A patch type heart function evaluation device based on an ultrasonic and DCS fusion probe

Abstract

The utility model relates to a patch type heart function evaluation device based on ultrasonic and DCS fusion probe, the device is "patch type" structure design, and the lower part is flexible round base, and the central position has embeddedly installed heart function evaluation module. The lower surface of heart function evaluation module is provided with ultrasonic detection hole and DCS detection hole, and its upper part is provided with ultrasonic signal generator, near infrared laser generator, echo receptor, DCS signal feedback ware, skin temperature detector and data processing element, and the data processing element is provided with image generator, light spot generator and calculation processor. The device adopts probe fusion design and multimodal signal fusion detection technology, realizes the synchronous, real -time monitoring of lung water retention and core - surface temperature difference, thereby accurately quantifies "fluid retention - heat imbalance" coupling effect, and the device has simple structure, convenient to use, can realize real -time, accurate heart function evaluation, has good clinical application prospect.

Description

Technical Field

[0001] This utility model relates to the field of medical device technology, specifically to a patch-type cardiac function assessment device based on a fusion probe of ultrasound and DCS (diffusion-related spectroscopy). Background Technology

[0002] Heart failure (HF) has become a major cardiovascular disease threatening public health. Acute decompensation is the core cause of repeated hospitalizations for HF patients. Approximately 31% of patients require emergency admission due to delayed warnings, and the mortality rate during hospitalization exceeds 12%. The readmission rate within one year of discharge is about 45%, which seriously affects patients' quality of life and the efficiency of medical resource utilization.

[0003] Heart failure, as the end stage of various cardiovascular diseases, has different clinical characteristics at different stages of its course. In our long-term clinical observation, we have found that high-risk patients (especially those with hypoperfusion heart failure, such as cold-cold heart failure) often present with unbearable chest heat accompanied by a strong craving for cold drinks. This is mainly due to a significant increase in lung fluid volume and the inability to effectively dissipate heat, leading to heat accumulation (e.g., Figure 1 As shown in the diagram, the core pathological mechanism is the synergistic effect of abnormally increased pulmonary fluid volume (pulmonary fluid retention, ΔV↑) and thermal imbalance (core-surface temperature difference ΔT↑). On the one hand, during the decompensated stage of heart failure, the decreased cardiac pumping function leads to reduced skin blood flow, while pulmonary blood return is obstructed, causing pulmonary congestion and pulmonary fluid retention. On the other hand, sympathetic nerve excitation causes vasoconstriction in the skin, further reducing skin blood flow and lowering the skin surface temperature, which further exacerbates the core-surface temperature difference (ΔT↑). From the perspective of the dynamic balance of heat production and dissipation in the human body, the main site of heat dissipation is the skin. During heart failure, the increased lung fluid does not dissipate heat through the skin. Under normal cardiac function, the heat that this portion of lung fluid (ΔV) should dissipate, according to the thermodynamic formula, should be: Q = ρ·c·ΔV·ΔT (where ρ is the density of lung fluid, c is the specific heat capacity of lung fluid, and ΔT is the temperature difference between lung fluid and the surface). However, as heart failure worsens, this heat cannot be effectively dissipated, thus accumulating in the patient's chest. That is, the coupling effect of lung fluid retention (ΔV) and heat imbalance (ΔT) significantly amplifies the accumulation of heat in the pleural cavity (Q value ↑↑). By measuring the Q value, the cardiac function status and disease progression of heart failure patients can be accurately assessed.

[0004] However, existing cardiac function monitoring devices still have significant limitations in accurately identifying such high-risk conditions: (1) Single-dimensional monitoring devices (such as ReDs pulmonary edema monitor, CardioMEMS pulmonary artery pressure sensor, etc.) can only monitor single indicators such as fluid retention or pressure, and cannot capture the core pathological coupling mechanism of "fluid retention-heat imbalance" in the deterioration of heart failure, resulting in insufficient early warning sensitivity and difficulty for patients to obtain early intervention opportunities.

[0005] (2) Traditional biomarkers (such as BNP / NT-proBNP) are affected by complex physiological states in the body, and the detection values ​​fluctuate greatly. They have limited correlation with clinical symptoms and are difficult to monitor in real time. If the test is performed after the patient develops clinical symptoms, the early intervention period has been missed. Multi-parameter scoring systems (such as MAGGIC, EHMRG, etc.) rely on static parameter assessment and are difficult to dynamically reflect the evolution of heart failure. They generally have the problem of early warning lag.

[0006] In summary, current technologies cannot comprehensively, in real-time, and accurately monitor the dynamic coupling characteristics of "fluid retention-thermal imbalance" during the deterioration of heart failure, nor can they accurately and reliably assess the patient's cardiac function status at this time. This makes it difficult to identify high-risk patients in a timely manner, thus hindering the improvement of heart failure prognosis. Therefore, there is an urgent need to develop a novel cardiac function assessment device that can simultaneously monitor multi-dimensional pathological parameters and capture core pathological mechanisms to improve the accuracy and timeliness of heart failure prognostic assessment.

[0007] In previous research, the inventors proposed a "Heart Failure Prognostic Assessment Instrument and Method" (CN118948332A). This application primarily elucidated the working mechanism and internal module design of the heart failure prognostic assessment instrument. While it introduced the concept of a heart failure prognostic assessment instrument, it did not provide a specific structural design for the device. For example, it lacked detailed explanations of the specific patch structure design and probe integration scheme, resulting in insufficient operability and significant difficulties in practical application. Therefore, it is essential to provide a detailed and specific structural design for the device proposed in the above-mentioned solution, enabling it to be more conveniently used for clinical patient cardiac function assessment to meet actual clinical application needs. Utility Model Content

[0008] To address the aforementioned issues, this invention, based on clinical practice, designs a novel patch-type cardiac function assessment device using a fusion probe of ultrasound and DCS. This cardiac function assessment device has a simple structure, is easy to use, and can achieve real-time and accurate cardiac function assessment, showing promising clinical application prospects. Furthermore, no similar invention or utility model patent applications were found during the search.

[0009] In this novel device, we adopted a probe fusion design and multimodal signal fusion detection technology, and innovatively used ultrasound-guided near-infrared blood flow detection technology to achieve synchronous and real-time monitoring of pulmonary water retention (ΔV) and core-surface temperature difference (ΔT), thereby accurately quantifying the coupling effect of "fluid retention-heat imbalance" (i.e., heat accumulation in the pleural cavity, Q value), providing a precise and real-time solution for the assessment of cardiac function in patients with heart failure.

[0010] Figure 2The diagram shows the overall design architecture of this application. In this utility model device, we specifically integrate the ultrasound probe and the DCS probe into a "pattern-type" design as the core component of the device. This patch-type probe, combined with ultrasound guidance and near-infrared blood flow detection technology, can simultaneously measure multiple key parameters such as pulmonary water retention (ΔV), core-surface temperature difference (ΔT, in this scheme, refers to the difference between the temperature of the human lung region (pulmonary water) and the skin surface temperature), and heat accumulation in the pleural cavity (Q value). Based on the thermodynamic calculation formula Q=ρ·c·ΔV·ΔT (where ρ is the density of pulmonary water and c is the specific heat capacity of pulmonary water), the changes in ΔQ are monitored in real time, realizing multi-dimensional coupled analysis and deterioration warning of cardiac function in heart failure patients.

[0011] Specifically, this utility model provides a patch-type cardiac function assessment device based on an ultrasound and DCS fusion probe. The cardiac function assessment device has a "patch-type" structure design, with a flexible circular base 2 at the bottom, a surface sticker 1 covering the lower surface of the circular base 2, a cylindrical shell 4 at the top of the circular base 2, and a cardiac function assessment module 5 embedded in the center of the circular base 2. The lower surface of the cardiac function assessment module 5 is provided with an ultrasound detection hole 501 and a DCS detection hole 502, respectively. The upper part of the cardiac function assessment module 5 is respectively equipped with an ultrasound signal generator 503, a near-infrared laser generator 504, an echo sensor 505, a DCS signal feedback device 506, a skin temperature detector 507, and a data processing element 6. The data processing element 6 is equipped with an image generator 601, a spot generator 602, and a computing processor 603.

[0012] Furthermore, when using the cardiac function assessment device of this utility model, after peeling off the surface sticker 1, the circular base 2 is pasted onto the detection area of ​​the skin, so that the lower surface of the cardiac function assessment module 5 can make close contact with the skin surface.

[0013] Optionally, in the cardiac function assessment device of this utility model, a data transmission line 3 is also connected to the upper part of the cardiac function assessment module 5, and the detection data obtained by the cardiac function assessment module 5 is transmitted to an external control center through the data transmission line 3.

[0014] Optionally, in the cardiac function assessment device of this invention, the cardiac function assessment module 5 transmits the detection data to an external control center via Bluetooth or wireless connection.

[0015] Furthermore, in the cardiac function assessment device of this invention, the ultrasonic signal emitted by the ultrasonic signal generator 503 enters the patient's body (lung region) through the ultrasonic detection hole 501, the echo sensor 505 receives the echo signal of the human body to the ultrasonic signal, the image generator 601 generates an ultrasonic image based on the human body echo signal received by the echo sensor 505, and the calculation processor 603 determines the lung water volume of the target human body based on the ultrasonic image.

[0016] Furthermore, in the cardiac function assessment device of this invention, the near-infrared laser emitted by the near-infrared laser generator 504 enters the patient's body (lung region) through the DCS detection port 502. The DCS signal feedback unit 506 receives the human body's response signal to the near-infrared laser. The spot generator 602 calculates and generates a scattered spot using the human body's response signal to the near-infrared laser. The calculation processor 603 determines the blood flow index of the target area (lung) of the human body based on the scattered spot. Then, it calculates the movement rate of red blood cells in the blood through the light intensity autocorrelation function and calculates the core temperature (lung region temperature) of the target area of ​​the human body by combining the Brownian motion diffusion coefficient formula.

[0017] Furthermore, in the cardiac function assessment device of this invention, the skin temperature detector 507 detects the skin surface temperature in real time.

[0018] Furthermore, in the cardiac function assessment device of this utility model, the computing processor 603 is provided with an early warning management module, which includes the following structural units: (1) Threshold configuration protocol unit: Supports receiving external configuration parameters via Bluetooth / USB; (2) Rate of change algorithm unit: used to calculate the change in heat from Q within the time interval Δt. t-1 Change to Q t The rate of change, i.e., the rate of change r ΔQ = (Q t- Q t-1 ) / Δt; (3) Monitoring mode adaptive unit: When the concentration of biomarkers provided by the external system exceeds the preset concentration threshold, the short time window monitoring mode is automatically activated. The biomarkers include, but are not limited to, heart failure-related indicators such as BNP and NT-proBNP.

[0019] Furthermore, in the cardiac function assessment device of this invention, the early warning management module performs the following functions: a) Based on the lung water volume, temperature of the target area, and real-time skin surface temperature, calculate the lung water retention value and core-surface temperature difference. Then, using the thermodynamic formula Q=ρ·c·ΔV·ΔT, calculate the accumulated heat value Q in the pleural cavity in real time, and monitor the change in Q value within the time interval Δt (ΔQ=Qt- Q t-1 ); b) When the rate of change of ΔQ (ΔQ / Δt) exceeds the preset dynamic threshold, an early warning signal is generated; c) The preset dynamic threshold can be dynamically configured through an external system, and the configuration basis includes NYHA classification, baseline physiological parameters and historical data trends.

[0020] In addition, the early warning management module may also include: (1) Acute exacerbation dynamic threshold configuration unit (related to heart failure severity index); (2) Deteriorating trend machine learning analysis unit (adjustable window width); (3) Warning signal output interface.

[0021] Furthermore, the aforementioned early warning management module supports: (1) High sensitivity mode: Use a short time window (example: ≤3 minutes) to monitor the instantaneous change of ΔQ; (2) High specificity model: Use long window (example: 7-day sliding window) to analyze the cumulative increase in trend.

[0022] In summary, this invention, based on clinical practice, designs a patch-type cardiac function assessment device with a simple structure, low cost, and convenient use, based on a fusion probe of ultrasound and DCS. This device has the following technical features: (1) Multidimensional monitoring: Unlike traditional single-dimensional monitoring devices, this device can simultaneously monitor multiple key parameters such as pulmonary water retention (ΔV), core-surface temperature difference (ΔT), and pleural heat accumulation (Q value), thereby comprehensively reflecting the cardiac function status of heart failure patients and avoiding the problem of inaccurate assessment caused by a single monitoring dimension.

[0023] (2) Dynamic early warning: Through the configurable ΔQ change rate analysis engine and dynamic threshold comparator, a graded early warning signal is generated to provide real-time data support for clinical decision-making.

[0024] (3) Non-invasive detection: The combination of ultrasonic flexible patch and DCS probe realizes non-invasive detection, avoids the risks that may be caused by invasive operation, and also broadens the application scope of the device in different scenarios and populations.

[0025] (4) Multi-parameter coupled assessment: By measuring the heat that cannot be dissipated in the increase of lung water, the synergistic effect of lung water retention (ΔV) and heat imbalance (ΔT) is simultaneously quantified, breaking through the limitations of traditional single-parameter monitoring. It can more comprehensively assess the condition and pathological state evolution of heart failure patients, especially in the monitoring of high-risk pathological states, which has a more significant advantage. Attached Figure Description

[0026] To more clearly illustrate the technical solution of this utility model, the drawings used in the description of the embodiments are briefly introduced below. Obviously, the drawings described below are only for specific embodiments of this utility model. For those skilled in the art, other drawings can be obtained from the following drawings without creative effort.

[0027] Figure 1 A schematic diagram illustrating the pathophysiological mechanism of heat accumulation in the pleural cavity of patients with heart failure.

[0028] Figure 2 This is the overall design architecture diagram of this application.

[0029] Figure 3 This is a bottom view of the cardiac function assessment device of this utility model.

[0030] Figure 4 This is a bottom view of the central function assessment module of the cardiac function assessment device of this utility model.

[0031] Figure 5 This is a top cross-sectional view of the cardiac function assessment device of this utility model.

[0032] Figure 6 This is a top view of the data processing element in the cardiac function assessment device of this utility model.

[0033] Figure 7 This is a flowchart of the early warning management module in the cardiac function assessment device of this utility model.

[0034] Figure label: 1-Surface sticker, 2-Circular base, 3-Data transmission cable, 4-Outer shell, 5-Cardiac function assessment module, 501-Ultrasound probe hole, 502-DCS probe hole, 503-Ultrasound signal generator, 504-Near-infrared laser generator, 505-Echo sensor, 506-DCS signal feedback device, 507-Skin temperature detector, 6-Data processing element, 601-Image generator, 602-Spot generator, 603-Computational processor. Detailed Implementation

[0035] The technical solution of this utility model is clearly and completely described below through specific examples. Obviously, the described embodiments are only some data processing element embodiments of this utility model, and not all embodiments. Those skilled in the art can easily understand other advantages of this utility model from the content disclosed in this specification. This utility model can also be implemented or applied through other different specific embodiments, and the details in this specification can also be modified or changed based on different viewpoints and applications without departing from the spirit of this utility model.

[0036] Before further describing the specific embodiments of this utility model, it should be understood that the protection scope of this utility model is not limited to the specific embodiments described below; the terminology used in the embodiments of this utility model is for describing specific embodiments and not for limiting the protection scope of this utility model.

[0037] Unless otherwise defined, all technical and scientific terms used in this invention have the same meaning as commonly understood by one of ordinary skill in the art. In addition to the specific methods, equipment, and materials used in the embodiments, based on the knowledge of the prior art possessed by one of ordinary skill in the art and the description of this invention, any prior art methods, equipment, and materials similar to or equivalent to those described, used, and materials in the embodiments of this invention may be used to implement this invention.

[0038] Unless otherwise specified, all devices and materials in this invention are commercially available or commonly used in the industry.

[0039] Terminology Explanation: Blood flow index ( B FI : The core parameter that quantifies the amount of erythrocyte perfusion in microvessels of tissue, measured by optical techniques (such as laser Doppler flowmeter (LDF) or diffusion-related spectroscopy (DCS)).

[0040] In DCS, B FI The core definition is: B FI = α×D b In the formula, α For dynamic scattering probability, D b The Brownian diffusion coefficient of effective red blood cells (RBCs); B FI For specific calculation methods, please refer to relevant literature reports, such as T Durduran. et al , Rep. Prog. Phys. 73(2010) 076701 (43pp), 1-43; Li Zhe et al., Progress in Lasers and Optoelectronics, Vol. 59, No. 6, March 2022.

[0041] in addition: B FI ∝ (Red blood cell concentration) × (Mean red blood cell motility); In other words, the product of the number of moving red blood cells and their average velocity within a unit detection volume directly reflects the blood perfusion intensity of the tissue microcirculation.

[0042] Note: The near-infrared laser power used in this device is ≤10mW, which complies with the Class 1 laser safety standard of GB7247.1-2012.

[0043] Example: A patch-type cardiac function assessment device based on an ultrasound and DCS fusion probe The structural design of this device is as follows: like Figure 3 As shown, the cardiac function assessment device of this utility model has a "patch-type" structure design. The lower part of the device is a circular base 2 made of skin-friendly material, and its lower surface is covered with a surface sticker 1. After peeling off the surface sticker 1, the circular base 2 can be pasted on the detection area of ​​the skin. The cardiac function assessment module 5 is embedded in the center of the circular base 2. When the circular base 2 is pasted on the detection area of ​​the skin, the lower surface of the cardiac function assessment module 5 makes close contact with the skin surface.

[0044] A cylindrical outer shell 4 is provided on the upper part of the circular base 2 to protect the various detection elements on the cardiac function assessment module 5.

[0045] As an optional design, the upper part of the cardiac function assessment module 5 can also be connected to the data transmission cable 3, which transmits the various test data acquired by the cardiac function assessment module 5 to an external control center. Similarly, the cardiac function assessment module 5 can also transmit test data to an external control center via Bluetooth or wireless connection.

[0046] like Figure 4 As shown, the lower surface of the cardiac function assessment module 5 is provided with an ultrasound probe 501 and a DCS probe 502. The ultrasound signal emitted by the ultrasound signal generator 503 (ultrasound probe) enters the patient's body (lung region) through the ultrasound probe 501 and receives the echo signal. An ultrasound image is generated based on the echo signal. The position and boundary of the lung in the thoracic cavity are determined based on the ultrasound image, and then the lung water volume of the target human body is determined. The near-infrared laser generator 504 (DCS probe) emits a near-infrared laser and enters the patient's body (lung region) through the DCS probe 502. The response signal of the human body to the near-infrared laser is detected, and a scattered light spot is obtained. The blood flow index of the target area (lung) of the human body is determined based on the scattered light spot. Then, the movement rate of red blood cells in the blood is calculated by the light intensity autocorrelation function, and the core temperature of the target area of ​​the human body (lung region temperature) is calculated by combining the Brownian motion diffusion coefficient formula.

[0047] like Figure 5As shown, the upper part of the cardiac function assessment module 5 is equipped with an ultrasound signal generator 503, a near-infrared laser generator 504, an echo sensor 505, a DCS signal feedback unit 506, a skin temperature detector 507, and a data processing element 6. The ultrasound signal generator 503 emits ultrasound signals to detect the lung water volume of the target human body; the near-infrared laser generator 504 emits near-infrared lasers to detect the blood flow index of the target area (lungs) of the human body; the echo sensor 505 receives the echo signal from the human body in response to the ultrasound signal; the DCS signal feedback unit 506 receives the response signal from the human body in response to the near-infrared laser; and the skin temperature detector 507 detects the skin surface temperature in real time.

[0048] like Figure 6 As shown, the data processing element 6 is equipped with an image generator 601, a spot generator 602, and a computing processor 603. The image generator 601 generates an ultrasound image from the human echo signal received by the echo sensor 505; the spot generator 602 calculates and generates a scattered spot using the human body's response signal to near-infrared laser; the computing processor 603 determines the position and boundary of the lungs in the thoracic cavity based on the ultrasound image, and then determines the lung water volume of the target human body; at the same time, it determines the blood flow index of the target area (lungs) of the human body based on the scattered spot, then calculates the movement rate of red blood cells in the blood through the light intensity autocorrelation function, and calculates the core temperature (lung area temperature) of the target area of ​​the human body by combining the Brownian motion diffusion coefficient formula; finally, it calculates the lung water retention (ΔV) and the core-surface temperature difference (ΔT) based on the above indicators, and calculates the heat accumulated in the thoracic cavity (Q value) according to the thermodynamic calculation formula Q=ρ·c·ΔV·ΔT (where ρ is the lung water density and c is the lung water specific heat capacity), monitors the change law of ΔQ in real time, and realizes multi-dimensional coupling analysis of cardiac function in heart failure patients.

[0049] As a preferred embodiment, the computing processor 603 in the cardiac function assessment device of this invention is equipped with an early warning management module, which includes the following structural units: (1) Threshold configuration protocol unit: Supports receiving external configuration parameters via Bluetooth / USB; (2) Rate of change algorithm unit: used to calculate the change in heat from Q within the time interval Δt. t-1 Change to Q t The rate of change, i.e., the rate of change r ΔQ = (Q t- Q t-1 ) / Δt; (3) Monitoring mode adaptive unit: When the concentration of biomarkers provided by the external system exceeds the preset concentration threshold, the short time window monitoring mode is automatically activated. The biomarkers include, but are not limited to, heart failure-related indicators such as BNP and NT-proBNP.

[0050] like Figure 7 As shown, the early warning management module performs the following functions: a) Based on the lung water volume, temperature of the target area, and real-time skin surface temperature, calculate the lung water retention value and core-surface temperature difference. Then, using the thermodynamic formula Q=ρ·c·ΔV·ΔT, calculate the accumulated heat value Q in the pleural cavity in real time, and monitor the change in Q value within the time interval Δt (ΔQ=Q t- Q t-1 ); b) When the rate of change of ΔQ (ΔQ / Δt) exceeds the preset dynamic threshold, an early warning signal is generated; c) The preset dynamic threshold can be dynamically configured through an external system, and the configuration basis includes NYHA classification, baseline physiological parameters and historical data trends.

[0051] The working process of this device is as follows: The patient lies flat on the measuring bed. The surface sticker 1 of the device is peeled off, and the circular base 2 is attached to the skin of the patient's lung area, so that the lower surface of the cardiac function assessment module 5 is in close contact with the skin surface.

[0052] The ultrasonic signal emitted by the ultrasonic signal generator 503 (ultrasound probe) enters the patient's body (lung region) through the ultrasonic detection port 501. The echo sensor 505 receives the echo signal of the human body to the ultrasonic signal. The image generator 601 generates an ultrasound image based on the human body echo signal received by the echo sensor 505. The near-infrared laser generator 504 (DCS probe) emits a near-infrared laser into the patient's body (lung region) through the DCS detection port 502. The DCS signal feedback unit 506 receives the human body response signal to the near-infrared laser. The spot generator 602 calculates and generates a scattered spot using the human body response signal to the near-infrared laser.

[0053] The 507 skin temperature detector measures skin surface temperature in real time.

[0054] The computing processor 603 on the data processing element 6 determines the position and boundary of the lungs in the thoracic cavity based on the ultrasound image, and then determines the lung water volume of the target human body; at the same time, it determines the blood flow index of the target area (lungs) of the human body based on the scattered light spot, and then calculates the movement rate of red blood cells in the blood through the light intensity autocorrelation function, and calculates the core temperature (lung area temperature) of the target area of ​​the human body by combining the Brownian motion diffusion coefficient formula; then, it combines the above indicators with the real-time temperature value of the skin surface to calculate the lung water retention (ΔV) and the core-surface temperature difference (ΔT), and calculates the heat accumulated in the thoracic cavity (Q value) according to the thermodynamic calculation formula Q=ρ·c·ΔV·ΔT (where ρ is the lung water density and c is the lung water specific heat capacity), monitors the change law of ΔQ in real time, and when the rate of change of ΔQ exceeds the preset dynamic threshold (configured by the external system), it outputs a graded warning signal for clinical decision reference, realizing the fusion analysis of multimodal data and the generation of warning signals.

[0055] The preferred embodiments and examples of this utility model have been described in detail above. However, this utility model is not limited to the above embodiments and examples. Within the scope of knowledge possessed by those skilled in the art, various changes can be made without departing from the concept of this utility model.

Claims

1. A patch-type cardiac function assessment device based on an ultrasound and DCS fusion probe, wherein the cardiac function assessment device has a "patch-type" structural design, the lower part of which is a flexible circular base (2), the lower surface of which is covered with a surface sticker (1), and the upper part of which is provided with a cylindrical shell (4), characterized in that, The cardiac function assessment module (5) is embedded in the center of the circular base (2); The lower surface of the cardiac function assessment module (5) is provided with an ultrasound detection hole (501) and a DCS detection hole (502). The upper part of the cardiac function assessment module (5) is respectively equipped with an ultrasound signal generator (503), a near-infrared laser generator (504), an echo sensor (505), a DCS signal feedback device (506), a skin temperature detector (507), and a data processing element (6). The data processing element (6) is respectively provided with an image generator (601), a spot generator (602) and a computing processor (603).

2. The cardiac function assessment device according to claim 1, characterized in that, When using the cardiac function assessment device, after peeling off the surface sticker (1), the circular base (2) is pasted onto the detection area of ​​the skin, so that the lower surface of the cardiac function assessment module (5) is in close contact with the skin surface.

3. The cardiac function assessment device according to claim 1, characterized in that, The upper part of the cardiac function assessment module (5) is also connected to a data transmission line (3), through which the detection data obtained by the cardiac function assessment module (5) is transmitted to the external control center.

4. The cardiac function assessment device according to claim 1, characterized in that, The cardiac function assessment module (5) transmits the detection data to an external control center via Bluetooth or wireless connection.

5. The cardiac function assessment device according to claim 1, characterized in that, The ultrasonic signal emitted by the ultrasonic signal generator (503) enters the patient's body through the ultrasonic probe (501). The echo sensor (505) receives the echo signal of the human body to the ultrasonic signal. The image generator (601) generates an ultrasonic image based on the human body echo signal received by the echo sensor (505). The calculation processor (603) determines the lung water volume of the target human body based on the ultrasonic image.

6. The cardiac function assessment device according to claim 1, characterized in that, The near-infrared laser emitted by the near-infrared laser generator (504) enters the patient's body through the DCS detection hole (502). The DCS signal feedback device (506) receives the response signal of the human body to the near-infrared laser. The spot generator (602) calculates and generates a scattered spot using the response signal of the human body to the near-infrared laser. The calculation processor (603) determines the blood flow index of the target area of ​​the human body based on the scattered spot, and then calculates the movement rate of red blood cells in the blood through the light intensity autocorrelation function, and calculates the core temperature of the target area of ​​the human body by combining the Brownian motion diffusion coefficient formula.

7. The cardiac function assessment device according to claim 1, characterized in that, The skin temperature detector (507) detects the skin surface temperature in real time.

8. The cardiac function assessment device according to claim 1, characterized in that, The computing processor (603) is provided with an early warning management module, which includes the following structural units: (1) Threshold configuration protocol unit: Supports receiving external configuration parameters via Bluetooth / USB; (2) Rate of change algorithm unit: used to calculate the change in heat from Q within the time interval Δt. t-1 Change to Q t The rate of change, i.e., the rate of change r ΔQ = (Q t -Q t-1 ) / Δt; (3) Monitoring mode adaptive unit: When the concentration of biomarkers provided by the external system exceeds the preset concentration threshold, the short time window monitoring mode is automatically activated. The biomarkers include BNP and NT-proBNP.

9. The cardiac function assessment device according to claim 8, characterized in that, The early warning management module performs the following functions: a) Based on the lung water volume of the target human body, the temperature value of the target area of ​​the human body, and the real-time temperature value of the skin surface, calculate the lung water retention value and the core-surface temperature difference value, and calculate the heat accumulation value Q in the pleural cavity in real time according to the thermodynamic calculation formula Q=ρ·c·ΔV·ΔT, and monitor the change of Q value ΔQ within the time interval Δt. b) An early warning signal is generated when the rate of change of ΔQ exceeds a preset dynamic threshold; c) The preset dynamic threshold can be dynamically configured through an external system, and the configuration basis includes NYHA classification, baseline physiological parameters and historical data trends.

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