CN202974934U - Glucose sensor - Google Patents
Glucose sensor Download PDFInfo
- Publication number
- CN202974934U CN202974934U CN 201220554688 CN201220554688U CN202974934U CN 202974934 U CN202974934 U CN 202974934U CN 201220554688 CN201220554688 CN 201220554688 CN 201220554688 U CN201220554688 U CN 201220554688U CN 202974934 U CN202974934 U CN 202974934U
- Authority
- CN
- China
- Prior art keywords
- working electrode
- layer
- sensor
- glucose sensor
- glucose
- Prior art date
- Legal status (The legal status is an assumption and is not a legal conclusion. Google has not performed a legal analysis and makes no representation as to the accuracy of the status listed.)
- Expired - Lifetime
Links
Images
Abstract
The utility model discloses a glucose sensor. The glucose sensor comprises a counter electrode and at least one working electrode, wherein the counter electrode is fixedly mounted on a base; and the outmost layer of the at least one working electrode is coated with a degradable layer. By coating one degradable layer on the surface of the working electrode of the sensor, a relay mechanism for releasing enzyme in sequence can be formed, the service life of the sensor can be remarkably prolonged compared with the existing life of 3-5 days, and the correcting frequencies of the sensor are reduced compared with the existing correcting frequencies. The glucose sensor is small in volume, relatively simple in manufacturing process and low in manufacturing cost. As the service life of the sensor is prolonged, a patient does not need to replace the sensor frequently, thus the financial burden of the patient is remarkably reduced. The implantable type or intrusive type glucose sensor for real-time detection with long service life and good biocompatibility has broad application prospects in implantable type or intrusive type medical inspection equipment.
Description
Technical field
The utility model relates to a kind of glucose sensor, belongs to the medical treatment detection device field.
Background technology
Diabetes serious threat human health, the diabetes patient needs to regulate diet by repeatedly measuring blood glucose concentration every day, to reach the purpose of controlling blood sugar.Traditional blood sugar monitoring methods is the finger tip blood collection method, the method testing result is accurate, but patient has sense of discomfort and fear more, and the number of times that detect every day is limited, can not be complete real-time reflection patient's change of blood sugar, therefore can not provide enough valuable treatment foundations, and the continuous detecting data message just can provide basic improvement for diagnosis and the treatment of diabetes.
Endermic implantating real time blood sugar monitoring system is implanted sensor probe subcutaneous, can continuous monitoring tissue fluid in the concentration of glucose, by calibration, can obtain the concentration value of glucose in blood.The general belly of implanting of subcutaneous implantation probe, wound to health is less, a probe generally can use 3-5 days, during implanting, the patient only needs come calibrating sensors 2-3 time from the finger tip blood sampling every day, just can obtain in real time the continuous blood sugar value of 24 hours, can reflect in real time patient's change of blood sugar, for control and the treatment of diabetes provides enough foundations.
But use when surpassing this time limit generally at 3-5 days sensing probe serviceable life of existing Endermic implantating real time blood sugar detecting sensor, and the measurement result of sensor can be inaccurate.The poor use rear stability reduction continuously that causes popping one's head in of sensor surface biocompatibility, measurement result is inaccurate is the restriction key factor in probe life-span.
The Chinese patent CN1644157A of Sheng Meidinuo medical science and technology company limited application discloses a kind of biology sensor of subcutaneous implantation, the positive and negative two pieces of electrodes of pin type are vertically fixed on pedestal, during use, positive and negative electrode is inserted hypodermis, the carcass below pedestal can be fixed in skin surface with sensor.Oxygen in tissue fluid and glucose enter enzyme reaction layer with the macromolecule infiltration rete of mode by electrode surface of diffusion, the strength of current that reaction produces is directly proportional to tested concentration of glucose, the dynamic glucose sensor controlled circuit that coordinates patent CN201001732Y can show in real time with detecting data.Sheng Meidinuo company is converted into product DGMS with this patent, the implantable subcutaneous 3-5 of sensor days, refreshed blood glucose concentration value one time in every 3 minutes, and recorded 480 blood glucose level datas every day, can directly show 4 hours on screen and can look back the dynamic glucose change curve of nearest 72 hours.
Chinese patent literature CN101530327A is poor for glucose sensor bio-compatibility in prior art, the deficiency of its blood glucose value at that time can not be provided to the user in real time, good needle amperometric determination type glucose sensor for subcutaneous tissue real-time monitoring of a kind of bio-compatibility and preparation method thereof is provided, the working electrode of this sensor has conductive layer, the macromolecular material theca interna, enzyme membrane layer and macromolecular material control diffusion layer cover successively from the inside to the outside and form.Macromolecular material is controlled the water wettability hydration layer of the surperficial parcel of diffusion layer one deck space lattice, can stop the loss of enzyme, slows down the diffusion of larger molecule such as protein, reduces electrode and disturbs.After this electrode implantation is subcutaneous, but continuous working is more than 72 hours.
Can be found out by above analysis, the serviceable life of existing Endermic implantating real time blood sugar detecting sensor is too short, and the patient needs often to change monitoring probe, and it is not very convenient using, and on market, the price of existing probe is about dozens of yuan, and frequent replacing can allow patient's financial burden sharply increase.
The utility model content
Technical problem to be solved in the utility model is to provide a kind of glucose sensor with new construction.
utility model design of the present utility model is: the electrode surface of existing insertion type glucose sensor can wrap up one deck biocompatible materials, as cellulose acetate, polyurethane, polyvinyl alcohol (PVA) and Nafion etc., these material properties are more stable, can very fast metabolism not fall, collagenous fibres can surround implant and form tunicle, be the tissue capsule of foreign object in causing, normal tissue and implant are kept apart, the formation of fibr tissue has stoped the diffusion of glucose to sensor internal, fibrage is thicker, the diffusion of glucose is more difficult, so implanting or get involved subcutaneous rear sensitivity meeting, reduces along with the increase of implantation or intervention time by sensor.
For this reason, on the basis of existing insertion type Real-Time Monitoring glucose sensing electrodes, the utility model applies one deck degradable biocompatibility material in the outmost surface of working electrode, on the one hand as protective material, can prevent the loss of enzyme; On the other hand, in the degradation process of material, enzyme is slowly discharged, the enzyme of rear release can make up the inefficacy of the enzyme that first discharges, by controlling the degradation rate of material, can make the inefficacy of enzyme and the release of enzyme reach balance, thereby make the catalytic efficiency of glucose oxidase keep constant, thereby form the relay mechanism that enzyme successively discharges.Moreover, after degradable material implants, catabolite is nontoxic, can participate in the metabolism in body and excrete, the good biocompatibility of material, so the formation of collagenous fibres relaxes with respect to non-degradation biological compatibility material, thinner fibrage to the barrier effect of glucose a little less than, the sensitivity after sensor is implanted can reduce relatively.In addition, degradation material can be made into the structure of porous, and the structure of porous can increase the formation of new blood vessel, the new blood vessel that forms can improve the continuity of tissue, reduce blood to the distance of sensor, blood also just can be easier to be diffused into sensor surface by sensor measurement, and sensor just can be measured the change of blood sugar of blood preferably.And the good fibr tissue that a large amount of new vascular distribution are arranged also can make sensor not proofread and correct long-term stable operation in the situation that distribute around sensor.
Kind and the thickness of the degradation material that the outmost surface of working electrode applies can be selected according to required degradation time.For commaterial, thickness is thicker or concentration is higher, and the required time of degrading all can correspondingly increase.Thickness or the concentration of the degradation material that applies by the surface of controlling working electrode just can be controlled the degradation time of material, thereby control the release rate of enzyme, reach the purpose of prolongation working sensor time.
Specifically, the technical scheme in the invention for solving the technical problem is: a kind of glucose sensor, comprise that of being fixedly installed on pedestal to electrode and at least one working electrode, wherein, has at least the outermost layer of a described working electrode to be coated with biodegradable layer.
Further, working electrode described in the utility model is one, and described biodegradable layer covers the outermost regional area of working electrode.
Further, working electrode described in the utility model is more than two, and to have a working electrode at least be to be coated with described biodegradable layer at its outermost regional area.
Further, the thickness of biodegradable layer described in the utility model is and increases progressively state.
Further, the thickness of biodegradable layer described in the utility model is stepped.
Further, working electrode described in the utility model is more than two, and has at least a working electrode not apply biodegradable layer.
Further, the thickness of biodegradable layer described in the utility model is and increases progressively state.
Further, the thickness of biodegradable layer described in the utility model is stepped.
Further, working electrode described in the utility model comprises metal conducting layer, enzymatic layer and macromolecular material control diffusion layer, and described metal conducting layer, enzymatic layer, macromolecular material control diffusion layer distribute by order from inside to outside.
Further, biodegradable layer described in the utility model is porous structure.
Compared with prior art, the beneficial effects of the utility model are: apply one deck biodegradable layer by the working electrode surface at sensor, can form the relay mechanism that enzyme successively discharges, and the life-span of sensor was significantly increased than existing 3-5 days, and the number of corrections of sensor also reduces to some extent than existing.The volume of the utility model sensor is little, manufacture craft is relatively simple, and cost of manufacture is low.And because improve the serviceable life of sensor, the patient does not need frequent replacing, and patient's financial burden also has significant reduction.The implanted of this long service life, good biocompatibility or insertion type detect in real time glucose sensor and have broad application prospects in implanted or insertion type medical treatment detection device.
Description of drawings
Vertical view when Fig. 1 is the utility model glucose sensor employing three-electrode system;
Side view when Fig. 2 is the utility model glucose sensor employing three-electrode system;
Fig. 3 is the structural representation that the surface portion of the working electrode of the utility model glucose sensor applies degradation material;
Fig. 4 is that working electrode in Fig. 3 is along the cut-open view of A-A face;
Fig. 5 is the structural representation that the surface portion of the single aciculiform working electrode of the utility model glucose sensor applies degradation material;
Fig. 6 is that the surface of the aciculiform working electrode of the utility model glucose sensor all evenly applies the structural representation of degradation material;
Fig. 7 is that the thickness of biodegradable coating on surface of the aciculiform working electrode of the utility model glucose sensor is the structural representation that increases progressively gradually state;
Fig. 8 is the stepped structural representation of thickness of biodegradable coating on surface of the aciculiform working electrode of the utility model glucose sensor;
Fig. 9 is the schematic diagram that the working electrode of the utility model glucose sensor adopts single plane electrode;
Figure 10 is that working electrode in Fig. 9 is along the cut-open view of A-A face;
Figure 11 is the schematic diagram that the working electrode of the utility model glucose sensor adopts a plurality of plane electrodes.
Embodiment
Referring to Fig. 1 and 2, the utility model glucose sensor comprises one to electrode 2 and at least one working electrode 3, and electrode 2 and working electrode 3 are installed on pedestal 1.In the utility model, the composition of electrode can for two-electrode system (namely by one, electrode 2 and at least one working electrode 3 being consisted of), also can be three-electrode system (namely by, electrode 2, at least one working electrode 3 and a contrast electrode 4 being consisted of) as depicted in figs. 1 and 2.
In the utility model, the shape of electrode can be needle electrode, also can be plane electrode.Wherein, plane electrode can have any shape, as circular, oval, square etc.Below take needle electrode and circular flat electrode as example, the utility model is described further.
Take the aciculiform working electrode as example, in embodiment shown in Figure 3, the working electrode 3 of glucose sensor comprises metal conducting layer 5, enzymatic layer 6, macromolecular material control diffusion layer 7, and metal conducting layer 5, enzymatic layer 6, macromolecular material control diffusion layer 7 distribute by order from inside to outside.As the glucose sensor working electrode 3 of implantation or insertion type, the base metal of metal conducting layer 5 is generally selected stainless steel, so that working electrode has enough rigidity, is easy to sting transdermal, implants or get involved subcutaneous.The surface of metal conducting layer 5 is by sputter or electroplate one deck noble metal nano particles layer, as gold or Pt nanoparticle; Then, form enzymatic layer 6 on metal nano-particle layer surface by enzyme immobilization methods such as crosslinked or embeddings; Then, apply one deck macromolecular material by the method for dipping on the surface of enzymatic layer 6 and control diffusion layer 7, wherein, it is cellulose acetate, polyurethane, polyurethane, Polyvinylchloride that macromolecular material is selected from usually, any one in Nafion.
Macromolecular material is controlled diffusion layer 7 due to the size in its aperture and the effect of surface group, has the selection impregnability, can stop the motion of larger molecule, and the diffusion as albumen in the loss of enzyme and tissue fluid reduces the interference of electrode.Can also be diffused into the amount of electrode surface by restriction glucose, form the relatively abundant state of oxygen molecule, reduce the dependence of electrode pair oxygen, when increasing the linear sensor scope, can also increase the serviceable life of sensor.
The utility model has increased one deck biodegradable layer 8 at the outermost layer of working electrode 3.Biodegradable layer 8 is comprised of the degradable biocompatibility material, can be the natural degradable material, as wherein any one of cellulose, chitin, collagen, fibrin; Can be also the synthesized degradable material, as any one in PLA, polyglycolic acid and multipolymer thereof, polybutylcyanoacrylate, poly-acid anhydrides, polycaprolactone, poly-para-dioxane ketone, poly phosphazene, polymer-amino-acid; It can also be the potpourri of natural degradable material and synthesized degradable material.
In the utility model, the quantity of working electrode 3 can be one, also can be for more than two.
When working electrode 3 was one, biodegradable layer 8 was coated in the outermost regional area of working electrode 3, and the degraded of the biodegradable layer 8 by being distributed in regional area forms the relay mechanism that enzyme successively discharges.
When working electrode 3 is two when above, have at least the outermost layer of a working electrode to be coated with biodegradable layer 8; And having a working electrode 3 at least is to be coated with biodegradable layer 8 at its outermost regional area, perhaps, has at least a working electrode 3 not apply biodegradable layer 8.At this moment, the working electrode 3 that is coated with biodegradable layer 8 can be that whole working electrode 3 all is coated with biodegradable layer 8, can be also only to be coated with biodegradable layer 8 in the subregion of working electrode 3.Degraded by biodegradable layer 8 forms the relay mechanism that enzyme successively discharges.
Fig. 3 and Fig. 4 show the state of subregion that biodegradable layer 8 is coated in the surface of working electrode.At this moment, biodegradable layer 8 can be coated in any position of working electrode 3, and the size of coating can be arbitrarily; The thickness that applies also can be selected according to required degradation time; Can be even coating, also can be inhomogeneous coating, uniform thickened applies as adopting, the stepped mode such as coating that thickens.
Fig. 5 shows a kind of embodiment that applies biodegradable layer 8 on the surface of aciculiform working electrode.As shown in Figure 5, biodegradable layer 8 is coated in the first half section of aciculiform working electrode in uniform mode.It is the surface that evenly is coated in working electrode due to degradable material, almost degraded simultaneously in vivo, discharge simultaneously enzyme, take over owing to not applying degradation material the enzyme that is about in vivo lose efficacy glucose response is carried out catalysis, thereby form relay mechanism, increased the serviceable life of glucose sensor.
Fig. 6 shows the schematic diagram that all applies biodegradable layer 8 on the whole surface of aciculiform working electrode.As shown in Figure 6, biodegradable layer 8 evenly is coated in the outermost layer of whole working electrode, and its painting method is: can first degradable material be made into solution, then evenly be coated in the surface of working electrode by the mode of dipping.
Fig. 7 shows the another kind of embodiment that all applies biodegradable layer 8 on the whole surface of aciculiform working electrode.As shown in Figure 7, on the surface of aciculiform working electrode, biodegradable layer 8 applies from tip to the mode of root with progressive additive of working electrode.Because the thickness of degradation material increases gradually, the degradation time of degradation material also increases successively, and the enzymatic layer is along with the time discharges lentamente, and the new enzyme that discharges is taken over the enzyme that lost efficacy and ran off, can make all the time the enzyme concentration on working electrode keep constant, glucose response is carried out catalysis.By controlling the degradation time of biodegradable layer 8, can control the release time of enzymatic layer, thus the serviceable life of prolongation working electrode.
Fig. 8 shows the another kind of embodiment that all applies biodegradable layer 8 on the whole surface of aciculiform working electrode.As shown in Figure 8, on the surface of aciculiform working electrode, biodegradable layer 8 applies from tip to the stepped mode of root of working electrode, makes biodegradable layer 8 be made of stepped regional 8a, 8b, 8c, the 8d that increases progressively of thickness.Can be by the thickness of controlling biodegradable layer 8 or the time that concentration is come control degradation.Usually, thickness is larger or concentration is higher, and the degradation time of biodegradable layer 8 all can correspondingly increase.By controlling the degradation time of biodegradable layer 8, can control the release time of enzymatic layer, thus the serviceable life of prolongation working electrode.
Working electrode of the present utility model can also be plane electrode except being needle electrode.Fig. 9 shows the schematic diagram that working electrode is plane electrode.Wherein, the shape of working electrode 3 can have any shape, as circular, oval, square etc.As an available example, select circular working electrode to describe in the utility model.
Figure 10 is the A-A cut-open view of working electrode in Fig. 9, similar to the aciculiform working electrode, wherein, working electrode 3 controls diffusion layer 7 by metal conducting layer 5, enzymatic layer 6, macromolecular material and biodegradable layer 8 consists of, and metal conducting layer 5, enzymatic layer 6, macromolecular material are controlled diffusion layer 7, biodegradable layer 8 distributes by order from inside to outside.The coating method of biodegradable layer 8 can be similar to the coating method of aciculiform working electrode: can be coated in whole working electrode 3 surfaces, can be also to apply in the subregion of working electrode 3; Can evenly be coated in macromolecular material and control outside diffusion layer 7, the mode of the mode (for example stepped with thickness) that also can increase gradually with thickness is coated in macromolecular material and controls outside diffusion layer 7.
As shown in figure 11, as another embodiment of the present utility model, adopted a plurality of planes working electrode 3, each plane working electrode 3 connects by wire 9.The coating method of biodegradable layer 8 can be similar to the aciculiform working electrode: can apply on the surface of whole plane working electrode, can be also only to apply in the subregion of plane working electrode; Can be coated in equably macromolecular material and control outside diffusion layer 7, the mode of the mode (for example stepped with thickness) that also can increase gradually with thickness is coated in macromolecular material and controls outside diffusion layer 7.
The utility model is because the outermost layer at working electrode applies biodegradable layer 8, make the enzymatic layer 6 of glucose sensor discharge by a kind of relay mechanism, the new enzyme that discharges is taken over the enzyme that lost efficacy and ran off, can make all the time the enzyme concentration on working electrode keep constant, glucose response is carried out catalysis; By controlling the degradation time of biodegradable layer 8, can control the release time of enzymatic layer 6, thus the serviceable life of prolongation working electrode 3.The glucose sensor of this long service life is being implanted or insertion type blood sugar monitoring field has broad application prospects.
Claims (10)
1. glucose sensor comprises be fixedly installed on pedestal one to electrode (2) and at least one working electrode (3), it is characterized in that: have at least the outermost layer of a described working electrode to be coated with biodegradable layer (8).
2. glucose sensor according to claim 1, it is characterized in that: described working electrode (3) is one, described biodegradable layer (8) covers the outermost regional area of working electrode (3).
3. glucose sensor according to claim 1, it is characterized in that: described working electrode (3) is more than two, and to have a working electrode (3) at least be to be coated with described biodegradable layer (8) at its outermost regional area.
4. the described glucose sensor of any one according to claim 1 to 3 is characterized in that: the thickness of described biodegradable layer (8) is and increases progressively state.
5. glucose sensor according to claim 4, it is characterized in that: the thickness of described biodegradable layer (8) is stepped.
6. glucose sensor according to claim 1, it is characterized in that: described working electrode (3) is more than two, and has at least a working electrode (3) not apply described biodegradable layer.
7. glucose sensor according to claim 6 is characterized in that: the thickness of described biodegradable layer (8) is and increases progressively state.
8. glucose sensor according to claim 7, it is characterized in that: the thickness of described biodegradable layer (8) is stepped.
9. 2,3,6,7 or 8 described glucose sensors according to claim 1,, it is characterized in that: described working electrode comprises metal conducting layer (5), enzymatic layer (6) and macromolecular material control diffusion layer (7), and described metal conducting layer (5), enzymatic layer (6), macromolecular material control diffusion layer (7) distribute by order from inside to outside.
10. according to claim 1,2,3,6,7 or 8 described glucose sensors, it is characterized in that: described biodegradable layer (8) is porous structure.
Priority Applications (1)
| Application Number | Priority Date | Filing Date | Title |
|---|---|---|---|
| CN 201220554688 CN202974934U (en) | 2012-10-26 | 2012-10-26 | Glucose sensor |
Applications Claiming Priority (1)
| Application Number | Priority Date | Filing Date | Title |
|---|---|---|---|
| CN 201220554688 CN202974934U (en) | 2012-10-26 | 2012-10-26 | Glucose sensor |
Publications (1)
| Publication Number | Publication Date |
|---|---|
| CN202974934U true CN202974934U (en) | 2013-06-05 |
Family
ID=48515993
Family Applications (1)
| Application Number | Title | Priority Date | Filing Date |
|---|---|---|---|
| CN 201220554688 Expired - Lifetime CN202974934U (en) | 2012-10-26 | 2012-10-26 | Glucose sensor |
Country Status (1)
| Country | Link |
|---|---|
| CN (1) | CN202974934U (en) |
Cited By (6)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| CN103983675A (en) * | 2014-05-30 | 2014-08-13 | 浙江大学 | Platinum and polyaniline compounded three-dimensional nanofiber functional structure glucose sensor with stainless steel needle as base and preparation method of sensor |
| CN110044986A (en) * | 2017-12-29 | 2019-07-23 | 深圳硅基传感科技有限公司 | Glucose monitoring probe |
| CN110057889A (en) * | 2018-12-29 | 2019-07-26 | 深圳硅基传感科技有限公司 | The working electrode and preparation method thereof of glucose monitoring probe |
| CN110186976A (en) * | 2019-06-24 | 2019-08-30 | 深圳硅基传感科技有限公司 | The working electrode and preparation method thereof of glucose monitoring probe |
| WO2021013175A1 (en) * | 2019-07-24 | 2021-01-28 | Xi'an Jiaotong-Liverpool University | Solid quantum dot sensor and method for producing the same as well as use thereof |
| WO2023279311A1 (en) * | 2021-07-08 | 2023-01-12 | Medtrum Technologies Inc. | Micro analyte sensor |
-
2012
- 2012-10-26 CN CN 201220554688 patent/CN202974934U/en not_active Expired - Lifetime
Cited By (14)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| CN103983675A (en) * | 2014-05-30 | 2014-08-13 | 浙江大学 | Platinum and polyaniline compounded three-dimensional nanofiber functional structure glucose sensor with stainless steel needle as base and preparation method of sensor |
| CN111307906B (en) * | 2017-12-29 | 2022-01-11 | 深圳硅基传感科技有限公司 | Analyte monitoring probe |
| CN110044986A (en) * | 2017-12-29 | 2019-07-23 | 深圳硅基传感科技有限公司 | Glucose monitoring probe |
| CN110044986B (en) * | 2017-12-29 | 2020-05-05 | 深圳硅基传感科技有限公司 | Glucose monitoring probe |
| CN111307906A (en) * | 2017-12-29 | 2020-06-19 | 深圳硅基传感科技有限公司 | Analyte monitoring probe |
| CN112710713B (en) * | 2017-12-29 | 2022-04-29 | 深圳硅基传感科技有限公司 | Implanted glucose monitoring probe |
| CN112964771B (en) * | 2017-12-29 | 2022-04-29 | 深圳硅基传感科技有限公司 | Glucose monitoring probe for continuous monitoring |
| CN112710713A (en) * | 2017-12-29 | 2021-04-27 | 深圳硅基传感科技有限公司 | Implanted glucose monitoring probe |
| CN112964771A (en) * | 2017-12-29 | 2021-06-15 | 深圳硅基传感科技有限公司 | Glucose monitoring probe for continuous monitoring |
| CN110057889A (en) * | 2018-12-29 | 2019-07-26 | 深圳硅基传感科技有限公司 | The working electrode and preparation method thereof of glucose monitoring probe |
| CN110186976A (en) * | 2019-06-24 | 2019-08-30 | 深圳硅基传感科技有限公司 | The working electrode and preparation method thereof of glucose monitoring probe |
| CN110186976B (en) * | 2019-06-24 | 2020-08-14 | 深圳硅基传感科技有限公司 | Working electrode of glucose monitoring probe and manufacturing method thereof |
| WO2021013175A1 (en) * | 2019-07-24 | 2021-01-28 | Xi'an Jiaotong-Liverpool University | Solid quantum dot sensor and method for producing the same as well as use thereof |
| WO2023279311A1 (en) * | 2021-07-08 | 2023-01-12 | Medtrum Technologies Inc. | Micro analyte sensor |
Similar Documents
| Publication | Publication Date | Title |
|---|---|---|
| CN102920465A (en) | Glucose sensor | |
| CN202974934U (en) | Glucose sensor | |
| AU2017264987B2 (en) | Tissue-Integrating Sensors | |
| CN100367906C (en) | Endermic implantating biological sensors | |
| US9532741B2 (en) | Membrane for use with implantable devices | |
| Castle et al. | Amperometric glucose sensors: sources of error and potential benefit of redundancy | |
| US7433727B2 (en) | Implantable biosensor | |
| Fang et al. | A needle-type glucose biosensor based on PANI nanofibers and PU/E-PU membrane for long-term invasive continuous monitoring | |
| CN105380669B (en) | Continuous blood sugar monitoring long-life implantable glucose sensor and preparation method thereof | |
| CN110208352A (en) | The factory calibration method of glucose sensor | |
| US20180160985A1 (en) | Methods and devices for determining metabolic states | |
| CN110044986A (en) | Glucose monitoring probe | |
| CN112964771B (en) | Glucose monitoring probe for continuous monitoring | |
| KR20200011369A (en) | Nonenzymatic determination of glucose at near neutral ph values based on the use of nafion and platinum black coated microneedle electrode array | |
| CN104535627B (en) | glucose sensing system | |
| Yu et al. | An investigation of long-term performance of minimally invasive glucose biosensors | |
| Vaddiraju et al. | Needle-implantable, wireless biosensor for continuous glucose monitoring | |
| CN204302217U (en) | A kind of glucose sensing system | |
| CN2782015Y (en) | Subcutaneous implantation type biosenser | |
| CN113030219A (en) | Continuous glucose monitoring sensor and application thereof | |
| CN110051365A (en) | A kind of implanted electrode for continuing to monitor for a long time | |
| CN201404203Y (en) | implanted biosensor | |
| CN209727836U (en) | Fibroin albumen microneedle electrodes and the sensor for detecting concentration of glucose | |
| CN101548878B (en) | Implanted biosensor | |
| CN117617964A (en) | Degradable fibrous calcium ion sensor and preparation method thereof |
Legal Events
| Date | Code | Title | Description |
|---|---|---|---|
| C14 | Grant of patent or utility model | ||
| GR01 | Patent grant | ||
| CX01 | Expiry of patent term |
Granted publication date: 20130605 |
|
| CX01 | Expiry of patent term |