JP2013188307A - Sphygmomanometer and method for controlling the same - Google Patents

Abstract

PROBLEM TO BE SOLVED: To provide a sphygmomanometer that can reduce blood pressure measuring time without requiring repeated blood pressure measurement.SOLUTION: A sphygmomanometer 1 includes: an airbag 20 arranged in a cuff part 3, which is pressurized to block blood flow of an upper arm T by supplying air; a pressure sensor 110 for detecting the pressure in the airbag; and a control part 100 for setting a pulse rate detection period t3 to calculate pulse rate from a plurality of pulse waves (WS1-WS4) between a pressure rise period in which air is supplied to the airbag for pressurizing the upper arm T by obtaining the pressure applied to the upper arm T by a pressure detection signal from the pressure sensor 110 and an optimum speed pressure reduction period t4 in which the pressure is reduced at an optimum speed by removing the air from the airbag.

Description

  The present invention relates to a sphygmomanometer that measures the blood pressure of a patient by wrapping an armband around an upper arm and a control method thereof.

  For example, a sphygmomanometer used by a medical staff such as a nurse in a medical institution includes, for example, a manual pressurization type that integrates an air balloon for feeding air to an armband and a sphygmomanometer body. The arm band portion of the blood pressure monitor has an ischemic air bag for blocking the artery and an arterial pulsation detecting air bag attached to the ischemic air bag. When a medical worker manually holds or releases the air balloon, air is sent from the sphygmomanometer body through the tube to the air bag for ischemia in the armband, and the patient's upper arm is pressurized to measure blood pressure. Medical personnel can easily operate the air balloon with one hand, and when sending air to the air bag for ischemia in the armband, a motor to send air is unnecessary, so quiet blood pressure measurement should be performed even at night (See Patent Document 1).

Japanese Patent No. 4673020

  The thickness of the upper arm of the patient who is the subject to be measured varies depending on the patient, but the rate at which the arm band attached to the upper arm is depressurized and then depressurized is constant. The specification is such that when a medical worker pressurizes the armband with an air balloon, the medical worker determines the pressure at which the pressurizing operation of the air balloon is stopped. Usually, the pressure for stopping the pressurizing operation needs to reach a pressure amount (overshoot pressure amount) higher by 30 mmHg to 40 mmHg in addition to the patient's maximum blood pressure value. If this amount of overshoot pressure is not sufficient, the armband will be under-pressurized against the upper arm. When the pressurization becomes insufficient, the medical staff needs to pressurize the air balloon again to secure the necessary overshoot pressure amount.

  By the way, at the actual blood pressure measurement site, medical personnel have judged that blood pressure can be measured if the pressure applied to the armband slightly exceeds the patient's maximum blood pressure value, and stopped the pressurization work with the air balloon May end up. In this case, if the required overshoot pressure amount is not secured, the number of pulse waves that can be detected before reaching the point at which the maximum blood pressure value can be measured is small, and the pulse rate cannot be measured. If the pulse rate cannot be obtained in this way, the maximum blood pressure value, the minimum blood pressure value, etc. cannot be accurately measured in a state where the pressure is reduced thereafter. For this reason, the medical worker repeatedly pressurizes the upper arm until the patient's pulse rate is obtained by performing the pressurization operation of the air balloon again, so that the blood pressure measurement time becomes long. If the blood pressure measurement time is long, the upper arm may cause pain such as numbness.

  Accordingly, an object of the present invention is to provide a sphygmomanometer capable of measuring blood pressure with high accuracy and reducing the burden on the patient by reducing the frequency of repressurization and shortening the blood pressure measurement time, and a control method thereof. To do.

The sphygmomanometer according to the present invention is a sphygmomanometer that measures blood pressure by attaching an armband part to the upper arm of a person to be measured, the pressurizing means for manually pressurizing the air bag of the armband part, and the arm Decompression speed control means for controlling the pressure reduction speed of the internal pressure of the air bag in the belt part, pressure detection means for detecting the internal pressure of the arm belt part, and the pressure detection means in the process of reducing the internal pressure of the arm belt part Blood pressure determining means for determining a systolic blood pressure value and a diastolic blood pressure value based on the output signal, and a control section, wherein the decompression speed control means is configured to perform the pulse rate detection period and the arm speed section of the optimum speed decompression period. The pressure reduction rate of the internal pressure is controlled by the control unit based on the pulse rate measured during the pressure reduction rate period. , The pulse wave detected in the optimum speed decompression period and the armband And determining the systolic blood pressure value and the diastolic blood pressure value based on the internal pressure.
According to the above configuration, since the determination of insufficient pressurization is performed, there is little pressure reduction until the determination of insufficient pressurization, the frequency of insufficient pressurization is reduced, and the blood pressure measurement time can be shortened. That is, the control unit can calculate the pulse rate of the patient from a plurality of pulse waves in the pulse rate detection period. The control unit can calculate an optimum decompression speed suitable for the measurement subject according to the magnitude of the pulse rate of the measurement subject. For this reason, the blood pressure measurement of the measurement subject can be accurately performed in a state where the pressure is reduced at an optimal pressure reduction rate suitable for the measurement subject.

Preferably, the pulse rate detection period is a low-speed decompression period in which decompression is performed at a decompression speed smaller than the decompression speed in the optimum speed decompression period.
According to the above configuration, the control unit obtains a plurality of pulse waves during the low-speed decompression period, and determines whether or not pressurization is insufficient. Therefore, there is little pressure reduction until the determination of insufficient pressurization, and the frequency of insufficient pressurization is reduced. .
Preferably, the pulse rate detection period is a pressure holding period in which the decompression speed is zero.
According to the above configuration, since the control unit obtains a plurality of pulse waves during the pressure holding period and determines the lack of pressurization, there is no need to repeatedly measure the blood pressure, and the blood pressure measurement time can be shortened. .

Preferably, the air bag of the armband part includes an air bag for ischemia that insulates the upper arm by supplying the air, and an arterial pulse that detects the pulsation of the artery of the upper arm by supplying the air. It is comprised by the air bag for a motion detection, The said air bag for an ischemia and the air bag for an arterial pulsation detection are accommodated by the armband | band | zone part cover.
According to the above configuration, the air bag for detecting arterial pulsation and the air bag for detecting arterial pulsation are housed in the armband cover, so that the air bag for detecting arterial pulsation can be easily positioned according to the artery of the upper arm. Can be wound. For this reason, accurate blood pressure measurement can be performed.

Preferably, it has a blood pressure monitor main body part connected to the air bag for ischemia of the armband part and the air bag for arterial pulsation detection using a tube, and the blood pressure monitor main body part is a housing And a balloon for sending the air through the tube to the air bag for ischemia and the air bag for detecting arterial pulsation by being attached to the housing and pushing. The medical worker can hold the air balloon with one hand, and the medical worker can wrap the arm band with the upper arm easily while positioning the arm band with the other hand. It can be improved.

  The present invention can provide a sphygmomanometer and a method for controlling the sphygmomanometer that can shorten the blood pressure measurement time without the need to repeatedly measure blood pressure.

1 is a perspective view showing a preferred embodiment of a sphygmomanometer according to the present invention. The front view of the sphygmomanometer shown in FIG. The figure which shows the example of the display item which the display part 8 can display. The figure which shows the example of a control circuit block arrange | positioned in the blood pressure meter main-body part, and the structural example of an armband part. The perspective view which shows the state which an arm band part is going to wind. 6A shows an inner surface side of the armband portion, and FIG. 6B is a perspective view showing an outer surface side of the armband portion. FIG. 7A is a plan view showing the outer surface side of the armband portion, and FIG. 7B shows an air bag for ischemia and an air bag for detecting arterial pulsation arranged inside the armband portion. The top view which shows the example of a shape. The figure which shows the example of the procedure which winds an arm belt part directly on the bare skin of the upper arm T of a patient. The blood pressure meter of embodiment of this invention WHEREIN: The figure which shows the example of the change of the pressure from which the pressure applied with respect to an upper arm by the air bag for ischemia changes with time passage, and the trend curve CC of a pulse (pulse wave). FIG. 10A shows an example of a change in pressure that changes with the passage of time shown in FIG. 9 and a pulse (pulse wave) trend curve CC, and FIG. 10B is outside the scope of the present invention. The figure which expands and shows the change example of the pressure which changes with time passage in a certain comparative example, and the trend curve DD of a pulse (pulse wave). The flowchart which shows the procedure in which the sphygmomanometer of embodiment of this invention performs a blood-pressure measurement. The figure which shows another embodiment of this invention.

Hereinafter, preferred embodiments of the present invention will be described in detail with reference to the drawings.
The embodiments described below are preferred specific examples of the present invention, and thus various technically preferable limitations are given. However, the scope of the present invention is particularly limited in the following description. Unless otherwise stated, the present invention is not limited to these embodiments.

FIG. 1 is a perspective view showing a preferred embodiment of the sphygmomanometer of the present invention. FIG. 2 is a front view of the sphygmomanometer shown in FIG.
As shown in FIG. 1, the sphygmomanometer 1 can measure a patient's blood pressure by pressurizing the patient's upper arm T by a manual pressurization method by a medical staff such as a nurse. This manual pressurization type sphygmomanometer 1 has an integrated air balloon and sphygmomanometer body, and a medical worker can pressurize the air balloon with one hand, and there is no motor sound. Blood pressure can be measured quietly at night.

  When using the sphygmomanometer 1, the medical staff can select three measurement modes according to the patient's pathological condition. The three measurement modes are a normal mode, a slow mode, and an auscultation mode. The normal mode is a mode in which blood pressure measurement can be performed more quickly by automatic measurement. Slow mode is a mode in which the pressure reduction rate after pressurization can be set slower than the pressure reduction rate after pressurization in normal mode, and blood pressure can be measured for patients with low blood pressure or patients with weak pulses. It is. The auscultation mode is a mode in which a medical worker measures blood pressure by an auscultation method using a stethoscope without performing automatic measurement.

The measurement method in the sphygmomanometer 1 shown in FIGS. 1 and 2 is an oscillometric method (so-called double cuff method), and as shown in FIG. 1, the measurement target site is the upper arm T of a patient who is a subject. A dry battery is used as a power source to be used.
As shown in FIGS. 1 and 2, the sphygmomanometer 1 has a sphygmomanometer main body 2 and an armband 3. The sphygmomanometer main body 1 has a housing 4 and an air balloon 5. The air balloon 5 is made of a stretchable material so that a medical worker can pressurize the internal air. The air balloon 5 is a rubber balloon, for example.

A housing 4 of the sphygmomanometer main body 2 shown in FIGS. 1 and 2 is made of plastic, and has a rectangular display unit 8, a power switch 9, a mode switch 10, and an exhaust switch 11. The display unit 8 is, for example, a liquid crystal display device or an organic EL (electroluminescence) display device, and may be a single color display or a color display. The display unit 8 can display a maximum blood pressure value, a minimum blood pressure value, a pulse rate, and which of the three measurement modes described above is selected.
The power switch 9 can be turned on or off by the medical staff by pressing the power switch 9. When the medical switch is pressed, the mode switch 10 can switch the measurement mode to any of the above-described normal mode, slow mode, and auscultation mode. The exhaust switch 11 can be forcibly discharged by a medical worker by pushing the air in the blood bag for ischemia and the air bag for detecting arterial pulsation in the armband portion 3 described later.

  The two tubes 6 and 7 are flexible tubes that connect the housing 4 of the sphygmomanometer body 2 and the armband 3. The tube 6 is thicker than the tube 7. One end portion 6 </ b> B of the tube 6 is connected to the upper portion of the housing 4 via the connector portion 12. One end portion 7B of the tube 7 is connected to the upper portion of the housing 4 via a plug 7C and a connector portion 12. The vicinity of the ends 6B and 7B of the tubes 6 and 7 are fixed by a holder 13. As described above, the tubes 6 and 7 are fixed by the holder 13 so that the tubes 6 and 7 are not separated, but the one end portion 7B of the thin tube 7 is connected to the one end portion 6B of the thick tube 6. In comparison, the length of the tube 6 is provided with a margin so that the movement of the tube 7 can follow the movement of the tube 6. As a result, even if the thick tube 6 is pulled in an unreasonable direction by pulling the thick tube 6, the thin tube 7 is not pulled by being pulled by the thick tube 6.

  As shown in FIG. 1, an extension portion 14 is formed on the lower portion of the housing 4 so as to protrude downward. The extension portion 14 is a thin plate-like member that covers a part of the front portion 5S of the air balloon 5. As shown in FIG. 2, the medical staff repeats the operation of grasping and releasing the air balloon 5 while supporting the extension 14 with the fingers of the hand H, whereby the air from the air balloon 5 is converted into the blood pressure monitor main body 2. It can be supplied to the air bag for ischemia and the air bag for detecting arterial pulsation in the armband portion 3 through the inner pipe and the tubes 6 and 7. Projections 4T are formed on both sides of the housing 4.

In FIG. 3, the example of the display item which the display part 8 displays with a liquid crystal is shown.
As shown in FIG. 3, the display unit 8 includes a maximum blood pressure value display area 8A, a minimum blood pressure value display area 8B, a pulse display area 8C, a pulse wave signal display area 8D, a previous value display area 8E, and a display area during exhaust. 8F, under-pressurized display area 8G, over-pressurized display area 8H, and selected mode display area 8K.
The systolic blood pressure value display area 8A displays the instantaneous pressure of blood pressure during pressurization and decompression, and finally displays the systolic blood pressure value. The lowest blood pressure value display area 8B displays the lowest blood pressure value finally determined.

  The pulse display area 8C shown in FIG. 3 displays the measured pulse value. The pulse wave signal display area 8D displays the magnitude of the detected pulse wave signal, and the magnitude of the pulse wave signal is displayed in a bar shape that moves to the left and right. In the case of a patient with a normal pulse, the display of the magnitude of the pulse wave signal rhythmically increases or decreases from side to side, but in the case of a patient with arrhythmia, the display of the magnitude of the pulse wave signal Rhythmically does not increase or decrease from side to side. By providing this pulse wave signal display region 8D, it is possible to visually determine whether or not the patient who is the subject has arrhythmia.

  The previous value display area 8E shown in FIG. 3 blinks or lights up when the power switch 9 is pressed to activate the operation of the sphygmomanometer body 2, and the highest blood pressure value (systolic blood pressure value) and the lowest blood pressure value measured last time. (Diastolic blood pressure value) and pulse value are displayed in the systolic blood pressure value display area 8A, the diastolic blood pressure value display area 8B, and the pulse display area 8C, respectively. Then, after a while or when the air balloon 5 is operated to supply air, the display of the highest blood pressure value, the lowest blood pressure value, and the pulse value measured last time disappears, and the display area 8E for the previous value is displayed. When the power switch 9 is pressed and the operation of the sphygmomanometer body 2 is started, the blinking or lighting is also extinguished. The display area 8 </ b> F during exhausting blinks when the air in the air bag for ischemia and the air bag for detecting arterial pulsation in the armband 3 is rapidly exhausted. The display area 8F during exhaust also blinks when the exhaust switch 11 is pressed.

When the underpressurized display area 8G shown in FIG. 3 is lit or blinking, it indicates that the pressure in the armband 3 has not reached a level sufficient for blood pressure measurement. Can be further encouraged to send air using the air balloon 5.
When the overpressurization display area 8H is lit or blinking, it indicates that the pressure in the armband 3 is equal to or higher than a predetermined pressure (for example, 320 mmHg or higher), and the medical staff By confirming the display area 8H, it is possible to prompt the user to stop the pressurizing operation.

  The selected mode display area 8K displays which mode is selected from the normal mode, the slow mode, and the auscultation mode by pressing the mode switch 10. By selecting this mode, the exhaust (decompression) speed can be changed. When the normal mode is selected, the exhaust speed is set to about 5 mmHg / sec, for example. In the normal mode, there is an advantage that the measurement time can be made relatively short because the exhaust speed is relatively fast. On the other hand, since the increment of the pressure change measurement is large, there is no particular problem when measuring a person with stable pulse, but when measuring the blood pressure of a person with arrhythmia, the pulse is easily lost. Measurement error may increase.

Therefore, a slow mode is provided. When this slow mode is selected, the exhaust speed is set to approximately half of the normal mode, for example, 2.0 to 2.5 mmHg / sec. In this manner, in the “slow” mode, the pressure change can be seen in detail by reducing the pressure more slowly than usual, so that the person with an arrhythmia that is likely to lose a pulse can be measured more accurately.
Further, the auscultation mode is a mode in which measurement is performed manually using a stethoscope. In this case, the exhaust speed is set to about half of the normal mode, for example, 2.0 to 3.0 mmHg / sec.

Next, an example of a control circuit block arranged in the sphygmomanometer body 2 of the sphygmomanometer 1 will be described with reference to FIG. FIG. 4 shows an example of a control circuit block arranged in the sphygmomanometer main body 2 and a configuration example of the armband 3.
A control unit 100 is disposed inside the housing 4 of the sphygmomanometer body 2 shown in FIG. 4, and the control unit 100 has a central processing unit (CPU) 101. The control unit 100 includes a display unit 8, a power control unit 102, a power switch 9, a mode switch 10, an exhaust switch 11, a pressure sensor 110, a ROM (read only memory) 111, and a RAM (random access memory). ) 112, the driving unit 113, and the buzzer 114.

The power of the battery 115 shown in FIG. 4 is supplied to the control unit 100 by being controlled by the power control unit 102. The battery 115 may be a dry battery or a secondary battery (rechargeable battery), but preferably a medical worker performs a pressurizing operation of the air balloon with one hand, so that power consumption during measurement is Since it is about 0.5 W, as a power source to be used, for example, only one AA dry battery (DC1.5V) or AA rechargeable battery (DC1.5V) is used. Therefore, when a new AA battery (DC1.5V) is used, blood pressure can be measured about 1000 times, and the entire sphygmomanometer 1 can be reduced in size and weight (about 135 g). The display unit 8 displays the display items described with reference to FIG.
The pressure sensor 110 detects the pressure in the air bag 20 for ischemia of the armband portion 3 and the pressure in the air bag 40 for detecting arterial pulsation, which will be described later. The pressure sensor 110 detects a change in pressure in the air bag 20 for ischemia. Moreover, the pressure in the air bag 40 for detecting arterial pulsation varies due to the vibration of the arterial wall due to the arterial pulsation of the upper arm T during blood pressure measurement, that is, due to the pulse wave of the artery of the upper arm T. This pressure fluctuation is detected. The air bag 20 for ischemia is also called a large cuff, and the air bag 40 for detecting arterial pulsation is also called a small cuff.

  The ROM 111 stores a control program and various data in advance. The RAM 112 temporarily stores calculation results and measurement results. The drive unit 113 drives the electromagnetic valve 116 according to a command from the control unit 100. When the armband portion 3 pressurizes the upper arm T, the fluctuation value of the pressure detected by the pressure sensor 110 is considerably larger than the fluctuation value of the pressure at the time of depressurization, which is the measurement time. For this reason, when the control unit 100 determines that the fluctuation value of the pressure detected by the pressure sensor 110 is greater than or equal to a predetermined value, the control unit 100 determines that the pressurization is currently being performed and instructs the drive unit 113 to The valve 116 is closed.

On the other hand, when the control unit 100 determines that the pressure fluctuation value (increase value) is substantially zero or in a reduced pressure state within a predetermined period with respect to the pressure detected by the pressure sensor 110, the control unit 100 instructs the drive unit 113. The electromagnetic valve 116 is opened so that the pressure reduction speed becomes a predetermined value. The operation of the sphygmomanometer 1 shifts from the pressurization mode to the measurement mode.
The forced exhaust valve 117 is opened by a command from the control unit 100 when the exhaust switch 11 is pressed.
The buzzer 114 generates a predetermined warning sound according to a command from the control unit 100. For example, the buzzer 114 may cause an error when the blood pressure value is determined when the power switch 9 of the sphygmomanometer body 2 is pressed and the display unit 8 is ready for display, when the mode is switched by pressing the mode switch 10, A warning sound is generated when an error occurs.

  The forced exhaust valve 117 shown in FIG. 4 is disposed between the one end 6 </ b> B of the tube 6 and the conducting tube 120. The air supply bulb 5 is connected to one end portion 6B of the tube 6 through the manifold 118, the branching portion 119, the conducting tube 120, and the forced exhaust valve 117. The other end 6A of the tube 6 is connected to the air bag 20 for ischemia. In addition, the air supply balloon 5 is connected to the pressure sensor 110 via the manifold 118, the branch portion 119, the manifold 121, and the branch portion 122. The branch portion 122 is connected to one end portion 7 </ b> B of the tube 7. The other end 7A of the tube 7 is connected to an air bag 40 for detecting arterial pulsation. In this way, the air bag 20 for ischemia and the air bag 40 for detecting arterial pulsation communicate with each other so that the internal pressure becomes equal.

  Thereby, the pressure sensor 110 can detect the pressure in the air bag 20 for ischemia and the fluctuation of the pressure, the pressure in the air bag 40 for detecting arterial pulsation, and the fluctuation of the pressure. When a medical worker grasps or separates the air balloon 5, the air enters the ischemic air bladder 20 through the manifold 118, the branch portion 119, the conducting tube 120, the forced exhaust valve 117, and the tube 6. While being able to send in, air can be sent into the air bag 40 for detecting arterial pulsation through the manifold 118, the branch part 119, the manifold 121, the branch part 122, and the tube 7.

Next, a structural example of the armband portion 3 shown in FIG. 1 will be described.
The arm band portion 3 is directly wound around the bare skin of the upper arm T of a patient (a person to be measured), and detailed structural examples are shown in FIGS.
FIG. 5 is a perspective view showing a state in which the armband portion 3 is about to be wound. FIG. 6A shows the inner surface side of the armband portion 3, and FIG. 6B is a perspective view showing the outer surface side of the armband portion 3. FIG. 7A is a plan view showing an outer surface side of the armband portion 3, and FIG. 7B is a blood-filling air bag 20 disposed inside the armband portion 3 and for detecting arterial pulsation. 4 is a plan view showing a shape example of an air bag 40. FIG.

As shown in FIGS. 5, 6, and 7 (A), the armband 3 includes a cuff cover 50, a blood cuff 20 for ischemia that is a large cuff, and an air bag 40 for detecting arterial pulsation that is a small cuff. have. The cuff cover 50 covers the ischemic air bladder 20 and the arterial pulsation detecting air bladder 40 by detachably storing them.
The cuff cover 50 includes an outer cloth 51 and an inner cloth 52, and the outer cloth 51 and the inner cloth 52 are rectangular. The end portion of the outer cloth 51 and the end portion of the inner cloth 52 are fixed by, for example, sewing with a thread. In the outer cloth 51 and the inner cloth 52, an air bag 20 for ischemia and arterial pulsation detection are provided. The air bag 40 can be detachably stored. Thereby, the cuff cover 50 can be removed from the air bag 20 for ischemia and the air bag 40 for detecting arterial pulsation, and can be replaced or disinfected.

  The outer cloth 51 and the inner cloth 52 of the cuff cover 50 shown in FIGS. 5, 6, and 7 (A) constitute a housing that covers the outer surface of the air bag for ischemia, and are not stretched in the circumferential direction and the longitudinal direction. It is a cloth member that is made of a flexible material and is deformable but has very low or almost no stretchability. Thereby, when the outer cloth 51 and the inner cloth 52 supply air into the air bag 20 for ischemia and the air bag 40 for detecting arterial pulsation, the air bag 20 for detecting ischemia and the air bag for detecting arterial pulsation are used. It is possible to prevent 40 from expanding outward in the radial direction of the armband portion 2. Therefore, the air bag 20 for ischemia and the air bag 40 for detecting arterial pulsation can apply pressure to the upper arm T side, which is the inner side in the radial direction. The pressure generated by the air bag 40 can be pressurized against the upper arm T without escaping to the outside of the armband portion 2, and accurate blood pressure measurement can be performed.

  As shown in FIG. 7A, the cuff cover 50 has an extraction opening 50P. The extraction opening 50P is a gap between the outer cloth 51 and the inner cloth 52, and is used to take out the ischemic air bag 20 and the arterial pulsation detecting air bag 40 housed in the cuff cover 50. On the contrary, it is provided to be inserted into the cuff cover 50. In order to easily take out the air bag 20 for ischemia and the air bag 40 for detecting arterial pulsation from the opening 50P into the cuff cover 50, or conversely, to insert into the cuff cover 50, a rectangular ischemic air bag. 20 has a trapezoidal extension 21. The trapezoidal extension portion 21 is located at a position corresponding to the opening portion 50P, and has an inclined portion 22 so that the extension portion 21 decreases in width toward the outside. As a result, when the medical staff grasps the extension portion 21 by hand, the air bag 20 for ischemia and the air bag 40 for detecting arterial pulsation are taken out through the opening portion 50P, or conversely, are inserted into the cuff cover 50. Can be done easily.

  Moreover, as shown in FIGS. 7A and 7B, the extended portion 21 is formed so that its position is slightly shifted from the center with respect to the longitudinal direction of the air bag 20 for ischemia. For this reason, when the air bag 20 for ischemia and the air bag 40 for detecting arterial pulsation are inserted into the cuff cover 50 from the opening portion 50P, they are prevented from being inserted in the opposite directions. That is, if the air bag 20 for ischemia and the air bag 40 for detecting arterial pulsation are inserted in the cuff cover 50 from the opening portion 50P in the correct direction, the extension portion 21 coincides with the position of the opening portion 50P. If inserted in the direction, the extension portion 21 does not coincide with the position of the opening portion 50P. From this, the medical staff can determine whether or not the blood bag 20 for ischemia and the air bag 40 for detecting arterial pulsation are inserted into the cuff cover 50 correctly.

As the arm band portion 3 shown in FIG. 7A, different sizes can be prepared in consideration of the dimensions of the patient's arm. The size of the armband part 3 is, for example, from small to large, SS size (applicable to upper arm circumference 13 to 20 cm), S size (applicable to upper arm circumference 17 to 26 cm), M size (upper arm circumference 24 to 32 cm), L size (applicable to upper arm circumference 32 to 42 cm), and LL size (applicable to upper arm circumference 42 to 50 cm). The armband portion 3 shown in FIG. 7A shows a length L1 and a width W1 in the horizontal direction, and examples of dimensions of each size are as follows.
For example, the lateral length L1 and width W1 of the cuff cover 50 of the SS-sized armband 3 are (345 ± 5 mm, 100 ± 4 mm), and the lateral length L2 and width W2 of the ischemic bladder 20 are (130). The lateral length L3 and the width W3 of the air bag 40 for detecting arterial pulsation are (30 ± 1 mm, 20 ± 1 mm).
For the S size cuff, for example, the lateral length L1 and width W1 of the cuff cover 50 of the armband portion 3 are (435 ± 5 mm, 130 ± 4 mm), and the lateral length L2 and width W2 of the air bag 20 for ischemia. (170 ± 10 mm, 110 ± 5 mm), the lateral length L3 and the width W3 of the air bag 40 for detecting arterial pulsation are (40 ± 1 mm, 25 ± 1 mm).
For the M size cuff, for example, the lateral length L1 and width W1 of the cuff cover 50 of the armband portion 3 are (520 ± 5 mm, 150 ± 4 mm), and the lateral length L2 and width W2 of the air bag 20 for ischemia. (240 ± 10 mm, 130 ± 5 mm), the lateral length L3 and width W3 of the air bag 40 for detecting arterial pulsation are (60 ± 1 mm, 30 ± 1 mm).
For the L size cuff, for example, the lateral length L1 and width W1 of the cuff cover 50 of the armband portion 3 are (640 ± 5 mm, 190 ± 4 mm), and the lateral length L2 and width W2 of the air bag 20 for ischemia. (320 ± 10 mm, 170 ± 5 mm), the lateral length L3 and width W3 of the air bag 40 for detecting arterial pulsation are (80 ± 1 mm, 40 ± 1 mm).
For the LL size cuff, for example, the lateral length L1 and width W1 of the cuff cover 50 of the armband portion 3 are (220 ± 4 mm, 830 ± 5 mm), and the lateral length L2 and width W2 of the air bag 20 for ischemia. (420 ± 10 mm, 200 ± 5 mm), the lateral length L3 and width W3 of the air bag 40 for detecting arterial pulsation are (100 ± 1 mm, 50 ± 1 mm).

Next, the structure of the cuff cover 50 of the armband portion 3 will be described with reference to FIGS. 5, 6, and 7 (A).
As shown in FIGS. 5, 6 </ b> B, and 7 </ b> A, the outer cloth 51 of the cuff cover 50 is provided with a female portion 53 of a hook-and-loop fastener. The female portion 53 of the surface fastener is a rectangular member, and is arranged from the start end portion 54 side of the outer cloth 51 to a substantially central position of the outer cloth 51. Two recognition marks 55 indicating the start end portion 54 are provided on the start end portion 54 side of the outer cloth 51. The two recognition marks 55 are triangular, for example. A ring-shaped recognition mark 56 is provided near the opening 50P of the outer cloth 51. This recognition mark 56 indicates a position where the artery of the patient's upper arm T shown in FIG. 1 is compressed. For this reason, as shown in FIG. 5, when the arm band portion 3 is wound around the upper arm T and fixed, the recognition mark 56 is positioned on the artery of the upper arm T. Thus, the air bag 40 for detecting arterial pulsation can be accurately positioned on the artery, and accurate blood pressure measurement can be performed.

  On the other hand, as shown in FIGS. 5 and 6A, the inner cloth 52 of the cuff cover 50 is provided with a male portion 57 of a hook-and-loop fastener. As shown in FIG. 5, when the armband portion 3 is wound and fixed around the upper arm T, the male portion 57 of the surface fastener is detachably attached to the female portion 53 of the surface fastener described above. By being attached, the armband portion 3 can be formed into a cylindrical shape and can be fixed so that the armband portion 3 does not shift with respect to the upper arm T. The male portion 57 of the surface fastener is provided at a position closer to the end portion 58 side of the inner cloth 52. As shown in FIG. 6A, two arrow marks 59 are provided at the center position of the inner fabric 52. Two arrow marks 59 indicate that the armband portion 3 is a surface that is in direct contact with the upper arm T and the direction in which the armband portion 3 is wound.

The air bag 20 for ischemia and the air bag 40 for detecting arterial pulsation shown in FIG. 7B are bag-like members formed of a flexible material. For example, the air bag 20 for ischemia is made of natural rubber, synthetic rubber, elastomer, or the like. The air bag 40 for detecting arterial pulsation is made of polyurethane or the like.
A hard plate 65 is disposed between the air bag 20 for ischemia and the air bag 40 for detecting arterial pulsation. By arranging the hard plate 65, a minute pressure fluctuation in the air bag 40 for detecting arterial pulsation can be detected without being affected by a large pressure fluctuation in the air bag 20 for ischemia. .

  As shown in FIG. 6, the extension portion 21 of the ischemic bladder 20 is connected to the other end 6 </ b> A of the tube 6, and the arterial pulsation detecting bladder 40 is connected to the other end 7 </ b> A of the tube 7. ing. Since the other end 7A of the tube 7 having a small diameter is loosened with respect to the other end 6A of the tube 6 having a large diameter, the air bag 20 for ischemia and arterial pulsation detection are detected through the opening 50P of the cuff cover 50. When the air bag 40 is taken out or the air bag 20 for detecting ischemia and the air bag 40 for detecting arterial pulsation are accommodated through the opening 50P of the cuff cover 50, the other end portion 7A of the tube 7 having a small diameter has a large diameter. This prevents the tube 6 from being damaged by being pulled by the other end 6A.

Next, a usage example of the above-described blood pressure monitor 1 will be described.
The medical staff wraps and fixes the armband 3 directly on the bare skin of the upper arm T of the patient shown in FIG. 1 as follows. FIG. 8 shows an example of a procedure for winding the armband portion 3 directly around the skin of the upper arm T of the patient.
As shown in FIG. 8A, the arm band portion 3 to be wound around the upper arm T has the outer cloth 51 side on the lower side and the inner cloth 52 on the upper side. First, FIG. 8 (A) to FIG. ), The inner cloth 52 side is applied from the lower side of the upper arm T. The medical worker holds the start end portion 54 of the armband portion 3 by hand and winds the armband portion 3 around the upper arm T along the R1 direction. At this time, the recognition mark 56 shown in FIGS. 5 and 6A is positioned in accordance with the position of the artery of the upper arm T as shown in FIG. 40 can be accurately positioned relative to the artery of the upper arm T.
Then, as shown in FIG. 8C, the medical worker holds the end portion 58 of the armband portion 3 by hand and winds the armband portion 3 around the upper arm T along the R2 direction. The male part 57 of the surface fastener on the terminal end 58 side is detachably attached to the female part 53 of the surface fastener described above. Since the female part 53 of the hook-and-loop fastener and the male part 57 of the hook-and-loop fastener are detachably engaged with each other, the armband portion 3 can be directly wound around the skin of the upper arm T and fixed so as not to be displaced.

Next, a procedure in which the sphygmomanometer 1 measures the blood pressure of the patient's upper arm T will be described with reference to FIGS. FIG. 9 shows a pressure change example in which the pressure applied to the upper arm by the air bag for ischemia changes with time and a pulse (pulse wave) trend curve CC in the sphygmomanometer 1 according to the embodiment of the present invention. ing. FIG. 10A is an enlarged view of the pressure change example shown in FIG. 9 and the pulse (pulse wave) trend curve CC. FIG. 10B is an enlarged view showing a pressure change example and a pulse (pulse wave) trend curve DD in a comparative example which is outside the scope of the present invention. FIG. 11 is a flowchart showing a procedure in which the sphygmomanometer 1 according to the embodiment of the present invention performs blood pressure measurement.
In the pressure change examples shown in FIG. 9 and FIG. 10 (A), there are a pressure increase period t1, a natural pressure reduction period t2, a low speed pressure reduction period t3 as a pulse rate detection period, an optimum speed pressure reduction period t4, and a forced exhaust period t5. doing. The flowchart of FIG. 11 includes steps ST1 to ST11.

  In step ST1 of FIG. 11, the medical staff presses the power switch 9 shown in FIG. 3 while the arm band 3 is held in the correct posture with respect to the upper arm T as shown in FIG. By pressing 10, for example, the normal mode is selected. In step ST2 of FIG. 11, as shown in FIG. 2, the air from the air supply ball 5 is changed by repeating the manual pressurization operation by holding and releasing the air supply ball 5 while supporting the extension portion 14 with the finger of the hand H. Air is sent into the air bag 20 for ischemia and the air bag 40 for detecting arterial pulsation in the armband 3 through the piping in the sphygmomanometer body 2 and the tubes 6 and 7, respectively. Thereby, the air bag 20 for ischemia and the air bag 40 for detecting arterial pulsation in the arm band 3 attached to the upper arm T of the patient are pressurized.

  Since air is sent into the air bag 20 for ischemia in the arm band 3 and the air bag 40 for detecting arterial pulsation, as shown in FIG. 9 and FIG. The pressure in the air bag 20 increases during the pressure increase period t1. During the pressure increase period t1, the CPU (central processing unit) 101 of the control unit 100 in FIG. 4 determines that the pressurization is currently being performed, and instructs the drive unit 113 to close the electromagnetic valve 116. And in step ST3 of FIG. 11, the operation | movement which a medical worker grasps or separates the air balloon 5 is stopped, and pressurization is complete | finished. Thus, the pressurizing pressure PP for blocking the upper arm T when the pressurization is completed is a pressure higher by an arbitrary overshoot pressurization amount, for example, 30 mmHg to 40 mmHg than the maximum blood pressure value of the patient. However, this overshoot pressurization amount may be lower than 30 mmHg.

In step ST4 of FIG. 11, since the air balloon 5 which is a rubber ball is used, the pressure naturally decreases a little during the natural pressure reduction period t2 shown in FIG. 9 and FIG. Wait for a period t2 (for example, a few seconds).
After the elapse of the natural decompression period t2, in step ST5 of FIG. 11, the pressure in the air bag 20 for ischemia in the armband 3 is controlled by the control unit 100 of FIG. 4 during the slow decompression period t3 as the pulse rate detection period. When the CPU 101 determines that the pressure is reduced, the pressure in the air bag 20 for ischemia in the armband 3 is reduced at a lower speed than the optimum deceleration speed in the next optimum speed reduction period t4. When the CPU 101 determines the pressure detected by the pressure sensor 110 in FIG. 4 during the low pressure reduction period t3, the CPU 101 instructs the drive unit 113 so that the pressure reduction speed of the electromagnetic valve 116 becomes a low pressure reduction speed of a predetermined value. Open to. Thereby, the pressure in the air bag 20 for ischemia in the armband portion 3 decreases at a low pressure reduction speed of a predetermined value. At this time, the low pressure reduction speed of a predetermined value in the low speed pressure reduction period t3 is, for example, more than 0 mmHg / second and 2 mmHg / second or less.

  In this low pressure reduction period t3, as shown in step ST6 and step ST7 of FIG. 11, the CPU 101 of FIG. 4 uses the pulse signal (pulse wave) shown in FIG. 9 and FIG. The pulse wave detection and the pulse rate in the trend curve CC are calculated. In the low pressure decompression period t3 illustrated in FIGS. 9 and 10A, the CPU 101 in FIG. 4 reliably obtains the pulse wave WS4 from, for example, the 4-beat pulse wave WS1 from the pressure signal from the pressure sensor 110. The CPU 101 calculates a detection time TM1 between the pulse wave WS1 and the pulse wave WS2, a detection time TM2 between the pulse wave WS2 and the pulse wave WS3, and a detection time TM3 between the pulse wave WS3 and the pulse wave WS4. Then, HR (heart rate) = average value VE (TM1, TM2, TM3) which is an average value of these three detection times TM1 to TM3 is calculated.

  Next, in step ST8 of FIG. 11, the optimum speed pressure reduction period t4 shown in FIGS. 9 and 10A is entered. The CPU 101 of the control unit 100 in FIG. 4 can calculate the patient's pulse rate from the HR (heart rate) described above. Then, the CPU 101 obtains the optimum decompression speed in the next optimum speed decompression period t4 according to the magnitude of the patient's pulse rate. For example, if the patient's pulse rate is 30, the optimal decompression rate is 2.5 mmHg / sec. If the patient's pulse rate is 60, the optimal decompression rate is 5 mmHg / sec. If the patient's pulse rate is 120, the optimal decompression rate is 10 mmHg / sec. That is, the CPU 101 of the control unit 100 controls to increase the decompression speed (mmHg / second) when the patient's pulse rate is large, and to decrease the decompression speed (mmHg / second) when the patient's pulse rate is small. These optimum decompression speed values are stored in advance in the storage unit 100M of the control unit 100 in FIG. In step ST9 of FIG. 11, the CPU 101 of FIG. 4 reads the optimum decompression speed that matches the patient's pulse rate from the storage unit 100M, and changes it as a new optimum decompression speed.

  In step ST10 of FIG. 11, when the CPU 101 of FIG. 4 determines that the pressure detected by the pressure sensor 110 of FIG. 4 is in the reduced pressure state during the optimum speed pressure reduction period t4 shown in FIG. 9 and FIG. Instructs the drive unit 113 to open the electromagnetic valve 116 so that the pressure reduction speed becomes an optimum pressure reduction speed of a predetermined value. The optimum decompression speed of a predetermined value in the optimum speed decompression period t4 is larger than the decompression speed in the slow decompression period t3, for example, 5 mmHg / second. As a result, the pressure in the air bag 20 for ischemia in the armband 3 is reduced at an optimal pressure reduction speed of a predetermined value. During this pressure reduction, the CPU 101 shown in FIG. A maximum blood pressure value (SYS), a minimum blood pressure value (D1A), and a pulse value (pulse value) are acquired.

  Thereafter, in step ST11 of FIG. 11, during the forced exhaust period t5 shown in FIGS. 9 and 10A, the CPU 101 of FIG. 4 operates the forced exhaust valve 117, thereby providing the air bag for ischemia in the armband portion 3. 20 and the air in the air bag 40 for detecting arterial pulsation are forcibly exhausted to return the pressure to atmospheric pressure.

By the way, FIG. 10B shows a pressure change example that changes with time and a pulse (pulse wave) trend curve DD in a comparative example that is outside the scope of the present invention.
In the comparative example of FIG. 10B, the low pressure reduction period t3 in FIG. 10A is not set, and the speed reduction period t6 starts as soon as the pressure increase period t1 ends. For this reason, as shown in the pulse (pulse wave) trend curve DD, at most two pulse waves WR1 and WR2 can be detected, and only one detection time TN between the pulse wave WR2 and the pulse wave WR1 is obtained. It is done. Since only one detection time TN is obtained in this way, the CPU cannot calculate the patient's pulse rate with only one detection time TN, so the CPU can accurately calculate the patient's pulse rate during the speed reduction period t6. The decompression speed cannot be calculated. For this reason, in the comparative example of FIG. 10 (B), since the decompression speed according to the patient's pulse rate cannot be selected, accurate blood pressure measurement cannot be performed.

  On the other hand, in the embodiment of the present invention shown in FIG. 10A, the CPU 101 in FIG. 4 reliably obtains the pulse wave WS4 from, for example, the 4-beat pulse wave WS1 during the low-speed decompression period t3. Detection time TM1 using detection time TM1 between pulse wave WS1 and pulse wave WS2, detection time TM2 between pulse wave WS2 and pulse wave WS3, and detection time TM3 between pulse wave WS3 and pulse wave WS4 HR (heart rate) = average value VE (TM1, TM2, TM3) which is an average value of TM3 can be calculated from the above. Therefore, the CPU 101 in FIG. 4 can calculate the patient's pulse rate from the above-described HR (heart rate). Since the CPU 101 can calculate the optimum decompression speed according to the magnitude of the patient's pulse rate, the CPU 101 can select the exact decompression speed according to the patient's pulse rate during the optimum speed decompression period t4. Accurate blood pressure measurement can be performed.

Next, FIG. 12 shows another embodiment of the present invention.
In FIG. 12, in the sphygmomanometer 1 according to another embodiment of the present invention, the pressure applied to the upper arm by the air bag for ischemia is a pressure change example that changes over time and the pulse (pulse wave) trend curve CC. Is shown.
In the embodiment of the present invention shown in FIG. 9 and FIG. 10 (A), in step ST5 of FIG. 11, the pressure in the air bag 20 for ischemia in the armband 3 is a low pressure decompression period t3 as a pulse rate detection period. When the CPU 101 of the control unit 100 in FIG. 4 determines that the pressure is reduced, the pressure is reduced at a lower speed than the deceleration speed in the optimum speed pressure reduction period t4.

  However, in the embodiment of the present invention of FIG. 12, in step ST5 of FIG. 11, the pressure in the air bag 20 for ischemia in the armband portion 3 is maintained at a constant pressure instead of the low-speed decompression period t3. The pressure holding period is t6. That is, in the pressure holding period t7 as the pulse rate detection period, the control unit 100 in FIG. 4 instructs the driving unit 113 to close the electromagnetic valve 116, thereby holding the pressure almost constant, that is, the pressure reduction rate is 0. ~ 0.5 mmHg / sec.

  Thus, by setting the pressure holding period t7 as the pulse rate detection period between the natural decompression period t2 and the optimum speed decompression period t4, the slow decompression period t3 of the embodiment of the present invention shown in FIG. 10A. Similarly, since the CPU 101 in FIG. 4 can reliably obtain the pulse wave WS4 from the pulse wave WS1 of 4 beats, for example, the CPU 101 detects the detection time TM1 between the pulse wave WS1 and the pulse wave WS2, and the pulse wave WS2. HR (heart rate) which is an average value of the detection time TM1, the detection time TM2, and the detection time TM3 using the detection time TM2 between the pulse waves WS3 and the detection time TM3 between the pulse waves WS3 and WS4 = Average value: VE (TM1, TM2, TM3) is calculated. The CPU 101 of the control unit 100 in FIG. 4 can calculate the patient's pulse rate from the HR (heart rate) described above. Since the CPU 101 can select an optimum decompression speed according to the magnitude of the patient's pulse rate in the optimum speed decompression period t4, accurate blood pressure measurement can be performed.

  The sphygmomanometer 1 according to the embodiment of the present invention is disposed in the armband portion 3 when the blood pressure is measured by attaching the armband portion 3 to the upper arm T of a patient who is a measurement subject and pressurizing it. , The pressure sensor 110 for detecting the pressure in the air bag, the pressure applied to the upper arm T by the pressure detection signal from the pressure sensor 110, and the upper arm T There are a plurality of pulse waves (for example, WS1 to WS4) between a pressure increase period in which air is supplied to the air bag to pressurize T and an optimum speed decompression period t4 in which air is extracted from the air bag and decompressed at an optimum speed. ) To set the pulse rate detection period t3 (t7) for calculating the pulse rate. For this reason, there is no need to repeatedly measure blood pressure, and blood pressure measurement time can be shortened. That is, the CPU 101 of the control unit 100 can calculate the patient's pulse rate from a plurality of pulse waves in the pulse rate detection period t3 (t7). The CPU 101 of the control unit 100 can calculate an optimal decompression speed suitable for the patient according to the patient's pulse rate. For this reason, a patient's blood pressure measurement can be accurately performed in a state where pressure is reduced at an optimum pressure reduction speed suitable for the patient. For this reason, there is no need to repeatedly measure blood pressure, and blood pressure measurement time can be shortened.

  Further, in the sphygmomanometer 1 according to the embodiment of the present invention, the pressurization pressure PP is a pressure higher by an arbitrary overshoot pressurization amount, for example, 30 mmHg to 40 mmHg than the patient's maximum blood pressure value in the pressure increase period t1. However, even if the overshoot pressurization amount is lower than 30 mmHg, the CPU 101 of the control unit 100 can determine insufficient pressurization from a plurality of pulse waves in the pulse rate detection period t3 (t7). The CPU 101 of the control unit 100 can calculate an optimal decompression speed suitable for the patient according to the patient's pulse rate. In other words, after the natural decompression period t2 has elapsed, in the low speed decompression period t3 (pressure holding period t7), which is the pulse rate detection period, the pressure rise period t1 is reduced by making it smaller than the optimum speed decompression period t4 thereafter. It is also possible to reduce the amount of overshoot pressure applied at. For this reason, the pain of the upper arm etc. in the pressure increase period t1 can be reduced.

The pulse rate detection period is a low-speed decompression period t3 in which decompression is performed at a decompression speed smaller than the decompression speed in the optimum speed decompression period. For this reason, the control unit 100 can reliably detect the pulse rate by obtaining a plurality of pulse waves (for example, WS1 to WS4) in the low-speed decompression period t3. Time can be shortened.
Preferably, the pulse rate detection period is a pressure holding period t7 in which the decompression speed is zero. For this reason, the control unit 100 can reliably detect the pulse rate by obtaining a plurality of pulse waves (for example, WS1 to WS4) in the pressure holding period t7. Time can be shortened.
The air bag of the armband part 3 includes an air bag 20 for blocking the upper arm by supplying air, and an air bag for detecting arterial pulsation that detects the pulsation of the artery of the upper arm T by supplying air. 40, and the air bag 20 for ischemia and the air bag 40 for detecting arterial pulsation are accommodated by an armband cover 50. For this reason, the air bag 40 for detecting arterial pulsation can be wound while being positioned easily according to the artery of the upper arm T. For this reason, accurate blood pressure measurement can be performed.

  The blood pressure monitor main body 2 is connected to the air bag 20 for ischemia of the armband 3 and the air bladder 40 for detecting arterial pulsation using the tubes 6 and 7. It has a body 4 and an air balloon 5 that is attached to the housing and pushed to send air to the blood-insufficating air bag 20 and the arterial pulsation air bag 40 through the tubes 6 and 7. For this reason, while a medical worker holds an air balloon with one hand, the medical worker can wrap the armband part with the other hand only while easily positioning the armband part on the upper arm. Can be improved.

  By using the sphygmomanometer 1 according to the embodiment of the present invention, the frequency of determination of insufficient pressurization can be reduced, the frequency of repressurization can be reduced, and the blood pressure measurement time can be shortened, thereby reducing the burden on the patient. be able to. In addition, it is not necessary to secure the amount of overshoot pressure and then rapidly reduce the pressure on the armband immediately from the point of time. Can do.

The present invention is not limited to the above embodiment, and various modifications can be made without departing from the scope of the claims.
The illustrated sphygmomanometer is of a manual pressurization type, but the sphygmomanometer of the present invention is not limited to this. The automatic sphygmomanometer has an arm band part and a blood pressure monitor main body part separate from the arm band part, and the arm band part is wound around the upper arm of a patient (a person to be measured). When the pump in the sphygmomanometer main body is driven, air can be sent from the sphygmomanometer main body through the tube to the air bag for ischemia and the air bag for detecting arterial pulsation.
In each of the embodiments of the present invention shown in FIGS. 9, 10 and 12, for example, the pulse wave WS4 is detected from the four pulse waves WS1, but the present invention is not limited to this. Three pulse waves or five or more pulses are used. The patient's pulse rate may be calculated by detecting the wave.
A part of each configuration of the above embodiment can be omitted, or can be arbitrarily combined so as to be different from the above.

  DESCRIPTION OF SYMBOLS 1 ... Blood pressure monitor, 3 ... Armband part, 2 ... Blood pressure monitor main-body part, 4 ... Housing | casing, 5 ... Air balloon, 6, 7 ... Tube, 8 ... Display part 20 ... Air bag for ischemia, 40 ... Air bag for arterial pulsation detection, 50 ... Cuff cover (armband part cover), 100 ... Control part, 101 ... CPU, 110 ... Pressure sensor, T ... Upper arm, t1 ... Pressure increase period, t2 ... Natural decompression period, t3 ... Low-speed decompression period as pulse rate detection period, t4 ... Optimal speed decompression Period, t5: Forced exhaust period, t6: Speed depressurization period, t7: Pressure holding period as pulse rate detection period

Claims (6)

A sphygmomanometer that measures the blood pressure by attaching an armband to the upper arm of the subject,
Pressurizing means for manually pressurizing the air bag of the armband portion, pressure reducing speed control means for controlling the pressure reducing speed of the inner pressure of the air bag of the armband portion, and detecting the internal pressure of the armband portion Pressure detecting means, blood pressure determining means for determining a systolic blood pressure value and a diastolic blood pressure value based on an output signal of the pressure detecting means in the process of reducing the internal pressure of the armband, and a controller.
The decompression speed control means includes
Controls the pressure reduction rate of the internal pressure of the armband during the pulse rate detection period and the optimum speed pressure reduction period,
In the optimum speed depressurization period, based on the pulse rate measured in the depressurization speed period, the depressurization rate of the internal pressure of the armband is controlled by the control unit,
The sphygmomanometer, wherein the systolic blood pressure value and the diastolic blood pressure value are determined based on the pulse wave detected in the optimum speed decompression period and the internal pressure of the armband.   The sphygmomanometer according to claim 1, wherein the pulse rate detection period is a low-speed decompression period in which decompression is performed at a decompression speed smaller than the decompression speed in the optimum speed decompression period.   The sphygmomanometer according to claim 1, wherein the pulse rate detection period is a pressure holding period in which a decompression speed is zero. The air bag of the armband portion is for detecting an arterial pulsation by detecting the pulsation of the arteries of the upper arm by supplying the air, and an air bag for ischemia that suppresses the upper arm by supplying the air. Of air bag and
The sphygmomanometer according to any one of claims 1 to 3, wherein the air bag for ischemia and the air bag for detecting arterial pulsation are accommodated by an armband cover.   The sphygmomanometer body part connected to the air bag for ischemia of the armband part and the air bag for arterial pulsation detection using a tube, the sphygmomanometer body part, 5. The blood pressure according to claim 4, further comprising an air balloon that is attached to the housing and pushes the air through the tube to send the air to the air bag for ischemia and the air bag for detecting arterial pulsation. Total. Pressurizing means for manually pressurizing the air bag of the armband portion, pressure reducing speed control means for controlling the pressure reducing speed of the internal pressure of the air bag of the armband portion, and pressure detection for detecting the internal pressure of the armband portion Means, blood pressure determining means for determining a systolic blood pressure value and a diastolic blood pressure value based on an output signal of the pressure detecting means in the process of reducing the internal pressure of the arm band, and a control unit, A method of controlling a sphygmomanometer that is mounted on the upper arm of a subject and measures blood pressure,
The decompression speed control means includes
Controls the pressure reduction rate of the internal pressure of the armband during the pulse rate detection period and the optimum speed pressure reduction period,
In the optimum speed depressurization period, based on the pulse rate measured in the depressurization speed period, the depressurization rate of the internal pressure of the armband is controlled by the control unit,
A control method for a sphygmomanometer, wherein the systolic blood pressure value and the diastolic blood pressure value are determined based on a pulse wave detected during the optimum speed decompression period and the internal pressure of the armband.

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