CN219070287U - Inflatable sleeve belt - Google Patents

Abstract

The utility model provides an inflatable cuff which comprises an outer layer air bag and an inner layer air bag, wherein the inner layer air bag is arranged on one side close to a pressed target, the outer layer air bag is arranged on one side far away from the pressed target to be bound, the outer layer air bag is connected with a first air pump assembly through a first air passage pipe, the inner layer air bag is connected with a second air pump assembly through a second air passage pipe, and the inner layer air bag is used for measuring pulse wave signals of the pressed target. The utility model solves the problem that the existing blood pressure cuff causes the distortion of the pulse wave waveform in acquisition and inaccurate pulse wave measurement, can provide support for the inner air bag under the condition of making the inner air bag narrow, keeps the external pressure of the inner air bag uniform, and avoids the development of the inner air bag in the direction of thickness expansion to greatly increase the volume when the inner air bag is inflated, thereby avoiding the distortion of the pulse wave waveform in acquisition and improving the accuracy of pulse wave measurement.

Description

Inflatable sleeve belt

Technical Field

The utility model belongs to the field of medical instruments, and particularly relates to an inflatable cuff.

Background

Along with the development of economy and the increase of importance of people on health, the demands of people on cardiovascular health monitoring are increasing, and the demands of people on health management of the aged are also increasing, so that accurate measurement of pulse wave and hemodynamic parameters becomes a hot spot of medical care systems and health monitoring products. The pulse wave acquired by the traditional blood pressure cuff can greatly differ from the actual intravascular pressure waveform due to the overlarge volume of the air bag, so that a significant source of hemodynamic parameter error is caused in the blood pressure cuff calculation; the supporting force of the over-narrow air bag for circularly pressurizing the tissue of the arterial part is limited, and the volume is greatly increased by the development of the air bag in the thickness expansion direction when the air bag is inflated, so that the filtering effect is generated, and the distortion in pulse wave waveform acquisition is also caused. Therefore, the existing blood pressure cuff causes distortion in acquisition of pulse wave waveforms, and the problem of inaccurate pulse wave measurement is caused.

Disclosure of Invention

The utility model provides an inflatable cuff, which aims to solve the problem that the existing blood pressure cuff causes inaccurate pulse wave measurement due to acquisition distortion of pulse wave waveforms, the compressed target is compressed by an inner layer air bag to measure pulse wave signals of the compressed target, and an outer layer air bag maintains certain air pressure so as to support the inner layer air bag, so that the inner layer air bag can be supported for the inner layer air bag under the condition of narrow inner layer air bag, the outer pressure of the inner layer air bag is kept uniform, the development of the inner layer air bag in the thickness expansion direction is avoided, the volume is greatly increased, the acquisition distortion of the pulse wave waveforms is avoided, and the pulse wave measurement accuracy is improved.

The present utility model is thus achieved, providing an inflatable cuff comprising: the inner layer air bag is arranged on one side close to the pressed target, the outer layer air bag is arranged on one side far away from the pressed target, the outer layer air bag is connected with the first air pump assembly through the first air pipe, the inner layer air bag is connected with the second air pump assembly through the second air pipe, and the inner layer air bag is used for measuring pulse wave signals of the pressed target.

Further, the inflatable cuff further comprises: the hard winding piece is arranged between the outer layer air bag and the inner layer air bag, the hard winding piece deforms when being subjected to external force larger than the critical force of the material, and the hard winding piece keeps unchanged in shape when being subjected to external force smaller than the critical force of the material.

Further, the inflation width of the outer layer air bag is 1-10cm.

Further, the inflation width of the inner layer air bag is 1-10cm.

Further, the inner layer airbag comprises a first surface layer close to the pressed target side and a second surface layer far away from the pressed target side, the first surface layer and the second surface layer are connected through sewing, the outer layer airbag comprises a third surface layer close to the pressed target side and a fourth surface layer far away from the pressed target side, and the third surface layer and the fourth surface layer are connected through sewing.

Further, the second surface layer has an area smaller than an area of the third surface layer.

Further, the inflation pressure of the outer layer air bag is 15-60 mmHg.

Further, the inflation pressure of the inner layer air bag is in the range of 60-120 mmHg.

In a second aspect, the present utility model also provides a pulse wave measuring device comprising a meter body and an inflatable cuff as provided in any one of the first aspects, wherein the meter body comprises: the device comprises a shell, a first air pump component, a second air pump component, a first air pipeline, a second air pipeline, a pulse wave signal detection circuit and a microprocessor unit, wherein the first air pump component, the second air pump component, the pulse wave signal detection circuit and the microprocessor unit are arranged in the shell, the microprocessor unit is respectively and electrically connected with the first air pump component, the first air pipeline is connected with the first air pipeline, the first air pipeline is connected with the first air pump component, the second air pipeline is connected with the second air pipeline, the second air pipeline is connected with the second air pump component, and the pulse wave signal detection circuit is connected with the inner-layer air bag through an air pressure sensor so as to obtain a pulse wave signal of a compression target through air pressure change detection of the inner-layer air bag.

In a third aspect, the present utility model further provides a pulse wave measurement system, where the pulse wave measurement system includes a terminal device and the pulse wave measurement apparatus provided in the second aspect, where the terminal device is in signal connection with the pulse wave measurement apparatus, and is configured to receive and process a pulse wave signal sent by the pulse wave measurement apparatus.

The utility model has the beneficial effects that: the utility model comprises an outer layer air bag and an inner layer air bag, wherein the inner layer air bag is arranged on one side close to a pressed target, the outer layer air bag is arranged on one side far away from the pressed target to be bound, the outer layer air bag is connected with a first air pump assembly through a first air passage pipe, the inner layer air bag is connected with a second air pump assembly through a second air passage pipe, and the inner layer air bag is used for measuring pulse wave signals of the pressed target. The utility model solves the problem of inaccurate pulse wave measurement caused by distortion in acquisition of pulse wave waveform due to the existing blood pressure cuff, the compressed target is compressed by the inner layer air bag to measure the pulse wave signal of the compressed target, and the outer layer air bag maintains certain air pressure, so that the inner layer air bag is supported, the inner layer air bag can be supported under the condition of narrow inner layer air bag, the outer pressure of the inner layer air bag is kept uniform, the development of the inner layer air bag in the thickness expansion direction is avoided, the volume is greatly increased, the distortion in acquisition of the pulse wave waveform is avoided, and the pulse wave measurement accuracy is improved.

Drawings

FIG. 1 is a schematic illustration of an inflatable cuff in accordance with an embodiment of the present utility model;

FIG. 2 is a schematic cross-sectional view of an inflatable cuff in accordance with an embodiment of the present utility model;

FIG. 3 is a schematic illustration of the application of an inflatable cuff in accordance with an embodiment of the present utility model;

FIG. 4 is a schematic view of a structure of a measuring apparatus according to an embodiment of the present utility model;

FIG. 5 is a schematic diagram of a pulse wave measurement system according to an embodiment of the present utility model;

FIG. 6 is a schematic waveform diagram of pulse wave at different inflation pressures according to an embodiment of the present utility model;

FIG. 7 is a graph illustrating harmonic gain analysis of a pulse wave according to an embodiment of the present utility model;

FIG. 8 is a schematic diagram illustrating harmonic characteristic stability analysis of a pulse wave according to an embodiment of the present utility model;

FIG. 9 is a diagram illustrating an alternative harmonic characteristic stability analysis of pulse waves according to an embodiment of the present utility model.

Wherein: 1. an outer layer balloon; 11. a first air tube; 2. an inner layer airbag; 21. a second air pipe; 3. a hard winding sheet; 4. an artery; 5. extraarterial tissue; 6. a meter body; 61. a housing; 62. a first gas path pipe; 63. a second air path pipe; 64. an air tap.

Detailed Description

The present utility model will be described in further detail with reference to the drawings and examples, in order to make the objects, technical solutions and advantages of the present utility model more apparent. It should be understood that the specific embodiments described herein are for purposes of illustration only and are not intended to limit the scope of the utility model. Rather, these embodiments are provided so that this disclosure will be thorough and complete.

It will be understood that when an element is referred to as being "fixed to" another element, it can be directly on the other element or intervening elements may also be present. When an element is referred to as being "connected" to another element, it can be directly connected to the other element or intervening elements may also be present. The terms "vertical," "horizontal," "left," "right," and the like are used herein for illustrative purposes only and are not meant to be the only embodiment.

The existing flashlight system can illuminate a designated place in the use process, is single in function, a user can only estimate the distance between the user and the illumination place in a visual measurement mode, the estimated distance is inaccurate, the flashlight is generally used in an outdoor environment at night, the illumination range is extremely limited, and if the estimated deviation of the distance between the user and the illumination place is large, safety problems are easy to occur in the outdoor walking process at night. According to the utility model, the distance measuring component is added in the flashlight, so that the flashlight has a distance measuring function, and a user can accurately know the distance between the user and an illumination place through the distance measuring and calculating function of the distance measuring component, so that the safety of outdoor walking at night is improved.

Example 1

Referring to fig. 1 to 3, as shown in fig. 1 to 3, an embodiment of the present utility model provides an inflatable cuff including: the outer layer gasbag 1 and inlayer gasbag 2, inlayer gasbag 2 sets up in being close by one side of oppression target, outer gasbag 1 sets up in keeping away from one side of waiting to bind the oppression, outer gasbag 1 is connected with first air pump assembly through first trachea 11, inlayer gasbag is connected with second air pump assembly through second trachea 21, inlayer gasbag is used for measuring the pulse wave signal by oppression target.

In the embodiment of the present utility model, the inner layer air bag 2 is attached to the skin area of the pressed target with a certain air pressure, and the hemodynamics of the pressed target causes the air pressure variation in the inner layer air bag 2, and according to the air pressure variation, the pulse wave signal of the pressed target can be measured.

The first air pipe 11 may be referred to as an upper air pipe, and the second air pipe 21 may be referred to as a lower air pipe.

Specifically, the air pressure sensor is used for detecting the air pressure change in the inner layer air bag 2, the air pressure sensor captures the pressure change generated by the air pressure change, and the pulse wave signal detection circuit is used for converting an analog signal into a digital signal and inputting the digital signal into the microprocessor unit for processing, so that the pulse wave signal of the pressed target is obtained.

In the embodiment of the utility model, the outer layer air bag 1 can provide different air bag pressures, and external pressure is provided for the inner layer air bag 2, so that annular binding force is provided for the inner layer air bag 2 during measurement, and the inner layer air bag 2 bears the maximum binding force because of the structural support of the outer layer air bag 1, so that stable and good pulse wave signals can be acquired with smaller inflation volume, and the energy loss and filtering effect of the inflation cuff on the pulse wave transmission to the sensor are reduced.

The inflatable cuff may be wrapped around a human body so as to press a portion to be measured of the human body, and the portion to be measured may be an arm, a wrist or an ankle. Included in the site to be measured is an artery 4 and extra-arterial tissue 5.

The inflatable cuff can also be wrapped around the mammal body so as to press the portion of the mammal to be measured, which can be the tail, the forepalm limb junction or the hindpalm limb junction.

The utility model solves the problem of inaccurate pulse wave measurement caused by distortion in acquisition of pulse wave waveform due to the existing blood pressure cuff, the compressed target is compressed by the inner layer air bag 2 to measure the pulse wave signal of the compressed target, and the outer layer air bag 1 maintains certain air pressure, so that the inner layer air bag is supported, the inner layer air bag 2 can be supported under the condition that the inner layer air bag 2 is narrow, the outer pressure of the inner layer air bag 2 is kept uniform, the development of greatly increased volume in the direction of thickness expansion when the inner layer air bag 2 is inflated is avoided, the distortion in acquisition of the pulse wave waveform is avoided, and the accuracy of pulse wave measurement is improved. The embodiment of the utility model has the advantages that the obtained pulse wave signals are accurate, the energy loss of each frequency spectrum is smaller, the stability is higher, and the high-precision hemodynamic parameters can be provided for the subsequent pulse wave analysis.

Further, the inflatable cuff further comprises: and a hard winding sheet 3 arranged between the outer layer airbag 1 and the inner layer airbag 2, wherein the hard winding sheet 3 deforms when an external force larger than a material critical force is applied, and the hard winding sheet 3 keeps unchanged in shape when an external force smaller than the material critical force is applied.

In the embodiment of the present utility model, the material critical force may be determined according to the pressure of the inflated outer layer airbag 1, and the material critical force of the hard winding sheet 3 may be smaller than the pressure of the inflated outer layer airbag 1, so that the hard winding sheet 3 may be deformed by the inflation of the outer layer airbag 1 and maintain the shape when the pressures of the inner layer airbag 2 and the outer layer airbag 1 are balanced, so that the inner layer airbag 2 is better structurally supported. Of course, the hard winding sheet 3 may be deformed by a human force, as long as the human force exceeds the material critical force.

According to the utility model, through the sandwich structure design that the hard winding sheet 3 is clamped between the double-layer air bags of the inner-layer air bag 2 and the outer-layer air bag 1, the hard winding sheet 3 effectively separates the inner-layer air bag 2 and the outer-layer air bag 1, the inner-layer air bag 2 can be bound to be attached to the skin, the outward expansion space of the inner-layer air bag 2 is limited, an effective back support structure is formed, and meanwhile, the structure can adapt to human tissues with different sizes. While the outer layer airbag 1 can provide different airbag pressures, providing annular restraining forces to the hard wrap sheet 3 and the inner layer airbag 2. The inner layer air bag 2 bears the maximum binding force due to the structural support of the hard winding sheet 3 and the outer layer air bag 1, so that stable and good pulse waves can be acquired with smaller inflation volume, and the energy loss and the filtering effect of the inflation cuff on the process of transmitting the pulse waves to the sensor are reduced. The pulse wave obtained in the mode is accurate, each frequency spectrum energy loss is smaller, the stability is higher, and the subsequent high-precision calculation of the hemodynamic parameters can be realized.

Further, the inflation width of the outer layer airbag 1 is 1-10cm.

In the embodiment of the present utility model, the inflation width of the outer layer airbag 1 is 1-10cm, specifically, the inflation width of the outer layer airbag 1 may be set larger when the inflation pressure of the inner layer airbag 2 is larger, and the inflation width of the outer layer airbag 1 may be set smaller when the inflation pressure of the inner layer airbag 2 is smaller.

Further, the inflation width of the inner layer airbag 2 is 1-10cm.

In the embodiment of the present utility model, the inflation width of the outer layer airbag 1 is 1-10cm, specifically, the determination is performed according to the measurement accuracy of the measuring instrument, when the measurement accuracy of the measuring instrument is large, the inflation width of the outer layer airbag 1 may be set to be larger, and when the measurement accuracy of the measuring instrument is small, the inflation width of the outer layer airbag 1 may be set to be smaller.

It should be noted that, because the sandwich structure design of sandwiching a layer of hard winding sheet 3 between the double-layer air bags of the inner layer air bag 2 and the outer layer air bag 1 is provided in the embodiment of the utility model, the hard winding sheet 3 effectively separates the inner layer air bag 2 and the outer layer air bag 1, and can bind the inner layer air bag 2 to make it adhere to the skin and limit the outward expanding space of the inner layer air bag 2, so as to form an effective back support structure, and simultaneously adapt to human tissues with different sizes. While the outer layer airbag 1 can provide different airbag pressures, providing annular restraining forces to the hard wrap sheet 3 and the inner layer airbag 2. The inner layer air bag 2 bears the maximum binding force due to the structural support of the hard winding sheet 3 and the outer layer air bag 1, so that stable and good pulse waves can be acquired with smaller inflation volume, and the energy loss and the filtering effect of the inflation cuff on the process of transmitting the pulse waves to the sensor are reduced.

Further, the inner layer balloon 2 includes a first surface layer near the side of the object to be compressed and a second surface layer far away from the side of the object to be compressed, the first surface layer and the second surface layer are connected by sewing, the outer layer balloon 1 includes a third surface layer near the side of the object to be compressed and a fourth surface layer far away from the side of the object to be compressed, and the third surface layer and the fourth surface layer are connected by sewing.

In the embodiment of the utility model, the inner layer airbag 2 is sewn through the first surface layer and the second surface layer, and the outer layer airbag 1 is sewn through the third surface layer and the fourth surface layer. Making the inner and outer airbags 2 and 1 stronger and more durable.

Further, the second surface layer has an area smaller than an area of the third surface layer.

In the embodiment of the present utility model, the area of the second surface layer is smaller than the area of the third surface layer, so that the area of the inner layer airbag 2 is smaller than the area of the outer layer airbag 1. Therefore, the inner layer air bag 2 can be better bound to be attached to the skin, the outward expansion space of the inner layer air bag 2 is limited, an effective back support structure is formed, and the device can adapt to human tissues with different sizes.

Further, the inflation pressure of the outer layer airbag 1 is 15-60 mmHg.

In the embodiment of the present utility model, the inflation pressure range of the outer layer airbag 1 can be adjusted by the first airbag pump assembly, and the adjustment range is 15-60 mmhg. Therefore, the inner layer air bag 2 is convenient to bind to the skin and limit the outward expansion space of the inner layer air bag 2, an effective back support structure is formed, and the device can adapt to human tissues with different sizes.

Further, the outer layer air bag 1 is inflated to 15-40 mmHg, and the outer layer air bag and the hard winding sheet 3 together achieve the function of stably supporting the inner layer air bag 2, can be suitable for limbs with different sizes and effectively constraint the expansion volume of the inner layer air bag 2, so that the inner layer air bag 2 is rapidly and stably boosted, and stable and fidelity pulse wave signals are obtained.

The material critical force of the hard rolled sheet 3 may be smaller than the pressure at which the outer layer airbag 1 is inflated at 60 mmhg. In this way, the inflatable cuff can be wrapped around the compressed object with less effort.

Further, the inflation pressure of the inner layer airbag 2 is in the range of 60-120 mmHg.

The inflation pressure range of the outer layer air bag 1 can be adjusted through the first air pump assembly, and the adjustment range is 60-120 mmHg. In this way, the measurement range of the pulse wave can be ensured.

The utility model comprises an outer layer air bag 1 and an inner layer air bag 2, wherein the inner layer air bag 2 is arranged on one side close to a pressed target, the outer layer air bag 1 is arranged on one side far away from the pressed target to be bound, the outer layer air bag 1 is connected with a first air pump assembly through a first air passage pipe 62, the inner layer air bag is connected with a second air pump assembly through a second air passage pipe 63, and the inner layer air bag is used for measuring pulse wave signals of the pressed target. The utility model solves the problem that the pulse wave measurement is inaccurate due to the distortion of the acquisition of the pulse wave waveform caused by the existing blood pressure cuff.

Example two

Referring to fig. 4, fig. 4 shows a pulse wave measuring device, the pulse wave measuring device includes a measuring instrument body 6 and the inflatable cuff according to any one of the first embodiment, wherein the measuring instrument body 6 includes: the casing 61 and set up first air pump subassembly, second air pump subassembly, first gas circuit pipe 62, second gas circuit pipe 63, pulse wave signal detection circuit, the microprocessor unit in the casing 61, wherein, the microprocessor unit respectively with first air pump subassembly second air pump subassembly the pulse wave signal detection circuit electricity is connected, first trachea 11 with first gas circuit pipe 62 is connected, first gas circuit pipe 62 with first gas pump subassembly is connected, second trachea 21 with second gas circuit pipe 63 is connected, second gas circuit pipe 63 with second air pump subassembly is connected, pulse wave signal detection circuit pass through an air pressure sensor with inner bag 2 is connected, in order to obtain the pulse wave signal of oppression target through the atmospheric pressure variation detection of inner bag 2.

The first air channel pipe 62 and the second air channel pipe 63 are connected with the first air pump component and the second air pump component through an air tap 64.

Example III

Referring to fig. 5, fig. 5 shows that the present utility model further provides a pulse wave measurement system, where the pulse wave measurement system includes a terminal device and the pulse wave measurement apparatus provided in the second aspect, and the terminal device is in signal connection with the pulse wave measurement apparatus and is configured to receive and process a pulse wave signal sent by the pulse wave measurement apparatus.

The pulse wave measuring device comprises a wireless transmission unit electrically connected with the microprocessor unit, and the pulse wave measuring device sends pulse wave signals to the terminal equipment through the wireless transmission unit. The wireless transmission unit may be a bluetooth transmission unit.

The terminal equipment is an intelligent terminal, and the intelligent terminal transmits and receives pulse wave signals through the wireless transmission and measurement instrument body and converts the pulse waves into time domain, frequency domain, heart rate, hemodynamic parameters and other characteristics.

Furthermore, after the intelligent terminal obtains the stable and high-fidelity pulse wave signals from the wireless transmission unit or the Bluetooth transmission unit, the characteristic calculation of heart rate, heart rate variability, respiration rate, respiration intensity and the like can be performed through the related algorithm in the intelligent terminal.

Furthermore, the stable and high-fidelity pulse wave signals obtained from the wireless transmission unit or the Bluetooth transmission unit at the intelligent terminal can also calculate the heart output power, the heart output per beat, the heart output variation degree per beat, the heart index and the like through the time domain and frequency pre-characteristics.

According to the stable and high-fidelity pulse wave signals acquired by the device in the mode of the embodiment, pulse wave characteristics and hemodynamic parameters can be calculated, and the characteristics and parameter sets can be used for further analysis of cardiovascular health conditions of old people or chronic diseases.

The utility model optimizes the sandwich structure of the inner layer air bag, the hard winding sheet and the outer layer air bag, and controls the inflation of the outer layer air bag to be under the low pressure of 15-60mmHg, the sandwich structure of the hard winding sheet can ensure that the inner layer air bag can be stably attached to the skin, the acquired pulse wave is more stable, the fidelity of the pulse wave waveform is higher, the restraint pressure of the outer layer air bag is lower, the volume of the air bag with higher inner layer pressure is smaller, therefore, the compression to the body is lighter, and the utility model is more suitable for long-time signal acquisition and landing of wearing application scenes compared with the traditional blood pressure cuff.

Referring to fig. 6, fig. 6 shows that the inner balloon maintains the human pulse wave acquired at 90 mmHg for two consecutive 10 seconds under the inflation pressure of the different outer balloons, and the inflation pressures of 0mmHg, 60mmHg, 40mmHg, 30mmHg, 15mmHg are respectively applied through the mechanical structure outer balloon of the present utility model. As shown in fig. 6, pulse waves of two successive times each, the stability of the pulse wave waveform can be seen to be extremely high.

Furthermore, the obtained pulse wave can be subjected to spectrum analysis under different outer-layer air bag inflation pressures respectively compared with a non-layer air bag structure system. The difference chart of harmonic amplitude analysis is shown in fig. 7, wherein the human pulse wave is collected for 10 seconds continuously under the condition that the inner pulse is maintained at 90 mmHg under the inflation pressure of the outer-layer-free air bag and the different outer-layer air bags. In fig. 7, the results show that the outer balloon with 40mmHg has more high frequency harmonic amplitude energy (C6-C10) than the outer balloon without the outer balloon (without the sandwich structure), indicating that the system of the present utility model has better high frequency response and higher fidelity of the acquired pulse wave.

Further, the harmonic amplitude variation analysis was performed on the obtained pulse wave compared with the external air bag system state of 0mmHg at different external air bag inflation pressures, and the result showed that the external air bag state of 40mmHg had more stable low-frequency harmonic amplitude energy (C1 CV to C5CV are lowest) than the other external air bag inflation states, and in fig. 8, the human pulse wave was collected for 10 seconds continuously while the inner pulse was maintained at 90 mmHg at the inflation pressure of the different external air bags. And carrying out harmonic amplitude analysis on the continuous pulse wave to obtain a harmonic amplitude variation degree comparison result of the low-frequency harmonic waves C1-C5. The non-inflated state (0 mmHg) of the outer balloon was used as a reference. The system has better stability, and the energy of the low-frequency harmonic component of the acquired pulse wave is stable.

Further, the obtained pulse wave was analyzed for harmonic amplitude variation in comparison with the 0mmHg external balloon system state at different external balloon inflation pressures, and the result showed that the 40mmHg external balloon state had more stable high-frequency harmonic amplitude energy (C6 CV to C10CV lowest) than the other external balloon inflation states, as shown in fig. 9, and the inner pulse was maintained at 90 mmHg for 10 seconds of human pulse wave acquisition at the inflation pressure of the different external balloons. And carrying out harmonic amplitude analysis on the continuous pulse wave to obtain a harmonic amplitude variation degree comparison result of the high-frequency harmonic C6-C11. The non-inflated state (0 mmHg) of the outer balloon was used as a reference. The system has better stability, and the collected pulse wave high-frequency harmonic component energy is stable.

The pulse wave measuring system can accurately and stably monitor the pulse wave and the circulation state of the body, is suitable for the study on the blood flow dynamics, is also suitable for being used as a daily health care monitoring of the old in the field of wearing equipment, or is a useful technology of a Kang Yang monitoring and diagnosis platform for slow patients.

The foregoing description of the preferred embodiments of the utility model is not intended to be limiting, but rather is intended to cover all modifications, equivalents, and alternatives falling within the spirit and principles of the utility model.

Claims (8)

1. An inflatable cuff, the inflatable cuff comprising: the inner layer air bag is arranged on one side close to the pressed target, the outer layer air bag is arranged on one side far away from the pressed target, the outer layer air bag is connected with the first air pump assembly through the first air pipe, the inner layer air bag is connected with the second air pump assembly through the second air pipe, and the inner layer air bag is used for measuring pulse wave signals of the pressed target.

2. The inflatable cuff of claim 1, wherein the inflatable cuff further comprises: the hard winding piece is arranged between the outer layer air bag and the inner layer air bag, the hard winding piece deforms when being subjected to external force larger than the critical force of the material, and the hard winding piece keeps unchanged in shape when being subjected to external force smaller than the critical force of the material.

3. An inflatable cuff as recited in claim 2, wherein said outer envelope has an inflation width of 1-10cm.

4. An inflatable cuff as recited in claim 3, wherein said inner bladder has an inflation width of 1-10cm.

5. An inflatable cuff as recited in claim 4, wherein said inner bladder includes a first surface layer on a side closer to a target to be compressed and a second surface layer on a side farther from the target to be compressed, said first surface layer and said second surface layer being joined by stitching, said outer bladder includes a third surface layer on a side closer to the target to be compressed and a fourth surface layer on a side farther from the target to be compressed, said third surface layer and said fourth surface layer being joined by stitching.

6. An inflatable cuff as recited in claim 5, wherein an area of said second surface layer is less than an area of said third surface layer.

7. An inflatable cuff as recited in claim 1, wherein said outer bladder has an inflation pressure in the range of 15-60 mmhg.

8. The inflatable cuff of claim 1, wherein the inflation pressure of the inner bladder ranges from 60 to 120 mmhg.

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