WO2010058724A1 - 電子血圧計 - Google Patents

電子血圧計 Download PDF

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Publication number
WO2010058724A1
WO2010058724A1 PCT/JP2009/069190 JP2009069190W WO2010058724A1 WO 2010058724 A1 WO2010058724 A1 WO 2010058724A1 JP 2009069190 W JP2009069190 W JP 2009069190W WO 2010058724 A1 WO2010058724 A1 WO 2010058724A1
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WO
WIPO (PCT)
Prior art keywords
value
pressurization
pressure
specific component
manual
Prior art date
Application number
PCT/JP2009/069190
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English (en)
French (fr)
Japanese (ja)
Inventor
広幸 木下
Original Assignee
オムロンヘルスケア株式会社
Priority date (The priority date is an assumption and is not a legal conclusion. Google has not performed a legal analysis and makes no representation as to the accuracy of the date listed.)
Filing date
Publication date
Application filed by オムロンヘルスケア株式会社 filed Critical オムロンヘルスケア株式会社
Priority to RU2011124909/14A priority Critical patent/RU2519751C2/ru
Priority to US13/128,437 priority patent/US8747326B2/en
Priority to MX2011004913A priority patent/MX2011004913A/es
Priority to CN2009801466010A priority patent/CN102223836B/zh
Priority to BRPI0922002A priority patent/BRPI0922002B8/pt
Priority to DE112009003636.8T priority patent/DE112009003636B4/de
Publication of WO2010058724A1 publication Critical patent/WO2010058724A1/ja

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    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B5/00—Measuring for diagnostic purposes; Identification of persons
    • A61B5/02—Detecting, measuring or recording pulse, heart rate, blood pressure or blood flow; Combined pulse/heart-rate/blood pressure determination; Evaluating a cardiovascular condition not otherwise provided for, e.g. using combinations of techniques provided for in this group with electrocardiography or electroauscultation; Heart catheters for measuring blood pressure
    • A61B5/021—Measuring pressure in heart or blood vessels
    • A61B5/022—Measuring pressure in heart or blood vessels by applying pressure to close blood vessels, e.g. against the skin; Ophthalmodynamometers
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B5/00—Measuring for diagnostic purposes; Identification of persons
    • A61B5/02—Detecting, measuring or recording pulse, heart rate, blood pressure or blood flow; Combined pulse/heart-rate/blood pressure determination; Evaluating a cardiovascular condition not otherwise provided for, e.g. using combinations of techniques provided for in this group with electrocardiography or electroauscultation; Heart catheters for measuring blood pressure
    • A61B5/021—Measuring pressure in heart or blood vessels
    • A61B5/022—Measuring pressure in heart or blood vessels by applying pressure to close blood vessels, e.g. against the skin; Ophthalmodynamometers
    • A61B5/0225—Measuring pressure in heart or blood vessels by applying pressure to close blood vessels, e.g. against the skin; Ophthalmodynamometers the pressure being controlled by electric signals, e.g. derived from Korotkoff sounds
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B5/00—Measuring for diagnostic purposes; Identification of persons
    • A61B5/02—Detecting, measuring or recording pulse, heart rate, blood pressure or blood flow; Combined pulse/heart-rate/blood pressure determination; Evaluating a cardiovascular condition not otherwise provided for, e.g. using combinations of techniques provided for in this group with electrocardiography or electroauscultation; Heart catheters for measuring blood pressure
    • A61B5/021—Measuring pressure in heart or blood vessels
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B5/00—Measuring for diagnostic purposes; Identification of persons
    • A61B5/02—Detecting, measuring or recording pulse, heart rate, blood pressure or blood flow; Combined pulse/heart-rate/blood pressure determination; Evaluating a cardiovascular condition not otherwise provided for, e.g. using combinations of techniques provided for in this group with electrocardiography or electroauscultation; Heart catheters for measuring blood pressure
    • A61B5/021—Measuring pressure in heart or blood vessels
    • A61B5/022—Measuring pressure in heart or blood vessels by applying pressure to close blood vessels, e.g. against the skin; Ophthalmodynamometers
    • A61B5/02225—Measuring pressure in heart or blood vessels by applying pressure to close blood vessels, e.g. against the skin; Ophthalmodynamometers using the oscillometric method

Definitions

  • the present invention relates to an electronic sphygmomanometer, and more particularly to a manual pressurization type electronic sphygmomanometer.
  • An automatic pressurization sphygmomanometer has a technique for estimating the maximum blood pressure in the pressurization process, ending the pressurization when the estimated maximum blood pressure reaches a predetermined value, and shifting to a decompression (Japanese Patent Laid-Open No. 4). -261638 (Patent Document 1)).
  • Patent Document 2 Japanese Patent Application Laid-Open No. 57-145640
  • Patent Document 2 Japanese Patent Application Laid-Open No. 57-145640
  • the user cannot determine how much pressure should be applied in the first pressurizing operation.
  • this anxiety may affect blood pressure values.
  • the burden on the user is not necessarily small when the pressure is excessively applied or when repressurization is required due to insufficient pressurization.
  • the present invention has been made to solve the above-described problems, and its purpose is to notify the user of how much pressure should be applied in a series of pressurizing operations.
  • a manual pressurization type electronic blood pressure monitor is provided.
  • An electronic sphygmomanometer is a manual pressurization type electronic sphygmomanometer, which is a cuff for wrapping around a predetermined body part and a manual pressurization for pressurizing a pressure in the cuff by a manual operation by a user.
  • a pressure sensor for detecting a cuff pressure signal representing the pressure in the cuff, and a cuff pressure signal obtained during pressurization, a combined wave of a manually fluctuating wave and a pressure pulse wave by a manual operation, a specific component A specific component detection unit for detecting the pressure, a derivation processing unit for deriving the pressurization target value based on the detection result by the specific component detection unit, and a notification for urging the pressurization to the pressurization target value A notification unit.
  • the derivation processing unit subtracts the interpolation curve from the first component and the first calculation unit for calculating the interpolation curve of the manual fluctuation wave for the specific component part from the waveforms before and after the specific component.
  • a second calculation unit for calculating the pulse wave component an estimation unit for estimating the systolic blood pressure value based on the amplitude of the pulse wave component, and a value obtained by adding a predetermined value to the estimated systolic blood pressure value Is included as a pressurization target value.
  • a pressure value detection unit for detecting a current pressure value from a cuff pressure signal obtained during pressurization is further provided, and the notification unit displays the current pressure value and the pressurization target value in association with each other.
  • the notification unit notifies the end of pressurization when the current pressure value reaches the pressurization target value.
  • the derivation processing unit includes a determination unit for determining, as the pressurization target value, a value obtained by adding a predetermined value to the pressure value at the time when the specific component is detected each time the specific component is detected.
  • the specific component detection unit detects, as the specific component, a pressure fluctuation component having an amplitude value less than the first threshold in the cuff pressure signal obtained during pressurization.
  • it further includes a determination unit for determining whether or not the manual amplitude representing the amplitude of the manually varying wave is equal to or greater than the second threshold, and the second threshold represents a value equal to or greater than the first threshold.
  • the notification unit performs notification for guiding the user so that the manual amplitude is equal to or greater than the second threshold.
  • a manual pressurization type sphygmomanometer can be notified to pressurize to a pressurization target value. Therefore, the user can continue the pressurizing operation with confidence until the pressurization target value is reached. Also, excessive compression can be prevented.
  • FIG. 1 It is a figure which shows the external appearance of the blood pressure meter in embodiment of this invention. It is a block diagram which shows the hardware constitutions of the blood pressure meter in embodiment of this invention.
  • (A), (B) is a figure which shows the difference in the pressure waveform (shape of a cuff pressure signal) by the difference in a pressurization system.
  • (A), (B) is a figure which shows the difference in the pressure waveform at the time of pressurization by the difference in a pressurization system.
  • (A) to (C) are diagrams showing examples of detection of specific components and extraction of pulse wave components when the stroke is large (in the case of rapid pressurization).
  • (A) to (C) are diagrams showing an example of detection of a specific component and extraction of a pulse wave component in the case of an ordinary stroke (in the case of a general speed).
  • (A) to (C) are diagrams showing examples of detection of specific components and extraction of pulse wave components when the stroke is small (in the case of low-speed pressurization).
  • (A) to (C) are diagrams showing an example of detection of a specific component and extraction of a pulse wave component when the stroke size is irregular.
  • (A), (B) is a figure which shows the difference in the pressure waveform by the difference in an arm periphery.
  • FIG. 1 is a diagram showing an appearance of a sphygmomanometer 1 according to the embodiment of the present invention.
  • a sphygmomanometer 1 includes a main body 10, a cuff 20 for wrapping around a predetermined body part of the measurement subject, for example, an upper arm, and an air tube for connecting the main body 10 and the cuff 20. 24A.
  • the sphygmomanometer 1 includes a manual pressurizing mechanism, and includes, for example, a rubber ball 30 and an air tube 24 ⁇ / b> B for connecting the rubber ball 30 and the main body 10.
  • the rubber ball 30 is compressed by the user to send air into the cuff 20 via the air tube 24 (24A, 24B).
  • a display unit 40 for displaying measurement results and an operation unit 41 for receiving an instruction input from a user (typically a person to be measured) are arranged on the surface 10A of the main body unit 10.
  • the operation unit 41 for example, a power switch 41A for switching power ON / OFF, a measurement switch 41B for inputting a measurement start instruction, and an instruction for reading and displaying past measurement results. And a memory switch 41C.
  • the display part 40 is comprised by displays, such as a liquid crystal, for example.
  • the air tubes 24A and 24B described above are connected to the left side surface 10B of the main body 10.
  • the shape of the main body 10 of the sphygmomanometer 1 is not limited to such an example.
  • the rubber ball 30 is provided as a manual pressurizing mechanism, the invention is not limited to this.
  • the fluid for pressurizing the cuff 20 is not limited to air.
  • FIG. 2 is a block diagram showing a hardware configuration of sphygmomanometer 1 in the embodiment of the present invention.
  • the cuff 20 of the sphygmomanometer 1 includes an air bag 21 in which air is contained.
  • the rubber ball 30 supplies or discharges air to the air bag 21 via an air tube 24 (including 24A and 24B).
  • an air tube 24 including 24A and 24B.
  • a very small exhaust port 31 for discharging air at a constant speed is provided.
  • the rubber ball 30 can rapidly exhaust air when a dedicated switch (not shown) included in the operation unit 41 is pressed. The user can supply air to the air bag 21 by compressing the rubber ball 30.
  • the main unit 10 includes a CPU (Central Processing Unit) 100 for centrally controlling and monitoring each unit, a pressure sensor 32, an oscillation circuit 35, a nonvolatile memory unit 39, a display unit 40, and an operation unit. 41, a power supply unit 42, a timing unit 43 for performing a timing operation, a buzzer 44 for outputting a warning sound and a beep sound, and an LED (Light Emitting Diode) 45 for outputting light.
  • a CPU Central Processing Unit
  • the main unit 10 includes a CPU (Central Processing Unit) 100 for centrally controlling and monitoring each unit, a pressure sensor 32, an oscillation circuit 35, a nonvolatile memory unit 39, a display unit 40, and an operation unit. 41, a power supply unit 42, a timing unit 43 for performing a timing operation, a buzzer 44 for outputting a warning sound and a beep sound, and an LED (Light Emitting Diode) 45 for outputting light.
  • LED Light Emitting Diode
  • the pressure sensor 32 is a device for detecting a cuff pressure signal representing the pressure in the air bladder 21 (hereinafter referred to as “cuff pressure”).
  • the capacitance value of the pressure sensor 32 changes depending on the detected pressure.
  • the oscillation circuit 35 outputs a signal having an oscillation frequency corresponding to the capacitance value of the pressure sensor 32 to the CPU 100.
  • the CPU 100 detects a pressure (cuff pressure) by converting a signal obtained from the oscillation circuit 35 into a pressure.
  • the memory unit 39 stores various information such as a program for causing the CPU 100 to perform a predetermined operation and measurement result information.
  • the power supply unit 42 supplies power to the CPU 100 in response to a power ON instruction from the operation unit 41.
  • FIGS. 3A and 3B are diagrams showing the difference in pressure waveform (the shape of the cuff pressure signal) due to the difference in the pressurization method, and FIG. 3A shows the pressure waveform of the manual pressurization type. FIG. 3B shows an automatic pressurization type pressure waveform.
  • the cuff in a manually pressurized blood pressure monitor, the cuff is pressurized by a user (typically a person to be measured) manually operating (compressing) a rubber ball a plurality of times. For this reason, a large pressure fluctuation accompanying manual operation appears in the pressure waveform during pressurization.
  • a wave indicating a pressure fluctuation caused by a manual operation that is, a pressure fluctuation wave caused by a manual operation is referred to as a “manual fluctuation wave”.
  • the component of the pressure pulse wave (hereinafter referred to as “pulse wave component”) can be easily captured from the pressure waveform at the time of pressurization.
  • the “pressure pulse wave” is a pressure fluctuation wave representing a fluctuation of the intravascular volume accompanying the pulsation of the heart.
  • FIG. 4 (A) and 4 (B) are diagrams showing the difference in pressure waveform during pressurization due to the difference in pressurization method.
  • FIG. 4 (A) shows the pressure waveform in the period TA in FIG. 3 (A). Is enlarged and the pressure waveform in the period TB of FIG. 3B is enlarged and displayed in FIG.
  • the “pressure fluctuation component” represents a waveform from the minimum value to the next minimum value when the difference between the minimum value of the pressure waveform and the next maximum value is defined as “amplitude”. Shall.
  • the pressure fluctuation component appearing in the pressure waveform is mainly composed of the manual fluctuation wave.
  • the speed at the time of compression release (when the cuff pressure is lowered) is slower (constant) than the speed at the time of compression (when the cuff pressure is raised). Therefore, a pulse wave component can be superimposed on the cuff pressure signal at the time of compression release.
  • a plurality of pressure fluctuation components (waveforms) appearing in the pressure waveform in the case of the manual pressurization type are constituted by only manual fluctuation waves (hereinafter referred to as “manual pressurization components”), manual fluctuation waves and pressure pulses. And a combined wave (hereinafter referred to as “specific component”).
  • the sphygmomanometer 1 derives the pressurization target value by detecting the specific component from the pressure waveform (cuff pressure signal) during pressurization.
  • a specific functional configuration example of the sphygmomanometer 1 according to the present embodiment will be described.
  • FIG. 5 is a functional block diagram showing a functional configuration of the sphygmomanometer 1 in the embodiment of the present invention.
  • the CPU 100 of the sphygmomanometer 1 functions as a determination unit 102, a specific component detection unit 104, a derivation processing unit 106, a pressure value detection unit 108, a blood pressure calculation unit 110, and a display. And a control unit 112.
  • a determination unit 102 determines whether a specific component detection unit 104 or a specific component detection unit 104 or a derivation processing unit 106 or a pressure value detection unit 108, a blood pressure calculation unit 110, and a display.
  • FIG. 5 only peripheral hardware that directly exchanges signals with each unit of the CPU 100 is shown for the sake of simplicity.
  • the specific component detection unit 104 is connected to the oscillation circuit 35 and detects a specific component, that is, a combined wave of a manual fluctuation wave and a pressure pulse wave, from a pressure waveform (cuff pressure signal) during pressurization.
  • FIG. 6 is a diagram illustrating a method for detecting a specific component.
  • the difference between the minimum value 61 and the maximum value 62 is expressed as an amplitude
  • those having an amplitude less than a predetermined constant level are specified components, Those whose amplitude is above a certain level can be recognized as a manual pressurizing component.
  • the specific component detection unit 104 detects, as the specific component, a pressure fluctuation component whose amplitude is less than a predetermined threshold value Va (a constant level).
  • a predetermined threshold value Va a constant level
  • the amplitude of the manual fluctuation wave (hereinafter referred to as “manual amplitude”) is the threshold value. It is necessary to be Va or higher. Therefore, when an amplitude greater than or equal to the threshold value Va cannot be detected, it is preferable to perform notification (guide processing) that promotes appropriate pressurization. Such guide processing is executed by the determination unit 102 and the display control unit 112.
  • FIGS. 7A to 7C are diagrams showing an example of detection of a specific component and extraction of a pulse wave component when the stroke is large (in the case of rapid pressurization).
  • FIGS. 8A to 8C are diagrams showing an example of detecting a specific component and extracting a pulse wave component in the case of an ordinary stroke (in the case of a general speed).
  • FIGS. 9A to 9C are diagrams showing an example of detection of a specific component and extraction of a pulse wave component when the stroke is small (in the case of low-speed pressurization).
  • FIGS. 10A to 10C are diagrams showing an example of detection of a specific component and extraction of a pulse wave component when the stroke size is irregular.
  • FIG. 7A shows a cuff pressure signal along the time axis when the rubber ball compression is 1.7 pitch / s and the average pressurization speed is 43 mmHg / s. Is shown. Since the value of the manual amplitude is large when the stroke of the compression operation is large, the difference between the manual amplitude and the actual pulse wave amplitude (the amplitude of the pressure pulse wave) is very large. Therefore, in such a case, a specific component having a small amplitude can be detected with high accuracy.
  • FIG. 7A shows a cuff pressure signal along the time axis when the rubber ball compression is 1.7 pitch / s and the average pressurization speed is 43 mmHg / s. Is shown. Since the value of the manual amplitude is large when the stroke of the compression operation is large, the difference between the manual amplitude and the actual pulse wave amplitude (the amplitude of the pressure pulse wave) is very large. Therefore, in such a case, a specific component having a small
  • the waveform (vertical axis: amplitude) of the pulse wave component extracted from the detected specific component is shown along the same time axis as the graph of FIG. 7A. The same applies to the following graphs. A specific method for extracting (calculating) the pulse wave component from the specific component will be described later.
  • FIG. 8 (A) shows the time axis of the cuff pressure signal when the rubber ball compression is 2.0 pitch / s and the average pressurization speed is 15 mmHg / s. Is shown along.
  • the stroke of the compression operation is normal, the difference between the manual amplitude and the actual pulse wave amplitude is relatively large. Therefore, even in such a case, a specific component having a small amplitude can be detected with high accuracy.
  • FIG. 9 (A) shows the time axis of the cuff pressure signal when the rubber ball compression is 1.3 pitch / s and the average pressurization speed is 7.8 mmHg / s. Is shown along.
  • the manual pressurization component may be erroneously recognized as a specific component.
  • the cuff pressure is taken on the horizontal axis, and the amplitude value of the extracted pulse wave component is shown on the vertical axis.
  • the systolic blood pressure value (SYS) and the systolic blood pressure value (DIA) estimated by applying a predetermined algorithm to the amplitude value of the extracted pulse wave component are shown.
  • the threshold value Va may be a value that is larger than the maximum value of the pulse wave amplitude obtained by a clinical experiment or the like. For example, it is assumed that the maximum value of the pulse wave amplitude obtained in the experiment is 1.5 mmHg and the minimum value of the manual amplitude is 6.0 mmHg. Further, it is assumed that the average value and standard deviation of the pulse wave amplitude are 0.34 mmHg and 0.3 mmHg, respectively, and the average value and standard deviation of the manual amplitude are 16.16 mmHg and 7.12 mmHg, respectively. Then, the threshold value Va may be determined in advance as, for example, 2.0 mmHg out of 1.5 to 6.0 mmHg. The reason why the threshold value Va is set to such a value is that the standard deviation of the pulse wave amplitude is small.
  • the threshold value for prompting an appropriate compression stroke is set to be larger than the threshold value Va used for detecting the specific component. That is, when a threshold value for promoting an appropriate compression stroke is expressed as “Vb”, the threshold value Vb is preferably larger than the threshold value Va. Therefore, in the case of the above example, the threshold value Vb may be predetermined as, for example, 4.0 mmHg out of 1.5 to 6.0 mmHg. However, it is not limited, and the threshold value Va and the threshold value Vb may be the same value.
  • the threshold value Vb can be set to a value equal to or greater than the minimum value of manual amplitude obtained by experiment (6.0 mmHg in the above example). However, if a very large value is set, a user with a weak grip force is always notified to increase the stroke, so it can be said that it is preferable to set a value as small as possible.
  • FIGS. 11A and 11B show the difference in pressure waveform due to the difference in arm circumference.
  • FIG. 11A shows a pressure waveform of a measurement subject having a normal thickness arm (arm circumference 26.5 cm)
  • FIG. 11B shows a measurement result of a thick arm (arm circumference 42 cm).
  • the pressure waveform of the person is shown.
  • the pressurization speed changes if the arm thickness of the person to be measured is different, but if the threshold value Vb is set to an appropriate value, the arm thickness is increased. Regardless of this, it is possible to detect the specific component with high accuracy.
  • the determination unit 102 is connected to the oscillation circuit 35 and determines whether or not the manual amplitude is equal to or greater than the threshold value Vb.
  • the display control unit 112 Based on the information from the determination unit 102, the display control unit 112 performs display for guiding the user so that the manual amplitude is equal to or greater than the threshold value Vb (so that the stroke of the compression operation is increased).
  • the derivation processing unit 106 derives the pressurization target value based on the detection result by the specific component detection unit 104.
  • the derivation processing unit 106 estimates the systolic blood pressure value by extracting a pulse wave component from the specific component. Then, a value obtained by adding a predetermined value (for example, 40 mmHg) to the maximum blood pressure is determined as the pressurization target value. Specific processing executed by the derivation processing unit 106 will be described later.
  • the pressure value detection unit 108 is connected to the oscillation circuit 35 and detects the current pressure value from the cuff pressure signal obtained during pressurization.
  • the current pressure value detection method is not particularly limited. Specifically, for example, the average pressure value of each pressure fluctuation component (the average of the minimum value and the maximum value) may be detected as the current pressure value.
  • the blood pressure calculation unit 110 is connected to the oscillation circuit 35 and calculates blood pressure (for example, maximum blood pressure, minimum blood pressure) from a cuff pressure signal obtained during pressure reduction at a constant speed.
  • the processing by the blood pressure calculation unit 110 may be realized by, for example, an oscillometric method.
  • the display control unit 112 displays various types of information on the display unit 40 in accordance with signals from each unit.
  • the operation of each functional block may be realized by executing software stored in the memory unit 39, or at least one may be realized by hardware.
  • FIG. 12 is a flowchart showing the flow of blood pressure measurement processing in the embodiment of the present invention.
  • the processing shown in the flowchart of FIG. 12 is stored in advance in the memory unit 39 as a program, and the blood pressure measurement processing function is realized by the CPU 100 reading and executing this program.
  • the blood pressure measurement process described below is started when, for example, the power switch 41A and the measurement switch 41B are pressed and the user starts the compression operation of the rubber ball 30.
  • the CPU 100 initializes the working memory and adjusts the pressure sensor 32 to 0 mmHg.
  • processing by the pressure value detection unit 108 is performed in parallel with the blood pressure measurement processing described below. Accordingly, it is assumed that the current pressure value detected by the pressure value detection unit 108 during the blood pressure measurement process is displayed in a predetermined display area of the display unit 40 by the display control unit 112.
  • determination unit 102 determines whether or not the amplitude of the manual pressurization component of the pressure waveform, that is, the manual amplitude is greater than or equal to threshold value Vb (step S2). . Note that immediately after the blood pressure measurement process is started, the measurement site is not yet compressed by the cuff 20, so the pulse wave component is not superimposed on the cuff pressure signal. Therefore, the pressure fluctuation component detected immediately after the start can be determined as the manual pressurization component.
  • step S2 If the manual amplitude is greater than or equal to the threshold value Vb (YES in step S2), the process proceeds to step S6.
  • step S4 If the manual amplitude is less than the threshold value Vb (NO in step S2), the display control unit 112 notifies that the pressurization stroke is increased (step S4). As a result, the user is guided to increase the pressurization stroke (increase the pressurization speed).
  • the pressure fluctuation component may be a specific component (combined wave of manual fluctuation wave and pressure pulse wave). Therefore, it is preferable to perform the process of step S4 only when a value less than the threshold value Vb is continuously detected a plurality of times (for example, twice).
  • step S6 the specific component detection unit 104 detects a pressure fluctuation component having an amplitude less than the threshold value Va as a specific component. This process is preferably performed only when it is detected at least once in step S2 that the amplitude of the pressure fluctuation component is greater than or equal to the threshold value Vb. This is because the manual pressurization component is erroneously recognized as a specific component if the process is performed while the pressurization stroke is small.
  • step S8 the derivation processing unit 106 interpolates the waveform in the case where there is no pulse wave component for the specific component portion from the previous and subsequent waveforms (step S8). That is, an interpolation curve of manual fluctuation waves is calculated for the specific component portion.
  • step S8 will be described in detail with reference to FIG.
  • FIG. 13 is a diagram showing a pulse wave component extraction method during manual pressurization.
  • the pressure waveform during pressurization includes a manual pressurization component 81 and a specific component 82.
  • the specific component 82 indicates a wave (pressure fluctuation component) from the minimum point P2 to the next minimum point P3.
  • a pressure fluctuation component 83 immediately before the specific component 82 indicates a wave from the minimum point P0 to the next minimum point P2.
  • a pressure fluctuation component 84 immediately after the specific component 82 indicates a wave from the minimum point P3 to the next minimum point P5.
  • a manual fluctuation wave is estimated by interpolation processing for the specific component portion from the waveforms before and after that, that is, pressure fluctuation components (manual pressurization components) 83 and 84.
  • a point P6 where a straight line passing through and intersects is obtained.
  • the interpolation curve 85 is calculated by regarding this point P6 as the minimum point of the manual fluctuation wave.
  • the derivation processing unit 106 calculates the pulse wave component by subtracting the interpolated waveform from the waveform of the specific component (step S10). Specifically, referring again to FIG. 13, pulse wave component 88 is extracted by subtracting interpolation curve 85 from specific component 82.
  • the derivation processing unit 106 regards the calculated pulse wave component as a pulse wave waveform for one beat. Then, a systolic blood pressure estimation process is executed based on the calculated amplitude of the pulse wave component by a conventional method (step S12). Specifically, for example, the maximum blood pressure can be estimated based on the change in the amplitude of the pulse wave using the technique disclosed in Japanese Patent Laid-Open No. 4-261638 (Patent Document 1). When a pulse wave is detected for only one beat, for example, the maximum blood pressure can be estimated using the pressure value at the time of detection + a predetermined value as the maximum blood pressure.
  • step S14 When the estimation of the maximum blood pressure is not completed, the process returns to step S2 and the above process is repeated.
  • the process proceeds to step S14.
  • step S14 the derivation processing unit 106 determines a value obtained by adding a predetermined value ⁇ (for example, 40 mmHg) to the estimated systolic blood pressure value as the pressurization target value.
  • the display control unit 112 displays the determined pressurization target value in a predetermined display area of the display unit 40. As described above, since the current pressure value is displayed in another display area of the display unit 40, the pressurization target value and the current pressure value are displayed in association with each other. Thereby, the user can grasp
  • the display of the pressurization target value is executed until pressurization is stopped (NO in step S16).
  • the pressurization is stopped (YES in step S16)
  • the depressurization is started (step S18).
  • the blood pressure calculation unit 110 calculates the maximum blood pressure and the minimum blood pressure (step S20).
  • the calculated maximum blood pressure and minimum blood pressure are displayed on the display unit 116 as measurement results and stored in the memory unit 39 (step S22).
  • the systolic blood pressure can be estimated even during manual pressurization. Therefore, a value equivalent to the pressure value at the end of pressurization in the automatic pressurization method (estimated systolic blood pressure value + ⁇ ) can be displayed as the pressurization target value.
  • estimate systolic blood pressure value + ⁇ a value equivalent to the pressure value at the end of pressurization in the automatic pressurization method
  • FIG. 14 is a diagram showing a display example of insufficient compression and a target pressure value in the embodiment of the present invention.
  • the display control unit 112 displays a screen such as the screen SC10 of FIG. 14 (step S4).
  • a current pressure value 401 and a predetermined mark 402 indicating insufficient compression are displayed. This guides the user to increase the stroke of the compression operation.
  • the predetermined mark 402 is used to notify the lack of compression, but a message may be used.
  • the level of insufficient compression may be displayed according to the difference between the manual amplitude and the threshold value Vb.
  • the display control unit 112 displays a screen such as a screen SC12 in FIG. On the screen SC12, the current pressure value 401 and the pressurization target value 403 are displayed in comparison.
  • the current pressure value 401 and the pressurization target value 403 are displayed in comparison (association). However, if it is known how much pressurization should be performed, such an example is shown. It is not limited. For example, when the pressurization target value is 100%, the level may be displayed so that the current pressure value can be understood.
  • the pressurization target value is notified by display, but it is not limited.
  • a voice output unit (not shown) may be notified by voice.
  • the user is notified to pressurize to the target pressure value.
  • notification display, warning sound, sound, light, etc.
  • the maximum blood pressure is estimated, and a value obtained by adding a predetermined value to the maximum blood pressure is reported as the final pressurization target value.
  • FIG. 15 is a flowchart showing the flow of blood pressure measurement processing in a modification of the embodiment of the present invention. The same steps as those in the flowchart of FIG. 12 are given the same step numbers. Therefore, description thereof will not be repeated.
  • step S14A is executed without performing steps S8 and S10.
  • step S14A the derivation processing unit 106A determines a value obtained by adding a predetermined value ⁇ (for example, 40 mmHg) to the pressure value at that time as the pressurization target value.
  • the display control unit 112 displays the determined pressurization target value in a predetermined display area of the display unit 40.
  • the display example here may also be the same as the screen SC12 of FIG.
  • the “pressure value at that time” is the pressure value at the time when the specific component is detected.
  • the pressure value displayed as the current pressure value at the time when the specific component is detected that is, the pressure value
  • Current pressure value detected by the value detector 108 may be a value within the pressure range of the specific component such as a maximum value or an average value of the detected specific component.
  • step S16 it is determined whether or not pressurization has been stopped. If pressurization has not been stopped (NO in step S16), the process returns to step S2 and the above process is repeated. Thereby, whenever a specific component is detected in step S6, the pressurization target value is updated and displayed.
  • step S16 When the pressurization is stopped (YES in step S16), the same processing (steps S18, S20, S22) as in the above embodiment is executed.
  • the pressurization target value is updated, but the user only needs to continue pressurization until the current pressure value becomes the pressurization target value. In the pressurizing operation, it is possible to pressurize until finally reaching an appropriate value.
  • Blood pressure monitor 10 body part, 20 cuff, 21 air bag, 24, 24A, 24B air tube, 30 rubber ball, 31 exhaust port, 32 pressure sensor, 35 oscillation circuit, 39 memory part, 40 display part, 41 operation part , 42 power supply unit, 43 timing unit, 44 buzzer, 100 CPU, 102 determination unit, 104 specific component detection unit, 106, 106A derivation processing unit, 108 pressure value detection unit, 110 blood pressure calculation unit, 112 display control unit, 116 display Department.

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  • Health & Medical Sciences (AREA)
  • Life Sciences & Earth Sciences (AREA)
  • Vascular Medicine (AREA)
  • Cardiology (AREA)
  • Biomedical Technology (AREA)
  • Heart & Thoracic Surgery (AREA)
  • Physiology (AREA)
  • Biophysics (AREA)
  • Pathology (AREA)
  • Engineering & Computer Science (AREA)
  • Ophthalmology & Optometry (AREA)
  • Physics & Mathematics (AREA)
  • Medical Informatics (AREA)
  • Molecular Biology (AREA)
  • Surgery (AREA)
  • Animal Behavior & Ethology (AREA)
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  • Measuring Pulse, Heart Rate, Blood Pressure Or Blood Flow (AREA)
PCT/JP2009/069190 2008-11-20 2009-11-11 電子血圧計 WO2010058724A1 (ja)

Priority Applications (6)

Application Number Priority Date Filing Date Title
RU2011124909/14A RU2519751C2 (ru) 2008-11-20 2009-11-11 Электронный сфигмоманометр
US13/128,437 US8747326B2 (en) 2008-11-20 2009-11-11 Electronic sphygmomanometer
MX2011004913A MX2011004913A (es) 2008-11-20 2009-11-11 Esfigmomanometro electronico.
CN2009801466010A CN102223836B (zh) 2008-11-20 2009-11-11 电子血压计
BRPI0922002A BRPI0922002B8 (pt) 2008-11-20 2009-11-11 esfigmomanômetro eletrônico de pressurização manual
DE112009003636.8T DE112009003636B4 (de) 2008-11-20 2009-11-11 Elektronisches Blutdruckmessgerät

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JP2008-296509 2008-11-20
JP2008296509A JP5309921B2 (ja) 2008-11-20 2008-11-20 電子血圧計

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CN107049290B (zh) * 2017-04-17 2020-05-29 北京大学 一种动态血压测量方法和系统
US11690520B2 (en) * 2018-06-20 2023-07-04 Samsung Electronics Co., Ltd. Apparatus and method for measuring bio-information
CN110876614B (zh) * 2018-12-26 2022-09-02 中山乐心电子有限公司 电子血压计
CN112206142A (zh) * 2020-10-22 2021-01-12 中山大学附属第一医院 一种体外反搏加压系统
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JP2010119640A (ja) 2010-06-03
BRPI0922002B8 (pt) 2021-06-22
CN102223836A (zh) 2011-10-19
CN102223836B (zh) 2013-10-30
BRPI0922002A2 (pt) 2015-12-15
JP5309921B2 (ja) 2013-10-09
RU2519751C2 (ru) 2014-06-20
BRPI0922002B1 (pt) 2020-03-10
DE112009003636T5 (de) 2012-05-24
DE112009003636B4 (de) 2024-05-08
US8747326B2 (en) 2014-06-10
US20110218447A1 (en) 2011-09-08
MX2011004913A (es) 2011-05-30

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