JP2011200610A - Electronic sphygmomanometer - Google Patents

Abstract

PROBLEM TO BE SOLVED: To provide an electronic sphygmomanometer capable of accurately measuring a blood pressure even if a measurer inserts an upper arm therein from either direction, and suppressing the production cost.SOLUTION: This electronic sphygmomanometer 1 is disposed with K-sound detecting air bags at both arm insertion slot sides of a cylindrical arm band; determines which is located on the downstream side of the arm based on a difference in changes in the amplitudes of pulse waves detected from low frequency components or high frequency components of signals of both the K-sound detecting air bags, an occurrence time difference getting to a threshold or more, or the presence/absence of the signals getting to the threshold or more; and measures the blood pressure using the signal of the determined downstream-side K-sound detecting air bag.

Description

  The present invention relates to an electronic sphygmomanometer, and in particular, an arm band part can be separated from a sphygmomanometer body, and even if the place of installation of the sphygmomanometer body is away from the measurer, the measurer stretches his back in the sitting position and applies abdominal pressure. The present invention relates to an electronic sphygmomanometer of a type that can be measured in the absence of the condition.

In recent years, pseudohypertension due to white coat hypertension has been a problem in blood pressure measurement for hypertension treatment performed in medical institutions. As a cause of this pseudohypertension, mental instability such as tension and anxiety in front of a doctor in a hospital is considered. On the other hand, attention has been focused on blood pressure values measured alone in a mentally stable home. For this reason, an electronic sphygmomanometer of the type that is used for home blood pressure measurement and is measured by one person is attracting attention.
The problem with this type of sphygmomanometer is how to wear the armband on the arm. When the position of the air bag for ischemia in the armband is not appropriate for the upper arm, or when the wrapping strength is not appropriate for the upper arm, the pressure of the air bag for ischemia in the armband is not correctly applied to the upper arm, Blood pressure may be measured high. In recent years, in order to solve this, simply by inserting the arm into the cylindrical armband, the air bag for ischemia in the armband is automatically placed at the correct position on the arm, and blood pressure is applied with the correct wrapping strength. An electronic sphygmomanometer that integrates a sphygmomanometer body and an arm band that can perform measurement has been developed (see Patent Document 1).

However, when the user uses the sphygmomanometer, the armband part into which the arm is inserted is integrated with the sphygmomanometer body, so if the position of the sphygmomanometer body is away from the measurer, It is easy to measure in the forward bending state. For this reason, the abdomen of the measurer is compressed and the abdominal pressure increases, and as a result, a phenomenon in which the blood pressure increases may be seen. This increase in blood pressure has been pointed out as the occurrence of new pseudohypertension.
Therefore, in order to deal with the inconvenience of the occurrence of such pseudo-hypertension, the armband can be separated from the sphygmomanometer body, and even if the place where the sphygmomanometer body is installed is away from the measurer, the measurer is in the sitting position. A type of electronic sphygmomanometer has been developed that can perform measurements without applying abdominal pressure when the back is stretched.
The armband part needs to press the arm with a stress corresponding to the internal pressure of the built-in air bag for ischemia. For that purpose, it is necessary to contact an area of 80% or more of the arm circumference in the radial direction of the arm and 40% or more of the arm circumference length in the thrust direction in a state where the air bag for ischemia does not fully expand.
For sphygmomanometers that can be measured by simply attaching the armband to the arm and manipulating the length of the armband before measurement, and making sure that it does not adhere to the arm thickness, the arm size ( 20 to 33 cm) is required to be automatically handled.
At present, in order to cope with these, a method of automatically attaching an air bag for ischemia to an arm by tightening a wire wound around the air bag for ischemia, or an outside of an air bag for ischemia. A close-up air bag is installed, and the close-up air bag is inflated to close the air bag against the arm, or a large air bag is inflated to achieve close contact and ischemia with a single air bag. There is a way to do it.
Of the above methods, the method of inflating one air bag greatly has the advantage that the structure is simple, but it has the problem that the air volume of the air bag is larger than other methods. is doing.
Due to this problem, the pulse wave detected by the air bag for ischemia is small, the oscillometric method using the change of this pulse wave cannot be adopted, and the Rivaloch Korotkoff method for detecting the K sound signal downstream of the armband, Alternatively, it is necessary to adopt a photoelectric volume pulse wave method that detects a change in blood vessel volume by absorption attenuation of infrared light, or an ultrasonic method that detects a change in blood vessel wall due to blood flow with an ultrasonic wave.

JP 2005-237427 A

In the electronic sphygmomanometer described above, the Ribaroch Korotkoff method is used as an example of a blood pressure measurement method, and blood pressure is measured by detecting Korotkoff sounds (K sounds).
After inflating the air bag for ischemia in the bracelet to increase the internal pressure of the air bag for ischemia above the maximum blood pressure, and once closing the blood vessel, the air in the air bag for ischemia is gradually exhausted to increase the pressure inside the air bag for ischemia After the detection of the generation and disappearance of the K sound signal that occurs on the downstream side of the armband in the process, the internal pressure of the air bag for ischemia when the K sound signal is generated is the maximum blood pressure value and the internal pressure at the time of disappearance The blood pressure is determined using the minimum blood pressure value.
The K sound is generated by the blood flow that opens under the brachial blood vessel and flows downstream, and the pressure in the air bag for ischemia falls below the minimum blood pressure while changing the tone as the pressure is reduced, until the blood vessel is no longer occluded. It is a sound signal generated in synchronization with the beat.
Therefore, since the arm band of this electronic blood pressure monitor employs a structure in which a K sound sensor is provided at one end of the air bag for ischemia, the end where the K sound sensor is mounted by the measurer is downstream. Normal blood pressure can be measured by inserting it into the upper arm in the direction of the side (hand side).
However, if the measurer mistakenly inserts the armband part in the reverse direction and the end on which the K sound sensor is mounted is placed on the upstream side (end on the shoulder side) of the air bag for ischemia, the K sound will be emitted. It becomes impossible to capture accurately and blood pressure cannot be measured correctly.
Accordingly, in order to solve the above-described problems, the present invention has an object to provide an electronic sphygmomanometer that can accurately measure blood pressure even if a measurer inserts an arm band part into an upper arm from either end. And

The electronic sphygmomanometer of the present invention is an electronic sphygmomanometer that measures with the upper arm, a cylindrical armband portion that can be inserted into the upper arm and can block the brachial artery, and a sphygmomanometer body formed separately from the armband portion, And the armband portion is disposed along the inside of the cylindrical armband in a cylindrical shape, and is supplied with air to block the artery of the upper arm, and ischemic air bag A pressure sensor that detects pressure fluctuations in the air in the ischemic bladder when the pressure is increased by supplying air therein, and a side of the tubular armband portion that is in close contact with the upper arm of the ischemic bladder. It has a K sound detection air bag which is disposed at a position near each end of the two openings, and has an air volume smaller than that of the air bag for ischemia, and further for detecting the K sound. A K sound sensor for detecting a K sound signal by detecting a change in air in the air bag, A frequency signal component lower than the frequency component of the K sound from the K sound detection air bag disposed at the one opening end obtained from the K sound sensor generated during pressure increase, and for the ischemia obtained from the pressure sensor Attenuation change of the amplitude of the frequency signal component lower than the frequency component of the K sound from the air bag, and a frequency signal lower than the frequency component of the K sound from the K sound detecting air bag disposed at the other opening end. For detecting the previous K sound, which is placed in either of the two openings of the armband, due to the difference in attenuation of the amplitude of the frequency signal component lower than the frequency component of the K sound from the air bag for ischemia obtained from the component and the pressure sensor It is determined whether the air bag is disposed on the downstream side (hand side) of the living body, and blood pressure is measured using the signal.
According to the above configuration, blood pressure can be accurately measured regardless of the direction in which the measurer inserts the armband portion into the upper arm.
That is, it is reliably determined whether one of the K sound detection air bag at one position of the armband portion or the K sound detection air bag at the other position is arranged on the downstream side (hand side) of the artery of the upper arm. The blood pressure can be measured from the air vibration in the air bag for detecting K sound on the side arranged on the downstream side of the artery of the upper arm.

Preferably, a plurality of the K sound detection air bags at the one position and the K sound detection air bags at the other position are respectively arranged along a circumferential direction of the hemostasis air bag. And
According to the above configuration, when the measurer inserts the armband into the upper arm, even if the K sound sensor of the armband is displaced from the artery position and rotated in the circumferential direction of the upper arm, Since the sound detection air bag can be disposed at a position near the artery of the upper arm, the K sound signal can be accurately obtained.

  Preferably, the K sound sensor is a condenser microphone disposed in the sphygmomanometer body disposed in the sphygmomanometer body and connected to the K sound detection air bag by a tube.

Preferably, a sheet-like backing having elasticity is attached between the air bag for ischemia and the air bag for detecting the K sound.
According to the above configuration, the influence of the compliance of the air bag for ischemia is reduced, and the K sound detection air bag is a device for efficiently detecting the K sound signal, thereby performing the K sound detection more accurately. Can do.

  According to the present invention, it is possible to provide an electronic sphygmomanometer that can accurately measure blood pressure even if the measurer inserts the upper arm from any direction of the armband.

It is a perspective view which shows preferable embodiment of the electronic blood pressure monitor of this invention from the front side. It is a disassembled perspective view of the arm band part of an electronic blood pressure monitor. It is sectional drawing which shows the internal structure of the arm band part of an electronic blood pressure monitor. It is a figure which shows the example of a shape of the bone member arrange | positioned inside an outer cloth. It is a side view which shows the arm band part which has a bone member. 6A is a perspective view showing the unit UT of the outer cloth and the air bag for ischemia, and FIG. 6B is a perspective view of the unit UT seen from another direction. ) Is a perspective view showing a state in which the unit UT is folded. 7A is a perspective view showing an air bag for ischemia and an air bag for detecting K sound, and FIG. 7B is an air bag for preventing blood, an outer cloth, an inner cloth cover, and air for detecting K sound. It is a figure which shows a bag. It is a figure which shows the example of a sheet | seat which forms the air bag for ischemia. It is a figure which shows a small air bag. It is a block diagram which shows the connection relationship of the air bag for ischemia, the air bag for K sound detection, a pump, and a K sound sensor. It is a block block diagram of an electronic sphygmomanometer. It is a blood-pressure measurement flowchart of this invention. FIG. 13A shows a frequency signal component signal (low frequency component signal) lower than the frequency component of the K sound from the air bag for ischemia obtained from the pressure sensor during pressurization, and the downstream side (hand side) of the armband portion. The low frequency component signal from the K sound detection air bag obtained from the K sound detection air bag through the K sound sensor is shown. FIG. 13B shows a low-frequency component signal from the ischemic bladder obtained from the pressure sensor during pressurization and a K-sound detection bladder from the upstream side (shoulder side) of the armband portion through the K-sound sensor. The low frequency component signal from the air bag for K sound detection to be shown is shown. From the magnitude of attenuation of the pulse wave amplitude of the time-series pulse wave detected from the low frequency component signal from the air bag for ischemia obtained from the pressure sensor and the low frequency component signal from the air bag for K sound detection during pressure increase It is a flowchart which shows the process of determining whether the air bag for K sound detection exists in an upstream or downstream. FIG. 15A shows the frequency component (high frequency component) of the K sound from the K sound detecting air bag obtained through the K sound sensor from the K sound detecting air bag on the downstream side (hand side) of the armband during decompression. Signal). FIG. 15B shows a high-frequency component signal from the K sound detection air bag obtained through the K sound sensor from the K sound detection air bag on the upstream side (shoulder side) of the armband during decompression. It is a flowchart which shows the process of determining whether the corresponding K sound detection air bag exists in the upstream or downstream from the high frequency component signal from the K sound detection air bag during decompression. FIG. 17A shows a high-frequency component signal from the K sound detection air bag obtained through the K sound sensor from the K sound detection air bag on the downstream side (hand side) of the armband during pressure increase. FIG. 17B shows a high-frequency component signal from the K sound detection air bag obtained through the K sound sensor from the K sound detection air bag on the upstream side (shoulder side) of the armband during pressure increase. It is a flowchart which shows the process of determining whether the corresponding K sound detection air bag exists in the upstream or downstream from the high frequency component signal from the K sound detection air bag during pressure increase.

Hereinafter, preferred embodiments of the present invention will be described in detail with reference to the drawings.
(Embodiment 1)
FIG. 1 is a perspective view showing a preferred embodiment of the electronic sphygmomanometer of the present invention from the front side, and FIG. 2 is an exploded perspective view of an arm band part of the electronic sphygmomanometer. FIG. 3 is a cross-sectional view showing the internal structure of the armband portion of the electronic blood pressure monitor.
The electronic sphygmomanometer 1 shown in FIG. 1 is also referred to as an automatic electronic sphygmomanometer, can separate the armband portion 2 from the sphygmomanometer main body 10, and the measurer is in the sitting position even if the place where the sphygmomanometer main body 10 is installed is away from the measurer. This is an electronic sphygmomanometer of the type that can be measured without stretching the back and applying abdominal pressure. This electronic sphygmomanometer 1 is a device that uses the Rivaloch Korotkoff method as an example of a blood pressure measurement method, and detects blood pressure by detecting the Korotkoff sound (K sound). As shown in FIG. 1, the electronic sphygmomanometer 1 includes an armband portion 2 of a soft cylindrical body made of a deformable and soft material, and a sphygmomanometer body 10. The armband part 2 and the blood pressure monitor main body 10 are separate bodies.

As shown in FIG. 3, this electronic sphygmomanometer 1 is a sphygmomanometer that measures blood pressure by inserting the armband portion 2 into the upper arm T of the measurer from the insertion opening 11R to the insertion opening 11P along the direction D1. . As shown in FIG. 1, a tube 4 as an air conduit for supplying and exhausting air to and from the blood bag 14 of the armband 2 and two blood bags 500A1 on the same side for detecting the K sound signal. An air connector 4Q that can be attached to and detached from the sphygmomanometer main body 10 by means of an elastomer tube of a multi-cylinder tube (also referred to as a multi-conduit) having 500A2 and tubes 4P1 and 4P2 connected to tubes from 500B1 and 500B2. The sphygmomanometer body 10 and the armband part 2 are connected to each other. The air bag 14 for ischemia of the armband 2 is connected to the pumps 44 and 45 side of the sphygmomanometer body 10 through the tube 4.
The tubes 4P1 and 4P2 are connected to the pumps 44 and 45 of the sphygmomanometer main body 10 through mechanical filters.

First, the structure of the sphygmomanometer body 10 will be described with reference to FIG.
As shown in FIG. 1, the sphygmomanometer body 10 includes a casing 30 and a display unit 31. The casing 30 is a member having a thin internal space made of plastic, for example, and has an inclined upper surface portion 32, a front end surface portion 33, a rear end surface portion 34, side surface portions 35 and 36, and a bottom surface portion 42. .
As shown in FIG. 1, an inclined display portion 31 is disposed on the upper surface portion 32 of the casing 30 so that the measurer can easily confirm the display content of the display portion 31. The casing 30 is provided with a start / stop button 37 as an example of a measurement start operation unit, a memory call / time / alarm setting button 38, and a button 39 that is not stored. This button is used to start or stop the blood pressure measurement operation when the measurer presses the start / stop button 37.

  In FIG. 1, when setting the time, for example, by simultaneously pressing and holding the memory call / time / alarm setting button 38 and the button 39 not to be stored, the display unit can be operated as an operation / setting / input function. A time setting screen is displayed at 31, and the time displayed on the time setting screen can be set while being selected by the memory call / time / alarm setting button 38.

  In FIG. 1, for example, by pressing the memory call / time / alarm setting button 38, for example, 100 blood pressure measurement records in the past can be displayed on the display unit 31. The maximum blood pressure value, the minimum blood pressure value, the pulse rate, and the date and time displayed on the display unit 31 can be displayed in order each time the memory call / time / alarm setting button 38 is pressed. The button 39 that is not stored is a button that is pressed only when, for example, the measurer does not store the maximum blood pressure value, the minimum blood pressure value, the pulse value, and the pulse pressure in the memory unit 69.

  The display unit 31 is arranged along the X direction. For example, a liquid crystal display device can be used as the display unit 31. As shown in FIG. 1, for example, the display unit 31 includes a maximum blood pressure value, a minimum blood pressure value, a pulse rate, a pulse pressure, and a display mark during measurement operation. Various measurement values such as battery replacement display marks can be displayed.

  As shown in FIG. 1, the side portions 35 and 36 are formed in a curved surface so that the measurer can easily hold the blood pressure monitor main body 10. The memory call / time / alarm setting button 38 and the non-stored button 39 are arranged in the vicinity of the display unit 31 on the upper surface 32. As shown in FIG. 1, the casing 30 includes a K sound sensor 600A, 600B, a speaker 43, two pumps 44, 45, an exhaust valve 46, a control valve 47, and a circuit board including a control system. 48 and a memory unit 69 are arranged. The speaker 43 is provided to output a voice guide or a music guide. In the drawing, a condenser microphone is shown as an example of the K sound sensors 600A and 600B.

Next, the structure of the armband portion 2 will be described with reference to FIGS.
As shown in FIG. 1, when measuring blood pressure, the measurer inserts the armband portion 2 into the upper arm T from the opening 11R in the direction D1. Further, in order to measure blood pressure simply by positioning the armband part 2 on the upper arm part above the elbow, the substantially belt-shaped structure (tubular body) in which both ends where the armband part 2 can be inserted into the upper arm T are cut off. )

  As shown in FIG. 2 and FIG. 3, the armband portion 2 is a deformable and soft cylindrical body, and is made lightweight. The armband portion 2 has an air bag for ischemia (also referred to as a large cuff or a large bag) 14, an outer cloth 16, and an inner cloth 17. The outer cloth 16 is also called an outer cloth cover, and the inner cloth 17 is also called an inner cloth cover. Both the outer cloth 16 and the outer cloth 17 are preferably cylindrical members (tubular bodies).

The inner surface of the outer cloth 16 can cover the outer surface of the air bag 14 for ischemia, and the inner cloth 17 covers the inner surface of the air bag 14 for ischemia.
Here, the inner cloth 17 uses a woven fabric rich in stretchability, and the outer cloth 16 is deformed, but it is preferable to use a member that has lower stretchability than the inner cloth 17 and preferably hardly stretches. Both the outer cloth 16 and the inner cloth 17 are cylindrical members (tubular bodies).
That is, since the inner cloth 17 that is a contact cloth portion that comes into contact with the measurement part of the human body has elasticity and smoothness, it is easy to insert the measurement part of the upper arm.
The outer cloth 16 is joined to the outer side of the inner cloth 17 that is a contact cloth portion so as to accommodate the air bag 14 for ischemia, and the outer cloth 16 is deformable but has a very low or almost no stretchability. For example, a fabric (201BE) which is difficult to stretch can be used, and the tensile strength is 1445 N / in for the vertical and 827 N / in for the horizontal as measured by the JIS L1096-A method. As the outer cloth 16, for example, a 100% polyester fabric can be used.

  The inner cloth 17 is a cylinder that covers the inner surface of the air bag 14 for ischemia, is deformable, has elasticity, and is a contact cloth portion that comes into contact with the surface to be measured of the upper arm T. For example, a jersey-like easily stretchable fabric, which is a smooth and stretchable fabric member, can be used as the inner fabric 17, and the tensile strength is 94.9 N / W as a value measured by the JIS L1096-A method. In, the width is 150.7 N / in. Tensile elongation is 517% in length and 400% in width as measured by JIS L1096-A method. The inner fabric is, for example, a fabric made of 80% nylon and 20% polyurethane.

The outer cloth 16 shown in FIG. 1 is disposed outside the ischemic air bag 14, and the inner cloth 17 is disposed inside the ischemic air bag 14. The outer cloth 16 and the inner cloth 17 are joined by joint portions 77 on both sides, and the air bag 14 for ischemia is accommodated in the space formed by the outer cloth 16 and the inner cloth 17. The joint portions 77 on both sides are formed by sewing using a thread, high-frequency fusion, bonding using an adhesive, or the like.
Further, as shown in FIG. 3, the value obtained by subtracting the width W along the direction D1 through which the upper arm of the hemostatic air bag 14 is passed from the width S along the direction D1 through which the upper arm of the outer cloth 16 as the outer member is passed is , Preferably 4 cm or less. As described above, the value of (width S−width W) is set to 4 cm or less because the air bag 14 for hemostasis is not stopped with respect to the outer cloth 16 and the dimension of the outer cloth 16 is allowed to have a margin. In order to cope with the expansion and contraction of the air bag 14 for ischemia. If the value of (width S−width W) exceeds 4 cm, the outward expansion of the air bag for ischemia is not regulated, and sufficient ischemia cannot be performed in the case of a thin arm, which is not preferable.

  1 is compressed by the air supplied through the tube 4 from the pumps 44 and 45 of the sphygmomanometer body 10 to compress the upper arm T. The air bag 14 for ischemia is, for example, vinyl chloride. , Polyurethane, synthetic rubber, natural rubber and other materials. The upper arm T is pressed into the air bag 14 by being inflated by being supplied with air through the tube 4 by the operation of pumps 44 and 45 indicated by broken lines in the blood pressure monitor main body 10 shown in FIG. In order to reduce the internal pressure of the ischemic bladder 14 at a constant speed, the control valve 47 can gradually exhaust the air from the ischemic bladder 14 to the outside. Air can be rapidly exhausted from inside 14. The detailed structure of the air bag 14 for ischemia will be described later.

Next, with reference to FIG. 4 and FIG. 5, the bone member 150 arrange | positioned inside the outer fabric 16 is demonstrated.
FIG. 4 shows an example of the shape of the bone member 150 disposed inside the outer fabric 16, and FIG. 5 is a side view showing the armband portion 2 having the bone member 150.
As shown in FIG. 4, the bone member 150 is fixed to the inner surface 16N of the outer cloth 16 by an adhesive, for example. The bone member 150 is a metal product or a plastic molded product, and is arranged along the longitudinal direction 16S of the outer cloth 16. The bone member 150 has a plurality of bones 150H. The bones 150H are arranged at the same interval so as to be parallel to the short direction 16T of the outer cloth 16. Each bone 150H has a circular cross-section or a rectangular cross-section, but the cross-sectional shape and number are not particularly limited.

  As described above, since the bone member 150 is disposed on the inner surface 16N of the outer cloth 16, even when the soft armband portion 2 is filled with air, the air for ischemia is filled with air. It is reduced that the bag 14 and the outer cloth 16 swell along the longitudinal direction 16S. Therefore, even in a thin arm, it is possible to hold the upper arm with a pressing force according to the internal pressure of the air bag for ischemia, so that the range of the applicable arm circumference of the armband can be increased. 6 and 7 show examples of the shape of the air bag 14 for ischemia and the air bag for detecting a K sound.

Here, structural examples of the air bag 14 for ischemia and the air bags 500A1, 500A2, 500B1, and 500B2 for detecting the K sound will be described.
FIG. 8 shows an example of a sheet for forming the ischemic air bag 14.
First, the structure of the air bag 14 for ischemia will be described. A sheet SW shown in FIG. 8 is a substantially rectangular plastic sheet, for example, and is formed of a polyurethane sheet as an example. The sheet SW includes a dust filter connecting pipe 220, four broken line portions (an example of a bent portion) 222, and joint portions 223 and 224.

As shown in FIG. 8, the air capacity in the sheet SW constituting the ischemic air bag 14 should be supplied from the pumps 44 and 45 to the inside of the sheet SW, that is, the inside of the ischemic air bag 14 as much as possible. In order to reduce the amount of air, an expandable / contractible cushion material 240 is disposed inside the seat SW.
As shown in FIG. 2, when the air bag 14 is inflated by inflating with air, the air bag 14 is divided into four parts so that the air bag 14 is inflated. The cushion material 240 and the K sound detecting air bag 500 are disposed between the plurality of broken line portions 222.

As shown in FIG. 7 (A) and FIG. 8, there are two K sound detection air bags 500A1, 500A2 and 500B1, respectively, on the upstream side 14M and the downstream side 14N of the inner side surfaces 14G, 14F of the ischemic air bag 14. 500B2 is arranged.
Air for detecting K sound is provided at one end 14M of the inner side surface (14G, 14F) of the air bag 14 and the other end 14N of the inner side surface (14G, 14F) of the air bag 14 respectively. Bags 500A1, 500A2 and 500B1,500B2 are arranged.
As described above, the K sound detection air bags are disposed at the end portions 14M and 14N of the inner side surfaces 14G and 14F of the ischemic air bag 14 for the following reason.
That is, since the air bag for ischemia 14 is mounted in a cylindrical armband in a shape rolled up so that the air bags 500A1, 500A2 and 500B1, 500B2 for K sound detection come inside, the K sound detection The air bags 500A1 and 500A2 are positioned on one insertion port side of the cylindrical armband, and 500B1 and 500B2 are positioned on the other insertion port side of the cylindrical armband. Even if it is inserted from the mouth, it can be inserted into the upper arm in the direction in which the end where the K sound sensor is mounted is arranged on the downstream side (hand side).
In addition, a plurality of K sound detection air bags 500 are disposed on the living body contact surface of the ischemic air bag along the circumferential direction of the armband portion 2 at the 14M side end and the 14N side end, respectively. When the upper arm T is inserted into the armband 2, the K sound detection air bag 500 rotates from the position on the brachial artery to the periphery of the upper arm T and is inserted into the upper arm T in a state of being displaced from the artery position. Even if the armband portion 2 is inserted into either the upper arm T of the right arm or the left arm, any one of the K sound detection air bags 500 is disposed at a position close to the artery of the upper arm T. K sound signal can be measured.

Next, referring to FIG. 10, the connection relationship between the above-described air bag 14 for ischemia, air bag 500 for detecting K sound (500A1, 500A2, 500B1, 500B2), pumps 44 and 45, K sound sensor 600, and the like will be described. To do.
As shown in FIG. 10, the Korotkoff sound (K sound) detection system 50 includes four K sound detection air bags 500 of the armband portion 2, two K sound sensors 600 (600A, 600B), and two mechanical filters. 700 (700A, 700B).
The two K sound detection air bags 500 on the same insertion port side of the armband are connected to the K sound sensor 600 via the tubes 4P (4P1, 4P2), The pressure fluctuation of air is transmitted to each K sound sensor 600 through the tube 4P. The two K sound sensors 600 are connected to the mechanical filters 700 through the tubes 4R.

  The mechanical filter 700 of FIG. 10 eliminates the control sound of the exhaust valve 46, the control sound of the control valve 47, and the pulsation caused by the three-cylinder pump chambers of the pumps 44 and 45, thereby affecting the detection signal of the condenser microphone 600. It is arranged not to give it, and to insert a small amount of air necessary for measurement during pressurization. The K sound detection air bladder 500 can be disposed at a position near and far from the artery of the upper arm T.

Next, FIG. 11 is a block diagram of the electronic blood pressure monitor 1 of FIG.
The functional blocks of the electronic sphygmomanometer 1 shown in FIG. 11 will be described. The functional blocks of the electronic sphygmomanometer 1 are indicated by broken lines, as shown in the Korotkoff sound (K sound) detection system 50, the pressurization system 51, the exhaust system 52, the pressure detection system 53, the power supply system 54, the sound system 55, and the control system 56. And have.

  The control system 56 includes a drive unit 58 of the display unit 31, a timer 59, a memory unit 69, and the like. The drive unit 58 of the display unit 31 controls the display unit 31 to display items to be displayed. The memory unit 69 is a ROM (read only memory) in which a program to be processed by the CPU (central processing unit) of the control system 56 is stored. The timer 59 counts various operation times. The operation unit 57 is electrically connected to the control system 56, and includes the start / stop button 37, the volume button 38, and the mode selection button 39 described above.

The Korotkoff sound (K sound) detection system 50 of FIG. 11 has already been described with reference to FIG. 10, but the four K sound detection air bags 500 of the armband portion 2, the two K sound sensors 600, and Two mechanical filters 700 are provided. The two K sound detecting air bags 500 are connected to the respective K sound sensors 600 through the tubes 4P.
The pressure fluctuation of the air in each K sound detecting air bag 500 is transmitted from the K sound detecting air bag 500 to the K sound sensor 600 through the tube 4P.
Each mechanical filter 700 is connected to the pressure sensor 64, the pumps 44 and 45, the exhaust valve 46, and the control valve 47 via the piping part 63.

  The K sound sensor 600 is amplified by the amplification unit, converted into a digital signal by the A / D conversion unit, and electrically connected to the control system 56. Each of the K sound sensors 600 is a K sound detection air bag. The vibration of the air in 500 is converted into an electrical signal and supplied to the control system 56.

A pressure detection system 53 shown in FIG. 11 includes a piping part 63, a pressure sensor 64, and a tube 4. The pressure sensor 64 is electrically connected to the control system 56 via an amplifier, a filter, and an A / D converter.
As shown in FIG. 1, when the measurer inserts the armband portion 2 into the upper arm T from the direction D1, which is the insertion direction, the control system 56 of FIG. 11 changes the air pressure input from the K sound sensor 600A. From the signal, a K sound signal, a generation point and a disappearance point of the K sound signal are detected.
Alternatively, when inserted opposite to D1 shown in FIG. 1, the control system 56 of FIG. 11 generates the K sound signal and the K sound signal from the air pressure fluctuation signal input from the K sound sensor 600B. Detect points and disappearance points.
As described above, in the electronic sphygmomanometer 1, the armband portion 2 is pressurized with the pumps 44 and 45, then exhausted at a slow speed and decompressed, and the pressure sensor 64 is used for the ischemic bladder of the armband portion 2. 14, the air vibration signal is detected using the K sound sensors 600 </ b> A and 600 </ b> B, and the signal is analyzed to determine which is located on the downstream side (hand side) of the upper arm, By detecting the generation point and disappearance point of the K sound signal from the K sound sensor connected to the K sound detection air bag located on the downstream side of the determined upper arm, the maximum blood pressure value and the minimum blood pressure value are calculated. The calculated maximum blood pressure value and minimum blood pressure value can be displayed on the display unit 31.
The control system 56 pressurizes and stops the blood flow in the blood vessel, then reduces the pressure, sets the pressure at the time when the first K sound signal when the blood flow again is detected to the maximum blood pressure value, and further reduces the pressure reduction. If the cross-sectional area of the blood vessel continues to expand sufficiently, and if the blood pressure is lost when the pressure of the air bag for ischemia falls below the minimum blood pressure, if the K sound signal is not detected, the last K sound signal is detected. The pressure at that time is set to the minimum blood pressure value. Further, the control system 56 calculates the pulse rate from the appearance interval of the vascular pulsation or the K sound signal obtained from the maximum blood pressure value and the minimum blood pressure value.

  The pressurization system 51 includes pumps 44 and 45 and a pump drive unit 62. The drive unit 62 drives and controls the pumps 44 and 45 according to a command from the control system 56. The pumps 44 and 45 are connected to the blood bag for ischemia of the armband portion 2 through the piping portion 63 of the pressure detection system 53.

  Next, the exhaust system 52 will be described. The exhaust system 52 includes two drive units 66 and 67, an exhaust valve (forced exhaust unit) 46, and a control valve (decompression control unit) 47. The exhaust valve 46 and the control valve 47 are arranged in the middle of the piping part 63. The control system 56 instructs the drive unit 66 to open and close the exhaust valve 46. Further, the pressure detection system 53 measures the speed for reducing the pressure in the air bag for ischemia, and the control system 56 instructs the drive unit 67 to achieve a constant pressure reduction speed. The opening area of the control valve 47 is controlled.

  The power supply system 54 includes a battery 68, a power supply control unit 69C, and a power supply monitoring unit 70. The battery 68 is, for example, a lithium ion battery that can be repeatedly charged, but the type is not particularly limited, and may be a dry battery or the like. The voltage of the battery 68 is controlled by the power control unit 69C and supplied to the control system 56, and also serves as a driving power source for the pumps 44 and 45 and a power source supplied to the sound control unit 71. The power monitoring unit 70 monitors the remaining amount of the battery 68 and the like. Moreover, a 100V commercial power supply can be used by using an AC adapter.

The audio system 55 includes an audio control unit 71 and an amplification unit 72. The voice control unit 71 and the amplification unit 72 are controlled by a command from the control system 56. The voice control unit 71 sends voice guidance data or music data to the amplifying unit 72 and amplifies it according to a command from the control system 56, so that the speaker 43 generates a voice announcement and a music guidance announcement. can do.
The procedure of blood pressure measurement according to the present embodiment will be described with reference to the flowcharts of FIGS. 12, 14, 16, and 18. The program according to the flowcharts of FIGS. 12, 14, 16, and 18 is stored in advance in the memory unit 69, and the CPU reads out and executes the instruction code of the program from the memory unit 69. Such blood pressure measurement processing is realized.

  First, the control unit 56 fully opens the exhaust valve 46 and the control valve 47, and initializes (for example, 0 mmHg) and adjusts the cuff pressure indicated by the pressure sensor 64 (step S1).

Thereafter, the control unit 56 fully closes the exhaust valve 46 and the control valve 47 via the drive units 66 and 67, and drives the pumps 44 and 45 in this state.
Air is sent to the air bag 14 for ischemia and the air bag 500 for detecting the K sound, and the air bag 14 for ischemia can be brought into close contact with the measurement site.
Furthermore, pressurization is performed up to a pressurization set pressure value higher than a preset maximum blood pressure.
The pulse wave superimposed on the pressure value of the ischemic bladder during pressurization is detected, and the low frequency component is detected from the amplitude value, the pressure value of the ischemic bladder, and the signals of the two K sound sensors 600A and 600B. Extract and detect the K sound, calculate its amplitude and store it in the memory. (Step S2).

  When the pressure is increased to the set pressure value, stop the pump. Thereafter, the determination process A for the K sound detection air bag placement location is performed (step S3). This process will be described later.

  The detection of the K sound is started using the signal of the K sound sensor connected to the air bag for detecting the K sound determined to be disposed on the downstream side. The exhaust control valve 47 gradually exhausts the air in the air bag 14 for ischemia at 3 to 5 mmHg / sec, and the process proceeds to a depressurization process (step S4).

  In this decompression process, a pulse wave superimposed on the pressure value of the ischemic bladder is detected, the amplitude value, the pressure value of the ischemic bladder, and the K sound sensor selected to be disposed on the downstream side. A high frequency component is extracted from the signal, a K sound is detected, its amplitude is calculated and stored in a memory. When the K sound detection air bag placement location is not determined during the pressurization or for the purpose of further improving the determination accuracy of the K sound detection air bag placement location, a separate determination process for the K sound detection air bag placement location B is performed (step S5). This process will be described later.

  Based on the pressure value indicated by the pressure sensor 64 and the K sound signal from the K sound sensor 600 determined to be disposed downstream, the systolic blood pressure and the systolic blood pressure (systolic blood pressure and diastolic blood pressure) are calculated. At the same time, the pulse rate is calculated (step S6).

  In step S7, the calculated blood pressure and pulse rate data are displayed on the display unit 31, and in step S8, the maximum blood pressure value, the minimum blood pressure value, and the pulse rate are stored in the memory together with the date and time.

  With reference to FIG. 14, FIG. 16, and FIG. 18, the procedure of determination processing A and determination processing B (steps S3 and S5) of the K sound detection air bag placement location in FIG. 12 will be described.

With reference to FIG. 13 and FIG. 14, the determination process A of the K sound detection air bag placement portion performed during pressure increase will be described.
This determination process is performed by the control system 56 as the control unit shown in FIGS.
FIG. 13A shows a low frequency component signal (0.5 to 10 Hz) ZS from the ischemic air bladder 14 and a low frequency component signal (0.5 to 10) obtained from the downstream K sound detecting air bladder 500. An example of 10 Hz) ZT is shown. FIG. 13B shows a low frequency component signal (0.8 to 5 Hz) ZS from the ischemic air bladder 14 and a low frequency component signal (0.8 to 5) obtained from the upstream K sound detecting air bladder 500. An example of 10 Hz) ZT1 is shown.
FIG. 14 shows that after supplying air to the air bag 14 for ischemia, the internal pressure value of the air bag 14 for ischemia reaches a pressure setting 30 to 40 mmHg higher than the preset maximum blood pressure. The pulse wave detected in the middle of pressurization and detected by the air bag for ischemia and the pulse wave detected by the two K sound sensors connected to the K sound detection air bags installed at the two arm insertion openings of the armband It is a flowchart which shows the process which determines whether it is an upstream or downstream based on this.
As shown in FIG. 13, the low-frequency component signal ZS from the air bag 14 for ischemia during pressurization is measured with waveforms having various amplitudes, and the time-series trend change of the amplitude is a mountain shape. Is forming.
Here, when the K sound detection air bag shown in FIG. 13 (A) is on the downstream side, the low frequency component signal obtained from the K sound detection air bag during the pressurization of the ischemic air bag 14 Similar to the low-frequency component signal ZS of the air bag 14, the time-series trend change of the magnitude of the amplitude forms a mountain shape.

On the other hand, when the K sound detection air bag shown in FIG. 13B is on the upstream side, the low-frequency component signal ZS from the ischemic air bag 14 during the pressurization has a time-series trend change in magnitude. The low-frequency component signal obtained from the K-sound detection air bag has a time-series trend change different from the low-frequency component signal ZS from the ischemic air bladder 14, whereas the chevron shape is formed. I understand that. From the above, for example, the regression curves of the peak points of the time series trend changes of the detected amplitudes of ZS and ZT are calculated, and the correlation coefficient of the two obtained regression curves is calculated to be 0.8. In the above case, it is determined that it is located on the downstream side, and when it is smaller than 0.8, it is determined that it is located on the upstream side.
Alternatively, as another method, the slope of the attenuation line of the amplitude of the low frequency component signal ZT obtained from the K sound detection air bag is calculated, and when the slope of the specified value multiple is gentler than the slope of the ZS attenuation line, the upstream side In addition, if it is the same, it is determined that it is located downstream.
If one of the two K sound sensors is confirmed, it can be determined which K sound sensor is connected to the K sound detecting air bag located downstream, and the downstream K sound sensor is determined. The blood pressure is measured using the signal.
After air pressure is supplied to the ischemic air bag 14 to increase the pressure and the pressure is sufficiently increased (after being pressurized to a level higher than the maximum blood pressure), the K sound detection air bag is on the downstream side or on the upstream side. Processing for determining whether or not there is will be described.

Alternatively, in FIG. 14, as another method, in step S <b> 11, the control system 56 measures the pressure fluctuations of the air in the air bag 14 and the K sound detection air bag by the pressure sensor 64 and the K sound sensor, respectively. In step S12, digital filter processing is performed to extract low frequency component signals from the air bag 14 for ischemia and low frequency component signals from the K sound sensors 600A and 600B. In step S13, the minimum value from the threshold A to the zero crossing is detected with respect to the low-frequency component signal from the ischemic bladder 14 shown in FIG. 13, and in step S14, the ischemic use signal shown in FIG. The maximum value from when the threshold B of the low frequency component signal from the air bag 14 is exceeded until the zero crossing is detected, and in step S15, the air bag 14 for the ischemia 14 is determined from the minimum and maximum values determined in steps S13 and S14. The pulse wave amplitude value in the low frequency component signal is calculated.
In step S16, the maximum value and the minimum value in the low frequency component of the air bag for detecting the K sound generated in the time from the time when the pulse wave falls below the threshold A in steps S13 and S14 to the time when the zero is crossed are detected. The pulse wave amplitude value is calculated from the low frequency component signal of the K sound detection air bag.
In step S17, after the pressure is increased to the maximum blood pressure or higher, the ischemic air bag 14 and the K sound detection at the timing when the maximum amplitude of the pulse wave of the low frequency component signal from the ischemic air bag 14 during the pressure increase occurs. Using the pulse wave amplitude of the low-frequency component signal of the air bag as a reference, the ratio (amplitude rate) of the amplitude for each detected pulse wave is calculated.
In step S18, the magnitude α of the amplitude rate attenuation in the calculated air bag 14 for ischemia and the K sound detection air bag is calculated using the following equation.
(Formula 1)
{(1−Amplitude rate after 1 beat from maximum amplitude) + (Amplitude rate after 1 beat from maximum amplitude−Amplitude rate after 2 beats from maximum amplitude)} / 2.0 = (Formula α)
In step S19, the magnitude of attenuation of the amplitude rate in the ischemic air bladder 14 and the K sound detecting air bag 500 is compared, and the magnitude of the attenuation of the amplitude rate in the ischemic air bladder 14 is determined as K sound detecting air bag 500. If the specified coefficient is larger than the magnitude α of the amplitude ratio, the air bag 500 for detecting the K sound on the side connected to the K sound sensor receiving this signal is judged to be upstream, and the other side. The signal of the K sound sensor is used for blood pressure measurement. (Step S20).
Note that a value close to 3 is set as the specified coefficient.

(Embodiment 2)
With reference to FIG. 15 and FIG. 16, the procedure of the determination process B of the K sound detection air bag arrangement location will be described.
In the second embodiment of the present invention shown in FIGS. 15 and 16, the control system 56 of FIG. 10 sufficiently boosts the blood pressure to the maximum blood pressure or higher, and after the pressurization is completed, the control system 56 is located at each insertion port of the armband being decompressed. From the high-frequency component signals (ZG, ZH) from the sound detection air bags 500A1 and 500A1, and 500B1 and 500B2, it is reliably determined which K sound detection air bag is on the upstream side or the downstream side. be able to.

FIG. 15A shows the high frequency component signal ZG obtained from the K sound detection air bag during decompression when the K sound detection air bag is on the downstream side, and FIG. 15B shows the K sound detection. The high-frequency component signal ZH obtained from the K sound detection air bag during decompression when the air bag is on the upstream side is shown.
FIG. 16 is a flowchart illustrating a process in which the control system 56 of FIG. 10 determines whether the K sound detection air bag is on the upstream side or the downstream side from the start of pressure reduction.
In step S101 of FIG. 16, the control system 56 of FIG. 10 starts signal measurement from the respective K sound detection air bags 500A1, 500B2, and 500B1, 2. In step S102, the pressure variation of the air in the K sound detection air bag is transmitted from the K sound detection air bag to the K sound sensors 600A and 600B through the tubes 4P1 and 4B. The K sound sensors 600A and B supply an air vibration signal to the control system 56, and the control system 56 extracts a high frequency component signal (50 to 100 Hz) from the vibration signal by a digital filter.

In step S103, it is observed whether the high frequency component signal ZG from the K sound detection air bag shown in FIG. 15A and the high frequency component signal ZH from the K sound detection air bag shown in FIG. To do. In step S104, the control system 56 of FIG. 10 immediately after starting the decompression (for example, a period TL within several seconds) has a signal KK exceeding the threshold C as shown in FIG. It is verified whether there is any signal KK exceeding the threshold C as shown in FIG.
In step S105 of FIG. 16, when the control system 56 of FIG. 10 determines that there is a signal KK exceeding the threshold C as shown in FIG. 15B, the side connected to the K sound sensor that has received this signal. It is determined that the K sound detection air bladder is on the upstream side (step S106). On the other hand, if the control system 56 of FIG. 10 determines that there is no signal KK exceeding the threshold value C as shown in FIG. 15A in step S105, K on the side connected to the K sound sensor that has received this signal. It is determined that the sound detection air bladder 500 is on the downstream side (step S107), and the control system 56 detects the K sound signal using the downstream K sound detection air bladder 500 and the K sound sensor. Proceed to

  As described above, in another embodiment of the present invention shown in FIGS. 15 and 16, the control system 56 starts the decompression by removing the air in the air bag for ischemia, and detects the K sound obtained from the K sound sensor. A high-frequency component signal is extracted from the air pressure fluctuation signal in the air bag, and when the high-frequency component signal exceeds a predetermined threshold immediately after the start of decompression, it is determined that the K sound detection air bag is on the upstream side. Can do. That is, from the high frequency component signals ZG and ZH from the K sound detection air bag during decompression, the control system 56 can reliably determine whether the K sound detection air bag is on the upstream side or the downstream side. it can.

(Embodiment 3)
With reference to FIG. 17 and FIG. 18, another procedure of the determination process A for the K sound detection air bag placement location detected during pressurization will be described.
In the third embodiment of the present invention shown in FIGS. 17 and 18, the control system 56 of FIG. 10 is configured as shown in FIG. 17A from the presence / absence of a high-frequency component signal from the K sound detection air bag 500 during pressure increase. It is possible to reliably determine whether the K sound detection air bag is on the downstream side or whether the K sound detection air bag is on the upstream side as shown in FIG. That is, in the third embodiment, when a signal exceeding the threshold D of the high-frequency component signal of the K sound detection air bag appears in a state where the pressure is higher than the maximum blood pressure, the signal is connected to the K sound sensor that exceeds the threshold. It is also possible to make a simple determination, for example, that the air bubble for detecting the K sound is on the upstream side.

As shown in FIG. 18, pressure increase is started in step S200, and signal measurement by the K sound detection air bag is started in step S201. In step S202, a high-frequency component signal is extracted by a filter, and in step S203, the control system 56 of FIG. 10 verifies whether there is a high-frequency component signal exceeding the threshold D in a state where the pressure is higher than the maximum blood pressure.
In step S204, when a signal exceeding the threshold D of the high frequency component signal of the K sound detection air bag appears in a state where the pressure is higher than the maximum blood pressure as in the high frequency component signal shown in FIG. It can be determined that the K sound detection air bag connected to the K sound sensor that has received this signal is on the upstream side (step S205). In step S204, if no signal exceeding the threshold D of the high frequency component signal of the K sound detection air bag appears in the state where the pressure is higher than the maximum blood pressure as shown in FIG. It can be determined that the K sound detection air bag connected to the received K sound sensor is on the downstream side (step S207).

  As a result, even if the measurer inserts the armband portion into any of the upper arms, the insertion of which one of the K sound detection air bags installed at both insertion ports is located downstream of the upper arm is inserted. It is possible to compare the signals from the K sound detection air bags installed in the mouth and identify them by time-series changes or occurrence time differences and magnitudes. And since a blood pressure is measured using the signal of the K sound detection air bag located in the identified downstream, a blood pressure can be measured correctly. Therefore, even if the measurer inserts the armband portion into the upper arm from which insertion port, the blood pressure can be accurately measured.

  In the electronic sphygmomanometer according to the present invention, a plurality of K sound detection air bags at one position and a K sound detection air bag at the other position are arranged along the circumferential direction of the ischemic air bag. Even when the person inserts the armband into the upper arm, even if the position of the air bag for detecting the K sound is shifted from the position on the artery of the upper arm, the air bag for detecting the K sound is detected. However, since it can be arranged in the vicinity of the position of the artery of the upper arm, the K sound signal can be measured accurately.

Since the bone member is provided inside the outer member, it is possible to prevent the phenomenon that the outer member of the armband swells outward when air is supplied to the air bag for ischemia, and accurate blood pressure measurement Can be done.
Further, a backing is preferably provided between the air bag for ischemia and the air bag for detecting the K sound. This is a device for efficiently transmitting vibrations from the human body to the K sound sensor by the K sound detection air bag, thereby making it possible to more accurately detect the K sound.

The present invention is not limited to the above embodiment, and various modifications can be employed. The display unit 31 is not particularly limited in type, for example, an organic EL device, a fluorescent display device, or the like other than a liquid crystal display device.
In the example of the electronic sphygmomanometer shown in the drawing, the armband portion is a structure that can be deformed and can be folded when blood pressure measurement is not performed, but as an electronic sphygmomanometer of the present invention, instead of a foldable outer cloth, For example, it is possible to employ a structure in which a blood-tight air bag is disposed in a hard housing made of plastic.
In the above-described embodiment of the present invention, when the measurement is not performed, the folded armband portion 2 is fixed to the upper surface of the blood pressure monitor main body 10 detachably using a fixing means when the measurement is not performed. Also good. As a fixing method of the armband part 2, for example, the armband part and the sphygmomanometer body are detachably fixed by a magnetic attraction force using a magnet and a metal plate, or a tape member having a male member And it can also fix so that attachment or detachment is possible by sticking the tape member which has the female type member which can be mechanically attached to this male type member so that attachment or detachment is possible.

Further, although the amplitude rate is calculated by using a signal up to 2 beats as the magnitude of attenuation, it can be made variable according to the pulse rate. Furthermore, although 3.0 is used as the magnitude of the coefficient α, it is not limited to this.
Moreover, although the condenser microphone is mentioned as an example of a K sound sensor, a piezoelectric microphone, a dynamic microphone, etc. can be utilized as a sensor which can measure K sound. Moreover, as long as only the insertion direction is notified, the sensor is not limited to a sensor that can measure the K sound, and examples thereof include a strain gauge and an optical sensor.

  DESCRIPTION OF SYMBOLS 1 ... Electronic blood pressure monitor, 2 ... Arm belt part, 4 ... Tube, 4P ... Auxiliary tube, 10 ... Blood pressure monitor main body, 14 ... Air bag for ischemia, 16 ... Outer cloth (an example of an outer member), 17... Inner cloth (an example of a contact cloth portion), 500 (500A1, 500A2, 500B1,500B2)... K sound detection air bag, 600A. 600B ... K sound sensor

Claims (4)

An electronic sphygmomanometer that measures with the upper arm, has a cylindrical armband that can block the upper arm, and a sphygmomanometer body that is formed separately from the armband,
The armband portion is an air bag for ischemia capable of compressing and blocking the upper arm by supplying air,
A K sound detecting air bag having an air capacity smaller than the air capacity of the air-blocking air bag disposed on the side in contact with the upper arm of the air-blocking air bag and in the vicinity of the ends of the two insertion ports in the previous period; Have
Further, in order to detect a change in air in the K sound detection air bag and detect a K sound signal, two K sound sensors in which K sound detection air bags arranged at two insertion ports are connected together. When,
The pulse wave detected from the low-frequency component signal of the signal detected by the air bag for preventing blood pressure generated during the pressurization by attaching the air bag for ischemia to the upper arm and the one insertion port obtained from the K sound sensor Detected from the pulse wave detected from the low frequency component signal from the K sound detection air bag arranged on the side and the low frequency component signal from the K sound detection air bag arranged on the other insertion port side From the pulse wave, the change in the magnitude of the pulse wave detected from the low-frequency component signal of the signal detected by the air bag for the first ischemia, and the K sound detection air bag disposed on the one insertion port side A difference in change in time-series magnitude of a pulse wave detected from a low-frequency component signal or a pulse wave detected from a low-frequency component signal from the K sound detection air bag disposed on the other insertion port side,
Or from the high frequency component signal from the K sound detection air bag located on the one insertion port side obtained from the K sound sensor immediately after the start of decompression in the ischemic air bag, and the other insertion port Each pulse wave is detected from the high frequency component signal from the K sound detection air bag located on the side, and from the start of the previous decompression until the magnitude of the pulse wave of each K sound sensor exceeds a predetermined threshold value Time difference between
Alternatively, from the high frequency component signal from the K sound detection air bag located on the one insertion port side obtained from the K sound sensor during pressurization in the ischemic air bag, and the other insertion port Each pulse wave is detected from a high frequency component signal from the K sound detection air bag located on the side, and after the pressure is increased to the maximum blood pressure or higher, the magnitude of the pulse wave of each K sound sensor is set to a predetermined threshold. The air bag for detecting the K sound is arranged in the vicinity of the two previous insertion ports based on the difference in time-series change in the magnitude of the detected pulse wave, the time difference, or the presence or absence of the signal. Is measured on the downstream side of the upper arm, and the blood pressure is measured using a signal from the previous-stage K sound sensor connected to the determined previous-stage K sound detection air bag located on the downstream side And a control unit that Electronic blood pressure monitor.   The K sound detection air bag at the one position and the K sound detection air bag at the other position are respectively arranged in a plurality along the circumferential direction of the hemostasis air bag. Item 2. The electronic blood pressure monitor according to Item 1.   3. The electronic blood pressure according to claim 1, wherein the K sound sensor is connected to a condenser microphone in the sphygmomanometer body by a tube with respect to the air bag for detecting the K sound. Total.   The electronic sphygmomanometer according to any one of claims 1 to 3, wherein a backing is attached between the air bag for ischemia and the air bag for detecting the K sound.

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