Analyte detection system

Abstract

The utility model discloses an analyte detection system, which comprises a mounting unit and an analyte detection device, an elastic pad is sleeved on an auxiliary needle at the contact position of the auxiliary needle and the analyte detection device, and when the auxiliary needle retracts, the elastic pad can press the wound caused by the auxiliary needle puncturing into the subcutaneous part. Blood is prevented from permeating into the analyte detection device and polluting the analyte detection device, so that the normal use of the analyte detection device is ensured.

Description

TECHNICAL FIELD

[0001] The utility model mainly relates to the field of medical apparatus and instruments, in particular to an analyte detection system. BACKGROUND

[0002] The pancreas in a normal human body can automatically monitor the glucose content in the human blood and automatically secrete the required insulin / glucagon. However, the pancreas of a diabetic patient is abnormal and cannot normally secrete the required insulin. Therefore, diabetes is a metabolic disease caused by abnormal function of the human pancreas, and diabetes is a lifelong disease. At present, medical technology cannot cure diabetes, and can only control the occurrence and development of diabetes and its complications by stabilizing blood sugar.

[0003] A diabetic patient needs to detect blood sugar before injecting insulin into the body. Most current detection methods can continuously detect blood sugar and send blood sugar data to a remote device in real time for the user to view. This detection method is called continuous glucose monitoring (CGM) method. The method requires a detection device to be attached to the skin surface, and a sensor carried by the installation device is inserted into the subcutaneous tissue fluid to complete the detection. However, when the sensor is inserted into the subcutaneous tissue, it may pierce a blood vessel, and the pressure of the subcutaneous tissue increases after the sensor is inserted into the subcutaneous tissue, which causes blood to flow to the skin surface along the electrode of the sensor, or even penetrate to the inner bottom surface of the analyte detection device, causing contamination inside the analyte detection device, affecting the normal use of the analyte detection device, or even causing a short circuit at the electrical connection between the sensor and the transmitter, making the analyte detection device completely unusable.

[0004] Therefore, the prior art urgently needs an analyte detection system that can prevent blood from penetrating into the interior. SUMMARY

[0005] The utility model discloses an analyte detection system, including installation unit and analyte detection device, in the position of the contact of auxiliary needle and analyte detection device lower shell, a elastic pad is set on auxiliary needle, when auxiliary needle retracts, elastic pad can seal the first through -hole of lower shell, prevent blood from penetrating to the inside of analyte detection device through the first through -hole, pollute analyte detection device, affect the normal use of analyte detection device.

[0006] The utility model provides an analyte detection system, including installation unit and analyte detection device, installation unit is used for installing analyte detection device on the user skin surface, at least including auxiliary needle, auxiliary needle at least includes opening area, analyte detection device at least includes transmitter, sensor, shell and battery, and the sensor includes in-vivo part and extracorporeal part, and the shell includes upper shell and lower shell, and still be provided with first through -hole on the lower shell, before installation, auxiliary needle passes through the lower shell from first through -hole, and opening area envelope in-vivo part, and elastic pad, set up in the position of lower shell and auxiliary needle contact, and set up in the outside of auxiliary needle.

[0007] According to an aspect of the utility model, the elastic pad is set on the outside or the inside of the lower shell.

[0008] According to an aspect of the utility model, the elastic pad is a hollow structure, and the inner diameter of the elastic pad is smaller than the outer diameter of the opening area.

[0009] According to an aspect of the utility model, the inner diameter of the elastic pad is smaller than the outer diameter of the in-vivo part.

[0010] According to an aspect of the utility model, the elastic pad is a solid structure, and the elastic pad is set on the outside of the auxiliary needle after being pierced by the opening area.

[0011] According to an aspect of the utility model, the thickness of the elastic pad is 0.01-5mm.

[0012] According to an aspect of the utility model, the thickness of the elastic pad is 0.3mm.

[0013] According to an aspect of the utility model, the material of the elastic pad is one of rubber, silicone or latex.

[0014] According to an aspect of the utility model, the elastic pad is fixed on the outside or the inside of the lower shell.

[0015] According to an aspect of the utility model, the fixing mode of the elastic pad at least includes double -sided adhesive paste, hot melt or ultrasonic welding.

[0016] According to an aspect of the utility model, the lower shell is provided with a first accommodating groove for accommodating the elastic pad.

[0017] According to an aspect of the utility model, the outer diameter of the elastic pad is greater than the diameter of the first accommodating groove.

[0018] According to an aspect of the utility model, the inside of the lower shell is provided with a second accommodating groove for accommodating the elastic pad.

[0019] According to an aspect of the utility model, the thickness of the elastic pad is greater than the depth of the second accommodating groove. According to an aspect of the utility model, the elastic pad is set between the inside of the lower shell and the bending part of the sensor.

[0020] According to one aspect of the present application, the analyte detection device and the mounting unit are in a separated state.

[0021] According to one aspect of the present application, the analyte detection device is built-in the mounting unit before installation.

[0022] Compared with the prior art, the technical scheme of the present application has the following advantages:

[0023] In the analyte detection system disclosed by the present application, the elastic pad is sleeved on the auxiliary needle, and when the auxiliary needle is retracted, the elastic pad can seal the first through hole of the lower shell, preventing blood from penetrating into the interior of the analyte detection device from the first through hole, polluting the analyte detection device and affecting the normal use of the analyte detection device.

[0024] Further, the elastic pad can be selectively arranged on the outside or the inside of the lower shell, increasing the flexibility of design.

[0025] Further, the outer diameter of the elastic pad is greater than the diameter of the first through hole, which can further prevent blood from penetrating into the interior of the analyte detection device.

[0026] Further, the elastic pad is fixed on the outside or the inside of the lower shell, preventing the elastic pad from moving when the auxiliary needle is retracted, so as to affect the blocking of the elastic pad to blood.

[0027] Further, the lower shell is provided with a first accommodating groove, and the elastic pad is embedded into the first accommodating groove, thereby reducing the pressure of the elastic pad on the skin surface and reducing the discomfort.

[0028] Further, the outer diameter of the elastic pad is slightly greater than the diameter of the accommodating groove, and the elastic pad is tightly embedded in the accommodating groove through interference fit, preventing the elastic pad from moving and thereby affecting the blocking of the elastic pad to blood.

[0029] Further, the lower shell is provided with a second accommodating groove, and the thickness of the elastic pad is slightly greater than the depth of the second accommodating groove, so that when the elastic pad is accommodated in the second accommodating groove, the elastic pad is slightly compressed, and the elastic pad abuts against the inside of the lower shell with elasticity, thereby achieving a tight seal of the first through hole, preventing blood from penetrating into the interior of the analyte detection device from the first through hole, polluting the analyte detection device and affecting the normal use of the analyte detection device. BRIEF DESCRIPTION OF DRAWINGS

[0030] Figure 1 FIG. 1 is a schematic view of the external structure of the analyte detection device mounting unit according to an embodiment of the present application;

[0031] Figure 2a FIG. 2 is a schematic view of the external structure of the shell according to an embodiment of the present application;

[0032] Figure 2b Structure diagram of the protective cover according to the embodiment of the present application;

[0033] Figure 3 Explosive structure diagram of the analyte detection device installation unit according to the embodiment of the present application;

[0034] Figure 4 Structure diagram of the analyte detection device according to the present application;

[0035] Figure 5a Diagram showing that the elastic pad is arranged outside the auxiliary needle before installation according to the present application;

[0036] Figure 5b Diagram showing that the elastic pad is arranged outside the auxiliary needle after the auxiliary needle is inserted into the subcutaneous tissue according to the present application;

[0037] Figure 5c Diagram showing that the elastic pad is arranged outside the sensor after the auxiliary needle is retracted according to the present application;

[0038] Figure 5d Structure diagram showing that the elastic pad is embedded outside the lower shell of the analyte detection device according to the present application;

[0039] Figure 5e Structure diagram showing that the elastic pad is embedded inside the lower shell of the analyte detection device according to the present application;

[0040] Figure 5f Structure diagram showing that the elastic pad is solid according to the present application;

[0041] Figure 5g Structure diagram showing that the elastic pad is hollow according to the present application;

[0042] Figure 6a Structure diagram of the analyte detection device with a siphon structure according to the present application;

[0043] Figure 6b is Figure 6a Local enlarged structure diagram of the M area;

[0044] Figures 6c-6f Top view of the siphon structure according to the present application;

[0045] Figure 6g Structure diagram of another analyte detection device with a siphon structure according to the present application. DETAILED DESCRIPTION

[0046] As described above, the prior art analyte detection device may be pricked into a blood vessel when the sensor is pricked into the subcutaneous tissue during installation, and blood may flow to the surface of the skin along the electrode of the sensor or even penetrate into the inner bottom surface of the analyte detection device due to the increased pressure in the subcutaneous tissue after the sensor is pricked into the subcutaneous tissue, which causes the internal pollution of the analyte detection device, affects the normal use of the analyte detection device, or even causes the short circuit of the electrical connection between the sensor and the transmitter, so that the analyte detection device cannot be used at all.

[0047] To solve the problem, the utility model provides an analyte detection system, a elastic pad is sleeved on the auxiliary needle at the position where the auxiliary needle and the analyte detection device contact, when the auxiliary needle is retracted, the elastic pad can press the wound caused by the auxiliary needle pricked into the subcutaneous tissue, prevent blood from penetrating into the inside of the analyte detection device, pollute the analyte detection device, affect the normal use of the analyte detection device.

[0048] Various exemplary embodiments of the utility model will now be described in detail with reference to the accompanying drawings. It should be understood that the relative arrangement, numerical expression and values of the components and steps set forth in these embodiments should not be understood as limiting the scope of the utility model unless otherwise specifically stated.

[0049] In addition, it should be understood that the sizes of the various components shown in the drawings are not necessarily drawn in accordance with the actual proportional relationship, for example, the thickness, width, length or distance of certain units can be enlarged relative to other structures.

[0050] The following description of the exemplary embodiments is merely illustrative in nature and is in no way intended to limit the present utility model and its application or use in any way. Techniques, methods, and devices known to those of ordinary skill in the relevant art can not be discussed in detail herein, but should be considered part of the present specification when applicable.

[0051] It should be noted that similar reference numbers and letters represent similar items in the following drawings, so once an item is defined or described in one drawing, it will not need to be further discussed in the subsequent drawing description.

[0052] The analyte detection system comprises a mounting unit of the analyte detection device and an analyte detection device built in the mounting unit. Figure 1An external structure schematic diagram of the analyte detection device installation unit is shown in the embodiment of the utility model. The external structure of the installation unit 100 comprises a shell 101 and a protective cover 102, and the shell 101 is used for bearing internal structural members. When the installation unit 100 is used, the end close to the skin of a user is the proximal end, and the end away from the skin is the distal end. A first opening is arranged at the proximal end of the shell 101. The protective cover 102 is used for protecting, sealing and preventing triggering of the internal structure and the internal structural members of the shell 101.

[0053] Figure 2a An external structure schematic diagram of the shell is shown in the embodiment of the utility model, Figure 2b An external structure schematic diagram of the shell is shown in the embodiment of the utility model,

[0054] The inner side of the outer cover 1021 is provided with an internal thread 10212, and correspondingly, the outer side of the inner cover 1023 is provided with an external thread 10231, and the internal thread 10212 and the external thread 10231 can be connected in cooperation to connect the outer cover 1021 and the inner cover 1023 together and keep fixed.

[0055] The inner side of the outer cover 1021 is provided with an internal thread 10212, and correspondingly, the outer side of the inner cover 1023 is provided with an external thread 10231, and the internal thread 10212 and the external thread 10231 can be connected in cooperation to connect the outer cover 1021 and the inner cover 1023 together and keep fixed.

[0056] In other embodiments of the utility model, the outer cover 1021 and the inner cover 1023 can also be fixedly connected through frictional cooperation or clamping cooperation.

[0057] In other embodiments of the utility model, the outer cover 1021 and the inner cover 1023 can also be fixedly connected through frictional cooperation or clamping cooperation.

[0058] Figure 3The exploded structural schematic view of the analyte detection device mounting unit is shown in the figure. The dotted line in the figure represents the mounting and cooperation relationship of each structural member. The internal structural members of the analyte detection device mounting unit 100 include a parallel sliding block module 103, an analyte detection device 104, an auxiliary needle module 105, a trigger module 106 and an elastic module 107. The elastic module 107 includes a first elastic member 1071 and a second elastic member 1072.

[0059] The analyte detection device 104 and the mounting unit 100 are not limited to Figure 3 The cooperation relationship. In some embodiments of the present application, before installation, the analyte detection device 104 is built into the mounting unit 100, and the user can install the analyte detection device 104 on the surface of the human skin by taking the mounting unit 100 out of the packaging box. In some other embodiments of the present application, before installation, the analyte detection device 104 and the mounting unit 100 are in a separated state, that is, the user needs to take the mounting unit 100 and the analyte detection device 104 out of the packaging box respectively, and then assemble the analyte detection device 104 into the mounting unit 100, and then the analyte detection device 104 can be installed on the surface of the human skin.

[0060] Figure 4 The structural schematic view of the analyte detection device is shown in the figure. Figure 3 In the embodiments of the present application, the analyte detection device 104 includes a shell 1041, a transmitter (not shown in the figure), a sensor 1042, a battery (not shown in the figure) and an internal circuit (not shown in the figure) arranged in the shell 1041 and electrically coupled with the sensor. The sensor 1042 is used to detect the analyte parameter information of the user's body fluid, and the above analyte parameter information is transmitted to the transmitter through the internal circuit, and then transmitted to the external device 200 by the transmitter.

[0061] In the embodiments of the present application, the shell 1041 includes an upper shell 10411 and a lower shell 10413, and the upper shell 10411 and the lower shell 10413 are spliced to form an internal space. The sensor 1042 includes an extracorporeal part and an intracorporeal part, and the extracorporeal part is bent relative to the intracorporeal part, as shown in FIG. 5a. The extracorporeal part, the transmitter, the battery and the internal circuit are arranged in the internal space, and the extracorporeal part is electrically coupled with the internal circuit. The intracorporeal part is provided with electrodes, film layers and other structures, and can detect analyte parameter information by penetrating into the subcutaneous tissue of the user. When the intracorporeal part penetrates into the subcutaneous tissue, a correct angle is required, for example, perpendicular to the skin surface. After the service life of the analyte detection device 104 ends, it is taken off from the surface of the user's skin and discarded as a whole.

[0062] In the embodiment of the utility model, the lower shell 10413 includes a first through hole 10414, and correspondingly, the upper shell 10411 includes a second through hole (not shown in the figure) on the axis of the first through hole 10414, and the in-vivo part of the sensor 1042 passes through the first through hole 10414 to the outside of the shell, so as to be easily inserted into the subcutaneous tissue of the user.

[0063] In other embodiments of the utility model, the analyte detection device 104 is not limited to the above structure. In some other embodiments of the utility model, the transmitter is arranged outside the shell 1041, and after the user installs the shell 1041 to the surface of the skin of the user through the installation unit 100, the transmitter is installed on the shell 1041.

[0064] In some other embodiments of the utility model, when the transmitter is separated from the shell 1041, the battery is built in the transmitter.

[0065] In some other embodiments of the utility model, when the transmitter is separated from the shell 1041, the battery is built in the shell 1041.

[0066] The auxiliary needle module 105 includes an auxiliary needle fixing structure 1051 and an auxiliary needle 1052, the auxiliary needle 1052 at least includes an opening area for accommodating the sensor 1042, and in the installation unit 100, the auxiliary needle 1052 sequentially passes through the second through hole and the first through hole 10414, so as to pass through the analyte detection device 104.

[0067] When the installation unit 100 is used, the outer cover body 1021 is rotated, the stand column 10211 is broken, the protective cover 102 is separated from the shell 101, the proximal end of the installation unit 100 is close to the skin of the user, until the outer ring of the trigger module 106 is attached to the surface of the skin, the user presses the shell 101 at the distal end, the shell 101 moves towards the skin, and the trigger module 106 remains stationary, so that the trigger module 106 moves towards the distal end relative to the shell 101, the parallel slider module 103 continues to move towards the proximal end under the pushing force of the first elastic member 1071, and simultaneously drives the auxiliary needle module 105 and the analyte detection device 104 to move towards the proximal end, the in-vivo part of the auxiliary needle 1052 and the sensor enveloped thereby is inserted into the subcutaneous tissue, until the analyte detection device 104 is in contact with the surface of the skin of the user. Under the pushing of the second elastic member 1072, the auxiliary needle module 105 moves towards the distal end, and finally returns to the initial position, the in-vivo part of the sensor of the analyte detection device 104 remains in the body, the auxiliary needle 1052 is retracted into the shell 101, so as to prevent the auxiliary needle 1052 from being exposed outside the shell 101, and avoid unnecessary harm.

[0068] When the auxiliary needle 1052 penetrates into the skin, it can pierce a blood vessel, and because the pressure under the skin increases after the auxiliary needle 1052 penetrates into the skin, after the auxiliary needle 1052 is retracted, blood can flow along the in-vivo part of the analyte detection device 104 to the skin surface, even penetrate into the inner bottom surface of the analyte detection device 104 through the first through hole 10414, causing contamination inside the analyte detection device 104, affecting the normal use of the analyte detection device, and even causing a short circuit at the electrical connection between the sensor and the transmitter, making the analyte detection device completely unusable.

[0069] Referring to Figure 5a , Figure 5a Figure 1 is a schematic view of the analyte detection device 104 according to the present application, and Figure 2 is a schematic view of the analyte detection device 104 according to the present application before installation. In order to solve the above problems, in some embodiments of the present application, before installation, an elastic pad 108 is sleeved outside the auxiliary needle 1052 at the contact position of the auxiliary needle 1052 and the analyte detection device 104 on the outside of the lower housing 10413. The needle body envelopes the in-vivo part 10422 of the sensor 1042. When installed, the auxiliary needle 1052 carrying the in-vivo part 10422 penetrates into the skin, the lower housing body 10413 of the analyte detection device 104 contacts the skin surface, and presses the elastic pad 108, as shown in Figure 3. Figure 5b Figure 5b Figure 4 is a schematic view of the elastic pad sleeved outside the auxiliary needle after the auxiliary needle penetrates into the skin according to the present application.

[0070] Referring to Figure 5c , Figure 5c Figure 5 is a schematic view of the elastic pad sleeved outside the sensor after the auxiliary needle is retracted according to the present application. In some embodiments of the present application, after the auxiliary needle 1052 carrying the in-vivo part 10422 penetrates into the skin to a predetermined position, it is retracted, leaving the in-vivo part 10422 remaining in the skin to detect analyte parameter information. The analyte detection device 104 is adhered to the skin surface under the action of the adhesive tape, so when the auxiliary needle 1052 is retracted, the elastic pad 108 is clamped between the lower housing body 10413 and the skin surface. After the auxiliary needle 1052 is completely retracted, the elastic pad 108 is contracted and sleeved outside the in-vivo part 10422 under the action of its own elasticity, pressing and covering the wound caused by the penetration of the auxiliary needle 1052 into the skin. This can prevent blood from overflowing from the wound and entering the inside of the analyte detection device 104 through the first through hole 10414, contaminating the analyte detection device 104, ensuring the normal use of the analyte detection device 104, and also preventing foreign matter from the outside from contaminating the wound, improving the healing speed of the wound.

[0071] The outer diameter d1 of the elastic pad 108 is greater than the diameter of the first through hole 10414, which can further prevent blood from penetrating into the inside of the analyte detection device 104.

[0072] ​In order to prevent the elastic pad 108 from moving during installation, such as when the auxiliary needle retracts, thereby affecting the blocking of the elastic pad 108 to the blood, in other embodiments of the present application, the elastic pad 108 is fixed on the outside of the lower shell 10413 of the analyte detection device 104 by means of double-sided tape, hot welding or ultrasonic welding, etc. The auxiliary needle 1052 passes through the first through hole 10414 and the elastic pad 108 concentrically.

[0073] Referring to Figure 5d , Figure 5d The structure diagram of the elastic pad embedded in the lower shell of the analyte detection device according to the present application, in some embodiments of the present application, a first accommodating groove 104131 is arranged on the outside of the lower shell 10413 of the analyte detection device 104, for accommodating the first elastic pad 108, and correspondingly, the first through hole 10414 is sunk into the inside of the lower shell 10413, so that after installation, the elastic pad 108 is flush with the lower shell 10413, so that the elastic pad 108 does not cause additional extrusion to the skin surface, thereby reducing discomfort. The outer diameter of the elastic pad 108 is greater than the diameter of the first through hole 10414, so that the elastic pad can completely block the first through hole 10414, preventing blood from penetrating from the first through hole 10414 to the inside of the analyte detection device 104. The outer diameter of the elastic pad 108 is slightly larger than the inner diameter of the first accommodating groove 104131, so that the elastic pad 108 is tightly embedded in the first accommodating groove 104131 by interference fit.

[0074] Referring to Figure 5e , Figure 5e The structure diagram of the elastic pad embedded in the lower shell of the analyte detection device according to the present application, in some embodiments of the present application, the elastic pad 108 is arranged on the inside of the lower shell 10413, the extracorporeal part 10421 of the sensor 1042 is bent relative to the intracorporeal part 10422, and the elastic pad 108 is clamped between the lower shell 10413 and the bent area of the sensor 1042. After the auxiliary needle 1052 is completely retracted, the elastic pad 108 is retracted and set on the outside of the intracorporeal part 10422 under the action of its own elasticity, thereby sealing the first through hole 10414, which can prevent blood from entering the inside of the analyte detection device 104 from the first through hole 10414, thereby preventing the analyte detection device 104 from being contaminated, and ensuring the normal use of the analyte detection device 104.

[0075] In order to prevent the elastic pad 108 from moving during installation, such as when the auxiliary needle retracts, thereby affecting the blocking of the elastic pad 108 to the blood, in other embodiments of the present application, the elastic pad 108 is fixed on the inside of the lower shell 10413 of the analyte detection device 104 by means of double-sided tape, hot welding or ultrasonic welding, etc. The auxiliary needle 1052 passes through the first through hole 10414 and the elastic pad 108 concentrically.

[0076] In another embodiment of the present application, the lower shell 10413 of the analyte detection device 104 is internally provided with a second accommodating groove 104132 for accommodating the elastic pad 108. The depth of the second accommodating groove 104132 is slightly smaller than the thickness of the elastic pad 108. Therefore, when the elastic pad 108 is accommodated in the second accommodating groove 104132, the elastic pad is slightly compressed in the vertical direction. The elastic pad 108 abuts against the first through hole 10414 and the second accommodating groove 104132 of the lower shell 10413 with a certain elasticity. At the same time, the outer diameter of the elastic pad 108 is slightly larger than the inner diameter of the second accommodating groove 104132. Therefore, the elastic pad 108 is tightly embedded in the second accommodating groove 104132 through interference fit. Thus, the elastic pad 108 can tightly seal the first through hole 10414, preventing blood from entering the interior of the analyte detection device 104 from the first through hole 10414 to contaminate the analyte detection device 104, and ensuring normal use of the analyte detection device 104.

[0077] Referring to Figure 5f , Figure 5f In some embodiments of the present application, the elastic pad 108 can be solid. After the auxiliary needle 1052 pierces the elastic pad 108, the elastic pad 108 is sleeved outside the auxiliary needle 1052.

[0078] Figure 5g In some embodiments of the present application, the elastic pad 108 can be hollow. The inner diameter d2 of the elastic pad 108 is smaller than the outer diameter d of the auxiliary needle 1052, so that the elastic pad 108 can be tightly sleeved outside the auxiliary needle 1052 to prevent the in-vivo part 10422 from separating from the envelope of the auxiliary needle 1052. In the preferred embodiment of the present application, the inner diameter d2 of the elastic pad 108 is also smaller than the outer diameter of the in-vivo part 10422. After the auxiliary needle 1052 is retracted, the elastic pad 108 can be contracted and tightly sleeved outside the in-vivo part 10422 to press and cover the wound caused by the auxiliary needle 1052 piercing the subcutaneous tissue (when the elastic pad 108 is arranged outside the lower shell 10413), or tightly seal the first through hole 10414 (when the elastic pad 108 is arranged inside the lower shell 10413), preventing blood from overflowing from the wound and entering the interior of the analyte detection device 104 from the first through hole 10414 to contaminate the analyte detection device 104.

[0079] In some embodiments of the present application, the thickness of the elastic pad 108 is 0.01-5mm. When the elastic pad 108 is arranged on the outside of the lower shell 10413, the excessive thickness of the elastic pad 108 will increase the pressure of the analyte detection device 104 on the skin surface, causing discomfort. When the elastic pad 108 is arranged on the inside of the lower shell 10413, the excessive thickness of the elastic pad 108 will increase the height of the analyte detection device 104, which is not conducive to the miniaturization of the analyte detection device 104. The excessive thinness of the elastic pad 108 will easily cause deformation, and the in-vivo part 10422 cannot be effectively constrained. In the preferred embodiments of the present application, the thickness of the elastic pad 108 is 0.3mm.

[0080] In some embodiments of the present application, the material of the elastic pad 108 is one of rubber, silicone or latex, which has good elasticity and can avoid contamination of the wound.

[0081] Figure 6a Figure 2 is a structural schematic view of the analyte detection device with a siphon structure according to the present application; Figure 6b Figure 3 is a sectional view of the analyte detection device with a siphon structure according to the present application; Figure 6a Figure 4 is a partial enlarged structural schematic view of the M area in Figure 3; Figures 6c-6f Figure 5 is a top view of the siphon structure according to the present application.

[0082] Reference Figures 6a-6f In other embodiments of the present application, the lower shell 10413 of the analyte detection device 104 is provided with a siphon structure, which includes a hydrophilic membrane 601 and a cooperating structure 602. The cooperating structure 602 is arranged on the lower shell 10413, and the hydrophilic membrane 601 is arranged on the cooperating structure 602. The hydrophilic membrane 601, the cooperating structure 602 and the lower shell 10413 form a gap 603 therebetween. When the auxiliary needle 1052 is retracted and blood overflows along the wound, the hydrophilic membrane 601 attracts the blood and guides it to a position away from the first through hole 10414 along the gap 603, as indicated by the arrow in Figures 6b-6f Figure 6, thereby preventing the blood from penetrating into the interior of the analyte detection device 104 through the first through hole 10414, avoiding contamination of the interior of the analyte detection device 104, affecting the normal use of the analyte detection device 104, and even causing short circuit of the sensor 1042, internal circuit and electrical connection of the battery, resulting in damage to the analyte detection device 104.

[0083] The height or thickness h of the cooperating structure 602 is the depth h of the gap 603. In the present application, the depth h of the gap 603 is 0.02mm-0.5mm, preferably 0.05mm-0.3mm, and more preferably 0.1mm. At this depth, the siphon effect of the siphon structure is the strongest, which is conducive to attracting blood and guiding it to a position away from the first through hole.

[0084] The material of the hydrophilic film 601 includes one or more of a polymer film, a glass film, a polyester film, a polyurethane film, a polytetrafluoroethylene film, and a polyacrylic acid film. Preferably, the material of the hydrophilic film 601 is a polymer film, and the polymer material has strong hydrophilicity, which can effectively improve the wetting performance of the material surface and make the material have better adhesion and stability.

[0085] In an embodiment of the utility model, the gap 603 includes a slot gap 6031. The matching structure 602 has multiple structures, which are distributed along the circumference of the first through hole 10414. The hydrophilic film 601 and the lower shell 10413 form multiple slot gaps 6031. Preferably, the multiple matching structures 602 are evenly distributed along the circumference of the first through hole 10414 on the lower shell 10413. Therefore, the multiple slot gaps 6031 are also evenly distributed between the hydrophilic film 601 and the lower shell 10413 along the circumference of the first through hole 10414. When blood spills from the wound, the hydrophilic film 601 attracts the blood and guides the blood to spread evenly in all radial directions from the circumference of the first through hole 10414. This prevents the blood from being guided or spread in a certain direction in time, causing the blood to gather in a certain direction, so that the blood enters the interior of the analyte detection device 104 from this direction of the first through hole 10414, avoiding pollution in the interior of the analyte detection device 104 and affecting the normal use of the analyte detection device 104.

[0086] In an embodiment of the utility model, the slot gap 6031 is a radial gap. The cross section of the slot gap 6031 can be square, circular, trapezoidal, or other irregular shapes. Preferably, the cross section is trapezoidal, and the side close to the skin is the lower side of the trapezoid. The closer to the skin, the greater the blood flow, and the trapezoidal cross section is more adaptable to the change in blood flow. The starting end of the slot gap 6031 is close to the wound, and the cross-sectional area of the starting end is k1. The terminal end is close to the terminal end A2 of the hydrophilic film 601, and the cross-sectional area of the terminal end is k2. k1 is not less than k2. The bleeding amount is large at the position close to the wound, and k1 is greater, which can more quickly attract blood to a position far from the first through hole 10414. When the blood spreads to the terminal end close to the gap 603, the blood flow may be very small, or even no blood continues to spread. Therefore, k2 can be smaller than k1, but in order to ensure that there is enough space for the blood to move away from the first through hole 10414 and the blood does not gather, k2 can be equal to k1.

[0087] In the utility model, gap 603 includes annular gap 6032. Hydrophilic film 601 includes positioning hole 6011, positioning hole 6011 corresponds with first through hole 10414, the correspondence here refers to that the position and size of positioning hole 6011 and first through hole 10414 are all consistent, that is, positioning hole 6031 and first through hole 10414 overlap in vertical direction. The circumference edge of positioning hole 6011 is the starting end A1 of hydrophilic film 601, the starting end B1 of cooperation structure 602 is spaced apart from the starting end A1 of hydrophilic film 601 by distance l1, so first annular gap 6032 with height h and width l1 can be formed along the circumference of positioning hole 6011, the starting end of first annular gap 6032 is the edge of first through hole 10414 and positioning hole 6011, and the terminal end of first annular gap 6032 is the starting end B1 of cooperation structure 602. Siphon phenomenon can be formed along the circumference of positioning hole 6011, so that the blood flowing along the sensor body inner part 10422 is rapidly attracted to first annular gap 6032 from the circumference edge of positioning hole 6011, and then is guided to the position away from first through hole 10414 along groove gap 6031, so that it is further ensured that the blood does not penetrate from first through hole 10414 to the inside of analyte detection device 104. In the embodiment of the utility model, width l1 is 0.02-0.35mm, preferably, width l1 is 0.1-0.2mm.

[0088] In another embodiment of the utility model, gap 603 can also only include annular gap 6032, as shown in Figure 6e and Figure 6f In order to accommodate sufficient blood in annular gap 6032 and prevent the blood from entering the inside of analyte detection device from first through hole 10414 after gathering, width l1 of annular gap 6032 is 1.5-2mm, in Figure 6e , cooperation structure 602 is a circular ring structure arranged along the edge of the terminal end A2 of hydrophilic film 601, in Figure 6f , cooperation structure 602 is a plurality of discrete structures arranged along the edge of the terminal end A2 of hydrophilic film 601, preferably, the plurality of discrete structures are uniformly distributed along the edge of the terminal end A2 of hydrophilic film 601. Since hydrophilic film 601, cooperation structure 602 and lower housing 10413 also form a gap along the edge of the terminal end A2 of hydrophilic film 601, when the blood is relatively much and diffuses to the edge of the terminal end A2 of hydrophilic film, the blood can further diffuse to adhesive tape 604. Since adhesive tape 604 is non-woven adhesive tape, the blood can be infiltrated in adhesive tape 604, so that the blood is prevented from penetrating to the inside of analyte detection device 104 from first through hole 10414 after gathering.

[0089] In the embodiment of the utility model, the terminal end B2 of the cooperation structure 602 is aligned with the terminal end A2 of the hydrophilic membrane 601, therefore, the length of the groove gap 6031 is the radial length L of the hydrophilic membrane 601. In other embodiments of the utility model, the terminal end B2 of the cooperation structure 602 is not aligned with the terminal end A2 of the hydrophilic membrane 601, therefore, the length of the groove gap 6031 can also not equal the radial length L of the hydrophilic membrane 601.

[0090] When the terminal end B2 of the cooperation structure 602 is aligned with the terminal end A2 of the hydrophilic membrane 601, if the blood can continue to diffuse after being guided to the terminal end B2 of the cooperation structure 602 along the gap 603, the blood will further diffuse to the adhesive tape 604. Since the adhesive tape 604 is a non-woven adhesive tape, the blood can be infiltrated in the adhesive tape 604, preventing the blood from gathering and permeating to the inside of the analyte detection device 104 from the first through hole 10414.

[0091] When the terminal end B2 of the cooperation structure 602 does not reach the terminal end A2 of the hydrophilic membrane 601, the distance is l2, as shown in Figure 6d the second annular gap 6033 with a width of l2 and a depth of h is formed between the hydrophilic membrane 601, the cooperation structure 602 and the lower shell 10413 at the outer circumference of the hydrophilic membrane 601, the starting end of the second annular gap 6033 is the terminal end B2 of the cooperation structure, and the terminal end of the second annular gap 6033 is the terminal end A2 of the hydrophilic membrane 601. If the blood can continue to diffuse after being guided to the terminal end B2 of the cooperation structure 602 along the groove gap 6031, the blood will diffuse to the terminal end A2 of the hydrophilic membrane in the radial direction, that is, when the terminal end B2 of the cooperation structure 602 does not reach the terminal end A2 of the hydrophilic membrane 601, the length of the groove gap 6031 is also the radial length L of the hydrophilic membrane 601. The blood will diffuse to the second annular gap 6033 with a width of l2 and a depth of h in the circumferential direction, which can accommodate more blood and better prevent the blood from gathering. In the embodiment of the utility model, the width l2 is 0.02-0.55mm, preferably, the width l2 is 0.2-0.4mm, more preferably, the width l2 is 0.3mm.

[0092] In other embodiments of the utility model, by appropriately setting the cooperation structure 602, more annular gaps can also be provided between the first annular gap 6032 and the second annular gap 6033, for example, each cooperation structure 602 is divided in the radial direction at the midpoint, and the width of the division is l3, that is, a third annular gap with a width of l3 and a height of h is formed between the lower shell 10413, the cooperation structure 602 and the hydrophilic membrane 601.

[0093] When the terminating end B2 of the mating structure 602 extends beyond the terminating end A2 of the hydrophilic membrane 601, at least a portion of the adhesive tape 604 covers the mating structure 602. An extended gap is also formed between the adhesive tape 604, the mating structure 602, and the lower outer shell 10413. That is, when the terminating end B2 of the mating structure 602 extends beyond the terminating end A2 of the hydrophilic membrane 601, the length of the groove-shaped gap 6031 is greater than the radial length L of the hydrophilic membrane. This extended gap lies on the extension line of the groove-shaped gap 6031. If blood, after being guided along the groove-shaped gap 603 to the terminating end B2 of the mating structure 602, can continue to diffuse, it will further diffuse into this extended gap, further accommodating more blood and better preventing blood aggregation.

[0094] refer to Figure 6a and Figure 6b An adhesive tape 604 is provided on the lower outer shell 10413 of the analytical substance detection device 104 of this utility model. In order to avoid the auxiliary needle module 105 during puncture, the adhesive tape 604 is provided with an avoidance hole 6041. The avoidance hole 6041 is concentric with the first through hole 10414, but the diameter of the avoidance hole 6041 is larger than the diameter of the first through hole 10414. The hydrophilic membrane 601 and the mating structure 602 are disposed in the clearance hole 6041 of the adhesive tape 604. The edges of the hydrophilic membrane 601 and the mating structure 602 are adjacent to the edges of the clearance hole 6041 of the adhesive tape 604. That is, the terminating end A2 of the hydrophilic membrane 601 and the terminating end B2 of the mating structure 602 are adjacent to the starting end C1 of the adhesive tape 604. At the same time, the thickness of the adhesive tape 604 is equal to the sum of the thicknesses of the hydrophilic membrane 601 and the mating structure 602, so that the adhesive tape 604 and the hydrophilic membrane 601 on the lower outer shell 10413 of the analyte detection device 104 are on the same plane, reducing user discomfort and improving user experience.

[0095] In another embodiment of this utility model, the hydrophilic membrane 601 and the adhesive tape 604 are an integral structure. That is, the lower surface of the adhesive tape 604, i.e., the side closest to the skin, is cleaned and treated to remove grease and impurities, ensuring a clean surface. The hydrophilic membrane 601 is evenly coated onto the lower surface of the adhesive tape 604 using a suitable coating tool. After coating, the adhesive tape is allowed to air dry or dried with hot air to ensure the hydrophilic membrane adheres firmly to the tape. Simultaneously, a portion of the hydrophilic membrane 601 also covers the mating structure 602, such as... Figure 6e As shown, the hydrophilic membrane and adhesive tape are integrated into one structure. This increases the integration between the two, while the hydrophilic membrane 601 improves the wettability of the adhesive tape 604, making it easier to contact the skin and thus enhancing adhesion. The wettability of the hydrophilic membrane 604 helps prevent moisture penetration, extending the service life of the adhesive tape 604. By increasing wettability, the hydrophilic membrane 601 can reduce friction and discomfort during use of the adhesive tape 604.

[0096] In an embodiment of the utility model, cooperation structure 602 is double -sided adhesive layer, double -sided adhesive layer includes the double -sided adhesive of spacing setting in hydrophilic membrane 601, and one side of double -sided adhesive pastes lower shell 10413, and the other side pastes hydrophilic membrane 601, and double -sided adhesive layer, hydrophilic membrane 601 and the lower shell 10413 of analyte detection device 104 form gap, through the setting of the shape, thickness, length, quantity, position etc. of double -sided adhesive, the gap formed includes the groove type gap and annular gap, and the characteristics of groove type gap and annular gap are also as the characteristics of groove type gap and annular gap.

[0097] In another embodiment of the utility model, cooperation structure 602 is the flow guide groove set up on lower shell 10413, and hydrophilic membrane 601 is pasted on lower shell 10413 by double -sided adhesive or is fixed on lower shell 10413 by hot melt or ultrasonic welding mode. Flow guide groove includes groove type flow guide groove and annular flow guide groove, and through the setting of the shape, thickness, length, quantity, position etc. of flow guide groove, the groove type gap and annular gap of lower shell 10413, flow guide groove and hydrophilic membrane 601 can also be formed, and the characteristics of groove type gap and annular gap are also as the characteristics of groove type gap and annular gap.

[0098] In still another embodiment of the utility model, cooperation structure 602 is the convex strip and / or convex block set on lower shell 10413, and the convex strip and / or convex block and lower shell 10413 can be integrally formed, can be connected by friction fit, buckle fit, or be connected by double -sided adhesive pasting, hot melt or ultrasonic welding mode, preferably, the convex strip and / or convex block and lower shell 10413 can be integrally formed. Hydrophilic membrane 603 is set on the convex strip and / or convex block by double -sided adhesive pasting, hot melt or ultrasonic welding mode. Through the setting of the shape, thickness, length, quantity, position etc. of convex strip and / or convex block, the gap formed includes the groove type gap and annular gap, and the characteristics of groove type gap and annular gap are also as the characteristics of groove type gap and annular gap.

[0099] In other embodiments of the utility model, cooperation structure 602 can also be any other possible structure, and here does not limit its specific structure form, and does not limit the setting mode of structure, as long as cooperation structure 602 can form gap 603 between lower shell 10413, hydrophilic membrane 601, when auxiliary needle 1052 is retracted, blood overflows along the wound, hydrophilic membrane 601 attracts blood and guides blood to the position far from first through -hole 10414 along gap 603, so that blood can be prevented from penetrating into the inside of analyte detection device 104 through first through -hole 10414.

[0100] In summary, the utility model discloses an analyte detection system, including installation unit and analyte detection device, in lower shell outside, the position of auxiliary needle and analyte detection device contact, set up an elastic pad on auxiliary needle, when auxiliary needle retracts, elastic pad can press the wound caused by the subcutaneous puncture of auxiliary needle, prevent blood penetration to the inside of analyte detection device, pollute analyte detection device, influence the normal use of analyte detection device.

[0101] Although some specific embodiments of the utility model have been described in detail by examples, those skilled in the art should understand that the above examples are only for illustration, and are not intended to limit the scope of the utility model. Those skilled in the art should understand that the above embodiments can be modified without departing from the scope and spirit of the utility model. The scope of the utility model is defined by the appended claims.

Claims

1. An analyte detection system, characterized by, The application relates to an analyte detection device and a mounting unit. The analyte detection device comprises a transmitter, a sensor, a housing and a battery, wherein the sensor comprises an in-vivo part and an in-vitro part, and the housing comprises an upper housing and a lower housing, and a first through hole is arranged on the lower housing, and the auxiliary needle passes through the lower housing from the first through hole before installation, and the opening area envelopes the in-vivo part. The elastic pad is arranged on the outside or the inside of the lower housing. The elastic pad is a hollow structure, and the inner diameter of the elastic pad is smaller than the outer diameter of the opening area. The inner diameter of the elastic pad is smaller than the outer diameter of the in-vivo part.

2. The analyte detection system of claim 1, wherein, The elastic pad is a solid structure, and the elastic pad is arranged on the outside of the auxiliary needle after being pierced by the opening area.

3. The analyte detection system of claim 2, wherein, The thickness of the elastic pad is 0.01-5 mm.

4. The analyte detection system of claim 3, wherein, The thickness of the elastic pad is 0.3 mm.

5. The analyte detection system of claim 2, wherein, The material of the elastic pad is one of rubber, silica gel and latex.

6. The analyte detection system of claim 2, wherein, The elastic pad is fixed on the outside or the inside of the lower housing.

7. The analyte detection system of claim 6, wherein, The fixing mode of the elastic pad comprises at least double-sided adhesive paste, hot melting or ultrasonic welding.

8. The analyte detection system of claim 2, wherein, The outside of the lower housing is provided with a first accommodating groove for accommodating the elastic pad.

9. The analyte detection system of claim 2, wherein, The outer diameter of the elastic pad is greater than the diameter of the first accommodating groove.

10. The analyte detection system of claim 9, wherein, The inside of the lower housing is provided with a second accommodating groove for accommodating the elastic pad.

11. The analyte detection system of claim 2, wherein, The thickness of the elastic pad is greater than the depth of the second accommodating groove.

12. The analyte detection system of claim 11, wherein, The elastic pad is arranged between the inside of the lower housing and the bending part of the sensor.

13. The analyte detection system of claim 2, wherein, Before installation, the analyte detection device is in a separated state from the mounting unit.

14. The analyte detection system of claim 13, wherein, Before installation, the analyte detection device is built in the mounting unit.

15. The analyte detection system of claim 2, wherein, ​ 16. The analyte detection system of claim 2, wherein, ​ 17. The analyte detection system of claim 2, wherein, ​

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