Adaptive parameter adjustment method and system for a shaping magnetic stimulator

Abstract

The application provides a self-adaptive parameter adjustment method and system of a shaping magnetic stimulation instrument, which comprises adjusting stimulation parameters of the magnetic stimulation instrument, collecting muscle strength values of a current user's target muscle group in real time, determining final stimulation parameters and muscle strength value change amplitudes in a first cycle; identifying a muscle type of the current user through the final stimulation parameters and the muscle strength value change amplitudes; determining a self-adaptive intensity adjustment strategy of the current user through the muscle type; and automatically adjusting stimulation parameters of a subsequent cycle of the user according to the final stimulation parameters and the muscle strength values and the self-adaptive intensity adjustment strategy. The application introduces objective indexes, so that the shaping process is visualized, and thus is safer and more reliable, each shaping cycle reaches a peak contraction most suitable for the current user, so that the shaping effect is improved, therapist resources are saved, and labor costs are reduced.

Description

Technical Field

[0001] This invention relates to the field of magnetic stimulation shaping technology, specifically to an adaptive parameter adjustment method and system for a shaping magnetic stimulator. Background Technology

[0002] With the development of society and the economy, a well-proportioned and beautiful body curve has become an increasingly popular goal for those who value beauty. The human body's contours are mainly shaped by muscles and fat. A suitable amount of fat evenly covers muscles and bones, forming the body's unique curves and creating an aesthetic texture and volume. Due to factors such as aging, pregnancy and childbirth, prolonged sitting at work, lack of exercise, and excessive diet, changes in the size and distribution of fat cells, as well as insufficient muscle, can cause the body to become out of shape, appearing bloated, loose, and aged. Currently, the mainstream body sculpting techniques include: fat pad removal, negative pressure liposuction, injectable lipolysis, autologous fat grafting, ultrasound-assisted liposuction, power-assisted liposuction, water jet-assisted liposuction, radiofrequency lipolysis, laser lipolysis, and magnetic stimulation body sculpting. Among these, the magnetic stimulation body sculpting technique, which has emerged in recent years, not only has the advantages of being non-invasive, painless, requiring no anesthesia, having no recovery period, not needing to wear shapewear for a long time, and allowing patients to leave immediately after the procedure, but it is also the only technique that simultaneously acts on muscles and fat, and is receiving increasing attention and praise.

[0003] Magnetic stimulation shaping technology generates a high-intensity changing magnetic field through the host and sends it to the coil head. This magnetic field penetrates adipose tissue and generates an induced current in the target muscle group, causing motor neurons to depolarize and inducing peak muscle contraction. This increases muscle strength and tone, improves muscle mass, accelerates fat metabolism, and shapes the body curves. At the same time, higher muscle mass can improve metabolic capacity, helping to better metabolize existing fat and prevent new fat accumulation, thus creating a lean physique.

[0004] However, current sensor materials are largely made of metal, and the alternating strong magnetic field generated by magnetic stimulators can severely interfere with sensors containing metal components, making it impossible to accurately collect real-time muscle strength data. Furthermore, the field of magnetic stimulation for body sculpting currently lacks scientifically quantifiable indicators for real-time monitoring of muscle contraction; treatment relies primarily on the therapist's personal experience, inquiries, and the user's subjective feelings and verbal feedback, making it difficult to guarantee objectivity and safety. Due to human tolerance mechanisms and muscle fatigue, different parameters need to be adjusted for different users in each stimulation cycle according to the progress of the treatment. When multiple users are sculpting simultaneously, the number of therapists is often insufficient. Additionally, during treatment, setting parameters too low results in insufficient muscle contraction and poor sculpting effects; setting parameters too high can easily cause muscle damage, induce stomach problems, menstrual issues in women, and even epilepsy. Summary of the Invention

[0005] To address the shortcomings of existing technologies, the purpose of this invention is to provide an adaptive parameter adjustment method and system for orthokeratology magnetic stimulators. This method can solve the problem that existing magnetic stimulators mainly rely on the therapist's personal experience and the user's subjective feelings and verbal feedback to guide the treatment process, making it difficult to guarantee objectivity and safety.

[0006] To achieve the above objectives, the present invention provides the following technical solution:

[0007] This invention is achieved through the following technical solution: an adaptive parameter adjustment method for a shaping magnetic stimulator, comprising:

[0008] Adjust the stimulation parameters of the magnetic stimulator, collect the muscle strength values ​​of the target muscle group of the current user in real time, and determine the final stimulation parameters and the range of change of muscle strength values ​​in the first cycle;

[0009] The muscle type of the current user is identified by the final stimulation parameters and the magnitude of the change in muscle strength.

[0010] The adaptive intensity adjustment strategy for the current user is determined based on the muscle type.

[0011] The stimulation parameters for subsequent cycles are automatically adjusted based on the final stimulation parameters, muscle strength values, and an adaptive intensity adjustment strategy.

[0012] Furthermore, the real-time acquisition of the muscle strength value of the current user's target muscle group includes acquiring the muscle strength value of the current user's target muscle group using a signal acquisition module; the signal acquisition module includes a pressure bladder, an air tube, a pressure sensor, an air pump, and a solenoid valve; the pressure bladder is connected to the pressure sensor and is installed on the coil head of the magnetic stimulator; the pressure bladder is connected to the air pump and the air tube, and a solenoid valve is installed inside the air tube.

[0013] Furthermore, this also includes initializing the airbag to achieve the optimal pressure state; including...

[0014] Set the initial default values ​​for the pressure airbag;

[0015] Determine the error between the current pressure value of the airbag and the initial default value, specifically as follows:

[0016] P_error(t)=P(t)-P_Initial_Set;

[0017] The control signal Control_Air(t) is calculated based on the error P_error(t) between the current pressure value of the airbag and the initial default value.

[0018] Based on the sign of the error P_error(t), the microcontroller sends a control signal to control the inflation and deflation of the airbag, so that the airbag is in the optimal pressure state.

[0019] Further, the stimulation parameters are an array, including stimulation intensity, frequency, number of pulses, interval, and duration.

[0020] Further, the determination of the final stimulation parameters in the first cycle is based on the real-time muscle strength value, waveform, and the subjective feeling of the current user; the first cycle includes a warm-up mode, a shaping mode, and a relaxation mode.

[0021] Further, the identification of the muscle type is as follows:

[0022] Adjust the muscle strength value to the preset reference value P_Start_Ref. The shaping mode has a total of N pulses, that is, N peak contractions are performed, and the contraction mean value is P_1_i (i = 1, 2,..., N);

[0023] According to the final stimulation parameter S_1 in the shaping mode of the first cycle and the amplitude change ΔP of the muscle strength value, identify the muscle strength type M(i): when Threshold_S_lb_i < S_1 ≤ Threshold_S_ub_i and Threshold_P_lb_i < ΔP ≤ Threshold_P_ub_i, determine that the muscle type is M(i);

[0024] Among them, Threshold_S_lb_i is the lower limit of the determination threshold of the stimulation parameter of the i-th muscle type, and Threshold_S_ub_i is the upper limit of the determination threshold of the stimulation parameter of the i-th muscle type;

[0025] Threshold_P_lb_i is the lower limit of the determination threshold of the amplitude change of the muscle strength value of the i-th muscle type, and Threshold_P_ub_i is the upper limit of the determination threshold of the amplitude change of the muscle strength value of the i-th muscle type.

[0026] Further, the determination of the adaptive intensity adjustment strategy for the current user based on the muscle type includes:

[0027] Set the difference between the muscle strength value at the current moment and the reference muscle strength value reached in the first cycle as:

[0028] P_delta(t) = (P_Start_Ref + ΔP) - P(t);

[0029] According to the current adaptive intensity adjustment strategy T(i) and the muscle strength value difference P_delta(t), calculate the control signal Control_delta(t):

[0030] Based on the sign of the muscle strength difference P_delta(t), the microcontroller sends a control signal Control_delta(t) to the stimulation host of the magnetic stimulator to adjust the stimulation parameters.

[0031] An adaptive parameter adjustment system for a shaping magnetic stimulator, the system comprising:

[0032] Signal acquisition module: The signal acquisition module is used to acquire the contraction state of the current user's target muscle group in real time;

[0033] Signal processing module: The signal processing module is connected to the signal acquisition module. The signal processing module is used to process the acquired signals, transform the signals into muscle strength values ​​that are easy to analyze and identify, and acquire the real-time stimulation parameters output by the magnetic stimulator.

[0034] Microcontroller: The microcontroller is connected to the signal processing module. The microcontroller is used to receive, store, and process muscle strength values ​​and stimulation parameters. The microcontroller identifies the current user's muscle type by controlling the real-time air pressure of the pressure bag and combining the information collected by the signal acquisition module, determines the current user's adaptive intensity adjustment strategy, and determines the stimulation parameters for the user's subsequent cycles.

[0035] Communication module: The communication module is connected to the microcontroller;

[0036] Display module: The display module is connected to the communication module and is used to display real-time muscle strength curves, muscle strength values, and magnetic stimulation parameters;

[0037] Magnetic stimulator: The magnetic stimulator is connected to a communication module. The magnetic stimulator receives signals sent by a microcontroller through the communication module and emits electromagnetic waves of corresponding frequency, intensity, number of pulses, interval, and duration to the coil tap head. The coil tap head applies the electromagnetic waves to the target muscles of the human body for shaping.

[0038] Furthermore, the communication module includes wired communication and wireless communication. The wired communication includes one or more of the following: STD and CAMAC bus, ISA bus, VXI bus, PCI, Compact and PXI bus, RS-232C, RS-422A, RS-485, USB, IEEE-1943, IEEE488, SCSI bus, and MXI bus. The wireless communication includes one or more of the following: IEEE 802.15.4 protocol, ZigBee protocol, Bluetooth protocol, LoRa, and UWB communication methods.

[0039] Compared with the prior art, the beneficial effects of the present invention include:

[0040] This invention collects the muscle strength values ​​of the target muscle group in real time, identifies the user's muscle type based on the final stimulation parameters and the magnitude of muscle strength changes during the first cycle, and determines an adaptive intensity adjustment strategy for the current user based on the identified muscle type. In subsequent cycles, the stimulation parameters are automatically adjusted according to the stimulation parameters, muscle strength values, and the adaptive intensity adjustment strategy to bring the target muscle group to the most suitable contraction state, thereby ensuring the shaping effect. This invention introduces objective indicators to make the shaping process visible, thus making it safer and more reliable. Each shaping cycle reaches the peak contraction most suitable for the current user, thereby improving the shaping effect, saving therapist resources, and reducing labor costs. Attached Figure Description

[0041] The disclosure of this invention is illustrated with reference to the accompanying drawings. It should be understood that the drawings are for illustrative purposes only and are not intended to limit the scope of protection of this invention. In the drawings, the same reference numerals are used to refer to the same parts. Wherein:

[0042] Figure 1 This is a schematic diagram of the adaptive parameter adjustment method of the shaping magnetic stimulator of the present invention;

[0043] Figure 2 This is a system block diagram of the adaptive parameter adjustment system of the shaping magnetic stimulator of the present invention;

[0044] Figure 3 This is a flowchart illustrating the adaptive intensity adjustment strategy for determining the current user based on muscle type, as described in this invention.

[0045] Figure 4 This is a diagram of the display interface of the present invention via the display module;

[0046] Figure 5 This is a schematic diagram of the initialization process of the present invention using a coil-loaded beater head;

[0047] Figure 6 This is a waveform diagram of the manually adjusted muscle strength value in an embodiment of the present invention;

[0048] Figure 7 The image shows the waveform of the adaptive adjustment parameter muscle strength value in an embodiment of the present invention. Detailed Implementation

[0049] It is readily understood that, based on the technical solution of this invention, those skilled in the art can propose various interchangeable structural methods and implementations without altering the essential spirit of the invention. Therefore, the following detailed embodiments and accompanying drawings are merely illustrative examples of the technical solution of this invention and should not be considered as the entirety of the invention or as limitations or restrictions on the technical solution of this invention.

[0050] This invention utilizes a signal acquisition module to collect the muscle strength values ​​of the target muscle group of the current user during the shaping process of a magnetic stimulator. The signal acquisition module includes a pressure bladder, an air tube, a pressure sensor, an air pump, and a solenoid valve. The pressure bladder is connected to the pressure sensor and is mounted on the coil head of the magnetic stimulator. The pressure bladder is connected to the air pump, which is used to inflate and pressurize the pressure bladder. The pressure bladder is also connected to the air tube, and a solenoid valve is installed inside the air tube. Opening the solenoid valve allows the gas inside the pressure bladder to be discharged, reducing the air pressure in the pressure bladder. The pressure value of the pressure sensor represents the muscle strength value during muscle contraction, thereby realizing the acquisition of muscle state signals.

[0051] The collected muscle state signals can also be electromyographic signals from the skin surface, pressure signals collected using pressure sensors and fluid devices, and mechanical waves (frequency in the range of 10 Hz to 10 Hz). 10 (Hz) or electromagnetic waves (frequency between 10Hz and 10Hz) 20 Image signals (Hz); surface electromyography signals use circular carbon fiber electrodes with notches attached to the target muscle group; pressure signals are signals collected by filling the acquisition device with fluids such as gas or liquid, and the target muscle deforms when stimulated, causing fluid changes; image signals can be ultrasound imaging, visible light imaging, infrared, microwave imaging, X-ray imaging, X-CT imaging, magnetic resonance imaging, radionuclide imaging, molecular imaging, etc.

[0052] For example, the present invention uses a pressure airbag to collect muscle state signals.

[0053] This invention provides an adaptive parameter adjustment method for a shaping magnetic stimulator, the method being as follows: Figure 1 As shown, it includes the following steps:

[0054] Step 1: Initialize the pressure airbag to achieve the optimal pressure state;

[0055] During the data acquisition process, if the air pressure of the pressure bag is too low, the pressure sensor will be inaccurate, resulting in inaccurate muscle strength values ​​and low algorithm discrimination. If the air pressure is too high, the distance between the patient's target muscle group and the coil head will be too large, reducing the intensity of magnetic stimulation and reducing the shaping effect. Therefore, before data acquisition, the air pressure of the pressure bag needs to be controlled at the most suitable initial default air pressure value P_Initial_Set.

[0056] Meanwhile, due to prolonged use by different users, the airbag will inevitably leak air and deform, causing the pressure value to deviate from the initial setting. To solve these problems, this invention discloses an intelligent pressure control algorithm that ensures the airbag is in the optimal pressure state before each user uses it.

[0057] The pressure airbag operates in two modes: intelligent pressure control mode and shaping mode.

[0058] Correspondingly, the working status variable of the airbag is Working_Flag;

[0059] When the switch is in the off state: Working_Flag = 0;

[0060] When the switch is on and no one is using the airbag: Working_Flag = 1, the airbag is in intelligent pressure control mode. The microcontroller controls the air pump and solenoid valve to intelligently inflate and deflate the airbag, keeping it at the initial default value: P_Initial_Set.

[0061] When the switch is on and the user is wearing a pressure airbag for shaping: Working_Flag=2, the pressure airbag is in shaping mode. The air pump and solenoid valve will not automatically inflate or deflate, but will only work under the user's command to adjust the air pressure of the pressure airbag according to the user's needs.

[0062] Specifically, when the device is first turned on or when a new user is using the magnetic stimulator, there is no pressure from the coil tap and straps on the pressure bladder. At this time, Working_Flag = 1, and intelligent pressure control is performed.

[0063] 1.1 Set the initial default value P_Initial_Set for the pressure airbag;

[0064] 1.2. The error between the current pressure value P(t) of the airbag and the initial default value P_Initial_Set is determined as follows:

[0065] P_error(t)=P(t)-P_Initial_Set;

[0066] 1.3 The microcontroller calculates the control signal Control_Air(t) based on the error P_error(t) between the current airbag pressure value and the initial default value. The calculation strategy is that the larger the absolute value of P_error(t), the larger the absolute value of the control signal Control_Air(t) should be. The specific algorithm includes, but is not limited to, a piecewise linear algorithm. The piecewise linear algorithm is as follows:

[0067]

[0068] In the formula, K j Threshold_j and Threshold_Neg_j represent K respectively. j Threshold_j is the adjustment coefficient, representing the positive error threshold; Threshold_Neg_j is the negative error threshold.

[0069] 1.4. Based on the sign of the error P_error(t), the microcontroller sends a control signal to control the inflation and deflation of the airbag, so that the airbag is in the optimal pressure state. Specifically:

[0070] When P_error(t) is negative, i.e. P_error(t)<0, the microcontroller sends the control signal Control_Air(t) to the air pump to inflate the pressure bladder;

[0071] When P_error(t) is positive, i.e. P_error(t)>0, the microcontroller sends the control signal Control_Air(t) to the solenoid valve to release the pressure bladder;

[0072] When P_error(t) = 0, neither the air pump nor the solenoid valve works.

[0073] Step 2: Adjust the stimulation parameters of the magnetic stimulator, collect the muscle strength values ​​of the target muscle group of the current user in real time, and determine the final stimulation parameters and the range of change in muscle strength values ​​in the first cycle;

[0074] A typical complete shaping process can be divided into 6 cycles, each cycle consisting of three modes: warm-up mode, shaping mode, and relaxation mode. The warm-up mode typically has a main frequency of 30Hz and its main function is to adapt muscles and warm up. The shaping mode has a main frequency of 40Hz and its main function is to achieve peak contraction and sculpt lines. The relaxation mode has a main frequency of 5Hz and its main function is to expel lactic acid and relieve fatigue.

[0075] In the first cycle: After adjusting the pressure bladder to the optimal pressure state in step one, fix the pressure bladder to the coil head, adjust the tension of the coil head strap, and wear the coil head, as follows. Figure 5 As shown, a coil patter head is worn on the waist; at the start of shaping, the tightness of the current user's strap is adjusted so that the pressure airbag value (i.e., muscle strength value) is the starting reference value P_Start_Ref; the stimulation parameters of the magnetic stimulator are manually adjusted; the stimulation parameters are an array, including stimulation intensity, frequency, number of pulses, interval, and duration; the expression of the stimulation parameters can be expressed as S(t)=[Strength(t); Frequency(t); Cycle(t); Gap(t); Duration(t)]; at the start of the first cycle, the therapist adjusts the tightness of the strap to adjust the pressure airbag value to the starting reference value P_Start_Ref, the shaping mode has a total of N pulses, that is, N peak contractions, the average contraction value is P_1_i (i=1,2,…,N); at the end of the first cycle, the final stimulation parameter S_1 of the shaping mode is determined according to the real-time muscle strength value, waveform and the current user's subjective feeling in the first cycle, and the amplitude of the change in muscle strength value △P is obtained, where △P is:

[0076]

[0077] Where N is the number of pulses, and P_1_i (i = 1, 2,..., N) is the average value of muscle contraction.

[0078] Step 3: Identify the muscle type of the current user based on the final stimulation parameter and the change range of muscle strength value;

[0079] Based on the final stimulation parameter S_1 and the change amplitude ΔP of muscle strength value obtained in Step 2, identify the muscle strength type M(i):

[0080] When Threshold_S_lb_i < S_1 ≤ Threshold_S_ub_i and Threshold_P_lb_i < ΔP ≤ Threshold_P_ub_i, determine that the muscle type is M(i).

[0081] Among them, Threshold_S_lb_i is the lower limit of the determination threshold of the stimulation parameter of the i-th muscle type, and Threshold_S_ub_i is the upper limit of the determination threshold of the stimulation parameter of the i-th muscle type;

[0082] Threshold_P_lb_i is the lower limit of the determination threshold of the change amplitude of the muscle strength value of the i-th muscle type, and Threshold_P_ub_i is the upper limit of the determination threshold of the change amplitude of the muscle strength value of the i-th muscle type.

[0083] Step 4: Determine the adaptive intensity adjustment strategy of the current user based on the muscle type; the process is as Figure 3 shown,

[0084] Based on the muscle type M(i) identified in the first cycle, find the corresponding adaptive intensity adjustment strategy T(i), specifically:

[0085] 4.1. Let the difference between the current muscle strength value and the reference muscle strength value reached in the first cycle be:

[0086] P_delta(t) = (P_Start_Ref + ΔP) - P(t)

[0087] 4.2. The single-chip microcomputer calculates the control signal Control_delta(t) according to the current adaptive intensity adjustment strategy T(i) and the muscle strength value difference P_delta(t):

[0088] Control_delta(t) = f(P_delta(t));

[0089] The specific algorithm includes but is not limited to the PID algorithm; the PID algorithm is specifically:

[0090]

[0091] Where: K p (i) represents the proportional term, T i (i) represents the integral term, T d (i) is the differential term; K p (i), T i (i), T d The value of (i) will significantly affect the speed and effectiveness of achieving the muscle strength target, and is determined by the adjustment strategy T(i); different T(i) correspond to different K values. p (i), T i (i), T d (i). First determine K. p (i) A suitable K p (i) Accelerate the adjustment speed; then determine T. i (i), T i (i) Steady-state error can be eliminated; finally, T is determined. d (i), T d (i) It can reflect the rate of change of the difference.

[0092] 4.3. Based on the sign of the muscle strength difference P_delta(t), the microcontroller sends a control signal Control_delta(t) to the stimulation host of the magnetic stimulator to adjust the stimulation parameters, specifically:

[0093] When P_delta(t) is positive, that is, P_delta(t)>0, the microcontroller sends the control signal Control_delta(t) to the stimulation host according to the current control strategy T(i) to increase the stimulation parameters;

[0094] When P_delta(t) is negative, that is, when P_delta(t) < 0, the microcontroller sends the control signal Control_delta(t) to the stimulation host according to the current control strategy T(i) to lower the stimulation parameters.

[0095] When P_delta(t) = 0, the stimulus parameters remain unchanged.

[0096] Step 5: Automatically adjust the stimulation parameters for subsequent cycles of the user based on the final stimulation parameters, muscle strength values, and adaptive intensity adjustment strategy;

[0097] The magnetic stimulator adaptively adjusts the stimulation parameters for the remaining five cycles based on the data from the first cycle, which can save five-sixths of the manpower cost. Based on objective muscle strength values, it can maximize user safety and the most suitable peak contraction, without being limited by the therapist's personal experience level.

[0098] Implementation Case:

[0099] Without loss of generality, take the second user in the tenth internal experiment as an example; the stimulation parameters S include stimulation intensity, frequency, number of pulses, interval, duration, etc. For the convenience of demonstration, in the specific embodiment, the intensity, which is the most frequently adjusted clinically, is taken as an example.

[0100] The pressure airbag is inflated to the initial set value P_Initial_Set = 8 mmHg. The user lies flat on the treatment bed, buckles the pressure airbag on the coil head, places it on the abdomen, and adjusts the tightness of the strap until the pressure value of the pressure airbag is the starting reference value P_Start_Ref = 30 mmHg.

[0101] The first shaping is manually adjusted by the therapist. In the first cycle, it is adjusted to 35% intensity, and no adjustment is made in subsequent cycles. The muscle strength value continuously decreases as the cycle progresses. The amplitude of the muscle strength value decreases from 40 to 20. The shaping effect continuously decreases from the second cycle to the sixth cycle, as Figure 6 shown.

[0102] For the convenience of understanding, a simplified version of the muscle type identification rule based only on stimulation intensity and the amplitude of muscle strength value (omitting stimulation parameters such as frequency, number of pulses, interval, duration, etc.) is as follows:

[0103] Muscle type M(1): 80 < S_1 ≤ 100 and △P > 20, with high magnetic tolerance, more abdominal fat, and more muscles;

[0104] Muscle type M(2): 80 < S_1 ≤ 100 and 10 < △P ≤ 20, with high magnetic tolerance, more abdominal fat, and average muscles;

[0105] Muscle type M(3): 80 < S_1 ≤ 100 and △P ≤ 10, with high magnetic tolerance, a lot of abdominal fat, and fewer muscles;

[0106] Muscle type M(4): 60 < S_1 ≤ 80 and △P > 20, with relatively high magnetic tolerance, average abdominal fat, and more muscles

[0107] Muscle type M(5): 60 < S_1 ≤ 80 and 10 < △P ≤ 20, with high magnetic tolerance, average abdominal fat, and average muscles

[0108] Muscle type M(6): 60 < S_1 ≤ 80 and △P ≤ 10, with high magnetic tolerance, average abdominal fat, and fewer muscles;

[0109] Muscle type M(7): 20 < S_1 ≤ 60 and △P > 20, with average magnetic tolerance, average abdominal fat, and more muscles;

[0110] Muscle type M(8): 20 < S_1 ≤ 60 and 10 < △P ≤ 20, with general magnetic tolerance, general abdominal fat, and general muscles;

[0111] Muscle type M(9): 20 < S_1 ≤ 60 and △P ≤ 10, with general magnetic tolerance, general abdominal fat, and less muscles;

[0112] Muscle type M(10): 0 < S_1 ≤ 20 and △P > 20, with low magnetic tolerance, little abdominal fat, and more muscles

[0113] Muscle type M(11): 0 < S_1 ≤ 20 and 10 < △P ≤ 20, with low magnetic tolerance, little abdominal fat, and general muscles;

[0114] Muscle type M(12): 0 < S_1 ≤ 20 and △P ≤ 10, with low magnetic tolerance, little abdominal fat, and less muscles;

[0115] The second shaping is the adaptive adjustment disclosed in the present invention. According to the final stimulation intensity value S_1 = 35% and the amplitude of muscle strength value change △P = 40 in the first cycle, it is identified that this user has general tolerance, general abdominal fat, and more muscles, and the adjustment strategy T(7) is selected; since the tolerance is general, the intensity change each time cannot be too large; the general fat thickness indicates that the user is not too sensitive to pain and the adjustment risk is small; more muscles mean that a smaller adjustment of the stimulation parameters can offset the effects brought by tolerance and muscle fatigue.

[0116] In the adjustment strategy T(7), K p (i) = 2, T i (i) = 5, T d (i) = 3. The intensity in the second cycle stabilizes at 38%, the intensity in the third cycle stabilizes at 41%, the intensity in the fourth cycle stabilizes at 43%, the intensity in the fifth cycle stabilizes at 45%, and the intensity in the sixth cycle stabilizes at 46%. The amplitude of the muscle strength value in each cycle stabilizes at about 40, and the shaping effect remains good, as Figure 7 shown.

[0117] The present invention provides an adaptive parameter adjustment system for a shaping magnetic stimulator, as Figure 2 shown, and the system includes:

[0118] Signal Acquisition Module: The signal acquisition module is used to acquire the contraction state of the target muscle group of the current user in real time. The signal acquisition module includes a pressure bladder, an air tube, a pressure sensor, an air pump, and a solenoid valve. The pressure bladder is connected to the pressure sensor and is installed on the coil head of the magnetic stimulator. The pressure bladder is connected to the air pump and the air tube, and a solenoid valve is installed inside the air tube. The pressure value of the pressure sensor is used to characterize the muscle force value during muscle contraction, thereby acquiring the muscle state signal. The acquired muscle state signal can also be the electromyographic signal of the skin surface. The pressure signal acquired using the pressure sensor and fluid device is based on mechanical waves (frequency between 10Hz and 10...). 10 (Hz) or electromagnetic waves (frequency between 10Hz and 10Hz) 20 Image signals (Hz); surface electromyography signals use circular carbon fiber electrodes with notches attached to the target muscle group; pressure signals are signals collected by filling the acquisition device with fluids such as gas or liquid, and the target muscle deforms when stimulated, causing fluid changes; image signals can be ultrasound imaging, visible light imaging, infrared, microwave imaging, X-ray imaging, X-CT imaging, magnetic resonance imaging, radionuclide imaging, molecular imaging, etc.

[0119] Signal processing module: The signal processing module is connected to the signal acquisition module. The signal processing module is used to process the acquired signals, transform the signals into muscle strength values ​​that are easy to analyze and identify, and acquire the real-time stimulation parameters output by the magnetic stimulator.

[0120] Microcontroller: The microcontroller is connected to the signal processing module. The microcontroller is used to receive, store, and process muscle strength values ​​and stimulation parameters. The microcontroller identifies the current user's muscle type by controlling the real-time air pressure of the pressure bag and combining the information collected by the signal acquisition module, determines the current user's adaptive intensity adjustment strategy, and determines the stimulation parameters for the user's subsequent cycles. The microcontroller model includes, but is not limited to, STM32 and GD32.

[0121] Communication Module: The communication module connects to the microcontroller; the communication module includes wired communication and wireless communication. The wired communication includes one or more of the following: STD and CAMAC bus, ISA bus, VXI bus, PCI, Compact and PXI bus, RS-232C, RS-422A, RS-485, USB, IEEE-1943, IEEE488, SCSI bus, and MXI bus; the wireless communication includes one or more of the following: IEEE 802.15.4 protocol, ZigBee protocol, Bluetooth protocol, LoRa, and UWB communication methods.

[0122] Display Module: The display module is connected to the communication module and is used to display real-time muscle strength curves, muscle strength values, and magnetic stimulation parameters; the interface displayed by the display module is as follows: Figure 4 As shown.

[0123] Magnetic stimulator: The magnetic stimulator is connected to a communication module. The magnetic stimulator receives signals sent by a microcontroller through the communication module and emits electromagnetic waves of corresponding frequency, intensity, number of pulses, interval, and duration to the coil tap head. The coil tap head applies the electromagnetic waves to the target muscles of the human body for shaping.

[0124] The adaptive parameter adjustment system of the orthokeratology magnetic stimulator also includes

[0125] Safety button: The safety button is used to start and stop the magnetic stimulator;

[0126] And / or infrared remote control: where the infrared transmitter is in a position that can be operated by the user of the magnetic stimulator, and the infrared receiver controls the start and stop of the magnetic stimulator through the logic control unit;

[0127] The magnetic stimulator can also be started and stopped via voice control and gesture control to address situations where parameters may increase beyond the user's pain threshold, causing discomfort.

[0128] This invention collects the muscle strength values ​​of the target muscle group in real time, identifies the user's muscle type based on the final stimulation parameters and the magnitude of muscle strength changes during the first cycle, and determines an adaptive intensity adjustment strategy for the current user based on the identified muscle type. In subsequent cycles, the stimulation parameters are automatically adjusted according to the stimulation parameters, muscle strength values, and the adaptive intensity adjustment strategy to bring the target muscle group to the most suitable contraction state, thereby ensuring the shaping effect. This invention introduces objective indicators to make the shaping process visible, thus making it safer and more reliable. Each shaping cycle reaches the peak contraction most suitable for the current user, thereby improving the shaping effect, saving therapist resources, and reducing labor costs.

[0129] The technical scope of this invention is not limited to the content described above. Those skilled in the art can make various modifications and variations to the above embodiments without departing from the technical concept of this invention, and all such modifications and variations should fall within the protection scope of this invention.

Claims

1. An adaptive parameter adjustment method for a shaping magnetic stimulator, characterized in that: including Adjust the stimulation parameters of the magnetic stimulator, collect the muscle strength value of the current user's target muscle group in real time, and determine the final stimulation parameters and the change range of muscle strength value in the first cycle; Identify the muscle type of the current user through the final stimulation parameters and the change range of muscle strength value; Determine the adaptive intensity adjustment strategy of the current user according to the muscle type; Automatically adjust the stimulation parameters of the user's subsequent cycles according to the final stimulation parameters, muscle strength value and adaptive intensity adjustment strategy; The real-time collection of the muscle strength value of the current user's target muscle group includes collecting the muscle strength value of the current user's target muscle group by using a signal collection module; the signal collection module includes a pressure airbag, an air duct, a pressure sensor, an air pump, and a solenoid valve; the pressure airbag is connected to the pressure sensor, and the pressure airbag is installed on the coil head of the magnetic stimulator; the pressure airbag is connected to the air pump, and the pressure airbag is connected to the air duct, and the solenoid valve is installed in the air duct; The identification of the muscle type is as follows: Adjust the muscle strength value to the preset reference value P_Start_Ref, and there are N pulses in the shaping mode, that is, N peak contractions are performed, and the contraction average value is P_1_i (i = 1, 2,..., N); According to the final stimulation parameter S_1 and the muscle strength value change amplitude △P in the shaping mode in the first cycle, identify the muscle strength type M(i): when Threshold_S_lb_i < S_1 ≤ Threshold_S_ub_i and Threshold_P_lb_i < △P ≤ Threshold_P_ub_i, determine that the muscle type is M(i); Among them, Threshold_S_lb_i is the lower limit of the determination threshold of the stimulation parameter of the i-th muscle type, and Threshold_S_ub_i is the upper limit of the determination threshold of the stimulation parameter of the i-th muscle type; Threshold_P_lb_i is the lower limit of the determination threshold of the muscle strength value change amplitude of the i-th muscle type, and Threshold_P_ub_i is the upper limit of the determination threshold of the muscle strength value change amplitude of the i-th muscle type; The determination of the adaptive intensity adjustment strategy of the current user according to the muscle type includes: Set the difference between the muscle strength value at the current moment and the reference muscle strength value reached in the first cycle as: P_delta(t) = (P_Start_Ref + △P) - P(t); According to the current adaptive intensity adjustment strategy T(i) and the muscle strength value difference P_delta(t), calculate the control signal Control_delta(t): According to the positive or negative of the muscle strength value difference P_delta(t), send the control signal Control_delta(t) to the stimulation host of the magnetic stimulator through the single-chip microcomputer to lower or raise the stimulation parameters.

2. The adaptive parameter adjustment method for the shaping magnetic stimulator according to claim 1, characterized in that: It also includes initializing the pressure airbag to make it in the optimal pressure state; including Set the initial default value of the pressure airbag; Determine the error between the pressure value of the pressure airbag at the current moment and the initial default value, specifically: P_error(t) = P(t) - P_Initial_Set; The control signal Control_Air(t) is calculated based on the error P_error(t) between the current pressure value of the airbag and the initial default value. Based on the sign of the error P_error(t), the microcontroller sends a control signal to control the inflation and deflation of the airbag, so that the airbag is in the optimal pressure state.

3. The adaptive parameter adjustment method for the shaping magnetic stimulator according to claim 1, characterized in that: The stimulation parameters are an array, including stimulation intensity, frequency, number of pulses, interval, and duration.

4. The adaptive parameter adjustment method for the shaping magnetic stimulator according to claim 1, characterized in that: The final stimulation parameters in the first cycle are determined based on real-time muscle strength, waveform, and the user's current subjective feelings; the first cycle includes a warm-up mode, a shaping mode, and a relaxation mode.

5. An adaptive parameter adjustment system for a shaping magnetic stimulator, a system according to any one of claims 1-4, comprising: Signal acquisition module: The signal acquisition module is used to acquire the contraction state of the current user's target muscle group in real time; Signal processing module: The signal processing module is connected to the signal acquisition module. The signal processing module is used to process the acquired signals, transform the signals into muscle strength values ​​that are easy to analyze and identify, and acquire the real-time stimulation parameters output by the magnetic stimulator. Microcontroller: The microcontroller is connected to the signal processing module. The microcontroller is used to receive, store, and process muscle strength values ​​and stimulation parameters. The microcontroller identifies the current user's muscle type by controlling the real-time air pressure of the pressure bag and combining the information collected by the signal acquisition module, determines the current user's adaptive intensity adjustment strategy, and determines the stimulation parameters for the user's subsequent cycles. Communication module: The communication module is connected to the microcontroller; Display module: The display module is connected to the communication module and is used to display real-time muscle strength curves, muscle strength values, and magnetic stimulation parameters; Magnetic stimulator: The magnetic stimulator is connected to a communication module. The magnetic stimulator receives signals sent by a microcontroller through the communication module and emits electromagnetic waves of corresponding frequency, intensity, number of pulses, interval, and duration to the coil tap head. The coil tap head applies the electromagnetic waves to the target muscles of the human body for shaping.

6. The adaptive parameter adjustment system of the shaping magnetic stimulator according to claim 5, characterized in that: The communication module includes wired communication and wireless communication. The wired communication includes one or more of the following: STD and CAMAC bus, ISA bus, VXI bus, PCI, Compact and PXI bus, RS-232C, RS-422A, RS-485, USB, IEEE-1943, IEEE488, SCSI bus, and MXI bus. The wireless communication includes one or more of the following: IEEE 802.15.4 protocol, ZigBee protocol, Bluetooth protocol, LoRa, and UWB communication methods.

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