Analyte detection sensor system

Abstract

The invention relates to an analyte detection sensor system, and belongs to the technical field of medical instruments. The sensor unit comprises a sensor probe, a conductive electrode, a battery, a bottom plate and a guide needle, the sensor probe is vertically connected with the conductive electrode, the sensor probe penetrates through the bottom plate, the conductive electrode and the battery to be arranged on the bottom plate, and a glue groove is formed in the periphery of the conductive electrode; the guide needle is coupled with the sensor probe and guides the sensor probe to be implanted into the skin; a connector unit for connecting the sensor unit and the transmitter unit; and the transmitter unit comprises a first conductive part and a second conductive part, the first conductive part is connected with the rigid part, and the second conductive part is connected with the battery. The excitation interval between the inner needle and the outer needle can be adjusted by controlling the pressing block, so that the excitation efficiency and stability are improved.

Description

Technical Field

[0001] This application relates to the technical field of medical devices, and particularly to an analyte detection sensor system. Background Art

[0002] With the continuous development of medical technology, continuous health monitoring systems play an increasingly important role in disease management and health maintenance. For example, diabetic patients can take appropriate actions by continuously monitoring glucose levels, such as administering insulin or consuming specific foods or beverages at appropriate times based on analyte levels or trends. Similarly, other analytes can be used to monitor different physiological conditions, or in some cases, multiple analytes can be used simultaneously to monitor multiple physiological conditions.

[0003] To achieve continuous monitoring, it is usually necessary to implant one or more sensors at least partially into an individual's tissue, such as dermis, subcutaneous, or intravenous, for in vivo analysis. These implanted sensors can collect analyte data on demand, according to a set schedule, or continuously, based on an individual's specific health needs and / or previously measured analyte levels. However, traditional analyte detection sensor systems have some significant technical problems in design and function, which affect their reliability and accuracy.

[0004] Insufficient guidance accuracy: In traditional structures, the movement of the sensor probe and the conductive electrode will affect the guidance accuracy between the puncture needle and the sensor probe, resulting in the sensor probe deviating from the puncture needle, thus affecting the correct implantation of the sensor and the accuracy of the data.

[0005] Unreliable contact method: The contact method between the connector spring piece and the electrode is unreliable, which may lead to unstable signal transmission, thereby affecting the stability and accuracy of the detection results.

[0006] Poor waterproof performance: The waterproof performance of traditional analyte detection sensor systems is unreliable. Loose sealing may cause liquid to seep in, affecting the accuracy of the detection data and even damaging the internal electronic components.

[0007] These above problems limit the performance and reliability of traditional analyte detection sensor systems. Summary of the Invention

[0008] Based on this, this application provides an analyte detection sensor system to improve the guidance accuracy, contact reliability, and waterproof performance of the sensor, thereby ensuring the stability and accuracy of the continuous health monitoring system.

[0009] To solve the above problems, the present invention provides an analyte detection sensor system, including:

[0010] The sensor unit includes a sensor probe, a conductive electrode, a battery, a base plate, and a guiding needle. The sensor probe is perpendicularly connected to the conductive electrode. The sensor probe penetrates through the base plate. The conductive electrode and the battery are placed on the base plate, and a glue groove is provided around the conductive electrode. The guiding needle is coupled with the sensor probe to guide the sensor probe to be implanted into the skin.

[0011] The connector unit is used to connect the sensor unit and the transmitter unit. The connector unit includes a base and at least one metal elastic piece. The metal elastic piece includes an elastic part and a rigid part. The elastic part is connected to the conductive electrode. The metal elastic piece is placed on the base. The base includes a proximal end face and a distal end face. The proximal end face contacts the transmitter unit. The distal end face is located in the glue groove and is fixed to the base plate after dispensing glue, sealing the elastic part and the conductive electrode.

[0012] The transmitter unit includes a first conductive part and a second conductive part. The first conductive part is connected to the rigid part. The second conductive part is connected to the battery. An elastic first sealing part is provided around the first conductive part, and an elastic second sealing part is provided around the second conductive part.

[0013] Further, after the transmitter unit is buckled with the sensor unit, the elastic first sealing part contacts and is compressed by the proximal end face to achieve sealing of the sensor probe. The elastic second sealing part contacts and is compressed by the base plate to achieve sealing of the battery.

[0014] Further, it further includes an applicator assembly to direct the sensor unit towards the skin.

[0015] Further, the transmitter unit further includes a signal processing unit to receive the biological information sent by the sensor unit, process the biological information, and send it to the outside.

[0016] Further, the conductive electrode is perpendicular to the base plate and is connected to the base plate in a keyway manner. The electrode contact is located on the side of the conductive electrode. The elastic parts are distributed on both sides of the conductive electrode and contact the electrode contacts.

[0017] Further, the base is made of plastic material, the metal elastic piece is embedded in the base, and the elastic part and the rigid part are sealed through the glue groove and the elastic first sealing part respectively.

[0018] Further, the sensor unit further includes a first buckle and a second buckle, and the transmitter unit further includes a first locking groove and a second locking groove.

[0019] After the emitter unit is latched with the sensor unit, the first latch is latched with the first latch groove, and the second latch is latched with the second latch groove;

[0020] A wrench is provided on the first latch and / or the second latch. By pulling the wrench, the disassembly between the emitter unit and the sensor unit can be achieved.

[0021] Furthermore, the sensor unit further includes an adhesive tape, which includes a first adhesive surface connected to the bottom plate and a second adhesive surface adhered to the skin.

[0022] Furthermore, the applicator assembly includes:

[0023] A driving unit, initially in a pre-loaded state;

[0024] A pressing unit. Pressing the pressing unit can release the potential energy of the driving unit;

[0025] A sensor unit, including a sensor probe and a guiding needle. The guiding needle is coupled with the sensor probe to guide the sensor probe to be implanted into the skin;

[0026] A moving unit, which drives the sensor unit to move towards the skin under the push of the driving unit;

[0027] A needle-withdrawing unit, initially in an unloaded state, at least a part of which is coupled with the moving unit and at least a part of which is coupled with the guiding needle;

[0028] During the process of the moving unit moving towards the skin, the needle-withdrawing unit is continuously loaded. When the sensor unit reaches the implantation position on the skin, the coupling states of the needle-withdrawing unit with the moving unit and the sensor unit are all broken; the sensor unit stays on the skin, the guiding needle guides the sensor probe to be implanted into the skin, and the potential energy loaded on the needle-withdrawing unit is released. Then, the needle-withdrawing unit drives the guiding needle to move away from the skin.

[0029] Furthermore, it further includes an inner shell, which includes an inner shell sleeve and inner shell claws; the pressing unit is placed outside the inner shell sleeve and abuts against the inner shell claws;

[0030] The needle-withdrawing unit includes a needle-withdrawing spring and a needle-withdrawing seat. The initial state of the needle-withdrawing spring is a free state. One end of the needle-withdrawing spring contacts the inner wall of the inner shell sleeve, and the other end contacts the needle-withdrawing seat;

[0031] The bottom of the needle-withdrawing seat is connected to the sensor unit.

[0032] Furthermore, the moving unit includes a moving seat hook and a moving seat arm; one end of the inner shell claw is provided with an inner shell hook;

[0033] In the initial state, the moving seat clamping arm is clamped on the needle withdrawing seat and is entirely placed in the inner shell sleeve; the moving unit abuts against the bottom of the needle withdrawing seat, the moving seat hook is clamped with the inner shell hook, and the guiding needle passes through the needle withdrawing seat; one end of the driving unit contacts the outer wall of the inner shell sleeve, and the other end contacts the moving unit.

[0034] Act on the pressing unit, the inner shell claw is pressed, and thus the clamping connection between the moving seat hook and the inner shell hook is released; the driving unit drives the moving unit to drive the needle withdrawing seat to move synchronously towards the skin direction, and the needle withdrawing spring continuously stores elastic potential energy; when the moving unit drives the sensor unit to reach the skin position, the sensor unit leaves the bottom of the needle withdrawing seat and stays on the skin, and the guiding needle guides the sensor probe to be implanted into the skin.

[0035] The moving seat clamping arm disengages from the inner shell sleeve, and thus the clamping connection between the moving seat clamping arm and the needle withdrawing seat is released; the elastic potential energy of the needle withdrawing spring drives the needle withdrawing seat to move away from the skin direction, and thus the needle withdrawing seat drives the guiding needle to withdraw from the skin.

[0036] Furthermore, it further includes an upper shell, a lower shell, a first seal and a second seal.

[0037] The pressing unit and the inner shell are placed in the upper shell, and the first seal is arranged between one end of the pressing unit and the upper shell; a support rib is arranged in the lower shell.

[0038] In the initial state, the upper shell and the lower shell are sealed through the second seal, so as to form a sealed cavity between the upper shell and the lower shell; the support rib in the lower shell is coupled with the other end of the pressing unit, and the pressing unit is limited; after removing the lower shell, the support rib in the lower shell is decoupled from the other end of the pressing unit, exciting the pressing unit, and the sensor unit can be fired.

[0039] Compared with the prior art, the present invention has the following beneficial effects:

[0040] The conductive electrode of the present invention is perpendicular to the bottom plate and is connected to the bottom plate by a keyway connection. The electrode contact is located on the side of the conductive electrode, and the elastic parts are distributed on both sides of the conductive electrode and are in contact with the electrode contact. First, it improves the guiding accuracy: by optimizing the guiding structure of the puncture needle and the sensor probe, the present invention significantly reduces the risk of deviation of the sensor probe during the implantation process, ensuring that the sensor can be accurately and stably implanted into the target tissue (such as dermis, subcutaneous or intravenous), thereby improving the reliability of the monitoring data. Second, it enhances the contact reliability: the present invention improves the contact method between the connector spring piece and the electrode, adopts a more stable connection design, ensures the continuity and stability of signal transmission, avoids data fluctuations or errors caused by poor contact in the traditional structure, and significantly improves the accuracy of the detection results. BRIEF DESCRIPTION OF THE DRAWINGS

[0041] Figure 1 Schematic diagram of the structure of the sensor unit in an embodiment of the present invention;

[0042] Figure 2 Schematic diagram of the cooperation relationship between the sensor unit and the guiding needle in an embodiment of the present invention;

[0043] Figure 3 Schematic diagram of the structure of the connector unit in an embodiment of the present invention;

[0044] Figure 4 Schematic diagram of the structure of the transmitter unit in an embodiment of the present invention;

[0045] Figure 5 Schematic diagram of the cooperation relationship between the sensor unit and the transmitter unit in an embodiment of the present invention;

[0046] Figure 6 Schematic diagram of the assembly between the sensor unit and the transmitter unit in an embodiment of the present invention;

[0047] Figure 7 Schematic diagram of the assembly between the sensor unit, the connector unit and the transmitter unit in an embodiment of the present invention;

[0048] Figure 8(a) is a schematic diagram of the structure of the applicator assembly in State 1 according to an embodiment of the present invention;

[0049] Figure 8(b) is a schematic diagram of the structure of the applicator assembly in State 2 according to an embodiment of the present invention;

[0050] Figure 8(c) is a schematic diagram of the structure of the applicator assembly in State 3 according to an embodiment of the present invention;

[0051] Figure 8(d) is a schematic diagram of the structure of the applicator assembly in State 4 according to an embodiment of the present invention;

[0052] Figure 9 Exploded view of the external structure of the applicator assembly according to an embodiment of the present invention;

[0053] Figure 10(a) is a schematic structural diagram of the applicator assembly in State 1 according to another embodiment of the present invention;

[0054] Figure 10(b) is a schematic structural diagram of the applicator assembly in State 2 according to another embodiment of the present invention;

[0055] Figure 10(c) is a schematic structural diagram of the applicator assembly in State 3 according to another embodiment of the present invention;

[0056] Wherein: the driving unit 1, the pressing unit 2, the sensor unit 3, the sensor probe 31, the guiding needle 32, the first latch 33 and the second latch 34, the wrench 35, the moving unit 4, the moving seat hook 41, the moving seat clamping arm 42, the inner shell 5, the inner shell sleeve 51, the inner shell claw 52, the inner shell hook 521, the needle withdrawal spring 61, the needle withdrawal seat 62, the upper outer shell 71, the first seal 711, the lower outer shell 72, the second seal 712, the conductive electrode 311, the battery 312, the bottom plate 313, the glue groove 314, the adhesive tape 315, the first bonding surface 3151, the second bonding surface 3152, the connector unit 21, the base 211, the proximal end surface 2111, the distal end surface 2112, the metal elastic sheet 212, the elastic part 2121, the rigid part 2122, the transmitter unit 11, the first conductive part 111, the elastic first seal part 1111, the second conductive part 112, the elastic second seal part 1121, the first lock groove 113, the second lock groove 114. Detailed implementation manners

[0057] The following further describes the present application in detail with reference to the accompanying drawings and embodiments. It should be understood that the specific embodiments described herein are only used to explain the present application and are not used to limit the present application.

[0058] An analyte detection sensor system provided by an embodiment of the present application includes:

[0059] The sensor unit 3, as Figure 5 , Figure 1 and Figure 2 shown, includes a sensor probe 31, a conductive electrode 311, a battery 312, a bottom plate 313 and a guiding needle 32. The sensor probe 31 is perpendicularly connected to the conductive electrode 311. The sensor probe 31 passes through the bottom plate 313. The conductive electrode 311 and the battery 312 are placed on the bottom plate 313, and a glue groove 314 is provided around the conductive electrode 311; the guiding needle 32 is coupled with the sensor probe 31 to guide the sensor probe 31 to be implanted into the skin;

[0060] Explanatorily, the sensor probe 31 penetrates through the bottom plate 313 to ensure that it can be accurately implanted into the skin to collect target physiological data such as blood glucose; the sensor probe 31 is made of biocompatible materials such as polymer materials to ensure its safety for the human body and the stability of long-term use. Exemplarily, micropores or microgrooves are designed on the surface of the sensor probe 31 to improve the sensitivity and accuracy of signal collection.

[0061] Explanatorily, the conductive electrode 311 is perpendicularly connected to the sensor probe 31 to ensure the shortest signal transmission path, reducing signal attenuation and interference. The electrode contacts are located on both side surfaces of the conductive electrode 311, which can better shield external electromagnetic interference, improve the signal-to-noise ratio of the signal, and at the same time reduce direct contact with the skin.

[0062] Explanatorily, the glue groove 314 is located around the conductive electrode 311 and is used to fill the sealant to ensure a firm and sealed connection between the conductive electrode 311 and the bottom plate 313, so as to improve the waterproof performance.

[0063] The connector unit 21, such as Figure 2 as shown in FIG. 3, is used to connect the sensor unit 3 and the transmitter unit 11; the connector unit 21 includes a base 211 and at least one metal elastic sheet 212. The metal elastic sheet 212 includes an elastic portion 2121 and a rigid portion 2122, and the elastic portion 2121 is connected to the conductive electrode 311; the metal elastic sheet 212 is placed on the base 211. The base 211 includes a proximal end surface 2111 and a distal end surface 2112. The proximal end surface 2111 contacts the transmitter unit 11, and the distal end surface 2111 is located in the glue groove 314 and is fixed to the bottom plate 313 after dispensing glue to seal the elastic portion 2121 and the conductive electrode 311;

[0064] Exemplarily, the distal end surface 2112 is located in the glue groove 314 and is fixed to the bottom plate 313 by dispensing glue to ensure a firm and sealed connection between the connector unit 21 and the sensor unit 3. Exemplarily, diversion grooves or grooves can be designed on the distal end surface 2112 to facilitate the uniform distribution of glue and improve the sealing effect.

[0065] Exemplarily, the elastic portion 2121 is made of a highly elastic material such as phosphor bronze or beryllium copper to ensure that it can still maintain good elasticity after multiple connections and disconnections.

[0066] Explanatorily, the rigid portion 2122 is used to support the elastic portion 2121 to ensure that the metal elastic sheet 212 will not undergo permanent deformation when stressed. The rigid portion 2122 is fixed to the base 211 to ensure the stable position of the metal elastic sheet 212.

[0067] Preferably, the contact surface of the metal elastic sheet 212 is subjected to plating treatment such as gold plating or silver plating to improve its conductivity and corrosion resistance.

[0068] Explanatorily, the physiological data collected by the sensor probe 31 is transmitted through the conductive electrode 311 to the metal shrapnel 212, and then through the connector unit 21 to the transmitter unit 11.

[0069] The transmitter unit 11, as Figure 4 shown, includes a first conductive part 111 and a second conductive part 112. The first conductive part 111 is connected to the rigid part 2122, and the second conductive part 112 is connected to the battery 312. An elastic first sealing part 1111 is arranged around the first conductive part 111, and an elastic second sealing part 1121 is arranged around the second conductive part 112. After the transmitter unit 11 is buckled with the sensor unit 3, the elastic first sealing part 1111 contacts and is compressed by the proximal end surface 2111 to achieve the sealing of the sensor probe 31. The elastic second sealing part 1121 contacts and is compressed by the bottom plate 313 to achieve the sealing of the battery 312.

[0070] Exemplarily, the first conductive part 111 is designed as a flat or needle-like structure to facilitate close contact with the rigid part 2122 and reduce the contact resistance. The elastic first sealing part 1111 is located around the first conductive part 111 and is made of a material with elastic properties such as silica gel or rubber. After the transmitter unit 11 is buckled with the sensor unit 3, the elastic first sealing part 1111 contacts and is compressed by the proximal end surface 2111 to achieve the sealing of the sensor probe 31 and prevent moisture, dust, etc. from entering.

[0071] Exemplarily, the second conductive part 112 is designed as a spring pin or elastic contact structure to facilitate close contact with the battery 312 and reduce the contact resistance. The elastic second sealing part 1121 is located around the second conductive part 112 and is made of a material with elastic properties such as silica gel or rubber. After the transmitter unit 11 is buckled with the sensor unit 3, the elastic second sealing part 1121 contacts and is compressed by the bottom plate 313 to achieve the sealing of the battery 312 and prevent moisture, dust, etc. from entering.

[0072] By adopting the above embodiments, on the one hand, the risk of deviation of the sensor probe during implantation is reduced, ensuring that the sensor can be accurately and stably implanted into the target tissue, such as the dermis, subcutaneous tissue or vein, thereby improving the reliability of the monitoring data. On the other hand, the contact mode between the connector spring piece and the electrode is improved, ensuring the continuity and stability of signal transmission, avoiding data fluctuations or errors caused by poor contact in the traditional structure, and significantly improving the accuracy of the detection results.

[0073] As an embodiment, it further includes an applicator assembly for guiding the sensor unit 3 to the skin.

[0074] As an embodiment, the transmitter unit 11 further includes a signal processing unit, which receives the biological information sent by the sensor unit 3, processes the biological information and sends it to the outside.

[0075] As an embodiment, the conductive electrode 311 is perpendicular to the bottom plate 313 and is connected to the bottom plate 313 in a keyway connection. The electrode contact is located on the side surface of the conductive electrode 311. The elastic parts 2121 are distributed on both sides of the conductive electrode 311 and are in contact with the electrode contacts. Exemplarily, the proximal end surface 2111 is designed with a positioning structure, such as a protrusion or a groove, to ensure accurate and stable connection with the transmitter unit 11 and prevent relative sliding.

[0076] As an embodiment, the base 211 is made of plastic, and the metal elastic sheet 212 is embedded in the base 211. The elastic part 2121 and the rigid part 2122 are sealed through the glue groove 314 and the elastic first sealing part 1111 respectively.

[0077] As an explanation, the base 211 is made of high-strength and corrosion-resistant engineering plastics, such as POM, PC or ABS, to ensure its mechanical strength and durability. In addition, the plastic material has good insulation performance, which can effectively isolate the metal elastic sheet 212 from the external environment and prevent short circuits.

[0078] As an embodiment, the sensor unit 3 further includes a first latch 33 and a second latch 34, and the transmitter unit 11 further includes a first lock groove 113 and a second lock groove 114; after the transmitter unit 11 is buckled with the sensor unit 3, the first latch 33 is buckled with the first lock groove 113, and the second latch 34 is buckled with the second lock groove 114; a wrench 35 is provided on the first latch and / or the second latch. By pulling the wrench 35, the disassembly between the transmitter unit 11 and the sensor unit 3 can be realized.

[0079] As an embodiment, the sensor unit further includes an adhesive tape 315, which includes a first adhesive surface 3151 connected to the bottom plate 313 and a second adhesive surface 3152 adhered to the skin.

[0080] As an embodiment, the applicator assembly includes:

[0081] The specific scheme is shown in Figure 8(a) and includes:

[0082] A driving unit 1, initially in a pre-loaded state, capable of providing elastic potential energy;

[0083] A pressing unit 2, pressing the pressing unit 2 can release the elastic potential energy of the driving unit 1;

[0084] A sensor unit 3, including a sensor probe 31 and a guide needle 32. The guide needle 32 is coupled with the sensor probe 31 to guide the sensor probe 31 to implant into the skin;

[0085] A motion unit 4, driven by the driving unit 1 to move the sensor unit 3 towards the skin;

[0086] The needle-withdrawal unit is initially in an unloaded state, at least a part of which is coupled to the motion unit 4 and at least a part of which is coupled to the guiding needle 32.

[0087] During the process of the motion unit 4 moving towards the skin, the needle-withdrawal unit is continuously loaded. When the sensor unit 3 reaches the implantation position on the skin, the coupling states of the needle-withdrawal unit with the motion unit 4 and the sensor unit 3 are both broken. As shown in FIG. 8(c), the sensor unit 3 stays on the skin, the guiding needle 32 guides the sensor probe 31 to be implanted into the skin, the potential energy stored in the loaded needle-withdrawal unit is released, and then the needle-withdrawal unit drives the guiding needle 32 to move away from the skin, as shown in FIG. 8(d).

[0088] As an embodiment of the present application, as Figure 9 , it further includes an upper housing 71, a lower housing 72, a first seal 711 and a second seal 712;

[0089] The pressing unit 2 and the inner housing 5 are placed in the upper housing 71, and a first seal 711 is provided between one end of the pressing unit 2 and the upper housing 71; a support rib is provided in the lower housing 72;

[0090] In the initial state, the upper housing 71 and the lower housing 72 are sealed by the second seal 712, so that a sealed cavity is formed between the upper housing 71 and the lower housing 72, and the cavity is sterilized by means such as irradiation, which can provide a sterile environment and block the transmission of microorganisms; the support rib in the lower housing 72 is coupled to the other end of the pressing unit 2, and the pressing unit 2 is limited; after the lower housing 72 is removed, the support rib in the lower housing 72 is decoupled from the other end of the pressing unit 2, the pressing unit 2 is activated, and the sensor unit 3 can be struck and attached to the human skin.

[0091] Traditional springs are prone to performance degradation under long-term compression, resulting in untimely or unstable needle withdrawal. An applicator assembly provided by an embodiment of the present application, through the dynamic loading mechanism of the needle-withdrawal unit, releases potential energy only after the sensor probe is implanted into the skin, ensuring that the guiding needle can be withdrawn from the skin in a timely and stable manner. This design significantly improves the reliability and service life of the device.

[0092] As an embodiment of the present application, the driving unit 1 adopts a high-precision spring or elastic material to ensure that sufficient elastic potential energy can be stably stored in the pre-loaded state. By optimizing the material and structural design of the spring, fatigue and performance degradation caused by long-term compression are avoided.

[0093] As an embodiment of the present application, as shown in Fig. 8(b), the preloading force of the driving unit 1 is adjustable to meet the requirements of different skin thicknesses or implantation depths. Exemplarily, a mechanism for adjusting the pre-tightening force of the spring is used in the driving unit 1, and the compression amount of the spring is changed by rotating or sliding the adjusting component, thereby adjusting the preloading force.

[0094] As an embodiment of the present application, the pressing unit 2 is equipped with a safety locking device to prevent the potential energy of the driving unit 1 from being prematurely released due to accidental touch or accidental pressing, ensuring the safety of the device in the unused state. The safety locking device is preferably a lower housing provided at the bottom of the pressing unit 2, which can block the triggering process of the pressing unit 2 before operation.

[0095] As an embodiment of the present application, under the push of the driving unit 1, the moving unit 4 adopts a linear guide rail or a low-friction sliding mechanism to ensure smooth movement towards the skin direction without jitter, avoiding additional damage to the skin. The moving speed of the moving unit 4 is optimized, neither causing impact due to excessive speed nor affecting the implantation efficiency due to too slow speed.

[0096] Exemplarily, a mechanical limit structure is designed on the moving unit 4 to ensure automatic stop when reaching the implantation position of the skin, avoiding damage to the skin caused by excessive movement, and preferably cooperating with the inner shell sleeve to achieve the limit.

[0097] As an embodiment of the present application, it further includes an inner shell 5, and the inner shell 5 includes an inner shell sleeve 51 and an inner shell claw 52; the pressing unit 2 is placed outside the inner shell sleeve 51 and abuts against the inner shell claw 52.

[0098] Exemplarily, the inner shell sleeve 51 is made of high-strength and lightweight materials, such as aluminum alloy or engineering plastics, to ensure its mechanical strength while reducing the overall weight. Guide grooves or guide rails are designed inside the sleeve inner shell sleeve 51 to guide the movement of the pressing unit 2 and the driving unit 1, ensuring the smoothness and accuracy of the operation process.

[0099] Exemplarily, the inner shell claw 52 is designed as an elastic structure, which can deform within a certain range to ensure that the potential energy release of the driving unit 1 can be smoothly triggered when the pressing unit 2 is pressed. The elastic material of the inner shell claw 52 is preferably a high-performance plastic to ensure its reliability.

[0100] Exemplarily, the contact surface between the pressing unit 2 and the inner shell claw 52 is designed as an arc or an inclined surface to ensure uniform transmission of the pressing force and avoid wear or damage caused by local stress concentration.

[0101] As an embodiment of the present application, the needle withdrawal unit includes a needle withdrawal spring 61 and a needle withdrawal seat 62. The needle withdrawal spring 61 is in a free state in its initial state. One end of the needle withdrawal spring 61 contacts the inner wall of the inner shell sleeve 51, and the other end contacts the needle withdrawal seat 62.

[0102] As a preferred embodiment, the needle withdrawal spring 61 is designed as a tension spring. As Figures 8(a)-8(d) shown, the needle withdrawal spring 61 is in a free state in its initial state. One end is fixed to the inner wall of the inner shell sleeve 51, and the other end is connected to the needle withdrawal seat 62. During the process of the movement unit 4 moving towards the skin, the needle withdrawal seat 62 is pulled, and the tension spring is gradually stretched and stores potential energy; when the sensor unit 3 reaches the implantation position, the potential energy of the tension spring is released, driving the needle withdrawal seat 62 and the guiding needle 32 to quickly withdraw.

[0103] As another preferred embodiment, the needle withdrawal spring 61 is designed as a compression spring. As Figures 10(a)-10(c) shown, the needle withdrawal spring 61 is in a free state in its initial state. One end is fixed to the inner wall of the inner shell sleeve 51, and the other end is connected to the needle withdrawal seat 62. During the process of the movement unit 4 moving towards the skin, the needle withdrawal spring 61 is gradually compressed and stores potential energy; when the sensor unit 3 reaches the implantation position, the potential energy of the needle withdrawal spring 61 is released, pushing the needle withdrawal seat 62 and the guiding needle 32 to quickly withdraw.

[0104] By adopting the above preferred embodiment, during the needle withdrawal process, on the one hand, it avoids the problem of performance attenuation caused by the traditional spring being in a compressed state for a long time, and on the other hand, it can effectively avoid the problem of premature needle withdrawal caused by the action of the spring potential energy, thereby reducing the potential medical risks caused by needle withdrawal failure or premature needle withdrawal.

[0105] As an embodiment of the present application, the movement unit 4 includes a movement seat hook 41 and a movement seat arm 42; one end of the inner shell claw 52 is provided with an inner shell hook 521.

[0106] In the initial state, the movement seat arm 42 is clamped on the needle withdrawal seat 62 and is integrally placed in the inner shell sleeve 51; the movement unit 4 abuts against the bottom of the needle withdrawal seat 62, the movement seat hook 41 is clamped with the inner shell hook 521, and the guiding needle 32 passes through the needle withdrawal seat 62; one end of the driving unit 1 contacts the outer wall of the inner shell sleeve 51, and the other end contacts the movement unit 4. Through the precise cooperation between the movement seat hook 41 and the inner shell hook 521, the movement of the movement unit 4 is ensured to be stable.

[0107] Press the pressing unit 2, the inner shell claw 52 is pressed, and then the engagement between the moving seat hook 41 and the inner shell hook 521 is released; the driving unit 1 drives the moving unit 4 to drive the needle withdrawing seat 62 to move synchronously towards the skin direction, and the needle withdrawing spring 61 continuously stores elastic potential energy; when the moving unit 4 drives the sensor unit 3 to reach the skin position, the sensor unit 3 leaves the bottom of the needle withdrawing seat 62 and stays on the skin, and the guiding needle 32 guides the sensor probe 31 to be implanted into the skin, and the moving seat arm 42 disengages from the inner shell sleeve 51, and then the engagement between the moving seat arm 42 and the needle withdrawing seat 62 is released; the elastic potential energy of the needle withdrawing spring 61 drives the needle withdrawing seat 62 to move away from the skin direction, and then the needle withdrawing seat 62 drives the guiding needle 32 to withdraw from the skin. The user only needs to press the pressing unit 2 to automatically complete a series of operations of driving, moving and needle withdrawing, which simplifies the operation process and improves the user experience.

[0108] Exemplarily, when in use, the operation process of the applicator assembly is as follows:

[0109] Remove the lower housing 72 and attach the bottom of the remaining applicator assembly to the skin;

[0110] Press the pressing unit 2, and the inner shell hook 521 expands outwards;

[0111] The driving unit 1 pushes the moving unit 4 to drive the sensor unit 3 to move towards the skin;

[0112] The needle withdrawing seat 62 is held by the moving seat arm 42 and moves together with the moving unit 4;

[0113] The needle withdrawing spring 61 is initially in a free state. As the needle withdrawing seat 62 moves towards the skin, the needle withdrawing spring 61 is stretched and has potential energy;

[0114] In the first half of the movement, the moving seat arm 42 is held by the inner shell sleeve 51 and cannot deform. The needle withdrawing seat 62 is held by the moving seat arm 42, and the needle withdrawing spring 61 continues to be stretched;

[0115] When the moving unit 4 drives the sensor unit 3 to reach the skin position, the moving seat arm 42 disengages from the inner shell sleeve 51;

[0116] The potential energy of the needle withdrawing spring 61 pulls the needle withdrawing seat 62 to move away from the skin direction. The moving seat arm 42 deforms so that the needle withdrawing seat 62 disengages from the moving unit 4, and then continues to move backward to complete needle withdrawal.

[0117] It should be noted that in this application, the term "comprising" or any other variant thereof is intended to cover non-exclusive inclusion, such that a method, article, or device comprising a series of elements includes not only those elements but also other elements not expressly listed, or elements inherent to such article or device. Without further limitation, an element defined by the statement "comprising..." does not preclude the presence of additional identical elements in the method, article, or device comprising said element.

[0118] In the description of this application, unless otherwise clearly defined, terms such as "set", "installed", "connected", etc. should be understood in a broad sense, and those skilled in the art can reasonably determine the specific meanings of the above terms in this application in combination with the specific content of the technical solution.

[0119] The various embodiments in this specification are described in a progressive manner. Each embodiment focuses on the differences from other embodiments. For the same or similar parts among the various embodiments, reference can be made to each other.

[0120] Specific examples are used in this application to illustrate the principles and implementation manners of the present invention. The descriptions of the above embodiments are only used to help understand the method and its core idea of the present invention. It should be noted that for those of ordinary skill in the art, various modifications, combinations, sub-combinations, and substitutions can be made without departing from the principles of the present invention. Any modifications, equivalent substitutions, and improvements made within the spirit and principles of this application shall be included within the protection scope of this application.

Claims

1. An analyte detection sensor system, characterized in that, Comprising: A sensor unit (3), including a sensor probe (31), a conductive electrode (311), a battery (312), a base plate (313) and a guide needle (32). The sensor probe (31) is perpendicularly connected to the conductive electrode (311). The sensor probe (31) passes through the base plate (313). The conductive electrode (311) and the battery (312) are placed on the base plate (313), and a glue groove (314) is provided around the conductive electrode (311). The guide needle (32) is coupled with the sensor probe (31) to guide the sensor probe (31) to be implanted into the skin. A connector unit (21) for connecting the sensor unit (3) and the transmitter unit (11). The connector unit (21) includes a base (211) and at least one metal elastic sheet (212). The metal elastic sheet (212) includes an elastic part (2121) and a rigid part (2122). The elastic part (2121) is connected to the conductive electrode (311). The metal elastic sheet (212) is placed on the base (211). The base (211) includes a proximal end face (2111) and a distal end face (2112). The proximal end face (2111) contacts the transmitter unit (11), and the distal end face (2111) is located in the glue groove (314) and is fixed to the base plate (313) after dispensing glue, so as to seal the elastic part (2121) and the conductive electrode (311). A transmitter unit (11), including a first conductive part (111) and a second conductive part (112). The first conductive part (111) is connected to the rigid part (2122), and the second conductive part (112) is connected to the battery (312). An elastic first sealing part (1111) is provided around the first conductive part (111), and an elastic second sealing part (1121) is provided around the second conductive part (112).

2. The analyte detection sensor system according to claim 1, wherein, After the transmitter unit (11) is buckled with the sensor unit (3), the elastic first sealing part (1111) contacts and is compressed by the proximal end face (2111) to realize the sealing of the sensor probe (31). The elastic second sealing part (1121) contacts and is compressed by the base plate (313) to realize the sealing of the battery (312).

3. The analyte detection sensor system according to claim 1, wherein It further includes an applicator assembly for guiding the sensor unit (3) to the skin.

4. The analyte detection sensor system according to claim 1, wherein The transmitter unit (11) further includes a signal processing unit, which receives the biological information sent by the sensor unit (3), processes the biological information and sends it to the outside.

5. The analyte detection sensor system according to claim 2, wherein The conductive electrode (311) is perpendicular to the base plate (313) and is connected to the base plate (313) in a keyway connection. The electrode contact is located on the side of the conductive electrode (311). The elastic parts (2121) are distributed on both sides of the conductive electrode (311) and contact the electrode contacts.

6. The analyte detection sensor system according to claim 2, wherein The base (211) is made of plastic, the metal shrapnel (212) is embedded in the base (211), and the elastic part (2121) and the rigid part (2122) are sealed through the glue groove (314) and the elastic first sealing part (1111) respectively.

7. The analyte detection sensor system according to claim 1, wherein The sensor unit (3) further includes a first latch (33) and a second latch (34), and the transmitter unit (11) further includes a first locking groove (113) and a second locking groove (114); After the transmitter unit (11) is latched with the sensor unit (3), the first latch (33) is latched with the first locking groove (113), and the second latch (34) is latched with the second locking groove (114); A wrench (35) is provided on the first latch and / or the second latch. By pulling the wrench (35), the disassembly between the transmitter unit (11) and the sensor unit (3) can be achieved.

8. The analyte detection sensor system according to claim 1, wherein The sensor unit further includes an adhesive tape (315), which includes a first adhesive surface (3151) connected to the bottom plate (313); and a second adhesive surface (3152) adhered to the skin.

9. The analyte detection sensor system according to claim 3, wherein The applicator assembly includes: A driving unit (1), initially in a pre-loaded state; A pressing unit (2). Pressing the pressing unit (2) can release the potential energy of the driving unit (1); A sensor unit (3), including a sensor probe (31) and a guide needle (32). The guide needle (32) is coupled with the sensor probe (31) to guide the sensor probe (31) to be implanted into the skin; A motion unit (4), which moves the sensor unit (3) towards the skin under the push of the driving unit (1); A needle withdrawal unit, initially in an unloaded state, at least a part of which is coupled with the motion unit (4) and at least a part of which is coupled with the guide needle (32); During the process of the motion unit (4) moving towards the skin, the needle withdrawal unit is continuously loaded. When the sensor unit (3) reaches the implantation position on the skin, the coupling states of the needle withdrawal unit with the motion unit (4) and the sensor unit (3) are both broken; the sensor unit (3) stays on the skin, the guide needle (32) guides the sensor probe (31) to be implanted into the skin, and the potential energy loaded on the needle withdrawal unit is released. Then, the needle withdrawal unit drives the guide needle (32) to move away from the skin.

10. The analyte detection sensor system according to claim 9, wherein It further includes an inner shell (5), and the inner shell (5) includes an inner shell sleeve (51) and inner shell claws (52); the pressing unit (2) is placed outside the inner shell sleeve (51) and abuts against the inner shell claws (52); The needle withdrawal unit includes a needle withdrawal spring (61) and a needle withdrawal seat (62). The initial state of the needle withdrawal spring (61) is a free state. One end of the needle withdrawal spring (61) contacts the inner wall of the inner shell sleeve (51), and the other end contacts the needle withdrawal seat (62); The bottom of the needle withdrawal seat (62) is connected to the sensor unit (3).

11. The analyte detection sensor system according to claim 9, wherein, The movement unit (4) includes a movement seat hook (41) and a movement seat arm (42); one end of the inner shell claw (52) is provided with an inner shell hook (521); In the initial state, the movement seat arm (42) is clamped on the needle withdrawal seat (62) and is entirely placed in the inner shell sleeve (51); the movement unit (4) abuts against the bottom of the needle withdrawal seat (62), the movement seat hook (41) is clamped with the inner shell hook (521), and the guiding needle (32) passes through the needle withdrawal seat (62); one end of the driving unit (1) contacts the outer wall of the inner shell sleeve (51), and the other end contacts the movement unit (4); When the pressing unit (2) is actuated, the inner shell claw (52) is pressed, and thus the clamping connection between the movement seat hook (41) and the inner shell hook (521) is released; the driving unit (1) drives the movement unit (4) to drive the needle withdrawal seat (62) to move synchronously towards the skin direction, and the needle withdrawal spring (61) continuously stores elastic potential energy; when the movement unit (4) drives the sensor unit (3) to reach the skin position, the sensor unit (3) leaves the bottom of the needle withdrawal seat (62) and stays on the skin, and the guiding needle (32) guides the sensor probe (31) to be implanted into the skin; The movement seat arm (42) disengages from the inner shell sleeve (51), and thus the clamping connection between the movement seat arm (42) and the needle withdrawal seat (62) is released; the elastic potential energy of the needle withdrawal spring (61) drives the needle withdrawal seat (62) to move away from the skin direction, and thus the needle withdrawal seat (62) drives the guiding needle (32) to withdraw from the skin.

12. The analyte detection sensor system according to any one of claims 1-11, characterized in that, It further includes an upper outer shell (71), a lower outer shell (72), a first seal (711), and a second seal (712); The pressing unit (2) and the inner shell (5) are placed in the upper outer shell (71), and the first seal (711) is arranged between one end of the pressing unit (2) and the upper outer shell (71); support ribs are arranged in the lower outer shell (72); In the initial state, the upper outer shell (71) and the lower outer shell (72) are sealed by the second seal (712), so as to form a sealed cavity between the upper outer shell (71) and the lower outer shell (72); the support ribs in the lower outer shell (72) are coupled with the other end of the pressing unit (2), and the pressing unit (2) is limited; after the lower outer shell (72) is removed, the support ribs in the lower outer shell (72) are decoupled from the other end of the pressing unit (2), triggering the pressing unit (2), and the sensor unit (3) can be fired.

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