Mobile device for analyzing a fluid, especially cerebrospinal fluid

Abstract

Device (1) adapted for measuring and / or influencing a property of a body fluid (95), in particular cerebrospinal fluid, provided in a fluidic module of the device, the device comprising the fluidic module (40), a reusable base part (10), adapted or configured to receive the fluidic module on or in the base part, an interface (5, 51), in particular designed as a connecting hose (5) or a hose coupling (8), adapted for connecting the device to a body fluid source (2), in particular a patient, wherein the body fluid source comprises a body fluid, such that the body fluid can be guided into the fluidic module by means of the interface, a microfluidic chip (60) arranged on or in the fluidic module adapted to influence the property of the body fluid.

Description

Field of the InventionThe present invention relates to a device by means of which a property of a body fluid can be measured and / or influenced. Furthermore, the present invention also relates to a fluidic module for such a device and to a microfluidic chip which is particularly suitable for the aforementioned device.BACKGROUND AND GENERAL DESCRIPTION OF THE INVENTIONThe starting point of the present technical development is the problem that certain analyses and diagnoses are still only accessible by laboratory investigations. Although a point-of-care diagnosis, also called in-situ diagnosis, would be desirable, it has not been possible to realize this up to now. The delays occurring due to laboratory transport of the sample(s) can be the basis for severe complications.Thus, delayed cerebral ischemia (DCI) occurs in up to one third of patients with subarachnoid aneurysm (aSAH). Untreated, it may lead to secondary cerebral infarctions and is often associated with death or severe disability. Free hemoglobin (fHb) and its derivatives in the cerebrospinal fluid (liquor; CSF cerebrospinal fluid) are the major cause of DCI in patients with aneurysmal subarachnoid hemorrhage. After an aneurysm is ruptured, erythrocytes in the subarachnoid space lyse and release free hemoglobin (Hb), which plays a key role in the development of DCI. Patients with corresponding symptoms are generally provided with intensive care. Furthermore, a ventricular or lumbal drainage is typically set, so that, in principle, liquor is already available for fHb quantification in the environment of such a patient.ASAH occurs worldwide with an incidence of 8 per 100,000 people years and is associated with an exceptionally high disease-specific burden on mortality and long-term impairment. aSAH is due to the rupture of an aneurysm which leads to bleeding into the liquor (CSF)-filled subarachnoid space. Brain damage in an aSAH occurs in two phases. Early brain damage is caused by the increasing intracranial pressure, decreased cerebral blood flow, transient global ischemia, and the early toxic effects of subarachnoid blood. Unique to aSAH, in one third of patients 3 to 14 days after the first bleeding, a delayed phase follows brain damage from delayed cerebral ischemia (DCI). DCI leads to secondary infarctions and is the most important cause of long term impairment in patients who have survived the first bleeding, or may result in death. After erythrocytolysis in the subarachnoid liquor space, cell-free hemoglobin (liquor-Hb) can be detected spectrophotometrically as oxygenated hemoglobin (oxyHb) and contributes significantly to the development of DCI. Previously, it was found that liquor-Hb severely interferes with vascular nitric oxide signaling in isolated cerebral arteries. OxyHb infused into the liquor of sheep induces highly reproducible acute vasospasm.Acute hydroencephalus occurs in 20% of patients with aSAH and is treated with liquor lead (external ventricular drain or lumbar drain) in the acute phase. The liquor is regularly drained, collected in measuring vessels and normally discarded. This offers the unique possibility of performing regular liquor analyses in aSAH patients without additional invasive methods, since the liquor is already present in measurement containers and is thus directly accessible for a measurement, even without the patient possibly having to be connected directly.Continuous bedside measurement of free liquor Hb in aSAH can allow the patient-specific time profile of erythrocytolysis in subarachnoid space to be determined and the risk of DCI to be monitored at any time of the disease. Moreover, these measurements can guide new therapeutic measures for reducing liquor Hb toxicity in aSAH patients. However, repeated Liquor spectrophotometer to monitor Liquor Hb levels in patients after aSAH is reserved for highly specialized sites and there is no system for point-of-care therapy (POCT) diagnostic assays. Today, liquor must be removed from the external ventricular drains and analyzed in special laboratories in a manual two-stage method, namely with the aid of a stationary laboratory centrifuge and corresponding trained and trained professionals, in order to exclude intact erythrocytes. The hemoglobin in the liquor (liquor-Hb) is analyzed in a conventional manner in a two-step method, which consists of centrifugation to exclude intact erythrocytes and subsequent spectrophotometric quantification. This approach has the disadvantage of in vitro hemolysis if the sample is not processed immediately, if erythrocytes release their hemoglobin prior to centrifugation, and if additional hemolysis occurs during centrifugation, resulting in inaccurately high readings for cell-free Hb. Such an effect can be attenuated by a POCT system, since the samples can be processed without delay.This likewise leads to several problems which are currently unsolved in practice. First, this limits the number of possible tests that can be performed. Second, the time difference between sampling and measurement increases the variability of the results. And third, this procedure, which also requires the laboratory to end the sample, lowers the accuracy of the measurement results.The invention proposed hereinafter solves the aforementioned problems. It can be used as a point-of-care device, in principle on the bed side on the patient for monitoring fAbs in the liquor. Alternatively, at least in the vicinity of the patient or in a diagnostic environment in clinic. It is capable of measuring the concentration of fRb and its derivatives and / or blood cells and blood serum proteins in an amount of liquor provided. This allows monitoring the risk of a DCI in the patient and allows earlier and reliable detection and treatment of DCI at the intensive care unit.In another aspect, in which the present invention provides improvements over the prior art, the present invention may be used to supplement existing methods. Thus, lumbar puncture (LP) is initially used for the diagnosis of subarachnoid hemorrhage if imaging methods such as computed tomography are not meaningful and / or not available. As in the case described above, a liquid sample obtained can be sent to a specialized laboratory for the analysis of the concentration of fRb and its derivatives, up to now. The laboratory also performs a two-stage manual analysis in this case. This in turn entails the aforementioned problems of the time difference between sampling and measurement (second) and a lower measurement accuracy (third).This is made more difficult, in particular in this case, namely in unfavourable, but not unusual circumstances, the large time difference from the LP to the diagnosis can be built up: the opening or acceptance times of the laboratory, which are generally not open at all on the weekend, the required processing time and the times for the sample shipping-in particular in rural areas. All these points increase the time until diagnosis and treatment, which in the meantime increases the risk for the patient.The device explained with the present description and usable as a point-of-care device can be used in particular for measuring the concentration of fRb and its derivatives and / or blood cells and / or blood serum proteins in liquor samples. It solves the aforementioned problems by replacing the laboratory process with automated, standardized (i.e., repeatable) and rapid measurement. This facilitates the diagnosis of subarachnoid hemorrhage as a life-threatening emergency in the acute stage.In addition, the device enables the detection and quantification of leukocytes in the liquor sample. This may be important, for example, for the diagnosis of infections and inflammations of the central nervous system, such as meningitis. The number and type of leukocytes can provide valuable diagnostic information and contribute to the more comprehensive assessment of patient condition.At present, the aforementioned problems cannot be addressed because there is no diagnostic point-of-care test system at present that could allow continuous and standardized testing.Thus, with current methods, liquor is removed from the external ventricular or lumbar drainage and sent to a specialized laboratory for measuring the fHb concentration. In the laboratory, the sample is first centrifuged to exclude intact erythrocytes and then the fKb in the supernatant is determined spectrophotometrically.This method is time consuming, provides only discontinuous, snapshot-like measurements, and has multiple sources of variance. If the sample is not processed immediately, in vitro hemolysis may occur. The erythrocytes release their hemoglobin before and possibly also during centrifugation, which leads to incorrectly high measurement values for fHb. The manual processing and different processing times result in additional uncertainties. In remote areas or outside the working times (weekend), laboratory analysis may not be possible at all.These problems are alleviated by the described point-of-care system with standardized and immediate sample processing. In addition, by means of adjustable and possibly shorter measurement intervals, the diagnostic value of the measurement results obtainable with the device can be greatly increased.The monitoring system explained in the present description can enable a nearly continuous and noninvasive quantification of fAbs, derivatives, blood cells and / or blood serum proteins in the liquor. It can be ensured that the liquor drainage system can optionally remain permanently connected. Furthermore, the device explained here makes it possible that conventional centrifugation of the sample is no longer necessary. In comparison with the daily liquor extraction with manual handling of the liquor sample as usual hitherto and the analysis thereof in a special laboratory, improved user-friendliness, significantly simplified handling and thus lower susceptibility to errors and reproducibility is obtained. By direct display on the device, it can be immediately recognized whether the sampling has expired or has expired correctly and is still being taken promptly if difficulties have occurred in the sampling. Until now, failed sampling (or sample degradation during transport or centrifugation, see above) could not be detected until the laboratory outcome returns. Finally, direct display of the primary DCI biomarker to the physician allows for early detection and treatment of DCI as well as primary diagnosis of Subarachnoidalblutungen. In other words, the device presented here enables the physician, when using the device, to independently and in particular promptly produce a corresponding finding without relying on results by a special laboratory.It is therefore an object of the present invention to provide an apparatus and a method which eliminate or improve the aforementioned disadvantages.The object is achieved by the subject matter of the independent claims. Dependent claims form further developments of the invention.The present description describes a device which is designed to measure and / or influence a property of a body fluid provided in a fluidic module of the device. The body fluid is in particular liquor. The property is, for example, the presence of foreign bodies or foreign bodies in the body fluid. In the case of liquor as body fluid, foreign bodies or foreign bodies are those constituents which should not be present in the liquor or should be present only in very small amounts, that is to say in particular blood cells such as, for example, leukocytes, erythrocytes and / or hemoglobin.The device is particularly advantageously configured such that it can be used directly on the patient in order to enable POCT analysis or in situ analysis of the body fluid. This means that the sample does not have to be transported to a laboratory center, but the analysis can take place directly at the patient, directly in the POCT environment or directly in the clinic. In particular, the device is designed in such a way that it can determine an analysis result independently or almost independently, so that the state of the body fluid can be evaluated in clinic.This has an at least two-part construction. At least the fluidic module and a base part for receiving the fluidic module are provided on or in the device. The base part can accommodate those components that are regularly and permanently reusable, such as control and electronic components. Thus, sensors, a pump, the power supply and data interfaces such as a radio module can be accommodated in the base part. In other words, it may be attempted to arrange those components which do not come into contact with the fluid to be measured or changed-and are thus not contaminated-in the base part. Those components which come into contact with the fluid are all arranged, for example, in the fluidic module. In the case of a reusable fluidic module, therefore, only the fluidic module is to be cleaned, but not the base part. In the case of the fluidic module being designed as a disposable module, the same can be disposed of. In both cases, the base part can be ready for receiving a fresh, i.e. cleaned or new, fluidic module. The components in the base part, which are particularly expensive, can be used further and more.The fluidic module can be designed as a disposable module. Disposable module means that the fluidic module, after use, is no longer usable in the POCT area or the clinical environment, but is to be disposed of or recycled.The disposable module is then likewise configured in such a way that those components are accommodated there which come into contact with the body fluid or could otherwise be contaminated. The fluidic module is disposed of after a single use, so that a complicated cleaning and recycling of the fluidic module is not necessary in this case. Since this is a relatively cost-intensive process in a clinical environment, a higher basic price can be justified by only simple use of the fluidic module as a disposable module, since measurement components are then also optionally disposed of after only one use. On the other hand, the fluidic module can be designed such that certain components to be arranged there are easily accessible, in particular components which, although they are to be arranged in the fluidic module for measurement reasons, do not actually come into contact with the body fluid. The fluidic module can then be set up in such a way that these components are pulled out of the fluidic module after use, for example, and are fed to a reprocessing (for example, a function control). Finally, it may also prove to be advantageous if the fluidic module, after use has been completed, is indeed supplied to a receiving container provided for this purpose, but the fluidic module or modules can subsequently be supplied to a reprocessing process after an incoming test and cleaning process. The complete reuse is to be evaluated, for example, according to economic scales, so that if further developments result in this area (or the material costs should increase in such a way in relation to lobby costs), it is not excluded that a single-use module can also be supplied to a new use after reprocessing has taken place. In this case, it can nevertheless be described as a disposable module, since after use it cannot be used again at first, in contrast to the basic module, which after replacement of the fluidic module can be used again directly for the next measurement or series of measurements. The fluidic module can thus be disposed of either after a single or multiple use depending on the application, or reused after appropriate cleaning and processing. During reuse, suitable sterilization methods can ensure that no cross-contamination occurs between different patients.The device may be configured to include an interface, such as a connection hose and / or a hose coupling, configured to connect the device to a body fluid source.In one example, the body fluid source is the patient to be treated or diagnosed. In this case, the connection to the body fluid source is advantageously established with a connecting hose.In another case, the body fluid source may be an external reservoir into which the body fluid has been previously admitted. The external reservoir may be dockable to the device. For example, the analysis module can have a reservoir receptacle; furthermore, for example, a depression or the like can be formed in the analysis module housing, into which depression the external reservoir can be inserted. If the interface is arranged in the reservoir receptacle, the fluidic connection between the external reservoir and the fluidic module can be established simultaneously with the insertion of the external reservoir into the reservoir receptacle. As a result, the body fluid can be guided, in particular through the connecting hose or the hose coupling, into the fluidic module of the device.In other words, the device can be used in various ways. Thus, the device can be connected directly to a patient and, on request by the device (next measurement desired) or, for example, when a cerebral overpressure of the liquor is detected (if this is measured simultaneously), a respective next sample can be taken and fed to a measurement in the fluidic module. On the other hand, the device can also be used completely separately from the patient and can be used for diagnosing a sample which has already been taken. The device can be used for the pure analysis of the sample introduced into the fluidic module, i.e. also in a nontherapeutic environment. However, the device can also be designed in a particularly advantageous manner to analyze the sample (by means of corresponding evaluation electronics typically arranged in the base part) and to output an analysis result, so that this analysis result can also be used to subsequently initiate a treatment of a patient for the analysis. The device can thus be used prior to a later treatment of a patient. However, the device itself does not perform one or more therapeutic steps at any time. In the usual form of use, the device does not influence a patient directly and, overall, no therapeutic step is carried out, which is why the device is not a therapeutic device overall and no therapeutic method is carried out with the device either.The device described here further comprises a microfluidic chip arranged on or in the fluidic module, which is configured to influence the property of the body fluid. In particular, a component of the body fluid can be separated with the microfluidic chip in order to enable, improve or simplify a subsequent measurement of the remaining body fluid.The device is advantageously a mobile device. For example, the device may be point-of-care diagnostic device designed or suitable. The device can thus be used directly at the body fluid source and carry out the relevant analysis there.The property of the body fluid is, for example, the presence of particles, suspended particles or cells such as blood cells and / or blood serum proteins in the body fluid. Blood cells are understood to mean the cellular constituents of the blood, in particular erythrocytes, leukocytes and / or platelets. Blood serum proteins include, for example, methemoglobin (MetHb), oxyhemoglobin (HbO2), albumin, heme albumin, and / or bilirubin. It has namely been shown that a property of the body fluid that is potentially relevant for the present description is bilirubin levels.The property of the body fluid may be further described as the presence of hemoglobin or a derivative thereof in the body fluid. Hemoglobin is a chromoprotein consisting of two α- and β-globin chains, each having a heme attached as a prosthetic group. In the context of the present invention, "hemoglobin or a derivative thereof" refers to molecules that contain α- and / or β-globin chains. These are understood to mean all human hemoglobin types and derivatives thereof, such as conformations or oxidation forms, such as oxygenated hemoglobin (oxyhemoglobin, oxyhemoglobin) or deoxygenated hemoglobin (deoxyhemoglobin, HHb), and also methemoglobin (MetHemoglobin) or carboxyhemoglobin (COHb). Preferably, the hemoglobin derivatives consist of two alpha and two beta globin chains. Furthermore, derivatives are also hemoglobin molecules whose primary structure has been modified by substitution, deletion or addition of amino acids. Also included are products of hemoglobin degradation, such as bilirubin.Within the scope of the aforementioned enumeration, some constituents fall under the term blood serum proteins as well as under the term hemoglobin or a derivative thereof. Hemoglobin is also a protein, but is typically located within the red blood cells (erythrocytes) rather than in blood serum. The constituents mentioned in the preceding paragraphs are also to be understood as being merely examples; they represent the important components to be recognized for a targeted main purpose, namely liquor analysis.Generally speaking, affecting the property of the body fluid may include separating particles, suspended particles, or cells from the body fluid.The device can furthermore comprise a measuring device arranged in or on the fluidic module for determining the property of the body fluid. The measuring device is preferably configured to detect or quantify hemoglobin or a derivative thereof in the body fluid. The measuring device can furthermore comprise an optical sensor arranged in or on the fluidic module, in particular a spectrophotometer.To further simplify the handling of the device, it can furthermore comprise a body fluid reservoir arranged in or on the fluidic module. It is advantageous if the body fluid storage container is arranged upstream of the microfluidic chip.The term upstream or upstream on the one hand or downstream or downstream on the other hand refers in this description to the flow profile through the fluidic module. The most upstream location in the fluidic module is where the liquid enters the fluidic module. The most downstream location in the fluidic module is where the liquid flow terminates - that is preferably in a residue receiving volume disposed in or on the fluidic module.If the residual material receiving volume is arranged downstream of the fluidic module in the flow direction, the residual material receiving volume can be configured to be even easier to empty or to be replaceable. For example, the residue-receiving volume can be docked to the fluidic module by means of a quick coupling, so that it can be removed by means of a handle. This is also advantageous if the fluidic module is designed to be usable multiple times and is flushed for reuse. This results in a larger amount of liquid which can be discharged from the fluidic module and disposed of in the residue-receiving volume.The body fluid reservoir may include a level sensor or level indicator. With the possible evaluation of the fill level of the body fluid storage container, it is possible to regulate the body fluid transfer through or in the fluidic module on the basis of this fill level. As long as the fill level of the body fluid reservoir is too low, the body fluid (liquor) is sucked in until the reservoir is sufficiently filled. The body fluid can then be conveyed further in the fluidic module, for example to one of the following components. This further delivery in the fluidic module can be effected, for example, under pressure regulation or under valve regulation (or both).Thus, at least one switchable valve, in particular a solenoid valve, can be arranged in the fluidic module. This switchable valve is preferably arranged downstream of the body fluid reservoir. Thus, in particular, the fluid path can be switchably set up on the outlet side of the body fluid storage container. In this case, it is in particular immaterial if, instead of a switchable valve, a controllable valve is used, with which the throughflow quantity can be controlled. Due to the present field of object and the very low fluid quantities, a switchable valve is considered advantageous. However, a controllable valve would also be usable; this is typically only more expensive.The fluidic module furthermore preferably comprises a residue receiving volume arranged in or on the fluidic module. The residue receiving volume further preferably comprises a reservoir, i.e. a vessel in which the residue receiving volume is arranged. The residue receiving volume is further preferably connected to the microfluidic chip, so that residues separated or separated from the body fluid can be discharged directly into the residue receiving volume from the microfluidic chip. The term "residues" is used in the preamble for components which are separated from the body fluid. Alternatively or cumulatively, the residue-receiving volume is connected to the measuring device, so that volumes of the body fluid measured by the measuring device can be discharged into the residue-receiving volume. The residue-receiving volume can comprise a fill level sensor or a fill level display for displaying the fill level of the residue-receiving volume, so that, in particular when a maximum fill level is reached, information is output or the fluidic module can be replaced by a new fluidic module. This is particularly helpful when the device is used continuously, i.e. measurements are carried out regularly or at regular intervals therewith and the quantity of accumulated residual materials in the fluidic module thus increases continuously.A flushing device can furthermore be arranged in or on the fluidic module. The arrangement of a flushing device in the fluidic module makes it possible to flush the fluidic module, for example, in waiting times between measurements, so that the body fluid possibly still present therein does not block the lines, for example, in which it agglomerates or adheres.A check valve can be arranged on the fluidic module on the input side, in particular upstream of the body fluid storage container. Alternatively or cumulatively, a non-return valve can also be arranged upstream of the storage container. The arrangement of a check valve can be helpful, for example, in the case described above when a flushing device is inserted in the fluidic module. Namely, when a flushing agent is expelled from the flushing device, an upstream check valve prevents the flushing agent from entering the connecting hose or the body fluid source.The microfluidic chip used in the fluidic module preferably has an inlet channel and / or a bifurcation. Via the inlet channel, the body fluid can enter the microfluidic chip. For example, the body fluid can be conveyed into the microfluidic chip via a pump. The inlet channel is preferably elongated. Alternatively or cumulatively, the microfluidic chip has a separation device for separating particles, particles or cells from the body fluid. The separation device can comprise at least one piezoelectric component, in particular a piezoelectric transducer. The separation device can be arranged, for example, on the inlet channel or act on the or a part of the inlet channel, so that the body fluid is separated in the inlet channel. By the correct setting of the separation device, it can be achieved that the component to be separated is split off from the body fluid in the microfluidic chip. For example, it can be designed such that the separation device acts on the body fluid in the inlet channel and there pushes the component to be separated into a center of the inlet channel and thereby escapes the remaining body fluid into the edge region of the inlet channel. With a corresponding configuration of the flow guidance through the microfluidic chip, it is thus possible to easily obtain a splitting of the two liquid streams.The separation device can be configured, for example, to provide a sound pressure, in particular for providing an akustophoresis. This applies an acoustic torque to the fluid in the input channel.Upstream of the microfluidic chip, a gas bubble detection and / or deposition device for identification and / or deposition of gaseous constituents may be arranged. In other words, this can be used to separate bubbles or gas inclusions from the body fluid, for example. Although no gaseous constituents should be present in the body fluid if the feed line and all connections are made tight. On the other hand, measurement of a gas bubbled body fluid would be expected to produce an erroneous result. Thus, the inclusion of a device for detecting or depositing gas bubbles can further improve the results obtainable with the device.The connection tube is, for example, adapted for connection to an external ventricular drain. Alternatively or cumulatively, the connecting hose is designed for direct connection to the fluidic module. Alternatively or cumulatively, the fluidic module can be configured for connection to the connecting hose. Finally, alternatively or cumulatively, the fluidic module can comprise a hose coupling for connecting to the connecting hose. In other words, the device preferably comprises an interface for direct connection to a body fluid source, in particular a patient or an external ventricular drain. This enables in situ analysis of the body fluid without prior transport to the laboratory.A fluid detector can be arranged in the device on or in the fluidic module, which enables the presence of body fluid in the fluidic module to be detected. By incorporating a fluid detector into the fluidic module, it is thus possible to ensure that it is possible to ascertain whether the body fluid reaches the fluidic module from the body fluid source. It is thus possible to direct corrective measures, such as the passage, in particular the hose passage. On the other hand, it is also possible to restrict or exclude blockages in the flow path outside or within the fluidic module.The device preferably comprises a pump for providing an overpressure and / or a negative pressure. Atmospheric air (optionally filtered) can preferably be used in order to provide an overpressure or underpressure in the fluidic module. Depending on the application, it is optionally also possible to use a gas which is optionally also already provided in an excess pressure (compressed gas cylinder). Thus, at least for the provision of an overpressure, no pump may be required. Typically, however, the use of a pump will be simpler and more expedient than the provision of a compressed gas cylinder which is emptied by use and thus the fill level thereof has to be monitored.The pump can be connected to the fluidic module in an advantageous manner, so that the overpressure and / or the underpressure can be provided in the fluidic module. Alternatively or cumulatively, the pump can be connected to the fluidic module by means of at least one pressure connection coupling.For connecting the pump to the fluidic module, in one embodiment only exactly one pressure connection coupling is provided on the fluidic module. In this embodiment, the pump is advantageously constructed in such a way that both overpressure and underpressure can be delivered to the fluidic module via the one pressure connection coupling.For connecting the pump to the fluidic module, on the other hand, a plurality of at least two pressure connection couplings can be respectively held on the base part and the fluidic module, so that in particular the negative pressure can be output to the fluidic module separately from the positive pressure. Alternatively or cumulatively, a control pressure connection clutch for controlling a compressed air-controlled device can be provided in the fluidic module.The overpressure and / or the underpressure can be used in an advantageous manner for influencing a fluid flow in the fluidic module. Alternatively or cumulatively, the body fluid can be aspirated by means of negative pressure, in particular can be aspirated from a ventricular drain or a patient into the body fluid storage container. Alternatively or cumulatively, the body fluid can be further conveyed in the fluidic module by means of overpressure, in particular from the body fluid storage container to the microfluidic chip.The body fluid storage container can be supplied with the negative pressure and / or the positive pressure. By means of the application of negative pressure, the body fluid can then be conveyed out of the connecting hose into the body fluid storage container. By applying overpressure, body fluid stored in the body fluid storage container can be conveyed in the direction of the microfluidic chip.The device, and there in particular the base module, is preferably further configured to house at least one of the following components: a control module configured to control the further delivery of the body fluid in the fluidic module and / or to control the measuring device, wherein control commands of the control module can be transmitted to the fluidic module via the at least one pressure connection and / or via electrical contacts, an evaluation module for evaluating the data obtained with the fluidic module, in particular the measuring device, and for providing a diagnostic result with respect to the property of the body fluid, a storage module for storing the measurement data obtained with the fluidic module, so that in particular the measurement can be continued without gaps even when the fluidic module is exchanged, a pump controller for controlling the pump arranged in the device, wherein the pump controller can be supplied to the controller with sensor data from the fluidic module, a wireless connecting device for connecting, for example, to a hospital network for data exchange therewith, and / or an electrical supply device comprising a power connection and / or an energy store.The control module can be configured to close the access in the event of a fault detection in the body fluid delivery, i.e. to act in particular in response to the above-described fluid detector, and / or to act on a control valve (solenoid valve) arranged in the fluidic module or on the ventricular drain in order to shut off the fluid flow.In principle, in this description, the terms control pressure and control are used in the pneumatic control of the fluidic module 40, wherein both the control (feedforward) and the regulation (feed-back) should be understood as appropriate. Since the device 1 described here is designed with regard to the provision and delivery of the body fluid 95 in the fluidic module 40 by a particular simplicity, and because of the particular structure, no regulated pumps are required, but rather pumps and valves can be switched simply "on" and "off", this is actually a control of the respective component. However, this should not exclude that the fluid pump 20 or the flow rate can be regulated accordingly, i.e. is regulated in response to sensor data.Within the scope of the present description, the fluidic module is also described as an inherent component, in which a fluid interface, such as in particular a connecting hose or a hose coupling, is set up for connecting the fluidic module to a body fluid source, in particular a patient. Thus, the body fluid can be guided through the connecting hose or the hose coupling into the fluidic module of the device. The fluidic module further comprises a microfluidic chip arranged on or in the fluidic module, which is configured to influence the property of the body fluid.Within the scope of the present description, the microfluidic chip, in particular configured for use in an apparatus described above for measuring and / or influencing a property of a body fluid, is also described. The microfluidic chip has an inlet channel, a bifurcation, a first and a second outlet openings, and a separation device for separating a portion of the body fluid, in particular particles, particles or cells, from the body fluid in the region of the bifurcation, so that the portion of the body fluid can be supplied to the first outlet opening and a purified body fluid can be supplied to the second outlet opening.In the microfluidic chip, the separation device can be configured to guide the portion of the body fluid, in particular by means of akustophoresis, into a central part of the inlet channel. The cleaned body fluid can then escape into a side region of the inlet channel, so that in the region of the bifurcation and with the presence of a fluid flow, the portion of the body fluid is guided to the first outlet opening and the cleaned body fluid is guided to the second outlet opening of the microfluidic chip.The separation device can further comprise a piezoelectric transducer. The microfluidic chip can comprise a glass wafer and / or a silicon wafer, optionally the glass wafer is bonded to the silicon wafer.Within the scope of the present description, a method for diagnosing a body fluid, in particular liquor, in particular using the above-described device and / or the above-described fluidic module or microfluidic chips is also within the scope of the present description. The method comprises the following steps: introducing the body fluid into a fluidic module, bringing the body fluid to a microfluidic chip arranged in or on the fluidic module for influencing a property of the body fluid, in particular for separating erythrocytes and / or leukocytes from the body fluid, by means of or in the microfluidic chip, further conveying the body fluid to a measuring device arranged in or on the fluidic module for determining the same or a further property of the body fluid, further conveying the body fluid from the measuring device and into a residual material receiving volume arranged in the fluidic module.The method can furthermore be equipped with the step of starting the conveying of the body fluid in the fluidic module as soon as a body fluid storage container arranged in the fluidic module is sufficiently stored with the body fluid. The steps of conveying the body fluid can be carried out, for example, by means of a feed pump arranged in the device, in particular in a base module of the device.The device can furthermore be designed as a mobile device. The method can be designed as a point-of-care diagnostic method.The device proposed here can be designed to automatically carry out a concentration measurement of fRb and its derivatives in liquor samples. These may be either repeated measurements in which liquor is removed from the tube system of a ventricular or lumbar drainage system for example over several days. Or it may be a single measurement in which the liquor sample is obtained by an LP.The following scheme again describes the structure of the device in other words: the system consists of the reusable medical device (MD) containing all electronic components and a disposable unit which comes into contact with the patient's liquor and can be disposed of and replaced between use on different patients. The reusable MD may include an embedded system that controls a pump, multiple valves, a cell sorting mechanism, multiple different sensors such as flow, pressure and temperature, and an optical sensing unit. Measurement results and user inputs are provided via the human-machine interface (HMI), e.g., a touch screen or the like. In particular, the liquid flows can be controlled by means of valves, but these are advantageously not part of the disposable product. The pump can selectively draw and push fluid depending on the automatically controlled valve setting.To make a measurement, the liquor sample is drawn into the reservoir until a certain volume is reached, which is detected by a level detector. The sample is then pushed into the cell sorting mechanism, which separates the erythrocytes and / or leukocytes from the sample. Cell sorting is achieved by akustophoresis. A liquid channel is ultrasonically excited by a piezoelectric element to concentrate erythrocytes and / or leukocytes in a certain region of the channel and separate them from purified liquor. Feedback control of the separation parameter setpoints is used to stabilize the cell focusing process based on a sensor measurement of the separation power. Subsequently, the spectrophotometric detection unit measures the photon absorption in the low-cell liquor. Based on the absorption at certain wavelengths or in certain spectral ranges, the concentration of fAbs and derivatives in the integrated processor can be calculated and displayed to the user on the HMI.Finally, liquor and cellular material are collected in the waste bag (waste uptake volume). An additional liquid path may allow the flushing of the disposable system with a cleaning solution. The system with the disposable article can be designed, for example, for repeated automated measurements over a period of up to 10 days on a single patient.Essential components of the present description are the cell-liquid separation unit (microfluidic chip), the pump and valve configuration for, e.g., passing liquor or flushing agent through the flow paths, and the measurement unit or photometric detection unit. The architecture and the interconnection of the blocks into a single system for liquor analysis enables a completely novel system which offers a multiplicity of innovations and thereby defines a new class of equipment which is also POC capable (which can be used at the site of treatment). In this case, the design of the system as a compact, mobile device, in particular with a reusable base module and an easily exchangeable analysis unit, with fluidic connection to the liquor outlet can contribute, on the other hand, in order to use it as a point-of-care diagnostic device.In the technical realization of the individual functional subsystems alternative solutions are possible; such alternative solutions are to be expressly considered covered by the present description. Cell sorting can be realized by any type of separation method, optionally with a different control. Examples are surface wave akustophoresisThe optical detection unit is either a broadband spectrometer which covers the spectral absorption range of the analyte or an arrangement of light sources with specific, narrowband spectra which are tailored to the absorption peaks of the analyte. The photometric measurement can be carried out in a separate cuvette in which the analyte is collected, or alternatively in the flow on the microfluidic chip.Finally, the pump need not be of a particular type, but merely meet the fluidic requirements of the system.The invention is explained in more detail below with reference to exemplary embodiments and with reference to the figures. In this case, similar or identical elements have in part the same reference numerals, and the features of the different exemplary embodiments can be combined with one another.Brief Description of the FiguresThe following are shown: FIG. 1 shows the schematic structure of a first embodiment of the device, FIG. 2 shows a schematic structure of a further embodiment of the device, FIG. 3 shows a schematic structure of a further embodiment of the device, FIG. 4 shows a schematic structure of a further embodiment of the device, FIG. 5 shows a schematic structure of a further embodiment of the device, FIG. 6 shows a schematic structure of a further embodiment of the device, FIG. 7 shows a schematic structure of a further embodiment of the device, FIG. 8 shows a schematic structure of a further embodiment of the device, FIG. 9 shows a schematic structure of a microfluidic chip, FIG. 10 shows a microscopic representation of a microfluidic chip used in prototype form with the shown splitting of the body fluid, FIG. 11 shows a flow chart of the method.DETAILED DESCRIPTION OF THE INVENTIONFIG. 1 shows a first embodiment of the device 1, which in this embodiment has a base part 10 and a / fluidic module 40 arranged thereon or held thereon. The representations are chosen schematically and show the information essential for the present description. Thus, the base part 10 can be designed as a trolley or as a small, manageable and in particular portable device of the size of the LiquoGuar ®- devices of the applicant Moller Medical. The receptacle of the fluidic module 40 on the base part 10 can be designed in the form of a cassette receptacle, or simply with latching noses on the base part 10.The fluidic module 40 has a connection line 5, which in this case extends as a directly connected line 41 directly to the body fluid reservoir 55 in the fluidic module 40, and is connected on its other side to the body fluid source 2. The body fluid source 2 can be a fluid container, schematically shown as a petri dish in FIG. 1, into which the body fluid 95 has been previously introduced. In this case, the device 1 is completely independent of a patient that may be treated and is not connected to the latter. The device 1 is then a pure analysis device of a measurement sample 2 provided in an external body fluid source 2, which is at least partially supplied to the fluidic module 40.For example, the connecting line 5 can be provided with a strain relief in the region of the housing passage 49 of the fluidic module housing 48 or can be pressed in or thickened there on the housing 48, but the connecting line 5 otherwise forms a continuous line with the inlet line 41. Body fluid 95 can be introduced into the fluidic module 40 via the connection line 5. If necessary, the hydrostatic force distribution between the test sample 2 and the fluidic module 40 can be adjusted such that the body fluid 95 automatically enters the storage container 55 until a measurement fill level is reached. For example, the measurement fill level in the storage container 55 can be above the height of the inlet opening of the connecting line 5 on the storage container 55, so that the liquid level 56 in the storage container 55 covers the inlet opening and thus stops the run-on of further body fluid 95. Typically, however, it is preferred to be able to control or regulate the fluid flow into the fluidic module 40 and in the fluidic module 40. In this case or when the body fluid 95 does not automatically enter the device 1, the inflow and the distribution in the fluidic module 40 can be controlled by means of the pump 20 arranged in the base part 10. In this embodiment, the pump 20 is connected to the fluidic module 40 by means of the pressure port 32. More precisely, the connection in the fluidic module 40 leads via the pressure connection 82, the connection line 84 to the body fluid reservoir container 55. Thus, the reservoir container 55 can advantageously act to a certain extent as a pressure compensation volume, so that when a negative pressure is applied to the reservoir container 55, a soft suction is produced on the connection line 5 and thus on the body fluid source 2. The storage volume 55 is filled until a measurement fill level 56 is set in the volume 55. For example, this can be checked by a fill level sensor 57. Subsequently, the pump 20 can be switched over to generate an overpressure, with which the volume 55 can be charged again. If necessary, it can be adjusted hydrostatically in such a way that no pressure is exerted on the connecting line 5, or a check valve, switching valve or other possibility, for example of shutting off in or on the connecting line 5, is provided, so that no overpressure acts back on the body fluid source.Connected to the body fluid reservoir 55 is a conduit 42 that connects a microfluidic chip 60. Thus, the body fluid 95 can pass from the reservoir 55 to the microfluidic chip 60. It is preferred if the fluid 95 is conveyed further with slight pressure, so that a stationary fluid column abuts the microfluidic chip 60 and thus the fluid does not arrive interrupted, which can possibly interfere with the function of the microfluidic chip 60 or of the downstream measuring device 70.The microfluidic chip 60 has two outputs 62, 63 (see FIGS. 8, 9 ) which connect, on the one hand, the measuring device 70 to the inlet line 43 and, on the other hand, a residue-receiving volume 75 to the inlet line 45. Separated constituents of the body fluid 95 can be discharged via line 45, whereas the remaining body fluid 95 without these constituents is supplied to the measuring device 70 via line 43. The presence of this fluid component is the property of the body fluid 95, the separation of the fluid component the influencing or alteration of the property of the body fluid 95. When the fluid is 95 liquor and the liquid component blood cells, the microfluidic chip 60 separates blood cells from the liquor. Hemoglobin in the liquor can then be detected by the measuring device 70. Alternatively or cumulatively, it may be advantageous to arrange between microfluidic chip 60 and residue receiving volume 75 a measuring device which establishes or quantitates the presence of blood cells.After the measurement with the measuring device 70, the body fluid 95 is likewise supplied to the residue-receiving volume 75. The residue receiving volume 75 then serves in the manner of a "waste collector" in the fluidic module 40 for receiving the residues, so that the fluidic module 40 does not require any further connections and in particular remains clinically clean. When the residue receiving volume 75 is filled, the fluidic module can be replaced to continue the measurements. Depending on the circumstances, the fluidic module can be supplied to disposal or recycling or reused after appropriate cleaning. Such recycling, if desired, advantageously takes place outside the clinical environment, but can be carried out in a correspondingly equipped operation. This may include the complete reprocessing of the fluidic module 40 or else only the removal of the valuable parts suitable for the reuse. Optionally, the fluidic module 40 may also be configured such that certain components are removably configured therefrom and are removable from the fluidic module 40 by the clinic before disposal of the same. These can be corresponding sensors, which can be detached from the fluidic module 40 for example via pushbuttons or other mechanically or electrically operated ejection devices and can be supplied for reuse without these parts being contaminated with body fluid 95 or other undesired fluid.In order to avoid repetitions, differences from those shown in FIG. 1 will be discussed below. Otherwise, the description explained with reference to FIG. 1, which is applicable in terms of the respective embodiments shown with reference to FIGS. 2 to 7.Referring to FIG. 2, a further embodiment of the device 1 is shown, wherein the connection line 5 is connected to a drain 4 on the body fluid source side and ends on the fluidic module side at a hose coupling 8 arranged on the fluidic module 40. In other words, the connecting line 5 is a separate part which can be plugged onto the fluidic module 40. This embodiment is possibly more practical to handle and also allows the use of a respectively adapted connecting line 5 depending on the location of use. Moreover, in this embodiment, the hose coupling 51 can be designed on the fluidic module 40 in such a way that it closes the line when the connecting line 5 is released. In other words, a check valve 52 can be integrated into the hose coupling 51 so that the fluid quantity located in the inlet line 41 cannot drain out of the fluidic module 40. This is advantageous in order to make the fluidic module 40 more hygienic. A check valve 52 may also be located separately from the hose coupling 51, for example at the inlet of the body fluid reservoir 55, the result being substantially the same. The body fluid storage container 55 has a fluid level 56 up to which the body fluid 95 is introduced before the later measurement and / or influencing of the body fluid 95 is started. In contrast to the embodiment shown in FIG. 1, the pressure connection line 84 is not connected directly to the storage volume 55, but downstream thereof. In the base part 10, in addition to the pump 20, an inlet-side and outlet-side pressure sensor 28, 29 are arranged.With a suitable hydrostatic design, the pump 20 can, for example, draw in fluid until fluid is detected in the connecting line 84 at the measurement point 85. Then, the fluid may be gravity fed to hold a fluid pressure and fed into the microfluidic chip 60. A further check valve 59 is arranged upstream of the microfluidic chip 60.In this embodiment, microfluidic chip 60 has only one output. For example, a property of the fluid 95 can be changed in this microfluidic chip 60 without a component to be separated being present, which would have to be discharged separately. The changed fluid is supplied to the measurement volume 72 of the measuring device 70 by means of the line 43, and the fluid 95 is measured by means of a sensor 74. The measured fluid is then supplied to the residue receiving volume 95. The residue-receiving volume 95 has a fill level sensor 76, so that the fill level or the reaching of a maximum fill level can be detected. If necessary, when a maximum fill level of the residue receiving volume 95 is reached, a signal can be output, so that the user experiences the fill level and can possibly take measures such as replacing the fluidic module 40 with a fresh module 40.In the embodiment shown in FIG. 2, a flushing device 90 is furthermore arranged in the fluidic module 40 for flushing the lines and possibly reusable components with a flushing agent. To select the fluid to be used from the line 42, the fluidic module 40 has the switching valves 58, 92 as solenoid valves 58, 92. Thus, after the completion of the measurements or if desired, the supply line 5 or the body fluid storage container 55 can be disconnected by means of the switching valve 58 and microfluidic chip 60 and measurement volume 72 can be flushed by means of the flushing device 90. If this can be done as a certified hygiene process, it is conceivable that after carrying out the rinsing process, clinical personnel are given the option of removing the microfluidic chip 60 and / or the measuring device 70 from the fluidic module 40 for reuse (optionally after additional cleaning).Among the advantages of a device 1 as shown here is also that the pumping process or the pump 20, 21 cannot cause hemolysis. It is essentially immaterial which type of fluid pump 20 is used, a simple and cost-effective disk pump 20 is sufficiently good, already because the fluid 95 does not have to be pumped by the pump 20, but rather the pump 20 can be arranged outside the fluid circuit or the lines 41, 42, 43, 44, 45 wetted with fluid 95 and acts on the fluidic module 40 from the outside, that is to say from the base part 10. This advantage applies to all the embodiments shown.With reference to FIG. 3, the same reference numerals again show the same items as explained with reference to FIGS. 1 and 2. The pump 20, which draws in air (overpressure) or blows out air via the air connection 36 and pressure sensor 29 (underpressure or vacuum), is connected to the fluidic module 40 via the pressure sensor 28 also shown in FIG. 2 and directly loads the body fluid reservoir 55 there (analogously to the exemplary embodiment shown in FIG. 1 ).In the inlet channel 41 of the fluidic module 40, a flow sensor 53 is arranged, by means of which a flow rate can be detected. Thus, a certain degree of certainty can be ensured whether body fluid 95 actually arrives in the fluidic module 40. This can increase the reproducibility of the measurement results.Microfluidic chip 60 shown in FIG. 3 has two outputs as in FIG. 1, so that output lines 43 and 45 are connected thereto. Furthermore, a further switching valve 73 (solenoid valve) is arranged between the measuring device 70 and the residue-receiving volume 75, so that the body fluid 95 can be discharged from the measuring volume 72 in a controlled manner. As a result, a certain control over the fluid column from the body fluid reservoir 55 via the microfluidic chip 60 to the valve 73 can also be carried out, so that the fluid flow through the fluidic module 40 can be influenced by controlling the valves 58, 73.The embodiment shown in FIG. 3 has a minimum dead volume, so that the need for body fluid ( 95), such as liquor, is further reduced. Furthermore, a screen can be used, for example, in the region of the hose coupling 51, with the nonreturn valve 52 or at least upstream of the microfluidic chip 60, for example with or in the nonreturn valve 59, for example, for filtering coagulated blood in the liquor.Overall, the entire fluidic module 40 could also be used as a screen in order to separate coagulated blood from the liquor if, instead of depositing the liquor in the residue receiving volume 75, the body fluid 95 purified in the microfluidic chip 60 was reused.Not shown is a bubble sensor that detects gas inclusions in the body fluid. Here too, there are already commercially available non-invasive sensors, for example on the basis of an ultrasonic measurement, by means of which gas bubbles in a fluid can be reliably detected. If necessary, the fluidic module 40 can be supplemented with such a bubble sensor.With reference to Fig. 4, a further embodiment of the apparatus is shown, wherein again the same reference numerals represent the same items as described above. A fluid detection device 54 is arranged on the input side of the fluidic module 40. For example, such a fluid detection 54 operates with an ultrasonic sensor, by means of which it is possible to infer whether a liquid is present in the inlet channel 41 after a time-of-flight measurement of the ultrasonic source and the signal response delay. In addition, in this embodiment, a flow sensor 53 (flow sensor) is also arranged in the inlet line 41. For example, the flow velocity can be determined by means of the flow sensor 53. If necessary, the fluid detection device 54 can be configured with the flow sensor 53 as a combined component 53 / 54.The body fluid reservoir 55 is disposed at a bifurcation of the inlet conduit 41 in the embodiment shown in FIG. 4. As shown in FIG. 1, the storage container 55 can also be supplied with overpressure and / or underpressure in this embodiment. In this embodiment, the pump 20 is connected to the body fluid reservoir 55 via two pressure ports 37, 38 and the mating ports 82, 84 of the fluidic module 40. In order to convey fluid into the storage container 55, a negative pressure can be applied, in order to convey fluid further in the fluidic module 40, an overpressure can be applied. The check valve 52 prevents a return flow into the connecting line 5. a further flow sensor 69 is furthermore arranged between the microfluidic chip 60 and the measuring device 70, so that it is also possible to ensure that body fluid 95 exits from the microfluidic chip 60 into the feed line 43 and is thus ready for measurement with the measuring device 70. This may ensure that the function of microfluidic chip 60 is monitored during the execution of the measurement.After separation in microfluidic chip 60, cleaned body fluid 95 is therefore guided, for example, to measuring device 70, which can perform a spectrophotometric analysis.In the embodiment shown in FIG. 4, the fluid control system is configured overall via solenoid valves 11, 12, 58, 73, 79, 92. The solenoid valves can be controlled by a controller 33 (cf. FIG. 7 ), i.e. switched on and off, in order to realize the corresponding fluid delivery in the fluidic module 40.Referring to Fig. 5, a further embodiment of the apparatus 1 is shown, wherein the pump 20 is further simplified with respect to the relevant connections. Both negative pressure and positive pressure can be delivered to the fluidic module 40 via only one pressure connection 37. In order to achieve this, a changeover device is arranged in the base part 10, which by means of the two solenoid valves allows the pump either to suck in air via air inlet 13, air inlet filter 14 and provides an overpressure at the connection 37 via the path P>P atm. Alternatively, the switching device draws air out of the fluidic module 40, which is pumped out via the path P<P atm, air outlet filter 16 and air outlet 15. The advantage of this arrangement is the smaller number of pressure connections, since only one connection 37 is inserted and the connection 38 is unnecessary. Thus, there are fewer connector parts between the base part 10 and the fluidic module 40, which may possibly fail. Depending on the desired configuration, the fluidic module 40 can automatically perform measurement and storage of the measurement, so that possibly no electrical connections between fluidic module 40 and base part 10 are necessary. On the other hand, it is likely that it is less expensive and advantageous overall to provide electrical connections (see FIG. 7 ) and also to control the measuring device 70 and store the data in the base part 10.Referring now to Fig. 6, there is shown yet another embodiment of the apparatus 1, in which case fluid control is effected via pneumatically controlled valves 58, 73, 79, 92. For this purpose, a plurality of switching outputs 30 are provided on the base part 10 for applying switching pressures to the fluidic module 40 for the individual switching of the respective pneumatic valves 58, 73, 79, 92. The arrangement of two separate pumps 20, 21 in the base part 10 enables a reliable separation of the switching unit and the compressed air lines connected thereto from the body fluid 95, since it is ensured there that no body fluid 95 reaches the lines. These components can thus be realized, if appropriate, more favorably or with smaller deposits. According to the embodiment of FIG. 6, the switching pump 21 is supplied with ambient air (or a gas) via the air inlet 22 and the inlet filter 23. A supply pressure can be stored in a pressure accumulator 25, which can be filled up to a supply pressure by means of the pressure sensor 24. If necessary, a different pressure range can be made available as a result than for the fluid delivery pump 20. By using two pumps 20, 21, it is thus also ensured that the lines carrying the body fluid are not subjected to an excessively high overpressure. Finally, a very finely meterable fluid pump 20 can thereby be used for the relatively low negative and positive pressures used for the fluid delivery, and a (more favorable) coarser control pump 21 can be used for the larger control pressures for controlling the valves.The individual control lines can be pressurized via the control valves 31 or shut off from the pressure accumulator 25. Each pressure valve 58, 73, 79, 92 typically has a "standard state", for example "normally closed" or "normally open", so that the respective valve assumes a failsafe "fail safe" state without pressurization. For example, the valve 92 of the flushing device 90 will be used in the failsafe state "normally closed", so that the flushing agent can only enter the fluid-conducting lines when the associated valve 92 is pressurized and thus changes the opening state from closed to open.Referring finally to FIG. 7, the embodiment of FIG. 6 is shown, wherein the electrical connecting lines 34 and the control module 33 are additionally inserted into the schematic illustration. In the embodiment shown, an evaluation module 93 for evaluating the measurement data generated by the measuring device 70 is also arranged in the control module 33. The evaluation module 93 can also be used to evaluate the measurement at the same time with the apparatus 1 and, if appropriate, output it to a display device. This can be displayed, similar to the example of the compact LiquoGuar from the home of the applicant, by means of a display on the practical large-format screen and, if appropriate, further information such as other measured values can also be obtained by means of inputs via keys or via a touch-sensitive screen or can be influenced on the measurement, for example the optical frequencies used for measurement using the sensor 74 can be changed. Furthermore, a storage module 94 is provided, by means of which the measurement data obtained with the measuring device 70 can be (temporarily) stored. Furthermore, further parameters of the device 1 can also be stored with the storage module 94, status or operating data of the pumps 20, 21, data of the microfluidic chip 60, sensor data of the various fluid sensors used and filling levels of the containers 55, 75.The pump control 97 and the corresponding control lines can be used, for example, to preset the operating direction of the fluid pump 20 (negative pressure or positive pressure) or else the control pressure of the control pump 21, and also to control the corresponding (magnetic) valves 17, 18, 31.A wireless connecting device 98 enables a data connection, for example with the hospital network or with other connecting means, so that a user of the apparatus 1 can be informed at any time during the measurement of the state or the presence of measurement results, and / or about the state of the apparatus 1, as ready for use or error state, and / or measurement data obtained via it can be transmitted into a correspondingly accessible patient record. Finally, the electrical supply device 99 provides for the electrical supply of the apparatus 1. the electrical supply device 99 can be designed as an accumulator or energy store or comprise a plug for connection to a local voltage supply.FIG. 8 shows an embodiment of the device 1, which is simplified compared to the previous embodiments, with a direct connection via the interface 5 to the body fluid source 2. the device 1 comprises the fluidic module 40 and a pump 20 integrated in the base module 10, which conveys the body fluid 95 into the fluidic module 40. The fluidic module 40 is designed to house the microfluidic chip 60, which enables the separation of components such as blood cells (erythrocytes, leukocytes) and / or blood serum proteins from the body fluid 95. In this embodiment, the measuring device 70 already monitors the microfluidic chip 60, so that the measurement can already be carried out on or in the region of the microfluidic chip 60. In other words, the measurement in the flow can be performed on the microfluidic chip 60.The body fluid sample 2 filled with body fluid 95 up to the liquid level 56 can, as shown in FIG. 8, be connected relatively freely to the device 1 via the interface 5. The interface 5 can also be designed as a holder, by means of which not only the fluid communication or the removal of the body fluid from the body fluid source 2 is ensured. Rather, the interface 5 can also be used to hold the body fluid source 2, in particular in the form of a reservoir, on the device 1. As soon as the measurement by means of the device 1 is finished and thus no further body fluid 95 is required any more, it can be provided that the components of the device 1 wetted with body fluid 95 or contacted are rinsed with a rinsing liquid. For this purpose, the device can have a rinsing liquid reservoir 90, which can be arranged, for example, in the fluidic module 40. For switching between flushing device 90 and body fluid source 2, a switching device 92 can be provided. In the example shown with FIG. 8, this is shown as a switching rocker. A changeover valve can also be provided at this location.The body fluid reaches the microfluidic chip 60 via the inlet line 42; in the microfluidic chip 60, the separation of the foreign substances from the body fluid 95 takes place. furthermore, in this example, the measurement of the body fluid 95 also takes place by means of the measuring device 70 in the region of the microfluidic chip 60. By means of the pump 20, the body fluid is conveyed further through the device and finally supplied via the inlet line 45 to the residual material receiving volume 75. In this example, the residue receptacle 75 is located in the fluidic module 40.The measurement results can be displayed on a display of the apparatus 1 and / or transmitted to the hospital information system via the wireless connection device, for example.This simplified embodiment allows particularly easy handling on the patient and emphasises the in situ analysis functionality of the device. The direct connection obviates the need to transport the sample into the laboratory, which saves time and improves the accuracy of the results since sample aging and contamination are minimized.FIG. 9 shows an embodiment of a microfluidic chip 60 according to the present description, as it can also be used in the preceding FIGS. 1 to 7, having an inlet 61 and two outlet openings 62, 63. The microfluidic chip 60 can be configured such that the body fluid 95 is influenced in the region of the inlet channel 64. Thus, in the embodiment shown with FIG. 8, a separation device 80 is shown, which exerts the influence on the body fluid 95 on the inlet channel by means of a separation effect. In this illustration, the separation device 80 is shown laterally of the inlet channel 64. The arrangement of the separation device 80 as compared to the microfluidic chip 60 may depend on the operation of the separation device 80, and an arrangement towards below the microfluidic chip 60 (so that the two outlet channels 68 extend laterally to the left and to the right and not closer to or further away from the separation device 80) is provided in the same way. The illustration is also chosen laterally because, in the case of an arrangement below the microfluidic chip 60, the separation device 80 would not be visible by illustration. For example, the separation device 80 is configured to separate components 96 of the body fluid 95 from the remaining body fluid. It can then be provided that the components to be separated are conducted to the first outlet channel 67 and thus to the first outlet opening 62, and the body fluid 95 is conducted in the direction of the second outlet channels 68 and thus to the second outlet opening 63. For example, blood cells such as erythrocytes and / or leukocytes can be separated from liquor in this manner.A photographic representation of a section of a microfluidic chip 60 is shown with FIG. 10, wherein actually body fluid 95 is conducted through the inlet channel 64 of the microfluidic chip 60 and a separation device 80 arranged below the microfluidic chip 60 effects a separation of the erythrocytes 96 (red) from the remaining body fluid 95 (white to slightly reddish). The remaining body fluid 95 escapes to the edge of the inlet channel 64. By means of the prevailing flow from the inlet channel 64 in the direction of the outlet channels 67, 68, the fluid flow is split up in the region of the bifurcation 65, in which as a result the constituents 96 to be separated are carried on centrally and can be fed to the first outlet opening 62. The remaining body fluid 95 is conducted around the outside into the outlet channels 68 and reaches the second outlet opening 63 (cf. FIG. 9 ). Subsequently, the remaining body fluid 95 can be passed on to the measuring device 70 and the separated components to the remaining material receiving volume 75.The device can be equipped, in addition or as an alternative to the fluid pump 20, with one or more micropumps, such as a microfluidic peristaltic pump. Such a pump acts on a similar principle to the microfluidic chip 60, wherein a plurality of, for example, three microvalves can form a pump for delivering the body fluid 95.Finally, with reference to FIG. 11, a flow diagram of a method 100 for measuring, influencing or diagnosing a body fluid 95 is presented. With step 110, the body fluid 95 is introduced into the device 1 or the fluidic module 40. Optionally, step 115 involves a detection of whether body fluid is located in the fluidic module 40, for example by means of one or more flow sensors 53, 59. step 120 involves the supply of the body fluid 95 to the microfluidic chip 60 arranged on or in the fluidic module 40, so that the influencing 130 of the body fluid 95 can be carried out by means of the microfluidic chip 60, for example the elimination of blood cells, such as erythrocytes and / or leukocytes 96, from the liquor 95, furthermore for example by means of the separation device 80. In other words, activation 125 of microfluidic chip 60 may take place in response to detection 115 in fluidic module 40.After influencing 130 the property of the body fluid 95, the body fluid 95 is conveyed further 135 to a measuring device 70 for the purpose of measuring 140 the same property or a further property of the body fluid 95. After measurement 140 has been carried out, the disposal 150 of the body fluid 95 and / or of the constituents 96 in the fluidic module 40 is finally carried out.Numerous experiments and experiments have also been carried out within the scope of the present description. A prototype microfluidic chip capable of separating blood cells, such as erythrocytes and / or leukocytes from liquor by means of acoustic forces has been prepared. The manipulation of cells with the aid of acoustic forces (acoustic force) is based on the generation of an acoustic pressure in a microfluidic channel via a piezoelectric element. At a defined frequency, a standing acoustic wave is generated in the channel, with the pressure node or nodes being / are located in the center of the channel. The blood cells, such as erythrocytes and / or leukocytes, are focused in the middle of the canal due to their positive acoustic contrast factor compared to blood plasma and liquor.The microfluidic chip 60 comprises in particular a base made of silicon and was produced, for example, by double-sided photolithography on a silicon wafer with a diameter of 4 inches and a thickness of 500 μm±10 μm. The microfluidic channel and access holes were fabricated by inductively coupled plasma deep reactive ion etching (ICP-DRIE, Bosch process, Estrellas, Oxford Instruments) on the front and back sides with a channel depth of 200 μm±5 μm, a channel width of 700±5 μm and an access hole diameter of 1000 μm.A glass wafer (thickness 700 μm) was anodically bonded to the silicon wafer (SB6, SUSS MicroTec, Garching, Germany) and then cut into rectangular chips (11 mm x 58 mm) with a wafer saw (DAD3221, Disco Corporation). The piezoelectric transducer (20 mm x 20 mm x 2 mm, PZ26, Ferroperm Piezoelectrics A / S, Kvistgard, Denmark) was bonded to the back of the scrambled chips with an epoxy resin (H20E, EPO-TEK). Two copper wires (0.25 mm diameter) were bonded to the electrodes of the piezoelectric transducer with silver paste and second adhesive. The chip was clamped in a holder and sealed with O-rings with three flanged PTFE tubes (1 / 16 inch x 0.75 mm outside and inside diameters respectively) that allow access to the inlet and two outlet ports.For testing the microfluidic chip, an in vitro testing stand of modular construction was constructed. It comprises an interface for connecting the particle separation device and the spectrophotometer, three syringe pumps (Nemesys 290N, low pressure syringe pump, Cetoni GmbH, Korbussen, Germany) and tubes with a diameter of 0.75 mm. The electronics for operating the piezoelectric transducer include a waveform generator (Series 333500B, Keyright, CA, USA) and a high wave 3.2 amplifier (Digitum Elektronik, Nurtingen, Germany). A camera (Toolcraft DigiMicro, Conrad Electronic, Hirschau, Germany) was used for imaging at the bifurcation of the microfluidic chip. In addition, the extended test environment included a laboratory spectrometer (photometer 4040v5+, Riele, Berlin, Germany) and a centrifuge (Universal 320 & Hematocrit Rotor, Hettich AG, Bach, Switzerland) to test the same samples in parallel. Thus, tests of the present plasmaphoresis chip can be evaluated and compared with the standard analysis (laboratory centrifuge).The microchips were tested with diluted porcine blood and liquor samples from six aSAH patients. The pig samples were diluted with phosphate buffered saline (PBS) to achieve the same hematocrit as the liquor sample, while the patient samples were not diluted. In order to remove any air inclusions, the entire system, i.e. the tubes and the microfluidic chip, is rinsed with the sample to be examined and the residues are collected in a container. After the first flushing of the system, the flow rate at the inlet is set to 60 μL / min and at the plasma outlet to -15 μL / min. At these flow rates, the apparatus could be operated for hours without any stability problems. The flow rates and division ratios could be increased at the expense of operating stability. At constant flow, the piezoelectric transducer is actuated, causing the erythrocytes and / or leukocytes to move toward the center of the channel. The input signal for the operation of the piezoelectric transducer was chosen as a sine wave having a frequency range of 1036-1050 kHz (half wavelength fitted in the channel width (λ / 2 mode) and a peak-to-peak amplitude of 28 V.The optimum operating point for the active blood particle separation device is determined by applying different voltages and frequencies to the piezoelectric transducer as well as different flow rates at the inlet and outlet. The resulting efficiency of focusing the blood particles is monitored. The separation of the blood particles is clearly made visible in a supplementary film still to be provided online by the applicant (OxyHbMeter FunctionalPrinciple), but this can also easily be concluded with the further description. In the supplemental film, the liquid flows from left to right and is separated as follows: wastes 96 (separated red blood cells) are extracted midway at the first outlet 62, and plasma or liquor 95 for liquor Hb detection is located in the two side arms 68.After all of the dead volume has been drained into the tubes, the plasma or liquor 95 is collected in the appropriate syringe. Operation of the system is continued for about 70 minutes until 1 ml of plasma or liquor 95 is collected in the plasma or liquor syringe. The collected plasma or liquor 95 is then analyzed with the spectrophotometer to determine the Hb concentration of the sample. Thereafter, the apparatus was purified with brine and ethanol to be reused for the next experiment.In the clinical environment, liquor samples from six patients 2 were analyzed, treated with a SAB and a hydrocephalus at the Neurocritic Care Unit of the University Hospital Zurich and required an external ventricular drainage 4. The study was approved by the Kanton Zurich, Switzerland local ethics commission, Approval Number 2021-01089. Written consent was granted by legal representatives, since all patients were unable to make judgments and the study was carried out in accordance with the declaration of Helsinki and their supplements. The liquor 95 was not taken directly from the patients 2 but in each case from a collecting bag 2 which contained the liquor 95 discharged in the last 2 to 3 hours.The separation efficiency and hemolysis induced by the separation of the microfluidic chip 60 were compared with the conventional centrifugation (prior art). The samples were centrifuged at 3600 RCF for 15 minutes and the separated liquor 95 was analyzed spectrophotometrically. The measured Hb values of the centrifuged sample served as a baseline to check the values of the sample separated with microfluidic chip 60. Five cuvette measurements were carried out for the spectrometer analysis of both separation methods.With the latest chip design and test setup, in vitro and clinical measurements were performed with diluted blood and liquor patient samples, respectively. These experiments were used to evaluate the separation efficiency and hemolysis induced by the separation of the microfluidic chip 60 as compared to conventional centrifugation.In a scientific paper to be published at present, results of the measurements are discussed in detail below, which are not relevant in any more detail for the present description at first. Nevertheless, the contents of this paper "OxyHbMeter - a novel bedside medical device for monitoring cell-free hemoglobin in the cerebrospinal fluid - proof of principles" are hereby incorporated by reference. Moreover, the above-mentioned study flanking the present property law demonstrates the basic feasibility and (industrial) applicability of the device 1 shown with the present description. The photographic representation shown with FIG. 9 shows the microfluidic chip 60 with the piezoelectric element 80 switched on, wherein the resonance frequency of the channel 64 is reached. The human sample erytroites 96 are concentrated in a narrow band at the center of the channel 64 and therefore exit only through the central outlet 62.The novel bedside monitoring system should allow continuous and non-invasive quantification of the liquor without the liquor drainage system having to be clipped or punctured. As compared to daily liquor sampling with manual processing of each sample, the OxyHbMeter would offer better user-friendliness, reduce the risk of infection and allow autonomous measurement of liquor Hb concentration. This method could improve reproducibility and be incorporated into an efficient warning system, for example by providing a biomarker for predicting DCI.In the tests, which are also the basis of the scientific publication, the flow rates were heuristically chosen in order to achieve a stable focusing of the particles during the entire extraction of plasma or liquor. The chip 60 used for this study had an optimum flow rate of 60 μL / min at the inlet and -15 μL / min at the liquor outlet, thereby balancing the particle concentration and yield at the plasma and liquor outlet and ensuring stable operation over hours. The effective flow rate was limited primarily by the length of the channel and the HCT value of the sample 95. Moreover, the focusing power in the channel could be controlled by the voltage applied to the piezoelectric transducer 80, but a higher voltage resulted in an elevated temperature of the device which damaged the cells. In this study we applied a peak-to-peak voltage of 28 V and always maintained the operating temperature below 30°C. In general, it would be possible to achieve higher flow rates by increasing the channel length or increasing the acoustic energy density in the channel by lateral driving or active cooling to increase the throughput and thus the yield at the liquor outlet 63 in clinical scenarios. The experimental setup was designed with a 45° inclination of the syringe pumps. As a result, the sedimentation of blood cells such as erythrocytes and / or leukocytes on the bottom of syringes could be delayed, enabling stable HTC in the sample 95 throughout the experiment.Processing the samples with microfluidic device 60 in our in vitro set-up took longer than centrifugation. In the future, however, this could result in more standardized liquor Hb measurements with fast and autonomous processing of the liquor 95. The samples no longer have to be sent to the laboratory for an indefinite period of time, and they are also no longer subjected to different centrifugation speeds. After the liquor 95 was separated with the microfluidic chip 60, the measured liquor Hb values were in a similar range to the measurements after centrifugation. There was little additional hemolysis induced by the device 1. However, a significant limitation of the clinical study so far made is the limited number of available clinical samples from aSAH patients.In the selected test environment, a lower HCT value in the sample 95 was more advantageous than a higher one, as a higher viscosity tends to plug the channel and make the separation more prone to errors. Residual contamination in the system could be another cause of measurement differences, although the chip 95 and all tubes were thoroughly cleaned before each experiment.The preliminary tests with the plasmapheresis chip 60 show that it is capable of continuously separating erythrocytes and / or leukocytes 96 from diluted blood and liquor samples 95, enabling standardized inline tests of biomarkers. The microfluidic chip 60 does not cause any additional hemolysis, in contrast to centrifugation, and the performance or the accuracy of the obtainable measurement results is absolutely comparable. The developed platform serves as a solid basis for the future development of a point-of-care device 1, as has already been explained in many details with the present description.In addition we present a platform technology suitable for several applications: First, the continuous measurement of the liquor Hb value at aSAH could promote our understanding of DCI, biosignal analysis and cognitive computing first in research and a second step in timely treatment. The data would be processed in real time and the results presented as a DCI prediction, prevention and decision assistance system. Comprehensive phenotypeization and advanced biosignal analysis will also contribute to a comprehensive understanding of the complex pathophysiology of DCI after aSAH. Liquor-Hb as biomarker for DCI could allow identifying high risk patients as a target group for researching new drugs, e.g., hemoglobin scavenger haptoglobin. Second, computed tomography (CT) is the diagnostic method of choice to diagnose subarachnoid hemorrhage in acute headache patients. If a CT examination is not performed in good time and the sensitivity is low several days after the beginning of headaches, the diagnosis may be missed. Lumbal puncture allows diagnosis of subarachnoid hemorrhage when xanthochromaticity is found in the supernatant of centrifuged liquor samples 95. Xanthochromatic activity serves to distinguish the increased erythrocyte count in the liquor of SAB from the increased erythrocyte count following traumatic lumbar puncture and is considered to be present when the absorption follows an oxyhemoglobin characteristic curve. False positive test results can only be avoided if the liquor 95 is centrifuged immediately and analyzed spectrophotometrically. A method which has been reserved up to now for highly specialized laboratory units, since the analytical methods require certified specialist staff. A POCT system could allow liquor spectrometry around the watch in the environment of an emergency room or intensive care unit. And third, not only the more frequent and standardized determination of the Liquor Hb value could benefit from the separation principle, but also other liquor analyses, such as cytology. The cellular composition of the liquor provides important first information about a broad spectrum of inflammatory diseases of the central nervous system. For cytometry, liquor samples must be immediately centrifuged and analyzed, ideally within one hour of collection.The principle of acoustic strophoresis is based on the generation of acoustic pressure in a microfluidic channel by a piezoelectric element. The acoustic pressure generates an acoustic radiation force on the particles. At a defined frequency, a standing wave is generated in the channel with the node in the center of the channel. The resonant frequency (f) depends on the channel geometry and the liquid properties. The wavelength (λ) is obtained from the channel width (D) and the selected resonance mode (k). In order to focus the particles in the middle of the channel along the channel width--which is exploited for the present application of the geometric separation of a constituent 96 from the body fluid 95--the first mode is used, in which half the wavelength fits into the channel width (k=1, λ / 2 mode). The frequency is dependent on the wavelength and the speed of sound (c0) in the liquid used:In a straight and rectangular microchannel environment, the acoustic wave can be approximated as a standing resonant pressure wave of the following shapeThe acoustic radiation force is the time-averaged force acting on particles suspended in a liquid which are exposed to a standing wave acoustic field. The force results from differences between the particle and the surrounding liquid, such as compressibility (κ), density (ρ) of the liquid and the particle, size of the particle, and frequency and acoustic energy density of the acoustic standing wave.The acoustic radiation potential, also called Grokov potential (U rad) is defined as:r p denotes the radius of the particle, while p p denotes the density, k p and c p denote the velocity of sound of the particle. p + 0, k 0 and c 0 denote the density, compressibility and velocity of sound of the fluid, respectively. p ∼ and k ∼ denote the relative density and compressibility, while 〈p_in^2 〉 and 〈v_in^2 〉 denote the time-averaged incident pressure and velocity square, respectively. f 1 is obtained from the mass flow in connection with the compressibility, while f 2 is determined from the translation movement. Based on the above terms and equations, the formula for the radiant acoustic force (F rad), which acts on a particle toward the acoustic pressure nodes of the standing wave field, is derived by taking the negative gradient of the Gor'kov potential:The magnitude and direction are dependent on the acoustic energy density E ac and the acoustic contrast factor φ, respectively for the liquid and particle, and are expressed as:In this equation, p a represents the pressure and v a represents the velocity amplitude. The contrast factor may result in a negative number. In this case, the particles are forced towards the pressure nodes and away from the pressure nodes. In our application, the blood cells have a positive acoustic contrast factor with respect to the liquid in which they are dissolved, i.e. the blood plasma and liquor, which enables us to focus them in the printing node and thus separate them.It will be apparent to those skilled in the art that the above-described embodiments are to be understood as exemplary and the invention is not limited thereto, but can be varied in many ways without departing from the scope of the claims. It will be further understood that the features, whether disclosed in the specification, claims, figures or otherwise, individually define essential components of the invention, even when collectively described with other features. In all figures, the same reference numerals represent the same objects, so that descriptions of objects, which may be mentioned only in one or at least not with respect to all figures, can also be transferred to these figures, with respect to which the object is not explicitly described in the description.List of reference characters1 Device 2 Body fluid source 4 Drainage 5 Interface, for example. Connecting line 8 Hose coupling 10 Base part 11 Solenoid valve, "normally closed" 12 Solenoid valve, "Normally open" 13 Air inlet 14 Air inlet filter 15 Air outlet 16 Outlet filter 17 First switching valve 18 Second switching valve 20 (external or arranged in the base part) Fluid pump 21 Switching pump 22 Air inlet 23 Inlet filter 24 Pressure sensor 25 Pressure accumulator 28 Pressure sensor 29 Pressure sensor 30 Switching outlet 31 Switching valve 32 Pressure connection in the base part 33 Control device 34 Control line 36 Air connection 37 Pressure connection in the base part 38 Second pressure connection in the base part 40 Fluidic module 41 Inflow line to the body fluid reservoir 42 Inflow line to the microfluidic chip 43 Inflow line to the measuring device 44 Inflow line from the measuring device to the residual material receiving volume 45 Inflow line from the microfluidic chip to the residual material receiving volume 48 Fluidic module housing 49 Housing passage 51 Hose coupling 52 Check valve in inflow line 53 Flow sensor 54 Liquid detection 55 Body fluid reservoir 56 Liquid level in the body fluid reservoir 57 Fill level sensor in the body fluid reservoir 58 Switching valve, e.g. solenoid valve 59 Check valve in front of microfluidic chip 60 Microfluidic chip 61 Inlet 62 First outlet opening 63 Second outlet opening 64 Inlet channel 65 Bifurcation 66 Wafer 67 First outlet channel 68 Second outlet channel 69 Flow rate sensor 70 Measuring device 72 Measuring volume 73 Switching valve, e.g. solenoid valve 74 Sensor, in particular optical sensor 75 Residual material intake volume 76 Fill level sensor in the residual material intake volume 79 Switching valve, For example, solenoid valve 80 separation device 82 pressure connection on or in fluidic module 83 second pressure connection on or in fluidic module 84 pressure connection line 85 measurement point in pressure connection line 86 switching connection 87 second switching connection 88 third switching connection 89 fourth switching connection 90 flushing device 92 switching device, switching valve, for example solenoid valve 93 evaluation module 94 storage module 95 body fluid 96 separated components of the body fluid 97 pump controller 98 wireless connection device 99 electrical supply device 100 method 110 introduction 115 detection of the body fluid in fluidic module 120 introduction of the body fluid 125 activation 130 influencing 135 onward conveying 140 measurement 150 disposal of the body fluid and / or of the components in the fluidic module

Claims

Device (1) configured to measure and / or influence a property of a body fluid (95), in particular liquor, provided in a fluidic module of the device, the device comprising the fluidic module (40), a reusable base part (10) configured or configured to receive the fluidic module on or in the base part, an interface (5, 51), in particular configured as a connecting hose (5) or a hose coupling (8), configured to connect the device to a body fluid source (2), in particular a patient, wherein the body fluid source comprises a body fluid that the body fluid can be guided into the fluidic module by means of the interface, a microfluidic chip (60) arranged on or in the fluidic module configured to influence the property of the body fluid.The device (1) according to the preceding claim, wherein the device is configured as a mobile device and / or as a point-of-care diagnostic device.The device (1) according to at least one of the preceding claims, wherein the property of the body fluid (95) is or comprises at least one of the following: the presence of foreign bodies or foreign bodies (96) in the body fluid, the presence of particles, suspended particles or cells (96) such as blood cells and / or blood serum proteins in the body fluid, the presence of hemoglobin or a derivative thereof in the body fluid and / or the bilirubin level in the body fluid.The device (1) according to at least one of the preceding claims, wherein the influencing of the property of the body fluid comprises the separation of particles, suspended particles or cells from the body fluid.The device (1) according to at least one of the preceding claims, further comprising a measuring device (70) arranged in or on the fluidic module (40) for determining the property of the body fluid (95).The device (1) according to the preceding claim, wherein the measuring device (70) is configured to detect or quantify hemoglobin or a derivative thereof in the body fluid (95).The device (1) according to one of the two preceding claims, wherein the measuring device (70) further comprises an optical sensor (74) arranged in or on the fluidic module (40), in particular a spectrophotometer.Device (1) according to at least one of the preceding claims, further comprising a body fluid storage container (55) arranged in or on the fluidic module (40), which is arranged in particular upstream of the microfluidic chip (60).The device (1) according to the preceding claim, wherein the body fluid reservoir (55) comprises a level sensor (57) or a level indicator.Device (1) according to at least one of the preceding claims, further comprising at least one switchable valve (58, 73, 79, 92), in particular a solenoid valve, in the fluidic module (40), in particular arranged downstream of the body fluid reservoir (55).The device (1) according to at least one of the preceding claims, further comprising a residue receiving volume (75) arranged in or on the fluidic module (40).The device (1) according to the preceding claim, wherein the residue receiving volume (75) comprises a reservoir.Device (1) according to at least one of claims 11 or 12, wherein the residue-receiving volume (75) is connected to the microfluidic chip (60), such that residues from the body fluid (95) can be discharged directly into the residue-receiving volume from the microfluidic chip.Device (1) according to at least one of Claims 11 to 13, wherein the residue-receiving volume (75) is connected to the measuring device (70) according to Claim 5, such that volumes of the body fluid (95) measured by the measuring device can be discharged into the residue-receiving volume.Device (1) according to at least one of claims 11 to 14, wherein the residue-receiving volume (75) comprises a fill level sensor (76) or a fill level display for displaying the fill level of the residue-receiving volume, so that, in particular when a maximum fill level is reached, information is output or the fluidic module (40) can be replaced by a new fluidic module.The device (1) according to at least one of the preceding claims, further comprising a flushing device (90) arranged in or on the fluidic module (40).Device (1) according to at least one of the preceding claims, further comprising a check valve arranged on the fluidic module (40) on the input side, in particular upstream of the body fluid storage container (55).The device (1) according to at least one of the preceding claims, wherein the microfluidic chip (60) has an inlet channel (64) and / or a bifurcation (65).The device (1) according to at least one of the preceding claims, wherein the microfluidic chip (60) has a separation device (80) for separating particles, particles or cells from the body fluid (95).The apparatus (1) according to at least one of the preceding claims, wherein the separation device (80) comprises at least one piezoelectric component, in particular a piezoelectric transducer.The apparatus (1) according to the preceding claim, wherein the separation device (80) is configured to provide a sound pressure, in particular for providing an akustophoresis.The device (1) according to at least one of the preceding claims, further comprising a gas bubble detection and / or separation device arranged upstream of the microfluidic chip (60) for identifying and / or separating gaseous constituents from the body fluid (95).Device (1) according to at least one of the preceding claims, wherein the interface (5, 51), in particular configured as the connecting tube, is configured for connection to an external ventricular drain (4).Device (1) according to at least one of the preceding claims, wherein the interface (5, 51), in particular configured as the connecting hose (5), is configured for direct connection to the fluidic module (40).Device (1) according to at least one of the preceding claims, wherein the fluidic module (40) is configured for connection to the interface (5, 51) or comprises the latter, wherein the interface is in particular configured as the connecting hose (5).The device (1) according to at least one of the preceding claims, wherein the fluidic module (40) comprises a hose coupling (51) for connecting to the connecting hose (5).The apparatus (1) of at least one of the preceding claims, further comprising a fluid detector (54) disposed on or in the fluidic module (40) configured to detect the presence of body fluid (95) in the fluidic module.Device (1) according to at least one of the preceding claims, the base part (10) comprising a pump (20) for providing an overpressure and / or an underpressure.Device (1) according to the preceding claim, configured such that the pump (20) can be connected to the fluidic module (40), such that an overpressure and / or an underpressure can be provided in the fluidic module.Device (1) according to at least one of claims 28 or 29, wherein the pump (20) is connectable to the fluidic module (40) by means of at least one pressure connection coupling (30, 37, 38).Device according to at least one of claims 28 or 30, wherein only exactly one pressure connection coupling (82) is provided on the fluidic module for connecting the pump (20) to the fluidic module (40), and by means of which a pressure connection coupling, in particular both overpressure and underpressure, can be output to the fluidic module.Device according to at least one of claims 28 to 31, wherein, for connecting the pump (20) to the fluidic module (40), a plurality of at least two pressure connection couplings (30, 37, 38, 82, 83, 86, 87, 88, 89) in each case is provided on the base part (10) and the fluidic module (40), so that in particular the negative pressure can be output to the fluidic module separately from the positive pressure.Device (1) according to at least one of the preceding claims, further comprising a control pressure connection clutch (30, 86, 87, 88, 89) for controlling a compressed air-controlled device in the fluidic module (40).Device (1) according to at least one of claims 28 to 33, wherein the overpressure and / or the underpressure can be used to influence a fluid flow in the fluidic module (40).Device (1) according to at least one of claims 28 to 34, wherein the body fluid (95) can be aspirated by means of negative pressure, in particular can be aspirated from a ventricular drain (4) or a body fluid source (2) into the body fluid storage container (55).Device (1) according to at least one of claims 28 to 35, wherein the body fluid can be conveyed further in the fluidic module (40) by means of overpressure, in particular from the body fluid storage container (55) to the microfluidic chip.Device (1) according to at least one of Claims 28 to 36, wherein the body fluid storage container (55) can be acted upon by the negative pressure and / or the positive pressure, such that the body fluid (95) can be conveyed from the connecting tube (5) into the body fluid storage container (55) by means of action of negative pressure and / or body fluid (95) stored in the body fluid storage container (55) can be conveyed in the direction of the microfluidic chip (60) by means of action of positive pressure.The device according to at least one of the preceding claims, wherein the base part (10) is further configured to house a control module (33) configured to control the further conveyance of the body fluid (95) in the fluidic module (40) and / or to control the measuring device (70), wherein control commands of the control module can be transmitted to the fluidic module via the at least one pressure connection and / or via electrical contacts.The device (1) according to at least one of the preceding claims, wherein the base part (10) is further configured to house an evaluation module (93) for evaluating the data obtained with the fluidic module (40), in particular the measuring device (70), and for providing a diagnostic result regarding the property of the body fluid (95).The device (1) according to at least one of the preceding claims, wherein the base part (10) is further configured to house a storage module (94) for storing the measurement data obtained with the fluidic module (40), so that in particular the measurement can be continued without gaps even when the fluidic module is exchanged.The device (1) according to at least one of the preceding claims, wherein the base part (10) is further configured to house a pump controller (97) for controlling the pump (20) arranged in the base module, wherein the pump controller is supplyable to the controller with sensor data from the fluidic module.The apparatus (1) of at least one of the preceding claims, wherein the base portion (10) is further configured to house a wireless connection device (98) for connection to, for example, a hospital network for communication therewith.The device (1) according to at least one of the preceding claims, wherein the base part (10) is further configured to house an electrical supply device (99) comprising a power connection and / or an energy store.Device (1) according to at least one of the preceding claims, wherein the base part (10), in particular with the control module (33) according to the preceding claim, is configured to close off the access in the event of a fault detection in the body fluid conveyance, i.e. in particular to act in response to the fluid detector (54) according to the preceding claim 27, and / or to act on a control valve arranged in the fluidic module (40) or on the ventricular drain (4) according to claim 23 for switching off the fluid flow.Device (1) according to at least one of the preceding claims, wherein the device is configured to carry out a method (100) for diagnosing a body fluid (95), in particular liquor, comprising the steps of introducing (110) the body fluid into a fluidic module (40), feeding (120) the body fluid to a microfluidic chip (60) arranged in or on the fluidic module for influencing a property of the body fluid, in particular for separating blood cells (96) from the body fluid, by means of the or in the microfluidic chip, forwarding (135) the body fluid to a measuring device (70) arranged in or on the fluidic module for determining the same or a further property of the body fluid, forwarding the body fluid from the measuring device and into a residue receiving volume (75) arranged in the fluidic module.The device (1) according to the preceding claim, further configured to carry out the following step: starting the conveying of the body fluid (95) in the fluidic module (40) as soon as a body fluid storage container (55) arranged in the fluidic module is sufficiently stored with the body fluid (95).Device (1) according to at least one of claims 45 or 46, wherein the steps of conveying the body fluid (95) are carried out by means of a feed pump (20) arranged in a base module (10).The device (1) according to at least one of claims 45 to 47, wherein the device is a mobile device and the method is a point-of-care diagnostic method.Fluidic module (40) for a device (1), in particular according to at least one of the preceding claims, the fluidic module comprising an interface (5, 51), in particular configured as a connecting hose (5) or a hose coupling (51), adapted for connecting the fluidic module to a body fluid source (2), in particular a patient, or a drain (4) such that the body fluid can be guided through the connecting hose or the hose coupling into the fluidic module, a microfluidic chip (60) arranged on or in the fluidic module, adapted for influencing a property of the body fluid.Microfluidic chip (60), in particular designed for use in a device (1) for measuring and / or influencing a property of a body fluid, the microfluidic chip having an inlet channel (64), a bifurcation (65), a first (62) and a second (63) outlet opening, a separation device (80) for separating a portion of the body fluid (95), in particular particles, particles or cells (96), in the region of the bifurcation from the body fluid, such that the portion of the body fluid can be fed to the first outlet opening and a purified body fluid can be fed to the second outlet opening.Microfluidic chip (60) according to the preceding claim, wherein the separation device (80) is configured to guide the portion of the body fluid (95), in particular by means of akustophoresis, into a central portion of the inlet channel (64), and wherein the purified body fluid escapes in a side region of the inlet channel, such that in the region of the bifurcation (65) and with the application of a fluid flow the portion of the body fluid is guided to the first outlet opening (62) and the purified body fluid is guided to the second outlet opening (63) of the microfluidic chip.Microfluidic chip (60) according to at least one of Claims 50 or 51, the separation device (80) comprising a piezoelectric transducer.The microfluidic chip (60) of at least one of claims 50 to 52, wherein the microfluidic chip comprises a glass wafer.

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