Portable cardiovascular health detection system

Abstract

The embodiment of the utility model discloses a portable cardiovascular health detection system which comprises an upper computer, a light source, an on-chip integrated Doppler vibration meter, an optical circulator and an integrated circuit board. The Doppler vibration meter divides an output light beam of the light source into a signal light beam and a reference light beam, the signal light beam is transmitted to a to-be-measured pulse through the optical circulator, and the optical circulator is used for receiving the signal light beam reflected by the to-be-measured pulse and coupling the signal light beam into the Doppler vibration meter. The signal light beam and the reference light beam generate an interference signal in the Doppler vibration meter, the interference signal is transmitted to the upper computer through the integrated circuit board, and then the cardiovascular health condition of a testee is analyzed by the upper computer according to the interference signal. By the adoption of the technical scheme, the cardiovascular health condition of the testee can be accurately analyzed through non-contact detection on the pulse of the testee, and the system has the advantages of being portable, non-invasive, capable of achieving real-time detection and extremely low in cost.

Description

Technical Field

[0001] This utility model relates to the field of optical technology, and in particular to a portable cardiovascular health detection system. Background Technology

[0002] Cardiovascular diseases such as coronary heart disease and stroke are among the major threats to human health, with extremely high morbidity and mortality rates. A key pathophysiological basis for cardiovascular diseases is atherosclerosis, which leads to stiffening and loss of elasticity of the arterial walls. Arterial stiffness is a long-term, gradual process, and timely detection and control are crucial for preventing and managing its progression.

[0003] Currently, pulse wave velocity (PWV) is widely recognized as the most important biological marker for assessing arterial stiffness. Non-invasive cardiovascular health monitoring technology, with its advantages of non-invasiveness, high precision, good repeatability, and ease of operation, can safely, accurately, and conveniently assess the level of systemic arterial stiffness, providing more reliable technical support for the early prevention and accurate diagnosis of cardiovascular diseases. However, existing desktop devices are often bulky, heavy, and difficult to carry, which significantly limits their application in clinical and home health monitoring scenarios. Utility Model Content

[0004] This utility model provides a portable cardiovascular health detection system. The system can accurately analyze the cardiovascular health status of the subject by non-contact detection of the pulse, and has the advantages of being portable, non-invasive and real-time.

[0005] According to one aspect of this utility model, a portable cardiovascular health monitoring system is provided, including a host computer, a light source, an on-chip integrated Doppler vibration meter, an optical circulator, and an integrated circuit board. The light source and the integrated circuit board are both electrically connected to the host computer. The output end of the light source is coupled to the input end of the Doppler vibration meter, and the integrated circuit board is connected to the output end of the Doppler vibration meter.

[0006] The host computer controls the light source to emit light. The output beam of the light source is incident on the Doppler vibration meter and is divided into a signal beam and a reference beam. The signal beam is output from the Doppler vibration meter and incident on the first end of the optical circulator. It is output from the second end of the optical circulator to the pulse to be measured. The signal beam returned by the pulse to be measured is incident from the second end of the optical circulator, exits from the third end of the optical circulator and is coupled into the Doppler vibration meter. The signal beam and the reference beam interfere within the Doppler vibration meter. The interference signal is transmitted to the host computer by the integrated circuit board. The host computer analyzes the cardiovascular health status of the subject.

[0007] Optionally, the portable cardiovascular health monitoring system further includes a converging lens disposed at the second end of the optical circulator.

[0008] Optionally, the converging lens is a zoom lens.

[0009] Optionally, the Doppler vibrometer includes a substrate and a first beam splitter, an IQ mixer, a first photodetector, and a second photodetector located on one side of the substrate;

[0010] The input terminal of the first beam splitter is connected to the output terminal of the light source, the first output terminal of the first beam splitter is connected to the first terminal of the optical circulator, the third terminal of the optical circulator is connected to the first input terminal of the IQ mixer, the second output terminal of the first beam splitter is connected to the second input terminal of the IQ mixer, the first and second output terminals of the IQ mixer are connected to the first photodetector, and the third and fourth output terminals are connected to the second photodetector.

[0011] Optionally, the Doppler vibration meter includes a first fiber array and a second fiber array. A first end of the first fiber array is connected to a first output end of the first beam splitter, a second end of the first fiber array is connected to a first end of the optical circulator, a first end of the second fiber array is connected to a third end of the optical circulator, and a second end of the second fiber array is connected to a first input end of the IQ mixer.

[0012] Optionally, both the first photodetector and the second photodetector are balanced photodetectors.

[0013] Optionally, the splitting ratio of the first beam splitter is adjustable.

[0014] Optionally, the Doppler vibration meter is integrated onto a silicon photonic chip.

[0015] Optionally, the size of the silicon photonic chip is less than or equal to 3mm × 3mm × 0.7mm.

[0016] Optionally, the portable cardiovascular health monitoring system further includes a second beam splitter, which has one input terminal and n output terminals. The number of Doppler vibration meters is n. The input terminal of the second beam splitter is connected to the output terminal of the light source, and the n output terminals of the second beam splitter are respectively connected to the input terminals of the n Doppler vibration meters.

[0017] Where n is an integer greater than or equal to 2.

[0018] The portable cardiovascular health monitoring system provided in this embodiment of the invention controls the output beam of the light source to be incident on a Doppler vibration meter via an electrical connection between a host computer and a light source. The Doppler vibration meter divides the output beam of the light source into a signal beam and a reference beam. The signal beam is transmitted to the pulse to be measured through an optical circulator. The optical circulator receives the signal beam reflected back from the pulse and couples it into the Doppler vibration meter, effectively reducing signal loss and interference during propagation and improving the accuracy of pulse detection. The signal beam and the reference beam interfere in the Doppler vibration meter, generating an interference signal. This interference signal is transmitted to the host computer via an integrated circuit board. The host computer then analyzes the interference signal to determine the cardiovascular health status of the subject. This non-contact pulse detection system accurately analyzes the subject's cardiovascular health status and offers advantages such as portability, non-invasiveness, real-time processing, and extremely low cost.

[0019] It should be understood that the description in this section is not intended to identify key or essential features of the embodiments of this utility model, nor is it intended to limit the scope of this utility model. Other features of this utility model will become readily apparent from the following description. Attached Figure Description

[0020] To more clearly illustrate the technical solutions in the embodiments of this utility model, the drawings used in the description of the embodiments will be briefly introduced below. Obviously, the drawings described below are only some embodiments of this utility model. For those skilled in the art, other drawings can be obtained based on these drawings without creative effort.

[0021] Figure 1 A structural block diagram of a portable cardiovascular health monitoring system provided in this embodiment of the present invention;

[0022] Figure 2 A structural block diagram of another portable cardiovascular health monitoring system provided in this embodiment of the present invention;

[0023] Figure 3 A partial structural block diagram of a portable cardiovascular health monitoring system provided in this embodiment of the present invention;

[0024] Figure 4 A partial structural block diagram of another portable cardiovascular health monitoring system provided in this embodiment of the present invention;

[0025] Figure 5 A partial structural block diagram of another portable cardiovascular health monitoring system provided in this embodiment of the present invention;

[0026] Figure 6A partial structural block diagram of another portable cardiovascular health monitoring system provided in this embodiment of the present invention;

[0027] Figure 7 A data graph of a pulse simulation experiment using a portable cardiovascular health monitoring system is provided as an embodiment of this utility model;

[0028] Figure 8 Another data graph of a pulse simulation experiment using a portable cardiovascular health monitoring system is provided as an embodiment of this utility model;

[0029] Figure 9 This invention provides a data graph of pulse measurement using a portable cardiovascular health monitoring system with dual channels, as part of an embodiment of the present invention. Detailed Implementation

[0030] To enable those skilled in the art to better understand the present invention, the technical solutions of the present invention will be clearly and completely described below with reference to the accompanying drawings of the embodiments. Obviously, the described embodiments are only some embodiments of the present invention, and not all embodiments. Based on the embodiments of the present invention, all other embodiments obtained by those skilled in the art without creative effort should fall within the protection scope of the present invention.

[0031] It should be noted that the terms "first," "second," etc., in the specification, claims, and accompanying drawings of this utility model are used to distinguish similar objects and are not necessarily used to describe a specific order or sequence. It should be understood that such data can be interchanged where appropriate so that the embodiments of the utility model described herein can be implemented in orders other than those illustrated or described herein. Furthermore, the terms "comprising" and "having," and any variations thereof, are intended to cover non-exclusive inclusion; for example, a process, method, system, product, or apparatus that comprises a series of steps or units is not necessarily limited to those steps or units explicitly listed, but may include other steps or units not explicitly listed or inherent to such processes, methods, products, or apparatus.

[0032] PWV describes the speed at which a pulsed pressure wave propagates from the aortic root along the arterial wall to other parts of the body, directly reflecting the rigidity of the arterial wall. Numerous authoritative studies have shown that higher PWV levels predict more severe atherosclerosis and a greater risk of cardiovascular disease. Research has found that for every 1 m / s increase in aortic PWV, the risk of stroke increases by 40%. Therefore, accurate assessment of PWV is crucial for early screening and precise diagnosis of cardiovascular disease.

[0033] However, traditional PWV measurement methods have many serious drawbacks:

[0034] 1. The operation is complex, the measurement error is large, and the repeatability is poor, such as the commonly used carotid-femoral artery PWV measurement;

[0035] 2. It can only reflect the condition of local arteries, such as percutaneous arterial compliance measurement;

[0036] 3. The measurement process poses potential risks to the patient;

[0037] 4. Novel non-invasive methods, such as cuff blood pressure monitoring, still suffer from poor accuracy and repeatability.

[0038] The aforementioned shortcomings severely limit the value of traditional PWV measurement technology in clinical and widespread applications. Existing primitive PWV measurement methods all suffer from various deficiencies, causing numerous inconveniences in clinical applications. Therefore, there is an urgent need for a novel PWV measurement technology that can safely, accurately, and conveniently assess the level of arterial stiffness throughout the body, providing crucial evidence for the early screening and accurate diagnosis of cardiovascular diseases.

[0039] Figure 1 This utility model provides a structural block diagram of a portable cardiovascular health monitoring system, suitable for detecting the cardiovascular health status of subjects and predicting the probability of various cardiovascular diseases. (Reference) Figure 1 The portable cardiovascular health monitoring system 100 provided in this embodiment includes a host computer 1, a light source 2, an on-chip integrated Doppler vibration meter 3, an optical circulator 4, and an integrated circuit board 5. The light source 3 and the integrated circuit board 5 are both electrically connected to the host computer 1. The output terminal of the light source 3 is coupled to the input terminal of the Doppler vibration meter 3, and the integrated circuit board 5 is connected to the output terminal of the Doppler vibration meter 3. The host computer 1 controls the light source 2 to emit light, and the output beam of the light source 2 is incident on the Doppler vibration meter 3 and split into a signal beam and a reference beam. Figure 1 (Not shown), the signal beam is output from the Doppler vibration meter 3 and incident on the first end of the optical circulator 4. It is output from the second end of the optical circulator 4 to the pulse to be measured 6. The signal beam returned by the pulse to be measured 6 is incident from the second end of the optical circulator 4 and exits from the third end of the optical circulator 4 and is coupled into the Doppler vibration meter 3. The signal beam and the reference beam interfere within the Doppler vibration meter 3. The interference signal is transmitted to the host computer 1 by the integrated circuit board 5. The host computer 1 analyzes the cardiovascular health status of the subject.

[0040] Among them, the light source 2 can be a laser, and this embodiment of the utility model does not specifically limit it; the Doppler vibration meter 3 is a measuring instrument that uses the laser Doppler effect, interference and other principles to measure the vibration of objects. It has the advantages of long-distance measurement, non-contact, high spatial resolution, short measurement time, wide response bandwidth and high velocity resolution. It is widely used in modal characteristic analysis of models, quality inspection, online control, structural flaw detection, health and medical fields.

[0041] Specifically, the host computer 1 sends control commands to the light source 2 through a communication protocol. The control commands may include turning on the light source, turning off the light source, adjusting the light intensity, and changing the beam direction. The light source 2 outputs a beam according to the control commands and it is incident into the Doppler vibration meter 3. The Doppler vibration meter 3 splits the beam into two beams, namely a signal beam and a reference beam. The signal beam is output through the Doppler vibration meter 3 and incident into the first end of the optical circulator 4. The optical circulator 4 is a multi-port optical device with non-reciprocal characteristics. When a signal beam enters the optical circulator 4 from the first end, the signal beam is output from the second end of the optical circulator 4 to the pulse to be measured 6 along a specific path. The second end receives the signal beam reflected back from the pulse to be measured 6, and then continues to output the signal beam from the third end to the Doppler vibration meter 3 along a specific path inside the optical circulator 4. Due to the non-reciprocity, low insertion loss, high isolation and high return loss of the optical circulator 4, the signal beam can effectively reduce signal loss and interference during propagation, improve the accuracy of pulse detection, and accurately measure the minute vibrations of blood vessels with a sensitivity down to the nanometer level.

[0042] After the signal beam carrying the vibration information of the pulse to be measured 6 is coupled into the Doppler vibration meter 3, the signal beam and the reference beam converge and interfere in the Doppler vibration meter 3. The reference beam provides a stable reference frequency, thereby forming an interference signal and outputting it to the integrated circuit board 5. The frequency of the interference signal includes the frequency difference information between the signal beam and the reference beam (i.e., Doppler frequency shift). The integrated circuit board 5 amplifies and digitizes the interference signal and transmits the processed data to the host computer 1. The host computer 1 then integrates, filters, performs frequency domain analysis, and velocity analysis on the detection data, and provides various parameters of skin vibration at the pulse to be measured 6, thereby analyzing the cardiovascular health status of the subject.

[0043] For example, when the pulse to be measured 6 is the carotid artery, the host computer controls the light source 2 to output a light beam. The output light beam is split into two beams by the Doppler vibration meter 3, namely a signal beam and a reference beam. The signal beam is output by the Doppler vibration meter 3 and incident on the first end of the optical circulator 4. The signal beam is output from the second end of the optical circulator 4 to the carotid artery according to a specific path, and the second end receives the signal beam reflected back from the carotid artery. Then, inside the optical circulator 4, the signal beam continues to be output from the third end to the Doppler vibration meter according to a specific path. Instrument 3 couples a signal beam carrying carotid artery vibration information into a Doppler vibrometer 3. The signal beam and reference beam converge in the Doppler vibrometer 3 to generate an interference signal. The interference signal is amplified and digitized by an integrated circuit board 5, and the processed data is transmitted to a host computer 1. The host computer 1 then integrates, filters, performs frequency domain analysis, and velocity analysis on the detected carotid pulse wave data to measure the pulse wave velocity (PWV) between the heartbeat and the carotid artery (hcPWV), which can directly reflect the stiffness of the core arterial trunk, including the ascending aorta. Compared with the traditional femoral-carotid PWV (cfPWV), hcPWV can more accurately assess the degree of systemic atherosclerosis. Its measurement process is fully automated, with high data repeatability, and does not require multiple measurement devices, greatly simplifying the detection process.

[0044] The technical solution of this utility model embodiment involves an upper computer electrically connecting to a light source to control the output beam of the light source to be incident on a Doppler vibration meter. The Doppler vibration meter divides the output beam of the light source into a signal beam and a reference beam. The signal beam is transmitted to the pulse to be measured through an optical circulator. The optical circulator receives the signal beam reflected back from the pulse to be measured and couples it into the Doppler vibration meter, effectively reducing signal loss and interference during propagation and improving the accuracy of pulse detection. The signal beam and the reference beam interfere in the Doppler vibration meter, generating an interference signal. This interference signal is transmitted from the integrated circuit board to the upper computer, which then analyzes the interference signal to determine the cardiovascular health status of the subject. This non-contact pulse detection system accurately analyzes the cardiovascular health status of the subject. It offers advantages such as portability, non-invasiveness, high precision, good repeatability, and ease of operation. It can safely, accurately, and conveniently assess the level of systemic arterial stiffness, providing more reliable technical support for the early prevention and accurate diagnosis of cardiovascular diseases.

[0045] Figure 2 A structural block diagram of another portable cardiovascular health monitoring system provided in this embodiment of the present invention is shown below. Figure 2 Optionally, the portable cardiovascular health monitoring system also includes a converging lens 7, which is located at the second end of the optical circulator 4.

[0046] Among them, the converging lens 7 refers to a lens with positive refractive power, which enables incident light rays parallel to the principal axis to be focused at a point after passing through the converging lens.

[0047] Specifically, when the signal beam transmitted by the optical circulator 4 is emitted through the converging lens 7, the converging lens 7 can refocus the diverging signal beam, improve the concentration of the signal beam, reduce the insertion loss during transmission in the optical circulator 4, thereby enhancing the intensity and quality of the signal beam, making the imaging clearer and sharper, and achieving efficient transmission of the signal beam.

[0048] Optionally, the converging lens 7 is a zoom lens.

[0049] Specifically, the converging lens 7 is a zoom lens and is located at the second end of the optical circulator 4. Users can adjust the focal distance as needed to adapt to different detection conditions, more accurately control the transmission and focusing of the signal beam, and enhance the flexibility and reliability of the portable cardiovascular health detection system.

[0050] Figure 3 A partial structural block diagram of a portable cardiovascular health monitoring system provided in this embodiment of the present invention is shown in the reference diagram. Figure 3 Optionally, the Doppler vibration meter 3 includes a substrate and a first beam splitter 31, an IQ mixer 32, a first photodetector 33, and a second photodetector 34 located on one side of the substrate; the input end of the first beam splitter 31 is connected to the output end of the light source 2, the first output end of the first beam splitter 31 is connected to the first end of the optical circulator 4, the third end of the optical circulator 4 is connected to the first input end of the IQ mixer 32, the second output end of the first beam splitter 31 is connected to the second input end of the IQ mixer 32, the first and second output ends of the IQ mixer 32 are connected to the first photodetector 33, and the third and fourth output ends are connected to the second photodetector 34.

[0051] Specifically, refer to Figure 1 and Figure 3The Doppler vibration meter 3 includes a substrate and a first beam splitter 31, an I (In-phase) Q (Quadrature) mixer 32, a first photodetector 33, and a second photodetector 34 located on one side of the substrate. The substrate can be silicon dioxide. The input end of the first beam splitter 31 is connected to the output end of the light source 2 and is used to split the output beam of the light source 2 into a signal beam and a reference beam according to a specific beam splitting ratio. The signal beam is input to the first end of the optical circulator 4 through the first output end of the first beam splitter 31. The signal beam is output from the second end of the optical circulator 4 to the pulse to be measured 6 along a specific path. The second end receives the signal beam reflected back from the pulse to be measured 6. Then, inside the optical circulator 4, the signal beam continues to be output from the third end to the first input end of the IQ mixer 32 along a specific path. The reference beam is output to the second input end of the IQ mixer 32 through the second output end of the first beam splitter 31. The IQ mixer then mixes the input signal beam with the reference beam to generate four optical signals with different phases. The four optical signals are input to the first photodetector 33 and the second photodetector 34 through the first, second, third and fourth output ends of the IQ mixer 32 in a certain combination. The first photodetector 33 and the second photodetector 34 then generate two output signals: an in-phase (I) component and a quadrature (Q) component, which are used to detect the movement direction of the pulse to be measured. The Doppler vibration meter 3 collects the patient's pulse information by emitting a signal beam to the pulse point 6 to be measured and receiving the signal light reflected back from the pulse point 6. The measurement process is harmless to the patient and extremely safe.

[0052] Figure 4 A partial structural block diagram of another portable cardiovascular health monitoring system provided in this embodiment of the present invention is shown below. Figure 4 Optionally, the Doppler vibration meter 3 includes a first fiber array 9 and a second fiber array 10. The first end of the first fiber array 9 is connected to the first output end of the first beam splitter 31, the second end of the first fiber array 9 is connected to the first end of the optical circulator 4, the first end of the second fiber array 10 is connected to the third end of the optical circulator 4, and the second end of the second fiber array 10 is connected to the first input end of the IQ mixer 32.

[0053] Specifically, refer to Figure 1 and Figure 4The first end of the first fiber array 9 is connected to the first output end of the first beam splitter 31. The first fiber array 9 is used to transmit the signal beam received from the first beam splitter 31 to the first end of the optical circulator 4. The signal beam is output from the second end of the optical circulator 4 to the pulse to be measured 6 along a specific path, and the second end receives the signal beam reflected back from the pulse to be measured 6. Then, inside the optical circulator 4, the signal beam continues to be output from the third end to the first end of the second fiber array 10 along a specific path. The second fiber array 10 is used to transmit the signal beam received from the optical circulator 4 to the first input end of the IQ mixer 32. By setting the first fiber array 15 and the second fiber array 16, the beam can be transmitted in the optical fiber, reducing optical loss and helping to improve system performance.

[0054] Optionally, both the first photodetector 33 and the second photodetector 34 are balanced photodetectors.

[0055] Specifically, in the Doppler vibration meter 3, since the reference beam and the signal beam may be subject to similar environmental interference, and the balanced photodetector is usually designed with a differential structure, this structure can effectively suppress common-mode noise and effectively reduce the impact of these interferences on the measurement results, thereby improving the reliability and accuracy of the portable cardiovascular health detection system.

[0056] Optionally, the splitting ratio of the first beam splitter 31 is adjustable.

[0057] The first beam splitter 31 may be composed of two or more optical elements, such as a semi-reflective lens, a prism, etc. This embodiment of the present invention does not specifically limit this.

[0058] Specifically, an external circuit can drive the actuator (such as piezoelectric ceramic, electromagnet, resistor, etc.) in the first beam splitter 31 by applying different voltages, thereby changing the position or angle of the optical element. This change can alter the separation ratio of the incident beam, thereby adjusting the beam splitting ratio of the first beam splitter 31. This not only improves the flexibility of measurement but also allows users to quickly adjust the beam splitting ratio according to different detection conditions and rationally allocate the optical power of the signal beam and the reference beam.

[0059] Optionally, the Doppler vibration meter 3 is integrated onto a silicon photonic chip.

[0060] Specifically, the low cost of silicon photonics chips is mainly due to the following factors: Mature manufacturing processes: Silicon-based semiconductor manufacturing processes are very mature and widely used in the electronics industry. Utilizing existing semiconductor manufacturing infrastructure, silicon photonics chips can be mass-produced, reducing production costs. High integration: Silicon photonics chips can integrate multiple optical and electronic functions onto a single chip, reducing the number of required components and assembly steps, thereby lowering the overall system cost. Low material costs: Silicon is an abundant and inexpensive material. Compared to other optical materials (such as gallium arsenide or indium phosphide), silicon is much cheaper. This makes large-scale production of silicon photonics chips more economical. Mass production advantages: Silicon photonics chips can be mass-produced using mass production technologies in the semiconductor industry. This scale effect can significantly reduce the production cost per chip. Compatibility: Silicon photonics chips are compatible with existing CMOS manufacturing processes and can be seamlessly integrated with electronic circuits. This reduces the cost of developing new processes and equipment while improving production efficiency. Reduced packaging and assembly costs: By integrating more functions on the chip, the complexity and cost of packaging and assembly can be reduced. This helps to reduce the overall system manufacturing cost.

[0061] Optionally, the size of the silicon photonic chip is less than or equal to 3mm × 3mm × 0.7mm, which effectively reduces the product size and improves the portability of the portable cardiovascular health monitoring system.

[0062] Figure 5 A partial structural block diagram of another portable cardiovascular health monitoring system provided in this embodiment of the present invention; Figure 6 A partial structural block diagram of another portable cardiovascular health monitoring system provided in this embodiment of the present invention is shown below. Figure 5 Optionally, the portable cardiovascular health monitoring system also includes a second beam splitter 8, which has one input terminal and n output terminals. The number of Doppler vibration meters 3 is n. The input terminal of the second beam splitter 8 is connected to the output terminal of the light source 2, and the n output terminals of the second beam splitter 8 are respectively connected to the input terminals of the n Doppler vibration meters 3; where n is an integer greater than or equal to 2.

[0063] Specifically, the second beam splitter 8 is used to split the output beam of the light source 2 into n beams. The n beams are output to n Doppler vibration meters 3 through n output terminals, where n is an integer greater than or equal to 2. This provides multiple pulse measurement channels, enabling the simultaneous measurement of multiple pulses 6 to be measured, thereby improving the detection efficiency and accuracy of the portable cardiovascular health detection system.

[0064] Exemplary, reference Figure 6When n is 2, the portable cardiovascular health detection system includes a light source 2, a second beam splitter 8, a first Doppler vibration meter 31, a second Doppler vibration meter 32, a first optical circulator 41, a second optical circulator 42, and an integrated circuit board 5. The second beam splitter 8 includes one input end and two output ends. There are two Doppler vibration meters (including a first Doppler vibration meter 31 and a second Doppler vibration meter 32). The input end of the second beam splitter 8 is connected to the output end of the light source 2, and is used to split the output beam of the light source 2 into a first output beam and a second output beam according to a specific beam splitting ratio. The two output ends of the second beam splitter 8 are respectively connected to the input ends of the first Doppler vibration meter 31 and the second Doppler vibration meter 32. The first output beam and the second output beam enter the first Doppler vibration meter 31 and the second Doppler vibration meter 32 respectively. The first output beam detects the pulse information at the first pulse to be measured 61 through the first Doppler vibration meter 31 and the first optical circulator 41. The second output beam detects the pulse information at the second pulse to be measured 62 through the second Doppler vibration meter 32 and the second optical circulator 42, thereby realizing synchronous dual-channel pulse measurement. This method is convenient and fast, eliminates the need for multiple measurement devices, and greatly simplifies the measurement process.

[0065] Figure 7 A data graph of a pulse simulation experiment using a portable cardiovascular health monitoring system is provided as an embodiment of this utility model; Figure 8 This invention provides another data graph of a pulse simulation experiment using a portable cardiovascular health monitoring system, as an embodiment of the present invention; see reference. Figure 7 and Figure 8 A portable cardiovascular health monitoring system was used to measure a soft-controlled simulated pulse. After the reflected laser mixing signal was processed by an integrated analysis system, the 5Hz and 20Hz fluctuation frequencies of the simulated pulse could be accurately detected. The spectrum clearly showed the corresponding frequency peaks, and the fluctuation amplitude was at the micrometer level. The result (red) matched the true value (black dashed line) and was much lower than the pulse fluctuation amplitude at the millimeter level, which verified the measurement accuracy and performance stability of the portable cardiovascular health monitoring system.

[0066] Figure 9 A data graph of pulse measurement using a portable cardiovascular health monitoring system with dual channels is provided as an embodiment of this utility model; see reference 6 and Figure 9 When the first pulse to be measured (61) is the carotid artery and the second pulse to be measured (62) is the femoral artery, a portable cardiovascular health monitoring system with dual detection channels can simultaneously measure both the carotid and femoral arteries. The measurement results are as follows: Figure 9As shown, the pulse fluctuation characteristics of the subject's carotid artery (black curve) and femoral artery (red curve) are displayed (top curve statistics chart) and frequency domain analysis is performed (bottom curve statistics chart). Based on this, the subject's pulse wave velocity and heart rate can be calculated, and the subject's cardiovascular condition can be analyzed.

[0067] The specific embodiments described above do not constitute a limitation on the scope of protection of this utility model. Those skilled in the art should understand that various modifications, combinations, sub-combinations, and substitutions can be made according to design requirements and other factors. Any modifications, equivalent substitutions, and improvements made within the spirit and principles of this utility model should be included within the scope of protection of this utility model.

Claims

1. A portable cardiovascular health monitoring system, characterized in that, The system includes a host computer, a light source, an on-chip integrated Doppler vibration meter, an optical circulator, and an integrated circuit board. The light source and the integrated circuit board are both electrically connected to the host computer. The output terminal of the light source is coupled to the input terminal of the Doppler vibration meter, and the integrated circuit board is connected to the output terminal of the Doppler vibration meter. The host computer controls the light source to emit light. The output beam of the light source is incident on the Doppler vibration meter and is divided into a signal beam and a reference beam. The signal beam is output from the Doppler vibration meter and incident on the first end of the optical circulator. It is output from the second end of the optical circulator to the pulse to be measured. The signal beam returned by the pulse to be measured is incident from the second end of the optical circulator, exits from the third end of the optical circulator and is coupled into the Doppler vibration meter. The signal beam and the reference beam interfere within the Doppler vibration meter. The interference signal is transmitted to the host computer by the integrated circuit board. The host computer analyzes the cardiovascular health status of the subject.

2. The portable cardiovascular health monitoring system according to claim 1, characterized in that, It also includes a converging lens, which is disposed at the second end of the optical circulator.

3. The portable cardiovascular health monitoring system according to claim 2, characterized in that, The converging lens is a zoom lens.

4. The portable cardiovascular health monitoring system according to claim 1, characterized in that, The Doppler vibration meter includes a substrate and a first beam splitter, an IQ mixer, a first photodetector, and a second photodetector located on one side of the substrate. The input terminal of the first beam splitter is connected to the output terminal of the light source, the first output terminal of the first beam splitter is connected to the first terminal of the optical circulator, the third terminal of the optical circulator is connected to the first input terminal of the IQ mixer, the second output terminal of the first beam splitter is connected to the second input terminal of the IQ mixer, the first and second output terminals of the IQ mixer are connected to the first photodetector, and the third and fourth output terminals are connected to the second photodetector.

5. The portable cardiovascular health monitoring system according to claim 4, characterized in that, The Doppler vibration meter includes a first fiber array and a second fiber array. The first end of the first fiber array is connected to the first output end of the first beam splitter, the second end of the first fiber array is connected to the first end of the optical circulator, the first end of the second fiber array is connected to the third end of the optical circulator, and the second end of the second fiber array is connected to the first input end of the IQ mixer.

6. The portable cardiovascular health monitoring system according to claim 4, characterized in that, Both the first photodetector and the second photodetector are balanced photodetectors.

7. The portable cardiovascular health monitoring system according to claim 4, characterized in that, The splitting ratio of the first beam splitter is adjustable.

8. The portable cardiovascular health monitoring system according to claim 4, characterized in that, The Doppler vibration meter is integrated onto a silicon photonic chip.

9. The portable cardiovascular health monitoring system according to claim 8, characterized in that, The size of the silicon photonic chip is less than or equal to 3mm × 3mm × 0.7mm.

10. The portable cardiovascular health monitoring system according to claim 1, characterized in that, It also includes a second beam splitter, which has one input terminal and n output terminals. The number of Doppler vibration meters is n. The input terminal of the second beam splitter is connected to the output terminal of the light source, and the n output terminals of the second beam splitter are respectively connected to the input terminals of the n Doppler vibration meters. Where n is an integer greater than or equal to 2.

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