WO2011096139A1 - 血圧情報測定装置および血圧情報測定装置の制御方法 - Google Patents
血圧情報測定装置および血圧情報測定装置の制御方法 Download PDFInfo
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- WO2011096139A1 WO2011096139A1 PCT/JP2010/072771 JP2010072771W WO2011096139A1 WO 2011096139 A1 WO2011096139 A1 WO 2011096139A1 JP 2010072771 W JP2010072771 W JP 2010072771W WO 2011096139 A1 WO2011096139 A1 WO 2011096139A1
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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
- 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
- A61B5/02108—Measuring pressure in heart or blood vessels from analysis of pulse wave characteristics
- A61B5/02125—Measuring pressure in heart or blood vessels from analysis of pulse wave characteristics of pulse wave propagation time
-
- 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
- A61B5/02141—Details of apparatus construction, e.g. pump units or housings therefor, cuff pressurising systems, arrangements of fluid conduits or circuits
-
- 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
- A61B5/02233—Occluders specially adapted therefor
-
- 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
- A61B5/0235—Valves specially adapted therefor
Definitions
- the present invention relates to a blood pressure information measuring device and a control method for the blood pressure information measuring device, and more particularly to a blood pressure information measuring device using a cuff and a control method for the blood pressure information measuring device.
- Patent Document 1 As disclosed in Japanese Patent Application Laid-Open No. 2004-113593 (hereinafter referred to as Patent Document 1), an ejection wave ejected from the heart is measured by measuring a pulse wave on the heart side while exciting the peripheral side.
- an arteriosclerosis index is calculated and determined based on an amplitude difference, an amplitude ratio, an appearance time difference, and the like by separating a reflected wave from a iliac bifurcation and a sclerosing site in an artery.
- Patent Document 2 Japanese Patent Application Laid-Open No. 2004-195071
- Patent Document 3 Japanese Patent Application Laid-Open No. 2003-204945
- Patent Document 5 Japanese Translation of PCT International Publication No. 2007-522857
- the measurement site of the measurement subject is compressed from above the skin with an air bag called a cuff, thereby compressing the artery of the measurement site.
- the artery is compressed by pressing the cuff with a constant pressing force against the measurement site of the measurement subject.
- the measurement subject's maximum blood pressure value +35 mmHg is shown as the constant pressing force.
- the rate at which cuff pressure is transmitted to the artery varies depending on the physical characteristics of the subject such as muscle mass, fat mass, and arterial depth. Therefore, even if the cuff is pressed against the measurement site of the subject with a constant pressing force, the ratio of the cuff pressure transmitted to the artery may be lower than expected depending on the physical characteristics of the subject. There is also. In this case, there is a problem that the pressure is insufficient and the pulse wave cannot be measured accurately.
- the rate at which cuff pressure is transmitted to the artery may be higher than expected. In this case, there is a problem that the measurement time becomes long and the burden on the person to be measured becomes large.
- the present invention has been made in view of such a problem, and an object of the present invention is to provide a blood pressure information measuring device and a blood pressure information measuring device control method capable of measuring blood pressure information with high accuracy. .
- a blood pressure information measuring device is a blood pressure information measuring device for measuring blood pressure information of a person to be measured, comprising a first fluid bag, a second fluid bag, Two states of a fluid bag, a first fluid bag and a second fluid bag, in which the internal fluid is connected so as to be able to go back and forth, and a non-connected state where these connected states are canceled so that the fluid cannot go back and forth
- a connection part for switching the pressure an adjustment part for adjusting the internal pressure of the first fluid bag and the second fluid bag, and a pressure sensor for measuring the internal pressure of the first fluid bag and the second fluid bag
- a calculation unit for calculating blood pressure information based on changes in internal pressure of the first fluid bag and the second fluid bag attached to the measurement site.
- the computing unit is configured such that the first fluid bag and the second fluid bag are connected in a state where the first fluid bag is attached to the central side of the measurement site and the second fluid bag is attached to the distal side of the measurement site.
- the calculation unit includes at least one fluid bag in a process of being pressurized while the first fluid bag is attached to the central side of the measurement site and the second fluid bag is attached to the distal side of the measurement site. Based on the change in internal pressure, the calculation part further executes an operation for calculating an index to be used in the operation for determining the blood transduction state, and the operation unit detects the convergence of the index in the process of being pressurized, thereby measuring the measurement site Determine that peripheral blood transfusion is complete.
- the index is a pulse wave amplitude, an AI (Augmentation Index) value that is a ratio between the amplitude of the ejection wave and the amplitude of the reflection wave, and TR (Time of Reflection) value.
- AI Application Index
- TR Time of Reflection
- the control method of the blood pressure information measuring device is a control method of the blood pressure information measuring device for measuring the blood pressure information of the measurement subject using the blood pressure information measuring device.
- the blood pressure information measuring device is connected to the first fluid bag, the second fluid bag, the first fluid bag, and the second fluid bag so that the internal fluid is connected so as to be able to go back and forth, and cannot go back and forth. And a connecting portion for switching between two states of the unconnected state in which these connected states are eliminated.
- the control method of the blood pressure information measuring apparatus is such that the first fluid bag and the second fluid bag are attached in a state where the first fluid bag is attached to the central side of the measurement site and the second fluid bag is attached to the distal side of the measurement site.
- control method of the blood pressure information measuring device further includes a step of calculating an index to be used in the step of determining a blood-feeding state based on a change in the internal pressure of the at least one fluid bag in the pressurizing step.
- step of determining the blood transfusion state it is determined that the peripheral blood transfusion on the measurement site has been completed by detecting that the index has converged in the pressurizing step.
- the index is a pulse wave amplitude, an AI (Augmentation Index) value that is a ratio between the amplitude of the ejection wave and the amplitude of the reflection wave, and TR (Time of Reflection) value.
- AI Application Index
- TR Time of Reflection
- the cuff is pressed against the measurement site with the optimum pressing force regardless of the physical characteristics of the subject. Therefore, blood pressure information can be accurately measured.
- a blood pressure information measuring device (hereinafter abbreviated as a measuring device) 1 according to an embodiment is connected to a base 2 and a base band 2 and is attached to an upper arm that is a measurement site. 9 and these are connected by an air tube 8.
- a display unit 4 for displaying various information including measurement results and an operation unit 3 operated to give various instructions to the measuring device 1 are arranged on the front surface of the base 2.
- the operation unit 3 includes a switch 31 that is operated to turn on / off the power source and a switch 32 that is operated to instruct the start of measurement.
- the arm band 9 is wound around the upper arm 100 which is a measurement site. Measurement is started when the switch 32 is pressed in this state.
- Blood pressure information includes blood pressure value, pulse wave waveform, heart rate, etc., and maximum blood pressure value, minimum blood pressure value, pulse rate, pulse wave amplitude, AI (Augmentation Index) value calculated from them, TR (Time of Reflection) value etc. are included.
- armband 9 includes air bag 13A and air bag 13B.
- the air bag 13A covers the entire measurement site, and the air bag 13B is on the central side and is located between the air bag 13A and the upper arm 100.
- a vibration isolating member for suppressing conduction of vibration between these air bags such as a urethane sheet, is provided between the air bags 13A and 13B.
- air bag 13A and air bag 13B have substantially the same length in the longitudinal direction of arm band 9 and have at least a circumferential length of upper arm 100 or more.
- the ratio of the length in the width direction of the armband 9 between the air bag 13A and the air bag 13B is about 5: 1.
- the size of the air bag 13A is the same as that of a normal blood pressure measuring air bag, and the size of the air bag 13B is 20 mm ⁇ 220 mm.
- pressure sensor 23A, pump 21 and exhaust valve 22 connected to air bag 13A by air tube 8 are connected to base body 2 of measuring apparatus 1, and air tube 8 is connected to air bag 13B.
- the pressure sensor 23A, the pump 21, the exhaust valve 22, and the pressure sensor 23B are connected by an air tube 8 with a two-port valve 51 interposed therebetween.
- the 2-port valve 51 is connected to the drive circuit 53.
- the pressure sensors 23A and 23B are connected to amplifiers 28A and 28B, and the amplifiers 28A and 28B are connected to A / D converters 29A and 29B.
- the pump 21 is connected to the drive circuit 26, and the exhaust valve 22 is connected to the drive circuit 27.
- the driving circuit 26, the driving circuit 27, the A / D converters 29A and 29B, and the driving circuit 53 are connected to a CPU (Central Processing Unit) 40 for controlling the entire measuring apparatus 1. Further, the display unit 4, the operation unit 3, and the memory 5 are connected to the CPU 40.
- a CPU Central Processing Unit
- the memory 5 stores a control program executed by the CPU 40 and the like. Furthermore, the memory 5 also serves as a work area when the CPU 40 executes the program.
- the CPU 40 executes a predetermined program stored in the memory 5 based on the operation signal input from the operation unit 3, and outputs a control signal to the drive circuit 26, the drive circuit 27, and the drive circuit 53.
- the drive circuit 26, the drive circuit 27, and the drive circuit 53 drive the pump 21, the exhaust valve 22, and the 2-port valve 51 according to the control signals, respectively.
- the driving of the pump 21 is controlled by a driving circuit 26 according to a control signal from the CPU 40, and air is injected into the air bag 13A and / or the air bag 13B.
- the opening and closing of the exhaust valve 22 is controlled by a drive circuit 27 according to a control signal from the CPU 40, and the air in the air bag 13A and / or the air bag 13B is discharged.
- the two-port valve 51 is connected to the air bag 13A with the pressure sensor 23A, the pump 21, and the exhaust valve 22 in between, and the side connected to the air bag 13B with the pressure sensor 23B in between. And the opening and closing of each valve is controlled by a drive circuit 53 in accordance with a control signal from the CPU 40.
- a drive circuit 53 in accordance with a control signal from the CPU 40.
- the pressure sensors 23A and 23B are capacitance type pressure sensors, and their capacitance values change due to changes in the internal pressure of the air bags 13A and 13B. Oscillation frequency signals corresponding to the capacitance values of the pressure sensors 23A and 23B are amplified to a predetermined frequency by the amplifiers 28A and 28B, converted into digital signals by the A / D converters 29A and 29B, and then input to the CPU 40.
- the CPU 40 executes a predetermined process based on the change in the internal pressure of the air bladders 13A and 13B obtained from the pressure sensors 23A and 23B, and controls the control signal to the drive circuit 26, the drive circuit 27, and the drive circuit 53 according to the result. Is output. Further, the CPU 40 calculates blood pressure information such as a blood pressure value and a pulse based on changes in the internal pressure of the air bags 13A and 13B obtained from the pressure sensor 23, and performs a process for displaying the measurement result on the display unit 4. Data for display and control signals are output to the display unit 4. Further, the CPU 40 performs a process for storing blood pressure information in the memory 5.
- the measuring device 1 extracts the vibration component accompanying the arterial volume change superimposed on the internal pressure change of the air bag 13B while driving the distal side with the air bag 13A while the arm band 9 is wound around the measurement site. Detect pulse waves. As a result, the ejection wave from the heart and the reflected wave from the iliac bifurcation and the sclerosing site in the artery are separated. The amplitude difference, the amplitude ratio, and the appearance time difference of each wave serve as an index for determining arteriosclerosis. Therefore, the measuring device 1 calculates an AI value or a TR value represented by an amplitude ratio between the ejection wave and the reflected wave as an arteriosclerosis index.
- the shape of the pulse wave to be measured changes as shown in FIGS. 4A to 4C depending on the degree of peripheral blood feeding. That is, when the distal side pressing force is low, the reflected wave from the periphery is superimposed on the pulse wave as shown in FIG. 4A. Therefore, AI1 which is the amplitude ratio (AI value) of the ejected wave and the reflected wave at this time is increased, and TR1 which is an appearance time difference (TR value) between the ejected wave and the reflected wave is decreased.
- AI1 which is the amplitude ratio (AI value) of the ejected wave and the reflected wave at this time
- TR1 which is an appearance time difference (TR value) between the ejected wave and the reflected wave
- the inventors detect the pulse wave by changing the pressure of the air bladders 13A and 13B using the measuring device 1 to calculate the changes in the pulse wave amplitude, the AI value, and the TR value, respectively.
- the result shown in FIG. 5A as a change in pulse wave amplitude according to the change
- the result shown in FIG. 5B as a change in AI value according to the change in the internal pressure of the air bag
- the change in TR value according to the change in the internal pressure of the air bag
- the pulse wave amplitude, the AI value, and the TR value change with the change in the internal pressure of the air bag until the blood pumping state is reached, when the blood pumping state is reached, the internal pressure of the air bag is further increased from the internal pressure P at that time. It is verified that these values converge to a substantially constant value even when increases. This is because the component of the reflected wave does not change even if the internal pressure of the air bag further increases in the blood-feeding state. From this result, it was verified that the peripheral blood-feeding state can be determined using the convergence of the pulse wave amplitude, AI value, or TR value.
- the CPU 40 of the measurement apparatus 1 has a pulse wave detection unit 41, a configuration for determining the peripheral blood pumping state using convergence of the pulse wave amplitude, AI value, or TR value, A calculation unit 42 and a determination unit 43 are included. These are functions mainly formed in the CPU 40 when the CPU 40 reads and executes the control program stored in the memory 5 in accordance with an operation signal from the operation unit 3, but at least some of these functions are included. It may be formed by the hardware configuration shown in FIG.
- FIG. 6 shows changes in the internal pressure P1 of the air bladder 13A and the internal pressure P2 of the air bladder 13B accompanying the measurement operation.
- CPU 40 initializes each part in step S1, and then outputs a control signal to drive circuit 26 in step S3 to operate pump 21 and compress air bag.
- the air bag 13A is pressurized.
- the CPU 40 outputs a control signal to the drive circuit 53 to open both valves of the 2-port valve 51.
- both the internal pressure P1 of the air bladder 13A and the internal pressure P2 of the air bladder 13B increase.
- step S5 the CPU 40 extracts a vibration component accompanying a change in the volume of the artery superimposed on the internal pressure of the air bladder 13A, and calculates a blood pressure value by a predetermined calculation.
- the blood pressure value calculation method here may be a calculation method based on an oscillometric method employed in a normal electronic blood pressure monitor.
- step S7 the CPU 40 performs processing for determining the peripheral blood-feeding state.
- step S101 the pulse wave detection unit 41 detects the pulse wave from the vibration component accompanying the volume change of the artery superimposed on the internal pressure of the air bladder 13A, and in step S103.
- the calculation unit 42 an index value to be used for determination of a blood-feeding state is calculated from a pulse wave for each beat.
- one of a pulse wave amplitude, an AI value, and a TR value is calculated as an index value.
- the calculated index value is temporarily stored.
- the CPU 40 determines in the determination unit 43 whether or not the index value calculated in step S103 has converged.
- the index value calculated in step S103 is compared with the index value previously calculated and temporarily stored, and the difference is stored in advance as a threshold value (for example, For example, a method of determining that the signal has converged when the average value is less than 10% of the average value of two beats.
- step S107 the CPU 40 returns a result that the peripheral side blood transfusion has been completed. If not (NO in step S105), a result indicating that peripheral blood feeding is incomplete is returned.
- any one of the pulse wave amplitude, AI value, and TR value is used for the determination.
- two or more of these indicators are used, and even one indicator converges. If not, it may be determined that the tourniquet has not been completed, and it may be determined that the tourniquet has been completed when it is determined that all the indices have converged. By using a plurality of indices, the accuracy of determination can be further increased.
- the index value for use in the determination is calculated based on the internal pressure of the air bladder 13A in the determination in step S7.
- the internal pressures of the air bags 13A and 13B may be used. This is because, as described above, in the pressurization process, both the air bags 13A and 13B are pressurized together to open both valves of the two-port valve 51 and operate the pump 21, and both internal pressures are equal. is there.
- a mechanism such as the internal pressure sensor 23B for measuring the internal pressure of the air bag 13B can be eliminated. .
- step S7 When the peripheral side blood transfusion is not completed in the determination in step S7 (NO in step S9), the CPU 40 repeats the pressurization of the air bag 13A in step S3 and the determination in step S7. As a result, as shown in FIG. 8, both the internal pressure P1 of the air bladder 13A and the internal pressure P2 of the air bladder 13B are increased until the peripheral blood feeding is completed.
- step S11 the CPU 40 outputs a control signal to the drive circuit 28 to stop pressurization, and the air bag 13A.
- the internal pressure of is fixed.
- step S13 the CPU 40 outputs a control signal to the drive circuit 53 to close both valves of the 2-port valve 51.
- the air bag 13A and the air bag 13B are separated from each other, and the air bag 13A maintains the internal pressure at which it is determined that the peripheral side blood pumping has been completed and compresses the measurement site.
- a peripheral blood-feeding state is maintained with respect to the air bag 13B used. That is, the air bag 13A functions as a pressure air bag.
- the central part is in contact with the measurement site most, and the pressing force by the air bag 13A is highest in the central part.
- the pressing force at the central portion of the air bag 13A becomes higher than the maximum blood pressure, and the artery located just below it is crushed.
- the pressing force from the air bag 13A gradually weakens at a position away from just below the center of the air bag 13A, the artery is not completely crushed as shown in FIG.
- the air bag 13B is located more centrally than the central portion of the air bag 13A when the armband 9 is attached to the upper arm 100, and the artery is located at that position as described above. It is not completely crushed. 2B, since the volume of the air bag 13B is smaller than the volume of the air bag 13A, the air bag 13B has higher sensitivity superimposed on the internal pressure of the arterial volume change. Therefore, as shown in FIG. 8, after the peripheral side blood pumping is completed and the two-port valve 51 is closed in step S13, the internal pressure P1 of the air bag 13A is not superposed on the internal pressure P1, and the pulse wave is not superimposed. Although a high internal pressure is maintained (FIG.
- step S15 an output waveform is measured from the vibration component of the internal pressure of the air bag 13B on which the pulse wave shown in FIG. 8 is superimposed ((B) of FIG. 8), and the pulse wave is detected.
- step S17 the CPU 40 outputs a control signal to the drive circuit 53 to open the 2-port valve 51, and further outputs a control signal to the drive circuit 27 to open the exhaust valve 22, thereby quickly opening the air bags 13A and 13B. Exhaust. Thereby, as shown in FIG. 8, the internal pressures P1, P2 of the air bags 13A, 13B rapidly return to the atmospheric pressure after step S17.
- step S19 the CPU 40 analyzes the pulse wave detected in step S15, and calculates an AI value, a TR value, and the like serving as an index of arteriosclerosis.
- step S21 the CPU 40 executes a process for causing the display unit 4 to display the blood pressure value measured in step S5, the index calculated in step S19, and the like as a measurement result, and ends a series of measurement operations.
- Transmission efficiency internal pressure when the peripheral pulse wave disappears / maximum blood pressure measured by an air bag attached to the upper arm.
- the transmission efficiency is 1
- the transmission efficiency is 1
- the transmission efficiency is affected by physical characteristics such as the muscle mass, fat mass, and arterial depth of the measurement subject.
- the internal pressure of the air bag when the peripheral pulse wave disappears is, for example, pressed with the air bag attached to the upper arm with the photoelectric pulse wave sensor attached to the fingertip, and the pulse wave amplitude disappears. Or, it is measured as an internal pressure when it falls below a predetermined threshold value (for example, 10% before pressing, etc.).
- the above-mentioned physical strength of the person to be measured is determined.
- the transmission efficiency may be lower than expected, resulting in insufficient pressing force.
- the transmission efficiency may be higher than expected, and the pressing force becomes excessive.
- the peripheral blood-feeding state is determined based on the convergence of an index value such as a pulse wave amplitude, an AI value, or a TR value, the measurement subject's muscle mass, fat mass, Without being affected by physical characteristics such as arterial depth, it is possible to achieve a blood-feeding state with an appropriate pressing force.
- the feature point of the ejection wave and the feature point of the reflected wave can be accurately detected without being affected by the physical characteristics of the measurement subject, that is, even for the measurement subjects having different transmission efficiencies.
- the degree of arteriosclerosis can be accurately determined.
- the burden on the measurement subject can be reduced.
- 1 measuring device 2 substrate, 3 operation unit, 4 display unit, 5 memory, 8 air tube, 9 armband, 13A, 13B air bag, 21 pump, 22 exhaust valve, 23A, 23B pressure sensor, 26, 27, 53 Drive circuit, 28A, 28B amplifier, 29A, 29B A / D converter, 31, 32 switch, 40 CPU, 41 pulse wave detection unit, 42 calculation unit, 43 determination unit, 51 2-port valve, 100 upper arm.
Abstract
Description
伝達効率=末梢側の脈波が消失するときの内圧/上腕に装着された空気袋により測定される最高血圧。
Claims (6)
- 被測定者の血圧情報を測定するための血圧情報測定装置であって、
第1の流体袋と、
第2の流体袋と、
前記第1の流体袋と前記第2の流体袋とを内部の流体が行き来可能に連結された連結状態、および行き来不可能にこれらの連結状態が解消された非連結状態の2つ状態を切替えるための連結部と、
前記第1の流体袋および前記第2の流体袋の内圧を調整するための調整部と、
前記第1の流体袋および前記第2の流体袋の内圧を測定するための圧力センサと、
測定部位に装着された前記第1の流体袋および前記第2の流体袋のそれぞれの内圧変化に基づいて血圧情報を算出するための演算部とを備え、
前記演算部は、
前記第1の流体袋が前記測定部位の中枢側、前記第2の流体袋が前記測定部位の末梢側に装着された状態で、前記第1の流体袋と前記第2の流体袋とが連結されて加圧される過程での、前記第1の流体袋および前記第2の流体袋のうちの少なくとも一方の流体袋の内圧変化に基づいて前記測定部位の末梢側の駆血状態を判定する演算と、
前記第1の流体袋が前記測定部位の中枢側、前記第2の流体袋が前記測定部位の末梢側に装着された状態で、前記測定部位の末梢側が駆血状態であると判定された後に前記第1の流体袋と前記第2の流体袋との連結が解消され、前記調整部が前記第2の流体袋の内圧を前記駆血状態であると判定された内圧に維持しているときの前記第1の流体袋の内圧変化に基づいて、前記血圧情報としての、動脈硬化を判定するための指標を算出する演算とを実行する、血圧情報測定装置。 - 前記演算部は、前記第1の流体袋が前記測定部位の中枢側、前記第2の流体袋が前記測定部位の末梢側に装着された状態で、前記加圧される過程での前記少なくとも一方の流体袋の内圧変化に基づいて、前記駆血状態を判定する演算において用いるための指標を算出する演算をさらに実行し、
前記演算部は、前記加圧される過程において前記指標が収束したことを検出することにより前記測定部位の末梢側の駆血が完了したことを判定する、請求項1に記載の血圧情報測定装置。 - 前記指標は、脈波振幅、駆出波の振幅と反射波の振幅との比率であるAI(Augmentation Index)値、および駆出波と反射波との出現時間差であるTR(Time of Reflection)値のうちの少なくとも1つである、請求項2に記載の血圧情報測定装置。
- 血圧情報測定装置を用いて被測定者の血圧情報を測定するための前記血圧情報測定装置の制御方法であって、
前記血圧情報測定装置は、
第1の流体袋と、
第2の流体袋と、
前記第1の流体袋と前記第2の流体袋とを内部の流体が行き来可能に連結された連結状態、および行き来不可能にこれらの連結状態が解消された非連結状態の2つ状態を切替えるための連結部とを含み、
前記第1の流体袋が前記測定部位の中枢側、前記第2の流体袋が前記測定部位の末梢側に装着された状態で、前記第1の流体袋と前記第2の流体袋とを連結して加圧するステップと、
前記加圧するステップでの前記第1の流体袋および前記第2の流体袋のうちの少なくとも一方の流体袋の内圧変化に基づいて、前記測定部位の末梢側の駆血状態を判定するステップと、
前記駆血状態を判定するステップにおいて前記測定部位の末梢側が駆血状態であると判定された後に前記第1の流体袋と前記第2の流体袋との連結を解消し、前記第2の流体袋の内圧を前記駆血状態であると判定された内圧に維持するステップと、
前記維持するステップでの前記第1の流体袋の内圧変化に基づいて、前記血圧情報としての、動脈硬化を判定するための指標を算出するステップとを備える、血圧情報測定装置の制御方法。 - 前記加圧するステップでの前記少なくとも一方の流体袋の内圧変化に基づいて、前記駆血状態を判定するステップにおいて用いるための指標を算出するステップをさらに備え、
前記駆血状態を判定するステップでは、前記加圧するステップにおいて前記指標が収束したことを検出することにより前記測定部位の末梢側の駆血が完了したことを判定する、請求項4に記載の血圧情報測定装置の制御方法。 - 前記指標は、脈波振幅、駆出波の振幅と反射波の振幅との比率であるAI(Augmentation Index)値、および駆出波と反射波との出現時間差であるTR(Time of Reflection)値のうちの少なくとも1つである、請求項5に記載の血圧情報測定装置の制御方法。
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