CN103584849B - A kind of blood pressure measuring device and pulse signal detection method - Google Patents
A kind of blood pressure measuring device and pulse signal detection method Download PDFInfo
- Publication number
- CN103584849B CN103584849B CN201310543620.5A CN201310543620A CN103584849B CN 103584849 B CN103584849 B CN 103584849B CN 201310543620 A CN201310543620 A CN 201310543620A CN 103584849 B CN103584849 B CN 103584849B
- Authority
- CN
- China
- Prior art keywords
- air bag
- pulse signal
- pressure
- downstream
- upstream
- Prior art date
- Legal status (The legal status 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 status listed.)
- Expired - Fee Related
Links
- 230000036772 blood pressure Effects 0.000 title claims abstract description 45
- 238000001514 detection method Methods 0.000 title claims description 14
- 238000011144 upstream manufacturing Methods 0.000 claims abstract description 325
- 238000000034 method Methods 0.000 claims abstract description 139
- 230000004873 systolic arterial blood pressure Effects 0.000 claims description 57
- 230000000740 bleeding effect Effects 0.000 claims description 44
- 230000011218 segmentation Effects 0.000 claims description 32
- 238000011897 real-time detection Methods 0.000 claims description 26
- 230000035487 diastolic blood pressure Effects 0.000 claims description 25
- 230000035488 systolic blood pressure Effects 0.000 claims description 17
- 230000007423 decrease Effects 0.000 claims description 16
- 230000003467 diminishing effect Effects 0.000 claims description 10
- 238000012544 monitoring process Methods 0.000 claims description 10
- 239000008280 blood Substances 0.000 claims description 9
- 210000004369 blood Anatomy 0.000 claims description 9
- 238000009530 blood pressure measurement Methods 0.000 claims description 6
- 230000035485 pulse pressure Effects 0.000 claims 2
- 230000017531 blood circulation Effects 0.000 abstract description 17
- 210000001367 artery Anatomy 0.000 abstract description 12
- 238000005259 measurement Methods 0.000 abstract description 8
- 210000003414 extremity Anatomy 0.000 description 26
- 102100033254 Tumor suppressor ARF Human genes 0.000 description 18
- 210000003437 trachea Anatomy 0.000 description 15
- 239000002775 capsule Substances 0.000 description 13
- 230000006837 decompression Effects 0.000 description 9
- 238000010586 diagram Methods 0.000 description 5
- 102220144047 rs7667001 Human genes 0.000 description 3
- 102220059912 rs786201931 Human genes 0.000 description 3
- 230000008321 arterial blood flow Effects 0.000 description 2
- 239000000523 sample Substances 0.000 description 2
- 210000000707 wrist Anatomy 0.000 description 2
- 230000004872 arterial blood pressure Effects 0.000 description 1
- 230000009286 beneficial effect Effects 0.000 description 1
- 230000000903 blocking effect Effects 0.000 description 1
- 230000006835 compression Effects 0.000 description 1
- 238000007906 compression Methods 0.000 description 1
- 230000000694 effects Effects 0.000 description 1
- 210000000245 forearm Anatomy 0.000 description 1
- 210000004247 hand Anatomy 0.000 description 1
- 230000002452 interceptive effect Effects 0.000 description 1
- 239000007788 liquid Substances 0.000 description 1
Landscapes
- Measuring Pulse, Heart Rate, Blood Pressure Or Blood Flow (AREA)
Abstract
The present invention is a kind of blood pressure measuring device, the main frame that blood pressure measuring device comprises oversleeve and is connected with oversleeve, upstream air bag and downstream air bag lay respectively at the upstream and downstream of tested limb artery blood flow, downstream air bag is for detecting the change information of pulse signal, the change of the blood flow pulse that real-time sensing is changed by the pressure of upstream air bag and produces, Microprocessor S3C44B0X air pump, gas bleeder valve and process detect the force value in one or two in upstream air bag and downstream air bag respectively or simultaneously by one or two in the first pressure transducer and the second pressure transducer, pulse signal, or force value and pulse signal.The device of Measure blood pressure provided by the invention is that colligation two inflatable bladders pressurize on limbs, effectively detects pressure wherein and pulse signal, thus accurately, reliably Measure blood pressure, and measurement result is stablized.
Description
Technical field
The invention belongs to technical field of medical instruments, particularly relate to a kind of method detecting arterial blood pulse signal and the blood pressure measuring device using the method, especially a kind of pass through two inflatable bladders a body part blood flow upstream and downstream simultaneously detected pressures and pulse signal method and in this approach based on blood pressure measuring device.
Background technology
One of method that blood pressure measurement is the most frequently used adopts a kind of cuff with an inflatable bladders, first human body limb artery blood flow is blocked by pressurization, then slowly reduce pressure, in decompression process, the Korotkoff's Sound produced during by detecting blood flow by blocking district, or the information such as the strong and weak changing value of the pulse wave signal that produces in cuff of arterial pressure, determine systolic pressure and the diastolic pressure of arterial blood.China Patent No. CN201010247968.6, the patent documentation that title is " a kind of Woundless blood pressure measuring device and measuring method thereof " describes a kind of pulse wave probe that uses and detects cuff downstream arterial pulse signal, thus determines the sphygomanometer of systolic pressure and diastolic pressure.This pulse wave probe detects cuff downstream arterial pulse signal by pressure inductor or photoelectric sensor.China Patent No. is CN201220159276.0, the patent documentation that title is " a kind of double bolloon bandage " describes a kind of binary articulated double bolloon oversleeve, described cuff has upstream air bag bandage body and downstream air bag bandage body, and described upstream air bag bandage body and described downstream air bag bandage body are be fixedly connected with within 30cm according to artery blood flow direction spacing.Described downstream air bag bandage body for detecting tested limbs downstream blood liquid stream moving pulse, and determines the pressure of tested limb artery blood with this.
Prior art not yet solves upstream and downstream air bag bandage and should pressurize by which kind of mode and be pressurized to which kind of degree of pressure, the blood flow pulse that can be used for measuring tested limbs blood pressure could be detected most effectively in upstream and downstream air bag bandage, thus accurately, the problem of reliably Measure blood pressure.
Summary of the invention
In order to solve the problem, the invention provides a kind of accurate, reliable sphygomanometer, a kind of two inflatable bladders to colligation on limbs are particularly provided to carry out pneumatic compression, effectively to detect the method for pulse signal wherein, and use the device of the method Measurement accuracy sphygomanometer.
In order to achieve the above object, the present invention is achieved by the following technical solutions:
A kind of blood pressure measuring device of the present invention, measuring device is used for measuring arteriotony by measured's body part, and measuring device comprises:
Two aerating gasbag upstream air bags and downstream air bag; Upstream air bag and downstream air bag are in same cuff or in two different cufves be connected or in two different cufves be not connected, and cuff is for being bundled in tested limbs;
Two with one or two pressure transducer first pressure transducer be connected respectively or simultaneously in upstream air bag and downstream air bag and the second pressure transducer;
A microprocessor, microprocessor performs the blood pressure measurement comprised the following steps:
A) by downstream gasbag pressurizes to the force value of between tested systolic arterial pressure and diastolic pressure, or the mean blood pressure value of tested tremulous pulse subtracts 10mmHg and average pressure value and adds a force value between 20mmHg, or a force value, makes the pulse signal amplitude detected in the air bag of downstream when this force value be greater than a set-point;
B) upstream air bag is pressurized to a force value higher than tested systolic arterial pressure;
C) upstream air bag is slowly lost heart, in the slow bleeding process of upstream air bag, the air pressure of constantly change in the air bag of upstream is measured by the first pressure transducer, and measure the pulse signal in the air bag of downstream by the second pressure transducer simultaneously, according to the relation between the air pressure in described pulse signal and upstream air bag, determine tested systolic arterial pressure.
Further improvement of the present invention is: in steps A) in, in the process to downstream gasbag pressurizes by a force value between downstream gasbag pressurizes to the systolic pressure and diastolic pressure of tested tremulous pulse and method that downstream gasbag pressurizes is subtracted to the mean blood pressure value of tested tremulous pulse the force value that 10mmHg and average pressure value add between 20mmHg, pulse signal in the air bag of real-time detection downstream, when pulse signal amplitude is increased to maximum by zero, when then starting to decline, stop pressurization; With by downstream gasbag pressurizes to a force value, with the method making the pulse signal amplitude detected in the air bag of downstream when this force value be greater than a set-point be, by in the process to downstream gasbag pressurizes, pulse signal in the air bag of real-time detection downstream entrained by air pressure signal, when pulse signal amplitude by zero be increased to be greater than set-point time, stop pressurization.
In steps A) in, pulse signal amplitude set-point is a value between 1.3mmHg to 1.8mmHg, is preferably 1.5mmHg.
In step B) in, by upstream air bag, the method be pressurized to higher than a force value of tested systolic arterial pressure is, in the process to described upstream gasbag pressurizes, the change of the pulse signal amplitude in the air bag of Real-Time Monitoring downstream, when the pulse signal amplitude in the air bag of described downstream with the increase of the air pressure of described upstream air bag from diminishing greatly, when finally disappearing, stop pressurization.
Further improvement of the present invention is: by downstream gasbag pressurizes to a force value, the method making the pulse signal amplitude detected in the air bag of downstream when this force value be greater than a set-point is, downstream air bag segmentation is pressurizeed, and after each section of pressurization terminates, detect the pulse signal in the air bag of downstream, when pulse signal amplitude is greater than set-point, stop pressurization, to the segmented objects of downstream air bag segmentation pressurization be: 80mmHg, 120mmHg, 160mmHg and 200mmHg.
Further improvement of the present invention is: in step C) in, in the slow bleeding process of upstream air bag, the air pressure of constantly change in the air bag of upstream is measured by the first pressure transducer, and the time of origin of first pulse signal in the air bag of downstream is measured by the second pressure transducer, air pressure when occurring according to described first pulse signal in the air bag of upstream, determines tested systolic arterial pressure.
Further improvement of the present invention is: in step C) in the slow bleeding process of upstream air bag, the air pressure of constantly change in the air bag of upstream is measured by the first pressure transducer, and amplitude and the time of origin of first and second pulse signal in the air bag of downstream is measured by the second pressure transducer, atmospheric pressure value when described first and second pulse signal occur in upstream air bag (1), determines tested arterial blood systolic pressure.
A kind of pulse signal detection method, the method is for detecting air pressure in the cuff be bundled on tested limbs and pulse signal and interrelationship, and pulse signal detection method comprises the following steps:
(1) upstream air bag and downstream air bag are bundled on tested limbs, upstream air bag and downstream air bag are in same cuff or in two different cufves be connected or in two different cufves be not connected, upstream air bag and downstream air bag lay respectively at the upstream and downstream of tested limb artery blood flow;
(2) the first pressure transducer and the second pressure transducer are connected with one or two in upstream air bag and downstream air bag respectively or simultaneously by gas UNICOM parts;
(3) by downstream gasbag pressurizes to the force value of between tested systolic arterial pressure and diastolic pressure, or the mean blood pressure value of tested tremulous pulse subtracts 10mmHg and average pressure value and adds a force value between 20mmHg, or a force value, makes the pulse signal amplitude detected in the air bag of downstream when this force value be greater than a set-point;
(4) upstream air bag is pressurized to a force value higher than tested systolic arterial pressure;
(5) upstream air bag is slowly lost heart, in the slow bleeding process of upstream air bag, the air pressure of constantly change in the air bag of upstream is measured by the first pressure transducer, and measure the pulse signal in the air bag of downstream by the second pressure transducer, thus measure the atmospheric pressure value when pulse signal occurs in the air bag of upstream simultaneously.
Further improvement of the present invention is:
In step (3), by the method for a force value between downstream gasbag pressurizes to the systolic pressure and diastolic pressure of tested tremulous pulse with by the method that downstream gasbag pressurizes subtracts to the mean blood pressure value of tested tremulous pulse the force value that 10mmHg and average pressure value add between 20mmHg be, in the process to downstream gasbag pressurizes, pulse signal in the air bag of real-time detection downstream entrained by air pressure signal, when pulse signal amplitude is increased to maximum by zero, when then starting to decline, stop pressurization, with by downstream gasbag pressurizes to a force value, with the method making the pulse signal amplitude detected in the air bag of downstream when this force value be greater than a set-point be, by in the process to downstream gasbag pressurizes, pulse signal in the air bag of real-time detection downstream entrained by air pressure signal, when pulse signal amplitude by zero be increased to be greater than set-point time, stop pressurization,
In step (4), by upstream air bag, the method be pressurized to higher than a force value of tested systolic arterial pressure is, in the process to upstream gasbag pressurizes, the change of the pulse signal amplitude in the air bag of Real-Time Monitoring downstream, instantly the pulse signal amplitude in faint breath capsule with the increase of the air pressure of upstream air bag from diminishing greatly, when finally disappearing, stop pressurization.
Further improvement of the present invention is: in step (3), and pulse signal amplitude set-point is a value between 1.3mmHg-1.8mmHg, is preferably 1.5mmHg.
By downstream gasbag pressurizes to a force value, the method making the pulse signal amplitude detected in the air bag of downstream when this force value be greater than a set-point is, downstream air bag segmentation is pressurizeed, and after each section of pressurization terminates, detect the pulse signal that in the air bag of downstream, air pressure signal carries, when pulse signal amplitude is greater than set-point, stop pressurization.
Further improvement of the present invention is: to the segmented objects of downstream air bag segmentation pressurization be: 80mmHg, 120mmHg, 160mmHg and 200mmHg.
Further improvement of the present invention is: in the slow bleeding process of upstream air bag, the air pressure of constantly change in the air bag of upstream is measured by the first pressure transducer, and measured the time of origin of first pulse signal in the air bag of downstream by the second pressure transducer, thus measure the air pressure when first pulse signal occurs in the air bag of upstream.
Further improvement of the present invention is: in the slow bleeding process of upstream air bag, the air pressure of constantly change in the air bag of upstream is measured by the first pressure transducer, and measured amplitude and the time of origin of first and second pulse signal in the air bag of described downstream by the second pressure transducer, thus to measure when described first pulse signal occurs and at this moment between previous pulse cycle in air pressure in the air bag of described upstream.
The invention has the beneficial effects as follows: the device of Measure blood pressure provided by the invention is that colligation two inflatable bladders pressurize on limbs, effectively detects pressure wherein and pulse signal, thus accurately, reliably Measure blood pressure, and measurement result is stablized.
Accompanying drawing explanation
Fig. 1 is the plane outspread drawing of the fan-shaped oversleeve of double bolloon of the present invention.
Fig. 2 is the use schematic diagram of the fan-shaped oversleeve of double bolloon of the present invention for hands forearm.
Fig. 3 is blood pressure measuring device connection diagram of the present invention.
Fig. 4 is blood pressure measuring device connection diagram of the present invention.
Fig. 5 is blood pressure measuring device connection diagram of the present invention.
Fig. 6 is that the present invention is reduced pressure measurement method systolic pressure and diastolic pressure pulse signal sequential chart.
Fig. 7 is 6A magnified partial view in Fig. 6 of the present invention.
Wherein: 1-upstream air bag, 2-downstream air bag, 3-first pressure transducer, 4-main frame, 5-second pressure transducer, 6-air pump, 7-gas bleeder valve, 8-oversleeve, 9-upstream trachea, 10-downstream trachea.
Detailed description of the invention
In order to deepen the understanding of the present invention, be described in further detail the present invention below in conjunction with drawings and Examples, this embodiment, only for explaining the present invention, not forming protection scope of the present invention and limiting.
As shown in figs. 1-7, the present invention is a kind of blood pressure measuring device, and described blood pressure measuring device comprises the fan-shaped oversleeve 8 of double bolloon, and the fan-shaped oversleeve of double bolloon also can be two common oversleeves, replaces the effect of upstream air bag 1 and downstream air bag 2 respectively.
Embodiment one, use decompression method measure systolic pressure pulse signal method and measuring device
The present invention is a kind of blood pressure measuring device, the main frame 4 that described blood pressure measuring device comprises oversleeve 8 and is connected with described oversleeve 8, described oversleeve 8 is the fan-shaped oversleeves of double bolloon, the fan-shaped oversleeve of described double bolloon is the cuff be bundled on tested limbs of two gas cells of the two trachea of band and upstream air bag 1 and downstream air bag 2, described upstream air bag 1 and described downstream air bag 2 lay respectively at the upstream and downstream of tested limb artery blood flow, after binding, described upstream air bag 1 is fixed on wrist pulse upstream and blocks measured's elbow arterial blood flow, and be connected with the upstream balloon interface on described main frame 4, described downstream air bag 2 is fixed on the downstream portion detection wrist beat pulse in arterial blood flow direction and is connected with the downstream balloon interface on described main frame 4, described downstream air bag 2 is for detecting the change information of pulse signal, the change of the blood flow pulse that real-time sensing is changed by the pressure of described upstream air bag 1 and produces, the interpersonal interactive interface comprising keyboard and display that described main frame 4 comprises a microprocessor and is connected with described microprocessor, described main frame 4 also comprises air pump 6, gas bleeder valve 7, described main frame 4 also comprises the first pressure transducer 3 and the second pressure transducer 5, described first pressure transducer 3 and the second pressure transducer 5 are connected respectively or simultaneously by one or two of gas UNICOM parts and described upstream air bag 1 and described downstream air bag 2, described air pump 6 is the air pump 6 that at least one is inflated for one or two in described upstream air bag 1 and described downstream air bag 2, described gas bleeder valve 7 is for one or two in described upstream air bag 1 and described downstream air bag 2 at a slow speed or the gas bleeder valve 7 of quick air releasing, air pump 6 described in described Microprocessor S3C44B0X, gas bleeder valve 7 and process detect the force value in one or two in described upstream air bag 1 and described downstream air bag 2 respectively or simultaneously by one or two in the first pressure transducer 3 and the second pressure transducer 5, pulse signal, or force value and pulse signal.
In described microprocessor, be provided with control and data processor, described control and handling procedure perform the blood pressure measurement comprised the following steps:
A) described downstream air bag 2 is pressurized to a force value between tested systolic arterial pressure and diastolic pressure, or the mean blood pressure value of tested tremulous pulse subtracts 10mmHg and average pressure value and adds a force value between 20mmHg, or a force value, makes the pulse signal amplitude detected in described downstream air bag 2 when this force value be greater than a set-point;
B) upstream air bag 1 is pressurized to a force value higher than tested systolic arterial pressure;
C) upstream air bag 1 is slowly lost heart, in upstream air bag 1 slowly bleeding process, the air pressure of constantly change in upstream air bag 1 is measured by the first pressure transducer 3, and the pulse signal measured by the second pressure transducer 5 in downstream air bag 2, according to the relation between the air pressure in described pulse signal and described upstream air bag 1, determine tested systolic arterial pressure.
Scheme one: as shown in Fig. 3 and 6-7, uses decompression method to detect double bolloon pulse signal and systolic pressure, comprises the steps:
1) by a fan-shaped cuff of double bolloon, or the non-fan-shaped cuff of a double bolloon, or two joining cufves, or two not joining cufves are bound on tested limbs, wherein upstream air bag 1 and downstream air bag 2 lay respectively at the upstream and downstream of limb artery blood flow, and are connected with the upstream balloon interface on main frame 4 and downstream balloon interface with downstream trachea 10 respectively by upstream trachea 9 with downstream air bag 2 by upstream air bag 1;
2) press the start key of main frame 4 keyboard, the second gas bleeder valve cuts out, and the downward faint breath capsule 2 of the second air pump is inflated, and the air pressure of downstream air bag 2 slowly increases from zero;
3) this step has 4 kinds of embodiments, respectively as step 3-1), 3-2), 3-3) and 3-4):
3-1) in the process that downstream air bag 2 is pressurizeed, pulse signal in real-time detection downstream air bag 2, when described pulse signal amplitude is increased to maximum, when then starting to decline by zero, stop pressurization, now downstream air bag 2 is pressurized to a force value between tested systolic arterial pressure and diastolic pressure;
3-2) in the process that downstream air bag 2 is pressurizeed, pulse signal in real-time detection downstream air bag 2, when described pulse signal amplitude is increased to maximum by zero, when then starting to decline, stop pressurization, the mean blood pressure value that now downstream air bag 2 is pressurized to tested tremulous pulse subtracts 10mmHg and average pressure value and adds a force value between 20mmHg;
3-3) in the process that downstream air bag 2 is pressurizeed, pulse signal in real-time detection downstream air bag 2, when described pulse signal amplitude by zero be increased to be greater than set-point time, stop pressurization, described pulse signal amplitude set-point is a value between 1.3mmHg to 1.8mmHg, and preferred pulse signal amplitude set-point is 1.5mmHg;
3-4) downstream air bag 2 segmentation is pressurizeed, and after each section of pressurization terminates, detect the pulse signal in downstream air bag 2, when described pulse signal amplitude is greater than set-point, stop pressurization, the described segmented objects to downstream air bag 2 segmentation pressurization is 80mmHg, 120mmHg, 160mmHg, 200mmHg, described pulse signal amplitude set-point is a value between 1.3mmHg to 1.8mmHg, and preferred pulse signal amplitude set-point is 1.5mmHg;
4) the first gas bleeder valve cuts out, and the first air pump upstream air bag 1 is inflated, and upstream air bag 1 pressure increases from zero;
5) this step has 2 kinds of embodiments, respectively as step 5-1) and 5-2):
5-1) in the process that upstream air bag 1 is pressurizeed, the change of the pulse signal amplitude in Real-Time Monitoring downstream air bag 2, instantly the pulse signal amplitude in faint breath capsule 2 with the increase of the air pressure of upstream air bag 1 from diminishing greatly, when finally disappearing, stop pressurization, now upstream air bag 1 is pressurized to a force value higher than tested systolic arterial pressure;
5-2) upstream air bag 1 segmentation is pressurizeed, the described segmented objects to upstream air bag 1 segmentation pressurization is 180mmHg, 240mmHg, 280mmHg, and after each section of pressurization terminates, detect the pulse signal in downstream air bag 2, after described pulse signal disappears, stop pressurization, now upstream air bag 1 is pressurized to a force value higher than tested systolic arterial pressure;
6) the first gas bleeder valve is controlled, upstream air bag 1 is slowly lost heart, in upstream air bag 1 slowly bleeding process, the air pressure of constantly change in upstream air bag 1 is measured by the first pressure transducer 3, and measure the pulse signal in downstream air bag 2 by the second pressure transducer, according to the air pressure in described pulse signal and upstream air bag 1, determine tested systolic arterial pressure, describedly determine that the method for tested systolic arterial pressure has 2 kinds, respectively as step 6-1) and 6-2):
6-1) in upstream air bag 1 slowly bleeding process, the air pressure of constantly change in upstream air bag 1 is measured by the first pressure transducer 3, and the time of origin of first pulse signal in downstream air bag 2 is detected by the second pressure transducer 5, according to the air pressure in the upstream air bag 1 when described first pulse signal occurs, determine tested systolic arterial pressure, such as, measure the generation moment of the peak value of first pulse signal in the downstream air bag 2 detected, with the atmospheric pressure value measured at the generation moment upstream air bag 1 of the peak value of described first pulse signal, the atmospheric pressure value of described upstream air bag 1 is tested systolic arterial pressure, or the atmospheric pressure value measured at the generation moment upstream air bag 1 of the peak value of described first pulse signal, with the meansigma methods of the atmospheric pressure value of upstream air bag 1 in former and later two moment pulse cycles in the generation moment of the peak value at described first pulse signal, described meansigma methods is tested systolic arterial pressure,
6-2) in upstream air bag 1 slowly bleeding process, the air pressure of constantly change in upstream air bag 1 is measured by the first pressure transducer 3, and amplitude and the time of origin of first and second pulse signal in downstream air bag 2 is measured by the second pressure transducer 5, with the atmospheric pressure value in the upstream air bag 1 when first and second pulse signal occur, determine tested arterial blood systolic pressure.Such as, measure the amplitude A 4 of first and second pulse signal and time of origin t4 and t5 of A5 and peak value in the downstream air bag 2 detected, with two atmospheric pressure value P4 and P5 of measurement in the time of origin t4 and t5 upstream air bag 1 of the peak value of described first and second pulse signal, then tested systolic arterial pressure is (P5-(P5-P4) * A5/ (A5-A4)).
8) open the first gas bleeder valve and the second gas bleeder valve, lose heart to upstream air bag 1 and downstream air bag 2.
As in Fig. 6, t0-t4 is shown as this device detects systolic pressure pulse signal sequential chart by decompression method.
Scheme two: as shown in Figure 4, uses decompression method to detect double bolloon pulse signal and systolic pressure, comprises the steps:
1) by a fan-shaped cuff of double bolloon, or the non-fan-shaped cuff of a double bolloon, or two joining cufves, or two not joining cufves are bound on tested limbs, wherein upstream air bag 1 and downstream air bag 2 lay respectively at the upstream and downstream of limb artery blood flow, and are connected with the upstream balloon interface on main frame 4 and downstream balloon interface with downstream trachea 10 respectively by upstream trachea 9 with downstream air bag 2 by upstream air bag 1;
2) press the start key of main frame 4 keyboard, the first gas bleeder valve cuts out, and the first switch valve cuts out, and second switch valve is opened, and the first air pump is inflated to air bag 2, and the air pressure of downstream air bag 2 slowly increases from zero;
3) this step has 4 kinds of embodiments, respectively as step 3-1), 3-2), 3-3) and 3-4):
3-1) in the process that downstream air bag 2 is pressurizeed, pulse signal in real-time detection downstream air bag 2, when described pulse signal amplitude is increased to maximum, when then starting to decline by zero, stop pressurization, now downstream air bag 2 is pressurized to a force value between tested systolic arterial pressure and diastolic pressure;
3-2) in the process that downstream air bag 2 is pressurizeed, pulse signal in real-time detection downstream air bag 2, when described pulse signal amplitude is increased to maximum by zero, when then starting to decline, stop pressurization, the mean blood pressure value that now downstream air bag 2 is pressurized to tested tremulous pulse subtracts 10mmHg and average pressure value and adds a force value between 20mmHg;
3-3) in the process that downstream air bag 2 is pressurizeed, pulse signal in real-time detection downstream air bag 2, when described pulse signal amplitude by zero be increased to be greater than set-point time, stop pressurization, described pulse signal amplitude set-point is a value between 1.3mmHg to 1.8mmHg, and preferred pulse signal amplitude set-point is 1.5mmHg;
3-4) downstream air bag 2 segmentation is pressurizeed, and after each section of pressurization terminates, detect the pulse signal in downstream air bag 2, when described pulse signal amplitude is greater than set-point, stop pressurization, the described segmented objects to downstream air bag 2 segmentation pressurization is 80mmHg, 120mmHg, 160mmHg, 200mmHg, described pulse signal amplitude set-point is a value between 1.3mmHg to 1.8mmHg, and preferred pulse signal amplitude set-point is 1.5mmHg;
4) the first gas bleeder valve cuts out, and second switch valve cuts out, and the first switch valve is opened, and the first air pump upstream air bag 1 is inflated, and upstream air bag 1 pressure increases from zero;
5) this step has 2 kinds of embodiments, respectively as step 5-1) and 5-2):
5-1) in the process that upstream air bag 1 is pressurizeed, the change of the pulse signal amplitude in Real-Time Monitoring downstream air bag 2, instantly the pulse signal amplitude in faint breath capsule 2 with the increase of the air pressure of upstream air bag 1 from diminishing greatly, when finally disappearing, stop pressurization, now upstream air bag 1 is pressurized to a force value higher than tested systolic arterial pressure;
5-2) upstream air bag 1 segmentation is pressurizeed, the described segmented objects to upstream air bag 1 segmentation pressurization is 180mmHg, 240mmHg, 280mmHg, and after each section of pressurization terminates, detect the pulse signal in downstream air bag 2, after described pulse signal disappears, stop pressurization, now upstream air bag 1 is pressurized to a force value higher than tested systolic arterial pressure;
6) the first gas bleeder valve is controlled, upstream air bag 1 is slowly lost heart, in upstream air bag 1 slowly bleeding process, the air pressure of constantly change in upstream air bag 1 is measured by the first pressure transducer 3, and measure the pulse signal in downstream air bag 2 by the second pressure transducer, according to the air pressure in described pulse signal and upstream air bag 1, determine tested systolic arterial pressure, describedly determine that the method for tested systolic arterial pressure has 2 kinds, respectively as step 6-1) and 6-2):
6-1) in upstream air bag 1 slowly bleeding process, the air pressure of constantly change in upstream air bag 1 is measured by the first pressure transducer 3, and the time of origin of first pulse signal in downstream air bag 2 is detected by the second pressure transducer 5, according to the air pressure in the upstream air bag 1 when described first pulse signal occurs, determine tested systolic arterial pressure, such as, measure the generation moment of the peak value of first pulse signal in the downstream air bag 2 detected, with the atmospheric pressure value measured at the generation moment upstream air bag 1 of the peak value of described first pulse signal, the atmospheric pressure value of described upstream air bag 1 is tested systolic arterial pressure, or the atmospheric pressure value measured at the generation moment upstream air bag 1 of the peak value of described first pulse signal, the meansigma methods of the atmospheric pressure value of upstream air bag 1 in former and later two pulse cycles during generation with the peak value at described first pulse signal, described meansigma methods is tested systolic arterial pressure,
6-2) in upstream air bag 1 slowly bleeding process, the air pressure of constantly change in upstream air bag 1 is measured by the first pressure transducer 3, and amplitude and the time of origin of first and second pulse signal in downstream air bag 2 is measured by the second pressure transducer 5, with the atmospheric pressure value in the upstream air bag 1 when first and second pulse signal occur, determine tested arterial blood systolic pressure.Such as, measure the amplitude A 4 of first and second pulse signal and time of origin t4 and t5 of A5 and peak value in the downstream air bag 2 detected, with two atmospheric pressure value P4 and P5 of measurement in the time of origin t4 and t5 upstream air bag 1 of the peak value of described first and second pulse signal, then tested systolic arterial pressure is (P5-(P5-P4) * A5/ (A5-A4)).
8) open the first gas bleeder valve and close the first switch valve, open second switch valve, lose heart to upstream air bag 1 and downstream air bag 2.
Scheme three: as shown in Figure 5, the method using decompression method to measure systolic pressure pulse signal and Measure blood pressure comprises the steps:
1) by a fan-shaped cuff of double bolloon, or the non-fan-shaped cuff of a double bolloon, or two joining cufves, or two not joining cufves are bound on tested limbs, wherein upstream air bag 1 and downstream air bag 2 lay respectively at the upstream and downstream of limb artery blood flow, and are connected with the upstream balloon interface on main frame 4 and downstream balloon interface with downstream trachea 10 respectively by upstream trachea 9 with downstream air bag 2 by upstream air bag 1;
2) press the start key of main frame 4 keyboard, the path of three-way air valve UNICOM downstream air bag 2 and air pump also blocks the path of upstream air bag 1, and air pump is inflated to air bag 2, and the air pressure of downstream air bag 2 slowly increases from zero;
3) this step has 4 kinds of embodiments, respectively as step 3-1), 3-2), 3-3) and 3-4):
3-1) in the process that downstream air bag 2 is pressurizeed, pulse signal in real-time detection downstream air bag 2, when described pulse signal amplitude is increased to maximum, when then starting to decline by zero, stop pressurization, now downstream air bag 2 is pressurized to a force value between tested systolic arterial pressure and diastolic pressure;
3-2) in the process that downstream air bag 2 is pressurizeed, pulse signal in real-time detection downstream air bag 2, when described pulse signal amplitude is increased to maximum by zero, when then starting to decline, stop pressurization, the mean blood pressure value that now downstream air bag 2 is pressurized to tested tremulous pulse subtracts 10mmHg and average pressure value and adds a force value between 20mmHg;
3-3) in the process that downstream air bag 2 is pressurizeed, pulse signal in real-time detection downstream air bag 2, when described pulse signal amplitude by zero be increased to be greater than set-point time, stop pressurization, described pulse signal amplitude set-point is a value between 1.3mmHg to 1.8mmHg, and preferred pulse signal amplitude set-point is 1.5mmHg;
3-4) downstream air bag 2 segmentation is pressurizeed, and after each section of pressurization terminates, detect the pulse signal in downstream air bag 2, when described pulse signal amplitude is greater than set-point, stop pressurization, the described segmented objects to downstream air bag 2 segmentation pressurization is 80mmHg, 120mmHg, 160mmHg, 200mmHg, described pulse signal amplitude set-point is a value between 1.3mmHg to 1.8mmHg, and preferred pulse signal amplitude set-point is 1.5mmHg;
4) gas bleeder valve cuts out, and the path of three-way air valve UNICOM upstream air bag 1 and air pump also blocks the path of downstream air bag 2, and air pump upstream air bag 1 is inflated, and upstream air bag 1 pressure increases from zero;
5) this step has 2 kinds of embodiments, respectively as step 5-1) and 5-2):
5-1) in the process that upstream air bag 1 is pressurizeed, the change of the pulse signal amplitude in Real-Time Monitoring downstream air bag 2, instantly the pulse signal amplitude in faint breath capsule 2 with the increase of the air pressure of upstream air bag 1 from diminishing greatly, when finally disappearing, stop pressurization, now upstream air bag 1 is pressurized to a force value higher than tested systolic arterial pressure;
5-2) upstream air bag 1 segmentation is pressurizeed, the described segmented objects to upstream air bag 1 segmentation pressurization is 180mmHg, 240mmHg, 280mmHg, and after each section of pressurization terminates, detect the pulse signal in downstream air bag 2, after described pulse signal disappears, stop pressurization, now upstream air bag 1 is pressurized to a force value higher than tested systolic arterial pressure;
6) gas bleeder valve is controlled, upstream air bag 1 is slowly lost heart, in upstream air bag 1 slowly bleeding process, the air pressure of constantly change in upstream air bag 1 is measured by the first pressure transducer 3, and measure the pulse signal in downstream air bag 2 by the second pressure transducer, according to the air pressure in described pulse signal and upstream air bag 1, determine tested systolic arterial pressure, describedly determine that the method for tested systolic arterial pressure has 2 kinds, respectively as step 6-1) and 6-2):
6-1) in upstream air bag 1 slowly bleeding process, the air pressure of constantly change in upstream air bag 1 is measured by the first pressure transducer 3, and the time of origin of first pulse signal in downstream air bag 2 is detected by the second pressure transducer 5, according to the air pressure in the upstream air bag 1 when described first pulse signal occurs, determine tested systolic arterial pressure, such as, measure the generation moment of the peak value of first pulse signal in the downstream air bag 2 detected, with the atmospheric pressure value measured at the generation moment upstream air bag 1 of the peak value of described first pulse signal, the atmospheric pressure value of described upstream air bag 1 is tested systolic arterial pressure, or with measurement is at the atmospheric pressure value of the generation moment upstream air bag 1 of the peak value of described first pulse signal, with the meansigma methods of the atmospheric pressure value of upstream air bag 1 in former and later two pulse cycles in the generation moment of the peak value at described first pulse signal, described meansigma methods is tested systolic arterial pressure,
6-2) in upstream air bag 1 slowly bleeding process, the air pressure of constantly change in upstream air bag 1 is measured by the first pressure transducer 3, and amplitude and the time of origin of first and second pulse signal in downstream air bag 2 is measured by the second pressure transducer 5, with the atmospheric pressure value in the upstream air bag 1 when first and second pulse signal occur, determine tested arterial blood systolic pressure.Such as, measure the amplitude A 4 of first and second pulse signal and time of origin t4 and t5 of A5 and peak value in the downstream air bag 2 detected, with two atmospheric pressure value P4 and P5 of measurement in the time of origin t4 and t5 upstream air bag 1 of the peak value of described first and second pulse signal, then tested systolic arterial pressure is (P5-(P5-P4) * A5/ (A5-A4)).
8) gas bleeder valve is opened, the path of three-way air valve UNICOM upstream air bag 1 and air pump also blocks the path of downstream air bag 2, lose heart to upstream air bag 1, then the path of three-way air valve UNICOM downstream air bag 2 and air pump is blocked the path of upstream air bag 1, lose heart to downstream air bag 2.
Embodiment two, measured the apparatus and method of pulse signal of diastolic pressure by decompression method
Device of the present invention is also applicable to the detection of the pulse signal of diastolic pressure, and be provided with control and data processor in microprocessor, described control and handling procedure perform the blood pressure measurement comprised the following steps:
A) described downstream air bag 2 is pressurized to a force value between tested systolic arterial pressure and diastolic pressure, or the mean blood pressure value of tested tremulous pulse subtracts 10mmHg and average pressure value and adds a force value between 20mmHg, or a force value, makes the pulse signal amplitude detected in described downstream air bag 2 when this force value be greater than a set-point;
B) upstream air bag 1 is pressurized to a force value higher than tested systolic arterial pressure;
C) upstream air bag 1 is slowly lost heart, in upstream air bag 1 slowly bleeding process, the air pressure of constantly change in upstream air bag 1 is measured by the first pressure transducer 3, and the pulse signal simultaneously measured by the second pressure transducer 5 in downstream air bag 2, according to the air pressure in the upstream air bag 1 when described pulse signal occurs, determine tested auterial diastole pressure.
Scheme one: diastolic pressure is measured pulse signal detection method and comprised the steps:
1) by a fan-shaped cuff of double bolloon, or the non-fan-shaped cuff of a double bolloon, or two joining cufves, or two not joining cufves are bound on tested limbs, wherein upstream air bag 1 and downstream air bag 2 lay respectively at the upstream and downstream of limb artery blood flow, and are connected with the upstream balloon interface on main frame 4 and downstream balloon interface with downstream trachea 10 respectively by upstream trachea 9 with downstream air bag 2 by upstream air bag 1;
2) press the start key of main frame 4 keyboard, the second gas bleeder valve cuts out, and the downward faint breath capsule 2 of the second air pump is inflated, and the air pressure of downstream air bag 2 slowly increases from zero;
3) this step has 4 kinds of embodiments, respectively as step 3-1), 3-2), 3-3) and 3-4):
3-1) in the process that downstream air bag 2 is pressurizeed, pulse signal in real-time detection downstream air bag 2, when described pulse signal amplitude is increased to maximum, when then starting to decline by zero, stop pressurization, now downstream air bag 2 is pressurized to a force value between tested systolic arterial pressure and diastolic pressure;
3-2) in the process that downstream air bag 2 is pressurizeed, pulse signal in real-time detection downstream air bag 2, when described pulse signal amplitude is increased to maximum by zero, when then starting to decline, stop pressurization, the mean blood pressure value that now downstream air bag 2 is pressurized to tested tremulous pulse subtracts 10mmHg and average pressure value and adds a force value between 20mmHg;
3-3) in the process that downstream air bag 2 is pressurizeed, pulse signal in real-time detection downstream air bag 2, when described pulse signal amplitude by zero be increased to be greater than set-point time, stop pressurization, described pulse signal amplitude set-point is a value between 1.3mmHg to 1.8mmHg, and preferred pulse signal amplitude set-point is 1.5mmHg;
3-4) downstream air bag 2 segmentation is pressurizeed, and after each section of pressurization terminates, detect the pulse signal in downstream air bag 2, when described pulse signal amplitude is greater than set-point, stop pressurization, the described segmented objects to downstream air bag 2 segmentation pressurization is 80mmHg, 120mmHg, 160mmHg, 200mmHg, described pulse signal amplitude set-point is a value between 1.3mmHg to 1.8mmHg, and preferred pulse signal amplitude set-point is 1.5mmHg;
4) the first gas bleeder valve cuts out, and the first air pump upstream air bag 1 is inflated, and upstream air bag 1 pressure increases from zero;
5) this step has 2 kinds of embodiments, respectively as step 5-1) and 5-2):
5-1) in the process that upstream air bag 1 is pressurizeed, the change of the pulse signal amplitude in Real-Time Monitoring downstream air bag 2, instantly the pulse signal amplitude in faint breath capsule 2 with the increase of the air pressure of upstream air bag 1 from diminishing greatly, when finally disappearing, stop pressurization, now upstream air bag 1 is pressurized to a force value higher than tested systolic arterial pressure;
5-2) upstream air bag 1 segmentation is pressurizeed, the described segmented objects to upstream air bag 1 segmentation pressurization is 180mmHg, 240mmHg, 280mmHg, and after each section of pressurization terminates, detect the pulse signal in downstream air bag 2, after described pulse signal disappears, stop pressurization, now upstream air bag 1 is pressurized to a force value higher than tested systolic arterial pressure;
6) the first gas bleeder valve is controlled, upstream air bag 1 is slowly lost heart, in upstream air bag 1 slowly bleeding process, the air pressure of constantly change in upstream air bag 1 is measured by the first pressure transducer 3, and the pulse signal measured by the second pressure transducer 5 in downstream air bag 2, according to the air pressure in described pulse signal and upstream air bag 1, determine tested auterial diastole pressure, describedly determine that the method for tested auterial diastole pressure has 6 kinds, respectively as step 6-1), 6-2), 6-3), 6-4), 6-5) and 6-6):
6-1) in upstream air bag 1 slowly bleeding process, the air pressure of constantly change in upstream air bag 1 is measured by the first pressure transducer 3, and the pulse signal measured by the second pressure transducer 5 in downstream air bag 2, according to the amplitude of described pulse signal change from small to big last no longer change time upstream air bag 1 in air pressure, determine tested auterial diastole pressure, such as, as Fig. 7, pulse signal p10 in the downstream air bag 2 detected, p11, p12, p13, the amplitude A 10 of p14 and p15, A11, A12, A13, A14 and A15, obtain A10<A11<A12<A13=A 14=A15, there is the moment in the pulse signal measured described pulse signal first amplitude is maximum and constant, the i.e. atmospheric pressure value of t13 moment upstream air bag 1, this atmospheric pressure value is tested auterial diastole pressure,
6-2) in upstream air bag 1 slowly bleeding process, the air pressure of constantly change in upstream air bag 1 is measured by the first pressure transducer 3, and the pulse signal measured by the second pressure transducer 5 in downstream air bag 2, according to the time width of described pulse signal all-wave change from small to big last no longer change time upstream air bag 1 in air pressure, determine tested auterial diastole pressure, such as, as Fig. 7, pulse signal p10 in the downstream air bag 2 detected, p11, p12, p13, the all-wave time width d0 of p14 and p15, d1, d2, d3, d4 and d5, obtain d0<d1<d2<d3=d4=d5, there is the moment in the pulse signal measured described pulse signal first all-wave time width is maximum and constant, the i.e. atmospheric pressure value of t13 moment upstream air bag 1, this atmospheric pressure value is tested auterial diastole pressure,
6-3) in the slow bleeding process of gas upstream capsule 1, the air pressure of constantly change in upstream air bag 1 is measured by the first pressure transducer 3, and the pulse signal in downstream air bag 2 measured by logical second excess pressure sensor 5, according to half-wave time width before described pulse signal change from small to big last no longer change time upstream air bag 1 in air pressure, determine tested auterial diastole pressure, such as, as Fig. 7, pulse signal p10 in the downstream air bag 2 detected, p11, p12, p13, the front half-wave time width d6 of p14 and p15, d7, d8, d9, d10 and d11, obtain d6<d7<d8<d9=d10=d 11, there is the moment in the pulse signal measured the front half-wave time width of described pulse signal first is maximum and constant, the i.e. atmospheric pressure value of t13 moment upstream air bag 1, this atmospheric pressure value is tested auterial diastole pressure,
6-4) in upstream air bag 1 slowly bleeding process, the air pressure of constantly change in upstream air bag 1 is measured by the first pressure transducer 3, and the pulse signal measured by the second pressure transducer 5 in downstream air bag 2, according to the rear half-wave time width of described pulse signal change from small to big last no longer change time upstream air bag 1 in air pressure, determine tested auterial diastole pressure, such as, as Fig. 7, pulse signal p10 in the downstream air bag 2 detected, p11, p12, p13, the rear half-wave time width d12 of p14 and p15, d13, d14, d15, d16 and d17, obtain d12<d13<d14<d15=d 16=d17, measure the pulse signal that half-wave time width is maximum and constant after described pulse signal first and the moment occurs, the i.e. atmospheric pressure value of t13 moment upstream air bag 1, this atmospheric pressure value is tested auterial diastole pressure,
6-5) in upstream air bag 1 slowly bleeding process, the air pressure of constantly change in upstream air bag 1 is measured by the first pressure transducer 3, and the pulse signal measured by the second pressure transducer 5 in downstream air bag 2, according to the area of described pulse signal change from small to big last no longer change time upstream air bag 1 in air pressure, determine tested auterial diastole pressure, such as, as Fig. 7, pulse signal p10 in the downstream air bag 2 detected, p11, p12, p13, the area S10 of p14 and p15, S11, S12, S13, S14 and S15, obtain S10<S11<S12<S13=S 14=S15, there is the moment in the pulse signal measured described pulse signal first area is maximum and constant, the i.e. atmospheric pressure value of t13 moment upstream air bag 1, this atmospheric pressure value is tested auterial diastole pressure,
6-6) in upstream air bag 1 slowly bleeding process, the air pressure of constantly change in upstream air bag 1 is measured by the first pressure transducer 3, and the pulse signal measured by the second pressure transducer 5 in downstream air bag 2, according to the area of described pulse signal change from small to big last no longer change time upstream air bag 1 in air pressure, determine tested auterial diastole pressure, such as, as Fig. 7, pulse signal p10 in the downstream air bag 2 detected, p11, p12, p13, the amplitude A 10 of p14 and p15, A11, A12, A13, A14 and A15, all-wave time width d0, d1, d2, d3, d4 and d5, front half-wave time width d6, d7, d8, d9, d10 and d11, rear half-wave time width d12, d13, d14, d15, d16 and d17, the product of pulse signal amplitude in downstream air bag 2 and above-mentioned random time width, i.e. A10*d0<A11*d1<A12*d2LEssT.LTss T.LTA13*d3=A14*d4=A15*d5, or A10*d6<A11*d7<A12*d8LEssT.LTss T.LTA13*d9=A14*d10=A15*d11, or A10*d12<A11*d13<A12*d14LEssT.L TssT.LTA13*d15=A14*d16=A15*d17, there is the moment in the pulse signal measured first of product of described pulse signal amplitude and above-mentioned random time width is maximum and constant, the i.e. atmospheric pressure value of t13 moment upstream air bag 1, this atmospheric pressure value is tested auterial diastole pressure,
8) open the first gas bleeder valve and the second gas bleeder valve, lose heart to upstream air bag 1 and downstream air bag 2.
Scheme two: in the diagram, uses decompression method to measure device and the measuring method of the pulse signal of diastolic pressure
Diastolic pressure is measured pulse signal detection method and is comprised the steps:
1) by a fan-shaped cuff of double bolloon, or the non-fan-shaped cuff of a double bolloon, or two joining cufves, or two not joining cufves are bound on tested limbs, wherein upstream air bag 1 and downstream air bag 2 lay respectively at the upstream and downstream of limb artery blood flow, and are connected with the upstream balloon interface on main frame 4 and downstream balloon interface with downstream trachea 10 respectively by upstream trachea 9 with downstream air bag 2 by upstream air bag 1;
2) press the start key of main frame 4 keyboard, the first gas bleeder valve cuts out, and the first switch valve cuts out, and second switch valve is opened, and the downward faint breath capsule 2 of the first air pump is inflated, and the air pressure of downstream air bag 2 slowly increases from zero;
3) this step has 4 kinds of embodiments, respectively as step 3-1), 3-2), 3-3) and 3-4):
3-1) in the process that downstream air bag 2 is pressurizeed, pulse signal in real-time detection downstream air bag 2, when described pulse signal amplitude is increased to maximum, when then starting to decline by zero, stop pressurization, now downstream air bag 2 is pressurized to a force value between tested systolic arterial pressure and diastolic pressure;
3-2) in the process that downstream air bag 2 is pressurizeed, pulse signal in real-time detection downstream air bag 2, when described pulse signal amplitude is increased to maximum by zero, when then starting to decline, stop pressurization, the mean blood pressure value that now downstream air bag 2 is pressurized to tested tremulous pulse subtracts 10mmHg and average pressure value and adds a force value between 20mmHg;
3-3) in the process that downstream air bag 2 is pressurizeed, pulse signal in real-time detection downstream air bag 2, when described pulse signal amplitude by zero be increased to be greater than set-point time, stop pressurization, described pulse signal amplitude set-point is a value between 1.3mmHg to 1.8mmHg, and preferred pulse signal amplitude set-point is 1.5mmHg;
3-4) downstream air bag 2 segmentation is pressurizeed, and after each section of pressurization terminates, detect the pulse signal in downstream air bag 2, when described pulse signal amplitude is greater than set-point, stop pressurization, the described segmented objects to downstream air bag 2 segmentation pressurization is 80mmHg, 120mmHg, 160mmHg, 200mmHg, described pulse signal amplitude set-point is a value between 1.3mmHg to 1.8mmHg, and preferred pulse signal amplitude set-point is 1.5mmHg;
4) the first gas bleeder valve cuts out, and second switch valve cuts out, and the first switch valve is opened, and the first air pump upstream air bag 1 is inflated, and upstream air bag 1 pressure increases from zero;
5) this step has 2 kinds of embodiments, respectively as step 5-1) and 5-2):
5-1) in the process that upstream air bag 1 is pressurizeed, the change of the pulse signal amplitude in Real-Time Monitoring downstream air bag 2, instantly the pulse signal amplitude in faint breath capsule 2 with the increase of the air pressure of upstream air bag 1 from diminishing greatly, when finally disappearing, stop pressurization, now upstream air bag 1 is pressurized to a force value higher than tested systolic arterial pressure;
5-2) upstream air bag 1 segmentation is pressurizeed, the described segmented objects to upstream air bag 1 segmentation pressurization is 180mmHg, 240mmHg, 280mmHg, and after each section of pressurization terminates, detect the pulse signal in downstream air bag 2, after described pulse signal disappears, stop pressurization, now upstream air bag 1 is pressurized to a force value higher than tested systolic arterial pressure;
6) the first gas bleeder valve is controlled, upstream air bag 1 is slowly lost heart, in upstream air bag 1 slowly bleeding process, the air pressure of constantly change in upstream air bag 1 is measured by the first pressure transducer 3, and the pulse signal measured by the second pressure transducer 5 in downstream air bag 2, according to the air pressure in described pulse signal and upstream air bag 1, determine tested auterial diastole pressure, describedly determine that the method for tested auterial diastole pressure has 6 kinds, respectively as step 6-1), 6-2), 6-3), 6-4), 6-5) and 6-6):
6-1) in upstream air bag 1 slowly bleeding process, the air pressure of constantly change in upstream air bag 1 is measured by the first pressure transducer 3, and the pulse signal measured by the second pressure transducer 5 in downstream air bag 2, according to the amplitude of described pulse signal change from small to big last no longer change time upstream air bag 1 in air pressure, determine tested auterial diastole pressure, such as, as Fig. 7, pulse signal p10 in the downstream air bag 2 detected, p11, p12, p13, the amplitude A 10 of p14 and p15, A11, A12, A13, A14 and A15, obtain A10<A11<A12<A13=A 14=A15, there is the moment in the pulse signal measured described pulse signal first amplitude is maximum and constant, the i.e. atmospheric pressure value of t13 moment upstream air bag 1, this atmospheric pressure value is tested auterial diastole pressure,
6-2) in upstream air bag 1 slowly bleeding process, the air pressure of constantly change in upstream air bag 1 is measured by the first pressure transducer 3, and the pulse signal measured by the second pressure transducer 5 in downstream air bag 2, according to the time width of described pulse signal all-wave change from small to big last no longer change time upstream air bag 1 in air pressure, determine tested auterial diastole pressure, such as, as Fig. 7, pulse signal p10 in the downstream air bag 2 detected, p11, p12, p13, the all-wave time width d0 of p14 and p15, d1, d2, d3, d4 and d5, obtain d0<d1<d2<d3=d4=d5, there is the moment in the pulse signal measured described pulse signal first all-wave time width is maximum and constant, the i.e. atmospheric pressure value of t13 moment upstream air bag 1, this atmospheric pressure value is tested auterial diastole pressure,
6-3) in the slow bleeding process of gas upstream capsule 1, the air pressure of constantly change in upstream air bag 1 is measured by the first pressure transducer 3, and the pulse signal in downstream air bag 2 measured by logical second excess pressure sensor 5, according to half-wave time width before described pulse signal change from small to big last no longer change time upstream air bag 1 in air pressure, determine tested auterial diastole pressure, such as, as Fig. 7, pulse signal p10 in the downstream air bag 2 detected, p11, p12, p13, the front half-wave time width d6 of p14 and p15, d7, d8, d9, d10 and d11, obtain d6<d7<d8<d9=d10=d 11, there is the moment in the pulse signal measured the front half-wave time width of described pulse signal first is maximum and constant, the i.e. atmospheric pressure value of t13 moment upstream air bag 1, this atmospheric pressure value is tested auterial diastole pressure,
6-4) in upstream air bag 1 slowly bleeding process, the air pressure of constantly change in upstream air bag 1 is measured by the first pressure transducer 3, and the pulse signal measured by the second pressure transducer 5 in downstream air bag 2, according to the rear half-wave time width of described pulse signal change from small to big last no longer change time upstream air bag 1 in air pressure, determine tested auterial diastole pressure, such as, as Fig. 7, pulse signal p10 in the downstream air bag 2 detected, p11, p12, p13, the rear half-wave time width d12 of p14 and p15, d13, d14, d15, d16 and d17, obtain d12<d13<d14<d15=d 16=d17, measure the pulse signal that half-wave time width is maximum and constant after described pulse signal first and the moment occurs, the i.e. atmospheric pressure value of t13 moment upstream air bag 1, this atmospheric pressure value is tested auterial diastole pressure,
6-5) in upstream air bag 1 slowly bleeding process, the air pressure of constantly change in upstream air bag 1 is measured by the first pressure transducer 3, and the pulse signal measured by the second pressure transducer 5 in downstream air bag 2, according to the area of described pulse signal change from small to big last no longer change time upstream air bag 1 in air pressure, determine tested auterial diastole pressure, such as, as Fig. 7, pulse signal p10 in the downstream air bag 2 detected, p11, p12, p13, the area S10 of p14 and p15, S11, S12, S13, S14 and S15, obtain S10<S11<S12<S13=S 14=S15, there is the moment in the pulse signal measured described pulse signal first area is maximum and constant, the i.e. atmospheric pressure value of t13 moment upstream air bag 1, this atmospheric pressure value is tested auterial diastole pressure,
6-6) in upstream air bag 1 slowly bleeding process, the air pressure of constantly change in upstream air bag 1 is measured by the first pressure transducer 3, and the pulse signal measured by the second pressure transducer 5 in downstream air bag 2, according to the area of described pulse signal change from small to big last no longer change time upstream air bag 1 in air pressure, determine tested auterial diastole pressure, such as, as Fig. 7, pulse signal p10 in the downstream air bag 2 detected, p11, p12, p13, the amplitude A 10 of p14 and p15, A11, A12, A13, A14 and A15, all-wave time width d0, d1, d2, d3, d4 and d5, front half-wave time width d6, d7, d8, d9, d10 and d11, rear half-wave time width d12, d13, d14, d15, d16 and d17, the product of pulse signal amplitude in downstream air bag 2 and above-mentioned random time width, i.e. A10*d0<A11*d1<A12*d2LEssT.LTss T.LTA13*d3=A14*d4=A15*d5, or A10*d6<A11*d7<A12*d8LEssT.LTss T.LTA13*d9=A14*d10=A15*d11, or A10*d12<A11*d13<A12*d14LEssT.L TssT.LTA13*d15=A14*d16=A15*d17, there is the moment in the pulse signal measured first of product of described pulse signal amplitude and above-mentioned random time width is maximum and constant, the i.e. atmospheric pressure value of t13 moment upstream air bag 1, this atmospheric pressure value is tested auterial diastole pressure,
8) open the first gas bleeder valve, close the first switch valve, open second switch valve, lose heart to upstream air bag 1 and downstream air bag 2.
Scheme three: as shown in Figure 5, uses decompression method to measure the method for diastolic pressure pulse signal and the method for Measure blood pressure, comprises the steps:
1) by a fan-shaped cuff of double bolloon, or the non-fan-shaped cuff of a double bolloon, or two joining cufves, or two not joining cufves are bound on tested limbs, wherein upstream air bag 1 and downstream air bag 2 lay respectively at the upstream and downstream of limb artery blood flow, and are connected with the upstream balloon interface on main frame 4 and downstream balloon interface with downstream trachea 10 respectively by upstream trachea 9 with downstream air bag 2 by upstream air bag 1;
2) press the start key of main frame 4 keyboard, the path of three-way air valve UNICOM downstream air bag 2 and air pump also blocks the path of upstream air bag 1, and air pump is inflated to air bag 2, and the air pressure of downstream air bag 2 slowly increases from zero;
3) this step has 4 kinds of embodiments, respectively as step 3-1), 3-2), 3-3) and 3-4):
3-1) in the process that downstream air bag 2 is pressurizeed, pulse signal in real-time detection downstream air bag 2, when described pulse signal amplitude is increased to maximum, when then starting to decline by zero, stop pressurization, now downstream air bag 2 is pressurized to a force value between tested systolic arterial pressure and diastolic pressure;
3-2) in the process that downstream air bag 2 is pressurizeed, pulse signal in real-time detection downstream air bag 2, when described pulse signal amplitude is increased to maximum by zero, when then starting to decline, stop pressurization, the mean blood pressure value that now downstream air bag 2 is pressurized to tested tremulous pulse subtracts 10mmHg and average pressure value and adds a force value between 20mmHg;
3-3) in the process that downstream air bag 2 is pressurizeed, pulse signal in real-time detection downstream air bag 2, when described pulse signal amplitude by zero be increased to be greater than set-point time, stop pressurization, described pulse signal amplitude set-point is a value between 1.3mmHg to 1.8mmHg, and preferred pulse signal amplitude set-point is 1.5mmHg;
3-4) downstream air bag 2 segmentation is pressurizeed, and after each section of pressurization terminates, detect the pulse signal in downstream air bag 2, when described pulse signal amplitude is greater than set-point, stop pressurization, the described segmented objects to downstream air bag 2 segmentation pressurization is 80mmHg, 120mmHg, 160mmHg, 200mmHg, described pulse signal amplitude set-point is a value between 1.3mmHg to 1.8mmHg, and preferred pulse signal amplitude set-point is 1.5mmHg;
4) gas bleeder valve cuts out, and the path of three-way air valve UNICOM upstream air bag 1 and air pump also blocks the path of downstream air bag 2, and air pump upstream air bag 1 is inflated, and upstream air bag 1 pressure increases from zero;
5) this step has 2 kinds of embodiments, respectively as step 5-1) and 5-2):
5-1) in the process that upstream air bag 1 is pressurizeed, the change of the pulse signal amplitude in Real-Time Monitoring downstream air bag 2, instantly the pulse signal amplitude in faint breath capsule 2 with the increase of the air pressure of upstream air bag 1 from diminishing greatly, when finally disappearing, stop pressurization, now upstream air bag 1 is pressurized to a force value higher than tested systolic arterial pressure;
5-2) upstream air bag 1 segmentation is pressurizeed, the described segmented objects to upstream air bag 1 segmentation pressurization is 180mmHg, 240mmHg, 280mmHg, and after each section of pressurization terminates, detect the pulse signal in downstream air bag 2, after described pulse signal disappears, stop pressurization, now upstream air bag 1 is pressurized to a force value higher than tested systolic arterial pressure;
6) the first gas bleeder valve is controlled, upstream air bag 1 is slowly lost heart, in upstream air bag 1 slowly bleeding process, the air pressure of constantly change in upstream air bag 1 is measured by the first pressure transducer 3, and the pulse signal measured by the second pressure transducer 5 in downstream air bag 2, according to the air pressure in described pulse signal and upstream air bag 1, determine tested auterial diastole pressure, describedly determine that the method for tested auterial diastole pressure has 6 kinds, respectively as step 6-1), 6-2), 6-3), 6-4), 6-5) and 6-6):
6-1) in upstream air bag 1 slowly bleeding process, the air pressure of constantly change in upstream air bag 1 is measured by the first pressure transducer 3, and the pulse signal measured by the second pressure transducer 5 in downstream air bag 2, according to the amplitude of described pulse signal change from small to big last no longer change time upstream air bag 1 in air pressure, determine tested auterial diastole pressure, such as, as Fig. 7, pulse signal p10 in the downstream air bag 2 detected, p11, p12, p13, the amplitude A 10 of p14 and p15, A11, A12, A13, A14 and A15, obtain A10<A11<A12<A13=A 14=A15, there is the moment in the pulse signal measured described pulse signal first amplitude is maximum and constant, the i.e. atmospheric pressure value of t13 moment upstream air bag 1, this atmospheric pressure value is tested auterial diastole pressure,
6-2) in upstream air bag 1 slowly bleeding process, the air pressure of constantly change in upstream air bag 1 is measured by the first pressure transducer 3, and the pulse signal measured by the second pressure transducer 5 in downstream air bag 2, according to the time width of described pulse signal all-wave change from small to big last no longer change time upstream air bag 1 in air pressure, determine tested auterial diastole pressure, such as, as Fig. 7, pulse signal p10 in the downstream air bag 2 detected, p11, p12, p13, the all-wave time width d0 of p14 and p15, d1, d2, d3, d4 and d5, obtain d0<d1<d2<d3=d4=d5, there is the moment in the pulse signal measured described pulse signal first all-wave time width is maximum and constant, the i.e. atmospheric pressure value of t13 moment upstream air bag 1, this atmospheric pressure value is tested auterial diastole pressure,
6-3) in the slow bleeding process of gas upstream capsule 1, the air pressure of constantly change in upstream air bag 1 is measured by the first pressure transducer 3, and the pulse signal in downstream air bag 2 measured by logical second excess pressure sensor 5, according to half-wave time width before described pulse signal change from small to big last no longer change time upstream air bag 1 in air pressure, determine tested auterial diastole pressure, such as, as Fig. 7, pulse signal p10 in the downstream air bag 2 detected, p11, p12, p13, the front half-wave time width d6 of p14 and p15, d7, d8, d9, d10 and d11, obtain d6<d7<d8<d9=d10=d 11, there is the moment in the pulse signal measured the front half-wave time width of described pulse signal first is maximum and constant, the i.e. atmospheric pressure value of t13 moment upstream air bag 1, this atmospheric pressure value is tested auterial diastole pressure,
6-4) in upstream air bag 1 slowly bleeding process, the air pressure of constantly change in upstream air bag 1 is measured by the first pressure transducer 3, and the pulse signal measured by the second pressure transducer 5 in downstream air bag 2, according to the rear half-wave time width of described pulse signal change from small to big last no longer change time upstream air bag 1 in air pressure, determine tested auterial diastole pressure, such as, as Fig. 7, pulse signal p10 in the downstream air bag 2 detected, p11, p12, p13, the rear half-wave time width d12 of p14 and p15, d13, d14, d15, d16 and d17, obtain d12<d13<d14<d15=d 16=d17, measure the pulse signal that half-wave time width is maximum and constant after described pulse signal first and the moment occurs, the i.e. atmospheric pressure value of t13 moment upstream air bag 1, this atmospheric pressure value is tested auterial diastole pressure,
6-5) in upstream air bag 1 slowly bleeding process, the air pressure of constantly change in upstream air bag 1 is measured by the first pressure transducer 3, and the pulse signal measured by the second pressure transducer 5 in downstream air bag 2, according to the area of described pulse signal change from small to big last no longer change time upstream air bag 1 in air pressure, determine tested auterial diastole pressure, such as, as Fig. 7, pulse signal p10 in the downstream air bag 2 detected, p11, p12, p13, the area S10 of p14 and p15, S11, S12, S13, S14 and S15, obtain S10<S11<S12<S13=S 14=S15, there is the moment in the pulse signal measured described pulse signal first area is maximum and constant, the i.e. atmospheric pressure value of t13 moment upstream air bag 1, this atmospheric pressure value is tested auterial diastole pressure,
6-6) in upstream air bag 1 slowly bleeding process, the air pressure of constantly change in upstream air bag 1 is measured by the first pressure transducer 3, and the pulse signal measured by the second pressure transducer 5 in downstream air bag 2, according to the area of described pulse signal change from small to big last no longer change time upstream air bag 1 in air pressure, determine tested auterial diastole pressure, such as, as Fig. 7, pulse signal p10 in the downstream air bag 2 detected, p11, p12, p13, the amplitude A 10 of p14 and p15, A11, A12, A13, A14 and A15, all-wave time width d0, d1, d2, d3, d4 and d5, front half-wave time width d6, d7, d8, d9, d10 and d11, rear half-wave time width d12, d13, d14, d15, d16 and d17, the product of pulse signal amplitude in downstream air bag 2 and above-mentioned random time width, i.e. A10*d0<A11*d1<A12*d2LEssT.LTss T.LTA13*d3=A14*d4=A15*d5, or A10*d6<A11*d7<A12*d8LEssT.LTss T.LTA13*d9=A14*d10=A15*d11, or A10*d12<A11*d13<A12*d14LEssT.L TssT.LTA13*d15=A14*d16=A15*d17, there is the moment in the pulse signal measured first of product of described pulse signal amplitude and above-mentioned random time width is maximum and constant, the i.e. atmospheric pressure value of t13 moment upstream air bag 1, this atmospheric pressure value is tested auterial diastole pressure,
8) gas bleeder valve is opened, the path of three-way air valve UNICOM upstream air bag 1 and air pump also blocks the path of downstream air bag 2, lose heart to upstream air bag 1, then the path of three-way air valve UNICOM downstream air bag 2 and air pump is blocked the path of upstream air bag 1, lose heart to downstream air bag 2.
The device of Measure blood pressure provided by the invention is that colligation two aerating gasbags pressurize on limbs, have and the most effectively the blood flow pulse that can be used for tested limbs blood pressure detected at upstream and downstream air bag bandage, the signal of effective detection wherein pulse, Measure blood pressure accurately and reliably, and measurement result is stablized.
Claims (7)
1. a blood pressure measuring device, described measuring device is used for measuring arteriotony by measured's body part, it is characterized in that: described measuring device comprises
Two aerating gasbags: upstream air bag (1) and downstream air bag (2); Described upstream air bag (1) and downstream air bag (2) are in same cuff or in two different cufves be connected or in two different cufves be not connected, and described cuff is for being bundled in tested described limbs;
Two pressure transducers: the first pressure transducer (3) be connected with described upstream air bag (1) and the second pressure transducer (5) be connected with described downstream air bag (2);
A microprocessor, described microprocessor performs the blood pressure measurement comprised the following steps:
A) described downstream air bag (2) is pressurized to a force value between tested systolic arterial pressure and diastolic pressure, or the mean blood pressure value of tested tremulous pulse subtracts 10mmHg and average pressure value and adds a force value between 20mmHg, or a force value, makes the pulse signal amplitude detected in described downstream air bag (2) when this force value be greater than a set-point;
B) described upstream air bag (1) is pressurized to a force value higher than tested systolic arterial pressure;
C) slowly lost heart in described upstream air bag (1), in described upstream air bag (1) slowly bleeding process, the air pressure of constantly change in described upstream air bag (1) is measured by described first pressure transducer (3), and the pulse signal simultaneously measured by described second pressure transducer (5) in described downstream air bag (2), according to the relation between the air pressure in described pulse signal and described upstream air bag (1), determine tested systolic arterial pressure;
Wherein:
At described step C) in, in described upstream air bag (1) slowly bleeding process, the air pressure of constantly change in described upstream air bag (1) is measured by described first pressure transducer (3), and the time of origin of first pulse signal in described downstream air bag (2) is measured by described second pressure transducer (5), air pressure when occurring according to described first pulse signal in described upstream air bag (1), determines tested systolic arterial pressure;
Or at described step C) in described upstream air bag (1) slowly bleeding process, the air pressure of constantly change in described upstream air bag (1) is measured by described first pressure transducer (3), and amplitude and the time of origin of first and second pulse signal in described downstream air bag (2) is measured by described second pressure transducer (5), with the atmospheric pressure value in when described first and second pulse signal occur described upstream air bag (1), determine tested arterial blood systolic pressure.
2. a kind of blood pressure measuring device according to claim 1, is characterized in that:
In described steps A) in, the method that the mean blood pressure value described downstream air bag (2) being pressurized to a force value between the systolic pressure of tested tremulous pulse and diastolic pressure and described downstream air bag (2) being pressurized to tested tremulous pulse subtracts the force value that 10mmHg and average pressure value add between 20mmHg is in the process of pressurizeing to downstream air bag (2), pulse signal in real-time detection downstream air bag (2), when described pulse signal amplitude is increased to maximum by zero, when then starting to decline, stop pressurization; A force value is pressurized to by downstream air bag (2), with the method making the pulse signal amplitude detected in downstream air bag (2) when this force value be greater than a set-point be, will in the process pressurizeed in described downstream air bag (2), pulse signal in real-time detection described downstream air bag (2) entrained by air pressure signal, when described pulse signal amplitude by zero be increased to be greater than set-point time, stop pressurization;
In described steps A) in, described pulse signal amplitude set-point is a value between 1.3mmHg to 1.8mmHg;
At described step B) in, by the method that described upstream air bag (1) is pressurized to higher than a force value of tested systolic arterial pressure be, in the process pressurizeed in described upstream air bag (1), the change of the pulse signal amplitude in downstream air bag (2) described in Real-Time Monitoring, when the pulse signal amplitude in described downstream air bag (2) with the increase of the air pressure of described upstream air bag (1) from diminishing greatly, when finally disappearing, stop pressurization.
3. a kind of blood pressure measuring device according to claim 1, it is characterized in that: described downstream air bag (2) is pressurized to a force value, the method making the pulse signal amplitude detected in described downstream air bag (2) when this force value be greater than a set-point is, air bag (2) segmentation of described downstream is pressurizeed, and after each section of pressurization terminates, detect the pulse signal in described downstream air bag (2), when described pulse signal amplitude is greater than described set-point, stop pressurization; The segmented objects of described downstream air bag (2) segmentation pressurization is: 80mmHg, 120mmHg, 160mmHg and 200mmHg.
4. a pulse signal detection method, the method, for detecting air pressure in the cuff be bundled on tested limbs and pulse signal and interrelationship, is characterized in that: described pulse signal detection method comprises the following steps:
(1) be bundled on tested limbs by upstream air bag (1) and downstream air bag (2), described upstream air bag (1) and described downstream air bag (2) are in same cuff or in two different cufves be connected or in two different cufves be not connected;
(2) the first pressure transducer (3) is connected with described upstream air bag (1), the second pressure transducer (5) is connected with described downstream air bag (2);
(3) described downstream air bag (2) is pressurized to a force value between tested systolic arterial pressure and diastolic pressure, or the mean blood pressure value of tested tremulous pulse subtracts 10mmHg and average pressure value and adds a force value between 20mmHg, or a force value, makes the pulse signal amplitude detected in downstream air bag (2) when this force value be greater than a set-point;
(4) described upstream air bag (1) is pressurized to a force value higher than tested systolic arterial pressure;
(5) slowly lost heart in described upstream air bag (1), in described upstream air bag (1) slowly bleeding process, the air pressure of constantly change in described upstream air bag (1) is measured by described first pressure transducer (3), and the pulse signal simultaneously measured by described second pressure transducer (5) in described downstream air bag (2), thus measure the atmospheric pressure value when described pulse signal occurs in upstream air bag (1);
Wherein:
In described upstream air bag (1) slowly bleeding process, the air pressure of constantly change in described upstream air bag (1) is measured by described first pressure transducer (3), and measured the time of origin of first pulse signal in described downstream air bag (2) by described second pressure transducer (5), thus measure the air pressure when described first pulse signal occurs in described upstream air bag (1).
5. a kind of pulse signal detection method according to claim 4, is characterized in that:
In described step (3), the method that the method described downstream air bag (2) being pressurized to a force value between the systolic pressure of tested tremulous pulse and diastolic pressure and the mean blood pressure value described downstream air bag (2) being pressurized to tested tremulous pulse subtract the force value that 10mmHg and average pressure value add between 20mmHg is, in the process pressurizeed in described downstream air bag (2), pulse signal in real-time detection described downstream air bag (2) entrained by air pressure signal, when described pulse signal amplitude is increased to maximum by zero, when then starting to decline, stop pressurization; A force value is pressurized to by described downstream air bag (2), with the method making the pulse signal amplitude detected in described downstream air bag (2) when this force value be greater than a set-point be, in the process pressurizeed in described downstream air bag (2), pulse signal in real-time detection described downstream air bag (2) entrained by air pressure signal, when described pulse signal amplitude by zero be increased to be greater than set-point time, stop pressurization;
In described step (4), by the method that described upstream air bag (1) is pressurized to higher than a force value of tested systolic arterial pressure be, in the process pressurizeed in described upstream air bag (1), the change of the pulse signal amplitude in downstream air bag (2) described in Real-Time Monitoring, when the pulse signal amplitude in described downstream air bag (2) with the increase of the air pressure of described upstream air bag (1) from diminishing greatly, when finally disappearing, stop pressurization, described pulse signal amplitude set-point is a value between 1.3mmHg-1.8mmHg.
6. a kind of pulse signal detection method according to claim 4, it is characterized in that: described downstream air bag (2) is pressurized to a force value, make the pulse signal amplitude detected in described downstream air bag (2) when this force value be greater than the method for set-point described in be, air bag (2) segmentation of described downstream is pressurizeed, and after each section of pressurization terminates, detect the pulse signal in described downstream air bag (2), when described pulse signal amplitude is greater than described set-point, stop pressurization, the segmented objects of described downstream air bag (2) segmentation pressurization is: 80mmHg, 120mmHg, 160mmHg and 200mmHg.
7. a kind of pulse signal detection method according to claim 4, it is characterized in that: in described upstream air bag (1) slowly bleeding process, the air pressure of constantly change in described upstream air bag (1) is measured by described first pressure transducer (3), and measured amplitude and the time of origin of first and second pulse signal in described downstream air bag (2) by described second pressure transducer (5), thus to measure when described first pulse signal occurs and at this moment between previous pulse cycle in air pressure in described upstream air bag (1).
Priority Applications (2)
| Application Number | Priority Date | Filing Date | Title |
|---|---|---|---|
| CN201310543620.5A CN103584849B (en) | 2013-11-06 | 2013-11-06 | A kind of blood pressure measuring device and pulse signal detection method |
| PCT/CN2014/090344 WO2015067173A1 (en) | 2013-11-06 | 2014-11-05 | Pulse signal checking method and blood pressure measuring device |
Applications Claiming Priority (1)
| Application Number | Priority Date | Filing Date | Title |
|---|---|---|---|
| CN201310543620.5A CN103584849B (en) | 2013-11-06 | 2013-11-06 | A kind of blood pressure measuring device and pulse signal detection method |
Publications (2)
| Publication Number | Publication Date |
|---|---|
| CN103584849A CN103584849A (en) | 2014-02-19 |
| CN103584849B true CN103584849B (en) | 2015-11-11 |
Family
ID=50075327
Family Applications (1)
| Application Number | Title | Priority Date | Filing Date |
|---|---|---|---|
| CN201310543620.5A Expired - Fee Related CN103584849B (en) | 2013-11-06 | 2013-11-06 | A kind of blood pressure measuring device and pulse signal detection method |
Country Status (1)
| Country | Link |
|---|---|
| CN (1) | CN103584849B (en) |
Families Citing this family (3)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| WO2015067173A1 (en) * | 2013-11-06 | 2015-05-14 | 康尚医疗技术（丹阳）有限公司 | Pulse signal checking method and blood pressure measuring device |
| CN106725403B (en) * | 2017-01-05 | 2019-07-23 | 广东润池科技有限公司 | A kind of blood pressure measuring device |
| JP6852446B2 (en) * | 2017-02-16 | 2021-03-31 | オムロンヘルスケア株式会社 | Blood pressure information measuring device |
Citations (8)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| GB1224510A (en) * | 1968-01-31 | 1971-03-10 | Phelps Dodge Copper Prod | Sphygmomanometer |
| US5607447A (en) * | 1993-09-28 | 1997-03-04 | Mcewen; James A. | Physiologic tourniquet |
| JP3790212B2 (en) * | 2002-11-28 | 2006-06-28 | コーリンメディカルテクノロジー株式会社 | Blood pressure measurement device |
| CN101588751A (en) * | 2007-01-24 | 2009-11-25 | 泰尔茂株式会社 | Cuff for measuring blood pressure, device for measuring blood pressure, method of measuring blood pressure, cuff and method of producing cuff |
| CN101912259A (en) * | 2010-08-06 | 2010-12-15 | 深圳瑞光康泰科技有限公司 | Non-invasive blood pressure measuring device and measuring method thereof |
| CN201977786U (en) * | 2010-11-19 | 2011-09-21 | 伍霆杰 | Measuring strip and sphygmomanometer used for blood pressure measuring device |
| EP2505133A1 (en) * | 2011-03-30 | 2012-10-03 | Nihon Kohden Corporation | Venous pressure measurement apparatus |
| CN103025231A (en) * | 2010-07-21 | 2013-04-03 | 欧姆龙健康医疗事业株式会社 | Electronic blood pressure sphygmomanometer |
-
2013
- 2013-11-06 CN CN201310543620.5A patent/CN103584849B/en not_active Expired - Fee Related
Patent Citations (8)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| GB1224510A (en) * | 1968-01-31 | 1971-03-10 | Phelps Dodge Copper Prod | Sphygmomanometer |
| US5607447A (en) * | 1993-09-28 | 1997-03-04 | Mcewen; James A. | Physiologic tourniquet |
| JP3790212B2 (en) * | 2002-11-28 | 2006-06-28 | コーリンメディカルテクノロジー株式会社 | Blood pressure measurement device |
| CN101588751A (en) * | 2007-01-24 | 2009-11-25 | 泰尔茂株式会社 | Cuff for measuring blood pressure, device for measuring blood pressure, method of measuring blood pressure, cuff and method of producing cuff |
| CN103025231A (en) * | 2010-07-21 | 2013-04-03 | 欧姆龙健康医疗事业株式会社 | Electronic blood pressure sphygmomanometer |
| CN101912259A (en) * | 2010-08-06 | 2010-12-15 | 深圳瑞光康泰科技有限公司 | Non-invasive blood pressure measuring device and measuring method thereof |
| CN201977786U (en) * | 2010-11-19 | 2011-09-21 | 伍霆杰 | Measuring strip and sphygmomanometer used for blood pressure measuring device |
| EP2505133A1 (en) * | 2011-03-30 | 2012-10-03 | Nihon Kohden Corporation | Venous pressure measurement apparatus |
Also Published As
| Publication number | Publication date |
|---|---|
| CN103584849A (en) | 2014-02-19 |
Similar Documents
| Publication | Publication Date | Title |
|---|---|---|
| CN103584846B (en) | A kind of pulse signal detection method and blood pressure measuring device | |
| CN103598881B (en) | A kind of double bolloon pulse signal detection method and blood pressure measuring device | |
| US11064896B2 (en) | Non-invasive blood pressure measuring apparatus and measuring method thereof | |
| CN103140165B (en) | Blood pressure information measurement device | |
| US9119535B2 (en) | Blood pressure manometer and a method of calculating indices of atherosclerosis using the blood pressure manometer | |
| CN103584849B (en) | A kind of blood pressure measuring device and pulse signal detection method | |
| CN101810475A (en) | Electronic auscultation sphygmomanometer based on combination of Korotkoff sound method and oscillometric method | |
| US20130211268A1 (en) | Blood pressure information measurement device and blood pressure information measurement method | |
| CN110840429A (en) | Korotkoff sound-based blood pressure measurement method and blood pressure measurement and cardiovascular system evaluation system | |
| CN103720465B (en) | A kind of blood pressure measuring device and double bolloon pulse signal detection method | |
| CN110420014A (en) | The wearable cardiovascular function evaluation system and method intelligently decomposed based on pulse wave | |
| CN103705227B (en) | For the fan-shaped cuff of blood pressure measurement | |
| JPH01265941A (en) | Wrist blood pressure measuring instrument | |
| WO2015067173A1 (en) | Pulse signal checking method and blood pressure measuring device | |
| KR101264105B1 (en) | Apparatus for measuring blood pressure including decision function of pulse condition, method for measuring blood pressure thereof and method for deciding pulse condition thereof | |
| CN116919369B (en) | Intelligent multimode sphygmomanometer integrating multiple measuring methods | |
| JP2001309894A (en) | Equipment for measuring peripheral venous pressure and its method | |
| CN211883777U (en) | Korotkoff sound-based blood pressure measurement and cardiovascular system evaluation system | |
| WO2015067174A1 (en) | Blood pressure measuring device and dual-balloon pulse signal detection method | |
| JP4398553B2 (en) | Electronic blood pressure monitor | |
| CN107752998A (en) | Shrink pressure measuring device | |
| JPH0445686Y2 (en) | ||
| JP4081921B2 (en) | Electronic blood pressure monitor | |
| CN203107109U (en) | Electronic sphygmomanometer | |
| CN1301523A (en) | Measuring method for electronic sphygmomanometer |
Legal Events
| Date | Code | Title | Description |
|---|---|---|---|
| C06 | Publication | ||
| PB01 | Publication | ||
| SE01 | Entry into force of request for substantive examination | ||
| SE01 | Entry into force of request for substantive examination | ||
| C14 | Grant of patent or utility model | ||
| GR01 | Patent grant | ||
| TR01 | Transfer of patent right | ||
| TR01 | Transfer of patent right |
Effective date of registration: 20170915 Address after: 212300, No. 8 Chang Xi Road, Danyang Economic Development Zone, Jiangsu, China Co-patentee after: Chen Yunquan Patentee after: Wang Qiang Address before: 212300 Danyang City, Jiangsu Province Economic Development Zone, St. Cheong Road, No. 8, No. Patentee before: Yasunao medical technology (Danyang) Co., Ltd. |
|
| CF01 | Termination of patent right due to non-payment of annual fee | ||
| CF01 | Termination of patent right due to non-payment of annual fee |
Granted publication date: 20151111 Termination date: 20191106 |