the disposable diagnostic parts 10 shown in the drawing can be used as microfluidic sample collectors or microsamplers for a blood sugar determination in a hand - held device 12 designed therefor , where it is possible to carry out a glucose detection with a minimal amount of sample in the disposable part . for this purpose the microsamplers 10 comprise a lancing element 14 with a slot - shaped collecting channel 16 which is open on both sides and a detection element 18 disposed therein for an optical or electrochemical measurement directly in the collecting channel 16 , where the detection element 18 and optionally also the lancing element 14 is provided with a special coating 20 made of non - ionic surfactants . a holder 22 for the lancing element and the detection element allows coupling to a lancing drive 24 for a puncture into the skin 26 for example of a finger of a user . as shown in fig1 the microsamplers 10 can be brought successively into an active application position in a magazine 28 which can be inserted into the instrument 12 . in this connection the tip 30 of the active lancing element 14 points in a distal direction towards the body part 26 while a coupling end 32 of the holder 22 is coupled with the lancing drive 24 for a drive coupling and signal coupling . the body fluid ( blood or tissue fluid ) taken up during the skin puncture in the collecting channel 16 can be analysed directly photometrically or electrochemically by means of the detection element 18 where the signals are evaluated in an evaluation unit 34 in the instrument . in this connection it is also possible to indicate the result of the measurement to the user on a display 36 thus enabling an on - site blood sugar monitoring without complicated handling steps . as shown in fig2 the shaft - shaped elongate lancing element 14 has a transverse continuous longitudinal slot as a collecting channel 16 . this slot enables , optionally by means of capillary action , the transfer of a microscopic amount of liquid onto the detection element 18 which is aligned in the direction of the tip 30 . the elongate slit opening that is open on both sides ensures an effective uptake of liquid without the risk of blockage by cell components . in order to withdraw blood in the gentlest possible manner with as little pain as possible it is provided that the volume of the collecting channel 16 is only a few tens of nanoliters . in the side view of fig3 it can be seen that the proximal end of the lancing element 14 is plugged onto the holder 22 provided with lateral grooves in a clamp - like manner so that the detection element 18 which is applied to the end of the holder 22 engages in the collecting channel 16 . the distal section of the lancing element 14 made of steel is ground such that it slopes towards the tip 30 in order to facilitate the skin puncture by a reduced cross - section . fig4 shows the detection element 18 composed of several layers in an enlarged section . a transparent support 38 is provided as a base which rests on an arrangement of light guides 40 which cross the holder 22 . a test layer 42 is located on the support 38 and is provided with reagents for a glucose detection in the blood fluid collected in the collecting channel 16 and optionally further auxiliary substances . the reagents can consist of a known enzymatic system which reacts irreversibly with glucose with a colour change but do not dissolve in the blood fluid . an optical detection by the instrument is enabled by means of scattering particles within the chemistry system with back - scattering of the measuring light that is radiated in via the arrangement of light guides 40 . the sealing layer 20 covers the test layer 42 and thus seals the reagents so that firstly a good storage stability is achieved and reagent particles are prevented from detaching from the dry - stored test surface . the sealing also results in an important user advantage in that it prevents direct skin contact with the test surface or with substances that are detached therefrom during the puncture . the sealing layer 20 also advantageously encloses the margins of the test area 42 in order to reliably prevent a detachment of particles . this is particularly important when the detection element 18 is made by cutting it from a large area of coated foil material . in order to not significantly impair the detection of the analyte , the sealing layer 20 is dissolvable when blood fluid which flows into the collection channel 16 is applied thereto . the time required for an adequate dissolution i . e . the time until a measurement signal that can be analysed is obtained should be less than 2 seconds in order not to limit the user convenience . accordingly the sealing layer 20 should have a high hydrophilicity where a liquid film design is advantageous . it goes without saying that the sealing layer 20 should be biocompatible so that it does not itself trigger disadvantageous reactions upon skin contact . this can be achieved in a particularly reliable manner by using pharmacologically approved harmless substances as well as harmless substances that are approved for food chemistry as a coating material . however , such substances should not have independent pharmacological functional properties within the scope of the pharmacological registration . finally the coating material should not have an effect on the test reagents and the test process and thus on the result , regardless of whether a contact with the test surface takes place during production , storage or not until sample measurement . ideally an existing test chemistry should not only be compatible with regard to the coating material but should also advantageously itself contain this material as the test area 42 . thus , the test area 42 can contain that substance which is also used as a sealing material , as a wetting agent which is in any case required . in this manner critical concentration gradients or disadvantageous changes in the overall system are avoided . a coating 20 ′ of the lancing element 14 can also prove to be advantageous in order to create a hydrophilic surface for the uptake of body fluid especially in the area of the collecting channel 16 . it is also possible to reduce the friction during lancing and thus the lancing pain by means of a coating in the area of the tip 30 . in this connection non - ionic surfactants and above all polysorbates have proven to be a particularly suitable coating material for fulfilling the aforementioned requirements and enabling a mass production of disposable articles in a practical manner . polysorbate 20 ( ps 20 ) which has the following advantages is particularly preferably used : ps 20 is used in pharmaceutical preparations ( injection solutions ) and is also found in foods . ps 20 can be stored for a long period and is still active even long after the expiry date . ps 20 has a high molecular weight and thus hardly diffuses through body tissue . ps 20 is viscous at room temperature and dissolves well in the solvent ethanol ( and not only in water ). ps 20 is sterile in the solvent ethanol , does not become contaminated with microorganisms and wetted areas are sterilized by the solvent . ps 20 can be easily applied in an ethanolic solution and rapidly and readily penetrates into capillary structures due to the low solvent viscosity . ps 20 applied from ethanol can be rapidly and reliably freed from ethanol ( e . g . by a stream of air or a vacuum ). ps 20 does not form a crystal lattice and consequently rapidly dissolves on contact with the water of the sample ( blood ) because a high enthalpy of solution is not required to overcome lattice forces . a rapid interaction with the sample also leads to a rapid wetting . ps 20 also creeps ( depending on the amount ) into the finest structures after drying . the hydrophilicity and wetting rate appears to become even better and not poorer after some storage time . ps 20 did not exhibit a detectable effect on the detection reaction in the initial experiments . ps 20 should inhibit coagulation to a slight extent but not in a functional manner ( and indeed only in the collecting channel , whereas outside the channel the dilution is too high ). the consistency or viscosity of ps 20 can , if necessary , be optimized by adding other components . for example an addition of poloxamer 188 ( solid ) can suitably modify the creep capability of ps 20 . polysorbate 80 has also proven to be a suitable coating material . the following detergents are further conceivable classes of substances which , although being foreign to the body , are nevertheless used in food chemistry and biochemistry or molecular biology : aeos : fatty alcohol polyglycol ethers ch3 —( ch2 ) 16 — ch2 —( och2ch2 ) n — oh n = 1 - 20 glucamides , derived from fatty acids and glucose r — co — nh — ch2 —( ch2 ) 4 — ch2 — oh r ═ c11h23 fatty alcohol ethoxylates apgs ( alkyl - polyglycosides ) polyglycosil - o —( ch2 ) n — ch3 n = e . g . 12 sucrose fatty esters ( sucrose : glucose - c6 )- o — co —( ch2 ) n — ch3 n = 10 - 16 of course combinations of these substances with one another or with other substances are conceivable . hence , when producing disposable diagnostic articles 10 it is advantageous that the lancing element 14 and / or the detection element 18 is at least partially coated with non - ionic surfactants as a coating material . this can be achieved by applying the coating material to the surface to be coated by dip coating , spray coating or contact coating . the coating material is advantageously applied to the surface to be coated in ethanol as a solvent and subsequently the solvent is removed for example by a stream of gas , a vacuum and / or heating . the detection element 18 as a cut - out piece of flat material can be attached after coating to the support 22 i . e . with its front end on the light guide 40 and subsequently the assembly unit consisting of support 22 and detection element 18 are assembled with the lancing element 14 . further details on this are given by the patent application pct / us07 / 65918 to which reference is expressly made in this connection .
the invention concerns a disposable diagnostic part comprising a lancing element which is designed for puncturing the skin and has a collecting channel for taking up body fluid , and comprising a detection element which has a test layer provided with reagents for the detection of an analyte in the body fluid and is disposed in the collecting channel . in order to ensure an improved stability and biocompatibility it is proposed that the detection element is provided with a sealing layer that is applied to the test layer and covers the reagents .