WO2021213208A1 - 治疗仪及其控制方法 - Google Patents

治疗仪及其控制方法 Download PDF

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Publication number
WO2021213208A1
WO2021213208A1 PCT/CN2021/086691 CN2021086691W WO2021213208A1 WO 2021213208 A1 WO2021213208 A1 WO 2021213208A1 CN 2021086691 W CN2021086691 W CN 2021086691W WO 2021213208 A1 WO2021213208 A1 WO 2021213208A1
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Prior art keywords
pressure value
air pressure
treatment head
monitoring unit
collected
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PCT/CN2021/086691
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English (en)
French (fr)
Inventor
雷晓兵
李亚楠
黄上快
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深圳半岛医疗有限公司
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Publication of WO2021213208A1 publication Critical patent/WO2021213208A1/zh

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    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61N—ELECTROTHERAPY; MAGNETOTHERAPY; RADIATION THERAPY; ULTRASOUND THERAPY
    • A61N1/00—Electrotherapy; Circuits therefor
    • A61N1/18—Applying electric currents by contact electrodes
    • A61N1/32—Applying electric currents by contact electrodes alternating or intermittent currents
    • A61N1/36—Applying electric currents by contact electrodes alternating or intermittent currents for stimulation
    • A61N1/36007—Applying electric currents by contact electrodes alternating or intermittent currents for stimulation of urogenital or gastrointestinal organs, e.g. for incontinence control
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B5/00—Measuring for diagnostic purposes; Identification of persons
    • A61B5/22—Ergometry; Measuring muscular strength or the force of a muscular blow
    • A61B5/224—Measuring muscular strength
    • A61B5/227—Measuring muscular strength of constricting muscles, i.e. sphincters
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B5/00—Measuring for diagnostic purposes; Identification of persons
    • A61B5/24—Detecting, measuring or recording bioelectric or biomagnetic signals of the body or parts thereof
    • A61B5/316—Modalities, i.e. specific diagnostic methods
    • A61B5/389—Electromyography [EMG]
    • A61B5/391—Electromyography [EMG] of genito-urinary organs
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B5/00—Measuring for diagnostic purposes; Identification of persons
    • A61B5/45—For evaluating or diagnosing the musculoskeletal system or teeth
    • A61B5/4519—Muscles
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B5/00—Measuring for diagnostic purposes; Identification of persons
    • A61B5/72—Signal processing specially adapted for physiological signals or for diagnostic purposes
    • A61B5/7225—Details of analog processing, e.g. isolation amplifier, gain or sensitivity adjustment, filtering, baseline or drift compensation
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B5/00—Measuring for diagnostic purposes; Identification of persons
    • A61B5/72—Signal processing specially adapted for physiological signals or for diagnostic purposes
    • A61B5/7235—Details of waveform analysis
    • A61B5/725—Details of waveform analysis using specific filters therefor, e.g. Kalman or adaptive filters

Definitions

  • This application relates to the technical field of therapeutic equipment, and in particular to a therapeutic equipment and a control method thereof.
  • female pelvic floor dysfunction disease female pelvic Floor dysfunction (FPFD) is a collective term for a group of diseases caused by pelvic floor dysfunction caused by pelvic floor muscle tissue relaxation, injury, and pelvic support structure defects or degeneration.
  • FPFD female pelvic floor dysfunction
  • urinary incontinence urinary incontinence
  • UI pelvic organ prolapse
  • POP pelvic organ prolapse
  • FSD female sexual dysfunction
  • FI fecal incontinence
  • urinary incontinence and pelvic organ prolapse are the most common.
  • FPFD has become one of the five major diseases that affect women's quality of life, with many causes, but epidemiological investigations show that pregnancy and childbirth are the main and independent risk factors.
  • the symptoms of pelvic organ prolapse are not obvious in the early postpartum period and the parturient has no uncomfortable reaction, if rehabilitation training is not performed, After 10 to 15 years, the patient will suffer greatly because of the serious impact of the disease on the quality of life.
  • the early postpartum period (42d-3 months postpartum) is the relatively weakest period of human body function, but it is also the best period for recovery.
  • the main purpose of this application is to propose a control method for a therapeutic instrument, which aims to solve the technical problem of poor therapeutic effect of the therapeutic instrument.
  • a method for controlling a therapeutic apparatus proposed in the present application includes a therapeutic head, a monitoring unit for collecting air pressure in the therapeutic head and collecting electrical signals of muscle tissue, and outputting electrical signals to drive the therapeutic head pair
  • the power source for electrical stimulation of muscle tissue, and the control method of the therapeutic apparatus includes:
  • the treatment head is controlled to output electrical signals according to the physical therapy mode to electrically stimulate the muscle tissue.
  • the application also proposes a therapeutic apparatus, which includes a controller, a treatment head, and a monitoring unit.
  • the controller includes a memory, a processor, and a therapy stored in the memory and running on the processor.
  • the control program of the treatment device when the control program of the treatment device is executed by the processor, realizes the steps of the above-mentioned control method of the treatment device, and the control unit is respectively connected with the monitoring unit and the treatment head;
  • the monitoring unit is used to detect the air pressure value of the treatment head and the electrical signal of the human tissue contacted by the treatment head;
  • the controller is configured to generate a control signal according to the difference between the air pressure value and a preset first air pressure value and/or the electrical signal;
  • the treatment head is used to control the treatment head to output electrical signals according to the control signal.
  • the control method of the treatment device in the embodiment of the present application obtains the air pressure value in the treatment head collected by the monitoring unit and/or the electrical signal of the human tissue that the treatment head contacts the treatment head collected by the monitoring unit.
  • the pressure value of the treatment head can reflect the muscle strength information of the muscle tissue to which the treatment head is attached
  • the electrical signal of the human tissue contacted by the treatment head can reflect the electromyographic information of the muscle tissue to which the treatment head is attached.
  • the corresponding physical therapy mode is determined according to the difference between the collected air pressure value in the treatment head and the preset first air pressure value and/or the collected electrical signal of the muscle tissue.
  • the difference between the air pressure value in the treatment head and the preset first air pressure value can represent the change value of muscle strength, that is, the muscle strength information of muscle tissue changes.
  • the treatment head is controlled according to the physical therapy mode Output electrical signals for electrical stimulation of muscle tissue.
  • different differences and changes in electrical signals correspond to different physiotherapy modes, so that when the treatment device using this scheme has different feedback values, there are corresponding physiotherapy modes, thus realizing real-time feedback.
  • And can make the physical therapy instrument adjust the physical therapy mode according to the feedback value, which is more suitable for each user's situation.
  • the parameters based on it are more reasonable, thereby further improving the therapeutic effect of the therapeutic instrument and shortening the user's physical therapy time.
  • the technical solution of the present application can solve the technical problem of poor treatment effect of the treatment device in the prior art.
  • FIG. 1 is a schematic flowchart of an embodiment of a control method of a therapeutic apparatus according to the present application
  • FIG. 2 is a schematic flowchart of an embodiment of the control method of the therapeutic apparatus according to the present application
  • FIG. 3 is a schematic flowchart of an embodiment of the control method of the therapeutic apparatus according to the present application.
  • Fig. 4 is a schematic diagram of modules of the therapeutic apparatus of the present application.
  • This application proposes a control method for a therapeutic instrument. It is used to solve the technical problem of poor treatment effect of the existing treatment instrument.
  • the pelvic floor muscle tissue is used as the starting point to illustrate the starting point of this application.
  • the pelvic floor muscle tissue is the main component that maintains the support structure of the pelvic floor organs.
  • the pelvic floor muscle tissue is mainly composed of the levator ani muscle, which contains type 1 muscle fibers that maintain continuous tension. And 11 types of muscle fibers that maintain reflex and voluntary contraction.
  • the etiology of pelvic floor organ prolapse is not yet fully understood. At present, many studies believe that POP is due to pelvic floor muscle tissue, fascia and uterine ligament damage caused by vaginal delivery, aging estrogen levels, and congenital pelvic floor dysfunction.
  • pelvic floor dysfunction such as pelvic organ prolapse (POP) and stress Urinary incontinence ( Stress urinary incontinence.SUD and other series of pelvic floor injuries and defects. If not prevented and treated in time, pelvic floor dysfunction will continue to exist and further aggravate, affecting the pelvic floor function during perimenopause and even old age.
  • the first program is to exercise Kegel exercise for pelvic floor muscle tissue, which was advocated by Arnold Kegel in 1948.
  • the method of pelvic floor muscle exercise is simply to train the contraction of the levator ani muscle group.
  • the conscious contraction of the pelvic floor muscle tissue will raise the pelvic floor upward and forward, and squeeze the urethra, vagina and rectum to lift inward.
  • Ultrasound and MRI studies have confirmed the existence of this kind of improvement.
  • Contraction exercises will also increase the tension of the pelvic floor muscle tissue, improve the responsiveness of the muscle tissue, and strengthen the support force of the muscle tissue to maintain the weight of the pelvic internal organs, thereby reducing or preventing organ prolapse .
  • this method has its obvious disadvantages.
  • the pelvic floor muscle tissue contraction signal is fed back to the patient in a visual or auditory form such as a waveform display through the computer, and the wrong contraction action is continuously corrected to help the patient find the correct exercise method.
  • the Kegel exercise alone cannot effectively guarantee the correct and effective contraction exercise of the pelvic floor muscles and is not easy to adhere to.
  • Biofeedback ensures correct and effective pelvic floor muscle training.
  • the ultimate goal of biofeedback is to allow patients to perform correct pelvic floor muscle training without the help of biofeedback equipment, but this method is mainly aided by machines, and its therapeutic effect is extremely unstable.
  • Estrogen has been used for conservative treatment of stress urinary incontinence for decades.
  • the mechanism of estrogen treatment of stress urinary incontinence is multi-faceted: stimulate the growth of urethral epithelium; increase urethral mucosa
  • the blood supply of the inferior venous plexus affects the function of the connective tissue next to the bladder and urethra; the most important thing is to increase the tension of the muscle tissue that supports the pelvic floor structure.
  • a control method of a therapeutic apparatus includes:
  • the gas volume in the treatment head has been adjusted so that the treatment head fits the human tissue, and the gas volume will not change anymore.
  • the pressure of the treatment head The value is only affected by the contraction and expansion of the muscle tissue.
  • the pressure value of the treatment head can reflect the muscle strength information of the muscle tissue to which the treatment head is attached.
  • the muscle strength information refers to the contraction and other actions of the muscle tissue.
  • the compression force is detected by the monitoring unit to detect the air pressure value.
  • the electrical signal of the human tissue contacted by the treatment head can reflect the electromyography information of the muscle tissue to which the treatment head is attached.
  • the electromyography information is the electrical signal fed back by the muscle tissue, and the electrical signal is detected by the monitoring unit.
  • two kinds of feedback information are added to comprehensively confirm the information of muscle tissue, which can increase the diversity of parameter values and improve the accuracy of confirming the state of muscle tissue.
  • the preset first air pressure value is the air pressure value measured when the therapeutic head is set to fit the muscle tissue under the resting state of the muscle tissue.
  • the change can be determined according to the difference between the air pressure value and the first air pressure value.
  • Muscle strength information The collected air pressure value in the treatment head is the measured air pressure value when the muscle tissue is in a contracted state, and the treatment head and the muscle tissue are fitted together. That is, when the initial value is the first air pressure value, the changed muscle strength information can be conveniently measured through the above steps, and the state of the muscle tissue at the moment can be accurately determined based on the muscle strength information and the electromyographic information.
  • the physical therapy mode can be determined separately by the difference between the air pressure value and the preset first air pressure value.
  • the physical therapy mode can be determined solely by the collected electrical signals of the muscle tissue. Both are measuring the related state of muscle tissue, and both can accurately reflect the real-time state.
  • the physical therapy mode can also be determined based on the difference between the air pressure value and the preset first air pressure value and the electrical signal at the same time, which can further increase the fit between the physical therapy mode and the user and improve the physical therapy effect.
  • the physical therapy mode is to change the preset multiple modes, respectively corresponding to the difference between different air pressure values and the first air pressure value and different electrical signals. This mode is used by experimenters to obtain better physical therapy modes through multiple experiments.
  • the physical therapy mode is to control the treatment head to output a specific frequency electrical signal within a preset time.
  • the preset time and specific frequency are all the electrical signals and specific frequencies that are matched by the experimenter through multiple experiments and data collection.
  • the preset time of course, the preset time can also be set by the user, which can better match the user's usage habits.
  • the muscle tissue can be electrically stimulated to perform physical therapy on the muscle tissue. Below, take the pelvic floor muscle tissue as an example to illustrate the principle of electrical stimulation:
  • Electrical stimulation uses electrodes placed in the vagina to stimulate the pelvic floor muscle tissue and fascia with currents of different frequencies to enhance its strength and function. Electrical stimulation of the tissue makes it produce contraction speed and contraction time. The contraction increases the elasticity of the ligaments, intermittently. Contract the levator ani muscle and external sphincter, promote the improvement of pelvic blood circulation of muscle tissue, maintain its normal metabolic function, further enhance the tension of the levator ani muscle and other pelvic floor muscles, accelerate the repair of damaged tissues, strengthen the entire pelvic floor muscles, and promote The various organs of the pelvic floor should be functionally restored. It can also restore proprioception, inhibit muscle spasm, and reduce muscle tension.
  • Direct current can promote the dissipation of inflammation, improve tissue function, and promote the regeneration process.
  • electrical stimulation wakes up the contraction of pelvic floor muscle tissue, improves muscle strength, improves pelvic floor muscle strength, endurance and tension as a whole, and restores the coordination of pelvic floor supporting functions.
  • urethra the altered expression of myosin isomers affects striated muscle and causes skeletal muscle fiber hypertrophy; electrical stimulation can promote type I and II muscle fiber hypertrophy and repair the pelvic floor
  • the urethral support system fixes the urethra on the pelvic fascia tendon arch and the puborectalis muscle to enhance the ability of urethral closure. At the same time increase the elasticity and contractility of the vagina.
  • electrical stimulation repairs nerves, increases mucosal blood circulation, and improves nerve sensitivity of organs.
  • the afferent fibers connect to the detrusor nucleus of the sacral spinal cord through neurons to inhibit the excitability of the detrusor nucleus, and then pass to the detrusor through the pelvic nerve to inhibit the contraction of the detrusor.
  • the treatment instrument includes a treatment head, a monitoring unit and a power supply.
  • the output end of the power supply is connected to the power supply end of the treatment head.
  • the detection end of the monitoring unit is connected to the air inlet and outlet of the treatment head.
  • the second detection end of the monitoring unit is connected to the electrode of the treatment head. ⁇ Piece connection.
  • the monitoring unit collects the air pressure value in the treatment head and collects the electrical signal of the muscle tissue
  • the automatic inflation unit performs the inflation and deflation action
  • the power source outputs the electrical signal to drive the treatment head to electrically stimulate the muscle tissue.
  • the method further includes:
  • the user takes the initiative to test.
  • the gas volume in the treatment head will not change, and the air pressure value has a basis value.
  • the user actively performs a preset action to contract specific muscle tissues, thereby increasing the air pressure value.
  • it is convenient for the user to view.
  • the preset air pressure value at this time can be set by the user, or can be set by data in the database, so that when the amplitude of the air pressure value reaches the preset air pressure value, the treatment head is controlled to output a single time of the preset size Electrical stimulation. It can realize real-time detection and real-time feedback treatment, and in conjunction with the user's active contraction, a single contraction combined with a single electrical stimulation can achieve more targeted treatment of muscle tissue, thereby achieving better treatment effects.
  • the preset size of a single electrical stimulation is the size corresponding to the air pressure value.
  • the manufacturer collects a variety of data in advance to set the parameters, that is, when the treatment head fits well with the cavity, then the treatment head With a certain fitting air pressure value, normal muscle tissue contraction corresponds to a normal air pressure value. If it is less than this value and is in the first preset range value, the treatment head outputs electrical stimulation of the first voltage value, if it is less than this value And when it is in the second preset range value, the treatment head outputs electrical stimulation of the second voltage value. Therefore, the treatment head can determine the magnitude of the corresponding output electrical stimulation voltage according to the air pressure values of different range values, and further achieve a better treatment effect. If it is designed into the game, it can be set to simple mode, normal mode, and difficult mode to stimulate the user's desire to win and lose, and to motivate the user to challenge next time in real time to achieve self-motivation.
  • the method further includes:
  • the treatment head When the amplitude of the electrical signal meets the preset electrical signal, the treatment head is controlled to output a single electrical stimulation of a preset magnitude.
  • the amplitude of continuous contraction is greater than 30uv, and the signal amplitude does not decrease or almost does not decrease during the entire 60s permanent contraction. It indicates that the muscle tissue is in a normal state, and if it is less than 30uv, it indicates that physical therapy is needed.
  • the preset electrical signal can be set to be lower than 30uv. Then the treatment head is controlled to output a single electrical stimulation of a preset size.
  • the therapeutic apparatus further includes an automatic inflation and deflation unit, which is connected to the treatment head through a gas path, and is used to perform inflation and deflation actions.
  • an automatic inflation and deflation unit which is connected to the treatment head through a gas path, and is used to perform inflation and deflation actions.
  • the second air pressure value is the air pressure value when the treatment head with a certain amount of gas is in the air state.
  • the third air pressure value is obtained after putting the therapeutic instrument into the cavity.
  • the cavity is the cavity of the muscle tissue to be measured, such as the vagina, because the third air pressure value in the treatment head is the same as the second air pressure value.
  • the difference between the values can indicate whether the treatment head is completely fitted to the cavity of the muscle tissue to be measured. Therefore, in order to make the treatment head meet the subsequent working conditions and improve the subsequent treatment effect, it is necessary to determine the real-time third air pressure value in the treatment head The difference from the second air pressure value. When the difference reaches the preset threshold range, it means that the treatment head is completely fitted to the cavity of the muscle tissue to be measured. At this point, in the subsequent detection process, the treatment head is in a closed state, and the amount of gas in it will not change anymore.
  • step S1 the air pressure value in the treatment head collected by the monitoring unit is substantially the same as the third air pressure value.
  • the step of obtaining the air pressure value in the treatment head collected by the monitoring unit includes:
  • the muscle tissue is tested through the preset muscle strength test mode to obtain the air pressure value in the treatment head.
  • the muscle strength test mode is to change the contraction speed and contraction time of the muscle tissue, and collect the real-time changing air pressure value.
  • the air pressure value that changes over a period of time can be obtained, which is more accurate.
  • the step of obtaining the electrical signal of the muscle tissue collected by the monitoring unit includes:
  • the muscle tissue is tested through the preset EMG test mode to obtain the electrical signal of the muscle tissue.
  • the EMG test mode is to change the contraction speed and contraction time of the muscle tissue, and collect real-time electrical signals.
  • the electrical signals that change over a period of time can be obtained, which is more accurate.
  • the muscle strength test mode is specifically:
  • the real-time air pressure value is determined as the air pressure value in the treatment head collected by the monitoring unit.
  • the muscle strength test mode is specifically:
  • the user performs a specific action multiple times to generate information.
  • the pressure values in the multiple treatment heads are recorded as a pressure value curve, and the pressure value curve is determined as the pressure value in the treatment head collected by the monitoring unit.
  • the monitoring unit can return multiple pressure values to form a pressure value curve, based on the pressure value
  • the multiple peaks of the curve and the duration of each peak are evaluated. For example, when multiple peaks are within the normal preset value range, and the duration of multiple peaks are within the normal preset value range, it indicates that the muscle tissue is in a normal state, otherwise, it indicates that the muscle tissue is in an abnormal state. It is necessary to control the treatment head to output electrical stimulation (single or multiple electrical stimulation) of a preset size.
  • the EMG test mode is specifically:
  • the user In the muscle strength test mode, the user generates information according to specific actions
  • the pelvic floor muscle tissue as an example. Assuming that the specific action at this time is to contract the pelvic floor muscles, during this process, the compression force of the user’s muscle tissue and the EMG signal will both change, and the monitoring unit measures The pressure value and electrical signal will also change. Taking the pelvic floor muscle tissue as an example, the contraction speed and contraction time of the muscle tissue can also be changed by specific action settings, and real-time changing electrical signals can be collected, accompanied by a variety of parameters. Thus, the muscle strength state of the muscle tissue can be fully detected.
  • the real-time electrical signal is determined as the electrical signal collected by the monitoring unit.
  • the electromyography test mode is specifically:
  • the user performs a specific action multiple times to generate information.
  • the electrical signals of multiple muscle tissues are recorded as electrical signal curves, and the electrical signal curves are determined as the electrical signals of the muscle tissue collected by the monitoring unit.
  • the monitoring unit can return multiple electrical signals to form electrical signal curves.
  • the multiple peaks of the curve and the duration of each peak are evaluated. For example, when multiple peaks are within the normal preset value range, and the duration of multiple peaks are within the normal preset value range, it indicates that the muscle tissue is in a normal state, otherwise, it indicates that the muscle tissue is in an abnormal state. It is necessary to control the treatment head to output electrical stimulation (single or multiple electrical stimulation) of a preset size.
  • the pressure value curve is also acquired.
  • the step of controlling the treatment head to output electrical signals to electrically stimulate muscle tissues according to the physical therapy mode further includes:
  • acquiring the air pressure value in the treatment head collected by the monitoring unit is a real-time feedback realized during the process of electrical stimulation of the muscle tissue by the treatment head outputting electrical signals, and the condition of the muscle tissue can be monitored in real time.
  • the air pressure value at this time is measured by the pressure sensor, ignoring the influence of the force area, the contraction force of the muscle tissue can be determined by the difference between the standard value of the air pressure and the measured pressure values, and the contraction force at this time is approximately equal to The difference between the standard pressure value and the measured pressure value.
  • Oxford muscle strength indexing method the contractility state of muscle tissue can be determined.
  • the air pressure feedback at this time can be detected while the treatment head outputs electrical signals to the muscle tissue, regardless of whether the treatment head outputs electrical signals at this time, the air pressure feedback will not be affected, so that real-time monitoring can be achieved and real meaning
  • the real-time feedback on the computer can make it easier to determine the accuracy of the corresponding physiotherapy mode in the follow-up.
  • the corresponding physical therapy mode is determined according to the difference between the collected air pressure value in the treatment head and the preset first air pressure value.
  • the physical therapy mode is to control the treatment head to output a specific frequency electrical signal within a preset time.
  • the preset time and specific frequency are all the electrical signals and presets that are matched by the experimenter through multiple experiments and data collection to a specific frequency with better effects. Time, of course, the preset time can also be set by the user, which can better match the user's usage habits.
  • the electrical signal of a specific frequency several recommended values with better effects can also be given, allowing the user to choose according to their own tolerance.
  • the muscle tissue can be electrically stimulated to perform physical therapy on the muscle tissue. Therefore, the air pressure value can be readjusted according to the difference between the real-time feedback air pressure value and the preset first air pressure value, which further improves the treatment effect of the treatment device.
  • the step of controlling the treatment head to output electrical signals to electrically stimulate muscle tissues according to the physical therapy mode further includes:
  • the acquisition of the air pressure value in the treatment head collected by the monitoring unit and the electrical signals that the monitoring unit collects in contact with the human tissue are real-time feedback realized during the process of electrical stimulation of the muscle tissue by the electrical signal from the treatment head, which can monitor the muscle tissue in real time. Status. Two kinds of real-time feedback can be carried out at the same time to more accurately determine the real-time condition of muscle tissue.
  • the air pressure value at this time is measured by a pressure sensor, ignoring the influence of the force area, the contraction force of the muscle tissue can be determined by the difference between the standard air pressure value and multiple measured air pressure values, and the contraction at this time The force is approximately equal to the difference between the standard air pressure value and the measured air pressure value.
  • the contractility state of muscle tissue can be determined. Because the air pressure feedback at this time can be detected while the treatment head outputs electrical signals to the muscle tissue, regardless of whether the treatment head outputs electrical signals at this time, the air pressure feedback will not be affected, so that real-time monitoring can be achieved and real meaning The real-time feedback on the computer can make it easier to determine the accuracy of the corresponding physiotherapy mode in the follow-up.
  • the corresponding physical therapy mode is determined according to the difference between the collected air pressure value in the treatment head and the preset first air pressure value and the collected electrical signal of the muscle tissue.
  • the pressure value can be readjusted according to the real-time feedback pressure value and electrical signal, and the therapeutic effect of the therapeutic device can be further improved.
  • the treatment head is controlled to output electrical signals according to the physical therapy mode to electrically stimulate the muscle tissue.
  • the muscle tissue was tested many times, and multiple feedback electrical signals were obtained.
  • the electric signal to be fed back is determined according to the average value of the electric signals.
  • the amplitude of continuous contraction is greater than 30uv, and the signal amplitude does not decrease or almost does not decrease during the entire 60s permanent contraction. It indicates that the muscle tissue is in a normal state, and if it is less than 30uv, it indicates that physical therapy is needed. Determining the feedback electrical signal according to the average value of the multiple electrical signals can ensure the accuracy of the measured data.
  • the step of determining the corresponding physical therapy mode according to the difference between the collected air pressure value in the treatment head and the preset first air pressure value and the collected electrical signal of the muscle tissue includes:
  • the corresponding physical therapy mode is determined according to the difference between the air pressure value and the first air pressure value.
  • the step of determining the corresponding physical therapy mode according to the difference between the collected air pressure value in the treatment head and the preset first air pressure value and the collected electrical signal of the muscle tissue includes:
  • a corresponding physical therapy mode is determined according to the electrical signal.
  • the physical therapy mode is specifically:
  • the treatment head outputs electrical signals at a preset frequency and a preset current level within a preset time.
  • the electrical signal of the treatment head when the difference is less than 1, the electrical signal of the treatment head lasts for 15 minutes and is an electrical signal with a preset frequency and a preset current.
  • the physical therapy mode is specifically:
  • the treatment head outputs an instantaneous pulse signal with a preset current level.
  • this mode is generally instant feedback, and the user has been performing contraction exercises.
  • the air pressure value or the electrical signal of the muscle tissue is detected in real time.
  • the preset first air pressure value is generally determined by the gas volume of the treatment head.
  • the threshold range is determined by the normal contraction force standard of the muscle tissue to be measured in the prior art.
  • the preset first electrical signal generally refers to the electrical signal setting of the muscle tissue to be measured under the normal state. It is worth noting that because the collected air pressure value in the treatment head is generally less than the preset first air pressure value, the difference is generally negative. For ease of understanding, the difference here is generally taken as the absolute value of the difference. calculate.
  • the therapeutic apparatus includes a controller, a treatment head 10, and a monitoring unit 20.
  • the controller includes a memory, a processor, and a device that is stored in the memory and can run on the processor.
  • the control program of the treatment device when the control program of the treatment device is executed by the processor, realizes the steps of the above control method of the treatment device, and the control unit is connected to the monitoring unit 20 and the treatment head 10 respectively.
  • the monitoring unit 20 detects the air pressure value of the treatment head and the electrical signal of the muscle tissue.
  • the controller outputs the control signal according to the difference between the air pressure value and the preset first air pressure value.
  • the controller outputs a control signal according to the electrical signal.
  • the controller outputs the control signal according to the difference between the air pressure value and the preset first air pressure value and the electrical signal.
  • the treatment head 10 controls the treatment head to output electrical signals according to the control signal to electrically stimulate the muscle tissue. So as to realize a variety of feedback control.
  • the charging and discharging network of the present application includes the control method of the above-mentioned therapeutic apparatus, therefore, the charging and discharging network of the present application includes all the embodiments and beneficial effects of the above-mentioned control method of the therapeutic apparatus, and will not be repeated here.
  • the monitoring unit 20 includes a pressure sensor 202, an electromyography parameter acquisition module 204, a first amplifying filter circuit 201, and a second amplifying filter circuit 203.
  • the detection end of the pressure sensor 202 is the detection port of the monitoring unit 20.
  • the output end of the sensor 202 is connected to the input end of the first amplifying and filtering circuit 201; the output end of the first amplifying and filtering circuit 201 is connected to the first detection end of the processor; the detection end of the electromyography parameter acquisition module 204 is arranged on the treatment head 10
  • the output terminal of the electromyographic parameter acquisition module 204 is connected to the input terminal of the second amplifying and filtering circuit 203, and the output terminal of the second amplifying and filtering circuit 203 is connected to the second detection terminal of the processor.
  • the pressure sensor 202 detects the air pressure value in the treatment head 10 and converts it into a first electrical signal.
  • the electromyographic parameter collection module 204 collects the potential signal of the muscle tissue contacted by the treatment head 10.
  • the first amplifying and filtering circuit 201 filters and amplifies the first electrical signal.
  • the second amplifying and filtering circuit 203 filters and amplifies the potential signal.
  • the myoelectric parameter collection module 204 is an electrical signal sensor.
  • the first amplifying and filtering circuit 201 and the second amplifying and filtering circuit 203 can be implemented by using a commonly used amplifying and filtering circuit or a chip with an amplifying and filtering function.
  • the automatic charging and discharging unit 50 includes an air pump 502 and a solenoid valve 503.
  • the controlled end of the air pump 502 is connected to the first output end of the processor, and the output end of the air pump 502 is connected to the first output end of the solenoid valve 503 through the pipe 504.
  • An air inlet and outlet are connected; the controlled end of the solenoid valve 503 is connected to the second output end of the processor, the air outlet 505 of the solenoid valve 503 is connected to the atmosphere, and the second air inlet and outlet of the solenoid valve 503 are connected to the treatment head 10 and The detection port of the monitoring unit 20 is connected.
  • the automatic charging and discharging unit 50 is controlled by the processor.
  • the air pump 502 and the solenoid valve 503 receive the second control signal, if the second control signal represents deflation, the solenoid valve 503 is opened, and the air pump 502 operates as the second control signal.
  • the deflation speed represented by the control signal exhausts the gas in the treatment head 10.
  • the second control signal represents inflation
  • the solenoid valve 503 is opened, and the air pump 502 fills the treatment head 10 with gas at the inflation speed represented by the second control signal. Therefore, the inflating and discharging process of the treatment head 10 can be realized quickly with a simple circuit and air circuit structure.
  • the user's sense of use is improved.
  • the treatment device also includes a heating component, and the heating component is connected with the controller.
  • the heating component detects the temperature of the treatment device. Before the treatment head is used, that is, before the air pressure value of the treatment head is detected in step S1, the controller outputs power according to the temperature to control the heating assembly to heat the treatment head.
  • the heating component is a semiconductor.
  • the power source 40 includes EMS (Electrical Muscle Stimulation) generating power source 402 and/or radio frequency generating power source 401, EMS generating power source 402 and RF generating power source 401 are both connected to the electrode pads on the treatment head 10.
  • EMS Electro Mechanical Muscle Stimulation
  • the EMS (Electrical Muscle Stimulation) generating power source 402 and the radio frequency generating power source 401 are powered by the power source.
  • the EMS generating power source 402 supplies low-frequency power to the electrode sheet.
  • the radio frequency generating power supply 401 supplies radio frequency power to the electrode sheet.
  • different power supplies are used to separately supply power to realize different functions of the treatment head 10, so that each function of the treatment head 10 can be distinguished, and it can also avoid the power supply damage and the unavailability of all functions.
  • the power source 40 includes a preheating power source 403, and the preheating power source 403 is electrically connected to the heating component 102.
  • the preheating power supply 403 supplies power to the heating assembly.

Abstract

一种治疗仪及其控制方法，治疗仪的控制方法包括：获取监测单元采集的治疗头内的气压值和/或监测单元采集的肌肉组织的电信号（S1）；根据采集的治疗头内的气压值与预设的第一气压值的差值和/或采集的肌肉组织的电信号确定对应的理疗模式（S2）；控制治疗头根据理疗模式输出电信号对肌肉组织进行电刺激（S3）。所述治疗仪及其控制方法能够解决现有治疗仪治疗效果较差的技术问题。

Description

治疗仪及其控制方法
本申请要求于2020年04月24日提交中国专利局、申请号为202010336697.5、发明名称为“治疗仪及其控制方法”的中国专利申请的优先权，其全部内容通过引用结合在本申请中。
技术领域
本申请涉及治疗仪器技术领域，特别涉及一种治疗仪及其控制方法。
 背景技术
目前，女性盆底功能障碍性疾病(female pelvic floor dysfunction，FPFD)是一组由于盆底肌肉组织松弛、损伤，盆腔支持结构缺陷或退化所导致盆底功能障碍造成的疾病的总称。临床常见的有尿失禁(urinary incontinence， UI)、盆腔脏器脱垂(pelvic organ prolapse，POP)、性功能障碍(female sexual dysfunction， FSD)、粪失禁(fecal incontinence，FI)等。其中以尿失禁和盆腔脏器脱垂最为常见。目前， FPFD已成为影响女性生活质量的五大疾病之一，其病因很多，但流行病学调查显示妊娠和分娩是其主要且独立的危险因素。虽然在产后早期，盆腔脏器脱垂的症状不明显，产妇无不适反应，但如不加以康复训练， 10~15年后，患者就会由于疾患严重影响生活质量而痛苦不堪。由于产后早期(产后42d-3个月)是人体机能相对最薄弱的时期，但同时也是康复的最佳时期。
虽然市面上已经存在一些电刺激治疗盆底障碍的设备，具有一定的理疗功能，需要有经验的医生进行实时控制，而且只能按按预设的方案进行电刺激治疗，不能根据用户的具体情况调整治疗方案。
 技术问题
本申请主要目的是提出一种治疗仪的控制方法，旨在解决治疗仪治疗效果较差的技术问题。
 技术解决方案
本申请提出的一种治疗仪的控制方法，治疗仪包括治疗头、用于采集治疗头内的气压值以及采集肌肉组织的电信号的监测单元、用于输出电信号以驱动所述治疗头对肌肉组织进行电刺激的功率电源，所述治疗仪的控制方法包括：
获取监测单元采集的治疗头内的气压值和/或监测单元采集接触人体组织的电信号；
根据采集的治疗头内的气压值与预设的第一气压值的差值和/或采集的肌肉组织的电信号确定对应的理疗模式；
控制所述治疗头根据所述理疗模式输出电信号对肌肉组织进行电刺激。
本申请还提出一种治疗仪，所述治疗仪包括控制器、治疗头和监测单元，所述控制器包括存储器、处理器以及存储在所述存储器上并可在所述处理器上运行的治疗仪的控制程序，所述治疗仪的控制程序被所述处理器执行时实现如上述的治疗仪的控制方法的步骤，所述控制单元分别与所述监测单元以及所述治疗头连接；
所述监测单元，用于检测所述治疗头的气压值以及所述治疗头接触的人体组织的电信号；
所述控制器，用于根据所述气压值与预设的第一气压值的差值和/或所述电信号出控制信号；
所述治疗头，用于根据所述控制信号控制所述治疗头输出电信号。
本申请的一个或多个实施例的细节在下面的附图和描述中提出。本申请的其它特征、目的和优点将从说明书、附图以及权利要求书变得明显。
 有益效果
本申请实施例的治疗仪的控制方法通过获取监测单元采集的治疗头内的气压值和/或监测单元采集的治疗头接触的人体组织的电信号。其中，治疗头的气压值的大小可以反应治疗头所贴合的肌肉组织的肌力信息，治疗头接触的人体组织的电信号可以反应治疗头所贴合的肌肉组织的肌电信息。根据采集的治疗头内的气压值与预设的第一气压值的差值和/或采集的肌肉组织的电信号确定对应的理疗模式。此时，治疗头内的气压值与预设的第一气压值的差值可以代表肌力的变化值，也即肌肉组织变化的肌力信息，最后，控制所述治疗头根据所述理疗模式输出电信号对肌肉组织进行电刺激。在上述方案中，不同的差值以及电信号的变化，对应了不同的理疗模式，从而使得在应用有此方案的治疗仪在不同反馈值时，均有对应的理疗模式，从而实现了实时反馈，并能使得理疗仪根据反馈值调整理疗模式，更能去适用于每个用户的情况。而且相比人工控制，在本方案中，其依据的参数更为合理，从而进一步提高治疗仪治疗效果，缩短用户的理疗时间。本申请技术方案能解决现有技术中治疗仪治疗效果较差的技术问题。
 附图说明
为了更清楚地说明本申请实施例中的技术方案，下面将对实施例中所需要使用的附图作简单地介绍，显而易见地，下面描述中的附图仅仅是本申请的一些实施例，对于本领域普通技术人员来讲，在不付出创造性劳动的前提下，还可以根据这些附图示出的结构获得其他的附图。
图1为本申请治疗仪的控制方法一实施例的流程示意图；
图2为本申请治疗仪的控制方法一实施例的流程示意图；
图3为本申请治疗仪的控制方法一实施例的流程示意图；
图4为本申请治疗仪的模块示意图。
本申请的实施方式
下面将结合本申请实施例中的附图，对本申请实施例中的技术方案进行清楚、完整地描述，显然，所描述的实施例仅仅是本申请的一部分实施例，而不是全部的实施例。基于本申请中的实施例，本领域普通技术人员在没有作出创造性劳动前提下所获得的所有其他实施例，都属于本申请保护的范围。
需要说明，若本申请实施例中有涉及方向性指示（诸如上、下、左、右、前、后……），则该方向性指示仅用于解释在某一特定姿态（如附图所示）下各部件之间的相对位置关系、运动情况等，如果该特定姿态发生改变时，则该方向性指示也相应地随之改变。
另外，若本申请实施例中有涉及“第一”、“第二”等的描述，则该“第一”、“第二”等的描述仅用于描述目的，而不能理解为指示或暗示其相对重要性或者隐含指明所指示的技术特征的数量。由此，限定有“第一”、“第二”的特征可以明示或者隐含地包括至少一个该特征。另外，若全文中出现的“和/或”的含义为，包括三个并列的方案，以 “A和/或B”为例，包括A方案，或B方案，或A和B同时满足的方案。另外，各个实施例之间的技术方案可以相互结合，但是必须是以本领域普通技术人员能够实现为基础，当技术方案的结合出现相互矛盾或无法实现时应当认为这种技术方案的结合不存在，也不在本申请要求的保护范围之内。
本申请提出一种治疗仪的控制方法。用于解决现有治疗仪的治疗效果较差的技术问题。
以下，以盆底肌肉组织为出发点说明本申请的出发点，盆底肌肉组织是维持盆底器官支持结构的主要成分，盆底肌肉组织主要由肛提肌组成，它包含维持持续张力的1类肌纤维和维持反射及自主收缩的11类肌纤维。盆底器官脱垂的病因尚不十分清楚，目前很多研究认为POP是由于经阴道分娩引起的盆底肌肉组织、筋膜及子宫韧带损伤、老龄化雌激素水平降低、先天性盆底功能缺陷等原因使得盆底肌肉组织失去张力，盆底组织松驰，导致支持功能薄弱而发生移位脱垂，出现盆底功能障碍(PFD) ，如盆腔器官脱垂（pelvic organ prolapse，POP)和压力性尿失禁( stress urinary incontinence.SUD等一系列盆底损伤与缺陷。如果不及时的预防和治疗，盆底功能障碍会一直持续存在及进一步加重，影响围绝经期甚至老年时期的盆底功能。
针对上述问题，提出了三种方案，第一种方案为盆底肌肉组织锻炼Kegel运动，是Arnold Kegel在1948年开始提倡的。盆底肌肉组织锻炼的方法简单而言就是训练肛提肌群的收缩，盆底肌肉组织有意识的收缩会使盆底向上、向前提升，并挤压尿道、阴道和直肠向内提升，超声和MRI研究都已证实这种提升存在，收缩运动同时会增强盆底肌肉组织的张力，提高肌肉组织反应性，增强肌群组织维持盆腔内脏器负重的支撑力，从而减轻或防止脏器的脱垂。但是，这种方式有及其明显的弊端，有研究显示，超过30%的患者第1次就诊后不能进行正确地收缩练习，普遍的错误收缩臀肌、腹肌，而不是盆底肌，错误的收缩反而使POP加重。因此，正确盆底肌肉组织锻炼是防治POP的关键。
在第二种方案中，通过计算机把盆底肌肉组织收缩的信号以波形显示等视觉或听觉的形式反馈给患者，不断纠正错误的收缩动作来帮助患者找到正确的锻炼方法。单纯Kegel运动多因不能有效保证盆底肌进行正确有效的收缩锻炼且不易坚持。生物反馈保证了正确的、有效的盆底肌锻炼。生物反馈最终目标是让患者在没有生物反馈设备的帮助下进行正确的盆底肌肉组织训练，但是这种方式也主要是机器为辅，其治疗效果及其不稳定。
第三种方案为雌激素治疗，雌激素用于保守治疗压力性尿失禁已有几十年的历史，雌激素治疗压力性尿失禁的机制为多方面的:刺激尿道上皮的生长；增加尿道黏膜下静脉丛血供；影响膀胱尿道旁的结缔组织的功能；最为重要的是增加支持盆底结构的肌肉组织的张力。
在一实施例中，如图1所示，一种治疗仪的控制方法，所述治疗仪的控制方法包括：
S1、获取监测单元采集的治疗头内的气压值和/或监测单元采集的治疗头接触的人体组织的电信号。
其中，在进行此步骤时，治疗头内的气体量已经调试好，使得治疗头与人体组织贴合，其气体量不会再变化，后续将治疗仪用于肌肉组织理疗时，治疗头的气压值仅受肌肉组织的收缩、扩张等动作的影响，其中，根据治疗头的气压值的大小可以反应治疗头所贴合的肌肉组织的肌力信息，肌力信息指代肌肉组织的收缩等动作的压缩力，通过监测单元检测气压值。治疗头接触的人体组织的电信号可以反应治疗头所贴合的肌肉组织的肌电信息，肌电信息为肌肉组织反馈的电信号，通过监测单元检测电信号。本方案中通过增加了两种反馈信息去综合确认肌肉组织的信息，从而可以增加参数取值的多样性，提高确认肌肉组织状态的准确性。
S2、根据采集的治疗头内的气压值与预设的第一气压值的差值和/或采集的肌肉组织的电信号确定对应的理疗模式。
其中，预设的第一气压值为肌肉组织静息状态下，治疗头与肌肉组织贴合设置时，所测定的气压值，此时，根据气压值与第一气压值的差值可以确定变化的肌力信息。采集的治疗头内的气压值为肌肉组织处于收缩状态，治疗头与肌肉组织贴合设置时，所测定的气压值。即当初始值为第一气压值时，通过上述步骤可以方便测得变化的肌力信息，根据肌力信息和肌电信息可以准确的判定此刻肌肉组织的状态。基于上述原理，在一方案中，可以通过气压值与预设的第一气压值的差值单独确定理疗模式。在另一方案中，可以通过采集的肌肉组织的电信号单独确定理疗模式。两者均是对肌肉组织的相关状态进行测量，均能准确反映实时状态。另外，还可以同时根据气压值与预设的第一气压值的差值以及电信号确定理疗模式，更能增加理疗模式与用户的契合度，提升理疗效果。另外，理疗模式为改变预设的多种模式，分别对应不同的气压值与第一气压值的差值以及不同的电信号，这个模式由实验人员通过多次实验获得效果较好的理疗模式。
S3、控制所述治疗头根据所述理疗模式输出电信号对肌肉组织进行电刺激。
其中，理疗模式为控制治疗头在预设时间内输出特定频率的电信号，其预设时间以及特定频率均是实验人员通过多次实验以及数据采集匹配到效果较好的特定频率的电信号以及预设时间，当然，预设时间也可以由用户设定，能更匹配用户的使用习惯。另外，在匹配特定频率的电信号时，也可以给出几个效果较好的建议值，让用户根据自身承受能力进行选择。从而可以对肌肉组织进行电刺激以对肌肉组织进行理疗。以下，以盆底肌肉组织为例说明电刺激原理：
电刺激是通过放置于阴道的电极用不同频率的电流刺激盆底肌肉组织和筋膜以增强其强度和功能，电刺激组织使之产生收缩速度和收缩时间性收缩运增加韧带弹力，间歇式地收缩肛提肌和外括约肌、促进肌肉组织盆底血液循环的改善、保持其正常代谢功能，进一步增强肛提肌及其他盆底肌张力，加速损伤组织的修复，强化整个盆底肌群，促进盆底各个器官应有功能的恢复。还能恢复本体感觉，抑制肌肉组织痉挛，降低肌张力。具体地，在直流电场作用下，由于局部小血管扩张（尤以阴极为明显），血流增加，血循环改善，持续时间较长。从而加强组织的营养供应，加速代谢产物的排除。直流电有促进炎症消散，提高组织功能，促进再生过程等作用。对于肌力：电刺激唤醒盆底肌肉组织收缩，提升肌力，整体提升盆底肌力，耐力和张力，恢复盆底承托功能的协调性。对于肌肉组织：电刺激增强盆底和尿道周围的肌肉组织力量：改变的肌球蛋白异构体的表达，影响横纹肌，引起骨骼肌纤维肥大；电刺激能促进Ⅰ、Ⅱ类肌纤维肥大，修复盆底尿道支持系统，使尿道固定在盆筋膜腱弓和耻骨直肠肌之上，增强尿道闭合能力。同时增加阴道的弹力和收缩力。对于敏感程度：电刺激修复神经、增加粘膜血液循环，提高器官的神经敏感性。对于神经：通过刺激阴部神经的传出纤维，以增强肛提肌及其他盆底诸肌及尿道周围横纹肌的功能，加强对尿道和膀胱颈的支撑作用，提高尿道闭合压；刺激经阴部神经的传入纤维，通过神经元的连接至骶髓逼尿肌核，抑制逼尿肌核的兴奋性，再经盆神经传至逼尿肌，抑制逼尿肌的收缩。对于激素：电刺激冲动上行至胸腰段，使交感神经元兴奋， α一肾上腺素能受体使膀胱颈部及尿道近段收缩，进一步增加尿道关闭功能，β一肾上腺素能受体兴奋，膀胱底松弛，增加膀胱颈的封闭性。从而可以通过电刺激同时实现多种效果，更为全面的促进肌肉组织的恢复。
在上述方案中，不同的差值以及电信号的变化，对应了不同的理疗模式，从而使得在应用有此方案的治疗仪在不同反馈值时，均有对应的理疗模式，从而实现了实时反馈，并能使得理疗仪根据反馈值调整理疗模式，更能去适用于每个用户的情况。而且相比人工控制，在本方案中，其依据的参数更为合理，从而进一步提高治疗仪治疗效果，缩短用户的理疗时间。
为了更加清楚的实现治疗仪的控制方法，如图4所示，下面对治疗仪的结构进行介绍：
治疗仪包括治疗头、监测单元和功率电源，功率电源的输出端与治疗头的电源端连接，监测单元的检测端与治疗头的进出气口连接，监测单元的第二检测端与治疗头的电极片连接。
其中，监测单元采集治疗头内的气压值以及采集肌肉组织的电信号，自动充放气单元执行充放气动作，功率电源输出电信号以驱动所述治疗头对肌肉组织进行电刺激。
在一实施例中，如图2所示，所述获取监测单元采集的治疗头内的气压值的步骤之后还包括：
S4、将所述实时检测的气压值记录成气压值曲线。
此时，一般是用户主动测试的情况，基于此种背景，即放入腔体的治疗头与腔体贴合良好的情况下，其治疗头内的气体容量均不会改变，其气压值有一基础值。在此背景之下，用户主动执行预设动作，使得特定肌肉组织收缩，从而使得气压值增加，当记录成曲线时，或者是利用小游戏形式去表现，可以方便用户去查看。
S5、当所述气压值的幅值达到预设气压值时，控制所述治疗头输出预设大小的单次电刺激。
此时的预设气压值可以用户设定，也可以由数据库中的数据去进行设定，这样在气压值的幅值达到预设气压值时，控制所述治疗头输出预设大小的单次电刺激。可以实现即时检测并即时反馈治疗，且配合用户的主动收缩，单次收缩配合单次电刺激，能更有针对性的实现对肌肉组织的治疗，从而实现更好的治疗效果。此时，单次电刺激的预设大小为与气压值对应的大小，此种对应关系，由厂商提前采集多种数据进行参数的设置，即在治疗头与腔体贴合良好，此时治疗头具备一定贴合气压值的情况下，正常肌肉组织收缩对应一个正常的气压值，若是小于这个数值并处于第一预设范围值时，治疗头输出第一电压值的电刺激，若是小于这个数值并处于第二预设范围值时，治疗头输出第二电压值的电刺激。从而使得治疗头可以根据不同范围值的气压值确定对应输出的电刺激的电压的大小，进一步实现更好的治疗效果。若是设计到游戏中，可以对应设置成简单模式、一般模式、以及困难模式，激发用户的胜负欲，实时激励用户下次挑战，以实现自我激励。
在一实施例中，所述获取监测单元采集接触人体组织的电信号的步骤之后还包括：
将所述实时检测的电信号记录成电信号曲线。
此时，一般是用户主动测试的情况，基于此种背景，即放入腔体的治疗头与腔体贴合良好的情况下，其治疗头内的气体容量均不会改变，在此背景之下，用户主动执行预设动作，使得特定肌肉组织收缩，从而使得肌肉组织反馈的电信号改变，当记录成曲线时，或者是利用小游戏形式去表现，可以方便用户去查看。
当所述电信号的幅值满足预设电信号时，控制所述治疗头输出预设大小的单次电刺激。
其中，以盆底肌肉组织为例，持续性收缩的幅度大于30uv ,在整个60s持久性收缩期间信号的振幅不下降或几乎不下降。则表明肌肉组织处于正常状态，若低于30uv，则表明需要进行理疗。此时可以将预设电信号设置为低于30uv。然后控制所述治疗头输出预设大小的单次电刺激。
在一实施例中，治疗仪还包括自动充放气单元，自动充放气单元与治疗头通过气路连接，并用于执行充放气动作。如图3所示，为了进一步提高治疗效果，在获取监测单元采集的治疗头内的气压值以及监测单元采集的肌肉组织的电信号的步骤之前还包括：
S6、获取治疗头的气体量。
S7、获取治疗仪内的第二气压值。
第二气压值为一定气体量的治疗头处于空气状态下的气压值。
S8、将所述治疗仪放入腔体后获取第三气压值。
此时，气体量为发生变化，治疗头的气压值受腔体影响而发生变化。
确定所述治疗头内的第二气压值与所述第三气压值的差值是否等于预设阈值范围。
此时，由于治疗头的第三气压值为放入腔体后的气压值，腔体为待测量肌肉组织的腔体，如阴道，由于治疗头内的第三气压值与所述第二气压值的差值可以表征治疗头是否完全与待测量肌肉组织的腔体完全贴合，因此，为了使得治疗头满足后续工作条件，提升后续治疗效果，需要确定实时的治疗头内的第三气压值与所述第二气压值的差值。当差值达到预设阈值范围，代表治疗头与待测量肌肉组织的腔体完全贴合。此时，在随后的检测过程中，治疗头为封闭状态，其内的气体量不会再发生变化。
S9、当所述治疗头内的第二气压值与所述第三气压值的差值小于预设阈值范围的最小值时，控制自动充放气单元进行充气动作，并重复执行获取治疗头的气体量的步骤。
S10、当所述治疗头内的第二气压值与所述第三气压值的差值大于预设阈值范围的最小值时，控制自动充放气单元进行放气动作。并重复执行获取治疗头的气体量的步骤。
当所述治疗头内的第二气压值与所述第三气压值的差值处于预设阈值范围时，则表示治疗仪的治疗头与腔体贴合良好，可以进行后续的获取监测单元采集的治疗头内的气压值以及监测单元采集的肌肉组织的电信号的步骤无需再执行自动充放气单元的充放气动作。此外，在步骤S1中，监测单元采集的治疗头内的气压值与第三气压值大致相同。
在一实施例中，所述获取监测单元采集的治疗头内的气压值的步骤包括：
通过预设的肌力测试模式对肌肉组织进行测试，以获取治疗头内的气压值。
其中，肌力测试模式为改变肌肉组织的收缩速度和收缩时间，采集实时变化的气压值，通过测试多种不同的收缩速度和收缩时间，从而可以得到一段时间内变化的气压值，从而比较准确的获得反应肌肉组织收缩能力的气压值。
在一实施例中，所述获取监测单元采集的肌肉组织的电信号的步骤包括：
通过预设的肌电测试模式对肌肉组织进行测试，以获取肌肉组织的电信号。
其中，肌电测试模式为改变肌肉组织的收缩速度和收缩时间，采集实时变化的电信号，通过测试多种不同的收缩速度和收缩时间，从而可以得到一段时间内变化的电信号，从而比较准确的获得反应肌肉组织收缩能力的电信号。
在一实施例中，所述肌力测试模式具体为：
在肌力测试模式下，用户按照特定的动作执行产生信息。
以盆底肌肉组织为例，假定此时特定的动作为收缩盆底肌，则在此过程中，用户的肌肉组织的压缩力和肌电信号均会发生改变，则监测单元测得的气压值和电信号也会改变，其中，以盆底肌肉组织为例，也可以将特定的动作设置为预设的收缩速度和收缩时间，采集实时变化的气压值，并伴有多种参数，从而可以充分检测到肌肉组织的肌力状态。
通过监测单元获取治疗头内的实时气压值。
并将实时气压值确定为监测单元采集的治疗头内的气压值。
在一实施例中，所述肌力测试模式具体为：
在肌力测试模式下，用户多次按照特定的动作执行产生信息。
通过监测单元获取多个治疗头内的气压值。
将多个治疗头内的气压值记录成气压值曲线，并将气压值曲线确定为监测单元采集的治疗头内的气压值。
在肌力测试模式下，用户多次按照特定的动作执行产生信息，也即通过连续测试多种不同的收缩速度和收缩时间，监测单元可以返回多个气压值，形成气压值曲线，根据气压值曲线的多个峰值以及每个峰值持续的时间来进行评估。例如，当多个峰值均在正常预设值范围之内，多个峰值的持续时间均在正常预设值范围之内，则表明肌肉组织处于正常状态，否则，表明肌肉组织处于不正常状态，需要控制所述治疗头输出预设大小的电刺激（单次或多次电刺激）。
在一实施例中，所述肌电测试模式具体为：
在肌力测试模式下，用户按照特定的动作执行产生信息；
其中，以盆底肌肉组织为例，假定此时特定的动作为收缩盆底肌，则在此过程中，用户的肌肉组织的压缩力和肌电信号均会发生改变，则监测单元测得的气压值和电信号也会改变，其中，以盆底肌肉组织为例，也可以将特定的动作设置改变肌肉组织的收缩速度和收缩时间，采集实时变化的电信号，并伴有多种参数，从而可以充分检测到肌肉组织的肌力状态。
通过监测单元获取接触人体组织的实时电信号。
并将实时电信号确定为监测单元采集的电信号。
在一实施例中，为了更加准确的获得电信号，所述肌电测试模式具体为：
在肌力测试模式下，用户多次按照特定的动作执行产生信息。
通过监测单元获取多个接触人体组织的电信号。
将多个肌肉组织的电信号记录成电信号曲线，并将电信号曲线确定为监测单元采集的肌肉组织的电信号。
在肌力测试模式下，用户多次按照特定的动作执行产生信息，也即通过连续测试多种不同的收缩速度和收缩时间，监测单元可以返回多个电信号，形成电信号曲线，根据电信号曲线的多个峰值以及每个峰值持续的时间来进行评估。例如，当多个峰值均在正常预设值范围之内，多个峰值的持续时间均在正常预设值范围之内，则表明肌肉组织处于正常状态，否则，表明肌肉组织处于不正常状态，需要控制所述治疗头输出预设大小的电刺激（单次或多次电刺激）。
在本实施例中，在获取电信号曲线的同时，还获取气压值曲线。
在一实施例中，在所述控制所述治疗头根据所述理疗模式输出电信号对肌肉组织进行电刺激的步骤时还包括：
获取监测单元采集的治疗头内的气压值。
此时，获取监测单元采集的治疗头内的气压值是在治疗头输出电信号对肌肉组织进行电刺激的过程中实现的实时反馈，可以实时监测肌肉组织的状况。此时的气压值均是通过压力传感器测得，忽略受力面积的影响，肌肉组织的收缩力可以由气压标准值和测得的多个气压值的差值确定，此时的收缩力约等于气压标准值和测得的气压值的差值。根据Oxford肌力分度法可以确定肌肉组织的收缩能力状态。由于此时的气压值反馈可以在治疗头对肌肉组织输出电信号的同时进行检测，无论此时治疗头是否输出电信号，气压值反馈均不会受到影响，从而可以实现实时监测，实现真正意义上的实时反馈，更能方便后续的确定对应的理疗模式的准确性。
根据采集的治疗头内的气压值与预设的第一气压值的差值确定对应的理疗模式。
理疗模式为控制治疗头在预设时间内输出特定频率的电信号，其预设时间以及特定频率均是实验人员通过多次实验以及数据采集匹配到效果较好的特定频率的电信号以及预设时间，当然，预设时间也可以由用户设定，能更匹配用户的使用习惯。另外，在匹配特定频率的电信号时，也可以给出几个效果较好的建议值，让用户根据自身承受能力进行选择。从而可以对肌肉组织进行电刺激以对肌肉组织进行理疗。从而可以根据实时反馈的气压值与预设的第一气压值的差值去重新调节气压值，进一步提高治疗仪的治疗效果。
在一实施例中，在所述控制所述治疗头根据所述理疗模式输出电信号对肌肉组织进行电刺激的步骤时还包括：
获取监测单元采集的治疗头内的气压值以及监测单元采集接触人体组织的电信号。
此时，获取监测单元采集的治疗头内的气压值以及监测单元采集接触人体组织的电信号是在治疗头输出电信号对肌肉组织进行电刺激的过程中实现的实时反馈，可以实时监测肌肉组织的状况。两种实时反馈同时进行可以更为准确的确定肌肉组织的实时状况。特别的，此时的气压值均是通过压力传感器测得，忽略受力面积的影响，肌肉组织的收缩力可以由气压标准值和测得的多个气压值的差值确定，此时的收缩力约等于气压标准值和测得的气压值的差值。根据Oxford肌力分度法可以确定肌肉组织的收缩能力状态。由于此时的气压值反馈可以在治疗头对肌肉组织输出电信号的同时进行检测，无论此时治疗头是否输出电信号，气压值反馈均不会受到影响，从而可以实现实时监测，实现真正意义上的实时反馈，更能方便后续的确定对应的理疗模式的准确性。
根据采集的治疗头内的气压值与预设的第一气压值的差值和采集的肌肉组织的电信号确定对应的理疗模式。
从而可以根据实时反馈的压力值以及电信号去重新调节气压值，进一步提高治疗仪的治疗效果。
控制所述治疗头根据所述理疗模式输出电信号对肌肉组织进行电刺激。
在一实施例中，为了增加所测得的电信号的准确程度：
利用肌电测试方法，多次对肌肉组织进行测试，获取到多个反馈电信号。根据多个所述电信号的平均值确定反馈的电信号。
其中，以盆底肌肉组织为例，持续性收缩的幅度大于30uv ,在整个60s持久性收缩期间信号的振幅不下降或几乎不下降。则表明肌肉组织处于正常状态，若低于30uv，则表明需要进行理疗。根据多个所述电信号的平均值确定反馈的电信号可以保证测得的数据的准确性。
在一实施例中，在根据采集的治疗头内的气压值与预设的第一气压值的差值和采集的肌肉组织的电信号确定对应的理疗模式的步骤包括：
当采集的治疗头内的气压值与预设的第一气压值的差值小于预设气压差值时，根据所述气压值与所述第一气压值的差值确定对应的理疗模式。
在一实施例中，在根据采集的治疗头内的气压值与预设的第一气压值的差值和采集的肌肉组织的电信号确定对应的理疗模式的步骤包括：
当所述肌肉组织的电信号小于预设第一电信号时，根据所述电信号，确定对应的理疗模式。
在一实施例中，所述理疗模式具体为：
所述治疗头在预设的时间内，以预设频率以及预设电流大小输出电信号。
例如，当差值小于1时，治疗头的电信号持续15分钟，为预设频率以及预设电流大小的电信号。
在一实施例中，所述理疗模式具体为：
所述治疗头以预设电流大小输出瞬时脉冲信号。
此时，这种模式一般为即时反馈，用户一直在进行收缩运动，此时，实时检测气压值或者肌肉组织的电信号，在气压值与预设的第一气压值小于阈值范围时，或者电信号小于预设第一电信号时，输出一个一定大小的瞬时脉冲信号。其中，预设的第一气压值一般由治疗头的气体量决定。阈值范围由现有技术中的待测量肌肉组织的正常收缩力标准决定。预设第一电信号一般参考待测量的肌肉组织的正常状态下电信号设置。值得注意的是，由于采集的治疗头内的气压值一般小于预设的第一气压值，所述其差值一般为负值，为了方便理解，这里的差值一般取差值的绝对值进行计算。
本申请还提出一种治疗仪，如图4所示，治疗仪包括控制器、治疗头10、和监测单元20，控制器包括存储器、处理器以及存储在存储器上并可在处理器上运行的治疗仪的控制程序，治疗仪的控制程序被处理器执行时实现如上的治疗仪的控制方法的步骤，控制单元分别与监测单元20以及治疗头10连接。
其中，监测单元20检测治疗头的气压值以及肌肉组织的电信号。在第一方案中，控制器根据气压值与预设的第一气压值的差值输出控制信号。在第二方案中，控制器根据电信号输出控制信号。在第三方案中，控制器根据气压值与预设的第一气压值的差值以及电信号输出控制信号。治疗头10根据控制信号控制治疗头输出电信号对肌肉组织进行电刺激。从而实现了多种反馈控制。
值得注意的是，由于本申请充放电网络包含了上述的治疗仪的控制方法，因此，本申请的充放电网络包含上述治疗仪的控制方法的所有实施例以及有益效果，在此不再赘述。
在一实施例中，监测单元20包括压力传感器202、肌电参数采集模块204、第一放大滤波电路201和第二放大滤波电路203，压力传感器202的检测端为监测单元20的检测口，压力传感器202的输出端与第一放大滤波电路201的输入端连接；第一放大滤波电路201的输出端与处理器的第一检测端连接；肌电参数采集模块204的检测端设置于治疗头10的电极片，肌电参数采集模块204的输出端与第二放大滤波电路203的输入端连接，第二放大滤波电路203的输出端与处理器的第二检测端连接。
其中，压力传感器202检测治疗头10内的气压值，并将其转换为第一电信号。肌电参数采集模块204采集治疗头10接触的肌肉组织的电位信号。第一放大滤波电路201对第一电信号进行滤波放大。第二放大滤波电路203对电位信号进行滤波放大。
上述实施例中，肌电参数采集模块204为电信号传感器。
上述实施例中，第一放大滤波电路201和第二放大滤波电路203可以采用常用的放大滤波电路或者具有放大滤波功能的芯片实现。
在一实施例中，自动充放气单元50包括气泵502和电磁阀503，气泵502的受控端与处理器的第一输出端连接，气泵502的输出端通过管道504与电磁阀503的第一进出气口连接；电磁阀503的受控端与处理器的第二输出端连接，电磁阀503的出气口505与大气连通，电磁阀503的第二进出气口通过管道504分别与治疗头10以及监测单元20的检测口连接。
其中，自动充放气单元50受处理器的控制，在气泵502和电磁阀503接收到第二控制信号时，若第二控制信号代表放气，则电磁阀503开启，则气泵502以第二控制信号代表的放气速度将治疗头10内的气体排出。若第二控制信号代表充气，则电磁阀503开启，则气泵502以第二控制信号代表的充气速度将气体充入治疗头10内。从而可以以简单的电路和气路结构，较快的实现治疗头10的充放气过程。
在一实施例中，为了方便用户使用，提升用户的使用感。治疗仪还包括加热组件，加热组件与控制器连接。
其中，加热组件检测治疗仪的温度。控制器在治疗头使用之前，即在步骤S1检测治疗头的气压值之前，根据温度输出电源以控制加热组件加热治疗头。
其中，加热组件为半导体。
在一实施例中，功率电源40包括EMS（Electrical Muscle Stimulation）发生电源402和/或射频发生电源401，EMS发生电源402以及射频发生电源401均与治疗头10上的电极片连接。
EMS（Electrical Muscle Stimulation）发生电源402和射频发生电源401由电源供电。
其中，EMS发生电源402为电极片供给低频电源。射频发生电源401为电极片供给射频电源。本方案中，通过不同的电源分开供电以实现治疗头10的不同功能，从而可以将治疗头10的每个功能区分开，还可以避免电源损坏导致所有功能不可用。
在一实施例中，功率电源40包括预热电源403，预热电源403与加热组件102电连接。
其中，预热电源403为加热组件供给电源。
以上所述仅为本申请的可选实施例，并非因此限制本申请的专利范围，凡是在本申请的发明构思下，利用本申请说明书及附图内容所作的等效结构变换，或直接/间接运用在其他相关的技术领域均包括在本申请的专利保护范围内。

Claims (19)

  1. 一种治疗仪的控制方法，治疗仪包括治疗头、用于采集治疗头内的气压值以及采集肌肉组织的电信号的监测单元、用于输出电信号以驱动所述治疗头对肌肉组织进行电刺激的功率电源，其特征在于，所述治疗仪的控制方法包括：
    获取监测单元采集的治疗头内的气压值和/或监测单元采集接触人体组织的电信号；
    根据采集的治疗头内的气压值与预设的第一气压值的差值和/或采集的肌肉组织的电信号确定对应的理疗模式；
    控制所述治疗头根据所述理疗模式输出电信号对肌肉组织进行电刺激。
  2. 如权利要求1所述的治疗仪的控制方法，其特征在于，所述获取监测单元采集的治疗头内的气压值的步骤之后还包括：
    将实时检测的气压值记录成气压值曲线；
    当所述气压值的幅值达到预设气压值时，控制所述治疗头输出预设大小的单次电刺激。
  3. 如权利要求1所述的治疗仪的控制方法，其特征在于，所述获取监测单元采集接触人体组织的电信号的步骤之后还包括：
    将实时检测的电信号记录成电信号曲线；
    当所述电信号的幅值满足预设电信号时，控制所述治疗头输出预设大小的单次电刺激。
  4. 如权利要求1所述的治疗仪的控制方法，其特征在于，所述治疗仪还包括自动充放气单元，所述自动充放气单元与所述治疗头通过气路连接，并用于执行充放气动作；
    在所述获取监测单元采集的治疗头内的气压值以及监测单元采集的肌肉组织的电信号的步骤之前还包括：
    获取治疗头的气体量；
    获取治疗仪内的第二气压值；
    将所述治疗仪放入腔体后获取第三气压值；
    当所述治疗头内的第二气压值与所述第三气压值的差值小于预设阈值范围的最小值时，控制自动充放气单元进行充气动作，并重复执行获取治疗头的气体量的步骤；
    当所述治疗头内的第二气压值与所述第三气压值的差值大于预设阈值范围的最小值时，控制自动充放气单元进行放气动作，并重复执行获取治疗头的气体量的步骤。
  5. 如权利要求1所述的治疗仪的控制方法，其特征在于，所述获取监测单元采集的治疗头内的气压值具体包括：
    通过预设的肌力测试模式对肌肉组织进行测试，以获取治疗头内的气压值。
  6. 如权利要求5所述的治疗仪的控制方法，其特征在于，所述预设的肌力测试模式具体为：
    在肌力测试模式下，用户按照特定的动作执行产生信息；
    通过监测单元获取治疗头内的实时气压值；
    并将实时气压值确定为监测单元采集的治疗头内的气压值。
  7. 如权利要求5所述的治疗仪的控制方法，其特征在于，所述预设的肌力测试模式具体为：
    在肌力测试模式下，用户多次按照特定的动作执行产生信息；
    通过监测单元获取多个治疗头内的气压值；
    将多个治疗头内的气压值记录成气压值曲线，并将气压值曲线确定为监测单元采集的治疗头内的气压值。
  8. 如权利要求1所述的治疗仪的控制方法，其特征在于，所述获取监测单元采集的肌肉组织的电信号的步骤包括：
    通过预设的肌电测试模式对肌肉组织进行测试，以获取肌肉组织的电信号。
  9. 如权利要求8所述的治疗仪的控制方法，其特征在于，所述肌电测试模式具体为：
    在肌电测试模式下，用户按照特定的动作执行产生信息；
    通过监测单元获取接触人体组织的实时电信号；
    并将实时电信号确定为监测单元采集的电信号。
  10. 如权利要求8所述的治疗仪的控制方法，其特征在于，所述肌电测试模式具体为：
    在肌电测试模式下，用户多次按照特定的动作执行产生信息；
    通过监测单元获取多个接触人体组织的电信号；
    将多个肌肉组织的电信号记录成电信号曲线，并将电信号曲线确定为监测单元采集的肌肉组织的电信号。
  11. 如权利要求10所述的治疗仪的控制方法，其特征在于，在所述通过监测单元获取多个接触人体组织的电信号的同时，通过监测单元获取多个治疗头内的气压值；
    在所述将多个肌肉组织的电信号记录成电信号曲线，并将电信号曲线确定为监测单元采集的肌肉组织的电信号的同时，将多个治疗头内的气压值记录成气压值曲线，并将气压值曲线确定为监测单元采集的治疗头内的气压值。
  12. 如权利要求1所述的治疗仪的控制方法，其特征在于，当执行所述控制所述治疗头根据所述理疗模式输出电信号对肌肉组织进行电刺激的步骤时还包括：
    获取监测单元采集的治疗头内的气压值；
    根据采集的治疗头内的气压值与预设的第一气压值的差值确定对应的理疗模式。
  13. 如权利要求1所述的治疗仪的控制方法，其特征在于，当执行所述控制所述治疗头根据所述理疗模式输出电信号对肌肉组织进行电刺激的步骤时还包括：
    获取监测单元采集的治疗头内的气压值以及监测单元采集接触人体组织的电信号；
    根据采集的治疗头内的气压值与预设的第一气压值的差值和采集的肌肉组织的电信号确定对应的理疗模式。
  14. 如权利要求1所述的治疗仪的控制方法，其特征在于，在根据采集的治疗头内的气压值与预设的第一气压值的差值和采集的肌肉组织的电信号确定对应的理疗模式的步骤包括：
    当采集的治疗头内的气压值与预设的第一气压值的差值小于预设气压差值时，根据所述气压值与所述第一气压值的差值确定对应的理疗模式。
  15. 如权利要求1所述的治疗仪的控制方法，其特征在于，在根据采集的治疗头内的气压值与预设的第一气压值的差值和采集的肌肉组织的电信号确定对应的理疗模式的步骤包括：
    当所述肌肉组织的电信号小于预设第一电信号时，根据所述电信号，确定对应的理疗模式。
  16. 如权利要求14或15所述的治疗仪的控制方法，其特征在于，所述理疗模式具体为：
    所述治疗头在预设的时间内，以预设频率以及预设电流大小输出电信号。
  17. 如权利要求14或15所述的治疗仪的控制方法，其特征在于，所述理疗模式具体为：
    所述治疗头以预设电流大小输出瞬时脉冲信号。
  18. 一种治疗仪，其特征在于，所述治疗仪包括控制器、治疗头和监测单元，所述控制器包括存储器、处理器以及存储在所述存储器上并可在所述处理器上运行的治疗仪的控制程序，所述治疗仪的控制程序被所述处理器执行时实现如权利要求1至17中任一项所述的治疗仪的控制方法的步骤，所述控制单元分别与所述监测单元以及所述治疗头连接；
    所述监测单元，用于检测所述治疗头的气压值以及所述治疗头接触的人体组织的电信号；
    所述控制器，用于根据所述气压值与预设的第一气压值的差值和/或所述电信号出控制信号；
    所述治疗头，用于根据所述控制信号控制所述治疗头输出电信号。
  19. 如权利要求18所述的治疗仪，其特征在于，所述治疗仪还包括加热组件，所述加热组件与所述控制器连接；
    所述加热组件，用于检测治疗头的温度；
    所述控制器，用于在治疗头使用之前，根据所述温度输出电源以控制所述加热组件加热所述治疗头。
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