Respiration therapeutic apparatus

Abstract

The invention discloses a breathing therapeutic apparatus, and relates to the technical field of medical equipment, and the breathing therapeutic apparatus comprises a host which is used for detecting the breathing state of a target object, and outputting an electric pulse with a preset frequency and a preset pulse width when detecting that the breathing state of the target object is snoring or apnea; wherein the value range of the preset frequency is between 18 kHz and 22 kHz, and the value range of the preset pulse width is between 45 microseconds and 55 microseconds; the gel patch is connected with the host, and the gel patch is used for being attached to the lower jaw of the target object so as to conduct the electric pulse to the lower jaw of the target object and stimulate the hypoglossal nerves of the target object; the invention aims to solve the technical problems that the endurance time of an existing breathing therapeutic apparatus is short and hypoglossal nerves cannot be well stimulated generally.

Description

Technical Field

[0001] The present invention relates to the technical field of medical devices, and particularly relates to a respiratory therapy device. Background Art

[0002] With the increasing attention of people to sleep quality, the respiratory therapy device, as a device for assisting in treating snoring, has gradually become an important tool for improving sleep health. The existing respiratory therapy devices act on the muscles of the user's mandible, neck or larynx through weak electrical stimulation or other physical intervention means, so as to regulate the activities of the respiratory muscle groups and reduce or eliminate the snoring phenomenon.

[0003] However, the existing respiratory therapy devices will be continuously in a working state when powered on. The continuous working will significantly shorten the battery life of the respiratory therapy device and affect the user experience. And in order to achieve better effects, the existing respiratory therapy devices will use a higher electrical stimulation intensity, but this may cause discomfort or even pain to the user, especially it is easy to wake up during night sleep. But if the electrical stimulation intensity is low, it may not be able to effectively activate the target muscles (such as the genioglossus muscle or the mandibular muscle), resulting in poor treatment effects. Summary of the Invention

[0004] The main object of the present invention is to propose a respiratory therapy device, aiming to solve the technical problems that the existing respiratory therapy devices have a short battery life and usually cannot stimulate the hypoglossal nerve well.

[0005] To achieve the above object, a respiratory therapy device proposed by the present invention includes:

[0006] A main body, which is used for detecting the breathing state of a target object, and outputting an electrical pulse with a preset frequency and a preset pulse width when detecting that the breathing state of the target object is snoring or apnea;

[0007] Wherein, the value range of the preset frequency is between 18 kHz and 22 kHz, and the value range of the preset pulse width is between 45 μs and 55 μs;

[0008] A gel patch, which is connected to the main body, and is used for adhering to the lower jaw of the target object to conduct the electrical pulse to the lower jaw of the target object and stimulate the hypoglossal nerve of the target object.

[0009] In an embodiment, the gel patch includes:

[0010] A first electrode sheet, a second electrode sheet and a gel component. The first electrode sheet and the second electrode sheet are both arranged on the side of the gel component close to the main body and are connected to the main body. The side of the gel component far from the main body is used for adhering to the human lower jaw.

[0011] The first electrode sheet and the second electrode sheet form an electrical pulse conduction path with the gel assembly to conduct electrical pulses to the human mandible.

[0012] In one embodiment, the gel assembly includes:

[0013] A base, a first gel sheet, and a second gel sheet. The first electrode sheet and the second electrode sheet are both disposed on one side of the base close to the main body and connected to the main body. The first gel sheet and the second gel sheet are both disposed on one side of the base away from the main body and respectively correspond to the positions of the first electrode sheet and the second electrode sheet;

[0014] The base has a first through hole and a second through hole. The first electrode sheet is connected to the first gel sheet through the first through hole, and the second electrode sheet is connected to the second gel sheet through the second through hole;

[0015] The first electrode sheet and the first gel sheet form an electrical pulse conduction path, and the second electrode sheet and the second gel sheet form an electrical pulse conduction path to conduct electrical pulses to the human mandible.

[0016] In one embodiment, the first electrode sheet and the second electrode sheet are both magnetic metals. The main body has a first magnetic attraction assembly and a second magnetic attraction assembly. The first magnetic attraction assembly is magnetically connected to the first electrode sheet, and the second magnetic attraction assembly is magnetically connected to the second electrode sheet. The main body is used to output electrical pulses through the first magnetic attraction assembly and / or the second magnetic attraction assembly, and the electrical pulses are transmitted to the human mandible through the electrical pulse conduction path to stimulate the hypoglossal nerve.

[0017] In one embodiment, the main body includes:

[0018] A sound sensor for detecting the sound emitted from the mandible of the target object and outputting corresponding sound data;

[0019] An electrical pulse output module, the output end of which is electrically connected to the gel patch;

[0020] A main control module, which is electrically connected to the electrical pulse output module and the sound sensor respectively. The main control module is used to compare the sound data with preset sound data, and when the coincidence ratio of the sound data and the preset sound data reaches a preset ratio, it is determined that the target object is in a snoring state and controls the electrical pulse output module to output electrical pulses with a preset frequency and a preset pulse width.

[0021] In one embodiment, the host further includes a vibration detection module, which is electrically connected to the main control module. The vibration detection module is configured to obtain the vibration frequency at the lower jaw of the target object, and the main control module is configured to determine that the target object is in a snoring state and control the electrical pulse output module to output an electrical pulse with a preset frequency and a preset pulse width when the coincidence ratio of the sound data and the preset sound data reaches a first preset threshold and the vibration frequency reaches a second preset threshold.

[0022] In one embodiment, the vibration detection module is a three-axis sensor.

[0023] In one embodiment, the host further includes:

[0024] A battery circuit;

[0025] A plurality of boost branches, and each boost branch includes:

[0026] A first switch circuit, a second switch circuit, a discharge circuit, and a capacitor module. The input end of the first switch circuit is connected to the discharge end of the battery circuit, the output end of the first switch circuit is connected to the first end of the capacitor module, and the controlled end of the first switch circuit is electrically connected to the main control module;

[0027] The input end of the second switch circuit is connected to the first end of the capacitor module, the output end of the second switch circuit is connected to the input end of the electrical pulse output module, and the controlled end of the second switch circuit is electrically connected to the main control module;

[0028] The input end of the discharge circuit is connected to the first end of the capacitor module, the output end of the discharge circuit is grounded, the controlled end of the discharge circuit is electrically connected to the main control module, and the second end of the capacitor module is grounded.

[0029] In one embodiment, when the gel patch includes a first electrode sheet and a second electrode sheet, the host further includes:

[0030] A third switch circuit, a fourth switch circuit, a fifth switch circuit, and a sixth switch circuit. The input ends of the third switch circuit and the fourth switch circuit are both connected to the output ends of the plurality of boost branches. The output end of the third switch circuit is electrically connected to the first electrode sheet, and the controlled end of the third switch circuit is connected to the main control module;

[0031] The output end of the fourth switch circuit is electrically connected to the second electrode sheet, and the controlled ends of the third switch circuit and the fourth switch circuit are both electrically connected to the main control module;

[0032] The input terminal of the fifth switch circuit is electrically connected to the first electrode sheet, the output terminal of the fifth switch circuit is grounded, and the controlled terminal of the fifth switch circuit is connected to the controlled terminal of the fourth switch circuit;

[0033] The input terminal of the sixth switch circuit is electrically connected to the first electrode sheet, the output terminal of the sixth switch circuit is grounded, and the controlled terminal of the sixth switch circuit is connected to the controlled terminal of the third switch circuit.

[0034] In an embodiment, when the gel patch includes a first electrode sheet and a second electrode sheet, the host further includes:

[0035] A wearing detection circuit, the detection terminal of the wearing detection circuit is electrically connected to the first electrode sheet / the second electrode sheet, and the output terminal of the wearing detection circuit is electrically connected to the main control module;

[0036] The wearing detection circuit is configured to output a wearing detection signal to the main control module when detecting current on the first electrode sheet / the second electrode sheet, so that the main control module controls the electrical pulse output module to output electrical pulses with a preset frequency and a preset pulse width.

[0037] The respiratory therapy device of the present invention includes a host and a gel patch. The host is used to detect the respiratory state of a target object and output electrical pulses with a preset frequency and a preset pulse width when detecting that the respiratory state of the target object is snoring or apnea; wherein, the value range of the preset frequency is between 18 kHz and 22 kHz, and the value range of the preset pulse width is between 45 μs and 55 μs; the gel patch is connected to the host and is used to adhere to the lower jaw of the target object to conduct the electrical pulses to the lower jaw of the target object and stimulate the hypoglossal nerve of the target object. With such a setting, in practical applications, the respiratory therapy device of the present invention only outputs electrical pulses when detecting that the target object has snoring or apnea phenomena, avoiding unnecessary continuous operation, thereby greatly reducing energy consumption and extending the battery life of the respiratory therapy device of the present invention.

[0038] Under the stimulation of electrical pulses with a frequency between 18 kHz and 22 kHz, the capacitive impedance of the skin decreases significantly, so that the current output by the host can more easily penetrate the stratum corneum, thereby acting on the hypoglossal nerve more efficiently, preferably stimulating the hypoglossal nerve of the user, so that the blocked respiratory tract of the user can be opened again and normal breathing can be restored. Among them, the frequency of 18 kHz to 22 kHz is a medium frequency and will not cause local temperature rise. And the electrical pulses with a pulse width between 45 μs and 55 μs can accurately cover the excitation period of the hypoglossal nerve fibers, ensuring that a single pulse completely triggers an action potential and avoiding incomplete opening of the channel due to too short a pulse width or repeated triggering due to too long a pulse width. Description of the Drawings

[0039] To more clearly illustrate the technical solutions in the embodiments of the present invention or the prior art, the following will briefly introduce the drawings required for use in the description of the embodiments or the prior art. Obviously, the drawings in the following description are only some embodiments of the present invention. For those of ordinary skill in the art, without creative efforts, other drawings can be obtained based on the structures shown in these drawings.

[0040] Figure 1 Structural schematic diagram of an embodiment of the present invention;

[0041] Figure 2 Structural schematic diagram of another embodiment of the present invention;

[0042] Figure 3 Structural schematic diagram of still another embodiment of the present invention;

[0043] Figure 4 Module schematic diagram of an embodiment of the present invention;

[0044] Figure 5 Module schematic diagram of another embodiment of the present invention;

[0045] Figure 6 Circuit structure schematic diagram of an embodiment of the present invention;

[0046] Figure 7 Module schematic diagram of still another embodiment of the present invention;

[0047] Figure 8 Module schematic diagram of yet another embodiment of the present invention;

[0048] Figure 9 Circuit structure schematic diagram of yet another embodiment of the present invention.

[0049] Explanation of the reference numerals in the drawings:

[0050] 10. Host; 11. First magnetic attraction component; 12. Second magnetic attraction component; 20. Gel patch; 21. First electrode sheet; 22. Second electrode sheet; 23. Gel component; 231. Base; 232. First gel sheet; 233. Second gel sheet; 30. Sound sensor; 40. Main control module; 50. Electric pulse output module; 60. Battery circuit; 70. Boosting branch; 71. First switch circuit; 72. Second switch circuit; 73. Discharge circuit; 74. Capacitor module; 80. Third switch circuit; 90. Fourth switch circuit; 100. Fifth switch circuit; 110. Sixth switch circuit; 120. Vibration detection module; 130. Wearing detection module.

[0051] The realization, functional characteristics and advantages of the object of the present invention will be further described with reference to the embodiments and the drawings. Detailed implementation manners

[0052] The technical solutions in the embodiments of the present invention will be clearly and completely described below with reference to the accompanying drawings in the embodiments of the present invention. Obviously, the described embodiments are only a part of the embodiments of the present invention, rather than all embodiments. All other embodiments obtained by those of ordinary skill in the art based on the embodiments of the present invention without creative efforts shall fall within the protection scope of the present invention.

[0053] It should be noted that if there are directional indications (such as up, down, left, right, front, back...) involved in the embodiments of the present invention, such directional indications are only used to explain the relative position relationship and movement conditions between components in a specific posture. If the specific posture changes, the directional indications will also change accordingly.

[0054] In addition, if there are descriptions such as "first" and "second" involved in the embodiments of the present invention, such descriptions of "first" and "second" are only for descriptive purposes and cannot be understood as indicating or implying their relative importance or implicitly indicating the quantity of the indicated technical features. Thus, the features defined with "first" and "second" may explicitly or implicitly include at least one such feature. In addition, if "and / or" or "and / or" appears throughout the text, its meaning includes three parallel solutions. Taking "A and / or B" as an example, it includes solution A, or solution B, or the solution where A and B are satisfied simultaneously. In addition, the technical solutions between various embodiments can be combined with each other, but it must be based on the fact that those of ordinary skill in the art can implement them. When the combination of technical solutions is contradictory or cannot be implemented, it should be considered that such a combination of technical solutions does not exist and is not within the protection scope required by the present invention.

[0055] With the increasing attention of people to sleep quality, as a device for assisting in the treatment of snoring, a respiratory therapy device has gradually become an important tool for improving sleep health. Existing respiratory therapy devices act on the user's mandible, neck or laryngeal muscles through weak electrical stimulation or other physical intervention means, thereby regulating the activities of respiratory muscle groups and reducing or eliminating snoring.

[0056] However, existing respiratory therapy devices will continuously operate when turned on, and continuous operation will significantly shorten the battery life of the respiratory therapy device and affect the user experience. Moreover, in order to achieve better effects, existing respiratory therapy devices will use a higher electrical stimulation intensity, but this may cause discomfort or even pain to the user, especially being easily awakened during nighttime sleep. However, if the electrical stimulation intensity is low, it may not be able to effectively activate the target muscles (such as the genioglossus or mandibular muscles), resulting in poor treatment effects.

[0057] To this end, the present invention provides a respiratory therapy device, aiming to solve the technical problems of short battery life and usually poor stimulation of the hypoglossal nerve in existing respiratory therapy devices. In an embodiment of the present invention, referring to Figure 1 , the respiratory therapy device includes:

[0058] A main unit 10, which is used to detect the breathing state of a target object and output electrical pulses with a preset frequency and a preset pulse width when it detects that the breathing state of the target object is snoring or apnea;

[0059] Among them, the value range of the preset frequency is between 18 kHz and 22 kHz, and the value range of the preset pulse width is between 45 μs and 55 μs;

[0060] A gel patch 20, which is connected to the main unit 10 and is used to adhere to the lower jaw of the target object to conduct the electrical pulse to the lower jaw of the target object and stimulate the hypoglossal nerve of the target object.

[0061] In this embodiment, optionally, the main unit 10 can output electrical pulses based on a single-chip microcomputer. The single-chip microcomputer controls the output of a PWM (pulse width modulation) signal through programming. After the PWM signal is amplified and filtered, it forms an electrical pulse suitable for human stimulation. Optionally, the main unit 10 can also use an electrical pulse output module 50 and a main control module 40 to output electrical pulses. Referring to Figure 4 , when the main control module 40 detects and determines that the target object is in a snoring state or an apnea state, it provides a control signal to the electrical pulse output module 50 so that the electrical pulse output module 50 generates the required electrical pulses. Among them, the electrical pulse output module 50 can be integrated with a waveform generator chip or a high-voltage pulse generation circuit and other circuit modules for outputting electrical pulses.

[0062] In this embodiment, referring to Figure 4 , the main unit 10 can use a sound sensor 30 and a main control module 40 to detect the breathing state of the target object. When the respiratory therapy device of the present invention is adhered to the lower jaw of the target object, the sound sensor 30 acquires the sound data emitted from the lower jaw of the target object and transmits it to the main control module 40. The main control module 40 is used to determine that the target object is in an apnea state when the sound data is less than the volume threshold; the main control module 40 is also used to compare the sound data with the preset sound data and determine that the target object is in a snoring state when the coincidence ratio of the sound data and the preset sound data reaches a first preset threshold (70% - 90%).

[0063] It should be noted that the preset sound data is template data extracted based on the sound characteristics during human snoring, and usually includes characteristics such as the frequency range of snoring, amplitude variation, periodicity, etc. The main control module 40 calculates the similarity between the collected sound data and the preset sound data through algorithms (such as spectrum analysis, pattern matching, etc.), and determines that the target object is in a snoring state when the similarity (coincidence ratio) is relatively large.

[0064] It should be considered that some snoring phenomena may be manifested as low-frequency vibrations but without obvious sound signals (such as mild snoring), and such snoring phenomena cannot be detected only by the sound sensor 30 and the main control module 40.

[0065] For this reason, in order to improve the accuracy of detecting whether the target object is in a snoring state, in addition to using the sound sensor 30 and the main control module 40, the host 10 can also use the vibration detection module 120 to detect the vibration frequency at the lower jaw of the target object. The main control module 40 determines that the target object is in a snoring state when the coincidence ratio of the sound data and the preset sound data reaches the first preset threshold and the vibration frequency reaches the second preset threshold (50 Hz to 200 Hz). In a relatively preferred embodiment, the vibration detection module 120 can be implemented by using a three-axis sensor.

[0066] It should be noted that the cell membrane and the intercellular lipid layer of keratinocytes form a structure similar to a capacitor, presenting capacitive impedance to alternating current. When using medium-frequency electric pulses (18 kHz to 22 kHz), the change of capacitive impedance follows the following rule: Xc = 1 / (2πfC), where Xc is the capacitive impedance, f is the frequency of the electric pulse, and C is the equivalent capacitance with a value ranging from 0.01 to 0.1 μF / cm 2 From the above formula, it can be known that the higher the frequency, the lower the capacitive impedance. The electric pulse frequency output by the existing respiratory therapy device is less than 10 kHz. The relatively small frequency will result in a relatively high impedance of the skin, and the high impedance of the skin will cause a large amount of energy loss in the epidermal layer, making it difficult for the lower-frequency electric pulses to effectively penetrate to the depth where the hypoglossal nerve is located. However, too high-frequency electric pulses (such as 50 kHz to 100 kHz) will cause a local temperature rise, thus causing skin burns or mucosal damage. Under the stimulation of medium-frequency electric pulses of 18 kHz to 22 kHz, the capacitive impedance of the stratum corneum decreases, making the current on the electrode patch easier to penetrate the skin surface layer, reducing the energy dissipation in the stratum corneum, enabling the electric pulses to be efficiently transmitted to the hypoglossal nerve, and the frequency of 18 kHz to 22 kHz is a medium frequency and will not cause a local temperature rise.

[0067] In addition, the human auditory perception range is approximately 20 Hz - 20 kHz. The frequency design from 18 kHz to 22 kHz places the main frequency of the electrical pulse signal at the edge of the audible frequency band (greater than 18 kHz), which not only avoids accidentally triggering the auditory nerve (such as tinnitus), but also reduces the user's perception sensitivity to electrical stimulation and improves comfort.

[0068] It should be noted that the absolute refractory period of the motor fibers of the hypoglossal nerve is approximately 50 μs - 60 μs. If the pulse width of the electrical pulse exceeds 60 μs, the latter half of the pulse will fall into the refractory period, resulting in energy waste; if it is shorter than 45 μs, a large increase in voltage is required to compensate for the energy, increasing power consumption and the risk of burns. Electrical pulses with a pulse width of 45 μs - 55 μs can accurately cover the excitation period of the hypoglossal nerve, ensuring the effective triggering of action potentials and avoiding incomplete opening of the ion channels (sodium ion channels) on the nerve cell membrane due to too short a pulse width or repeated triggering due to too long a pulse width. Repeated triggering may cause the hypoglossal nerve to contract out of the expected rhythm (such as maintaining airway patency), and instead lead to muscle spasms or loss of control due to high-frequency signal interference.

[0069] In one embodiment, referring to Figure 2 , the gel patch 20 includes:

[0070] A first electrode sheet 21, a second electrode sheet 22, and a gel assembly 23. The first electrode sheet 21 and the second electrode sheet 22 are both disposed on the side of the gel assembly 23 close to the host 10 and are connected to the host 10. The side of the gel assembly 23 away from the host 10 is used to fit against the human mandible.

[0071] The first electrode sheet 21 and the second electrode sheet 22 form an electrical pulse conduction path with the gel assembly 23 to conduct the electrical pulse to the human mandible.

[0072] The first electrode sheet 21 and the second electrode sheet 22 can be made of a conductive material (such as silver, stainless steel, or conductive polymer) to receive the electrical pulse signal output from the host 10 and conduct the electrical pulse to the human mandible through the gel assembly 23. When the gel assembly 23 is attached to the mandible of the target object, the first electrode sheet 21 and the second electrode sheet 22 form an electric current loop with the human body, enabling the electrical pulse to flow between the first electrode sheet 21 and the second electrode sheet 22, thereby acting on the mandible of the target object.

[0073] The gel assembly 23 can be made of a conductive hydrogel material to reduce the contact resistance between the electrode sheet and the skin and ensure that the electrical pulse can be efficiently and evenly transmitted to the mandible of the target object.

[0074] In one embodiment, referring to Figure 3 , the gel assembly 23 includes:

[0075] A base 231, a first gel sheet 232 and a second gel sheet 233. Both the first electrode sheet 21 and the second electrode sheet 22 are disposed on one side of the base 231 close to the host 10 and are connected to the host 10. Both the first gel sheet 232 and the second gel sheet 233 are disposed on one side of the base 231 away from the host 10 and correspond to the positions of the first electrode sheet 21 and the second electrode sheet 22 respectively;

[0076] The base 231 has a first through hole and a second through hole (not shown in the figure). The first electrode sheet 21 is connected to the first gel sheet 232 through the first through hole, and the second electrode sheet 22 is connected to the second gel sheet 233 through the second through hole;

[0077] The first electrode sheet 21 and the first gel sheet 232 form an electric pulse conduction path, and the second electrode sheet 22 and the second gel sheet 233 form an electric pulse conduction path to conduct the electric pulse to the human mandible.

[0078] In this embodiment, the base 231 can be implemented by using PU leather (the epidermis of polyurethane composition). The base 231 is used to fix the connection relationships between the first electrode sheet 21 and the second electrode sheet 22 and the first gel sheet 232 and the second gel sheet 233 respectively, to prevent them from separating from each other. Moreover, the base 231 is made of a soft material and can be bent according to the curve of the mandible, so that both the first gel sheet 232 and the second gel sheet 233 can fit on the mandible of the target object.

[0079] The first gel sheet 232 and the second gel sheet 233 can be made of a conductive hydrogel material. The conductive hydrogel material can reduce the contact resistance between the electrode sheet and the skin, and ensure that the electric pulse can be efficiently and evenly transmitted to the mandible of the target object.

[0080] In one embodiment, referring to Figure 3 , both the first electrode sheet 21 and the second electrode sheet 22 are magnetic metals. The host 10 has a first magnetic attraction component 11 and a second magnetic attraction component 12. The first magnetic attraction component 11 is magnetically connected to the first electrode sheet 21, and the second magnetic attraction component 12 is magnetically connected to the second electrode sheet 22. The host 10 is used to output an electric pulse through the first magnetic attraction component 11 and / or the second magnetic attraction component 12, and the electric pulse is transmitted to the human mandible through the electric pulse conduction path to stimulate the hypoglossal nerve.

[0081] The main body 10 is magnetically connected to the first electrode piece 21 and the second electrode piece 22 through the first magnetic attraction component 11 and the second magnetic attraction component 12 respectively, so that the main body 10 is detachably connected to the gel patch 20. With this setting, not only the operation convenience of the respiratory therapy device of the present invention is improved, but also the adsorption force provided by the magnetic attraction component is sufficient to ensure a stable mechanical connection and electrical connection between the gel patch 20 and the main body 10, avoiding detachment caused by movement or external force, and preventing signal attenuation or reduction of the treatment effect caused by poor contact. In practical applications, the user only needs to bring the side of the gel patch provided with the first electrode piece 21 and the second electrode piece 22 close to the main body 10, and the connection can be automatically completed by magnetic attraction, without complicated plugging or screwing operations.

[0082] In order to save the material cost and overall volume of the respiratory therapy device, the existing respiratory therapy devices generally use relatively common small lithium batteries for power supply. Since the power supply voltage of the small lithium battery is relatively small (about 3.3V or 5V), while the working voltage of the circuit module for outputting electrical pulses in the main body 10 is relatively large, usually dozens of volts, the power supply voltage of the small lithium battery needs to be boosted by a boost circuit before it can supply power to the electrical pulse output module 50.

[0083] It should be considered that the boost circuit usually has a charging and discharging process. If it is necessary to increase the output frequency and output voltage of the boost circuit, it is necessary to lengthen the discharging process of the boost circuit and shorten its charging process, but this will require extremely high performance of the boost circuit. There are few boost circuits with extremely high performance on the market, and the price is high.

[0084] In view of this, based on the above embodiment in which the main body 10 includes a sound sensor 30, an electrical pulse output module 50 and a main control module 40, in an embodiment of the present invention, referring to Figure 5 , the main body 10 further includes:

[0085] A battery circuit 60;

[0086] A plurality of boost branches 70, the boost branch 70 includes:

[0087] A first switch circuit 71, a second switch circuit 72, a discharge circuit 73 and a capacitor module 74. The input end of the first switch circuit 71 is connected to the discharge end of the battery circuit 60, the output end of the first switch circuit 71 is connected to the first end of the capacitor module 74, and the controlled end of the first switch circuit 71 is electrically connected to the main control module 40;

[0088] The input end of the second switch circuit 72 is connected to the first end of the capacitor module 74, the output end of the second switch circuit 72 is connected to the input end of the electrical pulse output module 50, and the controlled end of the second switch circuit 72 is electrically connected to the main control module 40;

[0089] The input end of the discharge circuit 73 is connected to the first end of the capacitor module 74, the output end of the discharge circuit 73 is grounded, the controlled end of the discharge circuit 73 is electrically connected to the main control module 40, and the second end of the capacitor module 74 is grounded.

[0090] In this embodiment, the first switch circuit 71 and the second switch circuit 72 can be implemented by at least one switching tube, such as a MOS tube, an IGBT tube, a thyristor, a triode, a power tube, etc.

[0091] In this embodiment, when the first switch circuit 71 is turned on and the second switch circuit 72 is turned off, the capacitor module 74 stores the electrical energy output by the access battery circuit 60. After the capacitor module 74 finishes storing energy, the first switch circuit 71 is controlled to be turned off and the second switch circuit 72 is turned on, so that the capacitor module 74 outputs a high voltage to the electric pulse output module 50. During the discharging process, the overall voltage received by the electric pulse output module 50 is the first preset voltage. When the voltage of the capacitor module 74 drops to the preset voltage value, the discharge circuit 73 is controlled to release the remaining charge of the capacitor module 74, and the first switch circuit 71 is turned on and the second switch circuit 72 is turned off, so that the battery circuit 60 recharges the capacitor module 74.

[0092] When one of the boost branches 70 discharges, the other boost branches 70 access the electrical energy output by the battery circuit 60 to charge their capacitor modules 74. When one of the boost branches 70 finishes discharging, another boost branch 70 is controlled to discharge, and the other boost branches 70 are controlled to charge. With such a setting, multiple boost branches 70 can discharge to the electric pulse output module 50 continuously or at a higher frequency, which is equivalent to lengthening the charging process of the boost branch 70 and shortening its charging process, so that the output frequency and output voltage of the boost branch 70 are higher and more stable, thereby meeting the power supply requirements of the electric pulse output module 50.

[0093] In one embodiment, referring to Figure 6 , the first switch circuit 71 includes:

[0094] A first switching tube Q1, a second switching tube Q2, a first resistor R1, a second resistor R2, a third resistor R3, and a fourth resistor R4. The input end of the first switching tube Q1 is connected to the discharge end of the battery circuit 60, the output end of the first switching tube Q1 is connected to the first end of the capacitor module 74, the first end of the first resistor R1 is connected to the controlled end of the first switching tube Q1, the first end of the second resistor R2 is connected to the input end of the first switching tube Q1, and the second end of the second resistor R2 is connected to the second end of the first resistor R1;

[0095] The input terminal of the second switching transistor Q2 is connected to the second terminal of the first resistor R1. The output terminal of the second switching transistor Q2 is grounded. The controlled terminal of the second switching transistor Q2 is connected to the second terminal of the third resistor R3. The first terminal of the third resistor R3 is electrically connected to the main control module 40. The first terminal of the fourth resistor R4 is connected to the controlled terminal of the second switching transistor Q2. The second terminal of the fourth resistor R4 is grounded;

[0096] The second switching circuit 72 includes:

[0097] A third switching transistor Q3, a fourth switching transistor Q4, a fifth resistor R5, a sixth resistor R6, a seventh resistor R7, and an eighth resistor R8. The input terminal of the third switching transistor Q3 is connected to the first terminal of the capacitor module 74. The output terminal of the third switching transistor Q3 is connected to the input terminal of the electric pulse output module 50. The first terminal of the fifth resistor R5 is connected to the controlled terminal of the third switching transistor Q3. The first terminal of the sixth resistor R6 is connected to the input terminal of the third switching transistor Q3. The second terminal of the sixth resistor R6 is connected to the second terminal of the fifth resistor R5;

[0098] The input terminal of the fourth switching transistor Q4 is connected to the second terminal of the fifth resistor R5. The output terminal of the fourth switching transistor Q4 is grounded. The controlled terminal of the fourth switching transistor Q4 is connected to the second terminal of the seventh resistor R7. The first terminal of the seventh resistor R7 is electrically connected to the main control module 40. The first terminal of the eighth resistor R8 is connected to the controlled terminal of the fourth switching transistor Q4. The second terminal of the eighth resistor R8 is grounded.

[0099] Among them, the first switching transistor Q1 and the third switching transistor Q3 are PNP triodes, and the second switching transistor Q2 and the fourth switching transistor Q4 are NPN triodes. When it is necessary to control the charging of the capacitor module 74, the main control module 40 controls the second switching transistor Q2 to conduct, and the base voltage of the first switching transistor Q1 is pulled down to make the first switching transistor Q1 conduct. The main control module 40 also controls the fourth switching transistor Q4 to turn off, and the base voltage of the third switching transistor Q3 is pulled down to make the third switching transistor Q3 turn off. At this time, the current of the battery circuit 60 flows through the first switching transistor Q1 to the capacitor module 74; on the contrary, when it is necessary to control the discharging of the capacitor module 74, the main control module 40 controls the second switching transistor Q2 to turn off, and the base voltage of the first switching transistor Q1 is pulled down to make the first switching transistor Q1 turn off. The main control module 40 also controls the fourth switching transistor Q4 to conduct, so that the base voltage of the third switching transistor Q3 is pulled down, and the third switching transistor Q3 conducts. The current of the battery circuit 60 discharges through the third switching transistor Q3 to the electric pulse output module 50.

[0100] It should be considered that when the gel patch 20 includes the first electrode piece 21 and the second electrode piece 22, the electrical pulse is transmitted to the human skin surface through the current loop formed by the first electrode piece 21 and the second electrode piece 22 in sequence to stimulate the hypoglossal nerve or related muscle groups to relieve snoring. However, if the current direction remains unchanged all the time, it will cause uneven distribution of ions on the skin surface, thus leading to charge accumulation. Charge accumulation may cause skin tingling, burning sensation or other discomforts, and even cause local skin damage.

[0101] In this regard, based on the above embodiment in which the host 10 includes the sound sensor 30, the electrical pulse output module 50 and the main control module 40, in an embodiment of the present invention, with reference to Figure 7 , in the case where the gel patch 20 includes the first electrode piece 21 and the second electrode piece 22, the host 10 further includes:

[0102] A third switch circuit 80, a fourth switch circuit 90, a fifth switch circuit 100 and a sixth switch circuit 110. The input ends of the third switch circuit 80 and the fourth switch circuit 90 are both connected to the output ends of the plurality of boosting branches 70. The output end of the third switch circuit 80 is electrically connected to the first electrode piece 21, and the controlled end of the third switch circuit 80 is connected to the main control module 40;

[0103] The output end of the fourth switch circuit 90 is electrically connected to the second electrode piece 22, and the controlled ends of the third switch circuit 80 and the fourth switch circuit 90 are both electrically connected to the main control module 40;

[0104] The input end of the fifth switch circuit 100 is electrically connected to the first electrode piece 21, the output end of the fifth switch circuit 100 is grounded, and the controlled end of the fifth switch circuit 100 is connected to the controlled end of the fourth switch circuit 90;

[0105] The input end of the sixth switch circuit 110 is electrically connected to the first electrode piece 21, the output end of the sixth switch circuit 110 is grounded, and the controlled end of the sixth switch circuit 110 is connected to the controlled end of the third switch circuit 80.

[0106] In this embodiment, the third switch circuit 80, the fourth switch circuit 90, the fifth switch circuit 100 and the sixth switch circuit 110 can all be implemented by at least one switching tube, such as MOS tube, IGBT tube, thyristor, triode, power tube, etc.

[0107] In this embodiment, the main control module 40 is configured to control the third switch circuit 80 to conduct and the fifth switch circuit 100 to conduct, and control the fourth switch circuit 90 and the sixth switch circuit 110 to turn off, so that the current output by the boost branch 70 flows through the path of the third switch circuit 80, the first electrode plate 21, the second electrode plate 22 and the sixth switch circuit 110. At this time, the first electrode plate 21 is the positive electrode and the second electrode plate 22 is the negative electrode. Positive charges will accumulate near the first electrode plate 21, and negative charges will accumulate near the second electrode plate 22. The main control module 40 is further configured to control the fourth switch circuit 90 and the sixth switch circuit 110 to conduct, and control the third switch circuit 80 and the fifth switch circuit 100 to turn off, so that the current output by the boost branch 70 flows through the path of the fourth switch circuit 90, the second electrode plate 22, the first electrode plate 21 and the fifth switch circuit 100. At this time, the first electrode plate 21 is the negative electrode and the second electrode plate 22 is the positive electrode, so that the previous charge distribution is reversed, thereby canceling the previous charge accumulation. With such a setting, by continuously exchanging the positions of the positive and negative electrodes, it is ensured that the charge distribution on the skin surface always remains balanced, avoiding long-term charge accumulation.

[0108] Based on the above embodiment in which the host 10 includes the sound sensor 30, the electric pulse output module 50 and the main control module 40, in an embodiment of the present invention, refer to Figure 8 , when the gel patch 20 includes the first electrode plate 21 and the second electrode plate 22, the host 10 further includes:

[0109] A wearing detection circuit 130, the detection end of the wearing detection circuit 130 is electrically connected to the first electrode plate 21 / the second electrode plate 22, and the output end of the wearing detection circuit 130 is electrically connected to the main control module 40;

[0110] The wearing detection circuit 130 is configured to output a wearing detection signal to the main control module 40 when detecting a current on the first electrode plate 21 / the second electrode plate 22, so that the main control module 40 controls the electric pulse output module 50 to output an electric pulse with a preset frequency and a preset pulse width.

[0111] It should be noted that when the gel patch 20 is attached to the human skin, the human skin and tissues, the first electrode patch 21 and the second electrode patch 22 form a low-impedance loop. When the respiratory therapy device of the present invention starts to work and the gel patch 20 is attached to the target object, the host 10 outputs current to the first electrode patch 21 / the second electrode patch 22. Since the human skin and tissues, the first electrode patch 21 and the second electrode patch 22 have formed a low-impedance loop, current flows through the first electrode patch 21 and the second electrode patch 22. When the wearing detection module 130 detects the current, it outputs a feedback signal to the main control module 40. After receiving the feedback signal, the main control module 40 controls the electrical pulse output module 50 to output electrical pulses with a preset frequency and a preset pulse width to the first electrode patch 21 and the second electrode patch 22.

[0112] When the gel patch 20 is not in contact with the human body, the resistance between the first electrode patch 21 and the second electrode patch 22 is extremely large, equivalent to an open circuit, resulting in almost no current flow. At this time, the wearing detection module 130 does not detect current, and the main control module 40 determines that the gel patch 20 is not in contact with the human body without receiving a feedback signal.

[0113] In this embodiment, the wearing detection module 130 can be implemented by a current detection circuit. The current detection circuit is used to detect the current on the positive / negative electrode and output a corresponding current detection signal. When the main control module 40 determines that there is current on the first electrode patch 21 / the second electrode patch 22 according to the current detection signal, it controls the electrical pulse output module 50 to output electrical pulses with a preset frequency and a preset pulse width.

[0114] In combination with the circuit structures of the above-mentioned third switch circuit 70, fourth switch circuit 80, fifth switch circuit 90 and sixth switch circuit 100, refer to Figure 9 , the wearing detection module 130 includes: a sixth switching tube Q6, a voltage stabilizing diode D1, a twelfth resistor R12, a thirteenth resistor R13 and a fourteenth resistor R14. The first end of the twelfth resistor R12 is connected to the discharge end of the battery circuit 40. The second end of the twelfth resistor R12 is connected to the input end of the sixth switching tube Q6. The input end of the sixth switching tube Q6 is also electrically connected to the main control circuit. The output end of the sixth switching tube Q6 is grounded. The controlled end of the sixth switching tube Q6 is respectively connected to the second end of the thirteenth resistor R13 and the first end of the fourteenth resistor R14. The second end of the fourteenth resistor R14 is grounded. The first end of the thirteenth resistor R13 is connected to the cathode of the voltage stabilizing diode D1. The anode of the voltage stabilizing diode D1 is grounded. The cathode of the voltage stabilizing diode D1 is also electrically connected to the output ends of the fifth switch circuit 90 and the sixth switch circuit 100.

[0115] The sixth switching transistor Q6 is an NPN transistor. When the gel patch 20 is attached to the human skin, a low-impedance loop is formed among the human skin, the first electrode sheet 21, and the second electrode sheet 22. When the respiratory therapy device of the present invention starts to work, the main control module 40 controls the fourth switching circuit 80 and the fifth switching circuit 90 to conduct / the third switching circuit 70 and the sixth switching circuit 100 to conduct. At this time, the current output by the boost branch 70 flows to the zener diode D1 and breaks down the zener diode D1. After the zener diode D1 is broken down, the voltage of the fourteenth resistor R14 rises to turn on the sixth switching transistor Q6. After the sixth switching transistor Q6 is turned on, the voltage of the GPIO interface of the main control module 40 for accessing the sixth switching transistor Q6 is pulled low. After detecting the low level, the main control module 40 controls the electric pulse output module 50 to output electric pulses.

[0116] When the gel patch 20 is not attached to the human skin, no path is formed between the first electrode sheet 21 and the second electrode sheet 22, and the current cannot flow to the zener diode D1. The zener diode D1 is not broken down. At this time, the sixth switching transistor Q6 is in the off state. When the main control module 40 detects the high level, it controls the electric pulse output module 50 to stop outputting electric pulses to avoid mis-triggering.

[0117] The above are only exemplary embodiments of the present invention, and do not limit the patent scope of the present invention accordingly. Any equivalent structural transformation made under the technical concept of the present invention by using the content of the specification and drawings of the present invention, or any direct / indirect application in other related technical fields is included in the patent protection scope of the present invention.

Claims

1. A respiratory therapy device, characterized in that, Including: A main unit, which is used to detect the breathing state of a target object and output an electrical pulse with a preset frequency and a preset pulse width when detecting that the breathing state of the target object is snoring or apnea; Wherein, the value range of the preset frequency is between 18 kHz and 22 kHz, and the value range of the preset pulse width is between 45 μs and 55 μs; A gel patch, which is connected to the main unit and is used to fit on the lower jaw of the target object to conduct the electrical pulse to the lower jaw of the target object and stimulate the hypoglossal nerve of the target object.

2. The respiratory therapy device according to claim 1, characterized in that, The gel patch includes: A first electrode sheet, a second electrode sheet and a gel assembly. The first electrode sheet and the second electrode sheet are both arranged on the side of the gel assembly close to the main unit and are connected to the main unit. The side of the gel assembly away from the main unit is used to fit on the human lower jaw; The first electrode sheet and the second electrode sheet form an electrical pulse conduction path to conduct the electrical pulse to the human lower jaw.

3. The respiratory therapy device according to claim 2, characterized in that, The gel assembly includes: A base, a first gel sheet and a second gel sheet. The first electrode sheet and the second electrode sheet are both arranged on the side of the base close to the main unit and are connected to the main unit. The first gel sheet and the second gel sheet are both arranged on the side of the base away from the main unit and are respectively corresponding to the positions of the first electrode sheet and the second electrode sheet; The base has a first through hole and a second through hole. The first electrode sheet is connected to the first gel sheet through the first through hole, and the second electrode sheet is connected to the second gel sheet through the second through hole; The first electrode sheet and the first gel sheet form an electrical pulse conduction path, and the second electrode sheet and the second gel sheet form an electrical pulse conduction path to conduct the electrical pulse to the human lower jaw.

4. The breathing treatment apparatus according to claim 2, wherein, The first electrode sheet and the second electrode sheet are both made of magnetic metal. The main unit has a first magnetic attraction component and a second magnetic attraction component. The first magnetic attraction component is magnetically connected to the first electrode sheet, and the second magnetic attraction component is magnetically connected to the second electrode sheet. The main unit is used to output an electrical pulse through the first magnetic attraction component and / or the second magnetic attraction component, and the electrical pulse is transmitted to the human lower jaw through the electrical pulse conduction path to stimulate the hypoglossal nerve.

5. The respiratory therapy device according to any one of claims 1 to 4, characterized in that, The main unit includes: A sound sensor, which is used to detect the sound emitted from the lower jaw of the target object and output corresponding sound data; An electrical pulse output module, whose output end is electrically connected to the gel patch; A main control module, which is electrically connected to the electrical pulse output module and the sound sensor respectively. The main control module is used to compare the sound data with preset sound data, and when the coincidence ratio of the sound data and the preset sound data reaches a preset ratio, determine that the target object is in a snoring state and control the electrical pulse output module to output an electrical pulse with a preset frequency and a preset pulse width.

6. The respiratory therapy device according to claim 5, characterized in that, The main unit further includes: A vibration detection module, which is electrically connected to the main control module. The vibration detection module is used to obtain the vibration frequency at the lower jaw of the target object, and the main control module is used to determine that the target object is in a snoring state and control the electrical pulse output module to output electrical pulses with a preset frequency and a preset pulse width when the coincidence ratio between the sound data and the preset sound data reaches a first preset threshold and the vibration frequency reaches a second preset threshold.

7. The respiratory therapy device according to claim 6, wherein, The vibration detection module is a three-axis sensor.

8. The respiratory therapy device according to claim 5, wherein, The host further includes: A battery circuit; Multiple boost branches, and each boost branch includes: A first switch circuit, a second switch circuit, a discharge circuit, and a capacitor module. The input end of the first switch circuit is connected to the discharge end of the battery circuit, the output end of the first switch circuit is connected to the first end of the capacitor module, and the controlled end of the first switch circuit is electrically connected to the main control module; The input end of the second switch circuit is connected to the first end of the capacitor module, the output end of the second switch circuit is connected to the input end of the electrical pulse output module, and the controlled end of the second switch circuit is electrically connected to the main control module; The input end of the discharge circuit is connected to the first end of the capacitor module, the output end of the discharge circuit is grounded, the controlled end of the discharge circuit is electrically connected to the main control module, and the second end of the capacitor module is grounded.

9. The respiratory treatment device according to claim 8, wherein, When the gel patch includes a first electrode patch and a second electrode patch, the host further includes: A third switch circuit, a fourth switch circuit, a fifth switch circuit, and a sixth switch circuit. The input ends of the third switch circuit and the fourth switch circuit are both connected to the output ends of the multiple boost branches. The output end of the third switch circuit is electrically connected to the first electrode patch, and the controlled end of the third switch circuit is connected to the main control module; The output end of the fourth switch circuit is electrically connected to the second electrode patch, and the controlled ends of the third switch circuit and the fourth switch circuit are both electrically connected to the main control module; The input end of the fifth switch circuit is electrically connected to the first electrode patch, the output end of the fifth switch circuit is grounded, and the controlled end of the fifth switch circuit is connected to the controlled end of the fourth switch circuit; The input end of the sixth switch circuit is electrically connected to the first electrode patch, the output end of the sixth switch circuit is grounded, and the controlled end of the sixth switch circuit is connected to the controlled end of the third switch circuit.

10. The respiratory therapy device according to claim 5, characterized in that, When the gel patch includes a first electrode patch and a second electrode patch, the host further includes: A wearing detection circuit. The detection end of the wearing detection circuit is electrically connected to the first electrode patch / the second electrode patch, and the output end of the wearing detection circuit is electrically connected to the main control module; The wearing detection circuit is used to output a wearing detection signal to the main control module when detecting that there is current on the first electrode patch / the second electrode patch, so that the main control module controls the electrical pulse output module to output electrical pulses with a preset frequency and a preset pulse width.

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