Automatic external defibrillator

Abstract

The utility model provides an automatic external defibrillator, which relates to the technical field of medical treatment, and is characterized in that an external electrode plate used for collecting bio-electricity signals is connected with an electrode connecting part, the electrode connecting part is then connected with an electrode wire, and the electrode wire penetrates through an inner hole of a magnetic ring part; due to the high magnetic conductivity of the magnetic ring part, most of the alternating magnetic field can be guided into the magnetic ring part, according to the law of electromagnetic induction, the alternating magnetic field can induce eddy current in the magnetic ring part, and electromagnetic energy can be consumed and converted into heat energy to be dissipated due to the generation of the eddy current. According to the automatic external defibrillator, the intensity of interference signals is greatly attenuated, the interference signals are difficult to continue to spread along the electrode wires, the impedance of the magnetic ring is small and the energy loss is low for bioelectricity signals with low frequency, so that the bioelectricity signals with low frequency cannot be obviously attenuated, normal transmission of the bioelectricity signals with low frequency can be ensured, and the reliability of the automatic external defibrillator is improved.

Description

Technical Field

[0001] This utility model relates to the field of medical technology, and more specifically, to an automated external defibrillator. Background Technology

[0002] In modern emergency medical care, AEDs (Automated External Defibrillators), as portable medical devices, play a crucial role in emergencies such as cardiac arrest. Their core function is to quickly identify a patient's cardiac rhythm and, if necessary, restore a normal heart rhythm through an electric shock, buying precious time to save the patient's life. To achieve this core function, AEDs need to accurately collect the patient's bioelectrical signals, such as electrocardiogram (ECG) signals, via electrode wires. These bioelectrical signals are often very weak but contain crucial information reflecting the heart's functional state; the accuracy of their collection directly affects the device's judgment of the heart rhythm and the effectiveness of subsequent treatment measures.

[0003] However, in real-world applications, the electromagnetic environment in which automated external defibrillators (AEDs) operate is often quite complex. In medical settings, the presence of high-frequency interference sources (such as surgical electrosurgical units or radio frequency signals from wireless devices) can cause the electrode wires to act like antennas, absorbing noise and interfering with the already weak bioelectrical signals, leading to signal distortion and increased noise. This can affect the AED's accurate rhythm recognition, potentially resulting in misdiagnosis or missed diagnosis, and reducing the device's reliability. Therefore, minimizing the impact of high-frequency electromagnetic interference on the bioelectrical signal acquisition process and ensuring the accuracy of signal acquisition is a critical technical challenge that needs to be addressed in the research and application of AEDs. Utility Model Content

[0004] The problem this invention addresses is: how to reduce the impact of high-frequency electromagnetic interference on the bioelectric signal acquisition process.

[0005] To address the above problems, this utility model provides an automated external defibrillator, including a main unit and a socket portion disposed on the main unit; the socket portion includes:

[0006] Electrode connection part, used to connect external electrode plates;

[0007] An electrode wire, which is electrically connected to the electrode connection portion;

[0008] The magnetic ring portion has at least a portion of the electrode wire passing through the inner hole of the magnetic ring portion.

[0009] Optionally, the automated external defibrillator further includes a magnetic ring fixing part, which is connected to the housing of the socket part; the magnetic ring fixing part includes two first limiting plates arranged at relative intervals and a first protrusion disposed on the opposing surfaces of the two first limiting plates; wherein, the extending direction of the first limiting plates is perpendicular to the axial direction of the magnetic ring part, the first limiting plates abut against the end face of the magnetic ring part, and the first protrusion abuts against the inner wall of the magnetic ring part to fix the magnetic ring part.

[0010] Optionally, the inner hole of the magnetic ring portion includes a first sub-hole and a second sub-hole, both of which penetrate the magnetic ring portion along its axial direction; wherein, the first sub-hole is located between the two first limiting plates, the first protrusion abuts against the inner wall of the first sub-hole, the second sub-hole is located outside the two first limiting plates, and the electrode wire passes through the second sub-hole.

[0011] Optionally, the end of the first protrusion near the second sub-hole is a first wedge-shaped portion, and the thickness of the first wedge-shaped portion gradually increases in the direction from the second sub-hole to the first sub-hole.

[0012] Optionally, the wedge angle of the first wedge portion is 10° to 25°.

[0013] Optionally, the end of the first protrusion away from the second sub-hole is the first end, and the thickness of the first end remains unchanged in the direction from the second sub-hole to the first sub-hole.

[0014] Optionally, the end of the first protrusion away from the second sub-hole is a second wedge-shaped portion, and the thickness of the second wedge-shaped portion gradually decreases in the direction from the second sub-hole to the first sub-hole.

[0015] Optionally, the end face of the first protrusion away from the second sub-hole is an arc surface corresponding to the inner wall of the first sub-hole.

[0016] Optionally, the magnetic ring fixing part further includes a second limiting plate, which is disposed on the side of the first sub-hole away from the second sub-hole and between the housing of the socket part and the magnetic ring part; wherein, the end face of the second limiting plate near the magnetic ring part is an arc surface that corresponds to and matches the outer cylindrical surface of the magnetic ring part, and the end face of the second limiting plate near the magnetic ring part abuts against the outer cylindrical peripheral wall of the magnetic ring part.

[0017] Optionally, the host includes a control element; wherein the electrode wire includes a first portion passing through the inner hole of the magnetic ring portion, a second portion surrounding the outer wall of the magnetic ring portion, and a third portion connected to the control element, the second portion extending in a direction parallel to the axial direction of the magnetic ring portion.

[0018] The beneficial effects of this automated external defibrillator (AED) are as follows: An external electrode pad for collecting bioelectrical signals is connected to an electrode connector, which in turn is connected to electrode leads. By passing the electrode leads through the inner hole of a magnetic ring, when high-frequency electromagnetic interference signals propagate through the leads, an alternating magnetic field is generated around them. Due to the high permeability of the magnetic ring, most of the alternating magnetic field is guided into the ring. According to the law of electromagnetic induction, eddy currents are induced in the ring, consuming electromagnetic energy and dissipating it as heat. The higher the frequency of the high-frequency signal, the more significant this energy loss, resulting in a substantial attenuation of the interference signal's intensity, making it difficult for it to continue propagating along the electrode leads, thus reducing its impact on subsequent circuitry or signal acquisition. For lower-frequency bioelectrical signals, the magnetic ring has lower impedance and energy loss, therefore it does not cause significant attenuation, ensuring the normal transmission of lower-frequency bioelectrical signals. This not only effectively reduces high-frequency electromagnetic interference but also ensures the integrity and accuracy of bioelectrical signals, improving the reliability of the AED. Attached Figure Description

[0019] Figure 1 This is a schematic diagram of the structure of an automated external defibrillator in an embodiment of this utility model;

[0020] Figure 2 This is a schematic diagram of another structure of the automated external defibrillator in this embodiment of the present invention;

[0021] Figure 3 for Figure 2 A magnified view of a portion of region A;

[0022] Figure 4 for Figure 2 Another enlarged view of region A;

[0023] Figure 5 This is a schematic diagram of another structure of the automated external defibrillator in this embodiment of the present invention;

[0024] Figure 6 for Figure 5 A magnified view of a portion of region B;

[0025] Figure 7 for Figure 5 Another enlarged view of region B;

[0026] Figure 8 for Figure 7 A magnified view of a portion of region C;

[0027] Figure 9 for Figure 7Another enlarged view of region C.

[0028] Explanation of reference numerals in the attached figures:

[0029] Automated external defibrillator 10; main unit 11; control element 12; socket 20; electrode connection 30; electrode wire 40; first part 41; second part 42; third part 43; magnetic ring 50; first sub-hole 51; second sub-hole 52; inner hole 53; magnetic ring fixing part 60; first limiting plate 61; first protrusion 62; first wedge 63; first end 64; second wedge 65; second limiting plate 66; external electrode pad 70. Detailed Implementation

[0030] To make the above-mentioned objects, features, and advantages of this utility model more apparent and understandable, specific embodiments of this utility model will be described in detail below with reference to the accompanying drawings. Although some embodiments of this utility model are shown in the drawings, it should be understood that this utility model can be implemented in various forms and should not be construed as limited to the embodiments set forth herein. Rather, these embodiments are provided to provide a more thorough and complete understanding of this utility model. It should be understood that the drawings and embodiments of this utility model are for illustrative purposes only and are not intended to limit the scope of protection of this utility model.

[0031] In the attached diagram, the Z-axis represents the vertical direction, i.e., up and down. The positive direction of the Z-axis represents upward, and the negative direction represents downward. The plane containing the X-axis and Y-axis in the attached diagram represents the horizontal plane, and any direction on the horizontal plane is horizontal. It should also be noted that the aforementioned representations of the Z-axis, Y-axis, and X-axis 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.

[0032] The term "comprising" and its variations as used herein are open-ended, meaning "including but not limited to"; the term "based on" means "at least partially based on"; the term "one embodiment" means "at least one embodiment"; the term "another embodiment" means "at least one additional embodiment"; the term "some embodiments" means "at least some embodiments"; and the term "optionally" means "optional embodiments". Definitions of other terms will be given in the following description. It should be noted that the concepts of "first," "second," etc., mentioned in this utility model are only used to distinguish different devices, modules, or units, and are not used to limit the order of functions performed by these devices, modules, or units or their interdependencies.

[0033] It should be noted that the terms "one" and "multiple" used in this utility model are illustrative rather than restrictive. Those skilled in the art should understand that, unless otherwise expressly indicated in the context, they should be understood as "one or more".

[0034] In the field of modern emergency medicine, the AED (Automated External Defibrillator), a portable medical device, plays a crucial role in emergencies such as cardiac arrest. Its core function is to quickly identify the patient's cardiac rhythm and, if necessary, restore a normal heart rhythm through an electric shock, buying precious time to save the patient's life. To achieve this core function, the AED needs to accurately collect the patient's bioelectrical signals, such as electrocardiogram (ECG) signals, via electrode wires. These bioelectrical signals are often very weak but contain crucial information reflecting the heart's functional state; the accuracy of their collection directly affects the device's judgment of the heart rhythm and the effectiveness of subsequent treatment measures. However, in real-world applications, the electromagnetic environment in which automated external defibrillators (AEDs) operate is often quite complex. In medical settings where high-frequency interference sources (such as surgical electrosurgical units or radio frequency signals from wireless devices) are present, the electrode wires can act as antennas, receiving noise and interfering with the originally weak bioelectrical signals. This can lead to signal distortion, increased noise, and other problems, affecting the AED's accurate identification of heart rhythms and potentially causing misdiagnosis or missed diagnosis. It can also reduce the reliability of the device. Therefore, how to reduce the impact of high-frequency electromagnetic interference on the bioelectrical signal acquisition process and ensure the accuracy of signal acquisition is a technical problem that urgently needs to be solved in the research, development, and application of AEDs.

[0035] To address the problems existing in the aforementioned related technologies, this utility model provides an automated external defibrillator 10. An external electrode pad 70 for collecting bioelectrical signals is connected to an electrode connection part 30, which is then connected to an electrode wire 40. By passing the electrode wire 40 through the inner hole 53 of a magnetic ring part 50, when a high-frequency electromagnetic interference signal propagates through the electrode wire 40, an alternating magnetic field is generated around the electrode wire 40. Due to the high permeability of the magnetic ring part 50, most of the alternating magnetic field is guided into the interior of the magnetic ring part 50. At this time, according to the law of electromagnetic induction, the alternating magnetic field induces eddy currents in the magnetic ring part 50. The generation of eddy currents consumes electromagnetic energy and converts it into heat energy, which is dissipated. The higher the frequency of the high-frequency signal, the more significant this energy loss becomes, thus greatly attenuating the intensity of the interference signal and making it difficult to continue propagating along the electrode wire 40, thereby reducing the impact on subsequent circuits or signal acquisition. For lower-frequency bioelectrical signals, the impedance of the magnetic ring is small, and the energy loss is also low, so it does not cause significant attenuation, ensuring the normal transmission of lower-frequency bioelectrical signals. This not only effectively reduces high-frequency electromagnetic interference, but also ensures the integrity and accuracy of bioelectrical signals, thus improving the reliability of the automated external defibrillator 10.

[0036] The following detailed description is based on specific embodiments.

[0037] Combination Figures 1 to 8 As shown in the figure, an automated external defibrillator 10 provided in this embodiment of the present invention includes a main unit 11 and a socket portion 20 disposed on the main unit 11; the socket portion 20 includes an electrode connection portion 30, an electrode wire 40 and a magnetic ring portion 50; the electrode connection portion 30 is used to connect an external electrode pad 70; the electrode wire 40 is electrically connected to the electrode connection portion 30; the electrode wire 40 passes through the inner hole 53 of the magnetic ring portion 50.

[0038] Understandably, the magnetic ring 50 is made of a high-permeability material, which can effectively absorb high-frequency interference signals. When the frequency of the high-frequency interference signal is high, according to the law of electromagnetic induction, the alternating magnetic field will induce eddy currents in the magnetic ring 50. The generation of eddy currents consumes electromagnetic energy and converts it into heat energy for dissipation, making the absorption effect of the magnetic ring 50 significant and greatly reducing the intensity of high-frequency interference signals. For lower-frequency bioelectrical signals, such as electrocardiogram signals with frequencies between 0.05Hz and 150Hz, the magnetic ring 50 has low impedance and low energy loss, so it will not cause significant attenuation and can ensure the normal transmission of lower-frequency bioelectrical signals. This design not only effectively reduces high-frequency electromagnetic interference but also ensures the integrity and accuracy of bioelectrical signals, improving the reliability of the automated external defibrillator 10.

[0039] Specifically, the magnetic ring 50 is made of a high permeability material, such as nickel-zinc ferrite or manganese-zinc ferrite. The relative permeability of nickel-zinc ferrite is between 100 and 1000, which can have a good suppression effect on the frequency band of 10 MHz to 1 GHz. The relative permeability of manganese-zinc ferrite is between 1000 and 15000, which can have a good suppression effect on the frequency band of 1 kHz to 30 MHz. When the frequency of high-frequency interference signal is high, such as greater than 10 kHz, its absorption effect is more significant and can effectively attenuate high-frequency signals. However, it has almost no effect on low-frequency bioelectrical signals such as electrocardiogram signals, ensuring the stability and accuracy of signal transmission and further improving the safety and effectiveness of the defibrillator.

[0040] In some embodiments, please refer to the following for details. Figure 3 , Figure 4 The automated external defibrillator 10 further includes a magnetic ring fixing part 60, which is connected to the housing of the socket part 20. The magnetic ring fixing part 60 includes two first limiting plates 61 arranged at intervals and a first protrusion 62 disposed on the opposing surfaces of the two first limiting plates 61. The extending direction of the first limiting plates 61 is perpendicular to the axial direction of the magnetic ring part 50. The first limiting plates 61 abut against the end face of the magnetic ring part 50, and the first protrusion 62 abuts against the inner wall of the magnetic ring part 50 to fix the magnetic ring part 50.

[0041] Specifically, the socket portion 20 is connected to the host unit 11, the electrode wire 40 can be disposed within the cavity of the host unit 11, the magnetic ring portion 50 can be disposed within the cavity of the host unit 11, and the magnetic ring fixing portion 60 can be disposed within the cavity of the host unit 11. The magnetic ring fixing portion 60 is connected to the housing of the socket portion 20, thereby achieving stable fixation of the magnetic ring portion 50 within the cavity of the host unit 11 and preventing the magnetic ring portion 50 from experiencing a decrease in shielding effect due to vibration or displacement during equipment operation or movement. Two first limiting plates 61 abut against the end face of the magnetic ring portion 50, limiting the axial displacement of the magnetic ring portion 50; the first protrusion 62 abuts against the inner wall of the magnetic ring portion 50, limiting its radial sway. The double limiting ensures that the position of the magnetic ring portion 50 is fixed, ensuring the relative position of the electrode wire 40 and the magnetic ring is stable, and maintaining a stable interference suppression effect.

[0042] In some embodiments, please refer to the following for details. Figure 3 , Figure 6The magnetic ring portion 50 is a hollow cylinder. The inner hole 53 of the magnetic ring portion 50 includes a first sub-hole 51 and a second sub-hole 52, both of which penetrate the magnetic ring portion 50 along its axial direction. The first sub-hole 51 is located between the two first limiting plates 61, and the first protrusion 62 abuts against the inner wall of the first sub-hole 51. The second sub-hole 52 is located outside the two first limiting plates 61, and the electrode wire 40 passes through the second sub-hole 52. The inner hole 53 of the magnetic ring portion 50 is divided into a first sub-hole 51 and a second sub-hole 52. The first sub-hole 51, in conjunction with the first protrusion 62, secures the magnetic ring portion 50. The second sub-hole 52 is specifically for the electrode wire 40 to pass through, separating the fixing structure from the signal transmission path. This prevents direct contact between the first protrusion 62 and the electrode wire 40, avoiding wear and protecting the wire insulation layer, thus extending the service life. The design of the first sub-hole 51 and the second sub-hole 52 extending along the axial direction of the magnetic ring portion 50 ensures that the electrode wire 40 passes through the magnetic ring smoothly, reduces wire bending or friction, reduces signal transmission loss, and facilitates wire insertion during assembly.

[0043] In some embodiments, please refer to the following for details. Figure 8 , Figure 9 The end of the first protrusion 62 near the second sub-hole 52 is a first wedge-shaped portion 63. The thickness of the first wedge-shaped portion 63 gradually increases in the direction from the second sub-hole 52 to the first sub-hole 51. In the figure, the direction from the second sub-hole 52 to the first sub-hole 51 can be considered the positive direction of the Y-axis, and will not be repeated below. The thickness of the first wedge-shaped portion 63 of the first protrusion 62 gradually increases along the direction from the second sub-hole 52 to the first sub-hole 51, serving a guiding function. During the installation of the magnetic ring portion 50, it can guide it to smoothly fit into the first protrusion 62, reducing the alignment difficulty during assembly and improving assembly efficiency.

[0044] In some embodiments, please refer to the following for details. Figure 8 , Figure 9 The wedge angle α of the first wedge portion 63 is between 10° and 25°. The wedge angle of the first wedge portion 63 is between 10° and 25°, which can optimize the guiding effect. If the angle is too small, the guiding stroke will be too long or it will not be able to form an effective abutment with the magnetic ring portion 50. If the angle is too large, it will increase the assembly resistance. This angle range balances the ease of assembly and the tightness of contact, ensuring that the magnetic ring portion 50 can be easily inserted and can form an effective abutment with the protrusion after installation, thus ensuring the reliability of fixation.

[0045] In some embodiments, please refer to the following for details. Figure 8The end of the first protrusion 62 furthest from the second sub-hole 52 is the first end portion 64. The thickness of the first end portion 64 remains constant in the direction from the second sub-hole 52 to the first sub-hole 51. This constant thickness of the first end portion 64, after guiding the magnetic ring portion 50 into place by the wedge-shaped portion, provides stable planar contact with the inner wall of the magnetic ring portion 50, increasing the contact area, enhancing the radial limiting force, and preventing the magnetic ring portion 50 from gradually loosening due to minor vibrations during long-term use, thus maintaining the durability of the fixing effect.

[0046] In some embodiments, please refer to the following for details. Figure 9 The end of the first protrusion 62 furthest from the second sub-hole 52 is a second wedge-shaped portion 65. The thickness of the second wedge-shaped portion 65 gradually decreases along the direction from the second sub-hole 52 to the first sub-hole 51. The thickness of the second wedge-shaped portion 65 of the first protrusion 62 gradually decreases along the direction from the second sub-hole 52 to the first sub-hole 51, forming a wedge-shaped structure at both ends of the first protrusion 62. After the magnetic ring portion 50 slides into the second wedge-shaped portion 65, the second wedge-shaped portion 65 can reduce the probability of the magnetic ring portion 50 sliding out, enhancing the axial limiting effect, ensuring the magnetic ring portion 50 remains stable during dynamic use, further reducing displacement caused by vibration, and improving the overall structure's durability and reliability.

[0047] In some embodiments, please refer to the following for details. Figure 3 , Figure 4 The end face of the first protrusion 62 away from the second sub-hole 52 is an arc surface corresponding to the inner wall of the first sub-hole 51. This arc surface can completely fit with the curved surface of the inner hole 53 of the magnetic ring portion 50, increasing the contact area while avoiding excessive local stress, preventing cracks from forming on the inner wall of the magnetic ring portion 50 due to point contact, extending the service life of the magnetic ring, and ensuring the stability of radial fixation.

[0048] In some embodiments, please refer to the following for details. Figure 3 , Figure 4The magnetic ring fixing part 60 further includes a second limiting plate 66. The second limiting plate 66 is disposed on the side of the first sub-hole 51 away from the second sub-hole 52, and is located between the housing of the socket part 20 and the magnetic ring part 50. The end face of the second limiting plate 66 near the magnetic ring part 50 is an arc surface corresponding to and matching the outer cylindrical surface of the magnetic ring part 50, and the end face of the second limiting plate 66 near the magnetic ring part 50 abuts against the outer cylindrical peripheral wall of the magnetic ring part 50. The second limiting plate 66, disposed on the side of the first sub-hole 51 away from the second sub-hole 52, cooperates with the housing of the socket part 20 to form a limiting position from the outside of the magnetic ring part 50, and forms a clamping fixing effect with the inner first protrusion 62, further restricting the radial displacement of the magnetic ring part 50, especially suitable for scenarios where the equipment is subjected to strong vibrations. Meanwhile, the arc surface of the second limiting plate 66 fits against the outer cylindrical peripheral wall of the magnetic ring part 50, avoiding wear of the outer wall of the magnetic ring part 50 by the rigid edges, and dispersing the contact stress to protect the integrity of the magnetic ring part 50 structure.

[0049] In some embodiments, please refer to the following for details. Figure 5 The host 11 includes a control element 12. The electrode wire 40 includes a first portion 41 passing through the inner hole 53 of the magnetic ring portion 50, a second portion 42 surrounding the outer wall of the magnetic ring portion 50, and a third portion 43 connected to the control element 12. The extension direction of the second portion 42 is parallel to the axial direction of the magnetic ring portion 50. The second portion 42 of the electrode wire 40, surrounding the outer wall of the magnetic ring portion 50 and parallel to the axial direction, increases the coupling length between the wire and the magnetic ring portion 50, allowing the alternating magnetic field generated by high-frequency electromagnetic interference to be more fully absorbed by the magnetic ring, enhancing energy loss and further improving the suppression capability against high-frequency interference. Simultaneously, the electrode wire 40 is wound around the magnetic ring portion 50, avoiding signal interference or wire wear caused by messy entanglement, and shortening the connection path with the control element 12. Utilizing the effective absorption of high-frequency interference by the magnetic ring portion 50, the stability and accuracy of signal transmission are ensured.

[0050] Specifically, the control element 12 may include control processing components such as a printed circuit board, a microprocessor, and a filter circuit. The microprocessor may be integrated on the printed circuit board for data processing, and the filter circuit may purify the input signal to ensure the accurate execution of control commands, further optimize the system response speed and stability, and improve the overall anti-interference performance.

[0051] Although the present invention has been disclosed above, its protection scope is not limited thereto. Those skilled in the art can make various changes and modifications without departing from the spirit and scope of the present invention, and all such changes and modifications will fall within the protection scope of the present invention.

Claims

1. An automated external defibrillator, characterized in that, Includes a main unit (11) and a socket portion (20) disposed on the main unit (11); the socket portion (20) includes: Electrode connection part (30) is used to connect an external electrode plate (70); Electrode wire (40), the electrode wire (40) is electrically connected to the electrode connection part (30); The magnetic ring portion (50) has at least a portion of the electrode wire (40) passing through the inner hole (53) of the magnetic ring portion (50).

2. The automated external defibrillator according to claim 1, characterized in that, The automated external defibrillator (10) also includes a magnetic ring fixing part (60), which is connected to the housing of the socket part (20); The magnetic ring fixing part (60) includes two first limiting plates (61) arranged at a relative interval and a first protrusion (62) provided on the opposite surface of the two first limiting plates (61). Wherein, the extension direction of the first limiting plate (61) is perpendicular to the axial direction of the magnetic ring part (50), the first limiting plate (61) abuts against the end face of the magnetic ring part (50), and the first protrusion (62) abuts against the inner wall of the magnetic ring part (50) to fix the magnetic ring part (50).

3. The automated external defibrillator according to claim 2, characterized in that, The inner hole (53) of the magnetic ring portion (50) includes a first sub-hole (51) and a second sub-hole (52), both of which penetrate the magnetic ring portion (50) along the axial direction of the magnetic ring portion (50). The first sub-hole (51) is located between the two first limiting plates (61), the first protrusion (62) abuts against the inner wall of the first sub-hole (51), the second sub-hole (52) is located outside the two first limiting plates (61), and the electrode wire (40) passes through the second sub-hole (52).

4. The automated external defibrillator according to claim 3, characterized in that, The first protrusion (62) has a first wedge-shaped portion (63) at one end near the second sub-hole (52). The thickness of the first wedge-shaped portion (63) gradually increases in the direction from the second sub-hole (52) to the first sub-hole (51).

5. The automated external defibrillator according to claim 4, characterized in that, The wedge angle of the first wedge (63) is 10° to 25°.

6. The automated external defibrillator according to claim 4, characterized in that, The end of the first protrusion (62) away from the second sub-hole (52) is the first end (64), and the thickness of the first end (64) remains unchanged in the direction from the second sub-hole (52) to the first sub-hole (51).

7. The automated external defibrillator according to claim 4, characterized in that, The end of the first protrusion (62) away from the second sub-hole (52) is a second wedge (65), and the thickness of the second wedge (65) gradually decreases in the direction from the second sub-hole (52) to the first sub-hole (51).

8. The automated external defibrillator according to any one of claims 3 to 7, characterized in that, The end face of the first protrusion (62) away from the second sub-hole (52) is an arc surface corresponding to the inner wall of the first sub-hole (51).

9. The automated external defibrillator according to any one of claims 3 to 7, characterized in that, The magnetic ring fixing part (60) further includes a second limiting plate (66), which is located on the side of the first sub-hole (51) away from the second sub-hole (52) and is located between the housing of the socket part (20) and the magnetic ring part (50). The end face of the second limiting plate (66) near the magnetic ring part (50) is an arc surface that corresponds to and matches the outer cylindrical surface of the magnetic ring part (50), and the end face of the second limiting plate (66) near the magnetic ring part (50) abuts against the outer cylindrical peripheral wall of the magnetic ring part (50).

10. The automated external defibrillator according to any one of claims 1-7, characterized in that, The host (11) includes a control element (12); The electrode wire (40) includes a first part (41) passing through the inner hole (53) of the magnetic ring part (50), a second part (42) surrounding the outer wall of the magnetic ring part (50), and a third part (43) connected to the control element (12). The extension direction of the second part (42) is parallel to the axial direction of the magnetic ring part (50).

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