In-vivo blood glucose monitoring device

Abstract

Disclosed in the present application is an in-vivo blood glucose monitoring device, which comprises a housing, a bottom cover, a puncture unit, and an in-vivo monitoring unit. The housing is provided with a first end and a second end which are oppositely arranged along a first direction, and an implantation opening is formed in the second end. The bottom cover is detachably connected with the housing. A needle-assist unit is movable along the first direction to execute an implantation action. The puncture unit is movable along a second direction to execute a needle withdrawal action. The in-vivo monitoring unit comprises a first electronic unit and a second electronic unit that are spaced apart. The first electronic unit comprises a sensor, and the second electronic unit comprises a signal processing module. Prior to use, the bottom cover is removed, and a single trigger causes the needle-assist unit to move, thereby inserting the sensor part into the host's body and electrically connecting the first electronic unit and the second electronic unit. The single trigger operation simultaneously completes the electrical connection of the first electronic unit and the second electronic unit and the implantation of the sensor, greatly simplifying the user's operation steps during the implantation process and shortening the entire implantation phase.

Description

In-body blood glucose monitoring device

[0001] This application claims priority to the Chinese patent application filed with the China Patent Office on March 29, 2024, with application number "202410377174.3" and invention name "A In Vivo Blood Glucose Monitoring Device", the entire contents of which are incorporated by reference into this application. Technical Field

[0002] The present application belongs to the technical field of medical equipment, and specifically relates to an in-vivo blood glucose monitoring device. Background Art

[0003] CGM (Continuous Glucose Monitoring) is a medical device used to continuously monitor blood sugar levels in patients with diabetes. Compared to traditional blood sugar monitoring methods, CGM provides continuous and detailed blood sugar level data, helping users better manage their blood sugar status.

[0004] To use the CGM, the user places the housing on the skin and presses the trigger button. The puncture needle and sensor pin inside the housing move toward the skin and puncture it. The bio-enzymes on the sensor react with the subcutaneous tissue fluid to produce an electrochemical reaction, which is converted into an electrical signal and then provided to the user as a blood sugar value. The sensor used to obtain the host's blood sugar level in real time and the electronic components that send signals to the display device are generally integrated into the on-body monitoring unit. Once implanted, the on-body monitoring unit is attached to the host's skin for continuous monitoring.

[0005] In-body monitoring units are generally categorized as either integrated or split. Integrated units are factory-assembled, with internal sensors, signal transmitters, and other electrical components already pre-connected, allowing for immediate use without any assembly. However, integrated units are more expensive to manufacture, and electronic components can easily fail during sterilization, leading to lower product yields and uncertain reliability.

[0006] While the split-type on-body monitoring unit is highly reliable, it is not fully assembled at the factory and must be assembled by the user before use. This results in a complex monitoring system structure and cumbersome usage steps, resulting in a high learning curve for users and a poor user experience.

[0007] Summary of the Invention

[0008] The present application provides an in vivo blood glucose monitoring device to solve the technical problems of complex monitoring system structure and cumbersome use steps.

[0009] The technical solutions adopted in this application are:

[0010] An in-vivo blood glucose monitoring device comprises an outer shell, the outer shell having a first end and a second end arranged relative to each other along a first direction, the second end having an implantation port; a bottom cover, the bottom cover being detachably connected to the second end and covering the implantation port; an auxiliary needle unit, the auxiliary needle unit being arranged inside the outer shell and being capable of moving relative to the outer shell along a first direction to perform an implantation action; a puncture unit, the puncture unit being arranged inside the outer shell, being capable of moving along the first direction with the auxiliary needle unit and being capable of moving relative to the auxiliary needle unit along a second direction to perform a needle withdrawal action, the second direction being opposite to the first direction; an in-vivo monitoring unit, the in-vivo monitoring unit comprising a first electronic unit and a second electronic unit arranged at intervals inside the outer shell, the first electronic unit comprising a sensor, and the second electronic unit comprising a signal processing module; before use, the bottom cover is removed, and a single trigger causes the auxiliary needle unit to move along the first direction to partially penetrate the sensor into the host body and to electrically connect the first electronic unit and the second electronic unit.

[0011] Preferably, the first electronic unit further comprises a battery, and the battery is capable of being in electrical communication with the second electronic unit.

[0012] Preferably, the first electronic unit includes an upper shell, the sensor is arranged in the upper shell, the second electronic unit includes a lower shell, the signal processing module is arranged in the lower shell, one of the upper shell and the lower shell is provided with a sealing rib, and the other is provided with a sealing groove, a sealing member is provided in the sealing groove, and the sealing rib can extend into the sealing groove and abut against the sealing member to seal.

[0013] Preferably, the shell includes a cover shell and a bottom shell, the cover shell has a connecting part, the bottom shell is connected to the connecting part, the implantation port is arranged at the end of the bottom shell away from the cover shell, and the bottom cover is detachably connected to the bottom shell to cover the implantation port; the first electronic unit is fixed inside the cover shell, and the second electronic unit is fixed inside the bottom shell.

[0014] Preferably, the bottom shell has a fixing portion, which is interference-fitted with the second electronic unit; the bottom cover is provided with a supporting column extending toward the outer shell, which is in contact with the second electronic unit to support the second electronic unit.

[0015] Preferably, the in vivo blood glucose monitoring device further comprises a pusher for driving the needle-assisting unit to move in a first direction, and a resetter for driving the puncture unit to move in a second direction. In the first direction, the pusher and the resetter at least partially overlap.

[0016] Preferably, the in vivo blood glucose monitoring device further comprises a trigger unit provided at the first end, the trigger unit being capable of moving or deforming along a first direction to trigger the needle assisting unit, so that the first electronic unit and the second electronic unit can move along the first direction.

[0017] Preferably, the auxiliary needle unit has a first mounting groove and a second mounting groove surrounding the outer circumference of the first mounting groove. The puncture unit is arranged in the first mounting groove. A reset member for driving the puncture unit to move along the second direction is arranged in the first mounting groove. A pushing member for driving the auxiliary needle unit to move along the first direction is arranged in the second mounting groove.

[0018] Preferably, the puncture unit includes a needle and a needle seat, the needle seat is provided with a matching groove, and the reset member is arranged in the matching groove.

[0019] Preferably, the needle seat at least partially overlaps with the needle assisting unit in the first direction.

[0020] Preferably, the in vivo blood glucose monitoring device includes a support member arranged inside the shell, the support member has a first positioning portion and a second positioning portion, the first positioning portion cooperates with the first mounting groove to form a first guide channel for accommodating the reset member, and the second positioning portion cooperates with the second mounting groove to form a second guide channel for accommodating the push member.

[0021] Preferably, the first positioning portion includes a positioning protrusion protruding toward the matching groove, and one end of the reset member is connected to the positioning protrusion, and the other end is connected to the puncture unit.

[0022] Preferably, a stopper is provided at one end of the needle-assisting unit away from the bottom cover, and the stopper abuts and cooperates with the end of the puncture unit away from the bottom cover to apply a force along the first direction to the puncture unit.

[0023] Preferably, the in-body blood glucose monitoring device further comprises an unlocking structure, which is located on the movement path of the stop portion. When the auxiliary needle unit moves to the implantation position along the first direction relative to the unlocking structure, the unlocking structure squeezes the stop portion to disengage the stop portion from the puncture unit.

[0024] Preferably, the stop portion includes a fixed end and a movable end, the movable end can swing around the fixed end, and the movable end is provided with a stop section extending toward the puncture unit for abutting and cooperating with the puncture unit, and a trigger section for cooperating with the unlocking structure.

[0025] Preferably, a guide transition surface is provided on a side opposite to the unlocking structure and / or the stop portion.

[0026] Preferably, the in-body blood glucose monitoring device further comprises a locking member arranged inside the shell, which can be elastically deformed or moved relative to the shell to have a locked state in which it cooperates with the auxiliary needle unit to limit the movement of the auxiliary needle unit, and an unlocked state in which it is loosened from the auxiliary needle unit.

[0027] Preferably, a mounting seat is provided inside the shell, and the locking member has a trigger portion located on one side of the mounting seat, and an action portion located on the other side of the mounting seat and cooperating with the auxiliary needle unit. The in vivo blood glucose monitoring device also includes a trigger unit provided at the first end and cooperating with the trigger portion. When the trigger unit squeezes the trigger portion, the action portion can swing around the mounting seat to switch to an unlocked state.

[0028] Due to the adoption of the above technical solution, the beneficial effects achieved by this application are as follows:

[0029] In the present application, the first electronic unit and the second electronic unit of the on-body monitoring unit are separated from each other when leaving the factory and fixed in the housing at intervals along the first direction. After the user performs a trigger operation, the first electronic unit can move along the first direction together with the needle-assisting unit and the puncture unit. When the puncture unit carries the sensor inside the first electronic unit into the host body, the first electronic unit and the second electronic unit are electrically connected synchronously. In this way, a single trigger operation is achieved, and the assembly of the on-body monitoring unit, the electrical connection between the first electronic unit and the second electronic unit, and the implantation of the sensor are completed at the same time. This greatly simplifies the operating steps during the user's implantation process, reduces the difficulty of operating the product, and reduces the user's learning cost. At the same time, it also shortens the time of the entire implantation stage, which helps to reduce the user's fear while waiting for implantation. The first electronic unit and the second electronic unit are separately arranged and can be sterilized separately. When the first electronic unit is sterilized, the electronic components of the data processing module of the second electronic unit will not be damaged.

[0030] In addition, a bottom cover is fixed to the implantation port of the shell, and the bottom cover is detachably connected to the shell. When leaving the factory, the bottom cover is fixed to the shell, and cooperates with the shell to form a relatively sealed environment to prevent external dust and bacteria from entering the interior during storage and transportation, thereby ensuring the cleanliness of the internal components. Before the user implants the device, the bottom cover needs to be removed from the shell, and the implantation port needs to be opened so that the internal sensor and puncture unit can be inserted into the body through the implantation port. In this way, when using the in-vivo blood glucose monitoring device of the present application, the user only needs to perform two steps. First, the bottom cover is removed from the shell to expose the implantation port, and the implantation port is close to the skin. Then, the needle-assisting unit is triggered, and the electrical connection between the first electronic unit and the second electronic unit and the implantation of the sensor can be achieved at the same time, completing the entire implantation process. There is no need to perform additional operations to assemble the upper and lower shells, thereby improving the user experience. BRIEF DESCRIPTION OF THE DRAWINGS

[0031] The drawings described herein are used to provide a further understanding of the present application and constitute a part of the present application. The illustrative embodiments of the present application and their descriptions are used to explain the present application and do not constitute an improper limitation on the present application. In the drawings:

[0032] FIG1 is a schematic structural diagram of a first electronic unit according to an embodiment of the present application;

[0033] FIG2 is a cross-sectional view of the first electronic unit in FIG1 ;

[0034] FIG3 is a cross-sectional view of a second electronic unit according to an embodiment of the present application;

[0035] FIG4 is a schematic structural diagram of an on-body monitoring unit in a state where the first electronic unit and the second electronic unit are separated according to an embodiment of the present application;

[0036] FIG5 is a cross-sectional view of an on-body monitoring unit according to an embodiment of the present application;

[0037] FIG6 is a cross-sectional view of a portion of an in-body blood glucose monitoring device according to an embodiment of the present application;

[0038] FIG7 is a cross-sectional view of a lower cover according to an embodiment of the present application;

[0039] FIG8 is a cross-sectional view of a portion of an in-body blood glucose monitoring device according to an embodiment of the present application;

[0040] FIG9 is a schematic structural diagram of a portion of an in-body blood glucose monitoring device according to an embodiment of the present application;

[0041] FIG10 is a cross-sectional view of the bottom shell and the bottom cover according to an embodiment of the present application;

[0042] Figure 11 is a schematic structural diagram of the bottom shell and bottom cover in Figure 10;

[0043] FIG12 is a cross-sectional view of an in-vivo blood glucose monitoring device in an initial state according to an embodiment of the present application;

[0044] FIG13 is a cross-sectional view of an in-body blood glucose monitoring device according to an embodiment of the present application with the bottom cover removed;

[0045] FIG14 is a cross-sectional view of an in-vivo blood glucose monitoring device according to one embodiment of the present application during implantation when the first electronic unit and the second electronic unit are assembled;

[0046] FIG15 is a cross-sectional view of an in-vivo blood glucose monitoring device after implantation according to an embodiment of the present application.

[0047] in:

[0048] 1 housing; 11 cover; 111 snap-fit ​​buckle; 112 unlocking structure; 113 trigger unit; 1131 trigger button; 12 bottom shell; 121 slot; 122 avoidance opening; 123 implantation opening; 124 through opening; 125 elastic rib position; 2 bottom cover; 21 support column; 3 needle-assisting unit; 31 first mounting slot; 32 second mounting slot; 33 stopper; 331 stopper section; 332 trigger section; 34 hook; 35 fixing opening; 4 puncture unit; 41 needle seat; 411 matching slot; 42 needle head; 5 support member; 51 positioning protrusion; 52 separation rib; 53 accommodating slot; 54 first guide passage channel; 55 second guide channel; 6 on-body monitoring unit; 61 first electronic unit; 611 upper shell; 612 fixing groove; 613 sensor; 6131 substrate; 6132 contact pin; 614 battery; 615 conductive silicone; 616 sealing silicone; 617 sealing rib; 618 snap; 619 through-hole; 62 second electronic unit; 621 lower shell; 622 adhesive layer; 623 snap; 624 retaining rib; 625 signal processing module; 626 sealing groove; 627 sealing member; 7 pushing member; 8 reset member; 9 locking member; 91 triggering part; 92 balancing arm; 93 action part. DETAILED DESCRIPTION

[0049] In order to more clearly illustrate the overall concept of the present application, a detailed description is given below in an illustrative manner in conjunction with the accompanying drawings.

[0050] As shown in Figures 1 to 15, an in-vivo blood glucose monitoring device includes a housing 1 having a first end and a second end disposed opposite to each other along a first direction, the second end being provided with an implantation port 123; a bottom cover 2 detachably connected to the second end and covering the implantation port 123; an auxiliary needle unit 3 disposed inside the housing 1 and capable of moving relative to the housing 1 in a first direction to perform an implantation operation; a puncture unit 4 disposed inside the housing 1 and capable of moving along the first direction with the auxiliary needle unit 3 and capable of moving relative to the auxiliary needle unit 123. The unit 3 moves in a second direction to perform the needle withdrawal action, and the second direction is opposite to the first direction; the in-body monitoring unit 6 includes a first electronic unit 61 and a second electronic unit 62 arranged at intervals inside the shell 1, the first electronic unit 61 includes a sensor 613, and the second electronic unit 62 includes a signal processing module 625; before use, the bottom cover 2 is removed, and a single trigger causes the auxiliary needle unit 3 to move in the first direction to partially penetrate the sensor 613 into the host body and to electrically connect the first electronic unit 61 and the second electronic unit 62.

[0051] It can be understood that, as shown in Figures 1 to 6, the first direction is parallel to the longitudinal axis of the shell 1 and toward the implantation port 123, and the second direction is parallel to the longitudinal axis of the shell 1 and away from the implantation port 123, that is, the first direction and the second direction are opposite. After the user presses the trigger unit 113, the auxiliary needle unit 3 carries the puncture unit 4 to move along the first direction, and at the same time, the first electronic unit 61 also moves along the first direction under the push of the auxiliary needle unit 3. During this process, the first electronic unit 61 and the second electronic unit 62 are assembled and electrically connected, and the puncture unit 4 carries the contact needle 6132 of the sensor 613 to pierce the host skin and enter the body. After the auxiliary needle unit 3 moves into place, it triggers the puncture unit 4, causing the puncture unit 4 to move alone in the second direction and be pulled out of the host body, completing the needle withdrawal. The second electronic unit 62 is provided with an adhesive layer 622 on the side facing the implantation port 123, which is bonded and fixed to the surface of the host skin and remains on the surface of the host skin, while the shell 1 and other internal components are removed.

[0052] It should be noted that the present application does not limit the time sequence of the electrical connection between the first electronic unit 61 and the second electronic unit 62, and the partial penetration of the sensor 613 into the host body. For example, in the process of the auxiliary needle unit 3, the puncture unit 4 and the first electronic unit 61 moving together along the first direction, the first electronic unit 61 and the second electronic unit 62 may complete the electrical connection first. At this time, the auxiliary needle unit 3 and the puncture unit 4 have not yet moved into place. As the movement continues, the puncture unit 4 penetrates into the host body to complete the implantation. That is to say, the electrical connection between the first electronic unit 61 and the second electronic unit 62 occurs before the puncture unit 4 penetrates into the host body. For another example, during the movement of the auxiliary needle unit 3, the puncture unit 4, and the first electronic unit 61 in the first direction, the puncture unit 4 first penetrates the host body. At this time, the auxiliary needle unit 3 and the puncture unit 4 have not yet moved into place. As the movement continues, the upper shell 611 and the lower shell 621 are assembled again, and at the same time, the first electronic unit 61 and the second electronic unit 62 are electrically connected. In other words, the puncture unit 4 penetrates the host body before the first electronic unit 61 and the second electronic unit 62 are electrically connected. In addition, the above two steps can also occur simultaneously.

[0053] However, regardless of the situation in the above examples, the user only needs to perform a single trigger operation and does not need to perform additional operations. Therefore, the situations in the above examples are all within the scope of protection of this application.

[0054] As shown in Figure 12, the first electronic unit 61 and the second electronic unit 62 of the on-body monitoring unit 6 are separated from each other and fixed in the housing 1 when they leave the factory. After the user triggers the operation, the upper shell 611 can move along the first direction with the needle-assisting unit 3 and the puncture unit 4, and simultaneously complete the puncture unit 4 carrying the sensor 613 inside the first electronic unit 61 into the host body, and the first electronic unit 61 and the second electronic unit 62 are electrically connected. In this way, a single trigger operation is achieved, and the electrical connection between the first electronic unit 61 and the second electronic unit 62 and the implantation of the sensor 613 are completed at the same time. This greatly simplifies the user's operating steps during the implantation process, reduces the difficulty of operating the product, and reduces the user's learning cost. At the same time, it also shortens the time of the entire implantation stage, which helps to reduce the user's fear while waiting for implantation.

[0055] In addition, as shown in Figures 12 and 13, a bottom cover 2 is fixed to the implantation port 123 of the housing 1. The bottom cover 2 is detachably connected to the housing 1. When shipped from the factory, the bottom cover 2 is fixed to the housing 1 and cooperates with the housing 1 to form a relatively sealed environment, preventing external dust and bacteria from entering the interior during storage and transportation, and ensuring the cleanliness of the internal components. Before the user implants the device, the bottom cover 2 needs to be removed from the housing 1 and the implantation port 123 opened, allowing the internal sensor 613 and the puncture unit 4 to penetrate the body through the implantation port 123.

[0056] Thus, when using the in-vivo blood glucose monitoring device of the present application, the user only needs to perform two steps: first, remove the bottom cover 2 from the outer shell 1 to expose the implantation port 123, place the implantation port 123 close to the skin, and then trigger the auxiliary needle unit 3. This simultaneously achieves the electrical connection between the first electronic unit 61 and the second electronic unit 62, and implants the sensor 613, completing the entire implantation process. No additional operation is required to assemble the upper and lower shells 621, which improves the user experience.

[0057] As a preferred embodiment of the present application, as shown in FIG2 , the first electronic unit 61 further includes a battery 614, which is electrically connected to the second electronic unit 62. The primary function of the battery 614 is to power the signal processing module 625. Before the user triggers implantation, the first and second electronic units 61 and 62 are separated, so the battery 614 is not electrically connected to the signal processing module 625. Only after the user triggers implantation does the battery 614 establish an electrical connection with the signal processing module 625. This reduces energy loss in the battery 614 before use and increases storage time.

[0058] Preferably, as shown in Figures 2, 3, and 5, the first electronic unit 61 includes an upper housing 611, on which the sensor 613 is disposed. The second electronic unit 62 includes a lower housing 621, on which the signal processing module 625 is disposed. The upper housing 611 and the lower housing 621 are secured by a snap-fit ​​connection, thereby simplifying the process of securing the two. Manual connection is unnecessary, and securement can be achieved solely by the power of the needle-assisting unit 3. Specifically, as shown in Figures 2 and 3, the upper housing 611 is provided with a buckle 618, and the lower housing 621 is provided with a latch 623. When the upper housing 611 collides with the needle-assisting unit 3 in a first direction, the buckle 618 slides into the latch 623 under the impact force, securing the upper and lower housings 611 and 621. Of course, the buckle 618 can also be provided on the lower housing 621, and the latch 623 can be provided on the upper housing 611 to achieve the same secure connection. Specifically, as shown in Figure 3, the buckle 618 is provided with a guide surface on the side facing the bayonet 623, and the bayonet 623 is provided with a retaining rib 624 on the side close to the buckle 618. The buckle 618 first contacts the retaining rib 624 and expands toward the outer shape under the squeezing of the retaining rib 624. When the buckle 618 continues to move to the bayonet 623, it loses the squeezing of the retaining rib 624, shrinks and deforms under the action of its own elasticity, and is locked into the bayonet 623.

[0059] The upper shell 611 is provided with a through opening 619 corresponding to the contact pin 6132 of the sensor 613. When the puncture unit 4 moves in the first direction, the needle 42 of the puncture unit 4 passes through the through opening 619 of the upper shell 611 and surrounds the contact pin 6132 of the sensor 613. During the movement of the auxiliary needle unit 3, the upper shell 611 and the lower shell 621 are assembled, and the puncture unit 4 carries the contact pin 6132 of the sensor 613 to pierce the host's skin and enter the body. After the auxiliary needle unit 3 moves into place, it triggers the puncture unit 4, causing the puncture unit 4 to move alone in the second direction and be pulled out of the host's body to complete the needle withdrawal. An adhesive layer 622 is provided on the side of the lower shell 621 facing the implantation port 123, which is bonded and fixed to the surface of the host's skin and remains on the surface of the host's skin. The outer shell 1 and other internal components are removed.

[0060] Preferably, as shown in Figures 2 and 3, one of the upper shell 611 and the lower shell 621 is provided with a sealing rib 617, and the other is provided with a sealing groove 626. A sealing member 627 is disposed within the sealing groove 626. The sealing rib 617 can extend into the sealing groove 626 and abut against the sealing member 627 to achieve a seal. The sealing rib 617 and the sealing member 627 within the sealing groove 626 are disposed in correspondence. When the upper shell 611 contacts the lower shell 621 along a first direction, the sealing rib 617 extends into the sealing groove 626, abuts against the sealing member 627, and squeezes and deforms the sealing member 627, thereby achieving a seal between the upper and lower shells. Specifically, as shown in Figures 2 and 3, the sealing rib 617 is disposed on the upper shell 611, and the sealing groove 626 is disposed on the lower shell 621. The sealing member 627 is an O-ring and is disposed within the sealing groove 626. The positions of the sealing rib 617 and the sealing groove 626 can also be interchanged, that is, the sealing rib 617 is provided on the lower shell 621, and the sealing groove 626 is provided on the upper shell 611. Preferably, as shown in FIG3 , the groove walls on both sides of the sealing groove 626 extend obliquely so that the width of the groove opening is greater than the width of the groove bottom. This guides the insertion of the sealing rib 617, making the insertion of the sealing rib 617 and the sealing groove 626 smoother and reducing any sticking during the insertion process.

[0061] Furthermore, as shown in Figure 2, sensor 613 includes a thin sheet-like substrate 6131 and a stylus 6132 extending downward and integrating multiple electrodes. It is designed to be inserted into the human epidermis and analyze the concentration of glucose and other analytes in an individual through electrochemical reactions in the tissue fluid within the epidermis. Conductive silicone 615 is provided on the underside of substrate 6131 to transmit the electrical signal generated by the electrochemical reaction in sensor 613 to signal processing module 625. Sealing silicone 616 is also provided on the underside of conductive silicone 615, primarily for waterproofing the electrode contacts of sensor 613. This seal, in conjunction with conductive silicone 615, allows for electrical connection to signal processing module 625 while simultaneously achieving an electrical connection.

[0062] As a preferred embodiment of the present application, as shown in Figures 6, 10, and 12, the housing 1 includes a cover shell 11 and a bottom shell 12. The cover shell 11 has a connecting portion, the bottom shell 12 is connected to the connecting portion, the implantation port 123 is provided at the end of the bottom shell 12 away from the cover shell 11, and the bottom cover 2 is detachably connected to the bottom shell 12 to cover the implantation port 123; the first electronic unit 61 is fixed inside the cover shell 11, and the second electronic unit 62 is fixed inside the bottom shell 12. Specifically, as shown in Figures 10, 11, and 12, the bottom cover 2 and the bottom shell 12 are fixed by a snap connection. Of course, the bottom cover 2 can also be fixed to the bottom shell 12 by means of threaded connection, interference fit, plug-in connection, etc., which are not limited here.

[0063] The outer shell 1 is a split structure, the needle-assisting unit 3, the puncture unit 4 and the first electronic unit 61 are fixed in the cover shell 11, and the second electronic unit 62 is fixed in the bottom shell 12, thereby dividing the in vivo blood glucose monitoring device into two modules, among which the puncture unit 4, the sensor 613 and other components with higher sterilization requirements are concentrated in one module (inside the cover shell 11). Therefore, before leaving the factory, the cover shell 11 and the bottom shell 12 modules can be sterilized with different processes or levels respectively. After the sterilization is completed, the cover shell 11 and the bottom shell 12 are assembled into one. The problem of failure of the sensor 613 or electronic components during the sterilization process is avoided. In addition, when leaving the factory, the bottom shell 12 and the cover shell 11 have been fixed. The user does not need to perform the fixing operation of the bottom shell 12 and the cover shell 11 before use. The user only needs to directly perform the triggering operation, which reduces the operating steps and improves the user experience.

[0064] As shown in Figures 6 and 12, in one embodiment, the sidewalls of the bottom shell 12 are provided with a slot 121, and the sidewalls of the cover shell 11 are provided with a snap-fit ​​buckle 111 to secure the two together. The snap-fit ​​buckle 111 can be provided on the inner wall of the cover shell 11 to allow the sidewalls of the bottom shell 12 to extend into the interior of the cover shell 11 and be secured thereto. The snap-fit ​​buckle 111 can also be provided on the outer wall of the cover shell 11 to allow the cover shell 11 to extend into the interior of the bottom shell 12 and be secured thereto. The cover shell 11 and the bottom shell 12 can also be secured together by other means, such as threaded connections, etc., which are not limited here.

[0065] Furthermore, as shown in Figures 10 and 11, the bottom shell 12 has a fixing portion that is interference-fitted with the second electronic unit 62. Specifically, as shown in Figures 10 and 11, the bottom shell 12 has a through opening 124, and a plurality of elastic ribs 125 are spaced along the edge of the through opening 124. The elastic ribs 125 form a mounting position for fixing the lower shell 621 of the second electronic unit 62. After the lower shell 621 is installed, the elastic ribs 125 are squeezed outward. Under the action of their own elastic force, the elastic ribs 125 squeeze inward and clamp the lower shell 621. When the lower shell 621 is pushed by the upper shell 611 in the first direction, or when the adhesive layer 622 of the lower shell 621 is bonded to the host's skin, the lower shell 621 can break away from the clamping of the elastic ribs 125 and fall off from the bottom shell 12.

[0066] As shown in Figures 1 and 6, the needle assist unit 3 is provided with a hook 34. A fixing groove 612 is provided around the periphery of the upper shell 611. The hook 34 engages with the fixing groove 612, securing the upper shell 611 to the needle assist unit 3 and enabling movement thereof. The walls of the fixing groove 612 act as stoppers against the hook 34, limiting rotation of the upper shell 611 relative to the needle assist unit 3. Furthermore, a clearance opening 122 is provided on the bottom shell 12, outside the opening 124. A trigger rib is provided on one side of the clearance opening 122, near the center of the bottom shell 12. When the needle assist unit 3, carrying the upper shell 611, moves toward the bottom shell 12, the trigger rib compresses the hook 34, causing it to expand and deform outward, disengaging from the fixing groove 612 and releasing the upper shell 611. Simultaneously, the hook 34 enters the clearance opening 122.

[0067] Preferably, as shown in FIG12 , the bottom cover 2 is provided with a support column 21 extending toward the outer shell 1 , and the support column 21 contacts the second electronic unit 62 to support the second electronic unit 62. As shown in FIG12 , before the user removes the bottom cover 2 , the support column 21 supports the second electronic unit 62, ensuring that the second electronic unit 62 is stably fixed in the bottom shell 12 to prevent it from falling off. Specifically, as shown in FIG13 , before use, the user first removes the bottom cover 2. As shown in FIG14 , after the user presses the trigger unit 113, the needle-assisting unit 3 loses its movement limit and moves along the first direction with the upper shell 611. During this movement, as shown in FIG14 , the upper shell 611 contacts and seals the lower shell 621. Simultaneously, the hook 34 is squeezed by the trigger rib on the bottom shell 12, releasing the first electronic unit 61. The second electronic unit 62, pushed by the first electronic unit 61, then disengages from the elastic rib 125. At this point, the upper shell 611 and the lower shell 621 are assembled, and the first electronic unit 61 and the second electronic unit 62 are electrically connected. As shown in FIG15 , the needle-assisting unit 3 and the on-body monitoring unit 6 continue to move along the first direction until the puncture unit 4 penetrates the host body and the adhesive layer 622 contacts and bonds with the host's skin surface. Preferably, the buckle 618, the snap buckle 111 and the hook 34 can be set to two or more as needed, and arranged at intervals along the circumference to form a uniform fixing force on the bottom shell 12 and the on-body monitoring unit 6 in the circumference to avoid tilting.

[0068] In a preferred embodiment, as shown in Figures 6 and 8, the in vivo blood glucose monitoring device includes a pusher 7 for driving the needle-assisting unit 3 in a first direction, and a reset member 8 for driving the puncture unit 4 in a second direction. In the first direction, the pusher 7 and reset member 8 at least partially overlap. Along the axis of the housing 1, the reset member 8 and the pusher 7 at least partially overlap, which improves the compactness of the structural arrangement and helps reduce the overall axial dimensions of the in vivo blood glucose monitoring device, achieving miniaturization. Specifically, as shown in Figure 6, both the pusher 7 and reset member 8 are springs. Initially, the pusher 7 is compressed, exerting a thrust on the needle-assisting unit 3 in the first direction. The reset member 8 is initially undeformed. As the needle-assisting unit 3 and the puncture unit 4 move in the first direction, the reset member 8 gradually elongates, exerting a tensile force on the puncture unit 4 in the second direction. This ensures that the puncture unit 4 does not withdraw prematurely before the implantation process is complete, resulting in implant failure, thereby improving the implantation success rate. It also prevents the reset member 8 from being in a deformed state for a long time, which could cause fatigue, thereby improving the needle withdrawal effect. Alternatively, the reset member 8 may be designed to be in an elongated state in the initial state, so as to increase the driving force of the reset member 8 on the puncture unit 4 .

[0069] Preferably, as shown in FIG6 , the in vivo blood glucose monitoring device further includes a trigger unit 113 disposed at the end of the housing 1 facing away from the implantation port 123. The trigger unit 113 is capable of moving or deforming in a first direction to trigger the needle-assisting unit 3, and the first and second electronic units 61 and 62 are capable of moving in the first direction. A user presses the trigger unit 113 in the first direction, causing it to trigger the needle-assisting unit 3. Once triggered, the needle-assisting unit 3 also moves in the first direction toward the implantation port 123, pushing the first and second electronic units 61 and 62 in the first direction to the implantation port 123, where they come into contact with and adhere to the patient's skin. In this embodiment, the pressing of the trigger unit 113, the implantation direction of the puncture unit 4, and the movement directions of the first and second electronic units 61 and 62 are aligned. This not only simplifies and compacts the arrangement of the needle-assisting structure within the housing 1, but also ensures more reliable movement of the components. This helps ensure the stability of the puncture unit 4 during movement, preventing any shaking during implantation that could cause pain to the user.

[0070] As a preferred embodiment of the present application, as shown in FIG6 , the needle-assisting unit 3 has a first mounting groove 31 and a second mounting groove 32 surrounding the outer periphery of the first mounting groove 31. The puncture unit 4 is disposed in the first mounting groove 31. A reset member 8 for driving the puncture unit 4 in the second direction is disposed in the first mounting groove 31. A pusher 7 for driving the needle-assisting unit 3 in the first direction is disposed in the second mounting groove 32. The puncture unit 4 is disposed in the first mounting groove 31.

[0071] The needle-assisting unit 3 has space for accommodating the pusher 7 and the resetter 8, allowing the pusher 7 and resetter 8 to be more centrally located. The pusher 7 surrounds the outer periphery of the resetter 8, reducing the radial space occupied by the housing 1 compared to a side-by-side arrangement. This helps reduce the radial dimensions of the housing 1 and achieve miniaturization. Furthermore, the second mounting groove 32 surrounds the first mounting groove 31, allowing the resetter 8 and the pusher 7 to partially overlap in the first direction (the axial direction of the housing 1) after installation. This helps reduce the axial space occupied by the resetter 8 and the pusher 7, reducing the dimensions of the housing 1 in both the axial and radial directions, making the entire device more compact and lightweight, and more convenient to use and store. Furthermore, the walls of the first and second mounting grooves 31 and 32 also guide the resetter 8 and the pusher 7, reducing the shaking of the puncture unit 4 during needle insertion and withdrawal, ensuring that the puncture unit 4 always moves along its axis and alleviating pain felt by the user during needle insertion and withdrawal. Specifically, as shown in FIG6 , the auxiliary needle unit 3 is a cylindrical structure having an inner wall and an outer wall. The inner wall forms a first mounting groove 31 in the central area of ​​the auxiliary needle unit 3 , and a second mounting groove 32 is formed between the inner wall and the outer wall.

[0072] Furthermore, as shown in FIG6 , the puncture unit 4 includes a needle 42 and a needle hub 41 . The needle hub 41 is provided with a mating groove 411 , and the reset member 8 is disposed within the mating groove 411 . The needle hub 41 is provided with a mating groove 411 , and the mating groove 411 has a mating opening facing away from the implantation opening 123 , for accommodating the reset member 8 . The use of the mating groove 411 further reduces the placement space of the reset member 8 , improves the limiting and guiding effect on the reset member 8 , and makes the deformation of the reset member 8 more reliable. Specifically, as shown in FIG6 , the depth of the mating groove 411 is greater than 1 / 2 of the reset member 8 , so as to further improve the guiding and limiting effect on the reset member 8 .

[0073] 6 , the needle hub 41 overlaps at least partially with the needle assisting unit 3 in the first direction. The needle hub 41 and the needle assisting unit 3 are coaxially arranged, and partially overlap in the axial direction, which can further improve the compactness of the structure, optimize the structural layout, and achieve a miniaturized design.

[0074] In a preferred embodiment, as shown in Figures 6, 7, and 8, the in vivo blood glucose monitoring device includes a support member 5 disposed within the housing 1. The support member 5 has a first positioning portion and a second positioning portion. The first positioning portion cooperates with the first mounting groove 31 to form a first guide channel 54 for accommodating the reset member 8, and the second positioning portion cooperates with the second mounting groove 32 to form a second guide channel 55 for accommodating the pusher 7. The support member 5 cooperates with the needle-assisting unit 3 to form channels for accommodating the reset member 8 and the pusher 7, respectively. The two channels are coaxial and telescopically arranged, resulting in greater height overlap, making the internal structure more compact and reducing product size. This also enhances the guiding function of the reset member 8 and the pusher 7, ensuring that the puncture unit 4 does not tilt during axial movement. The puncture unit 4 is disposed within the first guide channel 54.

[0075] Preferably, as shown in Figure 7, the support member 5 is provided with a separating rib 52 between the first guide channel 54 and the second guide channel 55 to separate the two guide channels and prevent interference between the reset member 8 and the pusher 7 during deformation. Furthermore, as shown in Figures 7 and 8, the first positioning portion includes a positioning protrusion 51 protruding toward the mating groove 411. One end of the reset member 8 is connected to the positioning protrusion 51 and the other end is connected to the puncture unit 4. The provision of the positioning protrusion 51 can provide a positioning effect for the installation of the reset member 8, reducing the difficulty of installation of the reset member 8, and can also serve as a guide during the deformation of the reset member 8, preventing the reset member 8 from tilting and deforming. Specifically, as shown in Figure 6, the reset member 8 is a spring, one end of which is sleeved on the outer periphery of the positioning protrusion 51 and the other end is abutted or fixedly connected to the puncture unit 4. Preferably, as shown in Figures 6 and 8, the support member 5 is coaxial with the needle-assisting unit 3.

[0076] In a preferred embodiment of the present application, as shown in Figures 6 and 8 , a stopper 33 is provided at the end of the needle-assisting unit 3 facing away from the bottom cover 2. The stopper 33 abuts against the end of the puncture unit 4 facing away from the bottom cover 2 to apply a force to the puncture unit 4 in a first direction. On the one hand, the stopper 33 abuts against the end of the puncture unit 4 facing away from the bottom cover 2 to form a stop for the puncture unit 4, limiting its movement in the second direction. This ensures the positional stability of the puncture unit 4 before implantation and prevents premature withdrawal of the puncture unit 4. On the other hand, when the needle-assisting unit 3 is triggered, the needle-assisting unit 3 moves in the first direction, and the force is transmitted to the puncture unit 4 via the stopper 33, driving the puncture unit 4 in the first direction to complete the insertion of the needle. This integrates the position-limiting and driving functions of the stopper 33, simplifying the structure while saving space within the housing 1 and reducing costs. Specifically, as shown in Figure 8 , the stopper 33 is located within the first mounting groove 31 and abuts against the puncture unit 4.

[0077] Preferably, as shown in Figures 6, 8, and 12 to 15, the in vivo blood glucose monitoring device further includes an unlocking structure 112. The unlocking structure 112 is located in the movement path of the stopper 33. When the auxiliary needle unit 3 moves relative to the unlocking structure 112 in the first direction to the implantation position, the unlocking structure 112 compresses the stopper 33 to disengage the stopper 33 from the puncture unit 4. The unlocking structure 112 is located in the movement path of the stopper 33 in the first direction and is fixed in position, not moving with the auxiliary needle unit 3. Therefore, when the auxiliary needle unit 3 and the puncture unit 4 are moved in the first direction together, the unlocking structure 112 compresses the stopper 33 to release the restraint on the puncture unit 4, thereby automatically triggering the unlocking of the puncture unit 4 and withdrawing the puncture unit 4 in the second direction. This eliminates the need for the user to perform additional needle withdrawal operations. A single triggering operation automatically completes the implantation and withdrawal steps, simplifying the user's operation steps, reducing operational difficulty, and significantly improving the user experience. Specifically, as shown in Figure 8, the stop portion 33 includes a fixed end and a movable end. The movable end can swing around the fixed end. The movable end is provided with a stop segment 331 extending toward the puncture unit 4 for abutting and cooperating with the puncture unit 4, and a trigger segment 332 for cooperating with the unlocking structure 112.

[0078] The fixed end of the stopper 33 is fixed to the needle-assisting unit 3 body or housing 1, while the movable end is free. This allows the stopper 33 to have a strong elastic deformation capability, allowing it to swing around the fixed end when squeezed. The movable end is provided with a stopper section 331 and a trigger section 332. When the stopper 33 moves into position in the first direction, the trigger section 332 contacts the unlocking structure 112 and is squeezed, causing the movable end to shift. The stopper section 331 moves with the movable end, disengaging from the puncture unit 4 and losing its stop position on the puncture unit 4. At this point, the puncture unit 4 can be moved in the second direction, driven by the reset member 8, to withdraw the needle.

[0079] Furthermore, as shown in Figure 8, a guide transition surface is provided on the opposite side of the unlocking structure 112 and / or the stop portion 33. The provision of the guide transition surface makes the cooperation between the unlocking structure 112 and the stop portion 33 smoother, reduces the sticking feeling caused by the contact between the two, and the stop portion 33 can expand and deform outward more smoothly, which helps to improve the timeliness of triggering the needle withdrawal movement and shorten the duration of the entire implantation process. At the same time, it can also reduce the relative position deviation of the stop portion 33 and the unlocking structure 112 caused by processing and assembly errors, so that the two can cooperate reliably. Preferably, the guide transition surface can be an inclined surface, an arc surface or other irregular curved surface, as long as it can guide the cooperation between the stop portion 33 and the unlocking structure 112, and is not limited here.

[0080] In the above embodiment, the stopper 33 is capable of elastic deformation and disengagement from the puncture unit 4. In another embodiment, the stopper 33 may also be configured to be movable relative to the puncture unit 4. When the unlocking structure 112 is triggered, the triggering structure pushes the stopper 33 to move, thereby disengaging from the puncture unit 4. This is not limited here.

[0081] In a preferred embodiment, as shown in Figures 6, 8, and 9, the in vivo blood glucose monitoring device further includes a locking member 9 disposed inside the housing 1. The locking member 9 can be elastically deformed or moved relative to the housing 1 to have a locked state in which it cooperates with the auxiliary needle unit 3 to restrict the movement of the auxiliary needle unit 3, and an unlocked state in which it is loosened from the auxiliary needle unit 3. The locking member 9 can lock the auxiliary needle unit 3 inside the housing 1 before the user triggers the trigger unit 113, preventing it from moving, thereby improving the overall reliability of the in vivo blood glucose monitoring device and preventing accidental triggering before use that would cause the product to be scrapped. Only after the user triggers the trigger unit 113 does the locking member 9 release the lock on the auxiliary needle unit 3. Specifically, as shown in Figures 6 and 8, the trigger unit 113 is a trigger button 1131 disposed at the end of the housing 1 away from the implant port 123, and the locking member 9 is disposed between the trigger button 1131 and the auxiliary needle unit 3. In the initial state, the locking member 9 cooperates with the auxiliary needle unit 3 to lock the position of the auxiliary needle unit 3. When the user presses the trigger button 1131, as shown in Figure 14, the trigger button 1131 can push the locking member 9 to move or elastically deform, thereby disengaging the auxiliary needle unit 3. As shown in Figure 12, the trigger button 1131 has a pressing protrusion protruding toward the locking member 9.

[0082] Furthermore, as shown in Figures 8 and 9, a mounting seat is provided inside the housing 1. The locking member 9 has a trigger portion 91 located on one side of the mounting seat, and an action portion 93 located on the other side of the mounting seat and cooperating with the needle-assisting unit 3. The in vivo blood glucose monitoring device also includes a trigger unit 113 located at the end of the housing 1 facing away from the implant port 123 and cooperating with the trigger portion 91. When the trigger unit 113 squeezes the trigger portion 91, the action portion 93 can swing around the mounting seat to switch to an unlocked state. The trigger portion 91 and the action portion 93 of the locking member 9 are located on both sides of the mounting seat, thereby forming a lever structure with the mounting seat. When the trigger portion 91 on one side of the mounting seat is squeezed by the trigger unit 113, the action portion 93 on the other side will swing around the mounting seat. Specifically, as shown in Figures 8 and 9, a contact plane is provided in the central area of ​​the locking member 9 for contacting the trigger button 1131, making the contact between the two more stable. The contact plane has a balancing arm 92 extending obliquely toward the implant port 123 on its circumferential side. The balancing arm 92 extends from one side of the mounting seat to the other side of the mounting seat. The contact plane is the trigger portion 91, and the end away from the contact plane is the action portion 93. Preferably, the locking member 9 is coaxially arranged with the needle-assisting unit 3 and the trigger unit 113. The action portion 93 is provided with a locking hook 34 extending radially inward along the needle-assisting unit 3. The side wall of the needle-assisting unit 3 is provided with a fixing port 35. The locking hook 34 extends into the fixing port 35 to engage the two. Taking Figure 8 as an example, when the contact plane is pressed downward, the action portion 93 at the lower end of the balancing arm 92 expands outward around the mounting seat, causing the fixing hook 34 to disengage from the fixing port 35, thereby unlocking the needle-assisting unit 3.

[0083] Preferably, the in vivo blood glucose monitoring device includes a support member 5, and at least a portion of the support member 5 constitutes a mounting seat. Specifically, as shown in Figures 8 and 9, the support member 5 has a receiving groove 53, and the bottom wall of the receiving groove 53 cooperates with the needle-assisting unit 3 to form a second guide channel 55 for accommodating the push member 7, and a first guide channel 54 for accommodating the reset member 8. The contact plane is located in the receiving groove 53, and the receiving groove 53 provides space for the up and down movement of the contact plane. The side wall of the receiving groove 53 is provided with a through opening for the balance arm 92 to pass through, so that the bottom wall of the receiving groove 53 constitutes a mounting seat. As shown in Figure 7, the side wall of the receiving groove 53 is fixed to the housing 1 by a snap-fit ​​method. Of course, the support member 5 can also be fixed to the housing 1 by other methods.

[0084] The foregoing is merely an embodiment of the present application and is not intended to limit the present application. For those skilled in the art, the present application may have various modifications and variations. Any modifications, equivalent replacements, improvements, etc. made within the spirit and principles of the present application should all be included within the scope of the claims of the present application.

Claims

1. An in-body blood glucose monitoring device, characterized in that: include: a housing having a first end and a second end disposed opposite to each other along a first direction, wherein the second end is provided with an implantation port; a bottom cover detachably connected to the second end and covering the implantation port; an auxiliary needle unit, the auxiliary needle unit being disposed inside the housing and being movable relative to the housing in a first direction to perform an implantation operation; a puncture unit, the puncture unit being disposed inside the housing, the puncture unit being capable of moving along the first direction with the auxiliary needle unit, and being capable of moving relative to the auxiliary needle unit in a second direction to perform a needle retraction action, the second direction being opposite to the first direction; and An on-body monitoring unit, the on-body monitoring unit comprising a first electronic unit and a second electronic unit spaced apart along the first direction inside the housing, the first electronic unit comprising a sensor, and the second electronic unit comprising a signal processing module; Before use, the bottom cover is removed, and a single trigger is used to move the auxiliary needle unit along the first direction, so as to partially penetrate the sensor into the host body and electrically connect the first electronic unit and the second electronic unit.

2. The in-body blood glucose monitoring device according to claim 1, wherein: The first electronics unit further includes a battery capable of electrically communicating with the second electronics unit.

3. The in-body blood glucose monitoring device according to claim 1, wherein: The first electronic unit includes an upper shell, the sensor is arranged in the upper shell, the second electronic unit includes a lower shell, the signal processing module is arranged in the lower shell, one of the upper shell and the lower shell is provided with a sealing rib, and the other is provided with a sealing groove, a sealing member is provided in the sealing groove, and the sealing rib can extend into the sealing groove and abut against the sealing member to seal.

4. The in-body blood glucose monitoring device according to claim 1, wherein: The housing includes a cover shell and a bottom shell, the cover shell has a connecting portion, the bottom shell is connected to the connecting portion, the implantation port is arranged at an end of the bottom shell away from the cover shell, and the bottom cover is detachably connected to the bottom shell to cover the implantation port; the first electronic unit is fixed inside the cover shell, and the second electronic unit is fixed inside the bottom shell.

5. The in-body blood glucose monitoring device according to claim 4, characterized in that: The bottom shell has a fixing portion, which is interference-fitted with the second electronic unit; the bottom cover is provided with a supporting column extending toward the outer shell, and the supporting column contacts the second electronic unit to support the second electronic unit.

6. The in-body blood glucose monitoring device according to claim 1, characterized in that: The in-body blood glucose monitoring device further includes a pushing member for driving the needle-assisting unit to move along the first direction, and a resetting member for driving the puncture unit to move along the second direction. In the first direction, the pushing member and the resetting member at least partially overlap.

7. The in-body blood glucose monitoring device according to claim 1, wherein: The in-body blood glucose monitoring device further includes a trigger unit disposed at the first end, wherein the trigger unit is capable of moving or deforming along the first direction to trigger the needle-assisting unit, so that the first electronic unit and the second electronic unit can move along the first direction.

8. The in-body blood glucose monitoring device according to claim 1, wherein: The auxiliary needle unit has a first mounting groove and a second mounting groove surrounding the outer circumference of the first mounting groove. The puncture unit is arranged in the first mounting groove. A reset member for driving the puncture unit to move along the second direction is provided in the first mounting groove. A pushing member for driving the auxiliary needle unit to move along the first direction is provided in the second mounting groove.

9. The in-body blood glucose monitoring device according to claim 8, characterized in that: The puncture unit includes a needle and a needle seat. The needle seat is provided with a matching groove, and the reset member is arranged in the matching groove. The needle seat at least partially overlaps with the needle-assisting unit in the first direction.

10. The in-body blood glucose monitoring device according to claim 9, characterized in that: The in-body blood glucose monitoring device includes a support member arranged inside the shell, the support member has a first positioning portion and a second positioning portion, the first positioning portion cooperates with the first mounting groove to form a first guide channel for accommodating the reset member, and the second positioning portion cooperates with the second mounting groove to form a second guide channel for accommodating the push member.

11. The in-body blood glucose monitoring device according to claim 10, characterized in that: The first positioning portion includes a positioning protrusion protruding toward the matching groove, and one end of the reset member is connected to the positioning protrusion, and the other end is connected to the puncture unit.

12. The in-body blood glucose monitoring device according to claim 1, wherein: The needle-assisting unit is provided with a stop portion, which is used to abut and cooperate with the puncture unit and apply force to the puncture unit along the first direction; the in-body blood glucose monitoring device also includes an unlocking structure, which is located on the movement path of the stop portion, and the unlocking structure can drive the stop portion to disengage from the puncture unit.

13. The in-body blood glucose monitoring device according to claim 12, characterized in that: The stop portion includes a fixed end and a movable end, the movable end can swing around the fixed end, and the movable end is provided with a stop section extending toward the puncture unit for abutting and cooperating with the puncture unit, and a trigger section for cooperating with the unlocking structure.

14. The in-body blood glucose monitoring device according to claim 1, wherein The in-body blood glucose monitoring device also includes a locking member arranged inside the shell, which can elastically deform or move relative to the shell to have a locked state that cooperates with the auxiliary needle unit to limit the movement of the auxiliary needle unit, and an unlocked state that is loose from the auxiliary needle unit.

15. The in-body blood glucose monitoring device according to claim 14, characterized in that: A mounting seat is provided inside the shell, and the locking member has a trigger portion located on one side of the mounting seat, and an action portion located on the other side of the mounting seat and cooperating with the needle-assisting unit. The in-vivo blood glucose monitoring device also includes a trigger unit provided at the first end and cooperating with the trigger portion. When the trigger unit squeezes the trigger portion, the action portion can swing around the mounting seat to switch to the unlocked state.

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