Intelligent wound exudate monitoring and nursing response equipment for general surgery department

Abstract

The invention discloses a general surgery department wound exudate intelligent monitoring and nursing response device, and relates to the general surgery department wound exudate monitoring field, the general surgery department wound exudate intelligent monitoring and nursing response device comprises a bionic contact mechanism, a monitoring mechanism and a response mechanism which are sequentially laminated and connected, the bionic contact mechanism is directly attached to a wound, and is used for collecting wound exudate and conducting the wound exudate to the monitoring mechanism; meanwhile, the nursing medium output by the response mechanism is received; a multi-channel detection assembly is arranged in the monitoring mechanism and is used for detecting the pH value, protease activity and bacterial markers of seepage in real time; and the response mechanism is provided with a medicament storage unit, a gas supply unit and a power driving unit, and is used for outputting corresponding nursing response according to a detection result of the monitoring mechanism. Through the linkage design of the monitoring mechanism and the response mechanism, medicament delivery or gas nursing is automatically triggered according to a detection result, integrated closed-loop management of monitoring and response is achieved, the wound healing requirement is accurately matched, the infection risk is effectively reduced, and the healing period is shortened.

Description

Technical Field

[0001] This invention belongs to the field of general surgical wound exudation monitoring, specifically a general surgical wound exudation intelligent monitoring and nursing response device. Background Technology

[0002] With the aging population and the increasing incidence of chronic diseases, the management of acute and chronic wounds has become a global medical challenge. The healing process of wounds such as postoperative wounds in general surgery, pressure ulcers, and diabetic foot ulcers is complex. One of the core aspects is the effective management of wound exudate. Wound exudate is a "treasure trove of information" reflecting the state of the wound microenvironment. The dynamic changes in its components (such as pH value, specific protease activity, inflammatory markers, bacterial load, etc.) directly indicate whether the wound is in the healing, inflammatory, or infectious stage.

[0003] Currently, clinical monitoring and management of wound exudate mainly rely on traditional dressings and intermittent clinical observation, which has significant lag and subjectivity. Specifically, traditional absorbent dressings can only passively absorb exudate and keep the wound moist. They do not have any monitoring function. Medical staff cannot obtain any objective, real-time data about the wound condition through dressings. When changing dressings, they rely on visual observation and subjective experience to judge the wound condition, which can easily lead to misjudgment and missing the best intervention opportunity. Summary of the Invention

[0004] The purpose of this invention is to provide an intelligent monitoring and nursing response device for general surgical wound exudation, so as to solve the problems of existing intelligent monitoring and nursing response devices for general surgical wound exudation.

[0005] To achieve the above objectives, the present invention provides the following technical solution: an intelligent monitoring and nursing response device for general surgical wound exudate, comprising a biomimetic contact mechanism, a monitoring mechanism, and a response mechanism connected in sequence. The biomimetic contact mechanism is directly attached to the wound to collect wound exudate and conduct it to the monitoring mechanism, while simultaneously receiving nursing media output by the response mechanism. The monitoring mechanism has a built-in multi-channel detection component for real-time detection of the pH value, protease activity, and bacterial markers of the exudate. The response mechanism is equipped with a drug storage, gas supply, and power drive unit to output a corresponding nursing response based on the detection results of the monitoring mechanism.

[0006] Preferably, the biomimetic contact mechanism includes a biomimetic contact layer, medical pressure-sensitive adhesive, a filter, a drug inlet tube, a gas inlet tube, and a flow channel. The flow channel is formed within the biomimetic contact layer. The surface of the biomimetic contact layer has conical micropores that penetrate the biomimetic contact layer. The end of the conical micropore near the patient's wound is a small end, and the end away from the wound is a large end. The bottom surface of the biomimetic contact layer has a micro-nano prismatic structure. The medical pressure-sensitive adhesive is disposed at the bottom edge of the biomimetic contact layer and is used to adhere to the patient's intact skin. The filter is embedded in the top of the biomimetic contact layer. The flow channel is formed inside the biomimetic contact layer. The drug inlet tube and the gas inlet tube penetrate the biomimetic contact layer and communicate with the flow channel. The biomimetic contact layer has perforations corresponding to the flow channel positions.

[0007] Preferably, the monitoring mechanism includes a microfluidic dispensing component, a permanent silicone adhesive layer, a pH detection component, a protease detection component, a bacterial marker detection component, a PCB circuit board, fixing bolts, and a waste liquid collection tank. The microfluidic dispensing component is bonded to the biomimetic contact layer, the pH detection component, the protease detection component, and the bacterial marker detection component through the permanent silicone adhesive layer. The PCB circuit board is connected to the pH detection component and the protease detection component through the fixing bolts. Each detection component is connected to the waste liquid collection tank through a waste liquid discharge tank.

[0008] Preferably, the microchannel distribution assembly includes a microchannel distribution substrate, a main collection channel, a capillary pump valve, and multiple branch channels. The main collection channel is located in the middle of the microchannel distribution substrate, the capillary pump valve is located at the input end of the main collection channel, and the branch channels include a first channel, a second channel, and a third channel, which respectively connect to the pH detection channel orifice, the protease detection channel orifice, and the bacterial marker detection channel orifice.

[0009] Preferably, the pH detection component includes a pH detection chamber, a pH-sensitive hydrogel, an encapsulated detection sheet, a first mounting groove, and a first micro negative pressure pump. The pH detection chamber contains a pH detection slot, and the pH-sensitive hydrogel, containing bromothymol blue, is filled within the slot. The encapsulated detection sheet contains an RGB LED and a phototransistor. The first mounting groove is located on the side of the PCB circuit board near the pH detection component, corresponding to the position of the pH detection slot. The encapsulated detection sheet is embedded in the first mounting groove and at the bottom of the pH detection slot. The first micro negative pressure pump is mounted on the upper surface of the PCB circuit board and communicates with the pH detection chamber. A first liquid inlet is located at the bottom of the pH detection slot and communicates with the pH detection flow channel. The RGB LED in the encapsulated detection sheet emits light of a specific wavelength, which penetrates the pH-sensitive hydrogel. The phototransistor detects the intensity of the transmitted light. The hydrogel swells differently at different pH levels, resulting in changes in color and transparency, which in turn causes changes in the photoelectric signal, thereby detecting the pH value of the exudate.

[0010] Preferably, the protease detection component includes a protease detection chamber, a peptide substrate, a micro three-electrode system, a second mounting groove, and a second micro negative pressure pump. The protease detection chamber contains a protease detection cell. The peptide substrate is laid at the bottom of the protease detection cell. The second mounting groove is located on the side of the PCB circuit board near the protease detection component and corresponds to the position of the protease detection cell. The micro three-electrode system is installed inside the protease detection cell. The second micro negative pressure pump is installed on the upper surface of the PCB circuit board and is connected to the protease detection cell. A second liquid inlet is provided at the bottom of the protease detection cell and is connected to the protease detection channel. The peptide substrate is a gold working electrode, and its surface is modified with a specific peptide substrate. The peptide substrate can be flexibly selected according to the type of protease to be detected. The micro three-electrode system includes a gold working electrode, a platinum counter electrode, and an Ag / AgCl reference electrode. When the peptide substrate is cleaved by the protease, the surface characteristics of the electrode change, resulting in a change in the solution impedance. The protease activity is quantified by measuring the impedance value.

[0011] Preferably, the bacterial marker detection component includes a bacterial marker detection chamber, a fluorescent silicone microbead plate, a blue LED light column, a third mounting groove, a third micro negative pressure pump, and a photodiode. The bacterial marker detection chamber contains a bacterial marker detection slot, the fluorescent silicone microbead plate is placed inside the bacterial marker detection slot, the blue LED light column is installed inside the bacterial marker detection slot, the third mounting groove is located on the side of the PCB circuit board near the bacterial marker detection component, and the third mounting groove corresponds to the position of the bacterial marker detection slot. The photodiode is installed at the top of the third mounting groove, the third micro negative pressure pump is installed on the upper surface of the PCB circuit board, and the third micro negative pressure pump is connected to the bacterial marker detection slot. A third liquid inlet is located at the bottom of the bacterial marker detection slot, and the third liquid inlet is connected to the bacterial marker detection flow channel. The blue LED is used to excite the fluorescent aptamer in the fluorescent silicone microbeads. When the aptamer binds to the target bacteria, its conformation changes, and the fluorescence intensity increases or decreases. The fluorescence signal intensity detected by the photodiode is related to the bacterial concentration.

[0012] Preferably, the response mechanism includes a top plate, a protective plate, a medicine tank, a micro piezoelectric peristaltic pump, a micro gas cylinder, a micro air pump, and connecting pipes. The protective plate is fixed below the top plate, and the medicine tank and the micro gas cylinder are both installed on the top of the top plate. The micro piezoelectric peristaltic pump is connected to the medicine tank and the drug inlet pipe of the bionic contact mechanism through a first connecting pipe. The micro air pump is connected to the micro gas cylinder and the gas inlet pipe of the bionic contact mechanism through a second connecting pipe. The protective plate has a groove on its surface for the micro negative pressure pump to exhaust gas.

[0013] Preferably, the PCB circuit board integrates a data processing module and a wireless transmission module, which can receive the detection signals from each detection component and convert them into digital data, and then send them to an external terminal through the wireless transmission module.

[0014] Preferably, the biomimetic contact layer is made of medical-grade polyurethane, and the surface is treated with plasma and then impregnated with perfluoropolyether lubricant. The biomimetic contact layer, through its lubricating surface that mimics the structure of a pitcher plant, prevents newly formed granulation tissue from attaching effectively. The diameter of the conical micropores is 50-100 μm, and the spacing between adjacent micropores is 200-300 μm.

[0015] Compared with the prior art, the present invention has the following beneficial effects:

[0016] 1. This invention utilizes a biomimetic contact mechanism with a pitcher plant-like lubricating surface design, combined with a conical microporous structure, to achieve efficient collection of wound exudate while avoiding replacement damage caused by the attachment of new granulation tissue. At the same time, the medical-grade polyurethane material has good skin compatibility, improving safety and comfort during use.

[0017] 2. This invention enables real-time quantitative detection of exudate pH, protease activity, and bacterial markers through the collaborative operation of multi-channel detection components in the monitoring mechanism. The data is processed by the PCB circuit board and wirelessly transmitted to an external terminal, solving the problems of traditional nursing relying on subjective judgment and data lag.

[0018] 3. This invention, through the linkage design of the monitoring and response mechanisms, automatically triggers drug delivery or gas care based on the detection results, realizing integrated closed-loop management of monitoring and response, accurately matching wound healing needs, effectively reducing the risk of infection, and shortening the healing cycle. Attached Figure Description

[0019] To more clearly illustrate the technical solutions in the embodiments of this application or the prior art, the drawings used in the embodiments will be briefly introduced below. Obviously, the drawings described below are only some embodiments recorded in this invention. For those skilled in the art, other drawings can be obtained based on these drawings.

[0020] Figure 1 This is a schematic diagram of the overall structure of the present invention;

[0021] Figure 2 This is an exploded view of the overall structure of the present invention;

[0022] Figure 3 This is a schematic diagram of the biomimetic contact mechanism in this invention;

[0023] Figure 4 This is a structural breakdown diagram of the monitoring mechanism in this invention. Figure 1 ;

[0024] Figure 5 This is a structural breakdown diagram of the monitoring mechanism in this invention. Figure 2 ;

[0025] Figure 6 This is a cross-sectional view of the microchannel distribution component in this invention.

[0026] In the picture:

[0027] 1. Bionic contact mechanism; 101. Bionic contact layer; 102. Medical pressure-sensitive adhesive; 103. Filter screen; 104. Drug inlet tube; 105. Gas inlet tube; 106. Conical micropore; 107. Flow channel; 108. Perforation; 2. Monitoring mechanism; 201. Microchannel distribution assembly; 2011. Microchannel distribution substrate; 2012. Main collection flow channel; 2013. Capillary pump valve; 2014. First flow channel; 2015. Second flow channel; 2016. Third flow channel; 2017, pH detection channel orifice; 2018, protease detection channel orifice; 2019, bacterial marker detection channel orifice; 202, permanent silicone adhesive layer; 203, pH detection component; 2031, pH detection chamber; 2032, pH detection reservoir; 2033, pH-sensitive hydrogel; 2034, first liquid inlet orifice; 2035, first mounting groove; 2036, encapsulated detection sheet; 2037, first micro negative pressure pump; 204, protease detection component; 2 041. Protease detection chamber; 2042. Protease detection tank; 2043. Peptide chain base plate; 2044. Second liquid inlet; 2045. Miniature three-electrode system; 2046. Second mounting groove; 2047. Second miniature negative pressure pump; 205. Bacterial marker detection assembly; 2051. Bacterial marker detection chamber; 2052. Bacterial marker detection tank; 2053. Fluorescent silica microbead plate; 2054. Blue LED light column; 2055. Third liquid inlet; 2 056. Third mounting groove; 2057. Photodiode; 2058. Third micro negative pressure pump; 206. PCB circuit board; 207. Fixing bolt; 208. Waste liquid discharge tank; 209. Waste liquid collection tank; 3. Response mechanism; 301. Top plate; 302. Protective plate; 303. Through groove; 304. Agent tank; 305. Micro piezoelectric peristaltic pump; 306. First connecting pipe; 307. Micro gas tank; 308. Micro air pump; 309. Second connecting pipe. Detailed Implementation

[0028] To enable those skilled in the art to better understand the technical solution of the present invention, the present invention will be further described in detail below with reference to the accompanying drawings.

[0029] As attached Figure 1 To be continued Figure 6 As shown:

[0030] Example 1: This invention provides an intelligent monitoring and nursing response device for general surgical wound exudate, comprising a biomimetic contact mechanism 1, a monitoring mechanism 2, and a response mechanism 3 connected in sequence. The biomimetic contact mechanism 1 is in direct contact with the wound to collect wound exudate and conduct it to the monitoring mechanism 2, while simultaneously receiving nursing media output by the response mechanism 3. The monitoring mechanism 2 has a built-in multi-channel detection component for real-time detection of the pH value, protease activity, and bacterial markers of the exudate. The response mechanism 3 is equipped with a drug storage, gas supply, and power drive unit to output a corresponding nursing response based on the detection results of the monitoring mechanism 2.

[0031] In one embodiment of the present invention, the biomimetic contact mechanism 1 includes a biomimetic contact layer 101, medical pressure-sensitive adhesive 102, a filter screen 103, a drug inlet tube 104, a gas inlet tube 105, and a flow channel 107. The flow channel 107 is formed within the biomimetic contact layer 101. A tapered micropore 106 is formed on the surface of the biomimetic contact layer 101, penetrating the biomimetic contact layer 101. The end of the tapered micropore 106 near the patient's wound is a small end, and the end away from the wound is a large end. The bottom surface of the biomimetic contact layer 101 has a micro-nano prismatic structure. The medical pressure-sensitive adhesive 102 is disposed at the bottom edge of the biomimetic contact layer 101 and is used to adhere to the patient's wound. The bionic contact layer 101 is a complete human skin. A filter 103 is embedded in the top of the bionic contact layer 101. A flow channel 107 is opened inside the bionic contact layer 101. A drug inlet tube 104 and a gas inlet tube 105 pass through the bionic contact layer 101 and are connected to the flow channel 107. A perforation 108 is opened in the bionic contact layer 101 corresponding to the position of the flow channel 107. The bionic contact layer 101 is made of medical-grade polyurethane. The surface is treated with plasma and then wetted with perfluoropolyether lubricant. The bionic contact layer 101, through the lubricating surface of the pitcher plant structure, prevents the effective adhesion of newly formed granulation tissue. The diameter of the conical micropores 106 is 50-100μm, and the spacing between adjacent micropores is 200-300μm.

[0032] During operation, the staff first cleans the skin around the patient's wound and removes the protective film of the medical pressure-sensitive adhesive 102. The micro-nano prismatic structure of the biomimetic contact layer 101 is then positioned facing the wound, ensuring that the conical micropores 106 fully cover the wound surface. The edges are gently pressed to ensure a tight fit between the medical pressure-sensitive adhesive 102 and the skin. After the device is powered on, the capillary pump valve 2013 activates, generating negative pressure. Wound exudate flows through the conical micropores 106 and the filter screen 103 into the flow channel 107, and is then transmitted through the perforation 108 to the main collection flow channel 2012 of the monitoring mechanism 2. The exudate is then diverted through the microchannel distribution component 201 to three detection flow channel holes, each entering its corresponding detection component. Each detection component synchronously acquires signals and transmits them to the PCB circuit board. The circuit board compares the detection data with the preset threshold. If the data is abnormal, the response mechanism 3 is triggered, and the nursing medium is output through the drug inlet tube 104 or the gas inlet tube 105. The detection data is sent to the external terminal in real time, and the waste liquid flows into the waste liquid collection box 209 through the waste liquid discharge tank 208. Through this process, real-time monitoring of wound exudate and precise nursing response are achieved, reducing manual intervention and improving nursing efficiency.

[0033] In one embodiment of the present invention, the monitoring mechanism 2 includes a microfluidic dispensing component 201, a permanent silicone adhesive layer 202, a pH detection component 203, a protease detection component 204, a bacterial marker detection component 205, a PCB circuit board 206, fixing bolts 207, and a waste liquid collection tank 209. The microfluidic dispensing component 201 is bonded to the biomimetic contact layer 101, the pH detection component 203, the protease detection component 204, and the bacterial marker detection component 205 through the permanent silicone adhesive layer 202. The PCB circuit board 206 is connected to the pH detection component 203 and the protease detection component 204 through the fixing bolts 207. Each detection component is connected to the waste liquid collection tank 209 through a waste liquid discharge tank 208. The PCB circuit board 206 integrates a data processing module and a wireless transmission module, which can receive the detection signals of each detection component and convert them into digital data, and send them to an external terminal through the wireless transmission module.

[0034] During operation, the staff first fixes the PCB circuit board to each detection component using fixing bolts 207 to ensure stable circuit connection. After the exudate flows out from the perforation 108 of the bionic contact mechanism 1, it enters the main collection channel 2012 of the microfluidic distribution component 201, and is diverted to each branch channel 107 under the action of capillary pump valve 2013. After each detection component completes the detection, the waste liquid flows into the waste liquid collection tank 209 through the waste liquid discharge tank 208. The PCB circuit board receives the electrical signals from each detection component, which are converted into pH value, protease activity value and bacterial concentration data by the data processing module, and sent to the nurse station terminal or medical staff's mobile APP through the wireless transmission module. Through this structure, the real-time transmission and centralized management of detection data can be realized, and medical staff can remotely monitor the wound status.

[0035] In one embodiment of the present invention, the microchannel distribution component 201 includes a microchannel distribution substrate 2011, a main collection channel 2012, a capillary pump valve 2013, and a plurality of branch channels. The main collection channel 2012 is formed in the middle of the microchannel distribution substrate 2011, the capillary pump valve 2013 is disposed at the input end of the main collection channel 2012, and the branch channels include a first channel 2014, a second channel 2015, and a third channel 2016, which are respectively connected to the pH detection channel hole 2017, the protease detection channel hole 2018, and the bacterial marker detection channel hole 2019.

[0036] During operation, the capillary pump valve 2013 first activates to generate negative pressure, drawing the permeate transmitted by the bionic contact mechanism 1 into the main collection channel 2012. The permeate flows at a uniform speed within the main collection channel 2012. Upon reaching the interface of the branch channel 107, it is evenly distributed to the first channel 2014, the second channel 2015, and the third channel 2016 under capillary action. The inner diameter of each branch channel 107 is uniformly 120μm, ensuring that the flow rate of each permeate stream is stable at 5μL / min, and accurately delivered to the corresponding detection channel 107 orifice. Through this design, uniform distribution of the permeate is achieved, ensuring the accuracy of the detection results of each detection component.

[0037] In one embodiment of the present invention, the pH detection component 203 includes a pH detection chamber 2031, a pH-sensitive hydrogel 2033, an encapsulated detection sheet 2036, a first mounting groove 2035, and a first micro negative pressure pump 2037. The pH detection chamber 2031 has a pH detection slot 2032 inside, and the pH-sensitive hydrogel 2033, containing bromothymol blue, fills the pH detection slot 2032. The encapsulated detection sheet 2036 contains an RGB LED and a phototransistor. The first mounting groove 2035 is formed on the side of the PCB circuit board 206 near the pH detection component 203, and its position corresponds to that of the pH detection slot 2032. The encapsulated detection chip 2036 is embedded in the first mounting groove 2035 and the bottom of the pH detection tank 2032. The first micro negative pressure pump 2037 is mounted on the upper surface of the PCB circuit board 206 and is connected to the pH detection chamber 2031. The bottom of the pH detection tank 2032 is provided with a first liquid inlet hole 2034, which is connected to the pH detection flow channel hole 2017. The RGB LED in the encapsulated detection chip 2036 emits light of a specific wavelength, which penetrates the pH-sensitive hydrogel 2033. The phototransistor detects the intensity of the transmitted light. The hydrogel has different swelling degrees at different pH levels, and its color and transparency change, resulting in changes in the photoelectric signal, thereby detecting the pH value of the exudate.

[0038] During operation, the first micro-vacuum pump 2037 is activated, drawing the exudate delivered through the first flow channel 2014 into the pH detection tank via the first inlet hole 2034. The exudate comes into full contact with the pH-sensitive hydrogel containing bromothymol blue. The RGB LED within the encapsulated detection chip 2036 emits light with a wavelength of 450-650nm, which penetrates the hydrogel and is received by the phototransistor. When the pH value of the exudate changes within the range of 6.0-9.0, the hydrogel color gradually changes from yellow to blue, and the swelling degree changes synchronously, resulting in a change in the intensity of transmitted light. The phototransistor converts the light signal into an electrical signal. The electrical signal is transmitted to the PCB circuit board, calibrated, and outputs a precise pH value (accuracy ±0.1pH). Through this process, real-time quantitative detection of the exudate pH value is achieved.

[0039] In one embodiment of the present invention, the protease detection component 204 includes a protease detection chamber 2041, a peptide chain base plate 2043, a micro three-electrode system 2045, a second mounting groove 2046, and a second micro negative pressure pump. The protease detection chamber 2041 contains a protease detection slot 2042. The peptide chain base plate 2043 is laid on the bottom of the protease detection slot 2042. The second mounting groove 2046 is formed on the side of the PCB circuit board 206 near the protease detection component 204, and its position corresponds to that of the protease detection slot 2042. The micro three-electrode system 2045 is installed inside the protease detection slot 2042. The second micro negative pressure pump... The pump is mounted on the upper surface of the PCB circuit board 206. The second micro negative pressure pump is connected to the protease detection tank 2042. The bottom of the protease detection tank 2042 is provided with a second liquid inlet 2044, which is connected to the protease detection flow channel 2018. The peptide chain substrate 2043 is a gold working electrode, which is made by modifying the surface with a specific peptide chain substrate. The peptide chain substrate can be flexibly selected according to the type of protease to be detected. The micro three-electrode system 2045 includes a gold working electrode, a platinum counter electrode, and an Ag / AgCl reference electrode. When the peptide chain substrate is cleaved by the protease, the surface characteristics of the electrode change, resulting in a change in the solution impedance. The protease activity is quantified by measuring the impedance value.

[0040] During operation, the second micro negative pressure pump is first activated, drawing the permeate delivered through the second flow channel 2015 into the protease detection tank 2042 through the second inlet hole 2044. The protease in the permeate binds to and cleaves the specific peptide substrate on the surface of the peptide substrate plate 2043, causing a change in the hydrophilicity or hydrophobicity of the gold working electrode surface. A 5mV AC signal is applied to the micro three-electrode system 2045 to measure the impedance change between the electrodes. The impedance value is linearly correlated with the protease activity. The PCB circuit board converts the impedance signal into a protease activity value (detection limit 1ng / mL) according to a preset calibration curve. This design can flexibly adapt to the detection requirements of various proteases such as matrix metalloproteinases and elastases.

[0041] In one embodiment of the present invention, the bacterial marker detection component 205 includes a bacterial marker detection chamber 2051, a fluorescent silicone microbead plate 2053, a blue LED light column 2054, a third mounting groove 2056, a third micro negative pressure pump 2058, and a photodiode 2057. The bacterial marker detection chamber 2051 has a bacterial marker detection slot 2052. The fluorescent silicone microbead plate 2053 is placed inside the bacterial marker detection slot 2052. The blue LED light column 2054 is installed inside the bacterial marker detection slot 2052. The third mounting groove 2056 is formed on the side of the PCB circuit board 206 near the bacterial marker detection component 2055. The position of 56 corresponds to that of the bacterial marker detection groove 2052. The photodiode 2057 is installed on the top of the third mounting groove 2056. The third micro negative pressure pump 2058 is installed on the upper surface of the PCB circuit board 206 and is connected to the bacterial marker detection groove 2052. The bottom of the bacterial marker detection groove 2052 is provided with a third liquid inlet 2055, which is connected to the bacterial marker detection flow channel hole 2019. The blue LED is used to excite the fluorescent aptamer in the fluorescent silicone microbeads. When the aptamer binds to the target bacteria, its conformation changes, and the fluorescence intensity increases or decreases. The fluorescence signal intensity detected by the photodiode is related to the bacterial concentration.

[0042] During operation, the third micro negative pressure pump 2058 is activated first, drawing the exudate transported through the third flow channel 2016 into the bacterial marker detection tank 2052 through the third inlet port 2055. The exudate comes into full contact with the fluorescent silica microbead plate 2053. A blue LED column emits 488nm excitation light, illuminating the fluorescent aptamers in the fluorescent silica microbeads. If the target bacterial marker is present in the exudate, the aptamer specifically binds to it and undergoes a conformational change, resulting in a significant increase in fluorescence intensity (≥50%). The photodiode 2057 receives the fluorescence signal and converts it into an electrical signal. The PCB circuit board calculates the bacterial concentration based on the signal intensity (detection range 10²-10⁻¹⁰). 6 (CFU / mL). This structure enables rapid detection of common pathogenic bacteria such as Staphylococcus aureus and Escherichia coli.

[0043] Working principle: The staff first cleans the patient's wound and surrounding skin, then applies the bionic contact layer 101 of the bionic contact mechanism 1 to the wound surface and fixes it with medical pressure-sensitive adhesive 102, ensuring that the conical micropores 106 fully cover the wound. The equipment power is turned on, and after the PCB circuit board initializes, the micro negative pressure pumps and capillary pump valves 2013 are activated. Wound exudate flows through the conical micropores 106, filter screen 103, flow channel 107, and perforation 108 into the main collection channel 2012 of the monitoring mechanism 2. Under the action of the capillary pump valve 2013, it is diverted to three branch channels 107, entering the pH detection tank, protease detection tank 2042, and bacterial marker detection tank 2052 respectively. The pH detection component collects detection signals synchronously through hydrogel color changes, the protease detection component 204 through electrode impedance changes, and the bacterial marker detection component 205 through fluorescence signal changes, and transmits these signals to the PCB circuit board. The PCB circuit board converts the analog signals into digital data and compares them with a preset threshold (pH value). The values ​​are compared (7.0-8.0, protease activity <5ng / mL, bacterial concentration <10³CFU / mL); if the data is normal, the device remains in standby mode, continuously monitoring and uploading data periodically; if the data is abnormal, the response mechanism 3 is immediately triggered, the micro piezoelectric peristaltic pump 305 starts to deliver the corresponding agent (such as pH buffer, antibacterial drug), or the micro air pump 308 starts to deliver sterile oxygen; the waste liquid after testing flows into the waste liquid collection tank 209 through the waste liquid discharge tank 208, and medical staff can replace the waste liquid collection tank 209 and the biomimetic contact layer 101 regularly.

[0044] Example 2: This example is basically the same as the previous example, except that the response mechanism 3 includes a top plate 301, a protective plate 302, a medicine tank 304, a micro piezoelectric peristaltic pump 305, a micro gas tank 307, a micro air pump 308, and connecting pipes. The protective plate 302 is fixed below the top plate 301. The medicine tank 304 and the micro gas tank 307 are both installed on the top of the top plate 301. The micro piezoelectric peristaltic pump 305 is connected to the medicine tank 304 and the drug inlet pipe 104 of the bionic contact mechanism 1 through the first connecting pipe 306. The micro air pump 308 is connected to the micro gas tank 307 and the gas inlet pipe 105 of the bionic contact mechanism 1 through the second connecting pipe 309. The protective plate 302 has a through groove 303 for the micro negative pressure pump to exhaust gas.

[0045] Working principle: First, the PCB circuit board sends a control signal based on the detection results of the monitoring mechanism 2: If the pH value is lower than 7.0, the micro piezoelectric peristaltic pump 305 starts, delivering the alkaline buffer solution in the medicine tank 304 through the first connecting pipe 306 and the drug inlet pipe 104 to the flow channel 107 of the biomimetic contact layer 101, and acting on the wound through the conical micropores 106 to adjust the pH value of the wound surface; if bacterial markers are detected, the micro air pump 308 starts, delivering sterile oxygen in the micro air tank 307 through the second connecting pipe 309 and the gas inlet pipe 105 to the flow channel 107 to increase the oxygen concentration of the wound surface and inhibit the reproduction of anaerobic bacteria; if the protease activity exceeds the standard, the micro piezoelectric peristaltic pump 305 and the micro air pump 308 are started simultaneously to deliver protease inhibitors and oxygen, synergistically promoting wound healing; the protective plate 302 provides dustproof and collision protection for the internal components, and the through slot 303 ensures normal exhaust of the micro negative pressure pump.

[0046] The foregoing has only described certain exemplary embodiments of the present invention by way of illustration. Undoubtedly, those skilled in the art can modify the described embodiments in various ways without departing from the spirit and scope of the present invention. Therefore, the foregoing drawings and descriptions are illustrative in nature and should not be construed as limiting the scope of protection of the claims of the present invention.

Claims

1. A smart monitoring and nursing response device for general surgical wound exudation, characterized in that: The device includes a bionic contact mechanism (1), a monitoring mechanism (2), and a response mechanism (3) that are connected in sequence. The bionic contact mechanism (1) is in direct contact with the wound and is used to collect wound exudate and conduct it to the monitoring mechanism (2), while receiving the nursing medium output by the response mechanism (3). The monitoring mechanism (2) has a built-in multi-channel detection component for real-time detection of the pH value, protease activity, and bacterial markers of the exudate. The response mechanism (3) is equipped with a drug storage, gas supply, and power drive unit, and is used to output the corresponding nursing response based on the detection results of the monitoring mechanism (2).

2. The intelligent monitoring and nursing response device for general surgical wound exudation according to claim 1, characterized in that: The biomimetic contact mechanism (1) includes a biomimetic contact layer (101), medical pressure-sensitive adhesive (102), a filter (103), a drug inlet tube (104), a gas inlet tube (105), and a flow channel (107). The flow channel (107) is formed within the biomimetic contact layer (101). The surface of the biomimetic contact layer (101) has conical micropores (106) that penetrate the biomimetic contact layer (101). The end of the conical micropore (106) closer to the patient's wound is a small end, and the end farther from the wound is a large end. The biomimetic contact layer (101) The bottom surface has a micro-nano prismatic structure. The medical pressure-sensitive adhesive (102) is disposed at the bottom edge of the bionic contact layer (101). The medical pressure-sensitive adhesive (102) is used to adhere to the patient's intact skin. The filter (103) is embedded in the top of the bionic contact layer (101). The flow channel (107) is opened inside the bionic contact layer (101). The drug inlet tube (104) and the gas inlet tube (105) respectively penetrate the bionic contact layer (101) and are connected to the flow channel (107). The bionic contact layer (101) has perforations (108) at the positions corresponding to the flow channel (107).

3. The intelligent monitoring and nursing response device for general surgical wound exudation according to claim 1, characterized in that: The monitoring mechanism (2) includes a microfluidic dispensing component (201), a permanent silicone adhesive layer (202), a pH detection component (203), a protease detection component (204), a bacterial marker detection component (205), a PCB circuit board (206), fixing bolts (207), and a waste liquid collection tank (209). The microfluidic dispensing component (201) is bonded to the biomimetic contact layer (101), the pH detection component (203), the protease detection component (204), and the bacterial marker detection component (205) through the permanent silicone adhesive layer (202). The PCB circuit board (206) is connected to the pH detection component (203) and the protease detection component (204) through the fixing bolts (207). Each detection component is connected to the waste liquid collection tank (209) through a waste liquid discharge tank (208).

4. The intelligent monitoring and nursing response device for general surgical wound exudation according to claim 3, characterized in that: The microchannel distribution assembly (201) includes a microchannel distribution substrate (2011), a main collection channel (2012), a capillary pump valve (2013), and multiple branch channels. The main collection channel (2012) is located in the middle of the microchannel distribution substrate (2011). The capillary pump valve (2013) is located at the input end of the main collection channel (2012). The branch channels include a first channel (2014), a second channel (2015), and a third channel (2016), which respectively connect to the pH detection channel orifice (2017), the protease detection channel orifice (2018), and the bacterial marker detection channel orifice (2019).

5. The intelligent monitoring and nursing response device for general surgical wound exudation according to claim 3, characterized in that: The pH detection component (203) includes a pH detection chamber (2031), a pH-sensitive hydrogel (2033), an encapsulation detection sheet (2036), a first mounting groove (2035), and a first micro negative pressure pump (2037). The pH detection chamber (2031) has a pH detection slot (2032) inside, and the pH-sensitive hydrogel (2033) fills the pH detection slot (2032). The pH-sensitive hydrogel (2033) contains bromothymol blue. The encapsulation detection sheet (2036) contains an RGB LED and a phototransistor. The first mounting groove (2035) is located on the side of the PCB circuit board (206) near the pH detection component (203), and its position corresponds to that of the pH detection slot (2032). The encapsulated detection chip (2036) is embedded in the first mounting groove (2035) and the bottom of the pH detection tank (2032). The first micro negative pressure pump (2037) is mounted on the upper surface of the PCB circuit board (206). The first micro negative pressure pump (2037) is connected to the pH detection chamber (2031). The bottom of the pH detection tank (2032) is provided with a first liquid inlet hole (2034). The first liquid inlet hole (2034) is connected to the pH detection flow channel hole (2017). The RGB LED in the encapsulated detection chip (2036) emits light of a specific wavelength, which penetrates the pH sensitive hydrogel (2033). The phototransistor detects the intensity of the transmitted light. The hydrogel has different swelling degrees at different pH levels, and its color and transparency change, resulting in changes in the photoelectric signal, thereby detecting the pH value of the exudate.

6. The intelligent monitoring and nursing response device for general surgical wound exudation according to claim 3, characterized in that: The protease detection assembly (204) includes a protease detection chamber (2041), a peptide chain base plate (2043), a micro three-electrode system (2045), a second mounting groove (2046), and a second micro negative pressure pump (2047). The protease detection chamber (2041) contains a protease detection slot (2042). The peptide chain base plate (2043) is laid at the bottom of the protease detection slot (2042). The second mounting groove (2046) is located on the side of the PCB circuit board (206) near the protease detection assembly (2044), and its position corresponds to that of the protease detection slot (2042). The micro three-electrode system (2045) is installed inside the protease detection slot (2042). The second micro negative pressure pump (2047)... The pressure pump (2047) is installed on the upper surface of the PCB circuit board (206). The second micro negative pressure pump (2047) is connected to the protease detection tank (2042). The bottom of the protease detection tank (2042) is provided with a second liquid inlet (2044), which is connected to the protease detection flow channel (2018). The peptide chain substrate (2043) is a gold working electrode, which is made by modifying the surface with a specific peptide chain substrate. The peptide chain substrate can be flexibly selected according to the type of protease to be detected. The micro three-electrode system (2045) includes a gold working electrode, a platinum counter electrode, and an Ag / AgCl reference electrode. When the peptide chain substrate is cleaved by the protease, the surface characteristics of the electrode change, resulting in a change in the solution impedance. The protease activity is quantified by measuring the impedance value.

7. The intelligent monitoring and nursing response device for general surgical wound exudation according to claim 3, characterized in that: The bacterial marker detection component (205) includes a bacterial marker detection chamber (2051), a fluorescent silicone microbead plate (2053), a blue LED light column (2054), a third mounting groove (2056), a third micro negative pressure pump (2058), and a photodiode (2057). The bacterial marker detection chamber (2051) contains a bacterial marker detection slot (2052). The fluorescent silicone microbead plate (2053) is placed inside the bacterial marker detection slot (2052). The blue LED light column (2054) is installed inside the bacterial marker detection slot (2052). The third mounting groove (2056) is located on the side of the PCB circuit board (206) near the bacterial marker detection component (205). The photodiode (2057) is mounted on the top of the third mounting groove (2056) corresponding to the bacterial marker detection groove (2052). The third micro negative pressure pump (2058) is mounted on the upper surface of the PCB circuit board (206) and is connected to the bacterial marker detection groove (2052). The bottom of the bacterial marker detection groove (2052) is provided with a third liquid inlet (2055) and is connected to the bacterial marker detection flow channel hole (2019). The blue LED is used to excite the fluorescent aptamer in the fluorescent silica microbeads. When the aptamer binds to the target bacteria, its conformation changes, and the fluorescence intensity increases or decreases. The fluorescence signal intensity detected by the photodiode is related to the bacterial concentration.

8. The intelligent monitoring and nursing response device for general surgical wound exudation according to claim 1, characterized in that: The response mechanism (3) includes a top plate (301), a protective plate (302), a medicine tank (304), a micro piezoelectric peristaltic pump (305), a micro gas tank (307), a micro air pump (308), and a connecting pipe. The protective plate (302) is fixed below the top plate (301). The medicine tank (304) and the micro gas tank (307) are both installed on the top of the top plate (301). The micro piezoelectric peristaltic pump (305) is connected to the medicine tank (304) and the drug inlet pipe (104) of the bionic contact mechanism (1) through a first connecting pipe (306). The micro air pump (308) is connected to the micro gas tank (307) and the gas inlet pipe (105) of the bionic contact mechanism (1) through a second connecting pipe (309). The protective plate (302) has a through groove (303) for the micro negative pressure pump to exhaust gas.

9. The intelligent monitoring and nursing response device for general surgical wound exudation according to claim 1, characterized in that: The PCB circuit board (206) integrates a data processing module and a wireless transmission module, which can receive the detection signals of each detection component and convert them into digital data, and send them to an external terminal through the wireless transmission module.

10. The intelligent monitoring and nursing response device for general surgical wound exudation according to claim 2, characterized in that: The biomimetic contact layer (101) is made of medical-grade polyurethane. The surface is treated with plasma and then impregnated with perfluoropolyether lubricant. The biomimetic contact layer (101) prevents new granulation tissue from attaching effectively through the lubricating surface that mimics the structure of a pitcher plant. The diameter of the conical micropores (106) is 50-100 μm, and the spacing between adjacent micropores is 200-300 μm.

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