Wearable air-promoting waistcoat based on intestinal sound features

Abstract

This invention discloses a wearable gas-inducing vest based on bowel sound characteristics. It includes a vest body, a base with guiding diagonal supports, an array of independent airbags arranged in segments along the physiological course of the colon, a high-fidelity bowel sound monitoring module, and a microprocessor. The microprocessor uses piezoelectric sensors for silent data acquisition, extracts the energy and frequency characteristics of bowel sounds, and incorporates them into a closed-loop control model to identify intestinal paralysis or spasm, dynamically outputting commands to strengthen motility or provide safety avoidance. This invention can monitor intestinal motility; when intestinal motility is insufficient, it outputs stronger squeezing force to awaken the intestines; when extremely high-frequency bowel sounds resembling intestinal spasm are detected, it immediately opens a valve to release pressure and provide emergency avoidance. The inclined guiding structure on the base of this invention converts vertical expansion force into clockwise tangential thrust, which, combined with the stepped actions triggered sequentially in four areas, can replicate the spontaneous unidirectional peristaltic waves of a healthy human intestine on the surface of the abdomen.

Description

Technical Field

[0001] This invention relates to the field of medical physiotherapy device technology, specifically a wearable gas-relieving vest based on bowel sound characteristics. Background Technology

[0002] Most abdominal massagers or gas-relieving devices currently on the market rely on blindly executing preset mechanical vibrations or airbag compression programs. These devices cannot perceive the true physiological state of the patient's intestines in real time, posing significant limitations and safety risks. For individuals with severe intestinal motility deficiency or mild indigestion, the massage intensity and timing output by the device are fixed, making it impossible to provide personalized treatment.

[0003] When a patient experiences a sudden onset of acute intestinal spasm or severe diarrhea, the intestines are already in a state of high sensitivity and abnormal contraction. If the device continues to blindly apply external pressure at this time, it will not only fail to promote gas expulsion but will also exacerbate the patient's severe abdominal pain and may even induce serious visceral mechanical damage such as intussusception. Summary of the Invention

[0004] To address the shortcomings of existing technologies, this invention provides a wearable gas-inducing vest based on bowel sound characteristics, thus solving the existing technical problems.

[0005] To achieve the above objectives, the present invention provides the following technical solution: A wearable gas-inducing vest based on bowel sound characteristics includes a wearable vest body, a base, and an intestinal tracking airbag assembly. The base is sewn or fixedly connected to the inner wall of the wearable vest body facing the abdomen. The intestinal trajectory airbag assembly is embedded in the pre-reserved mounting groove of the base. The inner wall of the mounting groove of the base is provided with a guide brace. The brace follows the clockwise direction of the physiological trajectory of the human intestine and is inclined downward. The intestinal trajectory airbag group contains a total of 8 independently operating airbag units, which divide the inner wall of the wearable vest body into four consecutive activating regions from right to left, and each activating region has 2 airbag units arranged in series along the intestinal direction. The four actuation zones are, in order: the first zone corresponding to the right ascending colon, the second zone corresponding to the transverse colon, the third zone corresponding to the left descending colon, and the fourth zone corresponding to the sigmoid colon at the end of the left lower abdomen. Each airbag unit is sealed at the end with an independent air inlet pipe, and each air inlet pipe is connected to multiple electronic valves in the electro-pneumatic assembly.

[0006] Preferably, the electro-pneumatic assembly includes an air pump, multiple electronic valves, a drive circuit, a processor, and a power supply. The air outlet of the air pump is connected in parallel with the air inlet of each electronic valve through a main air pipeline. The air outlet of each electronic valve is sealed and connected to the independent air inlet pipe corresponding to each airbag unit. The power supply is electrically connected to the processor, drive circuit, air pump and each electronic valve through the power management and voltage regulation module; the control signal output terminal of the processor is connected to the signal input terminal of the drive circuit, and the output terminal of the drive circuit is connected to the control terminal of the air pump and each electronic valve. The processor is configured to execute a stepped timing control algorithm comprising three stages: inflation, pressure holding, and deflation, to the drive circuit. The stepped timing control algorithm sequentially controls adjacent airbag units to perform the above three stages in the direction from the first region to the fourth region. When the i-th airbag unit located upstream starts the inflation stage and continues for a first preset time, and then enters the pressure holding stage, the microprocessor controls the (i+1)-th airbag unit located downstream to start the inflation stage. The deflation stage of the i-th airbag unit is only started after the (i+1)-th airbag unit starts the inflation stage and after a second preset time delay.

[0007] Preferably, it also includes a bowel sound monitoring feedback system, which includes multiple piezoelectric thin film sensors and an ADC conversion chip. The analog signal input terminal of the ADC conversion chip is electrically connected to the signal output terminal of the piezoelectric thin film sensor, and the microprocessor is connected to the digital signal output terminal of the ADC conversion chip via an I2C or SPI communication bus. The number of piezoelectric thin film sensors is at least four, which are distributed and fixedly installed on the surface of the base facing the abdomen of the human body along the physiological and anatomical direction of the human colon.

[0008] Preferably, the piezoelectric thin film sensor adopts a flexible silicone patch encapsulation structure.

[0009] Preferably, the microprocessor incorporates a closed-loop control algorithm for bowel sound monitoring and feedback. Within a set monitoring time window T, it acquires a discrete sequence of digital bowel sound signals x(n), where n = 1, 2, ..., N, and N is the total number of sampling points. The algorithm iteratively executes the following workflow: S1. Silent acquisition: Control the intestinal trajectory airbag group to obtain a pure signal sequence x(n); S2. Feature extraction: Calculate the short-time energy E of the sound signal and the frequency R of bowel sounds within the listening window T; S3, State determination: Input the extracted parameters (E,R) into the preset physiological state determination model, and output the state identifier variable S_state by comparing it with the preset baseline threshold. S4. Dynamic execution: Retrieve the matching airbag target inflation pressure P_target according to S_state, and control the airbag group to perform corresponding physical massage actions.

[0010] Preferably, in the feature extraction algorithm of step S2: The calculation formula for short-time energy E is: E = (1 / N) * Σx²(n) The microprocessor identifies valid bowel sound events through a preset amplitude threshold x_th. The calculation formula for the bowel sound occurrence frequency R is: R = (1 / T) * Σδ(x(n)) Where, when |x(n)| > x_th and the duration meets the preset conditions, the pulse function δ(x(n)) = 1; otherwise, δ(x(n)) = 0.

[0011] Preferably, in steps S3 and S4, the determination conditions and execution logic for the "intestinal paralysis or insufficient motility" state are: Set the energy baseline threshold for normal bowel sounds as E_base, and the frequency baseline threshold as R_base; When the determination model conditions are met: E < a * E_base and R < b * R_base, the microprocessor outputs the status flag S_state = 1; At this time, the microprocessor executes the enhanced activation mode: the output target inflation pressure P_target adopts the dynamic compensation formula: P_target = P0 + k_p * (R_base - R) Where, P0 is the basic massage pressure, and k_p is the pressure compensation coefficient, so that the air pump outputs an enhanced extrusion force proportional to the degree of intestinal motility defect.

[0012] Preferably, the safety protection model for the "intestinal spasm or hypersensitivity" state is: When extremely high-frequency bowel sounds are detected and the determination condition R > c * R_base is met, the microprocessor outputs the status flag S_state = 2; At this time, trigger the safety avoidance mode: the microprocessor immediately forcibly sets the target inflation pressure P_target = 0, opens all electronic valves to release pressure, and locks the air pump control port until the frequency R returns to the normal baseline range.

[0013] Preferably, the piezoelectric thin film sensor is model FDT1-028K, the ADC conversion chip is model ADS1115, the microprocessor is an ESP32 series microcontroller with a built-in wireless communication module, the driving circuit uses an AO3400 N-channel enhancement field-effect transistor to drive the micro air pump, a Darlington transistor array chip of model ULN2003A to drive multiple electronic valves, and the power management and voltage regulation module includes a boost power management chip of model IP5306 and a low dropout linear regulator of model ME6211.

[0014] This invention can monitor intestinal motility. When intestinal motility is insufficient, it outputs stronger squeezing force to awaken the intestine. When extremely high frequency bowel sounds suspected of intestinal spasm are detected, it will immediately open the valve to release pressure and avoid danger in an emergency.

[0015] The inclined guide structure on the base of this invention converts the vertical expansion force into a clockwise tangential thrust. Combined with the stepped action triggered sequentially by the four areas, it can replicate the spontaneous unidirectional peristaltic wave of the human healthy intestine on the surface of the human abdomen.

[0016] This invention uses overlapping timing interlocking logic to ensure that the upstream airbag will never release air before the downstream airbag generates effective pressure. It maintains an air pressure behind the gas, blocking the path of the gas back upstream, and ensuring that intestinal contents and waste gas can only be pushed unidirectionally towards the rectum. Attached Figure Description

[0017] Figure 1 This is a schematic diagram of the wearable vest and intestinal tracking airbag assembly of the present invention; Figure 2 This is a schematic diagram of the electrical circuit portion of the present invention; Figure 3 This is a flowchart of the closed-loop control algorithm and state determination based on bowel sound feedback of the present invention.

[0018] 1. Wearing vest; 2. Base support; 3. Intestinal tracking airbag assembly; 4. Piezoelectric thin film sensor. Detailed Implementation

[0019] The technical solutions of the embodiments of the present invention will be clearly and completely described below with reference to the accompanying drawings. Obviously, the described embodiments are only some embodiments of the present invention, and not all embodiments. Based on the embodiments of the present invention, all other embodiments obtained by those skilled in the art without creative effort are within the scope of protection of the present invention.

[0020] Please see Figures 1-3The present invention provides a wearable vest body 1, a base 2 and an intestinal tracking airbag assembly 3, wherein the base 2 is sewn or fixedly connected to the inner wall of the vest body 1 facing the human abdomen. The intestinal trajectory airbag assembly 3 is embedded in the pre-reserved installation groove of the base 2. The inner wall of the installation groove of the base 2 is provided with a guide brace. The brace follows the clockwise direction of the physiological trajectory of the human intestine and is set at an angle downward. Using the sturdy vest as the external force-bearing surface and the base mounting groove as the limiting groove, when the airbag is inflated, due to the downward-sloping guide brace at the bottom, the original vertical upward expansion force of the airbag is converted into a tangential thrust along the direction of intestinal peristalsis under the compression of the inclined surface.

[0021] The intestinal trajectory airbag group 3 contains a total of 8 independently operating airbag units, which divide the inner wall of the abdomen of the vest 1 into four consecutive mobilization zones from right to left, and each mobilization zone has 2 airbag units arranged in series along the intestinal direction; in terms of layout, the 8 airbags are distributed to the four key anatomical segments of the large intestine, and each segment is given the ability to inflate and deflate independently through 8 independent air inlet tubes. The four actuation zones are, in order: the first zone corresponding to the right ascending colon, the second zone corresponding to the transverse colon, the third zone corresponding to the left descending colon, and the fourth zone corresponding to the sigmoid colon at the lower left abdomen. Each airbag unit has an independent air inlet pipe sealed at its end, and each air inlet pipe is connected to multiple electronic valves in the electro-pneumatic assembly. The air source is provided by a unified air pump, and the airflow direction is controlled by multiple solenoid valves.

[0022] Preferably, the electro-pneumatic assembly includes an air pump, multiple electronic valves, a drive circuit, a processor, and a power supply. The air outlet of the air pump is connected in parallel with the air inlet of each electronic valve through a main air pipeline. The air outlet of each electronic valve is sealed and connected to the independent air inlet pipe corresponding to each airbag unit. The power supply is electrically connected to the processor, drive circuit, air pump and each electronic valve through the power management and voltage regulation module; the control signal output terminal of the processor is connected to the signal input terminal of the drive circuit, and the output terminal of the drive circuit is connected to the control terminal of the air pump and each electronic valve. The processor is configured to execute a stepped timing control algorithm comprising three stages: inflation, pressure holding, and deflation, to the drive circuit. This algorithm sequentially controls adjacent airbag units to perform these three stages, proceeding from the first region to the fourth region. When the upstream i-th airbag unit initiates its inflation stage and maintains it for a first preset time, then enters the pressure holding stage, the microprocessor controls the downstream (i+1)-th airbag unit to initiate its inflation stage. The deflation stage of the i-th airbag unit only begins after the (i+1)-th airbag unit has initiated its inflation stage and after a second preset time delay. This preset time delay ensures that the upstream airbag cannot deflate before the downstream airbag has inflated, creating a continuous, unidirectional biomimetic peristaltic wave on the abdominal surface, preventing gas from flowing back upstream during compression.

[0023] Preferably, it also includes a bowel sound monitoring feedback system, which includes multiple piezoelectric thin film sensors 4 and an ADC conversion chip. The analog signal input terminal of the ADC conversion chip is electrically connected to the signal output terminal of the piezoelectric thin film sensor, and the microprocessor is connected to the digital signal output terminal of the ADC conversion chip via an I2C or SPI communication bus. The number of piezoelectric thin film sensors 4 is at least four, which are distributed and fixedly installed on the surface of the base 2 facing the abdomen of the human body along the physiological and anatomical direction of the human colon.

[0024] Preferably, the piezoelectric thin film sensor 4 adopts a flexible silicone patch encapsulation structure.

[0025] Preferably, the microprocessor incorporates a closed-loop control algorithm for bowel sound monitoring and feedback. Within a set monitoring time window T, it acquires a discrete sequence of digital bowel sound signals x(n), where n = 1, 2, ..., N, and N is the total number of sampling points. The algorithm iteratively executes the following workflow: S1. Silent acquisition: Control the intestinal trajectory airbag group 3 to obtain a pure signal sequence x(n); S2. Feature extraction: Calculate the short-time energy E of the sound signal and the frequency R of bowel sounds within the listening window T; S3, State determination: Input the extracted parameters (E,R) into the preset physiological state determination model, and output the state identifier variable S_state by comparing it with the preset baseline threshold. S4. Dynamic Execution: Based on S_state, retrieve the matching airbag target inflation pressure P_target and control the airbag group to perform the corresponding physical massage action.

[0026] Preferably, in the feature extraction algorithm of step S2: The formula for calculating short-time energy E is: E=(1 / N)*Σx²(n) The microprocessor identifies valid bowel sound events through a preset amplitude threshold x_th. The calculation formula for the bowel sound occurrence frequency R is as follows: R=(1 / T)*Σδ(x(n)) Where, when |x(n)|>x_th and the duration meets the preset conditions, the pulse function δ(x(n)) = 1; otherwise, δ(x(n)) = 0. Using digital signal processing algorithms, the chaotic acoustic wave sequence x(n) is dimensionally reduced and extracted into two core mathematical features, loudness / intensity E and activity / frequency R.

[0027] Preferably, in steps S3 and S4, the determination conditions and execution logic for the "intestinal paralysis or insufficient motility" state are as follows: Set the energy baseline threshold for normal bowel sounds as E_base and the frequency baseline threshold as R_base; When the determination model conditions are met: E < a*E_base and R < b*R_base (where a and b are set proportionality coefficients, and 0 < a < 1, 0 < b < 1), the microprocessor outputs the status flag S_state = 1; At this time, the microprocessor executes the enhanced actuation mode: the target inflation pressure P_target output adopts the dynamic compensation formula: P_target = P0 + k_p*(R_base - R) Where, P0 is the basic massage pressure, and k_p is the pressure compensation coefficient, which makes the air pump output an enhanced extrusion force proportional to the degree of intestinal motility defect. It adopts a proportional control P logic similar to that in PID control. When it is detected that the intestine is in the "paralysis or dead silence" state, the deficit amount of the bowel sound frequency is calculated, multiplied by the compensation coefficient k_p, and superimposed on the basic pressure. The weaker the intestinal motility, the stronger the physical extrusion force output by the system, playing an external compensatory role.

[0028] Preferably, the safety protection model for the "intestinal spasm or hypersensitivity" state is as follows: When extremely high-frequency bowel sounds are monitored and the determination condition R > c*R_base is met (where c is the alarm coefficient, and c > 1.5), the microprocessor outputs the status flag S_state = 2; At this time, the safety avoidance mode is triggered: the microprocessor immediately forcibly sets the target inflation pressure P_target = 0, opens all electronic valves to release pressure, and locks the air pump control port until the frequency R returns to the normal baseline range. The system sets a safety threshold red line, that is, the frequency is extremely high, which is judged as a precursor to intestinal spasm or severe diarrhea. Once this red line is triggered, the system will directly open all electronic valves to release pressure through the highest-priority hardware interrupt to prevent continued external pressure from aggravating pain or even causing visceral damage when the patient has acute intestinal spasm.

[0029] Preferably, the piezoelectric thin film sensor 4 is model FDT1-028K, the ADC conversion chip is model ADS1115, the microprocessor is an ESP32 series microcontroller with a built-in wireless communication module, the driving circuit uses an AO3400 N-channel enhancement field-effect transistor to drive the micro air pump, a Darlington transistor array chip of model ULN2003A to drive multiple electronic valves, and the power management and voltage regulation module includes a boost power management chip of model IP5306 and a low dropout linear regulator of model ME6211.

[0030] Furthermore, any content not described in detail in this specification is existing technology known to those skilled in the art.

[0031] It should be noted that the above description and illustration of the basic principles, main features and advantages of the present invention are not limited to the above embodiments. The embodiments and descriptions in the specification are merely illustrative of the principles of the present invention. Various changes and modifications can be made to the present invention without departing from its spirit and scope. All such changes and modifications fall within the scope of the present invention as claimed. The scope of protection of the present invention is defined by the appended claims and their equivalents.

Claims

1. A wearable gas-promoting vest based on bowel sound characteristics, comprising a wearable vest body (1), a base (2) and an intestinal trajectory airbag group (3), wherein the base (2) is sewn or fixedly connected to the inner wall of the vest body (1) facing the abdomen of the human body; characterized in that The intestinal trajectory airbag group (3) is embedded in the mounting groove reserved in the base (2). The inner wall of the mounting groove of the base (2) is provided with a guide brace. The brace follows the clockwise direction of the human intestinal physiological trajectory and is inclined downward. The intestinal trajectory airbag group (3) contains a total of 8 independently operating airbag units, which divide the inner wall of the abdomen of the person wearing the vest (1) into four consecutive activation areas from right to left, and each activation area has 2 airbag units arranged in series along the intestinal direction. The four actuation zones are, in order: the first zone corresponding to the right ascending colon, the second zone corresponding to the transverse colon, the third zone corresponding to the left descending colon, and the fourth zone corresponding to the sigmoid colon at the end of the left lower abdomen. Each airbag unit is sealed at the end with an independent air inlet pipe, and each air inlet pipe is connected to multiple electronic valves in the electro-pneumatic assembly.

2. The wearable air-evacuating vest based on the characteristics of bowel sounds according to claim 1, characterized in that, The electro-pneumatic assembly includes an air pump, multiple electronic valves, a drive circuit, a processor, and a power supply. The air outlet of the air pump is connected in parallel to the air inlet of each electronic valve through a main air pipeline. The air outlet of each electronic valve is sealed and connected to an independent air inlet pipe corresponding to each airbag unit. The power supply is electrically connected to the processor, drive circuit, air pump and each electronic valve through a power management and voltage regulation module; the control signal output terminal of the processor is connected to the signal input terminal of the drive circuit, and the output terminal of the drive circuit is connected to the control terminal of the air pump and each electronic valve. The processor is configured to execute a stepped timing control algorithm comprising three stages: inflation, pressure holding, and deflation, to the drive circuit. The stepped timing control algorithm sequentially controls adjacent airbag units to perform the above three stages in the direction from the first region to the fourth region. When the i-th airbag unit located upstream starts the inflation stage and continues for a first preset time, and then enters the pressure holding stage, the microprocessor controls the (i+1)-th airbag unit located downstream to start the inflation stage. The deflation stage of the i-th airbag unit is only started after the (i+1)-th airbag unit starts the inflation stage and after a second preset time delay.

3. The wearable air-evacuating vest based on the characteristics of bowel sounds according to claim 2, characterized in that, It also includes a bowel sound monitoring feedback system, which includes multiple piezoelectric thin film sensors (4) and an ADC conversion chip. The analog signal input terminal of the ADC conversion chip is electrically connected to the signal output terminal of the piezoelectric thin film sensor. The microprocessor is connected to the digital signal output terminal of the ADC conversion chip via an I2C or SPI communication bus. The number of the piezoelectric thin film sensors (4) is at least four, which are distributed and fixedly installed on the surface of the base (2) facing the abdomen of the human body along the physiological and anatomical direction of the human colon.

4. A wearable gas-inducing vest based on bowel sound characteristics according to claim 3, characterized in that, The piezoelectric thin film sensor (4) adopts a flexible silicone patch encapsulation structure.

5. A wearable gas-inducing vest based on bowel sound characteristics according to claim 3, characterized in that, The microprocessor incorporates a closed-loop control algorithm for monitoring and feedback of bowel sounds. Within a set listening time window T, it collects a discrete digital signal sequence x(n) of bowel sounds, where n = 1, 2,..., N, and N is the total number of sampling points. The algorithm loops through the following workflow: S1. Silent acquisition: Control the intestinal tract trajectory airbag group (3) to obtain a pure signal sequence x(n). S2. Feature extraction: Calculate the short-time energy E and the bowel sound occurrence frequency R of the sound signal within the listening window T. S3. State determination: Input the extracted parameters (E, R) into a preset physiological state determination model. By comparing with the preset baseline threshold, output the state identification variable S_state. S4. Dynamic execution: According to S_state, retrieve the matching airbag target inflation pressure P_target and control the airbag group to perform the corresponding physical massage action.

6. A wearable gas-inducing vest based on bowel sound characteristics according to claim 5, characterized in that, In the feature extraction algorithm of step S2: The formula for calculating the short-time energy E is: E = (1 / N) * Σx²(n) The microprocessor identifies valid bowel sound events through a preset amplitude threshold x_th. The formula for calculating the bowel sound occurrence frequency R is: R = (1 / T) * Σδ(x(n)) Where, when |x(n)| > x_th and the duration meets the preset condition, the pulse function δ(x(n)) = 1; otherwise, δ(x(n)) = 0.

7. A wearable gas-inducing vest based on bowel sound characteristics according to claim 5, characterized in that, In steps S3 and S4, the determination conditions and execution logic for the "intestinal paralysis or hypomotility" state are: Set the energy baseline threshold for normal bowel sounds as E_base and the frequency baseline threshold as R_base. When the determination model condition is met: E < a * E_base and R < b * R_base (where a and b are set proportionality coefficients, and 0 < a < 1, 0 < b < 1), the microprocessor outputs the state identification S_state = 1. At this time, the microprocessor executes an enhanced activation mode: the output target inflation pressure P_target adopts a dynamic compensation formula: P_target = P0 + k_p * (R_base - R) Where, P0 is the basic massage pressure, and k_p is the pressure compensation coefficient, so that the air pump outputs an enhanced extrusion force proportional to the degree of intestinal motility deficiency.

8. A wearable gas-inducing vest based on bowel sound characteristics according to claim 5, characterized in that, The safety protection model for the "intestinal spasm or hypersensitivity" state is: When extremely high-frequency bowel sounds are detected and the determination condition R > c * R_base is met (where c is an alarm coefficient, and c > 1.5), the microprocessor outputs the state identification S_state = 2. At this time, trigger the safety avoidance mode: The microprocessor immediately forcibly sets the target inflation pressure P_target = 0, opens all electronic valves to relieve pressure, and locks the air pump control port until the frequency R returns to the normal baseline range.

9. A wearable gas-inducing vest based on bowel sound characteristics according to claim 5, characterized in that, The piezoelectric thin film sensor (4) is model FDT1-028K, the ADC conversion chip is model ADS1115, the microprocessor is an ESP32 series microcontroller with a built-in wireless communication module, the driving circuit uses an AO3400 N-channel enhancement field-effect transistor to drive the micro air pump, and a Darlington array chip with model ULN2003A to drive the multiple electronic valves. The power management and voltage regulation module includes a boost power management chip with model IP5306 and a low dropout linear regulator with model ME6211.

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