Portable blood circulation assisting device, control method and blood circulation assisting system

Abstract

The invention discloses a portable blood circulation auxiliary device, a control method and a blood circulation auxiliary system. The portable blood circulation auxiliary device integrates the functions of blood oxygen and electrocardiogram detection and multi-part electrical stimulation, is small in size, supports portable use, gets rid of dependence of a traditional air bag type device on a fixed power source, does not limit activities of a user and meets daily scene requirements. Moreover, by combining double-index dynamic adjustment of the electrocardio waveform and the blood oxygen data, the discharge frequency is determined through the real-time heart rate, the discharge intensity is adjusted based on the blood oxygen data, precise and personalized intervention is achieved, and the defect that a traditional device lacks self-adaptive adjustment is overcome to a certain degree. Besides, electric stimulation is released according to the time sequence that the crus delays K1 milliseconds at the peak of the R wave and the thigh delays K2 milliseconds at the peak of the R wave, the time sequence is synchronously continued to the starting point of the T wave, the physiological characteristics of lower limb muscles and the blood pumping rhythm of the heart are met, the use comfort is improved, meanwhile, blood backflow is efficiently promoted, and the heart burden is relieved.

Description

Technical Field

[0001] This application relates to the field of electrotherapy medical devices, and in particular to a portable blood circulation assist device, control method and blood circulation assist system. Background Technology

[0002] Traditional mainstream products for improving blood circulation are airbag compression devices, which use inflatable airbags to compress the limbs, simulating the function of a muscle pump to promote blood return. However, these devices have significant drawbacks. For example, they are bulky and require an external power source, restricting user movement and lacking portability. Furthermore, airbag devices are prone to uneven pressure distribution, which can easily cause limb discomfort. They also lack the ability to dynamically monitor and adaptively adjust physiological indicators such as heart rate and blood oxygenation, making it difficult to meet the needs of users with limited professional knowledge in daily life. Summary of the Invention

[0003] This application aims to provide a portable blood circulation assist device, control method, and blood circulation assist system that can provide high portability and effectively reduce the need for users' professional knowledge.

[0004] The portable blood circulation assist device according to an embodiment of this application includes: The device casing is equipped with a blood oxygen interface, a cardiac equipment interface, and multiple electrode connection interfaces; The device control module is located inside the device housing; The blood oxygen detection unit is electrically connected to the device control module through the blood oxygen interface to acquire blood oxygen data; The electrocardiogram (ECG) status detection unit is electrically connected to the device control module via the ECG equipment interface and is used to acquire ECG waveforms. At least four electrical stimulation components are electrically connected to the device control module through multiple electrode connection interfaces; the multiple electrical stimulation components release electrical stimulation signals to at least the lower legs and the thighs on both sides; The device control module is used to determine the real-time heart rate based on the electrocardiogram waveform, determine the discharge frequency of the plurality of electrical stimulation components based on the real-time heart rate, and determine the discharge intensity of the plurality of electrical stimulation components based on the blood oxygen data; the discharge intensity is negatively correlated with the blood oxygen data. The discharge frequency of the plurality of electrical stimulation components is negatively correlated with the real-time heart rate, and the discharge frequency of the plurality of electrical stimulation components is the same; during the R-wave cycle of the ECG waveform in which an electrical stimulation signal needs to be released, at a time K1 milliseconds after the R-wave peak, the electrical stimulation component used to release the electrical stimulation signal to the calf releases the electrical stimulation signal and continues until the beginning of the T-wave; at a time K2 milliseconds after the R-wave peak, the electrical stimulation component used to release the electrical stimulation signal to the thigh releases the electrical stimulation signal and continues until the beginning of the T-wave, where K1 is less than K2.

[0005] The blood circulation assist system according to an embodiment of this application includes a main device and a portable blood circulation assist device as described above that is detachably electrically connected to the main device. The main device includes a device housing, a device control module disposed within the device housing, and a visual interaction module disposed on the device housing.

[0006] The control method for a portable blood circulation assist device according to an embodiment of this application is applied to the portable blood circulation assist device as described above. The control method for the portable blood circulation assist device includes: Acquire electrocardiogram waveforms and blood oxygen data; Determine the real-time heart rate based on the described electrocardiogram waveform; Based on the real-time heart rate, the discharge frequency of multiple electrical stimulation components is determined; The discharge intensity of multiple electrical stimulation components is determined based on the blood oxygen data, and the discharge intensity is negatively correlated with the blood oxygen data; Based on the discharge frequency and the electrocardiogram waveform, the R-wave period of the electrocardiogram waveform for which an electrical stimulation signal needs to be released is determined. Within the R-wave cycle of the electrocardiogram waveform that requires the release of an electrical stimulation signal, the electrical stimulation component for releasing an electrical stimulation signal to the lower leg releases an electrical stimulation signal 30 milliseconds after the R-wave peak and continues until the start of the T-wave. Then, 50 milliseconds after the R-wave peak, the electrical stimulation component for releasing an electrical stimulation signal to the thigh releases an electrical stimulation signal and continues until the start of the T-wave.

[0007] The portable blood circulation assist device, control method, and blood circulation assist system of this application integrate blood oxygen, electrocardiogram (ECG) detection, and multi-site electrical stimulation functions. The device is compact and portable, eliminating the dependence on a fixed power source found in traditional airbag-type devices, and does not restrict user activity, adapting to daily needs. Furthermore, it dynamically adjusts based on both ECG waveform and blood oxygen data, determining the discharge frequency through real-time heart rate and adjusting the discharge intensity based on blood oxygen data, achieving precise and personalized intervention, thus avoiding the shortcomings of traditional devices that lack adaptive adjustment to some extent. In addition, electrical stimulation is released in a sequence of "K1 milliseconds after the R-wave peak in the calf and K2 milliseconds after the R-wave peak in the thigh," and continues synchronously until the T-wave initiation, conforming to the physiological characteristics of lower limb muscles and the heart's pumping rhythm, improving user comfort, and simultaneously efficiently promoting blood return and reducing the burden on the heart.

[0008] Other features and advantages of this application will be set forth in the following description, and will be apparent in part from the description, or may be learned by practicing this application. Attached Figure Description

[0009] The above and / or additional aspects and advantages of this application will become apparent and readily understood from the description of the embodiments taken in conjunction with the following drawings, in which: Figure 1 This is a schematic diagram of the blood circulation support system provided in the embodiments of this application; Figure 2 yes Figure 1 A magnified view of part A in the middle; Figure 3 A system diagram of the portable blood circulation assist device provided in the embodiments of this application; Figure 4 An isometric view of a portable blood circulation assist device provided in an embodiment of this application; Figure 5 Another isometric view of the portable blood circulation assist device provided in the embodiments of this application; Figure 6 This is a schematic diagram of the stacked structure of the electrical stimulation component provided in the embodiments of this application; Figure 7 A flowchart illustrating the control method of the portable blood circulation assist device provided in the embodiments of this application.

[0010] Figure label: Device housing 110; snap-fit ​​slot 111; shoulder strap buckle 112; slide groove 113; first power interface 114; first communication interface 115; device control module 120; blood oxygen detection unit 130; electrocardiogram status detection unit 140; electrical stimulation component 150; drug-permeable nonwoven fabric layer 151; conductive drug-loaded gel layer 152; electrode foil 153; insulating intermediate layer 154; graphene heating layer 155; insulating backing layer 156; button unit 160; indicator light 170. Equipment housing 210; mounting groove 211; slide rail 212; second power interface 213; second communication interface 214; limit slide 215; visual interaction module 220. Detailed Implementation

[0011] The embodiments of this application are described in detail below. Examples of the embodiments are shown in the accompanying drawings, wherein the same or similar reference numerals denote the same or similar elements or elements having the same or similar functions throughout. The embodiments described below with reference to the accompanying drawings are exemplary and are only used to explain this application, and should not be construed as limiting this application.

[0012] In the description of this application, the use of terms such as "first," "second," etc., is for the purpose of distinguishing technical features only and should not be construed as indicating or implying relative importance or implicitly indicating the number of technical features indicated or the order of the technical features indicated.

[0013] In the description of this application, it should be understood that the orientation descriptions, such as up, down, etc., are based on the orientation or positional relationship shown in the accompanying drawings, and are only for the convenience of describing this application and simplifying the description, and do not indicate or imply that the device or element referred to must have a specific orientation, or be constructed and operated in a specific orientation, and therefore should not be construed as a limitation of this application.

[0014] In the description of this application, it should be noted that, unless otherwise explicitly defined, terms such as "setup," "installation," and "connection" should be interpreted broadly, and those skilled in the art can reasonably determine the specific meaning of the above terms in this application in conjunction with the specific content of the technical solution.

[0015] The technical solution of this application will be clearly and completely described below with reference to the accompanying drawings. Obviously, the embodiments described below are some embodiments of this application, not all embodiments.

[0016] refer to Figures 1 to 6 One embodiment of this application provides a portable blood circulation assist device, which includes: The device housing 110 is equipped with a blood oxygen interface, a cardiac equipment interface, and multiple electrode connection interfaces; The device control module 120 is disposed inside the device housing 110; The blood oxygen detection unit 130 is electrically connected to the device control module 120 via a blood oxygen interface to acquire blood oxygen data; The electrocardiogram (ECG) status detection unit 140 is electrically connected to the device control module 120 via an ECG device interface and is used to acquire ECG waveforms. At least four electrical stimulation components 150 are electrically connected to the device control module 120 through multiple electrode connection interfaces; the multiple electrical stimulation components 150 release electrical stimulation signals to at least the lower legs and the thighs on both sides; The device control module 120 is used to determine the real-time heart rate based on the electrocardiogram waveform, determine the discharge frequency of multiple electrical stimulation components 150 based on the real-time heart rate, and determine the discharge intensity of multiple electrical stimulation components 150 based on blood oxygen data; the discharge intensity is negatively correlated with the blood oxygen data. Among them, the discharge frequency of multiple electrical stimulation components 150 is negatively correlated with the real-time heart rate, and the discharge frequency of multiple electrical stimulation components 150 is the same; during the R-wave cycle of the electrocardiogram waveform that needs to release electrical stimulation signals, at a time K1 milliseconds after the R-wave peak, the electrical stimulation component 150 used to release electrical stimulation signals to the lower leg releases electrical stimulation signals and continues until the beginning of the T-wave; at a time K2 milliseconds after the R-wave peak, the electrical stimulation component 150 used to release electrical stimulation signals to the thigh releases electrical stimulation signals and continues until the beginning of the T-wave, where K1 is less than K2.

[0017] In this embodiment, the device integrates blood oxygen and electrocardiogram (ECG) detection with multi-site electrical stimulation functions. It is compact and portable, eliminating the dependence on a fixed power source for traditional airbag-type devices, not restricting user activity, and adapting to daily needs. Furthermore, it dynamically adjusts the discharge frequency based on both ECG waveform and blood oxygen data, adapting to different heart rate states and adjusting the discharge intensity based on blood oxygen data to achieve safe and effective, precise, and personalized intervention, thus avoiding the shortcomings of traditional devices that lack adaptive adjustment to a certain extent. In addition, it releases electrical stimulation according to the timing sequence of "K1 milliseconds after the R-wave peak in the calf and K2 milliseconds after the R-wave peak in the thigh," and continues synchronously until the T-wave initiation, which matches the physiological characteristics of lower limb muscles and the heart's pumping rhythm, improving user comfort and efficiently promoting blood return, reducing the burden on the heart.

[0018] K1 can be 30 milliseconds, and K2 can be 50 milliseconds.

[0019] The outer shell 110 of the aforementioned device can be integrally injection molded from medical-grade ABS material, which has lightweight and sweat-proof and waterproof properties, making it suitable for daily wear and mobile scenarios.

[0020] The front end of the aforementioned housing can be centrally arranged with interfaces. Among them, the blood oxygen interface can be a standard USB-C interface for connecting a finger pulse oxygen sensor; the ECG device interface can be a conventional 8-lead dedicated interface, compatible with the signal transmission of conventional ECG electrode pads; at least four electrode pad connection interfaces are provided, corresponding to at least four electrical stimulation components 150 on both sides of the lower legs and both sides of the thighs.

[0021] The control module 120 of the above-mentioned device can have a built-in high-performance MCU chip, which can be a DSP or a high-performance microcontroller, such as an STM32 series processor. It can receive waveform data transmitted by the ECG status detection unit 140; at the same time, it can also receive blood oxygen saturation data from the blood oxygen detection unit 130 and map it to a discharge intensity level of 1-20; it can also accurately trigger the delay timing according to the R wave peak signal to control the start and end of the electrical stimulation signal.

[0022] The aforementioned pulse oximetry detection unit 130 can consist of a finger pulse oximetry sensor and a signal transmission cable. The sensor is electrically connected to the device control module 120 via a pulse oximetry interface. The signal transmission cable is flexible and not easily broken. The sensor housing can be made of medical-grade silicone, which is soft, conforms to the skin, and provides high wearing comfort.

[0023] The aforementioned ECG status detection unit 140 may include 8-lead ECG electrode pads and a signal acquisition cable. The electrode pads may be made of medical conductive gel and are attached to designated locations on the chest (RA, LA, V1, V5, RL, LL leads) for ECG waveform acquisition. The signal acquisition cable is connected to the device control module 120 via an ECG device interface and has a built-in shielding layer to reduce external electromagnetic interference. The ECG status detection unit 140 may have a built-in waveform recognition algorithm. It can accurately locate the R-wave peak by using an R-wave peak threshold that is more than twice the baseline amplitude, and identify the T-wave initiation point by using a T-wave slope change with a falling edge slope ≤ -0.5mV / s. The R-wave peak time, T-wave initiation time, and R-wave period data are transmitted to the device control module 120 in real time. Even if the ECG status detection unit 140 does not have strong computing power, the device control module 120 can directly calculate the R-wave peak time, T-wave initiation time, and R-wave period.

[0024] At least four electrical stimulation components 150 are provided, corresponding to the lower legs and thighs on both sides of the body, and can be arranged symmetrically. The electrical stimulation component 150 attached to the lower leg can be 5cm × 8cm (area 40cm²) in size and can be attached to the thickest part of the medial and lateral heads of the gastrocnemius muscle; the electrical stimulation component 150 attached to the thigh can be 10cm × 8cm (area 80cm²) in size and can be attached to the thickest part of the biceps femoris muscle. The electrical stimulation component 150 adopts a multi-layer composite structure, which can be configured sequentially from the skin contact surface upwards as follows: a drug-permeable non-woven fabric layer 151, a conductive drug-loaded gel layer 152 (some drug-active agents can be pre-mixed in the conductive drug-loaded gel layer 152, so that the effective ingredients in these agents can be absorbed through the contact area during electrical stimulation), an electrode foil 153 (which can be made of gold foil or silver foil; copper foil can be used if cost control is required), an insulating intermediate layer 154, a graphene heating layer 155 (the heating temperature is adjustable from 35-41℃, which can reduce patient discomfort to a certain extent in cold environments, and at the same time, the higher temperature can better allow the effective ingredients of the drug in the conductive drug-loaded gel layer 152 to be absorbed), and an insulating backing layer 156. The electrode foil 153 is connected to the electrode connection interface of the device housing 110 through wires, and the output voltage is adjustable from 1 to 20 levels, corresponding to an actual voltage of 2.5V-50V.

[0025] It should be noted that an energy storage unit is also installed inside the device housing 110. The energy storage unit is used to provide power to the device control module 120, blood oxygen detection unit 130, electrocardiogram status detection unit, multiple electrical stimulation components 150 and other components.

[0026] In some implementations, when the heart rate is between 60 and 80 bpm, the multiple electrical stimulation components 150 release an electrical stimulation signal once per R-wave cycle, and when the heart rate is between 80 and 120 bpm, the multiple electrical stimulation components 150 release an electrical stimulation signal once every two R-wave cycles.

[0027] In this embodiment, the discharge frequency is dynamically matched to different heart rate states. High-frequency stimulation ensures efficient blood return when the heart rate is slow, while low-frequency stimulation prevents increased cardiac load when the heart rate is fast, overcoming the shortcomings of traditional devices with fixed frequencies and single modes. Furthermore, personalized intervention is achieved through precise interval division, which not only matches the heart's pumping rhythm but also reduces excessive muscle contraction and fatigue, improving safety and auxiliary effects. It should also be noted that if the heart rate consistently exceeds 120 bpm, an alarm should be triggered to remind remote monitoring personnel to promptly notify the user to seek clinical observation at a professional institution. Therefore, for the device in this embodiment, it is not necessary to add electrical stimulation control logic for conditions exceeding 120 bpm, thereby further simplifying the process of determining the electrical stimulation frequency and improving the overall operational stability of the device.

[0028] In some implementations, the maximum voltage corresponding to the discharge intensity is 50V.

[0029] In this embodiment, the maximum voltage of 50V can better adapt to the stimulation needs of patients with different body types and muscle mass. Compared with low-voltage devices, it can effectively drive the contraction of deep muscles in the lower limbs and improve the blood return assist effect. At the same time, the stepped voltage adjustment can prevent insufficient or excessive stimulation intensity, balancing the effectiveness and safety of use.

[0030] The aforementioned device control module 120 can map blood oxygen data to 1-20 levels of discharge intensity, corresponding to a voltage range of 2.5V-50V. Each level of voltage increases by 2.5V in a step-like manner, and in some scenarios, a curve-like increase can also be used.

[0031] In some implementations, reference Figure 6 The electrical stimulation assembly 150 includes a drug-permeable nonwoven fabric layer 151, a conductive drug-loaded gel layer 152, an electrode foil 153, and an insulating backing layer 156 arranged in layers. The electrode foil 153 is used for electrical connection with the device control module 120.

[0032] In this embodiment, the layered structure achieves a synergistic effect of "electrical stimulation + transdermal traditional Chinese medicine". Compared with a simple electrical stimulation device, it adds a drug-assisted dimension, improving the effect of blood circulation. In addition, conductive drug-loaded gel layers 152 with different functions can be prefabricated according to needs. At the same time, the conductive drug-loaded gel layer 152 allows the entire electrical stimulation component 150 to better fit the skin, with stable conductivity and no irritation, solving the problems of poor contact and skin discomfort of traditional electrodes. In this embodiment, the functional areas of each layer of the electrical stimulation component 150 are clearly defined, the structure is compact and thin, there is no foreign body sensation when wearing it, it is suitable for long-term use, and it takes into account both effectiveness and comfort.

[0033] The aforementioned electrostimulation component 150 can be formed by stacking and pressing together the following layers: drug-permeable nonwoven fabric layer 151 → conductive drug-loaded gel layer 152 → electrode foil 153 → insulating backing layer 156. The drug-permeable nonwoven fabric layer 151 can be made of medical-grade spunlace fabric and can be pre-loaded with extracts of traditional Chinese medicine that promote blood circulation. The conductive drug-loaded gel layer 152 can contain medical conductive particles and a viscous matrix, and can be pre-mixed with drugs. The electrode foil 153 needs to have pre-reserved wiring terminals to complete the wiring with the device control module 120. The insulating backing layer 156 is a waterproof nonwoven fabric, which can effectively prevent current leakage. The electrode foil 153 is connected to the device electrode interface via shielded wires to achieve signal transmission.

[0034] In some implementations, reference Figure 6 An insulating intermediate layer 154 and a graphene heating layer 155 are arranged sequentially between the electrode foil 153 and the insulating backing layer 156. The graphene heating layer 155 is used for electrical connection with the device control module 120.

[0035] In this embodiment, the graphene heating layer 155 promotes skin blood circulation and transdermal absorption of traditional Chinese medicine ingredients, enhancing the synergistic effect of "electrical stimulation + drug," significantly improving auxiliary efficiency compared to structures without heating. Simultaneously, the insulating intermediate layer 154 isolates current and heat conduction, effectively preventing burns or short circuits. Furthermore, the heating temperature improves the user experience, enhances comfort in low-temperature environments, and optimizes the adhesiveness of the conductive gel, reducing the probability of detachment.

[0036] In the process described above, an insulating intermediate layer 154 is first bonded between the electrode foil 153 and the insulating backing layer 156, and then a graphene heating layer 155 is superimposed. The graphene heating layer 155 is electrically connected to the device control module 120 via wires, supporting constant temperature regulation. The insulating intermediate layer 154 completely covers the electrode foil 153 to prevent short circuits between the heating layer and the electrode; each layer can be fixed by lamination with medical-grade pressure-sensitive adhesive, with edges flush with the overall component to ensure a compact structure.

[0037] In some implementations, reference Figures 2 to 4 The aforementioned portable blood circulation assist device also includes: The button unit 160 is disposed on the device housing 110 and is electrically connected to the device control module 120.

[0038] In this embodiment, the button unit 160 allows for real-time adjustment of the electrical stimulation intensity and heating temperature without relying on an APP or main device. The operation is intuitive and convenient, suitable for elderly patients and other users unfamiliar with smart devices, and facilitates timely intervention through the physical button in case of discomfort.

[0039] The aforementioned button unit 160 may include a voltage level button group, a temperature adjustment button group, and a power switch. The voltage level button group can be used to adjust the discharge intensity of the electrical stimulation component 150, the temperature adjustment button group can be used to adjust the heating temperature of the graphene heating layer 155, and the power switch can be used for on / off control. In some embodiments, other buttons may be added to achieve special functions, such as a one-button alarm.

[0040] In some implementations, reference Figures 2 to 4 The aforementioned portable blood circulation assist device also includes: Indicator light 170 is mounted on the device housing 110 and is electrically connected to the device control module 120.

[0041] In this embodiment, the device's operating status can be intuitively fed back through color and flashing patterns. Users can quickly determine power supply, operation, and fault conditions without additional operation, solving the problem of unclear status in traditional devices. The fault alarm function promptly alerts users to abnormalities, effectively preventing equipment damage or usage risks, and is suitable for various user groups. In addition, the adjustable brightness design caters to different environmental needs, improving ease of use and safety.

[0042] The aforementioned indicator light 170 is located on the front surface of the device housing 110 and may include multiple high-brightness LEDs, corresponding to green for power supply, blue for operating status, and red for fault alarm. A constantly lit power light indicates normal power supply, a flashing operating light at a frequency of 1Hz indicates that electrical stimulation is in operation, and a flashing red light indicates alarms such as overvoltage / overcurrent / connection abnormalities. Furthermore, the brightness of the indicator light 170 is adjustable to adapt to different indoor and outdoor usage scenarios, and its adjacent arrangement to the button unit 160 facilitates observation.

[0043] In some embodiments, the portable blood circulation assist device described above further includes: The wireless communication module is located inside the device housing 110 and is electrically connected to the device control module 120.

[0044] In this embodiment, a wireless communication module is added to overcome the limitations of wired transmission, enabling wireless data synchronization and remote control. The system can monitor the patient's usage status and adjust parameters remotely in real time, increasing security. This is especially suitable for people with limited professional knowledge or educational background.

[0045] In some implementations, reference Figure 6 The rear end face of the device housing 110 is also provided with a first power interface 114 electrically connected to the energy storage unit and a first communication interface 115 electrically connected to the device control module 120.

[0046] The aforementioned first power interface 114 is compatible with conventional chargers and power banks, solving battery anxiety during portable use and making the usage scenarios more flexible.

[0047] The aforementioned first communication interface 115 can realize stable wired data transmission with the main device or other smart terminals, making up for the distance limitations of wireless communication and improving the flexibility of use.

[0048] In some implementations, reference Figure 1 , Figure 2 , Figure 4 The device housing 110 has a sliding groove 113 on both the left and right sides. The device housing 110 slides into the main device housing 210 through the sliding groove 113. The main device housing 210 has a mounting groove 211 corresponding to the device housing 110. The left and right sides of the mounting groove 211 have a slide rail 212 corresponding to the sliding groove 113. The bottom of the mounting groove 211 has a second power interface 213 and a second communication interface 214 corresponding to the first power interface 114 and the first communication interface 115.

[0049] The sliding grooves 113 on the left and right sides of the outer casing 110 of the aforementioned device can be integrally formed. The slide rail 212 of the main equipment mounting groove 211 is precisely matched with the sliding groove 113, and the surface of the slide rail 212 is smoothed to reduce sliding resistance. When the device is pushed into the mounting groove 211 along the slide rail 212, it is precisely positioned by the guide of the sliding groove 113. After being pushed to the bottom, the first power interface 114 and the first communication interface 115 at the rear end of the outer casing automatically align and fit with the second power interface 213 and the second communication interface 214 at the bottom of the groove, completing the electrical connection.

[0050] In this embodiment, the structural design allows for quick assembly and disassembly of the device and the main equipment, enabling both independent portable use and connection to the main equipment, thus balancing mobility and clinical expandability. The guiding design of the slide groove 113 and slide rail 212 ensures precise interface alignment, reducing the difficulty of manual insertion and removal alignment and making operation more convenient.

[0051] In some implementations, reference Figure 1 , Figure 2 , Figure 4 Both sides of the front end face of the device housing 110 are provided with snap-fit ​​grooves 111. The front end face of the device housing 210 is provided with two limiting slides 215. The two limiting slides 215 are located on both sides of the mounting groove 211. When the device housing 110 slides into the mounting groove 211 and slides to the bottom, each limiting slide 215 can slide into the corresponding snap-fit ​​groove 111.

[0052] The snap-fit ​​grooves 111 on both sides of the front end face of the device housing 110 are rectangular grooves that can be integrally injection molded with the device housing 110, and the edges of the grooves are chamfered.

[0053] The limiting slides 215 on both sides of the mounting groove 211 of the main equipment can be made of medical-grade plastic, and the exposed ends are equipped with anti-slip blocks. When the device slides to the bottom along the slide rail 212, the limiting slide 215 is manually pushed inward, and the front end of the slide is inserted into the corresponding locking groove 111 to complete the locking; when unlocking, the blocks are pushed in the opposite direction, and the slide is reset and disengaged from the locking groove 111 under the action of elasticity.

[0054] In this embodiment, the locking engagement between the limiting slider 215 and the locking slot 111 prevents the device from detaching due to collision or movement after being connected to the main equipment, maintaining the stability of power supply and data transmission, and resolving the potential hazards caused by loose connection of the slider 113 alone. Furthermore, the slider operation is intuitive and convenient, requiring no tools for locking and unlocking, significantly improving assembly and disassembly efficiency compared to screw fixing methods, and meeting the needs of rapid switching of clinical usage scenarios.

[0055] In some implementations, the blood oxygen interface, the electrocardiogram equipment interface, and the multiple electrode connection interfaces are all arranged on the front face of the device housing 110.

[0056] In this embodiment, the interfaces are centrally arranged on the front face of the device housing 110, which allows users to easily connect all devices at once, greatly improving operational efficiency. At the same time, the front face layout does not affect the wearing of the device and its docking with the main device, taking into account both portability and practicality, and improving ease of use and reliability.

[0057] The aforementioned blood oxygen interface, electrocardiogram equipment interface, and multiple electrode connection interfaces can be centrally arranged on the lower side of the front end face of the device housing 110.

[0058] In some implementations, reference Figure 4 At least one strap buckle 112 is also provided on the front end face of the device housing 110.

[0059] The aforementioned device housing 110 has two symmetrically arranged recesses on both sides of its front end face. Two strap buckles 112 are rotatably mounted in these recesses via a pivot, allowing the strap buckles 112 to switch between being hidden within the recesses and protruding from them. It should be noted that this retractable design is primarily used in scenarios where the device is connected to a main device, thereby reducing the safety hazards posed by the strap buckles 112 protruding from the device housing 110.

[0060] This application also proposes a blood circulation assist system, which includes a main device and a portable blood circulation assist device as described above that is detachably electrically connected to the main device. The main device includes a device housing 210 and a device control module disposed within the device housing 210 and a visual interaction module 220 disposed on the device housing 210.

[0061] In this embodiment, a detachable architecture combining a portable device and a main unit is adopted. This retains the advantages of mobile use of the portable device while expanding functional boundaries through the main unit, addressing the pain points of traditional systems that are either "weak in portability or limited in fixed use." Simultaneously, the visual interaction module 220 intuitively presents physiological data and device status, making it easier to use than pure button operation. Furthermore, the main unit supports data storage and traceability, facilitating user analysis of effects and optimization of treatment plans, while also enabling batch device management and improving the efficiency of clinical applications. In addition, the detachable design flexibly adapts to home rehabilitation and hospital treatment scenarios, balancing practicality and expandability, and offering a significantly superior overall experience and safety compared to traditional single-device systems.

[0062] The front surface of the main device's housing 210 can be provided with a mounting groove 211 adapted to the portable blood circulation assist device. Slide rails 212 are provided on both sides of the groove, and a second power interface 213 and a second communication interface 214 are provided at the bottom. Limiting slides 215 are provided on both sides of the groove. The device control module can have a built-in industrial-grade MCU, integrating data storage, protocol parsing, and command issuance functions. It can achieve bidirectional communication with the portable device through the bottom interface, and can also achieve wireless connection if a wireless communication module is available.

[0063] The aforementioned visualization interaction module 220 is a capacitive touch screen embedded in the top surface of the device housing 210, which can support real-time display of ECG waveforms, blood oxygen data, and stimulation parameters, as well as operations such as parameter setting, mode switching, and historical data query.

[0064] The aforementioned portable device slides and docks with the main equipment slide rail 212 via the slide groove 113. After locking, it automatically completes the power and communication interface adaptation to form a complete system.

[0065] like Figure 7 As shown, this application embodiment also provides a control method for a portable blood circulation assist device. The control method for the portable blood circulation assist device is applied to the device control module 120 in the portable blood circulation assist device described above. The control method for the portable blood circulation assist device includes steps S100 to S600. Step S100: Acquire ECG waveform and blood oxygen data; Step S200: Determine the real-time heart rate based on the electrocardiogram waveform; Step S300: Determine the discharge frequency of multiple electrical stimulation components 150 based on the real-time heart rate; Step S400: Determine the discharge intensity of multiple electrical stimulation components 150 based on blood oxygen data. The discharge intensity is negatively correlated with the blood oxygen data. Step S500: Based on the discharge frequency and the electrocardiogram waveform, determine the R-wave period of the electrocardiogram waveform for which the electrical stimulation signal needs to be released; In step S600, during the R-wave cycle of the electrocardiogram waveform in which the electrical stimulation signal needs to be released, 30 milliseconds after the R-wave peak, the electrical stimulation component 150 for releasing the electrical stimulation signal to the lower leg releases the electrical stimulation signal and continues until the beginning of the T-wave. 50 milliseconds after the R-wave peak, the electrical stimulation component 150 for releasing the electrical stimulation signal to the thigh releases the electrical stimulation signal and continues until the beginning of the T-wave.

[0066] In this embodiment, the control method is implemented based on the server in the aforementioned portable blood circulation assist device, thus possessing all the effective effects brought by the server in the aforementioned portable blood circulation assist device. Furthermore, the control method in this embodiment achieves personalized and efficient blood circulation assistance through the logic of "dual parameter acquisition - dynamic adjustment - precise timing triggering." First, ECG waveforms and blood oxygen data are acquired synchronously to provide comprehensive physiological basis for adjustment; then, the discharge frequency is determined based on the real-time negative correlation of heart rate to adapt to different heart rate states; subsequently, the discharge intensity is adjusted through the negative correlation of blood oxygen data to balance safety and effectiveness; finally, the target R-wave cycle is precisely locked, and stimulation is released with differentiated delay sequences of 30ms for the calf and 50ms for the thigh, continuing until the T-wave initiation. This aligns with the heart's pumping rhythm and the physiological characteristics of the lower limb muscles, improving blood return efficiency, reducing the burden on the heart, reducing the conflict between stimulation and ventricular contraction, reducing muscle fatigue and discomfort, resulting in better assistive effects, higher safety, and adaptability to diverse usage scenarios and different patient needs.

[0067] The aforementioned acquisition of ECG waveforms and blood oxygen data can be achieved by attaching the electrode pads of the ECG status detection unit 140 to designated lead positions (RA, LA, V1, V5, RL, LL, etc.) on the chest of the user via the 8-lead ECG device interface on the front side of the device housing 110. The electrode pads are tightly attached to the skin through conductive gel, capturing a complete ECG waveform including the P wave, QRS complex, and T wave. Simultaneously, a finger pulse oxygen sensor is connected via the blood oxygen interface. The sensor is clipped to the user's fingertip and uses a transmission photoelectric detection principle to collect blood oxygen saturation data, which is synchronously transmitted to the control module.

[0068] When the control module 120 of the aforementioned device processes the received electrocardiogram waveform data, it can use a peak detection algorithm to identify the R-wave peak. For example, a peak with a waveform amplitude more than twice the baseline is set as a candidate R-wave point, and the precise R-wave peak is selected by combining the waveform width of 0.06-0.12 seconds. Then, by recording the timestamps of three consecutive R-wave peaks, the time interval between adjacent R-waves is calculated, the average value is taken as the R-wave period, and the real-time heart rate is calculated using the formula "real-time heart rate = 60 ÷ R-wave period".

[0069] The control module 120 of the aforementioned device presets three heart rate thresholds (60 bpm, 80 bpm, and 120 bpm), forming two heart rate zones. When the real-time heart rate is between 60 and 80 bpm, the control module determines the discharge frequency to be "one electrical stimulation signal per R-wave cycle"; when the real-time heart rate is between 80 and 120 bpm, the discharge frequency is determined to be "one electrical stimulation signal every two R-wave cycles".

[0070] The aforementioned device control module 120 can map the received blood oxygen saturation data to a discharge intensity level of 1-20. Furthermore, the lower the blood oxygen level, the higher the discharge intensity, providing better blood return capability, optimizing blood oxygen data, and effectively adapting to the enhanced support needs under hypoxic conditions. In addition, users can manually adjust the intensity level within the 1-20 range via the button unit 160 on the device casing 110, a wirelessly connected companion APP, or a remote master device. It should be noted that after manual adjustment, the level obtained through manual adjustment has higher priority than the level obtained in automatic adjustment mode. If it is necessary to restore automatic mode, the automatic adjustment mode can be manually activated via the restore button in the button unit 160. At this time, the device can continue to execute the method process from steps S100 to S600.

[0071] The aforementioned device control module 120 can cache the R-wave cycle sequence of the electrocardiogram waveform in real time, and combine it with the discharge frequency determined in step S300 to determine the R-wave cycle of the electrocardiogram waveform that needs to release an electrical stimulation signal. Specifically, if the discharge frequency is "once per R-wave cycle", then all consecutive R-wave cycles are determined as "R-wave cycles that need to release an electrical stimulation signal"; if the discharge frequency is "once every two R-wave cycles", then according to the rule of "trigger-skip-trigger-skip", starting from the first R-wave cycle currently detected, the "R-wave cycle that needs to release an electrical stimulation signal" is determined once every R-wave cycle, and the timestamp of the trigger cycle is recorded by the timing unit to ensure that the triggering logic is coherent and without omissions.

[0072] Within the target R-wave cycle, the control module 120 of the aforementioned device starts timing from the peak of the R-wave. When the timing reaches 30 milliseconds, a trigger signal is sent to the drive channel connected to the calf electrical stimulation component 150. The drive unit outputs a pulse electrical signal of corresponding intensity level, and simultaneously activates the T-wave recognition algorithm to identify the T-wave initiation. The electrical stimulation signal continues until the T-wave initiation time. When the timing reaches 50 milliseconds, a trigger signal is sent to the drive channel connected to the thigh electrical stimulation component 150, outputting a pulse electrical signal of the same intensity level, which also continues until the T-wave initiation time. This ensures that the electrical stimulation of both the calf and thigh accurately matches the diastolic phase of the heart, achieving synergistic assistance in blood return. It should be noted that this fixed-delay electrical stimulation method can effectively reduce the complexity of device operation, thereby improving the stability of device operation to a certain extent, and is sufficient to meet the application needs of users who can engage in home-based activities.

[0073] In some implementations, when the heart rate is between 60 and 80 bpm, multiple electrical stimulation components 150 release an electrical stimulation signal once per R-wave cycle, and when the heart rate is between 80 and 120 bpm, multiple electrical stimulation components 150 release an electrical stimulation signal once every two R-wave cycles.

[0074] In this embodiment, the discharge frequency is dynamically matched to different heart rate states. High-frequency stimulation ensures efficient blood return when the heart rate is slow, while low-frequency stimulation prevents increased cardiac load when the heart rate is fast, overcoming the adaptation deficiencies of traditional devices with fixed frequencies and single modes. Furthermore, personalized intervention is achieved through precise interval division, which not only matches the heart's pumping rhythm but also reduces excessive muscle contraction and fatigue, improving safety and auxiliary effects. It should also be noted that if the heart rate consistently exceeds 120 bpm, an alarm should be triggered to remind remote monitoring personnel to promptly notify the user to seek clinical observation at a professional institution. Therefore, for the device in this embodiment, it is not necessary to add electrical stimulation control logic for conditions exceeding 120 bpm, thereby effectively simplifying the determination of the electrical stimulation frequency and improving the overall operational stability of the device.

[0075] In some implementations, the maximum voltage corresponding to the discharge intensity is 50V.

[0076] In this embodiment, the maximum voltage of 50V can better adapt to the stimulation needs of patients with different body types and muscle mass. Compared with low-voltage devices, it can effectively drive the contraction of deep muscles in the lower limbs and improve the blood return assist effect. At the same time, the combination of stepped voltage regulation and overvoltage protection design prevents insufficient or excessive stimulation intensity, solves the problem of uncontrollable pressure in traditional devices, balances effectiveness and safety, and improves adaptability.

[0077] The aforementioned device control module 120 can map blood oxygen data to 1-20 levels of discharge intensity, corresponding to a voltage range of 2.5V-50V. Each level of voltage increases by 2.5V in a step-like manner, and in some scenarios, a curve-like increase can also be used.

[0078] The above are merely specific embodiments of this application. Those skilled in the art will clearly understand that, for the sake of convenience and brevity, the specific working processes of the systems, modules, and units described above can be referred to the corresponding processes in the foregoing method embodiments, and will not be repeated here. It should be understood that the protection scope of this application is not limited thereto. Any person skilled in the art can easily conceive of various equivalent modifications or substitutions within the technical scope disclosed in this application, and these modifications or substitutions should all be covered within the protection scope of this application.

Claims

1. A portable blood circulation assist device, characterized in that, include: The device casing is equipped with a blood oxygen interface, a cardiac equipment interface, and multiple electrode connection interfaces; The device control module is located inside the device housing; The blood oxygen detection unit is electrically connected to the device control module through the blood oxygen interface to acquire blood oxygen data; The electrocardiogram (ECG) status detection unit is electrically connected to the device control module via the ECG equipment interface and is used to acquire ECG waveforms. At least four electrical stimulation components are electrically connected to the device control module through multiple electrode connection interfaces; the multiple electrical stimulation components release electrical stimulation signals to at least the lower legs and the thighs on both sides; The device control module is used to determine the real-time heart rate based on the electrocardiogram waveform, determine the discharge frequency of the plurality of electrical stimulation components based on the real-time heart rate, and determine the discharge intensity of the plurality of electrical stimulation components based on the blood oxygen data; the discharge intensity is negatively correlated with the blood oxygen data. The discharge frequency of the plurality of electrical stimulation components is negatively correlated with the real-time heart rate, and the discharge frequency of the plurality of electrical stimulation components is the same; during the R-wave cycle of the ECG waveform in which an electrical stimulation signal needs to be released, at a time K1 milliseconds after the R-wave peak, the electrical stimulation component used to release the electrical stimulation signal to the calf releases the electrical stimulation signal and continues until the beginning of the T-wave; at a time K2 milliseconds after the R-wave peak, the electrical stimulation component used to release the electrical stimulation signal to the thigh releases the electrical stimulation signal and continues until the beginning of the T-wave, where K1 is less than K2.

2. The portable blood circulation assist device according to claim 1, characterized in that, When the heart rate is between 60 and 80 bpm, multiple electrical stimulation components release an electrical stimulation signal once per R-wave cycle; when the heart rate is between 80 and 120 bpm, multiple electrical stimulation components release an electrical stimulation signal once every two R-wave cycles.

3. The portable blood circulation assist device according to claim 1, characterized in that, The electrostimulation component includes a drug-permeable nonwoven fabric layer, a conductive drug-loaded gel layer, an electrode foil, and an insulating backing layer arranged in layers. The electrode foil is used for electrical connection with the device control module.

4. The portable blood circulation assist device according to claim 3, characterized in that, An insulating intermediate layer and a graphene heating layer are sequentially arranged between the electrode foil and the insulating backing layer. The graphene heating layer is used for electrical connection with the device control module.

5. The portable blood circulation assist device according to claim 1, characterized in that, The rear end face of the device housing is also provided with a first power interface electrically connected to the energy storage unit and a first communication interface electrically connected to the device control module; the left and right sides of the device housing are provided with sliding grooves, and the device housing is slidably connected to the device housing of the main device through the sliding grooves; the device housing is provided with a mounting groove corresponding to the device housing; the left and right sides of the mounting groove are provided with slide rails corresponding to the sliding grooves; the bottom of the mounting groove is provided with a second power interface and a second communication interface corresponding to the first power interface and the first communication interface.

6. The portable blood circulation assist device according to claim 5, characterized in that, Both sides of the front end face of the device housing are provided with snap-fit ​​grooves, and the front end face of the device housing is provided with two limiting slides. The two limiting slides are located on both sides of the mounting groove. When the device housing slides into the mounting groove and slides to the bottom, each limiting slide can slide into the corresponding snap-fit ​​groove.

7. The portable blood circulation assist device according to claim 1, characterized in that, At least one strap buckle is also provided on the front end face of the device housing.

8. A blood circulation assist system, characterized in that, The device includes a main device and a portable blood circulation assist device as described in any one of claims 1 to 7 that is detachably electrically connected to the main device. The main device includes a device housing and a device control module disposed within the device housing and a visual interaction module disposed on the device housing.

9. A control method for a portable blood circulation assist device, characterized in that, The method for controlling the portable blood circulation assist device as described in any one of claims 1 to 7 includes: Acquire electrocardiogram waveforms and blood oxygen data; Determine the real-time heart rate based on the described electrocardiogram waveform; Based on the real-time heart rate, the discharge frequency of multiple electrical stimulation components is determined; The discharge intensity of multiple electrical stimulation components is determined based on the blood oxygen data, and the discharge intensity is negatively correlated with the blood oxygen data; Based on the discharge frequency and the electrocardiogram waveform, the R-wave period of the electrocardiogram waveform for which an electrical stimulation signal needs to be released is determined. Within the R-wave cycle of the electrocardiogram waveform that requires the release of an electrical stimulation signal, the electrical stimulation component for releasing an electrical stimulation signal to the lower leg releases an electrical stimulation signal 30 milliseconds after the R-wave peak and continues until the start of the T-wave. Then, 50 milliseconds after the R-wave peak, the electrical stimulation component for releasing an electrical stimulation signal to the thigh releases an electrical stimulation signal and continues until the start of the T-wave.

10. The control method for the portable blood circulation assist device according to claim 9, characterized in that, When the heart rate is between 60 and 80 bpm, multiple electrical stimulation components release an electrical stimulation signal once per R-wave cycle; when the heart rate is between 80 and 120 bpm, multiple electrical stimulation components release an electrical stimulation signal once every two R-wave cycles.

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