JP2011200609A - Electronic sphygmomanometer - Google Patents

Abstract

PROBLEM TO BE SOLVED: To provide an electronic sphygmomanometer capable of using a pulse wave gate even if a measurer is a person with weak pulses, setting a gate section from signals of K-sound detecting air bags for measuring the K-sound, and suppressing the cost by eliminating the need for dedicated measuring environment for using the pulse wave gate.SOLUTION: An arm band includes: an ischemic air bag that can pressurize an upper arm by feeding air thereto; a plurality of K-sound detecting air bags that are disposed inside the ischemic air bag and have the air volume smaller than the air volume of the ischemic air bag; and a K-sound sensor that acquires a signal by detecting fluctuations in the air inside the K-sound detecting air bags, generated when the blood flow flows again by depressurization after the ischemic air bag has pressurized the upper arm T to stop the blood flow. This electronic sphygmomanometer separates the signal DS1 from the K-sound sensor into a low frequency component signal DS2 and a high frequency component signal DS3, opens the gate section GT with a peak point PP of the low frequency component signal DS2 defined as the center, and extracts the high frequency component signal DS3 inside the gate section GT.

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). The arm band part of the electronic sphygmomanometer has an air bag for ischemia, and air is supplied from the pump of the sphygmomanometer into the air bag for ischemia so that the air bag for ischemia expands and compresses the upper arm To do. Then, the air can be gradually exhausted out of the ischemic air bag while reducing the internal pressure of the ischemic air bag at a constant speed.
A measurement microphone is provided at one end of the air bag for ischemia, and this microphone directly detects a K sound signal. This K sound signal is generated when the internal pressure of the air bag for ischemia is reduced by reducing the pressure in the air bag for ischemia after the blood vessel is closed by the air bag for ischemia, and the internal pressure of the air bag for ischemia becomes smaller than the maximum blood pressure in the blood vessel. The sound signal is generated when the blood flows through the blood vessel from the time of the maximum blood pressure to the time of the lowest blood pressure until the occlusion of the blood vessel disappears while changing the tone color.
Here, when the blood pressure is measured with the electronic sphygmomanometer that employs the above-described Ribaroch Korotkoff sound method, noise having a component close to the frequency component of the K sound signal among noises generated by the user is And a rubbing sound generated from a tube connecting the armband and the main body. As one of countermeasures against this noise, a technique called pulse wave gate method that opens the gate using the synchronism between the pulse wave detected by the air bag for ischemia and the K sound is proposed. Has been. In the method using the pulse wave gate, the gate interval is set by detecting the peak of the oscilloscope signal using the oscilloscope signal of the ischemic bladder (the low frequency component signal of the ischemic bladder). By measuring the K sound signal generated in the section, it is possible to reduce the noise stochastically, for example, the noise measured outside the gate section can be removed.
However, in the case of using an air bag for ischemia having a large air capacity, which is used for a blood pressure monitor for tightly adhering the blood bag for ischemia to the arm with the one air bag for ischemia, and when the measurer is a weak person with weak pulse. In some cases, in particular, the amplitude of the oscilloscope signal is reduced with respect to noise, so that the oscilloscope signal waveform is disrupted. In this case, the peak of the oscilloscope signal, which serves as a guide for opening the pulse wave gate, cannot be noticed. Thus, since the peak of the oscilloscope signal cannot be detected, the gate section cannot be set, and the K sound signal in the gate section cannot be reliably measured.
Therefore, in order to solve the above-described problems, the present invention can use a pulse wave gate even if the measurer is a pulse weak person, and further sets the gate interval from the signal of the K sound sensor for K sound measurement. Therefore, an object is to provide an electronic sphygmomanometer that can suppress costs because it does not require a dedicated measurement environment for using a pulse wave gate.

The electronic sphygmomanometer of the present invention has a cylindrical armband portion that can be pressurized through the upper arm, and a sphygmomanometer body formed separately from the armband portion, An air bag that can pressurize the upper arm by supplying air, and a plurality of K sounds that are arranged inside the air bag for ischemia and have an air volume smaller than the air volume of the air bag for ischemia A detection air bag, and the air bag for detecting the K sound generated when the blood flow flows again after the blood pressure in the blood vessel of the artery is decompressed after the air bag for ischemia pressurizes the upper arm to stop blood flow A K sound sensor for detecting a change in the air in the interior to obtain a signal, and separating the signal obtained from the K sound sensor into a low frequency component signal and a high frequency component signal that is a K sound signal; Open a gate section centered on the peak point of the low frequency component signal, and Characterized in that and a control unit for extracting a high frequency component signal.
According to the above configuration, the pulse wave gate can be used even if the measurer is a pulse weak person, and further, the gate section can be set from the signal of the K sound sensor for K sound measurement. Costs can be reduced because a dedicated measurement environment is not required to use the wave gate. That is, a K sound detection air bag and a K sound sensor may be used, and by performing signal processing on the signal obtained from the K sound sensor, the frequency components of the rubbing sound generated from the armband and the air tube are obtained. Separation into a separable low frequency component and a high frequency component signal containing K sound, setting a gate interval using the low frequency component signal, and providing an appropriate gate interval for the high frequency component signal ensures K A sound signal can be obtained. The electronic sphygmomanometer of the present invention is an electronic sphygmomanometer that can be measured by simply inserting a cuff into an arm and inflating one air bag greatly and automatically bringing the air bag into close contact with the arm.

Preferably, the peak point is from a time point when the low frequency component signal exceeds a predetermined first threshold, becomes a predetermined second threshold smaller than the first threshold, and falls below the second threshold. It is the first peak value obtained retroactively.
According to the said structure, a peak point can be obtained reliably using a 1st threshold value and a 2nd threshold value.

Preferably, as the setting of the gate section, a time period from when the low frequency component signal exceeds the first threshold value to a time point when it falls below the second threshold value is used.
According to the above configuration, the setting of the gate section can be reliably set using the low frequency component signal.
Preferably, the K sound sensor is connected to a condenser microphone in the sphygmomanometer main body by a tube with respect to the K sound detecting air bag.

Preferably, a backing is attached between the air bag for ischemia and the air bag for detecting the K sound.
According to the said structure, it is a device for the K sound detection air bag to efficiently transmit the vibration from the human body to the K sound sensor, and thereby K sound detection can be performed more accurately.

  According to the present invention, it is a sphygmomanometer using an air bag for large blood pressure that can be measured simply by passing it through an arm, and a pulse wave gate can be used even if the measurer is a weak pulse person, Furthermore, since the gate section can be set from the signal of the K sound sensor for K sound measurement, in order to use the pulse wave gate, a dedicated pulse wave signal that is superimposed on the pressure signal of the ischemic cuff is detected. Therefore, it is possible to provide an electronic sphygmomanometer that does not require a CPU with high calculation capability and can reduce costs.

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. FIG. 7A is a perspective view showing an air bag for ischemia and two air bags for detecting K sound, and FIG. 7B is an air bag for ischemia, an outer cloth, an inner cloth cover, and two K pieces. It is a figure which shows the air bag for sound detection. 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 the K sound detection 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 figure which shows another embodiment of this invention. FIG. 13A shows the raw signal DS1 of the K sound detection air bag (small cuff), and FIG. 13B shows the low frequency of the K sound detection air bag obtained by frequency separation of the raw signal DS1. The component signal (0.2 to 1 Hz) DS2 is shown, and FIG. 13C shows the high frequency component signal (40 to 80 Hz) DS3 of the K sound detection air bag obtained by frequency separation of the raw signal DS1. When the measurer is a pulse weak person, an example of the low frequency component signal DS0 of the air bag for ischemia (large cuff) and the high frequency component signal DS3 of the air bag for detecting K sound is shown. The procedure for extracting the high frequency component signal of the K sound detection air bag in the gate section GT from the raw signal DS1 of the K sound detection air bag will be described. FIG. 16A is a waveform diagram showing how the high frequency component signal DS3 of the K sound detection air bag in the gate section GT shown in FIG. 15 is extracted. FIG. 16A shows the high frequency component signal DS3 of the K sound detection air bag. FIG. 16B shows the low frequency component signal DS2 of the K sound detection air bag. It is an example shown for comparison, and is set to an oscilloscope signal DS0 that is a low frequency component of the air bag for ischemia, a K sound signal that is a high frequency component signal DS3 of the K sound detection air bag 500, and a high frequency component signal. It is a figure which shows the example of the gate area GT.

Hereinafter, preferred embodiments of the present invention will be described in detail with reference to the drawings.
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 measures the blood pressure by inserting a hand into the arm T of the measurer through the insertion opening 11R of the armband portion 2 and holding the armband on the upper arm portion above the elbow. A sphygmomanometer. The armband portion 2 and the sphygmomanometer body 10 are connected by a flexible tube 4 that is an air supply / exhaust passage and another tube 4P. As shown in FIG. 1, the tube 4 as an air conduit for supplying and exhausting air to and from the air bag 14 of the armband portion 2 and two K sound detection air bags 500 for detecting K sound signals are connected. The sphygmomanometer body 10 and the arm band 2 are connected to each other via an air connector 4Q that can be attached to and detached from the sphygmomanometer body 10 by an elastomer tube of a multiple body pipe (also referred to as a double conduit) that is provided with a tube 4P as an air conduit. Has been. 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 two K sound detection air bags 500 of the armband part 2 are connected to the pumps 44 and 45 side of the sphygmomanometer body 10 through another tube 4P.

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 600, a speaker 43, two pumps 44 and 45, an exhaust valve 46, a control valve 47, and a circuit board 48 including a control system. A memory unit 69 is 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 sensor 600.

Next, the structure of the armband portion 2 will be described with reference to FIGS.
As shown in FIG. 1, the armband portion 2 can be inserted with the upper arm T to press the upper arm T of the measurer in the state of passing through the opening portion 11R from the opening portion 11R in the direction D1 and exiting from the opening portion 11P during blood pressure measurement. It has a substantially cylindrical structure (tubular body) with both ends cut off. Thus, unlike the normal armband portion, the armband portion 2 does not have to be wound around the upper arm T of the measurer, and can be passed through either the left or right upper arm T, so that the measurer can easily measure blood pressure. Can do.

  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, as the inner cloth 17, an article having a high elasticity is used, and the outer cloth 16 is deformed, but it is preferable to use an article that has a lower elasticity than the inner cloth 17 and preferably hardly stretches. Both the outer cloth 16 and the inner cloth 17 are cylindrical members (tubular bodies). Thereby, the armband part 2 is lightweight and can be folded. That is, since the inner cloth 17 which is a contact cloth part which contacts the measurement site | part of a human body is equipped with the elasticity, it is easy to pass through the measurement site | part of an upper arm. The outer cloth 16 has a lower elasticity than the inner cloth 17 but is allowed to be deformed. For this reason, the electronic sphygmomanometer 1 having the compact armband portion 2 that is easy to use can be provided by being folded.
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. The inner cloth 17 may be a stretchable cloth member that is elastic and has elasticity, for example, and the tensile strength is 94.9 N / in in length as measured by the JIS L1096-A method. 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.

  For example, as shown in FIG. 1, the operation of inserting into the upper arm T of the left arm from the direction D1 or removing the armband portion 2 in the opposite direction can be performed with the armband portion 2 with the right hand. Further, the operation of inserting the upper arm T of the right arm from the direction D1 of the armband portion 2 or removing the armband portion 2 in the opposite direction can be performed by holding the armband portion 2 with the left hand. Thereby, the measurer can easily perform the attaching operation or the detaching operation of the armband portion 2 with respect to either the left or right upper arm T.

  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. The bag 14 and the outer cloth 16 do not swell along the longitudinal direction 16S. For this reason, it is possible to press the arm in the same manner as the armband portion in which the air bag for ischemia is arranged in the hard cylinder, and the measurer can stably and reliably measure the blood pressure with the upper arm. 6 and 7 show examples of the shape of the air bag 14 for ischemia and the air bag 500 for detecting a K sound.

Here, structural examples of the air bag 14 for ischemia and the air bag 500 for detecting a 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 connecting pipe 220 with a filter, 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.

FIG. 9 shows an example of the structure of the K sound detection air bag 500 in an enlarged manner, and a plurality of K sound detection air bags 500 are arranged on the inner surface portions 14F and 14G of the ischemic air bag 14, and The K sound detection air bag 500 is disposed on the downstream side of the artery of the upper arm T (that is, on the side closer to the finger, not on the side closer to the shoulder). The K sound detection air bladder 500 is adapted to closely contact the surface to be measured HM of the upper arm T of the measurer and correspond to the artery of the upper arm T.
As shown in FIG. 9, the material of the K sound detecting air bag 500 can be the same material as that of the blood blocking air bag 14, for example, and the K sound detecting air bag 500 has a rectangular shape. The four side portions 501, 502, 503, and 504 of the K sound detecting air bag 500 are sealed by, for example, fusion, and have an air accommodating portion 509. One end 506 of the tube 4P is inserted and fixed to the side portion 501. The other end 507 of the tube 4P is connected to the K sound sensor 600. The tube 4P is connected to the pumps 44 and 45 via the tube 4R, the mechanical filter 700, and the piping 63.

When air is supplied from the pumps 44 and 45 to the K sound detection air bag 500, the air in the K sound detection air bag 500 changes the movement of the artery to air vibration and transmits it to the K sound sensor 600 through the tube 4P. be able to. The K sound sensor 600 can obtain a K sound signal by converting the air vibration into an electric signal. The K sound sensor 600 and the pumps 44 and 45 are disposed on the sphygmomanometer main body 10 side, and the tube 4P is connected to the sphygmomanometer main body 10 from the armband portion 2 side together with the wire 3 and the tube 4 as shown in FIG. Connected to the side.
In this way, the air bag 14 for ischemia and the pumps 44 and 45 are connected by the tube 4, but the two air bags for detecting K sound 500, the K sound sensor 600 and the pumps 44 and 45 are connected to the tube 4. It is connected by another tube 4P. In addition, a backing is provided between the ischemic air bladder 14 and the K sound detecting air bladder 500. This is a contrivance for the K sound detection air bag 500 to efficiently transmit vibration from the human body to the K sound sensor 600, whereby K sound detection can be performed more accurately.

Next, with reference to FIG. 10, the connection relationship of the above-described air bag 14 for ischemia, the air bag 500 for detecting K sound, the pumps 44 and 45, the K sound sensor 600, and the like will be described.
As shown in FIG. 10, the Korotkoff sound (K sound) detection system 50 includes two K sound detection air bags 500 of the armband portion 2, one K sound sensor 600, and a mechanical filter 700. . The two K sound detection air bags 500 are connected to one K sound sensor 600 via the tube 4P, and the pressure fluctuation of the air in the K sound detection air bag 500 is caused by the K sound detection air bag 500. To the K sound sensor 600 through the tube 4P. The K sound sensor 600 is connected to the mechanical filter 700 via the tube 4R. The mechanical filter 700 is connected to the pressure sensor 64, the pumps 44 and 45, the exhaust valve 46, and the control valve 47 through the piping part 63.

  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 two K-sound detection air bags 500 can be disposed at positions close to 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.
A circuit block of the electronic sphygmomanometer 1 shown in FIG. 11 will be described. The circuit block of the electronic blood pressure monitor 1 is shown. As shown by the broken line in the circuit block of the electronic sphygmomanometer 1, the sphygmomanometer body 10 includes a Korotkoff sound (K sound) detection system 50, a pressurization system 51, an exhaust system 52, and a pressure detection system 53 shown in FIG. A power system 54, a sound system 55, and a control system 56.

  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. However, the two K sound detection air bags 500 of the armband portion 2, the K sound sensor 600, and the mechanical A filter 700 is included. The two K sound detection air bags 500 are connected to the K sound sensor 600 via the tube 4P, and the pressure fluctuation of the air in the K sound detection air bag 500 is changed from the K sound detection air bag 500 to the tube. It is transmitted to the K sound sensor 600 through 4P. The K sound sensor 600 is connected to the mechanical filter 700 via the tube 4R. The 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 electrically connected to the control system 56, and the K sound sensor 600 changes the pressure variation of the air in the K sound detection air bladder 500 into an electric signal to the control system 56. An air pressure fluctuation signal is supplied.

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 integration A / D unit 65.
The control system 56 of FIG. 11 detects the K sound signal, the generation point and the disappearance point of the K sound signal from the air pressure fluctuation signal input from the K sound sensor 600. 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 K sound signal is detected using the K sound sensor 600, and the generation point and the disappearance point of the K sound signal are detected to calculate the maximum blood pressure value and the minimum blood pressure value. Thus, the calculated maximum blood pressure value and minimum blood pressure value can be displayed on the display unit 31. The control system 56 as the control unit pressurizes and stops the blood flow in the blood vessel, and then reduces the pressure. Then, the pressure at the time when the first K sound signal when the blood flow again is detected is set as the maximum blood pressure value. Further, if the decompression is continued and the cross-sectional area of the blood vessel is sufficiently expanded, and the pressure of the air bag for ischemia is lower than the minimum blood pressure, the K sound signal is not detected when the blood vessel occlusion disappears. The pressure at the time when the sound signal is detected 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 commands the drive unit 66 to open and close the exhaust valve 46, and the control system 56 commands the drive unit 67 to open and close the control valve 47.

  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.

Next, the detection process of the K sound signal (the high frequency component signal of the K sound detection air bag 500) will be described with reference to FIGS. This detection process is performed by the control system 56 as a control unit shown in FIGS.
13A shows the raw signal DS1 of the K sound detecting air bag (small cuff) 500, and FIG. 13B shows the K sound detecting air bag 500 obtained by frequency separation of the raw signal DS1. FIG. 13C shows a high frequency component signal (40 to 80 Hz) DS3 of the K sound detection air bag 500 obtained by frequency separation of the raw signal DS1. Show.
FIG. 14 shows an example of the low-frequency component signal DS0 of the ischemic bladder (large cuff) and the high-frequency component signal DS3 of the K sound detection bladder 500 when the measurer is a pulse weak person. FIG. 15 shows a procedure for extracting the high-frequency component signal of the K sound detection air bladder 500 in the gate section GT from the raw signal DS1 of the K sound detection air bladder 500.

FIG. 16 is a waveform diagram showing a state in which the high frequency component signal DS3 of the K sound detection air bag 500 in the gate section GT shown in FIG. 15 is extracted. FIG. FIG. 16B shows the low frequency component signal DS2 of the K sound detection air bladder 500. FIG.
FIG. 17 is an example shown for comparison, and the oscilloscope signal DS0, which is a low-frequency component of the ischemic bladder, the K-sound signal that is the high-frequency component signal DS3 of the K-sound detection bladder 500, and the high-frequency component signal It is a figure which shows the example of the gate area GT set to (2).
First, frequency separation of the raw signal DS1 of the K sound detection air bladder 500 will be described with reference to FIG.
The K sound sensor 600 shown in FIGS. 10 and 11 changes the pressure variation of the air in the K sound detection air bag 500 into an electrical signal, and sends it as an air pressure variation signal to the control system 56 in FIG. A raw signal DS1 of the indicated K sound detection air bladder 500 is supplied.
The control system 56 uses the raw signal DS1 of the K sound detection air bag 500 shown in FIG. 13A as a low frequency component (0.2 to 1 Hz) of the K sound detection air bag 500 shown in FIG. 13B. Frequency separation is performed on DS2 and the high-frequency component signal (40 to 80 Hz) DS3 of the K sound detection air bladder 500 shown in FIG.

FIG. 14 shows the low-frequency component signal DS0 of the ischemic air bladder 14 and the high-frequency component signal DS3 of the K sound detecting air bladder 500 when the measurer is a weak pulse weak person. If the pulse is weak, the amplitude of the oscilloscope signal from the air bag 14 for ischemia is reduced. Since the low-frequency component signal DS0 of the air bag 14 for ischemia has a small detected pulse wave due to the large air capacity of the air bag for ischemia of the armband and pulse weakness, an exhaust bubble as a decompression valve shown in FIG. 46, the S / N is poor due to the influence of noise from the control valve 47, and it becomes difficult to set the pulse wave gate section.
Therefore, in order to be able to obtain a K sound signal even when the measurer is a weak pulse person, the low frequency component signal DS0 of the ischemic air bag 14 is not used, and the K sound detecting air bag is used. 500 and the condenser microphone 600 are used to use the raw signal DS1 of the K sound detecting air bag 500. With reference to FIGS. 15 and 16, a process of extracting the high-frequency component signal DS3 of the K sound detection air bladder 500 in the gate section GT from the raw signal DS1 of the K sound detection air bladder 500 will be described.
When the pressure reduction in the ischemic air bladder 14 is started in step S0 of FIG. 15, in step S1, the K sound sensor 600 starts measuring the raw signal DS1 of the K sound detecting air bladder 500 shown in FIG. To the control system 56. In step S2, the control system 56 of FIG. 11 uses the digital filter to convert the raw signal DS1 of the K sound detection air bag 500 into the low frequency component signal of the K sound detection air bag 500 shown in FIG. Frequency separation is performed on DS2 and the high-frequency component signal DS3 of the K sound detection air bag 500, which is the K sound signal shown in FIG.
In step S3, the control system 56 repeats the measurement of the low frequency component signal DS2 until the low frequency component signal DS2 of the K sound detection air bag 500 shown in FIG. 13B satisfies the following conditions 1 and 2. . Condition 1 is that the low frequency component signal DS2 exceeds the threshold A (A> 0) as shown in FIG. The condition 2 is that after satisfying the condition 1, the signal of the low frequency component signal DS2 becomes equal to or less than the threshold value B (B <0) as shown in FIG.

In step S4, the control system 56 detects the first peak point PP as shown in FIG. 16B by going back the time axis from the time point when the low frequency component signal DS2 exceeds (below) the threshold value B. In step S5, the control system 56 sets and opens the pulse wave gate section GT having the pulse wave open time point TM1 and the pulse wave close time point TM2 with respect to the high frequency component signal DS3 around the peak point PP. In step S6, the control system 56 extracts the high-frequency component signal DS3 of the K sound detection air bladder 500 in the opened pulse wave gate section GT.
Accordingly, in the embodiment of the present invention, as in the comparative example shown in FIG. 17, the peak 800 of the low-frequency component signal (oscilloscope signal) DS0 of the air bag 14 for ischemia is detected, and the gate is centered on this peak 800. The section 850 is opened, and the high frequency component signal DS3 of the K sound detecting air bag 500, which is a K sound signal, is used. For this reason, even if the measurer is a weak pulse weak person and the low-frequency component signal DS0 of the ischemic bladder 14 is weak, the low-frequency component signal (oscilloscope signal) DS0 of the ischemic bladder 14 is low. It is not necessary to use peak 800.

  That is, in the control system 56 according to the embodiment of the present invention, as shown in FIGS. 15 and 16, with respect to the high frequency component signal DS3 with the peak point PP in the low frequency component signal DS2 of the K sound detecting air bag 500 as the center. The pulse wave gate section GT having the pulse wave open time point TM1 and the pulse wave close time point TM2 is opened, and the high frequency component signal DS3 of the K sound detecting air bag 500 in the opened pulse wave gate section GT is extracted. This is because the K sound signal 900 can be obtained.

  In this way, a low frequency component signal in the detection signal from the K sound detection air bag 500 is obtained by obtaining a detection signal from the K sound detection air bag 500 which is a small cuff and applying a digital filter to the detection signal. DS2 is separated from the high frequency component signal DDS3, noise contained in the low frequency component signal DS2 is removed to obtain a peak point PP, and a gate is opened around the peak point PP to obtain a K sound signal. be able to.

Next, another embodiment of the present invention will be described with reference to FIG.
As shown in FIG. 12A, three small air bags 500 can be arranged on the downstream side of the inner surface portion of the ischemic air bag 14, and as shown in FIG. Four K-sound detection air bags 500 may be arranged on the downstream side of the inner surface portion.

  In the above-described electronic sphygmomanometer 1 according to the embodiment of the present invention, a plurality of K sound detection air bags 500 are arranged on the inner surface of the ischemic air bag 14, and the K sound detection air bags 500 are disposed in the arteries of the upper arm T. It is arranged on the downstream side (that is, the side closer to the fingers, not the side closer to the shoulder). Accordingly, when the measurer passes the armband portion 2 through the upper arm T, the armband portion 2 may be inserted into the upper arm while being rotated in the circumferential direction of the upper arm T from the correct position with respect to the upper arm T, or the right arm. Even if the arm band portion is passed through any of the upper arms T of the left arm, any of the K sound detecting air bags 500 can be disposed so as to contact the position of the artery of the upper arm T. Can be obtained. Moreover, air vibration in the K sound detection air bladder 500 can be detected by one K sound sensor 600 to obtain a K sound signal.

The pumps 44 and 45 pressurize the ischemic air bladder 14 at full speed to boost the ischemic air bladder 14 and the K sound detecting air bladder 500. When the control system 56 determines the disappearance of the pulse, the pressure increase in the armband 2 is stopped. Then, when the inside of the armband part 2 is gradually reduced, vibration corresponding to the systolic blood pressure in the artery is detected as vibration of air in the K sound detection air bag 500, and this vibration of air is detected as K sound. It is detected electrically by the sensor 600. As a result, the K sound sensor 600 is used, and the K sound signal can be reliably detected, and the electronic sphygmomanometer 1 detects the K sound signal and the generation point and disappearance point of the K sound signal, thereby The calculated maximum blood pressure value and minimum blood pressure value can be displayed on the display unit 31.
Since the plurality of K sound detection air bags 500 are arranged on the downstream side of the armband portion 2, when the measurer passes the armband portion 2 through the upper arm, the measurer rotates relative to the upper arm instead of the correct position. Even if it is attached to the position, any of the K sound detection air bags 500 can be brought into close contact with the artery, so that the K sound signal can be appropriately detected.

In the electronic sphygmomanometer 1 according to the embodiment of the present invention, the armband portion 2 does not require winding adjustment with respect to the upper arm, which has been necessary in the related art, can be simply passed through the arm, and can be easily folded. When the measurer passes the upper arm into the armband portion 2, the K sound detecting air bag 500 inside the blood blocking air bag 14 can be disposed at an appropriate position near the artery of the upper arm.
The air bag 14 for ischemia called a large cuff has a larger air capacity than the air bag 500 for detecting a K sound called a small cuff, so that a minute change in air pressure cannot be recognized as a minute signal change. . In addition, exhaust valve and control valve noises are mixed in the signal from the air bag 14 for ischemia.
On the other hand, the K sound detection air bag 500 having a smaller air capacity than the ischemic air bag 14 is disposed in the ischemic air bag 14, and the change in the air pressure in the K sound detecting air bag 500 is minute. It can be noticed as a change in signal. Further, noise from the exhaust valve and the control valve can be attenuated by the mechanical filter 700. For this reason, by using the K sound detection air bag 500 and the K sound sensor 600, the signal from the K sound detection air bag 500 is used without using the signal from the air bag 14 for the K sound detection. A high frequency component signal DS3 having a good S / N ratio can be obtained from the air bladder 500, and the high frequency component signal DS3 can be appropriately multiplied by the gate section GT to obtain the K sound signal 900.

In the electronic sphygmomanometer according to the embodiment of the present invention, the armband portion is disposed inside the air bag for ischemia capable of pressurizing the upper arm by supplying air, and the air in the air bag for ischemia. A plurality of K sound detection air bags having an air capacity smaller than the capacity, and after the air bag for ischemia pressurizes the upper arm to stop the blood flow in the blood vessel of the artery, A K sound sensor for detecting a change in the air in the air bag for detecting a K sound generated when flowing, a signal obtained from the K sound sensor, a low frequency component signal, and a high frequency signal that is a K sound signal A control unit that separates the signal into component signals, opens a gate section around the peak point of the low-frequency component signal, and extracts a high-frequency component signal in the gate section. Thus, only the K sound detection air bag and the K sound sensor need be used, and the gate section can be set from the signal of the K sound sensor for K sound measurement. A function for detecting a pulse wave superimposed on a signal is not required, and a CPU having a large processing capacity is not required, and an electronic sphygmomanometer that can reduce costs can be provided. That is, by using the K sound detection air bag and the K sound sensor, the signal from the K sound detection air bag is not used but the signal from the K sound detection air bag is used. The high-frequency component signal can be obtained, and the high-frequency component signal can be appropriately multiplied by a gate interval to reliably obtain the K sound signal.
This peak point is the first obtained retroactively from the time when the low frequency component signal exceeds the predetermined first threshold and becomes equal to or lower than the predetermined second threshold smaller than the first threshold. It is a peak value. Thereby, a peak point can be obtained reliably using the first threshold value and the second threshold value.
In addition, as the setting of the gate interval, the period from the time when the low frequency component signal exceeds the first threshold to the time when it falls below the second threshold is used. Thereby, the setting of a gate area can be reliably set using the said low frequency component signal.

  In the embodiment of the electronic sphygmomanometer according to the present invention, the abutting cloth portion that is in contact with the surface to be measured of the upper arm by being a cylindrical body that covers the inner surface of the ischemic bladder, and the abutment so as to accommodate the ischemic bladder An outer member joined to the outer side of the cloth part, the abutting cloth part is deformable and elastic, and the outer member is deformable but less elastic than the abutting cloth part It is formed of a cloth member. Thereby, since it can also fold, the electronic blood pressure meter which has an easy-to-use compact armband part can be provided.

A tube connected to the air bag for ischemia and the air bag for detecting K sound, and a pump for sending air to the air bag for preventing blood and the air bag for detecting K sound through each tube, and the K sound sensor and the pump Is arranged in the sphygmomanometer body.
In order to inflate the air bag for ischemia evenly by dividing it into four when inflated, there are provided a plurality of portions for thinning the meat attached to the air bag for ischemia to generate wrinkles when the bag is inflated. Since the K sound detecting air bag is arranged between the plurality of bent portions, the arm band portion including the air blocking air bag is used as the K sound detecting air bag. It can be reliably folded at the bent portion without being affected by the arrangement of the slab and can be stored compactly.
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.
The K sound sensor is connected to a condenser microphone in the sphygmomanometer body by a tube with respect to the K sound detection air bag. Thereby, the K sound sensor and the condenser microphone can be reliably connected using the tube.
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.
In the above-described embodiment of the present invention, the gate section set for the high frequency component signal DS3 of the K sound detection air bag opens the gate section around the peak point of the low frequency component signal, The high-frequency component signal is extracted.
However, for example, although the pulse differs for each measurer, the pulse of the measurer may be obtained in advance, and the gate interval may be set according to this pulse. Specifically, if the basic gate interval is 600 msec and the pulse rate is 180 times / minute (3 times / second), then 600 msec × 1/3 = 200 msec, 60 times / minute (1 time / second) The gate interval can be made variable according to the pulse wave number, such as 600 msec × 1/1 = 600. Moreover, it is also possible to set a gate section in a section from a time point exceeding the threshold value A to a time point exceeding the threshold value B by appropriately providing a threshold value instead of capturing a peak.
Although the threshold value A and the threshold value B in FIG. 16B are determined to be 3 (× 10 ⁻² ) mmHg from the result of the weak pulse person, they are not limited to this value. Further, it is conceivable to use a threshold value for setting the gate interval as described above, and it is desirable to set the threshold value according to the application.
Furthermore, although a 0.2 to 1 Hz signal is extracted as a low frequency component signal, it has been confirmed that a gate section can be provided with a 0.1 to 10 Hz signal. Since the SN is improved by using a low value as the frequency component, it is desirable to use a signal of 0.2 to 1 Hz. Although 40-80 Hz is used as the high frequency component, it is not limited to this as long as it is a frequency band suitable for K sound measurement.
Moreover, although a condenser microphone is mentioned as an example of the K sound sensor, a piezoelectric microphone, a dynamic microphone, a boundary microphone, or the like can be used as a sensor capable of measuring the K sound. Moreover, if only the gate section is set, 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.

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.

  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 an abutment cloth part), 56... Control system (control part), 500. K sound sensor, 900 ... K sound signal, PP ... peak point, DS1 ... K signal detection air bag (small cuff) raw signal, DS2 ... K sound detection air bag (small cuff) ) Low frequency component signal, DS3 ... K sound detection air bag (small cuff) high frequency component signal (K sound signal), GT ... gate section

Claims (5)

It has a cylindrical armband that can be pressed through the upper arm, and a sphygmomanometer body formed separately from the armband,
The armband is
An air bag for ischemia capable of pressurizing the upper arm by supplying air;
A plurality of K sound detection air bags disposed inside the ischemic air bag and having an air capacity smaller than the air capacity of the ischemic air bag,
Further, the air bag for ischemia pressurizes the upper arm to stop the blood flow in the blood vessel of the artery and then depressurizes the air bag to detect a change in air in the air bag for detecting the K sound that occurs when the blood flow again flows. K sound sensor for obtaining signals,
The signal obtained from the K sound sensor is separated into a low frequency component signal and a high frequency component signal that is a K sound signal, and a gate section is opened around a peak point of the low frequency component signal, and the gate An electronic blood pressure monitor, comprising: a control unit that extracts the high-frequency component signal in the section.   The peak point is obtained retrospectively from the time when the low-frequency component signal exceeds a predetermined first threshold value, becomes equal to or less than a predetermined second threshold value that is smaller than the first threshold value, and falls below the second threshold value. The electronic sphygmomanometer according to claim 1, wherein the electronic sphygmomanometer is an initial peak value.   3. The electron according to claim 1, wherein as the setting of the gate section, an interval from a time when the low frequency component signal exceeds a first threshold to a time when the low frequency component signal falls below a second threshold is used. Sphygmomanometer.   4. 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 K sound detection air bag. Total.   The electronic sphygmomanometer according to any one of claims 1 to 4, wherein a backing is provided between the air bag for ischemia and the air bag for detecting the K sound.

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