or the like, the pasted portion may be rash. In addition, the detection unit has to be attached every time measurement is performed, and the operation is troublesome and troublesome. In addition, there is a problem that the sleeping comfort is deteriorated, and the subject and the user are burdened. Furthermore, in the conventional home monitoring device, there is a problem that an apnea state by SIDS may be overlooked because the device may be erroneously operated as breathing due to external vibrations caused by walking of a person or the like.

SUMMARY OF THE INVENTION It is an object of the present invention to detect breathing without directly attaching the detecting portion to the body, and to reliably measure the body movement including the breathing of the subject to notify the apnea. It is to provide a respiration detection device.

[0010]

An apnea detecting apparatus according to a first aspect of the present invention is an apnea detecting apparatus for detecting an apnea state of a subject. A detection mat mounted on the detection mat, a pressure-sensitive portion provided in the detection mat, and generating a pressure change in synchronization with body movements including respiration of the subject, and a pressure inside the pressure-sensitive portion. Pressure sensor means for measuring the pressure at a predetermined time interval, and apnea detection means for receiving a signal from the pressure measurement means and detecting an apnea state from a pressure change of the pressure-sensitive section. Features.

With this configuration, the subject is laid down on a detection mat having a built-in pressure-sensitive part via a mattress or the like as necessary, and the body movement (including breathing) of the subject is performed. The pressure of the pressure-sensitive portion, which changes in synchronization with the body movement, is measured by the pressure measuring means, and a signal from the pressure measuring means is received, and the apnea detecting means detects the apnea state. As a result, respiration can be detected without attaching the detection portion to the body of the subject, and the body movement including the respiration of the subject can be reliably measured without imposing a burden on the subject. The breath is informed.

Further, as described in claim 2, it is preferable that the pressure-sensitive portion is formed of a pipe-shaped hollow body that can be elastically deformed. If the pressure-sensitive part is formed of an elastically deformable pipe-shaped hollow body, the sensitivity of the pressure-sensitive part can be made higher than that of a simple flat hollow body. Can also change the pressure inside the pressure sensitive part,
Respiration can be detected with that much precision. In addition, since the pressure-sensitive portion can be elastically deformed, the arrangement of the pressure-sensitive portion is not limited to a linear shape, but may be, for example, a substantially circular shape. Can be easily changed in accordance with the size of the device.

Further, as set forth in claim 3, the detection mat comprises a pressure-sensitive portion, and upper and lower plates disposed above and below the pressure-sensitive portion, and the upper plate is covered. It is configured to be elastically deformable by the examiner's breathing, and to generate a pressure change in the pressure sensitive part with the deformation of the upper plate due to the movement of the subject's body, and the lower plate is a hard member It is desirable to form by.

As described above, if the pressure change is caused to occur in the pressure-sensitive portion along with the deformation of the upper plate due to the movement of the body of the subject, the subject may be turned over by turning over or the like. Even if the subject moves from the upper position to an arbitrary position on the upper plate, the pressure-sensitive part changes as the upper plate deforms as long as the subject does not come off the upper plate. Of the person can be detected. In addition, since the lower plate is formed of a hard member that does not elastically deform, the pressure applied to the pressure-sensitive portion due to the deformation of the upper plate is hardly absorbed by the lower plate, and the pressure change inside the pressure-sensitive portion is reduced. Can be improved, and the sensitivity for detecting respiration can be improved.

According to a fourth aspect of the present invention, the pressure-sensitive portion is formed of a pipe-shaped hollow body that can be elastically deformed, and the lower plate has a crush amount regulating means for regulating the crush amount of the pressure-sensitive portion. Is preferably provided. According to this, the installation work can be easily performed, and since the position of the pressure-sensitive portion does not shift, stable detection sensitivity can be obtained.

Further, as set forth in claim 5, a pressure receiving chamber for receiving a pressure from the inside of the pressure sensing section is provided in the pressure sensor section, and the pressure measurement path connecting the pressure sensing section and the pressure receiving chamber is connected to the atmosphere. It is desirable to provide a communicating through-hole.

If such a through-hole is provided, the pressure measurement path may unnecessarily undergo pressure changes due to external factors (for example, changes in atmospheric pressure and ambient temperature, or effects of temperature changes due to the temperature of the newborn baby). Even if there is, after a predetermined time passes through the through hole, the pressure almost returns to the atmospheric pressure. Therefore, it is possible to quickly measure the respiration with a small pressure change, and to perform appropriate apnea detection.

According to a sixth aspect of the present invention, there is provided a pressure receiving chamber for receiving a pressure from the inside of the pressure sensing section to the pressure sensor section,
It is preferable to provide a back pressure chamber adjacent to the pressure receiving chamber, and to provide a through hole communicating with the atmosphere in each of the pressure receiving chamber and the back pressure chamber.
With this configuration, the back pressure chamber also communicates with the atmosphere, which can prevent a decrease in sensitivity due to a pressure change due to an external factor on the back pressure chamber side, and can measure a pressure change due to breathing with high sensitivity. it can.

Further, a pressure waveform obtained from a pressure change due to respiration may include a component having a higher frequency than that of respiration due to vibration due to external factors. Therefore, as described in claim 7, a pressure receiving chamber for receiving a pressure from the inside of the pressure sensing section is provided in the pressure sensor section, and a noise reduction throttle is provided in a pressure measurement path formed from the pressure sensing section to the pressure receiving chamber. It is desirable to provide a reservoir for maintaining the detection sensitivity of respiration.

As described above, if the noise reduction aperture and the respiration detection sensitivity maintenance reservoir are provided in the pressure measurement path, unnecessary components such as vibration due to external factors are reduced, and the pressure obtained from the pressure change due to respiration is reduced. The waveform can be smoothed, and a stable and good respiratory waveform can be extracted.

[0021]

Embodiments of the present invention will be described below with reference to the drawings. FIGS. 1 to 3 show an apnea detecting apparatus 1 to which a first embodiment of the present invention is applied.

An apnea detecting apparatus 1 detects a state of apnea by measuring a substantially flat rectangular parallelepiped, more specifically, a futon-shaped detection mat 2 and a change in pressure applied to the detection mat 2. And a monitor display 3 for displaying and alarming the apnea condition. On the detection mat 2,
A mattress 101 is placed as necessary, and a subject 100 such as a newborn baby is placed on the mattress 101.

As shown in FIG. 2A, the detection mat 2 is mounted in the detection mat 2 and is
A pressure-sensitive pipe 21 that is a pressure-sensitive part that generates a pressure change in synchronization with a body movement (body movement) including breathing of zero, an upper plate 22 and a lower plate 22 that are arranged above and below the pressure-sensitive pipe 21 in contact with each other. Board 2
3, a spacer 24 interposed at both ends in the longitudinal direction of the upper plate 22 and the lower plate 23 to form a predetermined gap between the two plates 22 and 23, and a protective cover 25 covering the whole thereof. It is configured. At this time, the size of the detection mat 2 is, for example, large enough to fit into a bed for a newborn if it is for a newborn.

The pressure-sensitive pipe 21 is formed of a flexible, elastically deformable pipe-shaped hollow body cut to a predetermined length, for example, a silicone resin tube. This pressure-sensitive pipe 2
One end 21A is sealed with an embedding plug 26, and the other end is provided with a noise reduction aperture 27A for adjusting the amount of pressure change due to breathing at its opening to reduce noise due to external factors. One end of a connection pipe 27 provided with a. The monitor display 3 is connected to the other end of the connection pipe 27 via a connection pipe 60 as described later in detail.

The lower plate 23 of the detection mat 2 is made of a hard member such as a hard plastic, and is formed so as not to be elastically deformable. On the center line in the longitudinal direction of the upper surface 23B of the lower plate 23, a groove 23A is formed, which is a means for restricting the amount of crush of the linear pressure-sensitive pipe 21 that houses the pressure-sensitive pipe 21. The groove 23A is formed over substantially the entire length in the longitudinal direction of the lower plate 23 except for the end of the lower plate 23 opposite to the monitor display connection side, and both ends of the groove 23A are deep and the central portion is formed. It is formed shallow.

More specifically, the depth of the groove 23A at the end 21A of the pressure-sensitive pipe 21 is approximately the same as the outer diameter of the pressure-sensitive pipe 21 (for example, 5 mm). Groove 23A corresponding to central portion 21B of 21
Is formed shallower than the outer diameter of the pressure-sensitive pipe 21 (for example, about 3 mm). Thereby, the end 21A of the pressure-sensitive pipe 21 is arranged so that the upper plate 22 does not come into contact with the upper plate 22 even if the upper plate 22 is deformed due to the weight of the subject 100 or the like. The portion 21B protrudes above the upper surface 23B of the lower plate 23 and is disposed so as to substantially contact the lower surface 22A of the upper plate 22 in an undeformed state.

Therefore, the groove 2 in the above specific example of dimensions is
With respect to the depth (3 mm) of the central portion of 3A and the outer diameter (5 mm) of the pressure-sensitive pipe 21, the thickness of the spacer 24 is 2 mm. The thickness of the spacer 24 is the maximum crushing allowance of the pressure-sensitive pipe 21, but the actual crushing allowance depends on the weight of the subject 100, the thickness of the upper plate 22, the bending elastic modulus, and the like, for example. It is set to about 0.2 to 1.8 mm. That is, the pressure-sensitive pipe 21 is not completely crushed by the groove 23A serving as the crushing amount regulating means.
The thickness of the pressure-sensitive pipe 21 is, for example, about 0.5 mm, the upper plate 22 is extremely bent due to excessive weight or the like, and the lower surface 22A of the upper plate 22 contacts the upper surface 23B of the lower plate 23. Even if the pressure-sensitive pipe 21 is crushed by the upper plate 22 to a position near the upper surface 23B of the lower plate 23, the central portion of the pressure-sensitive pipe 21 is sufficiently deformed. A space exists (see FIG. 2B), and a change in the internal pressure of the pressure-sensitive pipe 21 can be measured. In addition,
FIG. 2 (B) is overexpressed in comparison with FIG. 2 (A). In such a crushed state, the pressure-sensitive pipe 21
Does not permanently deform, and when deformed, the inner diameter of the pressure-sensitive pipe 21 is narrowed and does not affect the detection sensitivity of the pressure inside the pressure-sensitive pipe 21.

Further, the width of the groove 23A depends on the pressure-sensitive pipe 21.
Touches the groove wall 23C, the detection sensitivity of the pressure change inside the pressure-sensitive pipe 21 is reduced. Therefore, even when the pressure-sensitive pipe 21 is crushed to the upper surface 23B of the lower plate 23 as described above,
It is formed wider than the outer diameter of the pressure-sensitive pipe 21 so as not to touch the groove wall 23C.

The upper plate 22 is formed of a member that can be elastically deformed by the respiration of the subject 100, and is attached to the spacer 24 so as to act as a leaf spring with the spacer 24 as a fulcrum. Specifically, upper plate 2
2, the lower plate 23 and the spacer 24 interposed between these two plates 22 and 23 are bonded, nailed at the four corners thereof,
It is fixed by other fixing means. The upper plate 22 is required to have a certain degree of bending elasticity. However, any material can be used as long as it is an elastic material, and a resin plate, a wooden plate, cardboard, and other materials can be used. In this embodiment, specifically, it is formed of a light foamable resin material (for example, a foam made of vinyl chloride). The upper plate 22 made of the vinyl chloride foam has a different bending elastic modulus in its longitudinal direction, that is, the longitudinal direction of the pressure-sensitive pipe 21, and the direction perpendicular to the longitudinal direction. Large elastic modulus,
The amount of bending (deformation) of the plate due to the weight and body movement of the subject 100 is reduced. On the other hand, in the direction orthogonal to the longitudinal direction of the upper plate 22, the bending elastic modulus is smaller than in the longitudinal direction, and the plate is bent (deformed) due to the weight or body movement of the subject 100.
The amount is increasing.

The protective cover 25 is formed of a surface material and dimensions (thickness) that do not affect the detection sensitivity when detecting a pressure change of the pressure-sensitive pipe 21. That is, the protective cover 25 is made of a soft and thin member, more specifically, a soft plastic sheet, cloth, or the like, and covers the entire upper plate 22, lower plate 23, and spacer 24.

As shown in FIG. 1, the monitor display 3 includes pressure measuring means 4, apnea detecting means 5, and a battery 6 for driving the display. The pressure measurement unit 4 includes a pressure sensor unit 41 that detects a pressure change due to respiration inside the pressure-sensitive pipe 21 and a pressure measurement unit 42 that measures the pressure change detected by the pressure sensor unit 41 at predetermined time intervals. It is configured. In addition, the apnea detecting means 5 is provided with a pressure waveform obtained by measuring the pressure
1, an apnea detecting section 51 for detecting an apnea state from a pressure change in the inside, a display section 52 for displaying a pressure waveform obtained by being measured by the pressure measuring section 42, and an alarm section for notifying the apnea state when the apnea state is detected 53. The waveform, the detection result, and the like obtained by the monitor display 3 are output to a printing machine or the like through an appropriate external output terminal.

The pressure sensor 41 of the pressure measuring means 4 includes:
The other end of the connection pipe 27 is connected via the connection pipe 60. The inside diameter of the connecting pipe 60 is smaller than that of the pressure-sensitive pipe 21 in order to transmit the pressure change inside the pressure-sensitive pipe 21 due to breathing to the pressure sensor unit 41 of the monitor display 3 so as not to lower the detection sensitivity. In addition, a reservoir 60A for maintaining the detection sensitivity of respiration having a small internal volume is formed. Further, in consideration of the user moving the monitor display 3 around the bed, the connecting pipe 60 is formed of a tough pipe having a small bending radius and hard to be broken.

The pressure sensor section 41 of the pressure measuring means 4 may be any of various conventional structures as long as it can detect pressure, but as a specific example of the structure, as shown in FIG. 60, a pressure inlet 43 having a small internal volume so as not to lower the detection sensitivity, a pressure receiving chamber 44 for receiving pressure from the inside of the pressure sensitive pipe 21, and a pressure sensor above the pressure receiving chamber 44. A back pressure chamber 46 adjacent via the circuit section 45 is provided. Here, the path from the pressure-sensitive pipe 21 to the pressure receiving chamber 44 forms a pressure measurement path 30 which is a pressure path.

The pressure sensor circuit section 45 partitions the pressure receiving chamber 44 and the back pressure chamber 46, and is provided with a substrate 45A having an electronic circuit (not shown), a pressure sensor circuit disposed in the center of the substrate, and a pressure caused by breathing inside the pressure sensitive pipe 21. And a pressure sensor chip 45B for detecting a change. The pressure sensor chip 45B includes, for example, a diaphragm that deforms in response to a change in pressure. The deformation of the diaphragm is taken out as a distortion amount, a capacitance, and the like, and can be converted into an electric signal by an electronic circuit to measure the pressure. ing.

The pressure receiving chamber 44 is formed with a pressure receiving chamber air opening restriction 44A which is a through hole communicating with the atmosphere. If the pressure-receiving chamber air opening restrictor 44A is not formed, the pressure-receiving chamber 44 will be in a closed state. In this state, the pressure-receiving chamber 44 will not be affected by changes in atmospheric pressure or ambient temperature, or changes in temperature due to body temperature of the newborn. Due to an external factor having a slow pressure response, the air in the pressure receiving chamber 44 expands or compresses, the internal pressure in the pressure receiving chamber 44 gradually changes, and it becomes impossible to detect a minute pressure change due to breathing. However, the pressure receiving chamber 44
The pressure-reducing chamber air opening restrictor 44A is formed in the pressure-reducing chamber 44 so that the internal pressure of the pressure-receiving chamber 44 does not change due to an external factor, so that the atmospheric pressure can be maintained at all times. It has been. In addition, the hole shape of the pressure-receiving chamber open-to-atmosphere throttle 44A is formed to a size that does not receive the above-mentioned external factors and does not lower the respiration detection sensitivity.

The back pressure chamber 46 is also formed with a back pressure chamber air opening restriction 46A which is a through hole having the same shape as the restriction 44A formed in the pressure receiving chamber 44. When the back pressure chamber is not formed with the air opening restrictor 46A and the back pressure chamber 46 is opened to the atmospheric pressure, for example, the opening and closing of the door of the room in which the apnea detecting device 1 is installed, the wind of air conditioning, and the like. Due to the rapid change in the atmosphere, the back pressure chamber 46 is directly affected, and a pressure change close to respiration may appear, and it may not be possible to determine the respiration. However, since the back pressure chamber 46 is formed with the back pressure chamber air opening throttle 46A, a sudden change in the atmosphere is mitigated, and the throttle and the space in the pressure receiving chamber 44 are formed in the same shape as the pressure receiving chamber 44. However, the effect of a sudden change in the atmospheric pressure is reduced. By configuring the pressure sensor unit 41 in this way, it is possible to measure a pressure change accompanying respiration with high sensitivity.

Then, the pressure change due to breathing detected by the pressure sensor section 41 is measured at predetermined time intervals by the pressure measuring section 42, and a pressure waveform due to breathing as shown in FIG. 5 is obtained. At this time, the pressure waveform is
The diaphragm 27A for noise reduction and the reservoir 60A for maintaining the detection sensitivity of respiration formed in the connecting pipe 60 are provided with a damping vibration due to the spring characteristic of the upper plate 22 and a vibration such as vibration due to other external factors. The high frequency component is smoothed by removing and reducing the high frequency component, and the smoothed waveform is displayed on the display unit 5 of the monitor display 3.
2 is displayed.

When the weak breathing of a newborn baby during sleep is transmitted as a change in volume of the pressure-sensitive pipe 21, the pressure-sensitive pipe 21
The amount of pressure change ΔP generated in the above can be calculated by the following equation 1.

[0039]

## EQU1 ## ΔP = P ₀ × ΔV / V

Here, V indicates the internal volume of the pressure-sensitive pipe 21, ΔV indicates the amount of change in the internal volume of the pressure-sensitive pipe 21, and P ₀
Indicates the atmospheric pressure. That is, by reducing the internal volume V of the pressure-sensitive pipe 21 and increasing the internal volume change amount ΔV of the pressure-sensitive pipe 21, a large pressure change amount ΔP can be generated, and the detection sensitivity can be increased. It has become. Therefore, in designing the pressure-sensitive pipe 21,
The dimensions are set by understanding the above principle.

The entire length of the pressure-sensitive pipe 21 is preferably set to be approximately the same as the height of the newborn baby as the subject 100, and furthermore, a portion projecting from the lower plate upper surface 23B of the pressure-sensitive pipe 21 (central portion). About 2/3 of the length of the detection mat 2 in the longitudinal direction is good in sensitivity. More specifically, when the entire length of the detection mat 2 is about 700 mm,
The length of the protruding portion (central portion) of the pressure-sensitive pipe 21 is about 400 to 600 mm, more preferably about 500 m.
m. If the length is shorter than this range, the detection range is narrow, and if the length is longer, the inner volume increases and the sensitivity is reduced.

Next, a method of using the apnea detecting apparatus 1 of the present embodiment will be described. First, the subject 100 (newborn) is placed on the detection mat 2 via the mattress 101. Usually, the breathing of a newborn is abdominal breathing. In abdominal breathing, during inspiration, the diaphragm descends and the lungs expand, and the abdomen expands accordingly. On the other hand, at the time of expiration, the lungs contract, the diaphragm rises, and the abdomen contracts accordingly. During sleep, such a series of exercises causes regular abdominal up and down exercises. On the other hand, in the apnea state where the breathing is stopped, the vertical movement of the abdomen stops.

Therefore, when the subject 100 sleeps while being placed on the detection mat 2 and breathes regularly,
A pressure change occurs in the pressure-sensitive pipe 21 according to the amount of bending of the upper plate 22 due to the vertical movement of the abdomen. This pressure change is input to and detected by the pressure sensor unit 41 through the connection pipe 27 and the connection pipe 60. Next, the pressure detected by the pressure sensor unit 41 is changed every predetermined time by the pressure measurement unit 42.
, And the pressure measuring unit 42 creates a pressure waveform shown in FIG. 5 from the measured pressure. This pressure waveform is displayed by the display unit 52.

At this time, when the subject 100 is placed on the detection mat 2, the pressure change caused by the weight of the subject 100 is constant after the subject 100 is placed.
Is released to the atmosphere from a pressure-receiving chamber air opening throttle 44A provided in the pressure-receiving chamber 44, and has no effect after a certain time. Therefore, thereafter, only the pressure change due to breathing is detected.

Next, when there is a body movement including breathing,
This will be described in more detail with reference to FIG. At the time of inhalation, as the abdomen expands, the amount of bending of the upper plate 22 increases, the pressure-sensitive pipe 21 is compressed, and the pressure in the pressure measurement path 30 rises from the atmospheric pressure state (zero) to a high positive pressure. Thereafter, the pressure in the pressure measurement path 30 returns to the atmospheric pressure state by the pressure-receiving chamber air opening restriction 44A. On the other hand, at the time of exhalation, the amount of bending of the upper plate 22 decreases due to the contraction of the abdomen, the pressure-sensitive pipe 21 attempts to return to the original position, and the pressure of the pressure measurement path 30 decreases from the atmospheric pressure state to a low negative pressure. I do. Thereafter, the pressure in the pressure measurement path 30 returns to the atmospheric pressure state by the pressure-receiving chamber air opening restriction 44A. Such a series of pressure changes in the pressure measurement path 30 are repeated at a substantially constant cycle and amplitude around the atmospheric pressure state.

Then, the subject 100 breaths after the pressure value becomes equal to or higher than the upper limit breath detection level A of positive pressure from zero.
When it falls to or below the lower limit of the negative pressure detection level B of the negative pressure, it is determined to be the first respiration. In addition to the regular pressure change due to breathing, there are large movements of the body such as turning over and moving limbs.In this case, the pressure change is irregular in cycle but large in amplitude compared to breathing. It is assumed that you are doing. In addition, even after the internal pressure greatly changes due to such a movement of the body, the internal pressure immediately returns to the atmospheric pressure state (zero) by the pressure-receiving chamber air opening restriction 44A, so that the detection of the pressure change due to breathing is not affected. .

When the body movements including the above-mentioned respiration occur and the state becomes apnea, the pressure in the pressure measurement path 30 is maintained at the atmospheric pressure state (zero) as shown on the right side of FIG. Is almost gone. A respiratory stop time t in which the pressure value is less than the upper limit respiration detection level A and does not fall below the lower limit respiration detection level B
Is exceeded, the apnea detection unit 51 determines the apnea state,
In addition to displaying on the display unit 52, an appropriate alarm such as lighting of a buzzer or a warning lamp is output from the alarm unit 53. Thus, the apnea state of the subject 100 is detected.

According to this embodiment, the following effects can be obtained. The apnea detection device 1 includes a pressure-sensitive pipe 2
1, pressure measuring means 4 for measuring the pressure inside the pressure-sensitive pipe 21 at predetermined time intervals by a pressure sensor section 41, and apnea detecting means 5 for detecting an apnea state from a pressure change of the pressure-sensitive pipe 21. Therefore, as compared with the conventional detection unit attached to the body of the subject 100, respiration can be detected without wearing any cords or sensors, and the subject 1
The apnea state can be detected by reliably measuring the body movements including the respiration of the subject 100 without giving a burden to the patient 00.

Since the pressure-sensitive pipe 21 is formed of an elastically deformable pipe-shaped hollow body, the subject 100
The pressure inside the pressure-sensitive pipe 21 can be changed even by the minute breathing or the movement of the body, and the breathing can be detected precisely by that amount.

Further, since the pressure change is generated in the pressure-sensitive pipe 21 in accordance with the deformation of the upper plate 22 due to the movement of the body of the subject 100, the subject 100 turns over and the like.
Even if the subject 100 moves to an arbitrary position on the upper plate 22 from a position right above, as long as the subject 100 does not come off the upper plate 22,
Since the pressure change occurs in the pressure-sensitive pipe 21 with the deformation of the upper plate 22, the breathing of the subject 100 can be easily detected. Further, since the lower plate 23 is formed of a hard member that does not elastically deform, the pressure applied to the pressure-sensitive pipe 21 due to the deformation of the upper plate 22 is hardly absorbed by the lower plate 23, and the pressure-sensitive pipe The sensitivity of the pressure change in the inside 21 can be improved, and the sensitivity for detecting respiration can be improved.

Further, since the pressure-sensitive pipe 21 is formed of an elastically deformable pipe-shaped hollow body and this pressure-sensitive pipe 21 is disposed in the groove 23A formed in the lower plate 23, the pressure-sensitive pipe 21 Can be easily installed, and the position of the pressure-sensitive pipe 21 does not shift.
Stable detection sensitivity can be obtained.

Further, since the pressure-receiving chamber 44 is formed with the pressure-receiving chamber open-to-atmosphere throttle 44A, even if the pressure measurement path 30 temporarily changes in pressure due to an external factor, the pressure-receiving chamber 44 becomes open.
Can be quickly returned to the atmospheric pressure state, whereby only a pressure change due to respiration can be measured in a minute range. In addition, since the back pressure chamber 46 is provided with the back pressure chamber air opening restriction 46A, it is possible to alleviate a sudden change in the atmosphere, and to make the pressure receiving chamber 44 and the restriction and the internal volume of the space the same shape. In addition, the influence of a sudden change in the atmospheric pressure can be reduced.

Further, since the noise reduction aperture 27A and the respiration detection sensitivity maintaining reservoir 60A are provided in the pressure measurement path 30, unnecessary components such as vibration due to external factors are reduced, and the pressure change due to respiration is reduced. The obtained pressure waveform can be smoothed, and a stable and good respiratory waveform can be extracted.

FIG. 6 shows a detection mat 2 according to a second embodiment of the present invention. The same or equivalent components as those of the first embodiment are denoted by the same reference numerals, and description thereof will be omitted or simplified. In this embodiment, screws 23 provided at predetermined intervals are used as means for controlling the amount of collapse of the pressure-sensitive pipe 21.
The difference from the first embodiment is that F is used.

More specifically, as shown in FIG.
A plate-like member 23D made of a metal, a resin plate, or the like on which the pressure-sensitive pipe 21 made of silicone resin is placed is installed on the longitudinal center line of the upper surface 23B. Plate member 23D
Excluding the plug 26 and the connecting pipe 27 attached to the end 21A of the pressure-sensitive pipe 21, is formed to have a length extending substantially the entire length (central portion) in the longitudinal direction of the pressure-sensitive pipe 21. .

The pressure-sensitive pipe 2 placed on the plate member 23D
The central portion 21B of the first member 21 is provided on the upper surface 23E of the plate-like member 23D.
In addition to being adhered with a double-sided tape (not shown), about the upper half of the central portion 21B protrudes above the head of a screw described later. The central portion 21B of this pressure-sensitive pipe 21
Is a state in which the subject 100 is not placed,
When the upper plate 22 is deformed by the weight of the subject 100, the central portion 2
1B is further crushed and a pressure change is detected.

At both ends along the longitudinal direction of the plate member 23D, screws 23F for fixing the plate member 23D to the lower plate 23 are provided.
Are arranged at predetermined intervals along the longitudinal direction of the plate member 23D. These screws 23F are in a state where their heads 23G protrude upward from the upper surface 23E of the plate-like member 23D (for example, a protruding dimension H1 = about 2.5 mm). Therefore, the outer diameter of the pressure-sensitive pipe 21 is set to, for example, 5
mm, the height of the portion of the central portion 21B of the pressure-sensitive pipe 21 projecting above the head 23G of the screw 23F is set to about 2 mm, which is the maximum crushing allowance of the pressure-sensitive pipe 21. It has become. That is, since the head 23G of the screw 23F protrudes above the upper surface 23E of the plate member 23D, the pressure-sensitive pipe 21 is completely crushed and the inner diameter becomes 0 (zero). Without any permanent deformation. Also, between the screws 23F opposed to each other with the pressure-sensitive pipe 21 interposed therebetween, even when the pressure-sensitive pipe 21 is crushed as shown in FIG. It is more widely formed. This prevents the pressure-sensitive pipe 21 from touching the screw 23F from lowering the sensitivity of detecting a pressure change inside the pressure-sensitive pipe 21.

As shown in FIG. 8, the central portion 21B of the pressure-sensitive pipe 21 is placed on a plate-like member 23D,
A is arranged on the lower plate 23. Here, the thickness dimension H2 of the plate member 23D is such that when the upper plate 22 is deformed due to the weight of the subject 100 or the like, the upper plate 22 contacts the plug 26 or the connection pipe 27 before the upper plate 22 contacts the screw 23F. Not set. That is, the sum of the projecting dimension H1 of the screw 23F and the thickness dimension H2 of the plate member 23D is equal to or larger than the outer diameter dimension (height dimension from the lower plate 23) of the plug 26 and the connection pipe 27. Thus, even if the upper plate 22 is deformed,
2 is in contact with the screw 23F and is not in contact with the plug 26 or the connection pipe 27. For example, the outer diameter of the plug 26 and the connecting pipe 27 is about 5.5 mm, and the screw 2
When the protrusion dimension H1 of 3F is about 2.5 mm, the thickness dimension H2 of the plate-like member 23D may be about 3.5 mm or more. 6 to 8, the size of the screw 23F is shown larger than the actual size for convenience of explanation.

When the subject 100 is placed on the detection mat 2 via the mattress 101, the subject 10
The upper plate 22 is bent by the weight and breathing of zero, and the pressure-sensitive pipe 2
The central portion 21B of the subject 100 is crushed, the pressure change is detected, and the apnea state of the subject 100 is detected. At this time, if the heavier subject 100 is placed, the lighter subject 1
Although the amount of deflection of the upper plate 22 becomes larger than that of 00 and the amount of crushing of the pressure-sensitive pipe 21 increases accordingly,
Since the amount of crushing of the pressure-sensitive pipe 21 is regulated by this, the pressure-sensitive pipe 21 is not completely crushed and can be prevented from being permanently deformed.

According to this embodiment, the same effects as those of the above embodiment can be obtained, and the following effects can be obtained. By simply fixing the screw 23F to the lower plate 23 via the plate-like member 23D, the crushing amount regulating means of the pressure-sensitive pipe 21 can be formed. The forming operation can be easily performed.

Further, the amount of collapse of the pressure-sensitive pipe 21 can be regulated by the screws 23F for fixing the plate-like member 23D to the lower plate 23. For example, the plate-like member 23D is fixed in advance, and In comparison with the case where a spacer or the like is placed and the amount of crushing of the pressure-sensitive pipe 21 is regulated by the spacer, the fixing of the plate-like member 23D with the screw 23F and the regulation of the amount of crushing of the pressure-sensitive pipe 21 can be used. As a result, the number of working steps can be reduced, and the mounting operation can be easily performed.

Further, a plate-like member 23D on which the central portion 21B of the pressure-sensitive pipe 21 is placed is provided, and the sum of the projection H1 of the screw 23F and the thickness H2 of the plate-like member 23D is determined by inserting the plug 26 and By setting the outer diameter of the connection pipe 27 to be equal to or larger than the outer diameter of the connection pipe 27, the upper plate 22 can be prevented from contacting the plug 26 or the connection pipe 27 before contacting the screw 23F. When the plate 22 is bent, the upper plate 22
Of the pressure-sensitive pipe 21 can be prevented from occurring due to the lower surface 22A of the pressure-sensitive pipe 21 coming into contact with the plug 26 or the connection pipe 27.

It should be noted that the present invention is not limited to the above-described embodiment, but includes other configurations that can achieve the object of the present invention, and the following modifications are also included in the present invention.
For example, in the embodiment, the noise reduction aperture 27A and the respiration detection sensitivity maintenance reservoir 60A are connected to the pressure measurement path 3A.
Although provided at 0, the present invention is not limited to this. For example, it may be provided at the pressure sensor unit 41, the pressure measurement unit 42, and the like. Also, the noise reduction aperture 27A and the respiration detection sensitivity maintenance reservoir 60A may not be provided.

Further, in the above-described embodiment, the reduction of unnecessary components such as vibrations due to external factors and the smoothing of the pressure waveform obtained from the pressure change due to breathing are performed by the noise reduction diaphragm 27A and the maintenance of the breathing detection sensitivity. Although the operation was performed in the storage pool 60A, the present invention is not limited to this, and may be performed in the apnea detection unit 51, for example. That is, the apnea detection unit 51 electrically removes unnecessary components such as vibrations due to external factors included in the pressure waveform and extracts a pressure waveform that detects only the intended respiration. Waveform smoothing can also be performed by performing a moving average method that corrects the waveform with the average value of the data (1) and its own data (five consecutive data). At this time, the maximum value in the smoothed pressure waveform is detected, and the finally required respiratory rate is counted. If the breathing interval is equal to or longer than a preset breathing stop time, it is determined as apnea.

The through-hole functioning similarly to the pressure-receiving chamber open-to-atmosphere 44A is not limited to the case where the pressure-receiving chamber 44 is directly provided. May be provided at a location.

Further, in the above embodiment, the upper plate 22 is
Although it is made of a light foaming resin material, the material is not limited to this, and it may be made of a material such as a resin plate, a wooden board, or cardboard, and in other words, may be made of an elastic material. Further, the upper plate 22 may not be provided. In this case, for example, the mattress 10 is placed directly on the pressure-sensitive pipe 21.
1 and the like may be provided so that a pressure change is generated in the pressure-sensitive pipe 21 as the mattress 101 is deformed.

Further, in the above embodiment, the lower plate 23 is
It was made of hard plastic, but not limited to this,
For example, it may be formed of a wooden board, a resin board, or the like. In short, as the hard member constituting the lower plate 23, the upper plate 22
Any member may be used as long as it does not absorb the pressure applied to the pressure-sensitive pipe 21 due to the deformation of the pressure-sensitive pipe 21 and generates a pressure change inside the pressure-sensitive pipe 21. Further, the lower plate 23 may not be provided. In this case, for example, when the detection mat 2 is installed on the floor of the bed, the floor may be formed of a hard member, and the pressure-sensitive pipe 21 may be directly disposed on the floor.

The pressure-sensitive portion is not limited to the linear pressure-sensitive pipe 21, but may be, for example, a substantially circular pressure-sensitive pipe 21 as shown in FIG. Further, the pressure-sensitive portion may not be formed of a pipe-shaped hollow body, for example, may be a flat balloon-shaped or plate-shaped, and the shape of the pressure-sensitive portion may be appropriately determined in practice. . However, when formed in a pipe-shaped hollow body, the detection sensitivity can be increased by shortening the length and minimizing the internal volume of the pressure-sensitive pipe 21, and it is easy to manufacture and cheap. Is preferred.

Further, the means for closing one end of the pressure-sensitive pipe 21 is not limited to the plug 26. The lower plate may be formed by heat-welding or bending the end of the pressure-sensitive pipe 21 itself, sandwiching it with a pinch or the like, or bending it. Alternatively, it may be replaced by fixing to 23.

Further, in the above embodiment, the detection mat 2
Was formed so as to be suitable for both heavy and light newborns, but is not limited to this. For example, the thickness, material, flexural modulus or pressure-sensitive pipe of the upper plate 22 may be different for each newborn's weight. The detection mat 2 may be formed so as to be able to cope with the subject 100 having a different weight by changing the sensitivity of 21.

The noise-reducing diaphragm 27A, the respiration detection sensitivity maintaining reservoir 60A, the pressure-reception chamber air-release aperture 44A, or the configuration in which the back-pressure chamber air-release aperture 46A is added to the pressure-sensitive pipe in the above embodiment. 21 may be used as the sensitivity adjusting means, and may be replaced with an appropriate variable throttle or another fluid circuit element.

Further, in the second embodiment, the pressure-sensitive pipe 21 is fixed to the plate-like member 23D by bonding with a double-sided tape. However, the present invention is not limited to this. For example, as shown in FIG. A pressure-sensitive pipe 21 provided with a fixing portion 21C fixed to the plate-like member 23D is manufactured by extrusion or the like, and the fixing portion 21C of the pressure-sensitive pipe 21 is pressed onto the plate-like member 23D with a holding metal 23H, and a nail or a screw is formed. The pressure-sensitive pipe 21 may be fixed by fixing it with 23F or the like.

In the second embodiment, the plate-like member 2
The screws 23F are attached to both ends along the longitudinal direction of the 3D. However, the present invention is not limited to the screws 23F, and may be, for example, a spacer or the like arranged in a continuous or piece-like manner at predetermined intervals. That is, it is sufficient that the inner diameter of the pressure-sensitive pipe 21 is not completely crushed regardless of whether the crushing amount regulating means such as the groove 23A, the screw 23F, and the spacer are formed in a continuous shape or a piece shape.

In the second embodiment, the screw 23F
Are arranged at regular intervals. However, the present invention is not limited to this. For example, the screws 23F are intensively arranged in a portion where the load of the subject 100 is most applied, and the screws 23F are increased in other portions. It may be arranged with a gap.

The means for regulating the amount of collapse of the pressure-sensitive pipe 21 is not limited to the one formed by the groove 23A or the one formed by the screw 23F, but is formed so that the inner diameter of the pressure-sensitive pipe 21 is not completely collapsed. If it is a member that can be prevented or
For example, a pressure-sensitive pipe 21 may be installed in the concave portion using a long member having a concave cross section separate from the lower plate 23, and its shape and configuration may be appropriately selected in implementation.

[0076]

As described above, according to the apnea detecting apparatus of the present invention, it is not necessary to wear any cords or sensors, so that the subject does not have any discomfort. It is possible to detect respiration, and to measure the movement of the body including the respiration of the subject without fail to notify the apnea.

[Brief description of the drawings]

FIG. 1 is a sectional view and a block diagram showing an apnea detecting apparatus according to a first embodiment of the present invention.

FIGS. 2A and 2B are cross-sectional views taken along the line II-II of FIG. 1, wherein FIG. 2A is a view showing a state where a subject is not placed, and FIG.

FIG. 3 is a sectional view taken along the line III-III in FIG. 1;

FIG. 4 is a cross-sectional view illustrating an example of a structure of a pressure sensor unit used in the first embodiment of the present invention.

FIG. 5 is a diagram showing a pressure change in a pressure measurement path during sleep according to the first embodiment of the present invention.

FIG. 6A is a cross-sectional view illustrating a state in which a subject is not placed, and FIG. 6B is a cross-sectional view illustrating a state in which the subject is placed in the second embodiment of the present invention.

FIG. 7 is a perspective view showing an arrangement state of a pressure-sensitive pipe according to a second embodiment of the present invention.

FIG. 8 is a schematic sectional view showing an arrangement state of pressure-sensitive pipes according to a second embodiment of the present invention.

FIG. 9 is a cross-sectional view showing a substantially circular pressure-sensitive pipe according to a modification of the present invention.

FIG. 10 is a sectional view showing another modified example of the present invention, showing a shape and a fixing method of a pressure-sensitive pipe.

[Explanation of symbols]

 DESCRIPTION OF SYMBOLS 1 Apnea detection apparatus 2 Detection mat 4 Pressure measurement means 5 Apnea detection means 21 Pressure sensitive pipe which is a pressure sensitive part 22 Upper plate 23 Lower plate 23A Groove 23D which is a means for regulating the amount of crush of the pressure sensitive pipe 23D Plate member 23F Feeling Screw 27A as a means for regulating the amount of collapse of the pressure pipe 27A Noise reduction throttle 30 Pressure measurement path 44 Pressure receiving chamber 44A Pressure receiving chamber air opening throttle as a through hole 46 Back pressure chamber 46A Back pressure chamber air opening throttle as a through hole 60A Breathing Reservoir for maintaining detection sensitivity

 ──────────────────────────────────────────────────続 き Continuing from the front page (72) Inventor Shinichi Tsuchiya 1-30-4 Higashimagome, Ota-ku, Tokyo Nagano Keiki Co., Ltd. (72) Inventor Masaaki Inoue 2-16-9 Yushima, Bunkyo-ku, Tokyo Chidori Building 302 Skynet Co., Ltd. (72) Inventor Hiroshi Uno 2-16-9 Yushima, Bunshima-ku, Tokyo Chidori Building 302 Skynet Co., Ltd. F-term (reference) 4C038 ST04 SV01 SX01

Claims (7)

[Claims] 1. An apnea detecting apparatus for detecting an apnea state of a subject, comprising: a detection mat on which the subject is mounted directly or via a mattress; and a detection mat provided in the detection mat; A pressure-sensitive unit in which a pressure change occurs in synchronization with the movement of the body including the subject's breathing, and a pressure measuring unit that measures the pressure inside the pressure-sensitive unit at predetermined intervals by a pressure sensor unit, An apnea detecting device, comprising: apnea detecting means for receiving a signal from the pressure measuring means and detecting an apnea state from a pressure change of the pressure-sensitive portion. 2. The apnea detecting apparatus according to claim 1, wherein said pressure-sensitive portion is formed of an elastically deformable pipe-shaped hollow body. 3. The apnea detecting apparatus according to claim 1, wherein the detection mat includes the pressure-sensitive portion, and upper and lower plates disposed above and below the pressure-sensitive portion. The upper plate is formed so as to be elastically deformable by breathing of the subject, and a pressure change is generated in the pressure-sensitive portion due to the deformation of the upper plate due to the movement of the subject's body. Wherein the lower plate is formed of a hard member. 4. The apnea detecting apparatus according to claim 3, wherein the pressure-sensitive portion is formed of an elastically deformable pipe-shaped hollow body, and the lower plate has a crush amount of the pressure-sensitive portion. An apnea detecting device, comprising a crush amount regulating means for regulating. 5. The apnea detecting apparatus according to claim 1, wherein the pressure sensor section is provided with a pressure receiving chamber for receiving a pressure from inside the pressure sensing section. An apnea detecting apparatus, wherein a through-hole communicating with the atmosphere is provided in a pressure measurement path formed from a pressure unit to the pressure receiving chamber. 6. The apnea detecting apparatus according to claim 1, wherein the pressure sensor section includes a pressure receiving chamber that receives a pressure from inside the pressure sensing section, and is adjacent to the pressure receiving chamber. A back pressure chamber is provided, and the pressure receiving chamber and the back pressure chamber are each provided with a through hole that communicates with the atmosphere. 7. The apnea detecting apparatus according to claim 1, wherein the pressure sensor section is provided with a pressure receiving chamber for receiving a pressure from the inside of the pressure sensing section. An apnea detecting apparatus, characterized in that a pressure measurement path formed from a pressure section to the pressure receiving chamber is provided with a noise reduction aperture and a reservoir for maintaining respiration detection sensitivity.