[go: up one dir, main page]

WO2013191361A1 - Bande de capteur - Google Patents

Bande de capteur Download PDF

Info

Publication number
WO2013191361A1
WO2013191361A1 PCT/KR2013/003067 KR2013003067W WO2013191361A1 WO 2013191361 A1 WO2013191361 A1 WO 2013191361A1 KR 2013003067 W KR2013003067 W KR 2013003067W WO 2013191361 A1 WO2013191361 A1 WO 2013191361A1
Authority
WO
WIPO (PCT)
Prior art keywords
layer
reaction
biological material
sensor strip
reagent
Prior art date
Application number
PCT/KR2013/003067
Other languages
English (en)
Korean (ko)
Inventor
정소희
Original Assignee
(주)미코바이오메드
Priority date (The priority date 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 date listed.)
Filing date
Publication date
Application filed by (주)미코바이오메드 filed Critical (주)미코바이오메드
Publication of WO2013191361A1 publication Critical patent/WO2013191361A1/fr

Links

Images

Classifications

    • G—PHYSICS
    • G01—MEASURING; TESTING
    • G01N—INVESTIGATING OR ANALYSING MATERIALS BY DETERMINING THEIR CHEMICAL OR PHYSICAL PROPERTIES
    • G01N21/00—Investigating or analysing materials by the use of optical means, i.e. using sub-millimetre waves, infrared, visible or ultraviolet light
    • G01N21/75—Systems in which material is subjected to a chemical reaction, the progress or the result of the reaction being investigated
    • G01N21/77—Systems in which material is subjected to a chemical reaction, the progress or the result of the reaction being investigated by observing the effect on a chemical indicator
    • G01N21/78—Systems in which material is subjected to a chemical reaction, the progress or the result of the reaction being investigated by observing the effect on a chemical indicator producing a change of colour
    • G—PHYSICS
    • G01—MEASURING; TESTING
    • G01N—INVESTIGATING OR ANALYSING MATERIALS BY DETERMINING THEIR CHEMICAL OR PHYSICAL PROPERTIES
    • G01N21/00—Investigating or analysing materials by the use of optical means, i.e. using sub-millimetre waves, infrared, visible or ultraviolet light
    • G01N21/84—Systems specially adapted for particular applications
    • G01N21/8483—Investigating reagent band
    • G—PHYSICS
    • G01—MEASURING; TESTING
    • G01N—INVESTIGATING OR ANALYSING MATERIALS BY DETERMINING THEIR CHEMICAL OR PHYSICAL PROPERTIES
    • G01N33/00—Investigating or analysing materials by specific methods not covered by groups G01N1/00 - G01N31/00
    • G01N33/48—Biological material, e.g. blood, urine; Haemocytometers
    • G01N33/50—Chemical analysis of biological material, e.g. blood, urine; Testing involving biospecific ligand binding methods; Immunological testing
    • G01N33/52—Use of compounds or compositions for colorimetric, spectrophotometric or fluorometric investigation, e.g. use of reagent paper and including single- and multilayer analytical elements
    • G—PHYSICS
    • G01—MEASURING; TESTING
    • G01N—INVESTIGATING OR ANALYSING MATERIALS BY DETERMINING THEIR CHEMICAL OR PHYSICAL PROPERTIES
    • G01N33/00—Investigating or analysing materials by specific methods not covered by groups G01N1/00 - G01N31/00
    • G01N33/48—Biological material, e.g. blood, urine; Haemocytometers
    • G01N33/50—Chemical analysis of biological material, e.g. blood, urine; Testing involving biospecific ligand binding methods; Immunological testing
    • G01N33/52—Use of compounds or compositions for colorimetric, spectrophotometric or fluorometric investigation, e.g. use of reagent paper and including single- and multilayer analytical elements
    • G01N33/525—Multi-layer analytical elements

Definitions

  • the present invention relates to a sensor strip, and to a sensor strip for detecting a disease using a biological material.
  • the sensor strip is laminated with several layers including the reaction layer to which the reaction reagent is applied.
  • the sensor strip detects a disease by using the color of the reaction layer that the supplied biological material reacts with the reaction reagent and changes through the reaction.
  • the biomaterial may be reversely absorbed into the upper layer of the reaction layer according to the difference in absorbance of each layer. Therefore, the biomaterial and the reaction reagent of the reaction layer do not sufficiently react, and the extent of the reaction layer is weakened. Therefore, it is difficult to accurately determine whether or not a disease using the color of the reaction layer, the reliability of the sensor strip may be lowered.
  • the present invention provides a sensor strip that can prevent back-absorption of biological material into the upper layer of the reaction layer.
  • the sensor strip according to the present invention is applied to the net layer to uniformly spread the biological material, and a reaction reagent which is disposed under the net layer, and reacts with the biological material to confirm the disease using the biological material.
  • a reaction layer and a lower portion of the reaction layer to absorb the biomaterial and the reagent from the reaction layer while the biomaterial and the reagent react to prevent the biomaterial and the reagent from being absorbed back into the upper layer. It may include an absorbing layer.
  • the sensor strip may be disposed between the net layer and the reaction layer, and may further include a separation layer for separating blood cells from the blood when the biological material is blood.
  • the separation layer may be a glass fiber bound to the polymer.
  • the absorbing layer may be coated with a transparent film on the lower surface to prevent evaporation of the biological material and the reaction reagent absorbed in the absorbing layer into the atmosphere.
  • the sensor strip is disposed on the net layer, the upper case having a first opening for supplying the biological material to the net layer and is disposed below the absorber layer,
  • the display device may further include a lower case having a second opening for measuring a reflectance of the absorbing layer and coupled to the upper case.
  • the hydrophilic absorbent layer is disposed under the reaction layer to absorb the biomaterial and the reaction reagent, thereby minimizing the reverse absorption of the biomaterial into the upper layer. Therefore, since the color development of the absorbent layer is improved, the disease can be accurately detected using the color of the absorbent layer.
  • the biomaterial and the reaction reagent of the absorbent layer may be prevented from evaporating downward.
  • FIG. 1 is an exploded perspective view illustrating a sensor strip according to an embodiment of the present invention.
  • FIG. 2 is a side view illustrating the sensor strip shown in FIG. 1.
  • FIG 3 is a graph measuring the reflectance of the sensor strip including the absorbing layer according to the present invention.
  • first and second may be used to describe various components, but the components should not be limited by the terms. The terms are used only for the purpose of distinguishing one component from another.
  • the first component may be referred to as the second component, and similarly, the second component may also be referred to as the first component.
  • FIG. 1 is an exploded perspective view illustrating a sensor strip according to an exemplary embodiment of the present invention
  • FIG. 2 is a side view illustrating the sensor strip illustrated in FIG. 1.
  • the sensor strip 100 detects a disease using a biomaterial.
  • the biological material may constitute any human body or any substance capable of detecting the disease as a secretion of the human body, and examples thereof include blood and urine.
  • the sensor strip 100 includes a net layer 110, a separation layer 120, a reaction layer 130, an absorption layer 140, an upper case 150, and a lower case 160.
  • the net layer 110 has a net structure and allows the injected biomaterial to be uniformly spread.
  • the pore size of the net layer 110 is less than about 100 ⁇ m, the net layer 110 is too dense so that some of the components of the biological material having a large size are hooked to the net layer 110 so that the biomaterial is formed in the net layer ( It is absorbed into the lower layer of 110 and acts as a blocking element.
  • the biological material is blood
  • blood cells among the components of the blood may be caught in the net layer 110. Therefore, the time required for the biomaterial to be absorbed into the lower layer can be increased.
  • the pore size of the net layer 110 exceeds about 500 ⁇ m, the net layer 110 is sparse and may be absorbed into the lower layer before the biological material is uniformly spread. Therefore, the effect of spreading the biological material uniformly by the net layer 110 can be reduced.
  • the pore size of the net layer 110 is preferably about 100 to 500 ⁇ m.
  • the separation layer 120 is disposed under the net layer 110, and may separate specific components from the biological material.
  • the specific component may be a component having a relatively large size in the biological material.
  • the separation layer 120 may separate blood cells from the blood.
  • the separation layer 120 is made of glass fiber, and a polymer is bound to the glass fiber for separation of the specific component.
  • the separation layer 120 When the thickness of the separation layer 120 is less than about 300 ⁇ m, the separation layer 120 is thin so that the specific component is not properly separated. When the thickness of the separation layer 120 exceeds about 1000 ⁇ m, the separation layer 120 is so thick that it takes a very long time for the specific components to separate.
  • the thickness of the separation layer 120 may be about 300 to 1000 ⁇ m.
  • the sensor strip 100 may include a separation layer 120 because a process of separating specific components, for example, blood cells, from the biological material is required. Can be.
  • the sensor strip 100 when the sensor strip 100 is used for measuring anemia, the sensor strip 100 may not include the separation layer 120 because separation of the specific component from the biological material is not necessary. In addition, even when the sensor strip 100 is used for liver disease measurement and cholesterol level measurement, when the biological material is supplied with the specific component separated in advance, the separation of the specific component from the biological material is unnecessary. 100 may not include a separation layer 120.
  • the reaction layer 130 is disposed below the separation layer 120 and contains a reaction reagent.
  • the reaction reagent reacts with the biological material.
  • the reaction reagent may chemically react with plasma from which blood cells are separated from blood, which is the biological substance.
  • the type of reaction reagent included in the reaction layer 130 may vary depending on the type of disease to be measured and the type of the biological material.
  • the separation layer 120 is colored according to the reaction between the reaction reagent and the biological material.
  • the reaction layer 130 has an asymmetric structure for separation of specific components of the biological material. Specifically, the reaction layer 130 has fine pores penetrating up and down, and the pores have a structure in which the cross-sectional area becomes narrower from the upper surface of the reaction layer 130 to the lower surface. Therefore, when the biomaterial passes through the pores, a relatively large component of the biomaterial is caught by the micropores so that the reaction layer 130 may separate the specific component from the biomaterial.
  • the specific component may be blood cells.
  • the thickness of the reaction layer 130 is related to the absorption of the reaction layer 130.
  • the thickness of the reaction layer 130 is less than about 100 ⁇ m, there are relatively few reaction reagents included in the reaction layer 130. Therefore, since the biological material and the reaction reagent are not sufficiently reacted, the degree of generation of the reaction layer 130 is low, so that the sensitivity of the reaction layer 130 is lowered and an accurate measurement value of the biological material cannot be derived.
  • the thickness of the reaction layer 130 is about 500 ⁇ m or more, the reagent included in the reaction layer 130 is more than necessary, and the reaction reagent may be abused. Therefore, since the reaction reagent is excessively used, unnecessary cost loss may occur.
  • the absorber layer 140 is disposed below the reaction layer 130 and is made of a hydrophilic material.
  • the hydrophilic material include nitrocellulose, cotton, fiberglass, and the like.
  • the absorbing layer 140 is made of the hydrophilic material, the biomaterial and the reaction reagent are absorbed from the reaction layer 130 while the biomaterial and the reaction reagent are reacted in the reaction layer 130.
  • the absorber layer 140 absorbs the biological material and the reagent of the reaction layer 130, so that the biological material and the reagent of the reaction layer 130 can be prevented from being reversely absorbed into the upper layer, that is, the separation layer 120. Can be. Therefore, the absorption layer 140 can prevent the reaction sensitivity of the reaction layer 130 from being lowered.
  • the absorbing layer 140 absorbs the biological material and the reaction reagent, the absorbing layer 140 may be colored similarly to the reaction layer 130.
  • the absorption layer 140 needs an appropriate thickness to absorb the reaction reagent of the reaction layer 130.
  • the thickness of the absorber layer 140 is less than about 50 ⁇ m, the thickness of the absorber layer 140 is relatively thin, so that the absorbent layer 140 may not fully absorb the reaction reagent absorbed from the reaction layer 130, and the reaction reagent may overflow.
  • the thickness of the absorber layer 140 exceeds about 150 ⁇ m, the thickness of the absorber layer 140 is relatively thick, and the reaction reagent of the reaction layer 130 may not be sufficiently absorbed into the absorber layer 140. Therefore, the color of the absorber layer 140 is not normal.
  • the thickness of the absorber layer 140 is preferably about 50 to 150 ⁇ m.
  • the absorber layer 140 is coated with a transparent film on the lower surface.
  • the transparent film may prevent the biological material and the reaction reagent absorbed in the absorbing layer 140 from being evaporated through the lower surface.
  • the transparent film is transparent, the color of the absorbing layer 140 can be displayed as it is.
  • the upper case 150 is disposed on the net layer 110 and has a substantially rectangular flat plate shape.
  • the upper case 150 has first openings 152.
  • the first openings 152 are arranged in a line along the longitudinal direction of the upper case 150 and penetrate the upper and lower portions of the upper case 150.
  • the first openings 152 expose the mesh layer 110, and the biomaterial may be injected through the first openings 152.
  • the lower case 160 is disposed under the absorber layer 140 and has a substantially rectangular flat plate shape.
  • the lower case 160 has second openings 162.
  • the second openings 162 are arranged in a line along the length direction of the lower case 160 and penetrate the upper and lower sides of the lower case 160.
  • the number of second openings 162 is the same as the number of first openings 152, and the second openings 162 and the first openings 152 are disposed to correspond to each other.
  • the second openings 162 expose the absorbing layer 140, and the color of the absorbing layer 140 may be measured through the second openings 162.
  • the color measurement of the absorber layer 140 may be performed by measuring the reflectance of the absorber layer 140.
  • the upper case 150 and the lower case 160 may be coupled to each other.
  • the fastening holes 154 of the upper case 150 and the fastening pins 164 of the lower case 160 may be fastened.
  • the upper case 150 and the lower case 160 may be hinged by one side is coupled to each other by being provided with grooves and protrusions on the other side opposite to the one side, respectively.
  • the laminated structure including the net layer 110, the separation layer 120, the reaction layer 130, and the absorber layer 140 may include the number of first openings 152 between the upper case 150 and the lower case 160. Number of second openings 162) and spaced apart from each other. That is, the stacked structures are respectively disposed between the first opening 152 and the second opening 162 facing each other. Since the stacked structures are spaced apart from each other, the biomaterial supplied through the first openings 152 may be prevented from moving to the other stacked structures. Thus, different measurements can be made at each laminate structure.
  • fastening holes 154 of the upper case 150 and the fastening pins 164 of the lower case 160 may be disposed between measurement structures spaced apart from each other, the upper case 150 and the lower case 160. Can be fixed at a constant and strong pressure.
  • Figure 3 is a graph measuring the reflectance of the sensor strip containing the absorbing layer according to the present invention
  • Figure 4 is a graph measuring the reflectance of the sensor strip not containing the absorbing layer.
  • the reflectance at 300 seconds was about 72% at ALT 9.5U / L, about 59% at ALT 50U / L, and about 44% at ALT 265.7U / L.
  • the reflectance at 300 seconds when the absorbing layer is not included in the sensor strip is about 78% at ALT 9.5U / L, about 71% at ALT 50U / L, and about 54% at ALT 265.7U / L. appear.
  • the difference in reflectance between the ALT low concentrations of ALT 9.5U / L and ALT 50U / L in the sensor strip with absorbing layer is about 13%, and the ALT low concentrations of ALT 9.5U / L and ALT 50U / L in the sensor strip without absorbing layer The difference in reflectance is about 7%.
  • the inclusion of the absorbing layer reveals that the difference in reflectance between ALT 9.5U / L and 50U / L in the sensor strip is nearly doubled from about 7% to about 13%.
  • the reflectance of the sensor strip with absorbing layer was measured to be lower than that of the sensor strip without absorbing layer. Specifically, even at a high concentration of 265U / L, the reflectance of the sensor strip including the absorbing layer was about 44%, and was measured to be about 10% lower than the reflectance of about 44% of the sensor strip without the absorbing layer.
  • the absorption layer included in the sensor strip prevents reverse absorption and evaporation of the biomaterial and the reaction reagent, thereby improving the degree of color development of the sensor strip even at the same concentration of the biomaterial.
  • the sensor strip according to the present invention may have an absorbent layer coated on a lower surface thereof to prevent reverse absorption and evaporation of the biological material and the reaction reagent. Therefore, the sensitivity of the sensor strip can be improved to accurately measure the presence or absence of a disease using the biomaterial and the reliability of the sensor strip can be improved.

Landscapes

  • Health & Medical Sciences (AREA)
  • Life Sciences & Earth Sciences (AREA)
  • Immunology (AREA)
  • Chemical & Material Sciences (AREA)
  • Engineering & Computer Science (AREA)
  • Physics & Mathematics (AREA)
  • Hematology (AREA)
  • Pathology (AREA)
  • Biochemistry (AREA)
  • General Health & Medical Sciences (AREA)
  • General Physics & Mathematics (AREA)
  • Analytical Chemistry (AREA)
  • Molecular Biology (AREA)
  • Urology & Nephrology (AREA)
  • Biomedical Technology (AREA)
  • Cell Biology (AREA)
  • Biotechnology (AREA)
  • Microbiology (AREA)
  • Chemical Kinetics & Catalysis (AREA)
  • Plasma & Fusion (AREA)
  • Food Science & Technology (AREA)
  • Medicinal Chemistry (AREA)
  • Investigating Or Analysing Biological Materials (AREA)
  • Investigating Or Analysing Materials By The Use Of Chemical Reactions (AREA)

Abstract

La présente invention porte sur une bande de capteur, qui peut comprendre : une couche réticulaire pour diffuser uniformément une matière biologique ; une couche de réaction qui est disposée au-dessous de la couche réticulaire et sur laquelle un réactif est appliqué, ledit réactif réagissant avec la matière biologique de manière à déterminer une maladie à l'aide de la matière biologique ; et une couche d'absorption qui est disposée au-dessous de la couche de réaction et qui absorbe la matière biologique et le réactif provenant de la couche de réaction alors que la matière biologique et le réactif ont réagi l'un avec l'autre de manière à empêcher la matière biologique et le réactif d'être réabsorbés dans la couche supérieure. Par conséquent, la sensibilité de la bande de capteur est améliorée et la présence ou l'absence de la maladie peut être déterminée de manière précise.
PCT/KR2013/003067 2012-06-20 2013-04-12 Bande de capteur WO2013191361A1 (fr)

Applications Claiming Priority (2)

Application Number Priority Date Filing Date Title
KR10-2012-0066280 2012-06-20
KR1020120066280A KR101952957B1 (ko) 2012-06-20 2012-06-20 센서 스트립

Publications (1)

Publication Number Publication Date
WO2013191361A1 true WO2013191361A1 (fr) 2013-12-27

Family

ID=49768930

Family Applications (1)

Application Number Title Priority Date Filing Date
PCT/KR2013/003067 WO2013191361A1 (fr) 2012-06-20 2013-04-12 Bande de capteur

Country Status (2)

Country Link
KR (1) KR101952957B1 (fr)
WO (1) WO2013191361A1 (fr)

Cited By (4)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
WO2016156376A1 (fr) * 2015-03-31 2016-10-06 Roche Diagnostics Gmbh Carte de séparation de plasma
US11326992B2 (en) * 2016-02-24 2022-05-10 Partnership For Clean Competition Multilayer device for separating blood components and uses thereof
CN116754341A (zh) * 2023-05-17 2023-09-15 重庆云芯医联科技有限公司 一种谷丙、谷草转氨酶同测的检测卡及其制备方法
WO2025080880A1 (fr) * 2023-10-13 2025-04-17 Blackfly Investments, LLC, DBA Molecular Testing Labs Carte de collecte de tache de sang séché pour dispositif de collecte de taches de sang séché cible

Families Citing this family (5)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
KR102188654B1 (ko) * 2014-05-22 2020-12-08 (주) 미코바이오메드 센서 스트립 및 이를 이용한 헤모글로빈 농도 측정 장치
KR200489144Y1 (ko) * 2014-05-29 2019-05-10 주식회사 미코 센서 스트립 구조물
KR102001553B1 (ko) * 2016-10-20 2019-07-17 (주)플렉센스 바이오센서
KR101981862B1 (ko) * 2017-09-18 2019-05-23 주식회사 미코바이오메드 측면 흐름을 이용한 진단스트립
WO2019135526A1 (fr) * 2018-01-05 2019-07-11 주식회사 원드롭 Bande de mesure de substance biologique

Citations (5)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US4477575A (en) * 1980-08-05 1984-10-16 Boehringer Mannheim Gmbh Process and composition for separating plasma or serum from whole blood
US4587099A (en) * 1981-05-09 1986-05-06 Boehringer Mannheim Gmbh Test strips for the detection of a liquid sample component
KR20000017299A (ko) * 1998-08-13 2000-03-25 리젠펠드 제임스 시각적 혈액 포도당 테스트 스트립
KR20030097467A (ko) * 2002-06-21 2003-12-31 (주)지노첵 생식기관 분비물 채취키트 및 이를 이용한 생식기관 관련질환의 원격진단방법
US20110091914A1 (en) * 2006-01-14 2011-04-21 Roche Diagnostics Operations, Inc. Immunological Test Element with Improved Control Zone

Family Cites Families (3)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US5271895A (en) * 1991-02-27 1993-12-21 Boehringer Mannheim Corporation Test strip
DE19629656A1 (de) * 1996-07-23 1998-01-29 Boehringer Mannheim Gmbh Diagnostischer Testträger mit mehrschichtigem Testfeld und Verfahren zur Bestimmung von Analyt mit dessen Hilfe
KR101058743B1 (ko) * 2009-06-04 2011-08-24 주식회사 인포피아 콜레스테롤 측정 스트립 및 이를 이용한 콜레스테롤 검출 방법

Patent Citations (6)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US4477575A (en) * 1980-08-05 1984-10-16 Boehringer Mannheim Gmbh Process and composition for separating plasma or serum from whole blood
US4477575B1 (fr) * 1980-08-05 1992-04-21 Boehringer Mannheim Gmbh
US4587099A (en) * 1981-05-09 1986-05-06 Boehringer Mannheim Gmbh Test strips for the detection of a liquid sample component
KR20000017299A (ko) * 1998-08-13 2000-03-25 리젠펠드 제임스 시각적 혈액 포도당 테스트 스트립
KR20030097467A (ko) * 2002-06-21 2003-12-31 (주)지노첵 생식기관 분비물 채취키트 및 이를 이용한 생식기관 관련질환의 원격진단방법
US20110091914A1 (en) * 2006-01-14 2011-04-21 Roche Diagnostics Operations, Inc. Immunological Test Element with Improved Control Zone

Cited By (8)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
WO2016156376A1 (fr) * 2015-03-31 2016-10-06 Roche Diagnostics Gmbh Carte de séparation de plasma
CN107430114A (zh) * 2015-03-31 2017-12-01 豪夫迈·罗氏有限公司 血浆分离卡
US10663379B2 (en) 2015-03-31 2020-05-26 Roche Molecular Systems, Inc. Plasma separation card
CN107430114B (zh) * 2015-03-31 2020-07-24 豪夫迈·罗氏有限公司 血浆分离卡
US11326992B2 (en) * 2016-02-24 2022-05-10 Partnership For Clean Competition Multilayer device for separating blood components and uses thereof
US12163876B2 (en) 2016-02-24 2024-12-10 Partnership For Clean Competition Multilayer device for separating blood components and uses thereof
CN116754341A (zh) * 2023-05-17 2023-09-15 重庆云芯医联科技有限公司 一种谷丙、谷草转氨酶同测的检测卡及其制备方法
WO2025080880A1 (fr) * 2023-10-13 2025-04-17 Blackfly Investments, LLC, DBA Molecular Testing Labs Carte de collecte de tache de sang séché pour dispositif de collecte de taches de sang séché cible

Also Published As

Publication number Publication date
KR101952957B1 (ko) 2019-02-28
KR20130142768A (ko) 2013-12-30

Similar Documents

Publication Publication Date Title
WO2013191361A1 (fr) Bande de capteur
US6555061B1 (en) Multi-layer reagent test strip
EP0345781B1 (fr) Un dispositif d'essai ayant un volume déterminé
CN1143132C (zh) 可用肉眼观察的血糖检测条
US8377684B2 (en) Test strip and method for measuring blood cholesterol level using the same
EP1532267B1 (fr) Bandelette reactive pour la detection d'un analyte et procedes d'utilisation
CN100437114C (zh) 样品分析装置
SU1743372A3 (ru) Устройство дл определени составных частей жидкостей
SK99297A3 (en) Volume independent diagnostic test element and method to assay analytes using it
HU186398B (en) Apparatus for separating plasma or serum from whole blood
US8293189B2 (en) Test strip designed to improve spreadability of blood
ES2248951T3 (es) Capas difusoras, humectantes para su preparacion y su empleo en tiras de ensayo.
EP0408223A1 (fr) Dispositif et procédé pour la séparation du plasma du sang et la détermination de constituants du sang
EP0408222A1 (fr) Dispositif et procédé pour la séparation de composants d'un fluide
CA2519402A1 (fr) Membranes adherentes conservant une porosite et une activite biologique dans un dispositif d'essai concu pour mesurer le cholesterol serique associe a des lipoproteines haute densite
CN107991477A (zh) 一种甘油三酯的检测试剂及甘油三酯的检测试纸
CN109580489A (zh) 同时检测血糖和血脂的芯片及方法
ES2430072T3 (es) Elemento de ensayo para el análisis de un líquido corporal
WO2019054844A1 (fr) Bande de diagnostic utilisant un flux latéral
CN106706891B (zh) 血红蛋白的检测试剂及血红蛋白的检测试纸
EP4261539B1 (fr) Dispositif de test sanguin
KR20230145726A (ko) 마약 검출 스트립
WO2024214253A1 (fr) Dispositif d'aide pour test sanguin
GB2345133A (en) Polyspecific antibody immunodiagnostic device
JPH02141664A (ja) 試験具

Legal Events

Date Code Title Description
121 Ep: the epo has been informed by wipo that ep was designated in this application

Ref document number: 13806113

Country of ref document: EP

Kind code of ref document: A1

NENP Non-entry into the national phase

Ref country code: DE

122 Ep: pct application non-entry in european phase

Ref document number: 13806113

Country of ref document: EP

Kind code of ref document: A1