CN110403579B

CN110403579B - Pulse wave conduction parameter measuring system and method

Info

Publication number: CN110403579B
Application number: CN201810404068.4A
Authority: CN
Inventors: 庄少春; 叶飞; 陈仁库
Original assignee: Shenzhen Dama Technology Co Ltd
Current assignee: Oufeikang Technology Shenzhen Co ltd
Priority date: 2018-04-28
Filing date: 2018-04-28
Publication date: 2022-08-19
Anticipated expiration: 2038-04-28
Also published as: CN110403579A

Abstract

The embodiment of the invention discloses a pulse wave conduction parameter measuring system and method. The method comprises the following steps: obtaining, by one or more processors, first vibration information of a supine subject from a first fiber optic sensor configured to be placed under a back region corresponding to a fourth thoracic vertebral body of the supine subject; obtaining, by the one or more processors, second vibration information of the supine subject from a second fiber optic sensor configured to be positioned under a lumbar region corresponding to a fourth lumbar vertebra of the supine subject; generating, by the one or more processors, first hemodynamic-related information based on the first vibration information and second hemodynamic-related information based on the second vibration information, thereby determining an aortic pulse wave transit time of the supine subject.

Description

Pulse wave conduction parameter measuring system and method

Technical Field

The present application relates to a pulse wave conduction parameter measuring system and method, and more particularly, to a non-invasive pulse wave conduction parameter measuring system and method.

Background

The statements herein merely provide background information related to the present application and may not necessarily constitute prior art.

Worldwide, cardiovascular and cerebrovascular diseases are important causes of morbidity and mortality, and the morbidity and mortality of cardiovascular and cerebrovascular diseases are related to the pathological changes of arterial blood vessels. For example, angina, myocardial infarction, stroke, and intermittent claudication are associated with coronary artery disease, cerebral artery disease, and lower limb artery disease. The two major forms of arterial lesions include structural lesions, which manifest as vascular obstruction, such as atherosclerosis, and functional lesions, which manifest as changes in vascular function, such as vascular sclerosis. Among them, changes in the elasticity of arterial vessel walls underlie the occurrence and development of various cardiovascular events.

The periodic contraction and relaxation of the heart can not only cause the change of the blood flow velocity and the blood flow in the arterial blood vessel, but also generate pulse waves which are transmitted along the blood vessel wall. Pulse Wave Velocity (PWV) is related to elasticity of arterial vessels, and generally, the Pulse Wave Velocity is faster as the hardness of vessels is larger, so that the degree of elasticity of arteries can be evaluated by measuring the Pulse Wave Velocity.

Disclosure of Invention

The technical problem to be solved by the embodiments of the present invention is to provide a non-invasive pulse wave propagation parameter measuring system and method, aiming at the technical problem related to cardiovascular disease detection in the prior art.

In order to solve the above technical problem, in one aspect, an embodiment of the present invention provides a pulse wave propagation parameter measuring method, including: acquiring first vibration information of a supine object from a first optical fiber sensor, wherein the first optical fiber sensor is placed under a back region corresponding to a fourth thoracic vertebral body of the supine object; acquiring second vibration information of the supine object from a second optical fiber sensor, wherein the second optical fiber sensor is arranged below a waist region corresponding to a fourth lumbar vertebra of the supine object; generating first hemodynamic-related information based on the first vibration information and second hemodynamic-related information based on the second vibration information; determining an aortic valve opening time of the supine subject based on the first hemodynamic-related information and a pulse wave arrival time of the supine subject based on the second hemodynamic-related information; and determining an aortic pulse wave transit time of the supine subject based on the aortic valve opening time and the pulse wave arrival time.

Preferably, the first or second optical fiber sensor includes: an optical fiber arranged in a substantially planar configuration; a light source coupled to one end of the one or more optical fibers; a receiver coupled to the other end of the one optical fiber for sensing a change in light intensity through the optical fiber; and a mesh layer composed of meshes provided with openings, wherein the mesh layer is in contact with the surface of the optical fiber.

Preferably, generating first hemodynamic-related information based on the first vibration information and generating second hemodynamic-related information based on the second vibration information further comprises: filtering and scaling the first vibration information and the second vibration information respectively to generate the first hemodynamically-related information and the second hemodynamically-related information.

Preferably, determining the aortic valve opening time of the supine subject based on the first hemodynamic-related information further comprises: performing a second order differential operation on the first hemodynamic-related information; performing feature search on a waveform diagram of the first hemodynamic related information after second-order differential operation to determine a highest peak in a cardiac cycle; and determining an aortic valve open time for the supine subject based on the highest peak.

Preferably, the method further comprises: acquiring the distance between the first optical fiber sensor and the second optical fiber sensor along the height direction of the human body and generating an aortic pulse wave conduction distance; and determining, by the one or more processors, an aortic pulse wave velocity based on the aortic pulse wave travel distance and the aortic pulse wave travel time.

Preferably, the method further comprises: sending at least one of the aortic pulse transit time and the aortic pulse transit velocity to one or more output devices.

In another aspect, the present invention further provides a pulse wave conduction parameter measuring system, including: the first optical fiber sensor is arranged in the vicinity of a fourth thoracic vertebral body of the supine object and is used for acquiring first vibration information of the supine object; the second optical fiber sensor is arranged in the vicinity of a fourth lumbar vertebra body of the supine object and is used for acquiring second vibration information of the supine object; one or more processors; and one or more memories storing instructions which, when executed by the one or more processors, implement any of the methods described above.

In still another aspect, the present invention also provides a pulse wave conduction parameter measuring apparatus, including: the supine subject lying bed comprises a body, a first fixing part and a second fixing part, wherein the body is used for lying a supine subject, comprises an upper cover and a lower cover, and comprises a back area and a waist area; the first optical fiber sensor is arranged in the back area of the body and used for acquiring first vibration information of the supine object; the second optical fiber sensor group is arranged in the waist area of the body and is used for acquiring second vibration information of the supine object; the upper cover and the lower cover coat the first optical fiber sensor and the second optical fiber sensor group.

Preferably, the device further comprises a neck pillow arranged on the upper cover for the neck of the supine subject to rest on to ensure that the supine subject is in the measuring position.

Preferably, the device further comprises a shoulder stop disposed on the upper cover for the shoulders of the supine subject to abut against to secure the supine subject in a measuring position.

Preferably, the body further comprises a lower limb area, and the device further comprises a foot stopper, which is arranged on the lower limb area of the upper cover and is used for the foot or the lower leg of the supine subject to abut against so as to ensure that the supine subject is in the measuring position.

Preferably, the body upper cover can adopt a three-dimensional structure, and comprises a human body contour concave structure to ensure that the supine object is in a measuring position.

Preferably, two or more fibre-optic sensors of the second group of fibre-optic sensors are aligned along the longitudinal axis of the body.

Preferably, the optical fiber sensor includes: an optical fiber arranged in a substantially planar configuration; a light source coupled to one end of the one or more optical fibers; a receiver coupled to the other end of the one optical fiber for sensing a change in light intensity through the optical fiber; and a mesh layer composed of meshes provided with openings, wherein the mesh layer is in contact with the surface of the optical fiber.

The embodiment of the invention has the following beneficial effects: the aorta of the human body passes through the thoracic cavity and the abdominal cavity of the human body and is not the superficial body surface artery, and the traditional method for measuring the pulse wave conduction parameter of the superficial body surface artery is not suitable for measuring the pulse wave conduction parameter of the aorta. By adopting the method for measuring the human aortic pulse wave conduction parameters, a tester can measure only by lying on the measuring equipment without directly contacting the human body, and the method has the advantages of high measuring precision and simple operation, can greatly improve the comfort level of the tester, and can be widely applied to various scenes such as hospitals, families and the like.

Drawings

In order to more clearly illustrate the technical solutions of the embodiments of the present application, the drawings used in the description of the embodiments will be briefly introduced below. It is obvious that the drawings in the following description are only some embodiments of the invention, and it is obvious for a person skilled in the art that the invention can also be applied to other similar scenarios according to these drawings without inventive effort. Unless otherwise apparent from the context, or stated otherwise, like reference numerals in the figures refer to like structures and operations.

Fig. 1 is a schematic diagram of a pulse wave conduction parameter measurement system according to some embodiments of the present application;

FIG. 2 is a schematic diagram of the generation principle of pulse wave;

FIG. 3 is a schematic diagram of the principle of measurement of aortic pulse wave conduction parameters;

FIG. 4 is a block diagram of a computing device according to some embodiments of the present application;

FIG. 5 is a schematic diagram of a sensing device according to some embodiments of the present application;

FIG. 6 is a schematic illustration of a position of a sensing device according to some embodiments of the present application;

FIG. 7 is a flow chart of a method of pulse wave conduction parameter measurement according to some embodiments of the present application;

FIG. 8 is a signal waveform diagram of an object according to some embodiments of the present application;

FIG. 9 is a schematic view of a sensing device according to some embodiments of the present application;

FIG. 10 is a schematic view of a positioning indicator according to some embodiments of the present application; and

FIG. 11 is a schematic view of a positioning indicator according to other embodiments of the present application.

Detailed Description

As used in this application and the appended claims, the terms "a," "an," "the," and/or "the" are not intended to be inclusive in the singular, but rather are intended to be inclusive in the plural unless the context clearly dictates otherwise. In general, the terms "comprises" and "comprising" merely indicate that steps and elements are included which are explicitly identified, that the steps and elements do not form an exclusive list, and that a method or apparatus may include other steps or elements.

Fig. 1 is a schematic diagram of a pulse wave conduction parameter measurement system 100 according to some embodiments of the present application. As shown in fig. 1, the pulse wave conduction parameter measuring system 100 may include a sensing device 101, a network 103, a server 105, a storage device 107, and an output device 109.

The sensing device 101 may be configured to acquire vibration information of the object 102. In some embodiments, the sensing device 101 may be a vibration sensitive sensor, such as one or more of an acceleration sensor, a velocity sensor, a displacement sensor, a pressure sensor, a strain sensor, a stress sensor, or a sensor that equivalently transforms physical quantities based on acceleration, velocity, displacement, or pressure (e.g., a static charge sensitive sensor, an inflatable micro-motion sensor, a radar sensor, etc.). In some embodiments, the strain sensor may be a fiber optic strain sensor. In some embodiments, the sensing device 101 may further include a temperature sensitive sensor, such as an infrared sensor, to acquire body temperature information of the subject. The sensing device 101 may be configured to be placed on various types of beds such as a medical bed, a nursing bed, and the like, in which the subject 102 is located. The subject 102 may be a living being undergoing vital sign signal monitoring. In some embodiments, the subject 102 may be a hospital patient or a caretaker, such as an elderly person, a person being prohibited, or other person. The sensing device 101 may transmit the acquired vibration information of the object 102 to the server 105 through the network 103 for subsequent processing. In some embodiments, the vibration information obtained by the sensing device 101 can be processed to calculate vital sign signals of the subject, such as heart rate, respiratory rate, body temperature, and the like. In some embodiments, after the vibration information acquired by the sensing device 101 is processed, Pulse Wave propagation parameters of the subject, such as Pulse Wave Transit Time (PTT) and Pulse Wave propagation velocity PWV, can be calculated. The sensing device 101 may also transmit the acquired vibration information to the output device 109 for output, for example, by displaying a waveform diagram of the vibration information on a display. The sensing device 101 may also transmit the acquired vibration information of the object 102 to the storage device 107 through the network 103 for storage, for example, the system 100 may include a plurality of sensing devices, and the vibration information of a plurality of objects acquired by the plurality of sensing devices may be transmitted to the storage device 107 for storage as part of the customer data.

The network 103 may enable the exchange of information. In some embodiments, the components of the pulse wave propagation parameter measuring system 100 (i.e., the sensing device 101, the network 103, the server 105, the storage device 107, and the output device 109) can transmit and receive information to and from each other through the network 103. For example, the sensing device 101 may store the acquired vital sign related signals of the subject 102 to the storage device 107 via the network 103. In some embodiments, the network 103 may be a single network, such as a wired network or a wireless network, or may be a combination of networks. Network 103 may include, but is not limited to, a local area network, a wide area network, a shared network, a private network, and the like. The network 103 may include a variety of network access points, such as wireless or wired access points, base stations, or network access points, through which other components of the pulse wave conduction parameter measurement system 100 may connect to and communicate information over the network 103.

The server 105 is configured to process information. For example, the server 105 may receive vibration information of the subject 102 from the sensing apparatus 101, extract a hemodynamic related signal from the vibration information, and further process the hemodynamic related signal to obtain a pulse wave propagation parameter of the subject 102. In some embodiments, the server 105 may be a single server or a group of servers. The server farm may be clustered or distributed (i.e., the server 105 may be a distributed system). In some embodiments, the server 105 may be local or remote. For example, the server 105 may access data stored in the storage device 107, the sensing device 101, and/or the output device 109 via the network 103. For another example, the server 105 may be directly connected to the sensing device 101, the storage device 107, and/or the output device 109 for data storage. In some embodiments, the server 105 may also be deployed on a cloud platform, which may include, but is not limited to, a public cloud, a private cloud, a hybrid cloud, and the like. In some embodiments, the server 105 may be implemented on the computing device 400 shown in FIG. 4.

The storage device 107 is configured to store data and instructions. In some embodiments, the storage device 107 may include, but is not limited to, random access memory, read only memory, programmable read only memory, and the like. The storage device 107 may be a device that stores information by an electric energy method, a magnetic energy method, an optical method, or the like, such as a hard disk, a flexible disk, a core memory, a CD, a DVD, or the like. The above mentioned storage devices are only examples, and the storage device used by the storage apparatus 107 is not limited thereto. The storage device 107 may store vibration information of the subject 102 acquired by the sensing device 101, and may also store data processed by the server 105 on the vibration information, such as vital sign information (respiration rate, heart rate) of the subject 102. In some embodiments, the storage 107 may be an integral part of the server 105.

The output device 109 is configured to output data. In some embodiments, the output device 109 can output the vital sign signals generated after processing by the server 105, and the output mode includes, but is not limited to, one or more of a graphical display, a digital display, a voice broadcast, a braille display, and the like. The output device 109 may be one or more of a display, a cell phone, a tablet, a projector, a wearable device (watch, headset, glasses, etc.), a braille display, and the like. In some embodiments, the output device 109 may display vital sign signals (e.g., respiration rate, heart rate, etc.) of the subject 102 in real-time, and in other embodiments, the output device 109 may display a report in non-real-time, the report being a measurement of the subject 102 over a predetermined period of time, such as a heart rate per minute monitoring and a respiration rate per minute monitoring of the user during a sleep session. In some embodiments, the output device 109 may also output the warning prompt in a manner including, but not limited to, an audible alarm, a vibratory alarm, a visual display alarm, and the like. For example, the subject 102 may be a monitored patient, the output device 109 may be a display screen in a nurse station, the results displayed by the output device 109 may be a real-time heart rate, a real-time respiration rate, and the like, and when the heart rate and respiration rate are abnormal (e.g., exceed a threshold value or change greatly within a preset time period), the output device 109 may generate an alarm sound to prompt a medical staff, and the medical staff may rescue the patient in time, and the like. In other embodiments, the output devices 109 may be communication devices (e.g., mobile phones) carried by doctors, when the vital signs of the subject 102 are abnormal, one or more output devices 109 carried by one or more doctors may receive the warning information, and the warning information may be pushed according to the distance between the terminal device and the subject 102.

It should be understood that the application scenarios of the system and method of the present application are only examples or embodiments of the present application, and it is obvious for those skilled in the art that the present application can also be applied to other similar scenarios according to the drawings without any creative effort. The pulse wave conduction parameter measuring system 100 can be used in a home scenario, the sensing device 100 can be placed on a common home bed, when the subject 102 (e.g., elderly elder, people with cardiovascular disease, people in post-operative rehabilitation period) is in a sleep state at night, the sensing device 101 can continuously or in a predetermined or required manner obtain vibration information of the subject, and then transmit the vibration information of the subject (which can be transmitted in real time or can be transmitted to the cloud server 105 for processing at a predetermined time, such as the next morning, to the cloud server 105, the cloud server 105 can transmit the processed information (e.g., heart rate per minute, respiratory rate per minute, and aorta PWV) to the terminal 109, the terminal 109 can be a computer of a family doctor of the subject 102, and the family doctor can evaluate the physical condition of the subject 102 according to the processed information of the subject 102, Rehabilitation situations, etc.

It should be noted that the above-mentioned description is only a specific embodiment of the present application and should not be considered as the only embodiment. It will be apparent to persons skilled in the relevant art(s) that various modifications and changes in form and detail can be made therein without departing from the principles and arrangements of the invention, but the invention is not to be limited thereto. In some embodiments, the server 105, the storage 107 and the output 109 may be implemented as one device and implement the respective functions. For example, the pulse wave conduction parameter measuring system 100 may include a sensing device and a computer. The sensing device may be directly connected to a computer through a cable or may be connected to a computer through a network, and the computer may implement all functions of the server 105, the storage device 107, and the output device 109, and perform functions of data processing, storage, display, and the like. In other embodiments, the pulse wave conductance parameter measuring system 100 may include a sensing device and an integrated circuit integrated with the sensing device (e.g., integrated in a mat), the integrated circuit being connected to a display screen for performing the functions of the server 105 and the storage device 107, and the display screen serving as the output device 109 for performing the functions of data processing, storage, and display.

Fig. 2 is a schematic diagram illustrating the principle of generation of pulse waves. As shown in fig. 2, the left ventricle 201 is connected to the aorta 203 via the aortic valve 205. After the left ventricle 201 contracts to a certain pressure value, the Aortic Valve 205 is opened (AVO), blood is injected into the aorta 203 from the left ventricle 201, and since the blood vessel is an elastic tube, the blood expands the wall of the aorta when injected into the aorta, and the pulse propagates along the wall of the aorta to form a pulse wave 207. Hemodynamics (Hemodynmics) studies on the mechanics of blood flowing in the cardiovascular system, and takes the deformation and flow of blood and blood vessels as the study objects. The generation and transmission of pulse waves are related to blood flow and vascular deformation, and belong to the subjects of hemodynamic research. The velocity of the pulse wave 207 traveling along the aorta is related to the vascular elasticity of the aorta 203, and thus the degree of vascular stiffness can be estimated by the pulse wave velocity PWV.

FIG. 3 is a schematic diagram of the principle of measurement of aortic pulse wave conduction parameters. As shown in fig. 3, the aorta may be divided into ascending aorta, aortic arch and descending aorta, wherein the ascending aorta starts from the aortic orifice of the left ventricle and runs obliquely to the aortic arch towards the right anterior upper side, the aortic arch is provided with brachiocephalic artery, left common carotid artery and left subclavian artery, and the brachiocephalic artery is divided into right common carotid artery and right subclavian artery behind the right sternoclavian joint. The aortic arch is connected with ascending aorta, the arch is bent to the left rear direction at the rear of the sternum stem, and the arch moves to the left rear direction to the lower edge of the fourth thoracic vertebra body to move as descending aorta. The descending aorta is the longest segment of the aorta and is divided into the left and right common iliac arteries at the fourth lumbar vertebra. It can be seen that the pulse wave of the aorta section starts from the aorta starting point 301 and is conducted to the aorta and the left and right common iliac artery bifurcation 303 along the aorta, so the distance between the aorta starting point 301 and the aorta and the left and right common iliac artery bifurcation 303 along the aorta path is taken as the aorta pulse wave conduction distance, the time when the pulse wave is conducted from the point 301 to the point 303 is taken as the aorta pulse wave conduction time, and the ratio of the aorta pulse wave conduction distance to the conduction time is taken as the aorta pulse wave conduction velocity (aotic PWV, aofv).

FIG. 4 is a block diagram of a computing device 400 according to some embodiments of the present application. In some embodiments, the server 105, storage 107, and/or output 109 of fig. 1 may be implemented on the computing device 400. For example, the server 105 may be implemented on the computing device 400 and configured to perform the functions of the server 105 described herein. In some embodiments, the computing device 400 may be a dedicated computer, and for ease of description, only one server is depicted in fig. 1, and it will be understood by those of ordinary skill in the art that the computing functions associated with pulse wave conduction parameter measurement may also be implemented on multiple similarly functioning computing devices to distribute the computational load.

Computing device 400 may include a communication port 401, a processor (CPU) 403, a memory 405, and a bus 407. The communication port 401 is configured to exchange data with other devices through a network. The processor 403 is configured to perform data processing. The memory 405 is configured to store data and instructions, and the memory 405 may be various forms of memory such as a read only memory ROM, a random access memory RAM, a hard Disk, and the like. Bus 407 is configured to communicate data internally to computing device 400. In some embodiments, the computing device 400 may also include an input-output port 409, the input-output port 409 configured to support data input and output. For example, other personnel may input data to the computing device 400 through the input/output port 409 using an input device (e.g., a keyboard). The computing device 400 may also output data through the input-output port 409 to an output device such as a display or the like.

It should be understood that only one processor 403 is described herein for ease of description, it should be understood that the computing device 400 may include multiple processors, and that operations or methods performed by one processor 403 may be performed by multiple processors, either jointly or separately. For example, one processor 403 described herein may perform steps a and B, it being understood that steps a and B may be performed jointly or separately by multiple processors, such as a first processor performing step a and a second processor performing step B, or a first processor and a second processor performing step a and step B together.

FIG. 5 is a schematic diagram of a fiber optic sensing device 500 according to some embodiments of the present application. As shown in fig. 5, the optical fiber sensing device 500 is a strain sensor, when an external force is applied to the optical fiber sensing device 500, for example, when the optical fiber sensing device 500 is placed under a lying human body, when a subject is in a resting state, the human body may vibrate due to respiration, heartbeat, etc., the human body may vibrate to cause bending of the optical fiber 501, and the optical fiber bending may change parameters of light passing through the optical fiber, for example, light intensity. The change in light intensity can be processed to characterize body vibration of the human body.

The fiber optic sensing device 500 may include an optical fiber 501, a mesh layer 503, an upper cover 507, and a lower cover 505. Wherein one end of the optical fiber 501 is connected to a light source 509, the light source 509 may be an LED light source, the light source 509 is connected to a light source driver 511, and the light source driver 511 is configured to control the switching and energy level of the light source. The other end of the optical fiber 501 is connected to a receiver 513, the receiver 513 is configured to receive the optical signal transmitted through the optical fiber 501, the receiver 513 is connected to an amplifier 515, the amplifier 515 is connected to an analog-to-digital converter 517, and the analog-to-digital converter 517 can perform analog-to-digital conversion on the received optical signal to convert the received optical signal into a digital signal. The light source driver 511 and the analog-to-digital converter 517 are connected to the control processing module 519. The control processing module 519 is configured to perform signal control and signal processing, for example, the control processing module 519 may control the light source driver 511 to operate to drive the light source 509 to emit light, and the control processing module 519 may further receive data from the analog-to-digital converter 517, process the data to meet the requirements of various wireless or wired network data transmission, and transmit the data to other devices, such as the server 105, the storage device 107, and/or the output device 109 in fig. 1, through a wireless or wired network. The control processing module 519 can also control the sampling rate of the analog-to-digital converter 517 to have different sampling rates according to different requirements. In some embodiments, the light source driver 511, the receiver 513, the amplifier 515, the analog-to-digital converter 517, and the control processing module 519 may be implemented in combination as one module to perform all functions.

The optical fiber 501 may be a multimode optical fiber and may be a single mode optical fiber. The arrangement of the optical fibers may be of different shapes, such as a serpentine configuration, as shown at 501 in FIG. 5. In some embodiments, the arrangement of the optical fibers 501 may also be a U-shaped structure. The arrangement of the optical fibers 501 may also be a ring-like structure in some embodiments formed from a plurality of equally sized rings arranged with one optical fiber substantially in a plane, as shown at 521, wherein each ring within the ring-like structure overlaps and is laterally offset from an adjacent ring. Each fiber loop may form a substantially parallelogram-shaped structure (e.g., rectangle, square, etc.) with rounded edges, without sharp bends. In some embodiments, the looped fiber structure may comprise a circular or elliptical structure. In other embodiments, the ring-like structure may also be formed into an irregular shape without sharp bends.

The mesh layer 503 is composed of any suitable material having a repeating pattern of through-holes, and in some embodiments the mesh is composed of interwoven fibers, such as polymeric, natural, composite, or other fibers. When the optical fiber sensing device 500 is placed under the body of a subject, the subject applies an external force to the optical fiber sensing device 500, and the mesh layer 503 can disperse the external force that would otherwise be applied to a certain action point on the optical fiber and distribute the external force to the optical fiber around the action point. The optical fiber 501 is slightly bent, so that parameters (such as light intensity) of light transmitted by the optical fiber 501 are changed, and the receiver 513 can receive the changed light, and the control processing module 519 processes and determines the light change amount. The bending amount of the optical fiber 510 under the application of the external force depends on the external force, the diameter of the optical fiber, the diameter of the mesh fiber and the size of the mesh opening, and by setting different parameter combinations of the diameter of the optical fiber, the diameter of the mesh fiber and the size of the mesh opening, the bending amount of the optical fiber is different when the external force is applied, so that the optical fiber sensing device 500 has different sensitivities to the external force.

The upper cover 507 and the lower cover 505 may be made of a silicone material, and are configured to surround the optical fibers 501 and the mesh layer 503, so as to protect the optical fibers 501, and also to disperse an external force so that the external force is dispersed along a force application point. The top cover 507, the optical fibers 501, the mesh layer 503 and the bottom cover 505 may be integrally bonded, for example, by using a silicone adhesive, so that the optical fiber sensing device 500 forms a piece of sensing mat. The width and/or length of the sensor mat may vary depending on the arrangement of the optical fibers, and when a ring-shaped arrangement is used, the width of the sensor mat may be 6cm or other suitable width above 6cm, such as 8cm, 10cm, 13cm or 15 cm. The length of the sensor mat may vary depending on different usage scenarios, for example, for persons with a size in the normal range, the length of the sensor mat may be between 30cm and 80cm, for example 50cm, or other suitable dimensions, wherein a length of 45cm may be suitable for most persons. In some embodiments, the sensor mat may have a thickness of 1mm to 50mm, and preferably, a thickness of 3 mm. In some embodiments, the width and length of the sensor mat may be other dimensions, and different sensor sizes may be selected for different test subjects, for example, the test subjects may be grouped by age, height, and weight, with different groups corresponding to different sensor sizes. In some embodiments, when the optical fiber is in a U-shaped configuration, the width of the sensor mat may also be less than 6cm, for example, 1cm, 2cm, or 4 cm.

In some embodiments, the optical fiber sensing device 500 may further include an outer casing (not shown in fig. 5) that encloses the upper cover 507, the mesh layer 503, the optical fibers 501, and the lower cover 505, and the outer casing may be made of a waterproof and oil-proof material, such as a hard plastic. In other embodiments, the fiber sensing device 500 may further have a supporting structure (not shown in fig. 5), the supporting structure may be a rigid structure, such as cardboard, hard plastic board, wood board, etc., and the supporting structure may be disposed between the optical fiber 501 and the lower cover 505 to provide support for the optical fiber 501, and when an external force is applied on the optical fiber 501, the supporting structure may make the deformation of the optical fiber layer rebound faster and rebound time shorter, so that the optical fiber layer can capture a signal with a higher frequency.

FIG. 6 is a schematic illustration of a position of a sensing device according to some embodiments of the present application. As shown in fig. 6, sensing device 600 may include, but is not limited to, a fiber optic sensor 601 and a fiber optic sensor 603. In some embodiments, the fiber optic sensor 601 and the fiber optic sensor 603 may take the structure of the fiber optic sensing device 500.

In order to clearly clarify the positions and the mutual relationship of the parts of the human body and the relationship between the placement position of the sensing device and the parts of the human body in the present application, a human anatomy coordinate system is introduced, the human standard body positions are divided into an upright position and a supine position, and taking the supine position as an example, as shown in fig. 6, the X axis is a central transverse axis, the Y axis is a central sagittal axis, the Z axis is a central vertical axis, and the origin O is located at the midpoint of the upper edge of the phalanx joint, wherein the YZ plane is a central sagittal plane, which divides the human body into a left part and a right part, the XZ plane is a central coronal plane, which divides the human body into a front part and a rear part, and the XY plane is an origin transverse plane, which divides the human body into an upper part and a lower part. The anterior, posterior, superior, inferior, left, and right portions of the human body described in this application are described with reference to anatomical coordinates.

In some embodiments, the fiber optic sensor 601 may be placed under a posterior region of the body corresponding to the aortic origin of the subject 102, approximately under a dorsal body surface region corresponding to the fourth thoracic vertebral body of the human body. The fiber optic sensor 603 may be placed under the posterior region of the body of subject 102 where the aorta corresponds to the bifurcation of the left and right common iliac arteries, approximately under the dorsal body surface region corresponding to the fourth lumbar body of the human body. The lengths and widths of the

optical fiber sensors

601 and 603 can be selected according to actual requirements, for example, the lengths (along the X axis) can be 30cm to 80cm, the widths (along the Y axis) can be 1cm to 20cm, or other suitable dimensions according to different measurement objects and/or different application scenarios. In some embodiments, the fiber optic sensor 601 and the fiber optic sensor 603 are two separate sensors, and the placement positions of the two sensors can be adjusted manually, for example, the length of the aortic segment can be different due to different heights of different subjects, so the separation distance between the fiber optic sensor 601 and the fiber optic sensor 603 can be adjusted according to the heights of the subjects. In some embodiments, the sensing device 600 may further include a body for the subject to lie on, for example, the body may be a mat, the mat includes an upper cover and a lower cover, the upper cover and the lower cover are integrally attached, the mat may cover the optical fiber sensor 601 and the optical fiber sensor 603 in a space formed by the upper cover and the lower cover, and fix the positions of the optical fiber sensor 601 and the optical fiber sensor 603, wherein the interval between the optical fiber sensor 601 and the optical fiber sensor 603 may be preset according to actual requirements, for example, may be 20cm to 80cm, or may be another suitable distance. The shape and size of the sensing device 600 can be selected according to actual requirements, for example, the sensing device 600 can be a quadrilateral, a circle or other suitable shape. The sensing device 600 can be set to different sizes according to the height of the general crowd, for example, the size suitable for the crowd with the height of 155cm-160cm is 40cm, and set to be S, and the size suitable for the crowd with the height of 161cm-170cm can be increased by a certain distance on the basis of the S, for example, 3 cm. In other embodiments, the

fiber optic sensors

601 and 603 are housed inside a mat, where the position of either fiber optic sensor may be fixed (e.g., the fiber optic sensor 601 is fixed), and a living space may be provided inside the mat so that the position of the other fiber optic sensor (e.g., the fiber optic sensor 603) may be adjusted. For example, a sliding track is provided on the inside of the mat, the optical fiber sensor 603 is provided on the track, a control device is provided on the outside of the mat such that an operator can control the movement of the optical fiber sensor 603 via the control device, for example, the control device is a handle, the operator can manually control the movement of the optical fiber sensor 603, and if the control device is a switch, the optical fiber sensor 603 automatically moves toward or away from the optical fiber sensor 601 at a preset speed when the control device is in an on state, and the optical fiber sensor 603 becomes in a rest state when the control device is in an off state. Therein, the mat exterior may also be provided with scale markings, for example along the sliding track, so that the operator may directly read the distance separation between the fiber sensor 601 and the fiber sensor 603.

It should be understood that the application scenarios of the apparatus, system, and method of the present application are merely some examples or embodiments of the present application, and it will be apparent to those of ordinary skill in the art that the present application can also be applied to other similar scenarios according to the drawings without inventive effort. For example, the sensor device 101 may be applied to other scenarios without being limited to the form of the optical fiber sensor device 500 and the sensor device 600.

Fig. 7 is a flow chart of a method of pulse wave conduction parameter measurement according to some embodiments of the present application. In some embodiments, the method 700 may be implemented by the pulse wave conduction parameter measurement system 100 shown in fig. 1. For example, the method 700 may be stored in the storage 107 as a set of instructions and executed by the server 105, which server 105 may implement on the computing device 400.

At step 711, the processor 403 may obtain first vibration information of the supine subject from a first fiber optic sensor configured to be placed under a back region corresponding to a fourth thoracic vertebral body of the supine subject. In some embodiments, the supine subject may be a hospital patient or a caretaker, etc., lying in a supine position on the sensing device 600. The first fiber optic sensor may be the fiber optic sensor 601 in the sensing device 600, with the fiber optic sensor 601 positioned under the back region corresponding to the origin of the aorta of a supine subject, approximately under the back region corresponding to the fourth thoracic vertebral body. The first vibration information of the supine subject may include: the human body vibration information caused by respiration, the human body vibration information caused by cardiac contraction and relaxation, the human body vibration information caused by vascular deformation and the body movement information of the human body. The human body vibration caused by the systolic relaxation can include the human body vibration caused by the systolic relaxation and the human body vibration caused by the blood flow caused by the systolic relaxation, for example, the human body vibration caused by the blood impact on the aortic arch caused by the cardiac ejection. The human body vibration caused by the blood vessel deformation can be human body vibration caused by the conduction of the pulse wave along the blood vessel, wherein the pulse wave is formed by the expansion of the aorta wall caused by the blood ejection of the heart. The body movement information of the human body can comprise leg bending, leg lifting, turning over, shaking and the like. Specifically, when a human body breathes, the whole body, particularly a body part mainly including a thoracic cavity and an abdominal cavity, can be driven to vibrate rhythmically, the systolic and diastolic of the human body can also drive the whole body, particularly the body around the heart, to vibrate, the aortic arch can be impacted by blood at the moment when the left ventricle ejects blood to the aorta, the heart itself and the large blood vessel part connected with the heart as a whole can also move in a series, the vibration of the body part far away from the heart can be weaker, the pulse wave can be transmitted along the blood vessel to cause the vibration of the body part where the blood vessel is located, and the thinner the blood vessel and the farther the centrifugal heart are, the weaker the vibration of the body at the position can be. Therefore, when the sensor is located under different positions of the human body, the vibration information obtained by the sensor is the human body vibration information detected at the position, and the human body vibration information obtained when the positions are different is also different. The aorta is the thickest artery of the human body, starts from the left ventricle and is located in the abdominal cavity region of the thoracic cavity, so when the optical fiber sensor 601 is placed under the back region corresponding to the fourth thoracic vertebral body of the subject, the human body vibration information can be fully or partially acquired and the first vibration information can be generated due to the fact that the optical fiber sensor is located near the heart. As shown in fig. 8, a curve 821 is a waveform diagram of the first vibration information of the subject acquired by the optical fiber sensor 601 placed under the back region corresponding to the fourth thoracic vertebral body of the subject according to an embodiment of the present application, wherein the horizontal axis represents time, and the vertical axis represents the first vibration information of the subject after normalization processing, and is dimensionless.

At step 713, the processor 403 may obtain second vibration information of the supine subject from a second fiber optic sensor configured to be positioned under a lumbar region corresponding to a fourth lumbar vertebra of the supine subject. In some embodiments, the second fiber optic sensor may be fiber optic sensor 603 in sensing apparatus 600, with fiber optic sensor 603 being positioned below the lumbar location of the supine subject's descending aorta corresponding to the bifurcation of the left and right common iliac arteries, approximately below the lumbar region corresponding to the fourth lumbar vertebral body. Since the optical fiber sensor 603 is located at the end of the aorta of the subject and belongs to the abdominal cavity, the second vibration information obtained by the optical fiber sensor may include human body vibration caused by respiration, human body vibration caused by systole and diastole, and vibration caused by propagation of pulse wave along blood vessels. As shown in fig. 8, a curve 823 is a waveform diagram of second vibration information of a subject acquired by one optical fiber sensor 603 placed under a lumbar region corresponding to a fourth lumbar vertebra of the subject according to an embodiment of the present application, wherein the horizontal axis represents time, and the vertical axis represents the second vibration information of the subject after normalization processing, and is dimensionless.

At step 715, processor 403 may generate first hemodynamic-related information based on the first vibration information and generate second hemodynamic-related information based on the second vibration information. Hemodynamics (hemodynamics) is the mechanics of blood flowing in the cardiovascular system, and is the object of study on the deformation and flow of blood and blood vessels. "hemodynamic-related information" as described herein refers to any hemodynamic-related information, and may include, but is not limited to, one or more of information related to blood flow production (e.g., systolic relaxation of the heart resulting in ejection of blood), information related to blood flow (e.g., cardiac output, left ventricular ejection of blood impinging on the aortic arch), information related to blood flow pressure (e.g., systolic arterial pressure, diastolic arterial pressure, mean arterial pressure), and information related to blood vessels (e.g., vascular elasticity). The pulse wave conduction parameters, such as pulse wave conduction velocity, are related not only to the elasticity of blood vessels but also to the contraction and relaxation of the heart, the impact of the left ventricular ejection blood on the aortic arch, and therefore the measurement of the pulse wave conduction parameters involves the acquisition of hemodynamic related information. In some related documents, a series of periodic movements of a human body caused by the beating of the heart are represented by a Ballistocardiogram (BCG) signal, and in the human body vibration information acquired by the vibration sensitive sensor described in the present application, the human body vibration caused by the systolic and diastolic blood pressure can also be represented as the BCG signal. The hemodynamic related information described herein includes BCG signals. In some embodiments, the first hemodynamic-related information to be generated by processor 403 may include vibration caused by blood impacting the aortic arch when the left ventricular ejection and vibration information caused by vascular deformation (i.e., vibration caused by propagation of a pulse wave along a blood vessel) for the first vibration information acquired by fiber-optic sensor 601 in step 711. In the second vibration information obtained by the fiber sensor 603 in step 713, the second hemodynamic-related information to be generated by the processor 403 may include vibrations caused by propagation of the pulse wave along the blood vessel. As shown in fig. 8, a curve 825 is a time domain waveform of the first hemodynamic-related information generated by the processor 403 based on the first vibration information shown by the curve 821, a curve 827 is a time domain waveform of the second hemodynamic-related information generated by the processor 403 based on the second vibration information shown by the curve 823, and the horizontal axis represents time.

In some embodiments, the processor 403 may perform a series of processes on the acquired first and second vibration information to generate first and second hemodynamic-related information. The first vibration information and/or the second vibration information include various sub-vibration information (vibration caused by respiration, vibration caused by cardiac contraction, and vibration caused by vascular deformation), and the processor 403 may perform filtering processing of different frequency bands for different sub-vibration information. For example, the filtering frequency band of the respiration-induced vibration information may be set to be 1Hz or lower by the processor 403, the filtering method adopted by the processor 403 may include, but is not limited to, one or more of low-pass filtering, band-pass filtering, iir (infinite Impulse response) filtering, fir (finite Impulse response) filtering, wavelet filtering, zero-phase bidirectional filtering, polynomial fitting smoothing filtering, and at least one filtering process may be performed on the first vibration information and/or the second vibration information. If the vibration information carries a power frequency interference signal, a power frequency filter can be designed to filter power frequency noise. The processor 403 may perform filtering processing on the vibration information in the time domain or in the frequency domain. The processor 403 may further scale the filtered and denoised first/second vibration information according to the dynamic range of the signal to obtain a first/second hemodynamic-related signal.

At step 717, processor 403 may determine an aortic valve open time of the supine subject based on the first hemodynamic-related information and determine a pulse wave arrival time of the supine subject based on the second hemodynamic-related information. The first hemodynamic-related information may include vibration caused by impact of blood flow on the aortic arch when the left ventricle ejects blood, and vibration caused by propagation of pulse waves along blood vessels. In the heart cycle, the aortic valve is opened, the left ventricle emits blood, the moment when the blood enters the aorta is considered as the generation time point of the pulse wave, at the moment, the blood flow emitted by the left ventricle can impact the aortic arch, the heart and the connected large blood vessel part thereof generate a series of motions as a whole, and the body motion of the human body is caused to generate displacement. Due to the periodic contraction and relaxation of the heart, the displacement of the human body is also periodically changed, the vibration information can be transmitted through bones, muscles and the like of the human body, and the vibration information can be captured by the first optical fiber sensor which is arranged below the back area corresponding to the fourth thoracic vertebral body of the supine object. Because the time delay between the event that the aortic valve is opened and the event that the sensor captures the corresponding body vibration information is usually small, about within 10ms, the time delay can be selected to be ignored in the subsequent pulse wave conduction parameter measurement, that is, the time that the sensor captures the body vibration information caused by the opening of the aortic valve is taken as the aortic valve opening time, and a correction coefficient can be selected to be endowed to the actually measured aortic valve opening time for correction. The pulse wave is conducted along the blood vessel, and the vibration is also conducted along the blood vessel to cause the vibration of the human body, so that after the pulse wave is conducted to a certain position on the blood vessel, the vibration sensitive sensor at the body position of the blood vessel can capture the vibration information, and the second optical fiber sensor placed below the corresponding waist area of the fourth lumbar vertebra of the supine subject can capture the vibration information of the pulse wave conducted to the tail end of the aorta section (namely the bifurcation of the descending aorta and the left and right common iliac arteries). Similarly, the time delay between the pulse wave arrival time and the time when the second optical fiber sensor captures the corresponding body vibration information is small, the time delay can be selected to be ignored in the subsequent pulse wave conduction parameter measurement, namely the time when the sensor captures the body vibration information caused by the fact that the pulse wave arrives at the tail end of the aortic segment is used as the pulse wave arrival time, and a correction coefficient can be selected to be given to the actually measured pulse wave arrival time for correction.

In some embodiments, processor 403 may perform the following operations to determine an aortic valve open time of the supine subject based on the first hemodynamic-related information. As shown in fig. 8, a curve 825 is a time domain waveform of the first hemodynamic-related information, and the processor 403 may perform a second order differential operation on the curve 825 to obtain a curve 829. For the waveform map of 829, the processor 403 may perform a feature search to determine aortic valve opening feature points. Features in the feature search may include, but are not limited to, peaks, troughs, wave widths, wave amplitudes, maxima, minima, and the like. In some embodiments, the feature search for the curve 829 may employ a peak search, each period is used as a search range, a highest peak searched in one period is used as an aortic valve opening feature point, and a corresponding time is an aortic valve opening time. As shown by curve 829 in fig. 8, point 820 is the aortic valve opening characteristic point in the first complete cardiac cycle. In other embodiments, the processor 403 may also directly perform a feature search on the curve 825 to determine an aortic valve opening feature point, for example, with a cardiac cycle as a search interval, first search to obtain a J peak with a highest peak, then search in a time range before a time corresponding to the J peak, search to obtain an minimum value (AVO peak), and use the minimum value as the aortic valve opening feature point, where the corresponding time is the aortic valve opening time.

In some embodiments, processor 403 may perform the following operations to determine a pulse wave arrival time of the supine subject based on the second hemodynamic-related information. As shown in fig. 8, the curve 827 is a time domain waveform of the second hemodynamic-related information, and the processor 403 can perform a second order differential operation on the curve 827 to obtain a curve 831. For the waveform map of 831, the processor 403 may perform a feature search to determine pulse wave arrival feature points. The features in the feature search may include, but are not limited to, peaks, troughs, wave widths, amplitudes, maxima, minima, and the like. In some embodiments, the feature search for the curve 831 may employ a peak search, each cycle is used as a search range, a highest peak searched in a cycle is used as a pulse wave arrival feature point, and a corresponding time is a pulse wave arrival time. As shown by curve 831 in fig. 8, point 822 is the pulse wave arrival characteristic point in the first complete cardiac cycle.

In some embodiments, processor 403 may obtain information equivalent to performing a second order differential operation by other substantially equivalent digital signal processing methods, such as smoothing filtering using polynomial fitting.

In some embodiments, the first vibration information and the second vibration information of the supine subject are continuously obtained, and there may be a difference between the data waveform of one or some cardiac cycles and the data waveform of other cardiac cycles, and the aortic valve opening characteristic point and the pulse wave arrival characteristic point in the cardiac cycle may not be the respective highest peaks, and may be submerged, and the data of the cardiac cycle may be discarded.

In some embodiments, processor 403 may receive user input from one or more input devices to determine the aortic valve opening time and pulse wave arrival time of the supine subject. For example, the external input parameter may be input to the processing device 400 by a healthcare worker using an input device (e.g., mouse, keyboard) through the input-output port 409. Medical personnel are trained with the ability to determine characteristic points from the waveform of the vibration signal. For example, for the curve 825, the medical staff may manually perform waveform analysis, first select a highest peak in a cardiac cycle, then search for a waveform minimum value in the same cycle range before the time corresponding to the highest peak, mark the waveform minimum value as an aortic valve opening feature point, and perform calibration by using an input device, for example, select the feature point by using a mouse, so that the processor 403 may determine the input of the medical staff as the aortic valve opening feature point and automatically obtain the time corresponding to the aortic valve opening feature point as the aortic valve opening time.

At step 719, processor 403 may determine an aortic pulse transit time of the supine subject based on the aortic valve opening time and the pulse wave arrival time. In some embodiments, the processor 403 may take the difference between the aortic valve open time and the pulse wave arrival time (pulse wave arrival time minus aortic valve open time) in any one cardiac cycle as the aortic pulse transit time. In some embodiments, the processor 403 may select a plurality of cardiac cycles, for example 20 cardiac cycles, calculate the aortic pulse transit times (i.e., PTT1, PTT2 … PTT20) in each cardiac cycle, and then average the aortic pulse transit times. In some embodiments, the processor 403 may select a fixed duration, such as 60 seconds, calculate the pulse transit time for each cardiac cycle within that time (i.e., PTT1, PTT2 …), and average it to determine the pulse transit time. In other embodiments, the processor 403 may also automatically reject data with pulse transit times that are not within a reasonable range and take the average of the remaining other data as the pulse transit time. In other embodiments, the processor 403 may also calculate the pulse transit times for all cycles collected during the test and average them as the pulse transit time.

In step 721, the processor 403 may obtain the distance between the first optical fiber sensor and the second optical fiber sensor along the height direction of the human body as the aortic pulse wave propagation distance of the supine subject, and determine the aortic pulse wave propagation velocity based on the aortic pulse wave propagation distance and the aortic pulse wave propagation time. In some embodiments, the first and second fibre-optic sensors are separate devices, the spacing between which may be manually adjusted to accommodate test subjects of different heights. The aorta pulse wave conduction distance at this moment can adopt artifical survey, for example medical personnel utilize range finding instruments such as tape measure, ruler, line of taking the scale to measure the distance of first optical fiber sensor and second optical fiber sensor along human height direction as pulse wave conduction distance. In some embodiments, the separation between the first fiber sensor and the second fiber sensor may be fixed, and the distance between the two may be transmitted to the processor 403 as a fixed parameter at system initialization. In some embodiments, the processor 403 may directly use the obtained distance between the first optical fiber sensor and the second optical fiber sensor along the height direction of the human body as the aortic pulse wave propagation distance. In other embodiments, the processor 403 may correct the acquired distance between the first optical fiber sensor and the second optical fiber sensor along the height direction of the human body, for example, give a correction coefficient, and may add a constant, for example, to the correction coefficient, and then use the correction coefficient as the aortic pulse wave propagation distance.

In other embodiments, the aortic pulse transit distance may be estimated according to a formula, for example, the height, weight, age, etc. of the subject may be input via an input device of the system 100, and the processor 403 may estimate the pulse transit distance of the subject according to the formula. For example, the processor 403 may estimate the aortic length, i.e. the aortic pulse wave propagation distance, of the test subject according to the following formula:

l ═ a + b (age) + c · (height) + d · (weight)

Wherein L represents the length of the aorta in centimeters, the age in years, the height in centimeters and the weight in kilograms. a represents a constant, b, c and d are coefficients, and fitting calculation can be performed according to the actual manually measured aorta length and the age, height, weight and the like of each tester to obtain the values of a, b, c and d, for example, in some embodiments, a can be assigned to-21.3, b can be assigned to 0.18, c can be assigned to 0.32, and d can be assigned to 0.08.

At step 723, the processor 403 may send at least one of the pulse transit time and the pulse transit velocity to one or more output devices. For example, the pulse transit time may be sent to the output device 109 in the system 100 for output. The output means 109 may be a display device, such as a mobile phone, which may display the pulse wave transit time graphically or in text. The output device 109 may be a printing device that prints the measurement report of the pulse wave propagation parameter. The output device 109 may be a voice broadcasting device that outputs the pulse wave propagation parameter by voice. In some embodiments, the processor 403 may send the pulse transit time and/or the pulse transit velocity to an output device over a wireless network, for example, the output device is a cell phone. In other embodiments, the processor 403 may send the pulse transit time and/or the pulse transit velocity directly to an output device via a cable, for example, the output device is a display, which may be connected to the sensing device via the cable.

In some embodiments, the steps of method 700 may be performed sequentially, and in other embodiments, the steps of method 700 may be performed out of order, or simultaneously. For example, after step 719 determines that the pulse wave transit time is completed based on the aortic valve opening time and the pulse wave arrival time, step 721 obtains the distance between the first optical fiber sensor and the second optical fiber sensor in the height direction of the human body as the aortic pulse transit distance of the supine subject, determines the aortic pulse wave transit velocity based on the aortic pulse transit distance and the aortic pulse wave transit time, and step 723 sends the pulse wave transit time to one or more output devices, which may be performed simultaneously. Additionally, in some embodiments, method 700 may remove one or more steps therefrom, e.g., step 721 and/or step 723 may not be performed, and in other embodiments, other operations may be added to method 700, without departing from the spirit and scope of the subject matter described herein.

FIG. 9 is a schematic view of a sensing device according to some embodiments of the present application. As shown in fig. 9, sensing device 900 may include, but is not limited to, a body 901, a first fiber optic sensor 903, a second fiber optic sensor set 905, and a positioning indicator 907.

In order to clearly illustrate the positional relationship of the first fiber-optic sensor 903, the second fiber-optic sensor group 905, and the positioning indicator 907 with respect to each other and the body 901 in the present application, corresponding coordinates are introduced here into the description. Sensing device 900 may be placed on a bed or directly on a floor, so that the Z-axis represents the direction perpendicular to the ground, the direction away from the ground is the positive direction, the XY plane is parallel to the horizontal, the X-axis is along the width of sensing device 900, the Y-axis is along the length of sensing device 900, and the origin O is located at the midpoint of an end point edge of sensing device 900. The YZ plane divides the sensing device 900 into left and right portions. In the Y-axis direction, a relatively vertical direction may be indicated, for example, a boundary between the back region and the waist region may be referred to as a lower edge of the back region and an upper edge of the waist region.

The body 901 may include an upper cover 911 and a lower cover 913, the upper cover 911 and the lower cover 913 enclose the first optical fiber sensor 903 and the second optical fiber sensor group 905 therein, and the upper cover 911 and the lower cover 913 may be integrally attached by a suture or an adhesive. The body 901 may be sequentially divided into a back region, a waist region, and a lower limb region in the Y-axis direction. The size of the body 901 can be selected according to the size and height of the test subject, for example, the length (along the Y-axis) can be 190cm, the width can be 85cm, and the size is suitable for most people, and other suitable sizes can be adopted, without limitation. Accordingly, the width (along the X-axis) of the back region, waist region and lower limb region of the body may also be selected to test the size and height of the subject, for example, the back region may be 30cm wide and the waist region may be 50cm wide for most people, or any other suitable size, without limitation. When a subject is supine on the sensing device 900 in a supine position, the back, waist and lower limbs are located in the back region, waist region and lower limb region in that order, and the upper limbs are located in the back region and waist region. The upper cover 911 and the lower cover 913 may be made of various materials, such as leather, cotton, etc.

The first fiber sensor 903 is located in the back region. The first optical fiber sensor 903 may be an optical fiber sensor and may employ a structure as shown in fig. 5. In some embodiments, as shown in fig. 9, the length (along the X axis) of the first fiber sensor 903 may be selected according to the test object, for example, 50cm for most people, and the width (along the Y axis) may be selected according to the test object, for example, 30cm for most people, and other suitable dimensions, which are not limited herein. When a subject lies supine on the sensing device 900, the left and right body portions are generally symmetrical along the Y-axis, the upper edges of the shoulders are aligned with the upper edge of the back region, the back is located within the back region of the body, the legs are naturally closed, the hands are naturally hung on both sides of the body, and at this time, the back of the subject is located on the first optical fiber sensor 903. The first optical fiber sensor 903 is configured to acquire first vibration information of the object.

The second fiber sensor group 905 may include two or more fiber sensors, and the two or more fiber sensors (905-1,905-2, … 905-n) may be arranged in the waist region in sequence along the Y-axis direction. The Y-axis direction may also be referred to as the longitudinal axis direction of the body, and the X-axis direction is the transverse axis direction of the body. Two or more fiber optic sensors may be employed in the configuration shown in fig. 5. In some embodiments, as shown in fig. 9, the 6 optical fiber sensors may be arranged in sequence along the Y axis, and each optical fiber sensor may have a width (along the Y axis) of 1cm to 20cm and a length (along the X axis) of 10cm to 80cm, and may have other suitable sizes, which are not limited herein. In other embodiments, the number of the optical fiber sensors in the second optical fiber sensor group 905 may be varied, and when the height of the test subject is particularly high, the number of the optical fiber sensors may be increased, for example, to 8 or more, so that when the test subject lies on the back, the last optical fiber sensor in the second optical fiber sensor group 905 arranged along the Y-axis direction may be located below the hip bone of the test subject. When a subject lies supine on the sensing device 900, the left and right body portions are generally symmetrical along the Y-axis, the upper edges of the shoulders are aligned with the upper edge of the back region, the legs are naturally closed, and the hands are naturally positioned on either side of the body, with the waist and hips of the subject located within the waist region of the sensing device. The second optical fiber sensor group 905 is configured to acquire second vibration information of the subject, and the second vibration information may include human body vibration information detected by various sensors at the waist.

The positioning indicator 907 is configured to indicate and assist the test subject in quickly lying on the preferred measurement position. As shown in fig. 9, the alignment indicator 907 is a shoulder stop that may be fixedly disposed on the cover 911 of the body 901, e.g., integrally joined to the cover 911 by stitching. In some embodiments, the shoulder stopper may be detachably connected to the upper cap 911, for example, by a hook and loop fastener connected to the upper cap 911. In other embodiments, the positioning indicator 907 may include two or more shoulder stops, as shown in fig. 10, which is a top view of three sensing devices, wherein the positioning indicator of the sensing device 1001 may include two shoulder stops 1011 disposed on a side of and adjacent to a dividing line of the back region, the left and right shoulder stops may be distributed on both sides of the Y-axis, spaced apart such that the neck is positioned between the left and right shoulder stops when the subject lies down, and the left and right shoulders abut the left and right shoulder stops, respectively, such that the shoulders of the subject are aligned with the upper edge of the back region. In some embodiments, the spacing between the left shoulder stop and the right shoulder stop may be 130 mm. In some embodiments, the interval between the left shoulder stopper and the right shoulder stopper may be varied, and different intervals may be selected according to objects of different statures, for example, when the shoulder stopper is connected with the upper cover 911 using the hook and loop fastener, the size of the round hair of the hook and loop fastener on the upper cover 911 may be larger than the size of the thorn hair on the shoulder stopper, so that a measurement assistant person (e.g., a medical care person) may adjust the position of the shoulder stopper according to the stature of the object.

In some embodiments, the positioning indicator 907 may include one or more foot blocks, e.g., two foot blocks, disposed in the lower limb region for the subject's foot or lower leg to rest against when the subject is lying on the sensing device, such that the subject's legs are straightened and put into a closed position. In some embodiments, the foot stopper may be fixedly disposed on the upper cover 911 of the body 901, for example, by being integrally connected to the upper cover 911 by sewing. In some embodiments, the foot stopper may also be detachably connected to the upper cover 911, for example, by a hook and loop fastener connected to the upper cover 911. In some embodiments, the left foot block and the right foot block may be spaced 300mm apart. As shown in FIG. 10, sensing device 1001 may include two foot stops 1013. In some embodiments, the shape of the shoulder and foot stops may vary, as may the color, and the shape and color are not limited to this application. The positioning indicator of the sensing device 1003, such as that shown in fig. 10, includes two shoulder stops 1031 and two foot stops 1033.

In some embodiments, the positioning indicator 907 may include a neck pillow disposed on a side adjacent to and near the line of demarcation with the back region and centered (near the Y-axis). The neck pillow may rest the neck when the subject is lying down, such that the subject's shoulders are aligned with the upper edge of the back region. In some embodiments, the neck pillow may be fixedly disposed on the upper cover 911 of the body 901, for example, by being integrally connected to the upper cover 911 by sewing. In some embodiments, the neck pillow may be detachably connected to the upper cover 911, for example, by a hook and loop fastener connected to the upper cover 911. In some embodiments, the neck pillow may be cylindrical or approximately cylindrical in shape to conform to the physiological curvature of the neck of a human. As shown in fig. 10, the positioning indicator 1051 of the sensing device 1005 is one embodiment of a neck pillow.

In some embodiments, sensing device 900 may also include a support plate 909. The support plate 909 is configured to provide support for the first fiber sensor 903 and the second fiber sensor set 905, may be configured to be placed under the first fiber sensor 903 and the second fiber sensor set 905, and is encased within the body 901 together with the first fiber sensor 903 and the second fiber sensor set 905. The support plate 909 may be of a rigid construction such as wood, PVC, or the like.

FIG. 11 is a schematic view of a positioning indicator according to other embodiments of the present application. In some embodiments, the cover 911 of the body 901 of FIG. 9 can be a three-dimensional structure, for example, as shown in FIG. 11, the cover of the sensing device 1100 can include a body contour recessed structure 1101. When the subject is supine on the upper cover, the body may be placed on the body contour depression 1101. The body contour depression 1101 is disposed about the Y-axis of the sensing device and is symmetrically distributed along the Y-axis such that when a subject is placed supine in the body contour 1101, the head of the subject is positioned on the back of the sensing device 1100, the back is positioned on the back of the sensing device 1100, the waist is positioned on the waist of the sensing device 1100, and the lower limbs are positioned on the lower limbs of the sensing device 1100. In some embodiments, the sensing device may have different sizes according to the height of the subject, and accordingly, the body contour 1101 may vary according to the height and body type of the subject. For example, the size suitable for the crowd with the height of 155cm-160cm is set as S, the size suitable for the crowd with the height of 161cm-170cm can be increased by a certain size on the basis of the S, such as 2-5 cm. In some embodiments, the cover 911 of the body 901 in fig. 9 may have a planar structure, and in this case, the contour line with obvious identification may be used to represent the human body contour, for example, when the cover 911 is white, the human body contour may be identified by a red line.

It should be noted that the above-mentioned description is only a specific embodiment of the present application and should not be considered as the only embodiment. It will be apparent to persons skilled in the relevant art(s) that, upon attaining an understanding of the present disclosure and principles, may effect numerous modifications and changes in form and detail without departing from the principles and structures of the disclosure, which, however, may be practiced within the scope of the appended claims.

Claims

1. A pulse wave conduction parameter measurement method, comprising:

acquiring first vibration information of a supine object from a first optical fiber sensor, wherein the first optical fiber sensor is placed under a back region corresponding to a fourth thoracic vertebral body of the supine object;

acquiring second vibration information of the supine object from a second optical fiber sensor, wherein the second optical fiber sensor is arranged below a waist region corresponding to a fourth lumbar vertebra of the supine object;

generating first hemodynamic-related information based on the first vibration information, and generating second hemodynamic-related information based on the second vibration information;

determining an aortic valve opening time of the supine subject based on the first hemodynamic-related information, and determining a pulse wave arrival time of the supine subject based on the second hemodynamic-related information; and

determining an aortic pulse wave transit time of the supine subject based on the aortic valve opening time and the pulse wave arrival time;

determining an aortic valve open time of the supine subject based on the first hemodynamic-related information, further comprising:

performing a second order differential operation on the first hemodynamic-related information;

performing feature search on a waveform diagram of the first hemodynamic related information after second-order differential operation to determine a highest peak in a cardiac cycle; and

determining an aortic valve open time of the supine subject based on the highest peak;

the first hemodynamic related information comprises vibration information caused by impact of blood on an aortic arch when left ventricular ejection of blood and vibration information caused by deformation of blood vessels; the second hemodynamic-related information includes vibrations caused by propagation of a pulse wave along a blood vessel.

2. The method of claim 1, wherein the first or second fiber optic sensor comprises:

an optical fiber arranged in a substantially planar configuration;

a light source coupled to one end of the one or more optical fibers;

a receiver coupled to the other end of the one optical fiber for sensing a change in light intensity through the optical fiber; and a mesh layer composed of meshes provided with openings, wherein the mesh layer is in contact with the surface of the optical fiber.

3. The method of claim 1, wherein generating first hemodynamic-related information based on the first vibration information and generating second hemodynamic-related information based on the second vibration information, further comprises: filtering and scaling the first vibration information and the second vibration information respectively to generate the first hemodynamically-related information and the second hemodynamically-related information.

4. The method of claim 1, further comprising:

acquiring the distance between the first optical fiber sensor and the second optical fiber sensor along the height direction of the human body and generating an aortic pulse wave transmission distance; and

determining an aortic pulse wave velocity based on the aortic pulse wave propagation distance and the aortic pulse wave propagation time.

5. The method of claim 4, further comprising:

sending at least one of the aortic pulse transit time and the aortic pulse transit velocity to one or more output devices.

6. A pulse wave conduction parameter measuring system, comprising:

the first optical fiber sensor is arranged in the area near a fourth thoracic vertebral body of the supine object and is used for acquiring first vibration information of the supine object;

the second optical fiber sensor is arranged in the vicinity of a fourth lumbar vertebra body of the supine object and is used for acquiring second vibration information of the supine object;

one or more processors; and

one or more memories storing instructions that, when executed by the one or more processors, implement the method of any of claims 1 and 3-5.

7. The system of claim 6, wherein the first and second fiber optic sensors each comprise:

an optical fiber arranged in a substantially planar configuration;

a light source coupled to one end of the one or more optical fibers;

8. Pulse wave parameter measuring device for use in the pulse wave parameter measuring method according to any one of claims 1 to 5, comprising:

the supine subject lying bed comprises a body, a first fixing part and a second fixing part, wherein the body is used for lying a supine subject, comprises an upper cover and a lower cover, and comprises a back area and a waist area;

the first optical fiber sensor is arranged in the back area of the body and used for acquiring first vibration information of the supine object; and

the second optical fiber sensor group is arranged in the waist area of the body and used for acquiring second vibration information of the supine object;

the upper cover and the lower cover coat the first optical fiber sensor and the second optical fiber sensor group.

9. The apparatus of claim 8, further comprising a neck pillow disposed on the upper cover for resting the neck of the supine subject to secure the supine subject in a measuring position.

10. The apparatus of claim 8 further comprising a shoulder stop disposed on the upper cover for abutment by shoulders of the supine subject to secure the supine subject in a measuring position.

11. The apparatus of claim 8, wherein the body further comprises a lower limb region, the apparatus further comprising a foot stop disposed on the lower limb region of the upper cover for abutting a foot or lower leg of the supine subject to secure the supine subject in a measuring position.

12. The apparatus of claim 8 wherein said body cover is a three-dimensional structure comprising a body contour depression to secure said supine subject in a measuring position.

13. The apparatus of claim 8, wherein two or more fiber optic sensors of the second fiber optic sensor group are aligned along the body longitudinal axis.

14. The apparatus of claim 8, wherein the fiber optic sensor comprises:

an optical fiber arranged in a substantially planar configuration;

a light source coupled to one end of the one or more optical fibers;