A non-invasive electroencephalogram sensor and multifunctional monitoring system

Abstract

The utility model relates to a kind of noninvasive electroencephal sensor and multifunctional monitoring system, and one kind of noninvasive electroencephal sensor includes encryption identification component and sensor body, the sensor body is connected with the encryption identification component, the sensor body includes flexible base material, circuit coating and insulating layer, the circuit coating is coated on the flexible base material and formed with several sensing electrode positions, the insulating layer is covered on the circuit coating, first foam is pasted on the insulating layer, second foam is pasted on the sensing electrode position, stylus is pasted on the second foam, sponge disc is equipped on the stylus, conductive hydrogel is adsorbed on the sponge disc, the side of the flexible base material opposite to the circuit coating is printed with ink layer. The utility model has the beneficial effect that the contact surface of noninvasive electroencephal sensor electrode and skin is increased, and the quality and accuracy of electroencephal signal acquisition are improved.

Description

Technical Field

[0001] This utility model relates to the field of medical device technology, specifically to a non-invasive electroencephalogram (EEG) sensor and a multifunctional monitoring system. Background Technology

[0002] Non-invasive EEG sensors are instruments used to monitor the depth of anesthesia in real time. During anesthesia, the electrical activity of the brain changes accordingly with the use of anesthetic drugs. Non-invasive EEG sensors can continuously monitor these changes and accurately assess the depth of anesthesia by analyzing characteristic parameters of the EEG signals, such as frequency, amplitude, and rhythm. Based on the depth of anesthesia information monitored by non-invasive EEG sensors, anesthesiologists can adjust the dosage and administration rate of anesthetic drugs in a timely manner.

[0003] Traditional non-invasive EEG sensors have significant drawbacks in conductivity and skin contact. Some sensors use planar electrodes, resulting in limited contact area with the skin, leading to unstable contact and high contact resistance. This causes severe attenuation of EEG signals during transmission, resulting in weak signal strength and high noise levels, failing to accurately reflect the true electrical activity of the brain. Furthermore, even slight patient movement can cause relative displacement between the electrodes and the skin, further disrupting the contact and affecting the continuity and reliability of signal acquisition. Utility Model Content

[0004] The purpose of this invention is to provide a non-invasive EEG sensor and a multifunctional monitoring system that can increase the contact area between the electrodes of the non-invasive EEG sensor and the skin, thereby improving the quality and accuracy of EEG signal acquisition.

[0005] A non-invasive EEG sensor includes an encryption identification component and a sensor body. The sensor body is connected to the encryption identification component. The sensor body includes a flexible substrate, a circuit coating, and an insulating layer. The circuit coating is applied to the flexible substrate to form a plurality of sensing electrode sites. The insulating layer covers the circuit coating. A first foam is attached to the insulating layer. A second foam is attached to the sensing electrode sites. A stylus is attached to the second foam. The stylus has a sponge disc. Conductive hydrogel is adsorbed on the sponge disc. An ink layer is printed on the side of the flexible substrate opposite to the circuit coating.

[0006] In the above scheme, the flexible substrate serves as the support for the entire sensor body. The flexible substrate can bend and deform according to the shape of the head, increasing the contact area and fit between the sensor body and the scalp. A circuit coating is applied to the flexible substrate to form several sensing electrode positions. The number and position of these sensing electrode positions can be precisely arranged on the flexible substrate according to different structural requirements. An insulating layer covers the circuit coating except for the sensing electrode positions, protecting the electrical signals from exposure and ensuring safety against leakage. The first foam supports the second foam, the stylus, and the sponge disc. The second foam connects the sensing electrode positions and the stylus, providing some support to the stylus. The stylus can pierce the skin surface, increasing the contact area between the sensor body and the skin, resulting in better conductivity. The sponge disc better absorbs the conductive hydrogel, which can also flow from the gaps in the stylus and fill the second foam, allowing the conductive hydrogel to better cooperate with the sensing electrode positions, improving the quality and accuracy of EEG signal acquisition.

[0007] Furthermore, the insulating layer has the same shape as the flexible substrate, and the insulating layer has a first through hole at the position corresponding to the sensing electrode.

[0008] In the above scheme, the insulating layer and the flexible substrate have the same shape, which can achieve a perfect fit between the two. When the sensor is worn on the head, the flexible substrate will bend and deform with the shape of the head, and the insulating layer with a matching shape can follow this deformation synchronously and always be tightly bonded to the flexible substrate. The insulating layer has a first through hole at the position of the sensing electrode. This design can ensure that the sensing electrode is accurately exposed and can effectively interact with the outside world. It can ensure that the EEG signal can be smoothly transmitted from the scalp to the sensing electrode, improve the accuracy and reliability of EEG signal acquisition, and provide a better data foundation for subsequent signal analysis and diagnosis.

[0009] Furthermore, the first foam is PE foam, and the first foam has a second through hole at the position corresponding to the first through hole.

[0010] In the above scheme, PE foam has excellent flexibility, elasticity and cushioning properties, which can better support the second foam, stylus and sponge plate. The second through hole is provided at the position of the first through hole of the first foam to ensure that the sensing electrode position is accurately exposed through the first through hole and the second through hole. In this way, the sensing electrode position can directly contact the stylus, sponge plate and conductive hydrogel, thereby ensuring that the EEG signal can be smoothly transmitted from the scalp to the inside of the sensor, improving the quality and accuracy of EEG signal acquisition.

[0011] Furthermore, the second foam has a ring-shaped structure.

[0012] In the above scheme, the second foam is used to connect the sensing electrode position and the stylus, and provides a certain support for the stylus. The ring design can adhere to the stylus within the maximum range while also filling the conductive hydrogel to the maximum extent, thereby ensuring the stability of the stylus and increasing the conductive area.

[0013] Furthermore, the circuit coating is a silver chloride coating.

[0014] In the above scheme, silver chloride has good conductivity. As a circuit coating, it can significantly reduce the contact impedance between the electrode and the skin. The low contact impedance helps to collect EEG signals more efficiently and reduce signal attenuation and distortion during transmission. In EEG monitoring, weak EEG signals can be transmitted to the sensing electrode position more smoothly, improving the sensitivity and accuracy of signal acquisition, so that the collected EEG signals can more realistically reflect the electrical activity of the brain.

[0015] Furthermore, the stylus includes a main body and a needle-like structure disposed on the main body, the main body having a mesh structure.

[0016] In the above scheme, the main body of the mesh structure provides numerous gap channels for the conductive hydrogel, allowing the conductive hydrogel to flow freely and be evenly distributed within it. Combined with the needle-like structure, it can make better contact with the skin, thereby ensuring that the EEG signal can be transmitted from the scalp to the sensing electrode site more efficiently and stably, improving the accuracy and sensitivity of signal acquisition.

[0017] Furthermore, the encryption identification component includes an encryption chip and a handle card holder. The handle card holder has a card slot interface, the encryption chip is embedded in the card slot interface, and one end of the sensor body is mounted on the handle card holder.

[0018] In the above solution, the encryption chip is embedded in the card slot interface to achieve complete encapsulation of the encryption chip, thereby preventing leakage. The integrated design of the encryption identification component and the sensor body makes the EEG sensor easier to integrate with other external devices and systems.

[0019] A multifunctional monitoring system includes a non-invasive EEG sensor as described in any of the above embodiments, and further includes a dual-frequency index module and an anesthesia unit. The non-invasive EEG sensor is connected to the dual-frequency index module via a first connecting cable, and the dual-frequency index module is connected to the anesthesia unit via a second connecting cable.

[0020] In the above scheme, the anesthesia unit can be a monitor, an infusion pump, or an anesthesia machine with a monitor, enabling the non-invasive EEG sensor to be used in multiple scenarios, meeting the usage requirements of different clinical scenarios, simplifying the usage process, reducing the workload of anesthesiologists, improving patient comfort, saving the dosage of anesthetic drugs, and reducing the risk of postoperative over-anesthesia. The most common anesthesia unit is a monitor. The monitor can collect EEG information through a dual-frequency index module connected to the non-invasive EEG sensor. The anesthesiologist can observe the values ​​on the monitor to consider the patient's anesthetic dosage, thereby manually controlling the anesthesia machine to administer anesthesia.

[0021] Furthermore, the anesthesia unit includes an input unit and an infusion pump, the input unit being connected to the dual-frequency index module, and the infusion pump being used to connect to the patient.

[0022] In the above scheme, the anesthesia unit is an infusion pump. The information obtained by the input unit through the dual-frequency index module includes BIS value, electromyography (EMG) signal, burst count, burst inhibition rate, EEG waveform, and BIS value. The infusion pump can analyze the data information obtained by the dual-frequency index module to determine the patient's level of consciousness and increase or decrease the delivery dose of anesthetic solution according to the anesthesia requirements. The PID software is used to adjust and achieve a balanced anesthesia state for the patient.

[0023] Furthermore, the anesthesia unit includes a multi-parameter monitor and an anesthesia machine. The multi-parameter monitor is connected to the second connecting cable, and the anesthesia machine is connected to the multi-parameter monitor. The anesthesia machine is connected to an anesthesia tubing, and the anesthesia tubing is connected to an anesthesia mask, which is used to connect to the patient.

[0024] In the above scheme, the multi-parameter monitor can collect EEG information through the dual-frequency index module to determine the patient's level of consciousness. At the same time, it can be combined with non-invasive blood pressure, ECG, blood oxygen saturation, and end-tidal CO2 information. The multi-parameter display on the anesthesia machine and the multi-parameter monitor can share data through a data cable, so that the patient's information is displayed on the multi-parameter display of the anesthesia machine. The multi-parameter display can further determine the input concentration of anesthetic gas based on the patient's information parameters, and can pre-set the operation time, operation type, anesthetic gas type, and concentration information. During the patient's anesthesia operation, the anesthetic inhalation can be automatically fed back through the anesthesia tubing and anesthesia mask.

[0025] The present invention relates to a non-invasive EEG sensor and a multifunctional monitoring system, which has the beneficial effect of increasing the contact area between the electrodes of the non-invasive EEG sensor and the skin, thereby improving the quality and accuracy of EEG signal acquisition. The flexible substrate serves as the support for the entire sensor body. It can bend and deform to conform to the shape of the head, increasing the contact area and fit between the sensor body and the scalp. A circuit coating is applied to the flexible substrate to form several sensing electrode positions. The number and location of these positions can be precisely arranged on the flexible substrate according to different structural requirements. An insulating layer covers the circuit coating except for the sensing electrode positions, protecting the electrical signals from exposure and ensuring safety against leakage. The first foam supports the second foam, the stylus, and the sponge disc. The second foam connects the sensing electrode positions and the stylus, providing some support to the stylus. The stylus can pierce the skin surface, increasing the contact area between the sensor body and the skin, resulting in better conductivity. The sponge disc better absorbs the conductive hydrogel, which can also flow from the gaps in the stylus and fill the second foam, allowing the conductive hydrogel to better cooperate with the sensing electrode positions, improving the quality and accuracy of EEG signal acquisition. Attached Figure Description

[0026] Figure 1 This is a schematic diagram of a non-invasive EEG sensor structure according to one embodiment.

[0027] Figure 2 This is a schematic diagram of a sensor body according to one embodiment.

[0028] Figure 3 for Figure 2 A simplified diagram illustrating the decomposition at point A.

[0029] Figure 4 This is a schematic diagram of a flexible substrate according to one embodiment.

[0030] Figure 5 This is a schematic diagram of the circuit coating in one embodiment.

[0031] Figure 6 This is a schematic diagram of an insulating layer according to one embodiment.

[0032] Figure 7 This is a schematic diagram of the first foam in one embodiment.

[0033] Figure 8 This is a schematic diagram of the second foam in one embodiment.

[0034] Figure 9 This is a schematic diagram of a stylus according to one embodiment.

[0035] Figure 10 This is a schematic plan view of the main body of one embodiment.

[0036] Figure 11This is a schematic diagram of a handle holder according to one embodiment.

[0037] Figure 12 This is a schematic diagram of the multifunctional monitoring system in Example 1.

[0038] Figure 13 This is a schematic diagram of the multifunctional monitoring system in Example 2.

[0039] Figure 14 This is a schematic diagram of the multifunctional monitoring system in Example 2.

[0040] Figure 15 This is a schematic diagram of the multifunctional monitoring system in Example 3.

[0041] Figure 16 This is a schematic diagram of the multifunctional monitoring system in Example 3.

[0042] Explanation of reference numerals: 1. Encryption identification component; 11. Encryption chip; 120. Handle holder; 121. Card slot interface; 2. Sensor body; 21. Flexible substrate; 22. Circuit coating; 23. Insulating layer; 231. First through hole; 24. First foam; 241. Second through hole; 25. Second foam; 26. Stimulus needle; 261. Main body; 262. Needle structure; 27. Sponge disc; 28. Conductive hydrogel; 29. ​​Ink layer; 3. Sensing electrode position; 100. Non-invasive EEG sensor; 4. Dual-frequency index module; 5. Monitor; 6. First connecting cable; 7. Second connecting cable; 8. Input unit; 9. Infusion pump; 10. Multi-parameter monitor; 11. Anesthesia machine; 111. Multi-parameter display; 12. Anesthesia tubing; 13. Anesthesia mask. Detailed Implementation

[0043] The following will provide a more detailed description of the non-invasive electroencephalogram (EEG) sensor and multifunctional monitoring system of this utility model, in conjunction with specific embodiments and accompanying drawings.

[0044] like Figures 1 to 3 As shown in a preferred embodiment, a non-invasive EEG sensor 100 of this utility model includes an encryption identification component 1 and a sensor body 2. The sensor body 2 is connected to the encryption identification component 1. The sensor body 2 includes a flexible substrate 21, a circuit coating 22, and an insulating layer 23. The circuit coating 22 is coated on the flexible substrate 21 to form a plurality of sensing electrode positions 3. The insulating layer 23 covers the circuit coating 22. A first foam 24 is attached to the insulating layer 23. A second foam 25 is attached to the sensing electrode positions 3. A stylus 26 is attached to the second foam 25. A sponge disc 27 is provided on the stylus 26. Conductive hydrogel 28 is adsorbed on the sponge disc 27. An ink layer 29 is printed on the side of the flexible substrate 21 opposite to the circuit coating 22.

[0045] The flexible substrate 21 serves as the support for the entire sensor body 2. It can bend and deform to conform to the shape of the head, increasing the contact area and fit between the sensor body 2 and the scalp. A circuit coating 22 is applied to the flexible substrate 21 to form several sensing electrode positions 3. The number and position of the sensing electrode positions 3 can be precisely arranged on the flexible substrate 21 according to different structural requirements. An insulating layer 23 covers the portion of the circuit coating 22 except for the sensing electrode positions 3, protecting the electrical signals from exposure and ensuring leakage safety. The first foam 24 supports the second... The foam 25, stylus 26, and sponge disc 27 provide support. The second foam 25 connects the sensing electrode 3 and the stylus 26, providing some support for the stylus 26. The stylus 26 can pierce the skin surface, thereby increasing the contact area between the sensor body 2 and the skin, resulting in better conductivity. The sponge disc 27 can better absorb the conductive hydrogel 28, and the conductive hydrogel 28 can also flow from the gaps in the stylus 26 and fill the second foam 25, thus enabling the conductive hydrogel 28 to better cooperate with the sensing electrode 3, improving the quality and accuracy of EEG signal acquisition.

[0046] In the above embodiments, the flexible substrate 21 can be a PET substrate. PET substrate has good support and insulation properties. During preparation, it is cut into the required shape using a special die. The design thickness is suitable in the range of 0.04mm-0.08mm, so that it is not easy to break while maintaining good flexibility.

[0047] The ink layer 29 is screen-printed with black or colored ink. The ink material is UV ink or solvent-based ink. Using this ink, the following requirements must be met after printing: After rubbing the printed pattern three times with a 500g weight wrapped in white cloth, there should be no ink flaking; wiping with a cloth soaked in distilled water, alcohol, or isopropyl alcohol for 15 seconds should not cause any color loss. This printing allows anesthesiologists to clearly identify the correct information required by the EEG sensor and ensures that its effectiveness is not lost when cleaning with alcohol or other solutions.

[0048] like Figure 4 and Figure 6As shown, in some embodiments, the insulating layer 23 has the same shape as the flexible substrate 21, and the insulating layer 23 has a first through hole 231 at the position corresponding to the sensing electrode 3. The insulating layer 23 and the flexible substrate 21 have the same shape, which can achieve a perfect fit between the two. When the sensor is worn on the head, the flexible substrate 21 will bend and deform with the shape of the head, and the insulating layer 23 with a matching shape can synchronously follow this deformation and always be tightly bonded to the flexible substrate 21. The insulating layer 23 has a first through hole 231 at the position corresponding to the sensing electrode 3. This design can ensure that the sensing electrode 3 is accurately exposed and can effectively interact with the outside world. It can ensure that the EEG signal can be smoothly transmitted from the scalp to the sensing electrode 3, improve the accuracy and reliability of EEG signal acquisition, and provide a better data foundation for subsequent signal analysis and diagnosis.

[0049] The insulation layer 23 can be made of transparent nylon with a thickness of 0.05mm. The insulation layer 23 is attached to the circuit coating 22 and has been tested to withstand 1000V high voltage without being broken down, thus meeting the electrical safety requirements of the product.

[0050] like Figure 7 As shown, in some embodiments, the first foam 24 is made of PE foam, and a second through-hole 241 is provided at the position corresponding to the first through-hole 231. PE foam has excellent flexibility, elasticity, and cushioning properties, which can better support the second foam 25, the stylus 26, and the sponge disc 27. It is made of polyethylene, which is safe and reliable, and its thickness is between 1.8-2.0 mm. Using this material and the design dimensions, the product has good support performance. The second through-hole 241 at the position corresponding to the first through-hole 231 of the first foam 24 ensures that the sensing electrode 3 is accurately exposed through the first through-hole 231 and the second through-hole 241. In this way, the sensing electrode 3 can directly contact the stylus 26, the sponge disc 27, and the conductive hydrogel 28, thereby ensuring that the EEG signal can be smoothly transmitted from the scalp to the inside of the sensor, improving the quality and accuracy of EEG signal acquisition.

[0051] like Figure 8 As shown, in some embodiments, the second foam 25 has a ring-shaped structure. The second foam 25 has double-sided adhesive, which is used to connect the sensing electrode position 3 and the stylus 26, providing some support for the stylus 26. The ring design allows for maximum adhesion to the stylus 26 while also maximizing the filling of the conductive hydrogel 28, thereby ensuring the stability of the stylus 26 and increasing the conductive area. In assembling the second foam 25, one side of the release paper is first peeled off and adhered to the sensing electrode position 3, and then the other side of the release paper is peeled off for adhering to the stylus 26.

[0052] like Figure 5As shown, in some embodiments, the circuit coating 22 is a silver chloride coating. Silver chloride has good conductivity, and as the circuit coating 22, it can significantly reduce the contact impedance between the electrode and the skin. Low contact impedance helps to acquire EEG signals more efficiently, reducing signal attenuation and distortion during transmission. In EEG monitoring, weak EEG signals can be transmitted to the sensing electrode 3 more smoothly, improving the sensitivity and accuracy of signal acquisition, so that the acquired EEG signals can more accurately reflect the electrical activity of the brain.

[0053] The preparation of the silver chloride coating affected key electrical properties. Different formulations and circuit designs revealed that it specifically impacted the following electrical properties: AC impedance, DC offset voltage, internal noise, simulated defibrillation overload recovery performance, simulated defibrillation AC impedance, and bias current withstand capability. The key parameters for preparing the AgCl circuit coating are as follows: Electrical properties: The resistivity of the material is suitable at 0.01Ω*mil-0.03Ω*mil. Other properties of the AgCl coating material: Boiling point (°C): 214 °C; Density: 4.1 g / cm³; Flash point (°C): 107 °C; Insoluble in water; The material contains silver and trace amounts of diethylene glycol monoethyl ether acetate. The overall design thickness is suitable at 0.005 mm-0.015 mm.

[0054] The design, after testing, achieves the following electrical characteristics: AC impedance: ≤2.0 kΩ (10Hz); DC offset voltage: ≤100mV; internal noise: ≤150μV (peak-to-peak); simulated defibrillation overload recovery performance: electrode pair voltage ≤100mV 5s after discharge; average rate of change ≤±1mV / s over the following 30s; AC impedance after simulated defibrillation: ≤1.5kΩ (10Hz); bias current tolerance: ≤100mV. These electrical characteristics are sufficient to meet clinical performance requirements for the product.

[0055] like Figure 9 and Figure 10 As shown, in some embodiments, the stylus 26 includes a main body 261 and a needle-like structure 262 disposed on the main body 261, the main body 261 having a mesh structure. The mesh structure of the main body 261 provides numerous slit channels for the conductive hydrogel 28, allowing the conductive hydrogel 28 to flow freely and be evenly distributed therein. Combined with the needle-like structure 262, it can make better contact with the skin, thereby ensuring that the electroencephalogram (EEG) signal can be transmitted more efficiently and stably from the scalp to the sensing electrode site 3, improving the accuracy and sensitivity of signal acquisition.

[0056] like Figure 11As shown, in some embodiments, the encryption identification component 1 includes an encryption chip 11 and a handle card holder 120. The handle card holder 120 has a card slot interface 121, and the encryption chip 11 is embedded in the card slot interface 121. One end of the sensor body 2 is mounted on the handle card holder 120. The encryption chip 11 being embedded in the card slot interface 121 can achieve complete coverage of the encryption chip 11, thereby preventing leakage. The integrated design of the encryption identification component 1 and the sensor body 2 makes it easier for the EEG sensor to be integrated with other external devices and systems.

[0057] This invention relates to a non-invasive EEG sensor. A circuit coating 22 is applied to a flexible substrate 21 to form several sensing electrode positions 3, which can accurately sense EEG signals on the scalp surface. The sensor is placed on the scalp, and the stylus 26 pierces the skin surface, increasing the contact area between the sensor body 2 and the skin, resulting in better conductivity. Conductive hydrogel 28 flows from the gaps in the stylus 26 and fills the second foam 25, thus better cooperating with the sensing electrode positions 3 and guiding the EEG signals to the sensing electrode positions 3. The collected EEG signals are transmitted to the encryption identification component 1 through the circuit coating 22.

[0058] A multifunctional monitoring system includes a non-invasive EEG sensor 100 as described in any of the above embodiments, a dual-frequency index module 4, and an anesthesia unit. The non-invasive EEG sensor 100 is connected to the dual-frequency index module 4 via a first connecting cable 6, and the dual-frequency index module 4 is connected to the anesthesia unit via a second connecting cable 7. The anesthesia unit can be a monitor 5, an infusion pump, or an anesthesia machine 11 with a monitor 5, enabling the non-invasive EEG sensor 100 to be used in multiple scenarios, meeting the usage requirements of different clinical scenarios, simplifying the usage process, reducing the workload of anesthesiologists, improving patient comfort, saving the dosage of anesthetic drugs, and reducing the risk of postoperative over-anesthesia. The following describes the multifunctional monitoring system in detail with reference to embodiments. Example 1

[0059] like Figure 12 As shown, in this embodiment, the anesthesia unit is a monitor 5. The monitor 5 can collect EEG information through a dual-frequency index module 4 connected to the non-invasive EEG sensor 100. The anesthesiologist can measure the patient's anesthesia dosage by observing the values ​​of the monitor 5, and then manually control the anesthesia machine to perform anesthesia. Example 2

[0060] like Figure 13As shown, in this embodiment, the anesthesia unit includes an input unit 8 and an infusion pump 9. The input unit 8 is connected to the dual-frequency index module 4, and the infusion pump 9 is used to connect to the patient. This anesthesia unit is an infusion pump. The information obtained by the input unit 8 through the dual-frequency index module 4 includes BIS value, electromyography (EMG) signal, burst count, burst inhibition rate, EEG waveform, and BIS value. The infusion pump 9 can analyze the data information obtained from the dual-frequency index module 4 to determine the patient's level of consciousness and increase or decrease the delivery dose of anesthetic solution according to the anesthesia requirements. The PID software is used to adjust and achieve a balanced anesthesia state for the patient.

[0061] Specifically, refer to Figure 14 The infusion pump 9 includes a control unit and an output execution unit. Users can set closed-loop parameters in the control unit according to actual needs. The control unit mainly includes a closed-loop switch: which can turn the closed-loop execution program on or off; a start time: setting or reading the start time; a target value setting: setting the target value parameter; emptying: the infusion pump 9 can be manually run to empty the medicine when needed; running and pausing: setting the start and stop of running; and sensor detection: the connection status of the dual-frequency index module 4 can be detected at any time.

[0062] The output execution unit controls the drug concentration and plasma concentration based on the closed-loop parameters and the relevant values ​​of the dual-frequency index module 4. The drug concentration refers to the concentration of intravenous anesthetic drugs such as propofol. Other similar anesthetic drugs include etomidate, ketamine, and thiopental sodium. The anesthesia unit, i.e., the infusion pump, can display the set concentration, flow rate, effect concentration, and current total amount information, which is convenient for medical staff to observe the real-time status of the closed loop. Example 3

[0063] like Figure 15 and Figure 16As shown, in this embodiment, the anesthesia unit includes a multi-parameter monitor 10 and an anesthesia machine 11. The multi-parameter monitor 10 is connected to a second connecting cable 7, and the anesthesia machine 11 is connected to the multi-parameter monitor 10. The anesthesia machine 11 is connected to an anesthesia tubing 12, and the anesthesia tubing 12 is connected to an anesthesia mask 13, which is used to connect to the patient. The multi-parameter monitor 10 can collect EEG information through the dual-frequency index module 4 to determine the patient's level of consciousness. At the same time, it can collect information on non-invasive blood pressure, ECG, blood oxygen saturation, and end-tidal CO2. The multi-parameter display 111 on the anesthesia machine 11 and the multi-parameter monitor 10 share data through a data cable, so that the patient's information is displayed on the multi-parameter display 111 of the anesthesia machine 11. The multi-parameter display 111 continues to determine the input concentration of anesthetic gas based on the patient's information parameters, and can pre-set the operation time, operation type, anesthetic gas type, and concentration information. During the patient's anesthesia operation, the anesthesia tubing 12 and the anesthesia mask 13 can realize an automated feedback process of anesthetic inhalation.

[0064] In the description of this utility model, it should be understood that terms such as "upper", "lower", "front", "back", "left", "right", "vertical", "horizontal", "top", "bottom", "inner", and "outer" indicate the orientation or positional relationship based on the orientation or positional relationship shown in the accompanying drawings. They are only for the convenience of describing this utility model and simplifying the description, and do not indicate or imply that the device or element referred to must have a specific orientation, or be constructed and operated in a specific orientation. Therefore, they should not be construed as limitations on this utility model.

[0065] Furthermore, the terms "first" and "second" are used for descriptive purposes only and should not be construed as indicating or implying relative importance or implicitly specifying the number of technical features indicated. Thus, a feature defined as "first" or "second" may explicitly or implicitly include one or more of that feature. In the description of this utility model, "a plurality of" means two or more, unless otherwise explicitly specified.

[0066] In this utility model, unless otherwise explicitly specified and limited, the terms "installation," "connection," "joining," and "fixing," etc., should be interpreted broadly. For example, they can refer to a fixed connection, a detachable connection, or an integral part; they can refer to a mechanical connection or an electrical connection; they can refer to a direct connection or an indirect connection through an intermediate medium; they can refer to the internal communication of two components or the interaction between two components. Those skilled in the art can understand the specific meaning of the above terms in this utility model according to the specific circumstances.

[0067] Although the description of this utility model has been given in conjunction with the specific embodiments described above, it is obvious to those skilled in the art that many substitutions, modifications, and variations can be made based on the above description. Therefore, all such substitutions, modifications, and variations are included within the spirit and scope of the appended claims.

Claims

1. A non-invasive electroencephalogram (EEG) sensor, characterized in that, The device includes an encryption identification component and a sensor body. The sensor body is connected to the encryption identification component. The sensor body includes a flexible substrate, a circuit coating, and an insulating layer. The circuit coating is applied to the flexible substrate to form a plurality of sensing electrode positions. The insulating layer covers the circuit coating. A first foam is attached to the insulating layer. A second foam is attached to the sensing electrode positions. A stylus is attached to the second foam. The stylus is provided with a sponge disk. Conductive hydrogel is adsorbed on the sponge disk. An ink layer is printed on the side of the flexible substrate opposite to the circuit coating.

2. The non-invasive EEG sensor according to claim 1, characterized in that, The insulating layer has the same shape as the flexible substrate, and the insulating layer has a first through hole at the position corresponding to the sensing electrode.

3. The non-invasive EEG sensor according to claim 2, characterized in that, The first foam is PE foam, and the first foam has a second through hole at the position corresponding to the first through hole.

4. The non-invasive EEG sensor according to claim 1, characterized in that, The second foam has a ring structure.

5. The non-invasive EEG sensor according to claim 1, characterized in that, The circuit coating is a silver chloride coating.

6. The non-invasive EEG sensor according to claim 1, characterized in that, The stylus includes a main body and a needle-like structure disposed on the main body, wherein the main body has a mesh structure.

7. The non-invasive EEG sensor according to claim 1, characterized in that, The encryption identification component includes an encryption chip and a handle card holder. The handle card holder has a card slot interface, the encryption chip is embedded in the card slot interface, and one end of the sensor body is installed on the handle card holder.

8. A multifunctional monitoring system, characterized in that, The device includes a non-invasive EEG sensor as described in any one of claims 1 to 7, and further includes a dual-frequency index module and an anesthesia unit. The non-invasive EEG sensor is connected to the dual-frequency index module via a first connecting cable, and the dual-frequency index module is connected to the anesthesia unit via a second connecting cable.

9. The multifunctional monitoring system according to claim 8, characterized in that, The anesthesia unit includes an input unit and an infusion pump. The input unit is connected to the dual-frequency index module, and the infusion pump is used to connect to the patient.

10. The multifunctional monitoring system according to claim 8, characterized in that, The anesthesia unit includes a multi-parameter monitor and an anesthesia machine. The multi-parameter monitor is connected to the second connecting cable, and the anesthesia machine is connected to the multi-parameter monitor. The anesthesia machine is connected to an anesthesia tubing, and the anesthesia tubing is connected to an anesthesia mask. The anesthesia mask is used to connect to the patient.

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