CA2310762C - Capillary active test element having an intermediate layer situated between the support and the covering - Google Patents
Capillary active test element having an intermediate layer situated between the support and the covering Download PDFInfo
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- CA2310762C CA2310762C CA002310762A CA2310762A CA2310762C CA 2310762 C CA2310762 C CA 2310762C CA 002310762 A CA002310762 A CA 002310762A CA 2310762 A CA2310762 A CA 2310762A CA 2310762 C CA2310762 C CA 2310762C
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- capillary
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- 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
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- 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
- G01N33/53—Immunoassay; Biospecific binding assay; Materials therefor
- G01N33/543—Immunoassay; Biospecific binding assay; Materials therefor with an insoluble carrier for immobilising immunochemicals
- G01N33/54366—Apparatus specially adapted for solid-phase testing
- G01N33/54386—Analytical elements
-
- B—PERFORMING OPERATIONS; TRANSPORTING
- B01—PHYSICAL OR CHEMICAL PROCESSES OR APPARATUS IN GENERAL
- B01L—CHEMICAL OR PHYSICAL LABORATORY APPARATUS FOR GENERAL USE
- B01L3/00—Containers or dishes for laboratory use, e.g. laboratory glassware; Droppers
- B01L3/50—Containers for the purpose of retaining a material to be analysed, e.g. test tubes
- B01L3/502—Containers for the purpose of retaining a material to be analysed, e.g. test tubes with fluid transport, e.g. in multi-compartment structures
- B01L3/5023—Containers for the purpose of retaining a material to be analysed, e.g. test tubes with fluid transport, e.g. in multi-compartment structures with a sample being transported to, and subsequently stored in an absorbent for analysis
-
- B—PERFORMING OPERATIONS; TRANSPORTING
- B01—PHYSICAL OR CHEMICAL PROCESSES OR APPARATUS IN GENERAL
- B01L—CHEMICAL OR PHYSICAL LABORATORY APPARATUS FOR GENERAL USE
- B01L2200/00—Solutions for specific problems relating to chemical or physical laboratory apparatus
- B01L2200/02—Adapting objects or devices to another
- B01L2200/026—Fluid interfacing between devices or objects, e.g. connectors, inlet details
- B01L2200/027—Fluid interfacing between devices or objects, e.g. connectors, inlet details for microfluidic devices
-
- B—PERFORMING OPERATIONS; TRANSPORTING
- B01—PHYSICAL OR CHEMICAL PROCESSES OR APPARATUS IN GENERAL
- B01L—CHEMICAL OR PHYSICAL LABORATORY APPARATUS FOR GENERAL USE
- B01L2300/00—Additional constructional details
- B01L2300/08—Geometry, shape and general structure
- B01L2300/0809—Geometry, shape and general structure rectangular shaped
- B01L2300/0825—Test strips
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- B—PERFORMING OPERATIONS; TRANSPORTING
- B01—PHYSICAL OR CHEMICAL PROCESSES OR APPARATUS IN GENERAL
- B01L—CHEMICAL OR PHYSICAL LABORATORY APPARATUS FOR GENERAL USE
- B01L2300/00—Additional constructional details
- B01L2300/08—Geometry, shape and general structure
- B01L2300/0887—Laminated structure
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- B—PERFORMING OPERATIONS; TRANSPORTING
- B01—PHYSICAL OR CHEMICAL PROCESSES OR APPARATUS IN GENERAL
- B01L—CHEMICAL OR PHYSICAL LABORATORY APPARATUS FOR GENERAL USE
- B01L2400/00—Moving or stopping fluids
- B01L2400/04—Moving fluids with specific forces or mechanical means
- B01L2400/0403—Moving fluids with specific forces or mechanical means specific forces
- B01L2400/0406—Moving fluids with specific forces or mechanical means specific forces capillary forces
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- G—PHYSICS
- G01—MEASURING; TESTING
- G01N—INVESTIGATING OR ANALYSING MATERIALS BY DETERMINING THEIR CHEMICAL OR PHYSICAL PROPERTIES
- G01N35/00—Automatic analysis not limited to methods or materials provided for in any single one of groups G01N1/00 - G01N33/00; Handling materials therefor
- G01N35/00029—Automatic analysis not limited to methods or materials provided for in any single one of groups G01N1/00 - G01N33/00; Handling materials therefor provided with flat sample substrates, e.g. slides
- G01N2035/00099—Characterised by type of test elements
- G01N2035/00108—Test strips, e.g. paper
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- Y—GENERAL TAGGING OF NEW TECHNOLOGICAL DEVELOPMENTS; GENERAL TAGGING OF CROSS-SECTIONAL TECHNOLOGIES SPANNING OVER SEVERAL SECTIONS OF THE IPC; TECHNICAL SUBJECTS COVERED BY FORMER USPC CROSS-REFERENCE ART COLLECTIONS [XRACs] AND DIGESTS
- Y10—TECHNICAL SUBJECTS COVERED BY FORMER USPC
- Y10T—TECHNICAL SUBJECTS COVERED BY FORMER US CLASSIFICATION
- Y10T436/00—Chemistry: analytical and immunological testing
- Y10T436/25—Chemistry: analytical and immunological testing including sample preparation
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- Y—GENERAL TAGGING OF NEW TECHNOLOGICAL DEVELOPMENTS; GENERAL TAGGING OF CROSS-SECTIONAL TECHNOLOGIES SPANNING OVER SEVERAL SECTIONS OF THE IPC; TECHNICAL SUBJECTS COVERED BY FORMER USPC CROSS-REFERENCE ART COLLECTIONS [XRACs] AND DIGESTS
- Y10—TECHNICAL SUBJECTS COVERED BY FORMER USPC
- Y10T—TECHNICAL SUBJECTS COVERED BY FORMER US CLASSIFICATION
- Y10T436/00—Chemistry: analytical and immunological testing
- Y10T436/25—Chemistry: analytical and immunological testing including sample preparation
- Y10T436/25375—Liberation or purification of sample or separation of material from a sample [e.g., filtering, centrifuging, etc.]
- Y10T436/255—Liberation or purification of sample or separation of material from a sample [e.g., filtering, centrifuging, etc.] including use of a solid sorbent, semipermeable membrane, or liquid extraction
Abstract
The invention relates to a device for collecting samples of liquid test samples for analytic elements in which the test sample is transported from a sampling location to the determination location via a capillary active canal. The capillary active canal is essentially produced by a carrier, a covering and an optional intermediate layer which lies between the covering and the support, whereby a recess is located in an area, said area constructing the canal which permits capillary liquid transport, on the edge of the analytic test element, said edge constructing the test sample feeding opening, such that the edge of the test element, said edge constructing the test sample feeding opening, is at least partially discontinuous on one side, and the area opposite the recess is open. The invention also relates to a method for accommodating a liquid test sample in an analytic element with the assistance of the inventive device.
Description
CAPILLARY ACTIVE TEST ELEMENT HAVING AN INTERMEDIATE
LAYER SITUATED BETWEEN THE SUPPORT AND THE COVERING
The invention concerns a device for withdrawing samples of liquid samples for analytical elements in which the sample is transported in the analytical element in a capillary-active channel from a sample application opening to the determination site for the sample and in which the capillary-active channel is essentially formed by a carrier, a cover and optionally an intermediate layer lying between the cover and carrier. In addition the invention concerns a process for withdrawing a liquid sample into an analytical element with the aid of the said device.
So-called carrier-bound tests are often used for the qualitative or quantitative analytical determination of components of body fluids, in particular of blood. In these the reagents are embedded in corresponding layers of a solid carrier which is contacted with the sample.
If a target analyte is present, the reaction of the liquid sample and reagents leads to a detectable signal, in particular a colour change which can be evaluated visually or with the aid of an instrument, usually by reflection photometry.
Test elements or test carriers are often in the form of test strips which are essentially composed of an elongate carrier layer made of plastic material and detection layers which are applied thereto as test fields. However, test carriers are also known which are in the shape of small quadratic or rectangular plates.
LAYER SITUATED BETWEEN THE SUPPORT AND THE COVERING
The invention concerns a device for withdrawing samples of liquid samples for analytical elements in which the sample is transported in the analytical element in a capillary-active channel from a sample application opening to the determination site for the sample and in which the capillary-active channel is essentially formed by a carrier, a cover and optionally an intermediate layer lying between the cover and carrier. In addition the invention concerns a process for withdrawing a liquid sample into an analytical element with the aid of the said device.
So-called carrier-bound tests are often used for the qualitative or quantitative analytical determination of components of body fluids, in particular of blood. In these the reagents are embedded in corresponding layers of a solid carrier which is contacted with the sample.
If a target analyte is present, the reaction of the liquid sample and reagents leads to a detectable signal, in particular a colour change which can be evaluated visually or with the aid of an instrument, usually by reflection photometry.
Test elements or test carriers are often in the form of test strips which are essentially composed of an elongate carrier layer made of plastic material and detection layers which are applied thereto as test fields. However, test carriers are also known which are in the shape of small quadratic or rectangular plates.
Test elements for clinical diagnostics that are evaluated visually or by reflection photometry are frequently constructed like electrochemical sensors and biosensors such that the sample application zone and the detection zone are arranged one above the other in a vertical axis. This mode of construction is problematic.
When the test strip loaded with sample has to be inserted into an instrument, for example a reflection photometer, for measurement, potentially infectious sample material can come into contact with parts of the instrument and may contaminate them. Furthermore volumetric dosing can only be achieved with difficulty especially in cases in which the test strips are used by untrained persons for example in the self-control of blood sugar by diabetics.
Recently test elements have become available which provide a capillary channel or gap with the aid of which at least some of the described problems can be solved.
EP-B-0 034 049 concerns a test element in which the sample is applied to a central sample application site for example an opening in a cover and is transported by capillary force to several detection zones which are spatially separated from the sample application site. In this case it is remarkable that a special design for the geometry of the sample application opening which is also described in EP-B-0 010 456 is emphasized as being particularly preferable. A regular hexagonal shape of the sample entry opening in top view is claimed to centre a drop of liquid sample in the opening. This is claimed to facilitate penetration of the sample into the capillary-active channel which is perpendicular to the sample application opening.
whereas in the desc:rOoec~ r:api 1 r< y, ~~zp te:st elements l:he sample i:; a',pp L ie>d t:lrr:ouc~l~ ,av c:>p -r.irrg in thF~ test element wh:iclr i.~~ ~~e>rptm~3it:i..r:1_ax ~_~ ~ t rue coal:.i.lla:r,~ qap, i.n otrrer dc:si_:~n~> tlme ;~rr;rple 1 iclr, a:_. _~p~;lied :iirectly into the capillary c~al:> 1;.3ra:Llf~. ~ ~, :e directican of :>pread. Z'h:LS is mo.~'t. ::,irnp:Ly lc a~trry:~1 ~~;lved. by th:~ t.est element having an E:~dg<:> w~~h~.re 'tlrc- <:a .;i=l.laxy gap ends and which is dir:w,;tl.y ~~u;rvt ~~c:tc_cl ~. _t Ir ~.r samp:l.e ~ iquid acrd is taken up by tu:km w~Ea ~nuE;:1 v~~t~.~.c o :i:~ capa.bl~c, c>f capillary _Liquid t:i <~m;pc:;rt::.
A frequent pr~obl.em wit-.la tk~re lal:t::c~z t:est elements is t:hat. liquid drops wlxic;'Lr are al:al> _. ~r eYca to the Sample application opening oi' t:he~ crap ~ . r-a.r~~ c.~a,p are tn~t able t:o ~>enetrate int ~~ t.lm~a chap . ~r~lr:i ~ i~l:~e uc~rnennn c,an have different cawses. 1t i~ c~>nme.,i.~..~4vk~l~ that i.n tlc manufacture of such t f-~:~t: ~ lemt:mt t ~v~e openirlq for fabrication reasons does root h.-ev«~ t ~e ci~.mensica::vs that.
are required l=or a 4arnp ve dLC.La t c:~ ~nt-c.i_ into t.'.'o.e caapi..llary ch a:nnel fear ce,.:arryale: k~~- . :::ru ~e~ the opening has been contarnirrated car .rqtrar=heci wr7t.~o -:lre test e:l~ment was cut to :Le'ngtEr, c.ur ~:ar staml>r~:1 ca~.zt . :Another reason may be. that tree hydroploeobrci.t~,~ ~:;t tire: rrratera a:l~~~ which are often used to nranmf~rcture ~ L::~ s aid test a L~-_~ments w~Lich as for ~~xarryLE: h~:~da;~al~lm~bi ~ , '~a sta_cs, impaa r, delay or prevent pc,net ~ xt:..~ori cat ~ 1.e sample Lnl~c~, the capillary gap. For exa:znrl.~lc.:: ~ i c.1~5:.;dzop already does not enter into the :insi.cle of r~ c~y;~il.la:ry channel or canly very slowl~r i.f i.t:~r inner' ,ur rv,a :i:s are indc=red.
hydrophilic b'~at. thEV cl.at ~~c~ge i. ° arrd~°opho';ic due to the materials rrs~=~::i.
1'he present invention sc.~eka to e-,: i.nrirr.at~e tLre disadvantages of tire pr icar ,art .
The invention concerns a device for withdrawing liquid samples for analytical elements in which the sample is transported in a capillary-active channel from the sample amplification opening to the site of determination of the sample in the analytical element and in which the capillary-active channel is essentially formed by a carrier, a cover and optionally an intermediate layer lying between the cover and Garner which is characterized in that there is a notch in one of the surfaces forming the channel capable of capillary liquid transport at the edge of the analytical element that forms the sample application opening so that one side of the edge of the device forming the sample application opening is at least partially interrupted and the opposite surface of the notch is exposed.
Thus, in accordance with the invention, there is provided a device for withdrawing a liquid sample for analytical elements in which the sample is transported in a capillary-active channel from the sampling site to the determination site and in which the capillary-active channel is essentially formed by a carrier and a cover wherein a notch in the form of a partial groove is located in one of the surfaces forming the channel capable of capillary liquid transport on a lateral face of the device containing a sample application opening, the notch beginning at said lateral face of the device and pointing towards the capillary active channel from the sampling site so that the surface opposite to the notch is exposed.
The device according to the invention particularly preferably contains one such notch. However, other designs can also be realised in which several and at DOCSMTL: 2054621\1 _ ~~ ~~
Least two no t;ches are pxe=>ent~ tyo~~etrler i.r~ one su dace or are offset on oppo~~i to s~.zi: f ~c c~~a . ':'here are rno limits to the shapc7 oC: ;:_tm zo#: ~=lm~> i>r.c»Tici.ed at lE;ast wart: of the edge which ~ormx~ r3~~=~ ,~;s nple application c:~per~ing is at least p~~:ct:i,ull~~ m:_r ~~rr_vz~>ted by. tire notch. Herzc:e trianc~ul<:.~r or ~:ac.~L J~;..~x~a. as well a~ round oz: elliptic:.al. fc>rnl;:~ ax-e possiL~i_e~ Z r...,i~,gular sh~ipes a:=a also not excluded.
The notch :in a srzrface iorminc;~ t c.~e :~~pi_l.lary c~ual:mel at the edge :oaf t=he te:;t e~erneat. :rm.~kv farms tma s~ampie ~~.pplication oper~ixic~ ser~,.ue~; to c o.u_iz~> that the ~arnple liquid can enter into the capillary channel. This is achieved in that the sample drop can be directly applied to one of the surfaces, whose extension forms the inner surface of the capillary, at the edge of the device that is broken by the notch which is nearest the sample application opening. Suitable selection of the geometry and dimensions of the notch ensures that the liquid drop comes into contact with the capillary active zone with very high probability, independent of the exact position of the dosing and is readily sucked into the inside of the capillary. For example the size of the exposed surface should be selected such that at least one site of the liquid drop that is applied thereto comes into contact with the capillary-active zone. For example one dimension of the notch, such as its width, should be selected such that the diameter of the liquid drop is slightly larger than the selected dimension of the notch. A notch width of 1 mm has proven to be suitable for a drop of 3 ~1. Suction of the sample drop into the capillary channel is particularly preferably achieved by the area exposed by the notch being hydrophilized and bordering directly on a capillary active zone at least in the direction of the capillary transport channel.
In this connection hydrophilic surfaces are water-attracting surfaces. Aqueous samples, also including blood, spread well on such surfaces. Such surfaces are characterized among others in that a water drop placed on it forms an acute rim angle or contact angle at the interface. In contrast an obtuse rim angle is formed at the interface between the water drop and the surface on hydrophobic i.e. water repellent surfaces.
The rim angle which is a result of the surface tensions of the test liquid and of the surface to be examined is a measure of the hydrophilicity of a surface. Water for example has a surface tension of 72 mN/m. If the value of the surface tension of the observed surface is much below this value i.e. more than 20 mN/m, then the wetting is poor and the resulting rim angle is obtuse.
Such a surface is referred to as hydrophobic. If the surface tension approximates the value which is found for water then the wetting is good and the rim angle is acute. If, in contrast, the surface tension is the same as or higher than that of the value found for water, then the drop runs and there is a total spreading of the liquid. It is then no longer possible to measure a rim angle. Surfaces which form an acute rim angle with water drops or on which a total spreading of a water drop is observed are referred to as hydrophilic.
The ability of a capillary to suck up a liquid depends on the wettability of the channel surface with the liquid. This means for aqueous samples that a capillary should be manufactured from a material whose surface tension almost reaches 72 mN/m or exceeds this value.
Sufficiently hydrophilic materials for the construction of a capillary which rapidly sucks up aqueous samples are for example glass, metal or ceramics. However, these materials are unsuitable for use in test carriers since they have some severe disadvantages such as risk of breaking in the case of glass or ceramics or change in the surface properties with time in the case of numerous metals. Therefore plastic foils or moulded parts are usually used to manufacture test elements. As a rule the plastics used hardly exceed a surface tension of 45 mN/m.
Even with the, in a relative sense, most hydrophilic plastics such as polymethylmethacrylate (PMMA) or polyamide (PA) it is only possible - if at all - to construct slowly sucking capillaries. Capillaries made of hydrophobic plastics such as for example polystyrene (PS), polypropylene (PP) or polyethylene (PE) essentially do not suck aqueous samples. Consequently it is necessary to endow the plastics used as a construction material for test elements with capillary active channels with hydrophilic properties i.e. to hydrophilize them.
In a preferred embodiment of the analytical test element according to the invention at least one, but preferably two and especially preferably two opposite surfaces which form the inner surface of the channel capable of capillary liquid transport are hydrophilized. At least the exposed surface opposite the notch is very preferably hydrophilized. If more than one surface is hydrophilized then the surfaces can either be made hydrophilic using the same or different methods.
Hydrophilization is particularly necessary when the materials that form the capillary active channel, in particular the carrier, are themselves hydrophobic or only very slightly hydrophilic because they are for example composed of nonpolar plastics. Nonpolar plastics such as for example polystyrene (PS), polyethylene (PE), polyethylene terephthalate (PET) or polyvinyl chloride (PVC) are advantageous as carrier materials because they do not absorb the liquids to be examined and thus the sample volume can be effectively utilized by the detection layer. The hydrophilization of the surface of the capillary channel enables a polar, preferably aqueous, sample liquid to readily enter the capillary channel and be rapidly transported to the site of determination of the sample. In this connection the site of determination is understood as that site or that zone to which the sample should be transported in the analytical element in order to achieve the desired _ g _ result. If the analytical element is for example a test carrier that is to be evaluated optically or photometrically, the site of determination of the sample is the detection zone of the test carrier in which a reaction with a change in colour is observable. If the analytical element is an electrochemical sensor the site of determination of the sample is understood as an electrode integrated into the sensor which is capable of the desired electrochemical detection reaction. If the analytical element does not itself serve to detect an analyte in a sample, but for example is only used for volume dosing or taking up a certain amount of sample material, the site of determination of the sample can be simply a mark on the analytical element up to which the capillary gap has to be filled in order to for example measure a certain minimum sample volume.
Ideally the hydrophilizaton of the surface of the capillary channel is achieved by using a hydrophilic material in its manufacture which, however, cannot itself suck up the sample liquid or only to a negligible extent. In cases where this is not possible a hydrophobic or only very slightly hydrophilic surface can be hydrophilized by suitable coating with a stable hydrophilic layer that is inert towards the sample material for example by covalently binding photoreactive hydrophilic polymers onto a plastic surface by applying layers containing wetting agents or by coating surfaces with nanocomposites by means of sol-gel technology.
Furthermore it is also possible to achieve an increased hydrophilicity by thermal, physical or chemical treatment of the surface.
The hydrophilization is quite especially preferably achieved by using thin layers of oxidized aluminium.
_ g _ These layers are either applied directly to the desired components of the test element for example by vacuum coating the work pieces with metallic aluminium and subsequently oxidizing the metal, or by using metal foils or metal-coated plastics for the construction of the test carriers which also have to be oxidized to achieve the desired hydrophilicity. In this case metal layer thicknesses of 1 to 500 nm are adequate. The metal layer is subsequently oxidized to form the oxidized form in which case above all oxidation in the presence of water vapour or by boiling in water have proven to be especially suitable methods in addition to electrochemical, anodic oxidation. The oxide layers formed in this manner are between 0.1 and 500 nm, preferably between 10 and 100 nm thick depending on the method. Larger layer thicknesses of the metal layer as well as of the oxide layer can in principle be realised in practice but do not exhibit any additional advantageous effects.
A second subject matter of the invention concerns a process for withdrawing a liquid sample, in particular a body fluid such as blood, plasma, serum, urine, saliva, sweat etc. with the aid of a device according to the invention. In this process the liquid sample is firstly contacted with the device at the edge of the sample application opening which is interrupted by the notch.
The sample liquid is transported into the inside of the device by capillary forces in the channel that is capable of capillary liquid transport so that it can reach its site of determination.
The invention is elucidated in more detail by figures 1 and 2 and by the following examples.
Figure 1 shows a particularly preferred embodiment of the device according to the invention. A schematic top view of the device according to the invention is shown in Figure lA. Figures 1B to 1G each show cross-sectional views along the lines A-A'(1B), B-B'(1C), C-C'(1D and 1G), D-D'(lE) and E-E'(1F) respectively.
Figure 2 shows a perspective detailed enlargement of the sample application region of the device according to the invention.
The numbers in the Figures denote:
1 carrier 2 detection element 3 capillary channel 4 sample application opening notch for sample application 6 vent opening 7 cover 8 gap cover foil 9 intermediate layer support foil Various views (Figures lA to 1F) of a particularly preferred embodiment of the device according to the invention are shown schematically in Figure 1. The views shown are intended to give a three-dimensional impression of the device according to the invention. An intermediate layer (9) is mounted on a carrier (1) for example in the form of a double-sided adhesive tape. In the area of the capillary channel (3) the intermediate layer (9) has a recess which determines the length and width of the channel (3). Its height is given by the thickness of the intermediate layer (9). On the side of the capillary channel (3) which is opposite to the carrier (1), a cover (7) e.g. a plastic foil is located adjacent to the detection element (2) e.g. a reagent-impregnated membrane. A gap cover foil (8) is provided to ensure capillary continuity between the detection element and cover. This can be hydrophilized to enable a rapid transport of sample from the sample application opening (4) to the vent opening (6) which marks the opposite end of the capillary channel. An additional advantage of the hydrophilization is that a drop of sample liquid can be applied directly to a hydrophilic surface in the area of the notch (5) which is surrounded on several boundary sides by the capillary active zone (3). This leads to a rapid penetration of the liquid drop into the test element.
The capillary zone (3) extends from the sample application opening (4) to the opposite end of the detection element (2) and thus ensures that the sample liquid can contact the whole area of the detection element (2) and thus a homogeneous sample distribution over the detection element (2). The sample application opening (4) and vent opening (6) limit the capillary active region (3) in the direction of capillary transport.
Fig. 1G shows how the intermediate layer (9) can be covered by a supporting foil (10) in order to cover areas of the adhesive tape that are exposed. However, the vent opening (6) must not be covered.
When using the device shown, its sample application opening (4) is for example contacted with a blood drop located on a fingertip. In this connection it is unimportant whether the blood drop comes into contact with the device according to the invention containing the sample application opening (4) from above i.e. on the flat side of the carrier (1) or from the front i.e.
from the front side of the test element. This largely rules out an erroneous application of sample which would for example be expected of users that are used to conventional test strips that have to be dosed from above. when the device according to the invention is used the blood drop comes into contact with the exposed surface which is optionally hydrophilized and simultaneously with the capillary channel (3) through the notch (5) in the carrier (1). The capillary channel fills itself with sample until it is filled from the sample application opening (4) to the vent opening (6).
Afterwards the device is removed from the patient's finger which ensures that only the sample that is present in the capillary channel (3) is available for the detection element (2). Thus overdosing is excluded.
The defined height of the capillary channel provides a defined layer thickness of the sample on the detection element.
A detail enlargement of a perspective view of the sample application area of a particularly preferred embodiment of the test element according to the invention is shown in Figure 2. The notch (5) in the carrier (1) facilitates penetration of a sample liquid from the sample application opening (4) into the capillary active zone (3) which in the present case is formed by the carrier (1), intermediate layer (9) and cover (7). In addition to the shape shown the notch can also have any other desired shape which serves the purpose according to the invention. Among others semicircular, triangular or polygonal shapes and the use of one or several adjacent staggered opposing notches are possible.
Example 1 Manufacture of the analytical test element according to the invention A double-sided adhesive tape with a thickness of 100 ~m is glued onto a 350 ~m thick foil of polyethylene terephthalate (Melinex~, ICI, Frankfurt am Main, Germany) coated with a 30 nm thick layer of aluminium which was completely oxidized with water vapour. The foil has a length of 25 mm and is 5 mm wide. A central notch-shaped recess of 1 mm width and 2 mm length is located on one of the short sides. The adhesive tape has a punched hole of 2 mm width and more than 15 mm length which defines the dimensions of the capillary channel.
The length of the punched hole is selected to be slightly larger than the desired length of the capillary-active channel which is determined by its cover in order to ensure venting of the channel during filling with sample liquid. A 3 mm long and 5 mm wide detection film is glued onto the side of the adhesive tape which provides the venting at a distance of 1 mm from the end of the punched hole. A film is used as the detection film as is known from the German Patent Application No. P 196 29 656Ø The detection film is specific for the detection of glucose. A 12 mm long and 5 mm wide cover layer is glued onto the region of the adhesive tape that is still open between the notch-shaped recess and detection film so that the cover layer and detection film abut one another. The cover layer is composed of a 150 ~,m thick polyethylene terephthalate foil provided on one side with adhesive onto which a 6 ~.m thick polyethylene terephthalate foil (both:
Hostaphan~, Hoechst, Frankfurt am Main, Germany) coated with a 30 nm thick oxidized aluminium layer on the side facing the capillary channel is glued. In this case the thinner foil extends ca. 500 ~,m beyond the thicker foil on the side facing the detection film. When the cover layer is mounted on the adhesive tape care must be taken that the protruding end of the thinner foil comes to lie between the detection element and the thicker foil of the cover layer. In order to cover areas of the adhesive foil that are still exposed, these are covered with a 175 ~Cm thick Melinex~ foil without, however, covering functional areas.
The test element obtained in this manner has a capillary channel of 15 mm length, 2 mm width and 0.1 mm height.
The channel can take up 3 ~.1 sample liquid. An area of 3 mm x 2 mm of the detection film is wetted by the sample.
Example 2 Measurement of the blood glucose concentration with the aid of the test element from example 1 The sample application side of the test element from example 1 is placed on a drop of sample liquid. The capillary of the test element automatically fills with sample within 2 s. If glucose is present in the sample a colour development is visible in the detection film after a few seconds. The end point of the reaction is reached after ca. 30 to 35 s. The colour obtained can be correlated with the glucose concentration of the sample and either evaluated visually or by reflection photometry.
When the test strip loaded with sample has to be inserted into an instrument, for example a reflection photometer, for measurement, potentially infectious sample material can come into contact with parts of the instrument and may contaminate them. Furthermore volumetric dosing can only be achieved with difficulty especially in cases in which the test strips are used by untrained persons for example in the self-control of blood sugar by diabetics.
Recently test elements have become available which provide a capillary channel or gap with the aid of which at least some of the described problems can be solved.
EP-B-0 034 049 concerns a test element in which the sample is applied to a central sample application site for example an opening in a cover and is transported by capillary force to several detection zones which are spatially separated from the sample application site. In this case it is remarkable that a special design for the geometry of the sample application opening which is also described in EP-B-0 010 456 is emphasized as being particularly preferable. A regular hexagonal shape of the sample entry opening in top view is claimed to centre a drop of liquid sample in the opening. This is claimed to facilitate penetration of the sample into the capillary-active channel which is perpendicular to the sample application opening.
whereas in the desc:rOoec~ r:api 1 r< y, ~~zp te:st elements l:he sample i:; a',pp L ie>d t:lrr:ouc~l~ ,av c:>p -r.irrg in thF~ test element wh:iclr i.~~ ~~e>rptm~3it:i..r:1_ax ~_~ ~ t rue coal:.i.lla:r,~ qap, i.n otrrer dc:si_:~n~> tlme ;~rr;rple 1 iclr, a:_. _~p~;lied :iirectly into the capillary c~al:> 1;.3ra:Llf~. ~ ~, :e directican of :>pread. Z'h:LS is mo.~'t. ::,irnp:Ly lc a~trry:~1 ~~;lved. by th:~ t.est element having an E:~dg<:> w~~h~.re 'tlrc- <:a .;i=l.laxy gap ends and which is dir:w,;tl.y ~~u;rvt ~~c:tc_cl ~. _t Ir ~.r samp:l.e ~ iquid acrd is taken up by tu:km w~Ea ~nuE;:1 v~~t~.~.c o :i:~ capa.bl~c, c>f capillary _Liquid t:i <~m;pc:;rt::.
A frequent pr~obl.em wit-.la tk~re lal:t::c~z t:est elements is t:hat. liquid drops wlxic;'Lr are al:al> _. ~r eYca to the Sample application opening oi' t:he~ crap ~ . r-a.r~~ c.~a,p are tn~t able t:o ~>enetrate int ~~ t.lm~a chap . ~r~lr:i ~ i~l:~e uc~rnennn c,an have different cawses. 1t i~ c~>nme.,i.~..~4vk~l~ that i.n tlc manufacture of such t f-~:~t: ~ lemt:mt t ~v~e openirlq for fabrication reasons does root h.-ev«~ t ~e ci~.mensica::vs that.
are required l=or a 4arnp ve dLC.La t c:~ ~nt-c.i_ into t.'.'o.e caapi..llary ch a:nnel fear ce,.:arryale: k~~- . :::ru ~e~ the opening has been contarnirrated car .rqtrar=heci wr7t.~o -:lre test e:l~ment was cut to :Le'ngtEr, c.ur ~:ar staml>r~:1 ca~.zt . :Another reason may be. that tree hydroploeobrci.t~,~ ~:;t tire: rrratera a:l~~~ which are often used to nranmf~rcture ~ L::~ s aid test a L~-_~ments w~Lich as for ~~xarryLE: h~:~da;~al~lm~bi ~ , '~a sta_cs, impaa r, delay or prevent pc,net ~ xt:..~ori cat ~ 1.e sample Lnl~c~, the capillary gap. For exa:znrl.~lc.:: ~ i c.1~5:.;dzop already does not enter into the :insi.cle of r~ c~y;~il.la:ry channel or canly very slowl~r i.f i.t:~r inner' ,ur rv,a :i:s are indc=red.
hydrophilic b'~at. thEV cl.at ~~c~ge i. ° arrd~°opho';ic due to the materials rrs~=~::i.
1'he present invention sc.~eka to e-,: i.nrirr.at~e tLre disadvantages of tire pr icar ,art .
The invention concerns a device for withdrawing liquid samples for analytical elements in which the sample is transported in a capillary-active channel from the sample amplification opening to the site of determination of the sample in the analytical element and in which the capillary-active channel is essentially formed by a carrier, a cover and optionally an intermediate layer lying between the cover and Garner which is characterized in that there is a notch in one of the surfaces forming the channel capable of capillary liquid transport at the edge of the analytical element that forms the sample application opening so that one side of the edge of the device forming the sample application opening is at least partially interrupted and the opposite surface of the notch is exposed.
Thus, in accordance with the invention, there is provided a device for withdrawing a liquid sample for analytical elements in which the sample is transported in a capillary-active channel from the sampling site to the determination site and in which the capillary-active channel is essentially formed by a carrier and a cover wherein a notch in the form of a partial groove is located in one of the surfaces forming the channel capable of capillary liquid transport on a lateral face of the device containing a sample application opening, the notch beginning at said lateral face of the device and pointing towards the capillary active channel from the sampling site so that the surface opposite to the notch is exposed.
The device according to the invention particularly preferably contains one such notch. However, other designs can also be realised in which several and at DOCSMTL: 2054621\1 _ ~~ ~~
Least two no t;ches are pxe=>ent~ tyo~~etrler i.r~ one su dace or are offset on oppo~~i to s~.zi: f ~c c~~a . ':'here are rno limits to the shapc7 oC: ;:_tm zo#: ~=lm~> i>r.c»Tici.ed at lE;ast wart: of the edge which ~ormx~ r3~~=~ ,~;s nple application c:~per~ing is at least p~~:ct:i,ull~~ m:_r ~~rr_vz~>ted by. tire notch. Herzc:e trianc~ul<:.~r or ~:ac.~L J~;..~x~a. as well a~ round oz: elliptic:.al. fc>rnl;:~ ax-e possiL~i_e~ Z r...,i~,gular sh~ipes a:=a also not excluded.
The notch :in a srzrface iorminc;~ t c.~e :~~pi_l.lary c~ual:mel at the edge :oaf t=he te:;t e~erneat. :rm.~kv farms tma s~ampie ~~.pplication oper~ixic~ ser~,.ue~; to c o.u_iz~> that the ~arnple liquid can enter into the capillary channel. This is achieved in that the sample drop can be directly applied to one of the surfaces, whose extension forms the inner surface of the capillary, at the edge of the device that is broken by the notch which is nearest the sample application opening. Suitable selection of the geometry and dimensions of the notch ensures that the liquid drop comes into contact with the capillary active zone with very high probability, independent of the exact position of the dosing and is readily sucked into the inside of the capillary. For example the size of the exposed surface should be selected such that at least one site of the liquid drop that is applied thereto comes into contact with the capillary-active zone. For example one dimension of the notch, such as its width, should be selected such that the diameter of the liquid drop is slightly larger than the selected dimension of the notch. A notch width of 1 mm has proven to be suitable for a drop of 3 ~1. Suction of the sample drop into the capillary channel is particularly preferably achieved by the area exposed by the notch being hydrophilized and bordering directly on a capillary active zone at least in the direction of the capillary transport channel.
In this connection hydrophilic surfaces are water-attracting surfaces. Aqueous samples, also including blood, spread well on such surfaces. Such surfaces are characterized among others in that a water drop placed on it forms an acute rim angle or contact angle at the interface. In contrast an obtuse rim angle is formed at the interface between the water drop and the surface on hydrophobic i.e. water repellent surfaces.
The rim angle which is a result of the surface tensions of the test liquid and of the surface to be examined is a measure of the hydrophilicity of a surface. Water for example has a surface tension of 72 mN/m. If the value of the surface tension of the observed surface is much below this value i.e. more than 20 mN/m, then the wetting is poor and the resulting rim angle is obtuse.
Such a surface is referred to as hydrophobic. If the surface tension approximates the value which is found for water then the wetting is good and the rim angle is acute. If, in contrast, the surface tension is the same as or higher than that of the value found for water, then the drop runs and there is a total spreading of the liquid. It is then no longer possible to measure a rim angle. Surfaces which form an acute rim angle with water drops or on which a total spreading of a water drop is observed are referred to as hydrophilic.
The ability of a capillary to suck up a liquid depends on the wettability of the channel surface with the liquid. This means for aqueous samples that a capillary should be manufactured from a material whose surface tension almost reaches 72 mN/m or exceeds this value.
Sufficiently hydrophilic materials for the construction of a capillary which rapidly sucks up aqueous samples are for example glass, metal or ceramics. However, these materials are unsuitable for use in test carriers since they have some severe disadvantages such as risk of breaking in the case of glass or ceramics or change in the surface properties with time in the case of numerous metals. Therefore plastic foils or moulded parts are usually used to manufacture test elements. As a rule the plastics used hardly exceed a surface tension of 45 mN/m.
Even with the, in a relative sense, most hydrophilic plastics such as polymethylmethacrylate (PMMA) or polyamide (PA) it is only possible - if at all - to construct slowly sucking capillaries. Capillaries made of hydrophobic plastics such as for example polystyrene (PS), polypropylene (PP) or polyethylene (PE) essentially do not suck aqueous samples. Consequently it is necessary to endow the plastics used as a construction material for test elements with capillary active channels with hydrophilic properties i.e. to hydrophilize them.
In a preferred embodiment of the analytical test element according to the invention at least one, but preferably two and especially preferably two opposite surfaces which form the inner surface of the channel capable of capillary liquid transport are hydrophilized. At least the exposed surface opposite the notch is very preferably hydrophilized. If more than one surface is hydrophilized then the surfaces can either be made hydrophilic using the same or different methods.
Hydrophilization is particularly necessary when the materials that form the capillary active channel, in particular the carrier, are themselves hydrophobic or only very slightly hydrophilic because they are for example composed of nonpolar plastics. Nonpolar plastics such as for example polystyrene (PS), polyethylene (PE), polyethylene terephthalate (PET) or polyvinyl chloride (PVC) are advantageous as carrier materials because they do not absorb the liquids to be examined and thus the sample volume can be effectively utilized by the detection layer. The hydrophilization of the surface of the capillary channel enables a polar, preferably aqueous, sample liquid to readily enter the capillary channel and be rapidly transported to the site of determination of the sample. In this connection the site of determination is understood as that site or that zone to which the sample should be transported in the analytical element in order to achieve the desired _ g _ result. If the analytical element is for example a test carrier that is to be evaluated optically or photometrically, the site of determination of the sample is the detection zone of the test carrier in which a reaction with a change in colour is observable. If the analytical element is an electrochemical sensor the site of determination of the sample is understood as an electrode integrated into the sensor which is capable of the desired electrochemical detection reaction. If the analytical element does not itself serve to detect an analyte in a sample, but for example is only used for volume dosing or taking up a certain amount of sample material, the site of determination of the sample can be simply a mark on the analytical element up to which the capillary gap has to be filled in order to for example measure a certain minimum sample volume.
Ideally the hydrophilizaton of the surface of the capillary channel is achieved by using a hydrophilic material in its manufacture which, however, cannot itself suck up the sample liquid or only to a negligible extent. In cases where this is not possible a hydrophobic or only very slightly hydrophilic surface can be hydrophilized by suitable coating with a stable hydrophilic layer that is inert towards the sample material for example by covalently binding photoreactive hydrophilic polymers onto a plastic surface by applying layers containing wetting agents or by coating surfaces with nanocomposites by means of sol-gel technology.
Furthermore it is also possible to achieve an increased hydrophilicity by thermal, physical or chemical treatment of the surface.
The hydrophilization is quite especially preferably achieved by using thin layers of oxidized aluminium.
_ g _ These layers are either applied directly to the desired components of the test element for example by vacuum coating the work pieces with metallic aluminium and subsequently oxidizing the metal, or by using metal foils or metal-coated plastics for the construction of the test carriers which also have to be oxidized to achieve the desired hydrophilicity. In this case metal layer thicknesses of 1 to 500 nm are adequate. The metal layer is subsequently oxidized to form the oxidized form in which case above all oxidation in the presence of water vapour or by boiling in water have proven to be especially suitable methods in addition to electrochemical, anodic oxidation. The oxide layers formed in this manner are between 0.1 and 500 nm, preferably between 10 and 100 nm thick depending on the method. Larger layer thicknesses of the metal layer as well as of the oxide layer can in principle be realised in practice but do not exhibit any additional advantageous effects.
A second subject matter of the invention concerns a process for withdrawing a liquid sample, in particular a body fluid such as blood, plasma, serum, urine, saliva, sweat etc. with the aid of a device according to the invention. In this process the liquid sample is firstly contacted with the device at the edge of the sample application opening which is interrupted by the notch.
The sample liquid is transported into the inside of the device by capillary forces in the channel that is capable of capillary liquid transport so that it can reach its site of determination.
The invention is elucidated in more detail by figures 1 and 2 and by the following examples.
Figure 1 shows a particularly preferred embodiment of the device according to the invention. A schematic top view of the device according to the invention is shown in Figure lA. Figures 1B to 1G each show cross-sectional views along the lines A-A'(1B), B-B'(1C), C-C'(1D and 1G), D-D'(lE) and E-E'(1F) respectively.
Figure 2 shows a perspective detailed enlargement of the sample application region of the device according to the invention.
The numbers in the Figures denote:
1 carrier 2 detection element 3 capillary channel 4 sample application opening notch for sample application 6 vent opening 7 cover 8 gap cover foil 9 intermediate layer support foil Various views (Figures lA to 1F) of a particularly preferred embodiment of the device according to the invention are shown schematically in Figure 1. The views shown are intended to give a three-dimensional impression of the device according to the invention. An intermediate layer (9) is mounted on a carrier (1) for example in the form of a double-sided adhesive tape. In the area of the capillary channel (3) the intermediate layer (9) has a recess which determines the length and width of the channel (3). Its height is given by the thickness of the intermediate layer (9). On the side of the capillary channel (3) which is opposite to the carrier (1), a cover (7) e.g. a plastic foil is located adjacent to the detection element (2) e.g. a reagent-impregnated membrane. A gap cover foil (8) is provided to ensure capillary continuity between the detection element and cover. This can be hydrophilized to enable a rapid transport of sample from the sample application opening (4) to the vent opening (6) which marks the opposite end of the capillary channel. An additional advantage of the hydrophilization is that a drop of sample liquid can be applied directly to a hydrophilic surface in the area of the notch (5) which is surrounded on several boundary sides by the capillary active zone (3). This leads to a rapid penetration of the liquid drop into the test element.
The capillary zone (3) extends from the sample application opening (4) to the opposite end of the detection element (2) and thus ensures that the sample liquid can contact the whole area of the detection element (2) and thus a homogeneous sample distribution over the detection element (2). The sample application opening (4) and vent opening (6) limit the capillary active region (3) in the direction of capillary transport.
Fig. 1G shows how the intermediate layer (9) can be covered by a supporting foil (10) in order to cover areas of the adhesive tape that are exposed. However, the vent opening (6) must not be covered.
When using the device shown, its sample application opening (4) is for example contacted with a blood drop located on a fingertip. In this connection it is unimportant whether the blood drop comes into contact with the device according to the invention containing the sample application opening (4) from above i.e. on the flat side of the carrier (1) or from the front i.e.
from the front side of the test element. This largely rules out an erroneous application of sample which would for example be expected of users that are used to conventional test strips that have to be dosed from above. when the device according to the invention is used the blood drop comes into contact with the exposed surface which is optionally hydrophilized and simultaneously with the capillary channel (3) through the notch (5) in the carrier (1). The capillary channel fills itself with sample until it is filled from the sample application opening (4) to the vent opening (6).
Afterwards the device is removed from the patient's finger which ensures that only the sample that is present in the capillary channel (3) is available for the detection element (2). Thus overdosing is excluded.
The defined height of the capillary channel provides a defined layer thickness of the sample on the detection element.
A detail enlargement of a perspective view of the sample application area of a particularly preferred embodiment of the test element according to the invention is shown in Figure 2. The notch (5) in the carrier (1) facilitates penetration of a sample liquid from the sample application opening (4) into the capillary active zone (3) which in the present case is formed by the carrier (1), intermediate layer (9) and cover (7). In addition to the shape shown the notch can also have any other desired shape which serves the purpose according to the invention. Among others semicircular, triangular or polygonal shapes and the use of one or several adjacent staggered opposing notches are possible.
Example 1 Manufacture of the analytical test element according to the invention A double-sided adhesive tape with a thickness of 100 ~m is glued onto a 350 ~m thick foil of polyethylene terephthalate (Melinex~, ICI, Frankfurt am Main, Germany) coated with a 30 nm thick layer of aluminium which was completely oxidized with water vapour. The foil has a length of 25 mm and is 5 mm wide. A central notch-shaped recess of 1 mm width and 2 mm length is located on one of the short sides. The adhesive tape has a punched hole of 2 mm width and more than 15 mm length which defines the dimensions of the capillary channel.
The length of the punched hole is selected to be slightly larger than the desired length of the capillary-active channel which is determined by its cover in order to ensure venting of the channel during filling with sample liquid. A 3 mm long and 5 mm wide detection film is glued onto the side of the adhesive tape which provides the venting at a distance of 1 mm from the end of the punched hole. A film is used as the detection film as is known from the German Patent Application No. P 196 29 656Ø The detection film is specific for the detection of glucose. A 12 mm long and 5 mm wide cover layer is glued onto the region of the adhesive tape that is still open between the notch-shaped recess and detection film so that the cover layer and detection film abut one another. The cover layer is composed of a 150 ~,m thick polyethylene terephthalate foil provided on one side with adhesive onto which a 6 ~.m thick polyethylene terephthalate foil (both:
Hostaphan~, Hoechst, Frankfurt am Main, Germany) coated with a 30 nm thick oxidized aluminium layer on the side facing the capillary channel is glued. In this case the thinner foil extends ca. 500 ~,m beyond the thicker foil on the side facing the detection film. When the cover layer is mounted on the adhesive tape care must be taken that the protruding end of the thinner foil comes to lie between the detection element and the thicker foil of the cover layer. In order to cover areas of the adhesive foil that are still exposed, these are covered with a 175 ~Cm thick Melinex~ foil without, however, covering functional areas.
The test element obtained in this manner has a capillary channel of 15 mm length, 2 mm width and 0.1 mm height.
The channel can take up 3 ~.1 sample liquid. An area of 3 mm x 2 mm of the detection film is wetted by the sample.
Example 2 Measurement of the blood glucose concentration with the aid of the test element from example 1 The sample application side of the test element from example 1 is placed on a drop of sample liquid. The capillary of the test element automatically fills with sample within 2 s. If glucose is present in the sample a colour development is visible in the detection film after a few seconds. The end point of the reaction is reached after ca. 30 to 35 s. The colour obtained can be correlated with the glucose concentration of the sample and either evaluated visually or by reflection photometry.
Claims (10)
1. A device for withdrawing a liquid sample for analytical elements in which the sample is transported in a capillary-active channel from the sampling site to the determination site and in which the capillary-active channel is essentially formed by a carrier and a cover wherein a notch in the form of a partial groove is located in one of the surfaces forming the channel capable of capillary liquid transport on a lateral face of the device containing a sample application opening, the notch beginning at said lateral face of the device and pointing towards the capillary active channel from the sampling site so that the surface opposite to the notch is exposed.
2. A device as claimed in claim 1 further including an intermediate layer which lies between a second cover and the carrier.
3. A device as claimed in claim 1 or 2, wherein at least two notches are located next to one another.
4. A device as claimed in claim 1, 2 or 3 wherein notches are staggered on opposite sides.
5. A device as claimed in any one of claims 1 to 4, wherein at least one of the surfaces forming the inner surface of the channel capable of capillary liquid transport is hydrophilized.
6. A device as claimed in claim 5, wherein the exposed surface opposite to the notch is hydrophilized.
7. A device as claimed in claim 5 or 6, wherein the hydrophilization is achieved by use of a hydrophilic material.
8. A device as claimed in claim 5 or 6, wherein the hydrophilization is achieved by coating a less hydrophilic material with a hydrophilic layer.
9. A device as claimed in claim 7 or 8, wherein a layer of oxidized aluminium is used for the hydrophilization.
10. A process for withdrawing a liquid sample into an analytical element with the aid of a device as claimed in any one of claims 1 to 9, wherein the liquid sample is contacted with the analytical element at the edge of the sample application opening broken by the notch and transported by capillary forces into the channel capable of capillary liquid transport.
Applications Claiming Priority (3)
| Application Number | Priority Date | Filing Date | Title |
|---|---|---|---|
| DE19753850.9 | 1997-12-04 | ||
| DE19753850A DE19753850A1 (en) | 1997-12-04 | 1997-12-04 | Sampling device |
| PCT/EP1998/007854 WO1999029428A1 (en) | 1997-12-04 | 1998-12-03 | Capillary active test element having an intermediate layer situated between the support and the covering |
Publications (2)
| Publication Number | Publication Date |
|---|---|
| CA2310762A1 CA2310762A1 (en) | 1999-06-17 |
| CA2310762C true CA2310762C (en) | 2007-02-13 |
Family
ID=7850758
Family Applications (1)
| Application Number | Title | Priority Date | Filing Date |
|---|---|---|---|
| CA002310762A Expired - Lifetime CA2310762C (en) | 1997-12-04 | 1998-12-03 | Capillary active test element having an intermediate layer situated between the support and the covering |
Country Status (15)
| Country | Link |
|---|---|
| US (2) | US7238534B1 (en) |
| EP (1) | EP1035920B1 (en) |
| JP (1) | JP3418173B2 (en) |
| KR (1) | KR20010032723A (en) |
| CN (1) | CN1115198C (en) |
| AT (1) | ATE220953T1 (en) |
| AU (1) | AU742823B2 (en) |
| CA (1) | CA2310762C (en) |
| DE (2) | DE19753850A1 (en) |
| ES (1) | ES2180229T3 (en) |
| HK (1) | HK1035875A1 (en) |
| HU (1) | HUP0004513A3 (en) |
| PL (1) | PL340913A1 (en) |
| TW (1) | TW396273B (en) |
| WO (1) | WO1999029428A1 (en) |
Families Citing this family (90)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| DE19753848A1 (en) * | 1997-12-04 | 1999-06-10 | Roche Diagnostics Gmbh | Modification of surfaces to increase surface tension |
| DE19753850A1 (en) * | 1997-12-04 | 1999-06-10 | Roche Diagnostics Gmbh | Sampling device |
| US6391005B1 (en) | 1998-03-30 | 2002-05-21 | Agilent Technologies, Inc. | Apparatus and method for penetration with shaft having a sensor for sensing penetration depth |
| AU771122B2 (en) † | 1999-07-07 | 2004-03-11 | 3M Innovative Properties Company | Detection article having fluid control film with capillary channels |
| US8641644B2 (en) | 2000-11-21 | 2014-02-04 | Sanofi-Aventis Deutschland Gmbh | Blood testing apparatus having a rotatable cartridge with multiple lancing elements and testing means |
| WO2002084291A1 (en) * | 2001-04-12 | 2002-10-24 | Arkray, Inc. | Specimen analyzing implement |
| US9795747B2 (en) | 2010-06-02 | 2017-10-24 | Sanofi-Aventis Deutschland Gmbh | Methods and apparatus for lancet actuation |
| DE60238119D1 (en) | 2001-06-12 | 2010-12-09 | Pelikan Technologies Inc | ELECTRIC ACTUATOR ELEMENT FOR A LANZETTE |
| US8337419B2 (en) | 2002-04-19 | 2012-12-25 | Sanofi-Aventis Deutschland Gmbh | Tissue penetration device |
| US9427532B2 (en) | 2001-06-12 | 2016-08-30 | Sanofi-Aventis Deutschland Gmbh | Tissue penetration device |
| JP4841063B2 (en) * | 2001-06-12 | 2011-12-21 | テクノクオーツ株式会社 | Microchannel structure and manufacturing method thereof |
| US9226699B2 (en) | 2002-04-19 | 2016-01-05 | Sanofi-Aventis Deutschland Gmbh | Body fluid sampling module with a continuous compression tissue interface surface |
| US7316700B2 (en) | 2001-06-12 | 2008-01-08 | Pelikan Technologies, Inc. | Self optimizing lancing device with adaptation means to temporal variations in cutaneous properties |
| US7749174B2 (en) | 2001-06-12 | 2010-07-06 | Pelikan Technologies, Inc. | Method and apparatus for lancet launching device intergrated onto a blood-sampling cartridge |
| US7025774B2 (en) | 2001-06-12 | 2006-04-11 | Pelikan Technologies, Inc. | Tissue penetration device |
| US7981056B2 (en) | 2002-04-19 | 2011-07-19 | Pelikan Technologies, Inc. | Methods and apparatus for lancet actuation |
| EP2290358B1 (en) * | 2001-07-27 | 2015-11-11 | ARKRAY, Inc. | Analyzing instrument |
| ATE519420T1 (en) * | 2001-09-11 | 2011-08-15 | Arkray Inc | INSTRUMENT FOR MEASURING A CONCENTRATION OF A COMPONENT IN A LIQUID SAMPLE |
| US7331931B2 (en) | 2002-04-19 | 2008-02-19 | Pelikan Technologies, Inc. | Method and apparatus for penetrating tissue |
| US8221334B2 (en) | 2002-04-19 | 2012-07-17 | Sanofi-Aventis Deutschland Gmbh | Method and apparatus for penetrating tissue |
| US9795334B2 (en) | 2002-04-19 | 2017-10-24 | Sanofi-Aventis Deutschland Gmbh | Method and apparatus for penetrating tissue |
| US8372016B2 (en) | 2002-04-19 | 2013-02-12 | Sanofi-Aventis Deutschland Gmbh | Method and apparatus for body fluid sampling and analyte sensing |
| US9248267B2 (en) | 2002-04-19 | 2016-02-02 | Sanofi-Aventis Deustchland Gmbh | Tissue penetration device |
| US7909778B2 (en) | 2002-04-19 | 2011-03-22 | Pelikan Technologies, Inc. | Method and apparatus for penetrating tissue |
| US7713214B2 (en) | 2002-04-19 | 2010-05-11 | Pelikan Technologies, Inc. | Method and apparatus for a multi-use body fluid sampling device with optical analyte sensing |
| US7232451B2 (en) | 2002-04-19 | 2007-06-19 | Pelikan Technologies, Inc. | Method and apparatus for penetrating tissue |
| US7547287B2 (en) | 2002-04-19 | 2009-06-16 | Pelikan Technologies, Inc. | Method and apparatus for penetrating tissue |
| US8360992B2 (en) | 2002-04-19 | 2013-01-29 | Sanofi-Aventis Deutschland Gmbh | Method and apparatus for penetrating tissue |
| US7976476B2 (en) | 2002-04-19 | 2011-07-12 | Pelikan Technologies, Inc. | Device and method for variable speed lancet |
| US8784335B2 (en) | 2002-04-19 | 2014-07-22 | Sanofi-Aventis Deutschland Gmbh | Body fluid sampling device with a capacitive sensor |
| US7491178B2 (en) | 2002-04-19 | 2009-02-17 | Pelikan Technologies, Inc. | Method and apparatus for penetrating tissue |
| US7901362B2 (en) | 2002-04-19 | 2011-03-08 | Pelikan Technologies, Inc. | Method and apparatus for penetrating tissue |
| US9314194B2 (en) | 2002-04-19 | 2016-04-19 | Sanofi-Aventis Deutschland Gmbh | Tissue penetration device |
| US7175642B2 (en) | 2002-04-19 | 2007-02-13 | Pelikan Technologies, Inc. | Methods and apparatus for lancet actuation |
| US7892183B2 (en) | 2002-04-19 | 2011-02-22 | Pelikan Technologies, Inc. | Method and apparatus for body fluid sampling and analyte sensing |
| US8267870B2 (en) | 2002-04-19 | 2012-09-18 | Sanofi-Aventis Deutschland Gmbh | Method and apparatus for body fluid sampling with hybrid actuation |
| US8702624B2 (en) | 2006-09-29 | 2014-04-22 | Sanofi-Aventis Deutschland Gmbh | Analyte measurement device with a single shot actuator |
| US7674232B2 (en) | 2002-04-19 | 2010-03-09 | Pelikan Technologies, Inc. | Method and apparatus for penetrating tissue |
| US8579831B2 (en) | 2002-04-19 | 2013-11-12 | Sanofi-Aventis Deutschland Gmbh | Method and apparatus for penetrating tissue |
| US7297122B2 (en) | 2002-04-19 | 2007-11-20 | Pelikan Technologies, Inc. | Method and apparatus for penetrating tissue |
| US7229458B2 (en) | 2002-04-19 | 2007-06-12 | Pelikan Technologies, Inc. | Method and apparatus for penetrating tissue |
| DE10220296A1 (en) | 2002-05-07 | 2003-11-20 | Roche Diagnostics Gmbh | Device for sampling liquid samples |
| AUPS309002A0 (en) | 2002-06-20 | 2002-07-11 | Vision Biosystems Limited | A covertile for a substrate |
| CN1318142C (en) * | 2002-10-11 | 2007-05-30 | Zbx公司 | Diagnostic devices |
| US8574895B2 (en) | 2002-12-30 | 2013-11-05 | Sanofi-Aventis Deutschland Gmbh | Method and apparatus using optical techniques to measure analyte levels |
| JP2004333141A (en) * | 2003-04-30 | 2004-11-25 | Toppan Printing Co Ltd | Liquid reaction inspecting tool |
| US8262614B2 (en) | 2003-05-30 | 2012-09-11 | Pelikan Technologies, Inc. | Method and apparatus for fluid injection |
| US7850621B2 (en) | 2003-06-06 | 2010-12-14 | Pelikan Technologies, Inc. | Method and apparatus for body fluid sampling and analyte sensing |
| WO2006001797A1 (en) | 2004-06-14 | 2006-01-05 | Pelikan Technologies, Inc. | Low pain penetrating |
| WO2005033659A2 (en) | 2003-09-29 | 2005-04-14 | Pelikan Technologies, Inc. | Method and apparatus for an improved sample capture device |
| DE10346417A1 (en) * | 2003-10-07 | 2005-06-02 | Roche Diagnostics Gmbh | Analytical test element comprising a network for forming a capillary channel |
| EP1680014A4 (en) | 2003-10-14 | 2009-01-21 | Pelikan Technologies Inc | Method and apparatus for a variable user interface |
| US8668656B2 (en) | 2003-12-31 | 2014-03-11 | Sanofi-Aventis Deutschland Gmbh | Method and apparatus for improving fluidic flow and sample capture |
| US7822454B1 (en) | 2005-01-03 | 2010-10-26 | Pelikan Technologies, Inc. | Fluid sampling device with improved analyte detecting member configuration |
| DE102004007274A1 (en) | 2004-02-14 | 2005-09-15 | Roche Diagnostics Gmbh | Test element for a human or animal fluid sample, e.g. to test for glucose, has a sampling surface and an actuator field to pull the sample to a test field |
| DE102004009012A1 (en) * | 2004-02-25 | 2005-09-15 | Roche Diagnostics Gmbh | Test element with a capillary for transporting a liquid sample |
| DE602004011688D1 (en) * | 2004-03-05 | 2008-03-20 | Egomedical Swiss Ag | ANALYSIS TEST SYSTEM FOR DETERMINING THE CONCENTRATION OF AN ANALYTE IN A PHYSIOLOGICAL LIQUID |
| WO2006011062A2 (en) | 2004-05-20 | 2006-02-02 | Albatros Technologies Gmbh & Co. Kg | Printable hydrogel for biosensors |
| US20050266398A1 (en) * | 2004-06-01 | 2005-12-01 | Peter Lea | Method and device for rapid detection and quantitation of macro and micro matrices |
| EP1765194A4 (en) | 2004-06-03 | 2010-09-29 | Pelikan Technologies Inc | Method and apparatus for a fluid sampling device |
| US9775553B2 (en) | 2004-06-03 | 2017-10-03 | Sanofi-Aventis Deutschland Gmbh | Method and apparatus for a fluid sampling device |
| US7766845B2 (en) | 2004-06-21 | 2010-08-03 | Roche Diagnostics Operations, Inc. | Disposable lancet and lancing cap combination for increased hygiene |
| US8652831B2 (en) | 2004-12-30 | 2014-02-18 | Sanofi-Aventis Deutschland Gmbh | Method and apparatus for analyte measurement test time |
| US7846311B2 (en) | 2005-09-27 | 2010-12-07 | Abbott Diabetes Care Inc. | In vitro analyte sensor and methods of use |
| DE102006025477B4 (en) * | 2006-05-30 | 2009-01-15 | Ekf - Diagnostic Gmbh | Cuvette and process for its preparation |
| CA2666887A1 (en) * | 2006-10-18 | 2008-04-24 | Research Development Foundation | Alpha-msh therapies for treatment of autoimmune disease |
| JP4811267B2 (en) * | 2006-12-22 | 2011-11-09 | パナソニック株式会社 | Microchip and analytical device using the same |
| EP2254699A1 (en) * | 2008-03-11 | 2010-12-01 | Koninklijke Philips Electronics N.V. | Filtering apparatus for filtering a fluid |
| EP2265324B1 (en) | 2008-04-11 | 2015-01-28 | Sanofi-Aventis Deutschland GmbH | Integrated analyte measurement system |
| US9375169B2 (en) | 2009-01-30 | 2016-06-28 | Sanofi-Aventis Deutschland Gmbh | Cam drive for managing disposable penetrating member actions with a single motor and motor and control system |
| KR101110561B1 (en) * | 2009-06-04 | 2012-02-15 | 주식회사 인포피아 | biosensor |
| US9216413B2 (en) * | 2009-07-07 | 2015-12-22 | Boehringer Ingelheim Microparts Gmbh | Plasma separation reservoir |
| US8965476B2 (en) | 2010-04-16 | 2015-02-24 | Sanofi-Aventis Deutschland Gmbh | Tissue penetration device |
| US9157903B2 (en) * | 2011-02-25 | 2015-10-13 | Honeywell International Inc. | Microfluidic separation of plasma for colormetric assay |
| KR101215006B1 (en) * | 2011-08-16 | 2012-12-24 | 바디텍메드 주식회사 | Capillary microcuvette having dual sampling means |
| EP2636750A1 (en) | 2012-03-06 | 2013-09-11 | Roche Diagniostics GmbH | Compatible solute ectoine as well as derivatives thereof for enzyme stabilization |
| CN104246482B (en) | 2012-04-19 | 2017-04-12 | 霍夫曼-拉罗奇有限公司 | Method and device for determining an analyte concentration in blood |
| WO2014140164A1 (en) | 2013-03-15 | 2014-09-18 | Roche Diagnostics Gmbh | Methods of using information from recovery pulses in electrochemical analyte measurements as well as devices, apparatuses and systems incorporating the same |
| EP2972268B1 (en) | 2013-03-15 | 2017-05-24 | Roche Diabetes Care GmbH | Methods of failsafing electrochemical measurements of an analyte as well as devices, apparatuses and systems incorporating the same |
| CN105164523B (en) | 2013-03-15 | 2017-09-12 | 豪夫迈·罗氏有限公司 | Scale the method for the data for constructing biology sensor algorithm and merge the unit and system of methods described |
| WO2014140177A2 (en) | 2013-03-15 | 2014-09-18 | Roche Diagnostics Gmbh | Methods of detecting high antioxidant levels during electrochemical measurements and failsafing an analyte concentration therefrom as well as devices, apparatuses and systems incorporting the same |
| EP2994536B1 (en) | 2013-05-08 | 2017-06-14 | Roche Diabetes Care GmbH | Stabilization of enzymes by nicotinic acid |
| EP2811299A1 (en) | 2013-06-07 | 2014-12-10 | Roche Diagniostics GmbH | Test element for detecting at least one analyte in a body fluid |
| SG11201605911RA (en) | 2014-01-24 | 2016-08-30 | Hoffmann La Roche | Method of manufacturing uni- and no-code test stripes |
| EP2905618A1 (en) | 2014-02-05 | 2015-08-12 | Roche Diagnostics GmbH | Use of rare metals as key components |
| EP2927319A1 (en) | 2014-03-31 | 2015-10-07 | Roche Diagnostics GmbH | High load enzyme immobilization by crosslinking |
| RU2618845C1 (en) * | 2015-12-03 | 2017-05-11 | Общество с ограниченной ответственностью "Научно-исследовательский центр "Модифицированные полимеры" | Method of manufacture of cuvette for analysis of liquid samples with hydrophilic interior surface |
| US20180024073A1 (en) * | 2016-07-21 | 2018-01-25 | Ronald Schornstein | Reach-extended test strip |
| CN109804240A (en) | 2016-10-05 | 2019-05-24 | 豪夫迈·罗氏有限公司 | Detection reagent and electrode arrangement and its application method for multiple analyte diagnostic test element |
| US20240091779A1 (en) * | 2022-09-19 | 2024-03-21 | Parhelia Biosciences Corporation | Histological Containment System with Cover Pad |
Family Cites Families (63)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| BE754658A (en) | 1969-08-12 | 1971-02-10 | Merck Patent Gmbh | INDICATOR SHEET, CONSISTING OF AN IMPREGNATED, ABSORBENT, SHEATHED HAIR MATERIAL |
| JPS5466194A (en) * | 1977-11-04 | 1979-05-28 | Kuraray Co | Fet sensor |
| US4138216B1 (en) * | 1977-12-23 | 1997-06-17 | Info Chem Inc | Device for monitoring ethylene oxide sterilization process |
| US4250257A (en) * | 1978-08-24 | 1981-02-10 | Technicon Instruments Corporation | Whole blood analyses in porous media |
| US4254083A (en) * | 1979-07-23 | 1981-03-03 | Eastman Kodak Company | Structural configuration for transport of a liquid drop through an ingress aperture |
| CA1129498A (en) * | 1978-10-25 | 1982-08-10 | Richard L. Columbus | Structural configuration and method for transport of a liquid drop through an ingress aperture |
| DE2910134A1 (en) | 1979-03-15 | 1980-09-25 | Boehringer Mannheim Gmbh | DIAGNOSTIC AGENT FOR DETECTING COMPONENTS OF BODY LIQUIDS |
| US4323536A (en) | 1980-02-06 | 1982-04-06 | Eastman Kodak Company | Multi-analyte test device |
| JPS5731616A (en) | 1980-08-01 | 1982-02-20 | Kyowa Hakko Kogyo Co Ltd | Relaxing agent for muscle comprising benzofurancarboxylic acid amide |
| GB2090659A (en) * | 1981-01-02 | 1982-07-14 | Instrumentation Labor Inc | Analytical device |
| ES8405624A1 (en) * | 1982-05-14 | 1984-06-16 | Astra Meditec Ab | Articles exhibiting a biocompatible surface layer and process for providing articles with such a surface layer. |
| US4439526A (en) * | 1982-07-26 | 1984-03-27 | Eastman Kodak Company | Clustered ingress apertures for capillary transport devices and method of use |
| SE8305704D0 (en) | 1983-10-18 | 1983-10-18 | Leo Ab | Cuvette |
| US4900663A (en) * | 1985-09-13 | 1990-02-13 | Environmental Diagnostics, Inc. | Test kit for determining the presence of organic materials and method of utilizing same |
| CA1271399A (en) * | 1986-04-08 | 1990-07-10 | William G. Meathrel | Ethylene oxide monitoring device |
| DE3711418A1 (en) | 1987-04-04 | 1988-10-20 | Agfa Gevaert Ag | COLOR PHOTOGRAPHIC RECORDING MATERIAL WITH A COUPLER RELEASING A PHOTOGRAPHICALLY EFFECTIVE CONNECTION |
| US5006474A (en) * | 1987-12-16 | 1991-04-09 | Disease Detection International Inc. | Bi-directional lateral chromatographic test device |
| US5126247A (en) | 1988-02-26 | 1992-06-30 | Enzymatics, Inc. | Method, system and devices for the assay and detection of biochemical molecules |
| DE3814370A1 (en) * | 1988-04-28 | 1989-11-09 | Boehringer Mannheim Gmbh | TEST PROVIDER FOR THE ANALYSIS OF A SAMPLING FLUID, METHOD FOR CARRYING OUT SUCH ANALYSIS AND METHOD OF PRODUCTION |
| US4933092A (en) | 1989-04-07 | 1990-06-12 | Abbott Laboratories | Methods and devices for the separation of plasma or serum from whole blood |
| US4952373A (en) * | 1989-04-21 | 1990-08-28 | Biotrack, Inc. | Liquid shield for cartridge |
| GB8911462D0 (en) * | 1989-05-18 | 1989-07-05 | Ares Serono Res & Dev Ltd | Devices for use in chemical test procedures |
| US4943415A (en) * | 1989-07-14 | 1990-07-24 | Eastman Kodak Company | Grooved cover for test elements |
| US5100627A (en) * | 1989-11-30 | 1992-03-31 | The Regents Of The University Of California | Chamber for the optical manipulation of microscopic particles |
| GB9002856D0 (en) | 1990-02-08 | 1990-04-04 | Alcan Int Ltd | Fluid detection device |
| US5147606A (en) * | 1990-08-06 | 1992-09-15 | Miles Inc. | Self-metering fluid analysis device |
| US5208163A (en) * | 1990-08-06 | 1993-05-04 | Miles Inc. | Self-metering fluid analysis device |
| US5173433A (en) * | 1990-10-11 | 1992-12-22 | Toxi-Lab Incorporated | Method for chemical analysis |
| US5271895A (en) * | 1991-02-27 | 1993-12-21 | Boehringer Mannheim Corporation | Test strip |
| US5264103A (en) * | 1991-10-18 | 1993-11-23 | Matsushita Electric Industrial Co., Ltd. | Biosensor and a method for measuring a concentration of a substrate in a sample |
| US6017696A (en) * | 1993-11-01 | 2000-01-25 | Nanogen, Inc. | Methods for electronic stringency control for molecular biological analysis and diagnostics |
| JP3382632B2 (en) * | 1992-03-13 | 2003-03-04 | オリンパス光学工業株式会社 | Method for measuring biological substance and reaction vessel used for the method |
| US5308775A (en) * | 1992-09-15 | 1994-05-03 | Abbott Laboratories | Assay devices for concurrently detecting an analyte and confirming the test result |
| FR2701117B1 (en) * | 1993-02-04 | 1995-03-10 | Asulab Sa | Electrochemical measurement system with multizone sensor, and its application to glucose measurement. |
| CA2158162A1 (en) * | 1993-03-17 | 1994-09-29 | Juan Pedro De Zoeten | Apparatus for the detection of a specifically reacting substance |
| US5843691A (en) | 1993-05-15 | 1998-12-01 | Lifescan, Inc. | Visually-readable reagent test strip |
| US5405511A (en) * | 1993-06-08 | 1995-04-11 | Boehringer Mannheim Corporation | Biosensing meter with ambient temperature estimation method and system |
| DE4427363A1 (en) * | 1993-08-03 | 1995-03-09 | A & D Co Ltd | A disposable chemical sensor |
| US5384030A (en) * | 1994-02-15 | 1995-01-24 | General Motors Corporation | Exhaust sensor including a composite tile sensing element and methods of making the same |
| US5762770A (en) * | 1994-02-21 | 1998-06-09 | Boehringer Mannheim Corporation | Electrochemical biosensor test strip |
| US5437999A (en) * | 1994-02-22 | 1995-08-01 | Boehringer Mannheim Corporation | Electrochemical sensor |
| JP3027306B2 (en) * | 1994-06-02 | 2000-04-04 | 松下電器産業株式会社 | Biosensor and manufacturing method thereof |
| CA2215346C (en) | 1995-03-14 | 2003-05-27 | Howard Milne Chandler | Sample collection device |
| DE19523049A1 (en) * | 1995-06-24 | 1997-01-02 | Boehringer Mannheim Gmbh | Multilayer analysis element for the determination of an analyte in a liquid |
| US6174420B1 (en) | 1996-11-15 | 2001-01-16 | Usf Filtration And Separations Group, Inc. | Electrochemical cell |
| AUPN661995A0 (en) | 1995-11-16 | 1995-12-07 | Memtec America Corporation | Electrochemical cell 2 |
| US5962215A (en) * | 1996-04-05 | 1999-10-05 | Mercury Diagnostics, Inc. | Methods for testing the concentration of an analyte in a body fluid |
| DE19629654A1 (en) | 1996-07-23 | 1998-05-07 | Boehringer Mannheim Gmbh | Diagnostic test carrier with capillary gap |
| DE19629655A1 (en) | 1996-07-23 | 1998-01-29 | Boehringer Mannheim Gmbh | Diagnostic test carrier and method for determining an analyte with the aid thereof |
| DE19629657A1 (en) | 1996-07-23 | 1998-01-29 | Boehringer Mannheim Gmbh | Volume-independent diagnostic test carrier and method for determining analyte with its aid |
| DE19629656A1 (en) | 1996-07-23 | 1998-01-29 | Boehringer Mannheim Gmbh | Diagnostic test carrier with multilayer test field and method for the determination of analyte with its aid |
| US6194220B1 (en) * | 1996-09-25 | 2001-02-27 | Becton, Dickinson And Company | Non-instrumented assay with quantitative and qualitative results |
| US5714123A (en) * | 1996-09-30 | 1998-02-03 | Lifescan, Inc. | Protective shield for a blood glucose strip |
| WO1998022625A1 (en) | 1996-11-20 | 1998-05-28 | The Regents Of The University Of Michigan | Microfabricated isothermal nucleic acid amplification devices and methods |
| JP3739537B2 (en) * | 1997-03-26 | 2006-01-25 | 大日本印刷株式会社 | Measuring chip for optical analyzer |
| US5759364A (en) * | 1997-05-02 | 1998-06-02 | Bayer Corporation | Electrochemical biosensor |
| JP3498201B2 (en) * | 1997-08-27 | 2004-02-16 | アークレイ株式会社 | Vacuum generator and sample analyzer using the same |
| DE19753851A1 (en) * | 1997-12-04 | 1999-06-10 | Roche Diagnostics Gmbh | Capillary liquid transport device |
| DE19753847A1 (en) * | 1997-12-04 | 1999-06-10 | Roche Diagnostics Gmbh | Analytical test element with capillary channel |
| DE19753850A1 (en) * | 1997-12-04 | 1999-06-10 | Roche Diagnostics Gmbh | Sampling device |
| DE19753849A1 (en) | 1997-12-04 | 1999-06-10 | Roche Diagnostics Gmbh | Analytical test element with a tapered capillary channel |
| US5997817A (en) * | 1997-12-05 | 1999-12-07 | Roche Diagnostics Corporation | Electrochemical biosensor test strip |
| DE19815684A1 (en) * | 1998-04-08 | 1999-10-14 | Roche Diagnostics Gmbh | Process for the preparation of analytical aids |
-
1997
- 1997-12-04 DE DE19753850A patent/DE19753850A1/en not_active Withdrawn
-
1998
- 1998-12-03 JP JP2000524077A patent/JP3418173B2/en not_active Expired - Lifetime
- 1998-12-03 PL PL98340913A patent/PL340913A1/en unknown
- 1998-12-03 AT AT98965748T patent/ATE220953T1/en not_active IP Right Cessation
- 1998-12-03 DE DE59804930T patent/DE59804930D1/en not_active Expired - Lifetime
- 1998-12-03 KR KR1020007006012A patent/KR20010032723A/en not_active Application Discontinuation
- 1998-12-03 WO PCT/EP1998/007854 patent/WO1999029428A1/en not_active Application Discontinuation
- 1998-12-03 EP EP98965748A patent/EP1035920B1/en not_active Expired - Lifetime
- 1998-12-03 CA CA002310762A patent/CA2310762C/en not_active Expired - Lifetime
- 1998-12-03 CN CN98813487A patent/CN1115198C/en not_active Expired - Lifetime
- 1998-12-03 AU AU21576/99A patent/AU742823B2/en not_active Ceased
- 1998-12-03 HU HU0004513A patent/HUP0004513A3/en unknown
- 1998-12-03 US US09/554,793 patent/US7238534B1/en not_active Expired - Fee Related
- 1998-12-03 ES ES98965748T patent/ES2180229T3/en not_active Expired - Lifetime
- 1998-12-04 TW TW087120207A patent/TW396273B/en not_active IP Right Cessation
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2001
- 2001-09-19 HK HK01106620A patent/HK1035875A1/en not_active IP Right Cessation
-
2007
- 2007-05-29 US US11/807,548 patent/US7799578B2/en not_active Expired - Fee Related
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| HUP0004513A3 (en) | 2001-05-28 |
| HUP0004513A2 (en) | 2001-04-28 |
| PL340913A1 (en) | 2001-03-12 |
| US20070266803A1 (en) | 2007-11-22 |
| DE19753850A1 (en) | 1999-06-10 |
| JP2001525553A (en) | 2001-12-11 |
| CA2310762A1 (en) | 1999-06-17 |
| JP3418173B2 (en) | 2003-06-16 |
| US7799578B2 (en) | 2010-09-21 |
| AU2157699A (en) | 1999-06-28 |
| CN1290195A (en) | 2001-04-04 |
| ES2180229T3 (en) | 2003-02-01 |
| EP1035920B1 (en) | 2002-07-24 |
| US7238534B1 (en) | 2007-07-03 |
| EP1035920A1 (en) | 2000-09-20 |
| AU742823B2 (en) | 2002-01-10 |
| CN1115198C (en) | 2003-07-23 |
| HK1035875A1 (en) | 2001-12-14 |
| WO1999029428A1 (en) | 1999-06-17 |
| ATE220953T1 (en) | 2002-08-15 |
| TW396273B (en) | 2000-07-01 |
| KR20010032723A (en) | 2001-04-25 |
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