JP6081962B2 - Medical pump device - Google Patents

Description

  The present invention relates to medical pump devices, and more precisely to detecting malfunctions in medical pump devices.

  In particular, detection of malfunctions in medical devices is important because the life of a patient can depend on the proper functioning of the medical device. For example, in the case of an infusion pump, a potentially dangerous result caused by a failure is typically excessive or insufficient infusion of the drug into the patient.

  Examples of malfunctions include leaks, blockages, or the presence of air bubbles in the pumping line.

  A state-of-the-art device and method for detecting malfunctions in medical devices are disclosed in, for example, Patent Documents 1 to 3.

  When using certain drugs, such as insulin, detection of occlusion will be particularly important since it is known that catheters can be occluded in a very large number of environments. Any occlusion that has not been detected can result in insufficient delivery of insulin because the occlusion remains undetected for an extended period of time. Current occlusion detectors operate on the syringe driver piston and need to generate high pressure in the syringe before an occlusion is detected. Other occlusion detectors consist of a pressure sensor located on the patient's tube after the pump mechanism, which is less sensitive due to factors such as compliance of the line of the tube. If no obstruction is detected when the occlusion begins, the need to increase insulin levels increases the patient's plasma glucose concentration and causes a reprogramming of the pump that occurs when the occlusion is suddenly released, and more Many doses of insulin are administered rapidly and patients can be at serious risk.

US Patent Application Publication No. 2008/214979 European Patent No. 1762263 U.S. Pat. No. 7,104,763

  The present invention provides several other improvements over state-of-the-art apparatus and methods.

  In the present invention, malfunction detection is based on the measurement result of the pumping line pressure, and more precisely based on the measurement result of the pumping line pressure between the inlet and the outlet of the pump chamber.

  The above configuration provides higher sensitivity and the ability to detect several types of potential malfunctions.

Especially, the present invention is related to the medical pumping apparatus.

According to a preferred embodiment of the invention, the inlet and outlet of the pump device have passive valves. According to a preferred embodiment of the invention, the at least one valve can be further controlled externally.

Advantageously, but not limited to, within the scope of the invention, highly miniaturized infusion pumps are contemplated. This pump is a membrane pump with two passive valves and is formed using microelectromechanical system technology. Unlike infusion driven pumps, silicon micropumps, preferably micropumps, are made of silicon and require potential for more complex fluid passages and more precise control of delivery, but in the presence of particles It has a valve with a hard seat that can leak. Also advantageously, the pump is a micropump having a variable volume of the pump chamber, consisting of 10 nl to 10 μl.

  In a further preferred embodiment of the invention, a pressure sensor comprising a silicon film is used.

  In another advantageous embodiment of the invention, the pressure sensor is arranged between the pump chamber and the outlet. This arrangement handles other objectives such as detection of malfunction while more precisely controlling the occlusion (including the possibility of detecting directly at the onset of occlusion during any pumping cycle).

  According to another preferred embodiment of the invention, the system comprises a further pressure sensor.

This further pressure sensor can preferably be arranged after the outlet valve in the downstream line. Further, the pump device includes a flow restrictor in the downstream line. This additional pressure sensor is also positioned between the outlet valve and the flow restrictor.

  In some embodiments, the system further comprises a temperature sensor.

  The pressure sensor of the present invention can generally detect several types of malfunctions such as clogging, air bubbles, infusion line disconnection, etc. in a very short time, i.e. a few seconds, when the pump is operating. .

  Another object of the present invention is to accurately characterize and / or monitor the pump characteristics during the manufacturing cycle to prevent any potential malfunction during use.

  The goal is to guarantee the quality of each pump delivered to the patient for the manufacture of any medical device. In any of the above medical products, the use of liquid is generally the only way to detect pump malfunction. The above test is only possible if it takes a long time, requires considerable cost, and the entire fluid line is changed after the above test. For single-use products (such as disposable pumps), the fluid line cannot be changed and therefore it is not possible to test each of the pumps manufactured above due to liquid contamination during the test. It is. Therefore, a single sampling is run and the above test does not guarantee 100% quality control and is considered destructive to the pump.

  The present invention further provides a system and method for complete control of each pump produced without causing contamination of the pump. The above test is preferably realized using sanitized air and provides a detailed analysis of all important parameters and safety characteristics in a very short time of only a few seconds. This method is compatible with the above cost targets of disposable pumps that need to be very inexpensive to manufacture.

  The invention will be better understood in the following using the detailed description including the examples shown in the following figures.

1 shows a cross-sectional view of a micropump of a preferred embodiment of the present invention. Fig. 4 shows a possible process for pump function testing. Fig. 4 shows a possible process for pump function testing. Figure 5 shows another pressure characteristic of a functional test indicating dysfunction. Figure 3 shows typical pressure characteristics during an operating cycle. Fig. 4 illustrates the working cycle of one preferred embodiment. Figure 2 shows an air and water pumping cycle. Fig. 5 shows a typical development of outlet pressure characteristics when there is a blockage. Fig. 4 shows a typical development of inlet pressure characteristics when there is a blockage. It shows an example of monitoring the pressure at the outlet during blockage. It shows the pressure characteristics of the pump when there is a leak. Fig. 4 shows monitoring of pump accuracy when the flow rate is decreasing. It shows the relative change in viscosity for a temperature change of 1 ° C. The words “vertex” and “horizontal region” indicate the method used in the figure.

  The micropump 1 shown in FIG. 1 is very small and is a reciprocating membrane pump mechanism. The micropump 1 is made of silicon and glass using a technique called MEMS (micro electro mechanical system). The micropump 1 has an inlet control member, in this embodiment, an inlet valve 2, a pump member 3, a function detector 4 that can detect various defects in the system, and an outlet valve 5. The principle of the micropump is known, for example, in US Pat. No. 5,759,014.

  FIG. 1 shows a glass layer (blue) as a substrate 8, a silicon layer (purple) as a second plate 9 fastened to the substrate 8, and an upper plate fastened to the silicon plate 9. A pump is shown in which a second glass layer 10 (blue) is deposited, defining a pump chamber 11 having a volume.

  The pump member can be controlled and displaced by an actuator (not shown in the present specification) connected to the mesa unit 6. Furthermore, a passage 7 is present to connect the outlet valve 5 which is an outlet control member to an outlet port located on the opposite side of the pump.

Detector Principle In the pump 1, the pressure in the pump chamber is varied during the pumping cycle, such as operating speed, inlet pressure, outlet pressure, potential presence of bubble volume, valve characteristics and valve leakage rate. It varies depending on the factors.

  The purpose of the present invention is to monitor this pressure and analyze the contour from one stroke to another in order to detect potential malfunctions.

Integrated pressure sensor The pressure sensor 4 in the micropump 1 is made of a silicon film disposed between the pump chamber and the outlet of the pump. The pressure sensor 4 is located in a passage formed between the surface of the silicon layer of the micropump and the glass layer on the upper surface thereof. In addition, the pressure sensor 4 includes a set of strain sensing resistors in a Wheatstone bridge configuration on the membrane and utilizes the giant piezoresistive effect of silicon. The change in pressure induces membrane distortion and therefore the bridge cannot be balanced. The pressure sensor is designed to generate a signal that is linear with pressure within the typical pressure range of the pump.

  The fluid is in contact with the surface of the interconnect leads and the piezoelectric resistor. By using a further surface doping of the opposite polarity to that of the lead and the piezoelectric resistor, good electrical insulation of the bridge is ensured.

  In another preferred embodiment of the present invention, the pressure sensor includes an optical sensor. This sensor is preferably arranged on the outside of said fluid passage, which can measure the pressure between the two valves, one part contained in the pump path and the pressure inside the fluid passage. And at least some optical components. In another example, the optical detector can be placed completely inside the pump to measure the pressure between two valves in the fluid path. In another embodiment, the astigmatism element is located in the optical path, i.e. between the flexible membrane in the pump and the optical sensor. Any pressure change in the pump induces a change in the shape of the light beam caused by the displacement of the film, the change of the optical path, and the presence of this astigmatism element. The optical sensor preferably senses the shape of the light beam, for example by having a codrant photodetector.

Functional test The first step of the present invention that can be carried out with a pump is, for example, a functional test of the pump at the manufacturing level.

  Although known functional tests using water last for several hours and are considered harmful, functional tests using the pump of the present invention can be performed in seconds using only gas. This uses a small dead volume of the pump for this test and the integrated pressure sensor described above.

The principle of this functional test process is as follows.
Excessive pressure is generated inside the pump with the actuator, and the user monitors the pressure decay in the pump chamber, which directly indicates the leak rate. Maximum pressure is related to pump compression ratio and self-priming capability. The user can also withdraw the valve pretension during a typical operating cycle.

  To generate a high pressure in the pump chamber, the user can control the outlet valve, for example pneumatically, to keep the outlet valve closed during compression as shown in FIGS.

In particular, FIGS. 2 and 3 show a functional test of the pump according to the invention (FIG. 2 shows a schematic process and FIG. 3 shows the corresponding pressure characteristics).
During this test, the user monitors the detector signal by:
A zero pressure indicates the rest position of the membrane.
The peak of pressure indicates the compression ratio of the micropump,
Pressure decay indicates the leakage rate of the valve
The pressure in step 3 indicates the pretension of the outlet valve,
The pressure in step 4 indicates the pretension of the inlet valve.

  As illustrated (eg, in a continuous position in FIG. 2), the above test is initiated from a standby position. Initially, a pulling step of “inhaling” gas from the inlet valve 2 into the chamber is performed by movement of the membrane 3.

  This is followed by a pushing step to empty the chamber with gas and the outlet valve 5 is open. In the next step, the outlet valve 5 closes again and a further pulling step is carried out on the membrane 3, then in the next step the user opens the outlet valve 5 to relax the pressure in the chamber.

  Finally, the outlet valve 5 is closed and the user performs a pushing step corresponding to the compression step with the membrane 3. At this time, the chamber is under high pressure, and the pressure decay (see FIG. 3) indicates the leakage rate of the valve.

  The sensitivity of the above method is very high due to the high pressure generated and the associated minute volume.

  Direct correlation between compression ratio and stroke volume SV if the dead volume DV is assumed not to change too much by appropriate process control (eg microelectromechanical system technology) during the initial manufacture of the pump Is found.

  FIG. 4 shows pressure characteristics when there is a defect in the functional test.

  In this case, the pump inlet valve is joined (maintained closed) and there is also a leak. These problems with the inlet valve can be derived by the large pressurization that occurs during the pushing motion of the pump and the decrease in pressure decay after each actuation. Leakage is indicated by pressure decay at the end of the high compression step at the end of the test cycle.

  Same during pump operation when fluid from a drug reservoir located in front of the first valve (eg at the end of the reservoir) is depleted, especially when using a soft reservoir that is closed without vents Results are obtained.

In-line malfunction detection As noted above, the pressure in the pump chamber during fluid operation is not limited to inlet pressure or outlet pressure, operating characteristics, but also valve tightness, actual stroke volume, or valve pre- Depends on various functional and / or external parameters such as micropump characteristics such as tension.

  A typical pressure profile during an operating cycle with liquid is shown in FIG.

  This change in properties can be caused by pump malfunction, inlet or outlet pressure (eg, due to poor ventilation, under or excessive pressure in the liquid reservoir located in front of the inlet valve, or obstruction after the outlet valve). Indicates an increase or decrease.

  In particular, the position of the horizontal zone immediately after the first peak of pressure measured in the pump chamber directly indicates the pressure at the outlet of the pump after the outlet valve. After the second apex, the user gets a direct indication of the pressure at the inlet, before the inlet valve. Due to the tightness of the valve and / or the presence of bubbles, changes in the amplitude between the vertices and the width of the vertices are induced. Analysis of the pressure decay after each peak of pressure indicates the leak rate of the valve.

  The displacement of the membrane of one embodiment of the present invention during the normal operating cycle of the pump is shown in FIG.

  According to the exemplary embodiment described above, the actuation cycle is initiated by a first pushing motion of the membrane, resulting in an increase in pressure, opening of the outlet valve and draining of liquid. The operating cycle is followed by a full stroke to fill the pump (negative peak of pressure during pump filling), then the pumping membrane is released and therefore returns to its standby position, Trigger a second positive vertex.

  As mentioned above, the gradual change in pressure within the pump chamber is directly dependent on the operating characteristics of the membrane.

  For example, it is possible to have a cycle starting with a full stroke, resulting from a full pulling movement, followed by a full pushing movement. The above cycle is typically useful during high speed operation of the pump, eg, during bolus administration. In a similar operation, only two vertices can be measured, the first negative vertex and the positive vertex. This analysis can be correlated with operating characteristics, which results in the detection of the same type of malfunction.

As a result, the following features can always be measured during the pumping cycle using the pressure signal from the sensor located between the two valves, directly indicating the following characteristics:
1. The position of the horizontal region immediately after the positive apex (+) of the pressure depends on the pretension of the outlet valve and the pressure at the pump outlet after the outlet valve.
2. The position of the horizontal region immediately after the negative peak of pressure (-) depends on the pre-tension of the inlet valve and the pressure at the pump inlet before the inlet valve.
3. Valve tightness and hence leakage correlates with decay with time of pressure after each apex.
4. The relative position of the two horizontal regions also correlates directly with the leak rate.
5). The height and width of the apex of pressure (positive or negative) correlates with the presence of air in the pump.

Priming and air detection Pump priming can also be monitored. A significant difference in the signals monitored while pumping air and water is shown in FIG.

  As mentioned above, the pressure peak is corrected by the presence of air in the pump.

Hereinafter, the detection of air can be verified by:
1) Monitor the height of the top of the pressure, which can be a warning at a predetermined threshold,
2) Monitor the width of the peak of pressure, which can be a warning at a given threshold,
3) Monitor the height and width (e.g., via signal integration), which is the established warning threshold.

Outlet Pressure Monitoring FIG. 8 shows a typical development of pressure characteristics during operation when there is pressure at the outlet of the pump after the outlet valve.

Inlet Pressure Monitoring FIG. 9 is a graph similar to FIG. 8 showing a typical development of pressure characteristics during operation when there is pressure at the inlet.

  Thus, accurate monitoring of both inlet pressure and outlet pressure is obtained during the operating cycle.

  If the reservoir is, for example, a soft reservoir with no vents, monitoring of the inlet pressure can help detect that the drug reservoir is empty.

Blockage detection By monitoring the outlet pressure, blockage can be detected as shown in FIG.

  There are several ways to analyze the curve reproduced in FIG. 10 during occlusion. For example, the pressure transition can be simply observed after each push motion.

The blockage can be detected as follows.
1) Typically, when the position of the horizontal area (+) is equal to the initial height of the vertex (+), the position of the horizontal area (+) and the established warning threshold are monitored.
2) Monitor the warning threshold and the height and width of the vertex (+).

  Since the pressure measurement in the pump is performed in the fluid path and in correlation with other measurements that indicate other potential malfunctions, the pressure measurement in the pump can cause a very high blockage. It is detected accurately and precisely. Therefore, the measured result value can correlate to true occlusion or fluid restriction outside the pump and prevent the patient from being informed of the need to check the infusion line or change the injection site.

Leak Detection FIG. 11 shows the pressure characteristics of the pump when there is a leak. After each actuation, the pressure relaxes very quickly to the external pressure. If there is a leak, the pressure should relax to the valve pretension, expressed in units of pressure.

  Therefore, leakage can be detected by the detection method of the present invention while preventing free flow by the pretension of the valve.

According to the notation shown in FIG. 14, leakage can be detected by the following.
1) Monitor the relative position of the horizontal (+) and horizontal (-) and the established warning threshold.
2) Monitor the pressure lag after each apex of pressure and a confirmed warning, typically using a time constant.

Monitoring pump accuracy for closed loop applications, for example with insulin According to the present invention, the user can detect defects such as valve leaks and bubbles that can implement pump accuracy within accuracy specifications.

  FIG. 12 shows an example of the pump signal showing nominal stroke volume and the detector signal of the same pump with particles implementing 15% pumping accuracy. The leakage induced by these particles can be easily detected by analyzing the level difference before and after the large negative apex.

  This feature allows for closed loop applications by connecting a micropump to a glucometer with control of insulin delivery accuracy via a detector.

Here, detection is similar to leak detection, but the only focus is leaks that affect accuracy.
1) Typically, the relative position of the horizontal (+) and horizontal (-) and fixed when their positions are equal after a typical time constant immediately following the vertex (+) and vertex (-) Monitor the warning threshold.
2) Monitor pressure delays after each peak of pressure and established warnings, typically using time constants.

  In the absence of precise monitoring of the pump accuracy, any of the above closed-loop systems will depend on the measured parameters (in the above case, for example, blood glucose level in the plasma or subcutaneous region) without considering changes in pump delivery. Or continuously monitoring interstitial fluid), eg, increasing or decreasing the dose of insulin. For closed-loop systems, it is most important to ensure that the pumping parameters are well understood and controlled over time to prevent any false compensation that may be related to the pump mechanism and not related to patient characteristics. is there. In particular, over-infusion of insulin due to increased glucose readings can potentially put patients at risk when associated with an unknown defective pump or infusion set. This is especially true when glucose readings indicate glucose plasma levels within a 10-30 minute delay. In the above case, a defective pump will cause the patient's condition to be misinterpreted, while pump behavior (e.g., infusion line occlusion) may be avoided to prevent endangering the patient due to the misinterpretation. Any modification of removal or modification of pumping characteristics is not detected over time.

Infusion Line Disconnection Detection In some instances, the infusion line is disconnected from the pump and a leak can occur between the pump outlet and the infusion line connector. Leakage can also be present when the user connects an unapproved infusion line to the pump outlet. Thereby, the fluid resistance is lowered at the outlet of the pump due to the leakage. A small decrease in pressure at the pump outlet when leakage is significant can be detected by using an integrated detector or by placing a second pressure sensor in the micropump and after the outlet valve. . The sensitivity of this sensor must be adapted to the pressure loss of the injection line in standard conditions.

  Since the pressure drop in the injection line is directly proportional to the flow rate, a high instantaneous flow rate of the pump due to the pump's functional principle is very favorable.

  If necessary, preferably before the patient is connected (eg during pump priming), during the draining of the liquid during pump setting, for example by creating a stroke at a faster rate, the infusion line Specific tests of airtightness can be performed.

A further pressure sensor main detector at the outlet of the pump is arranged in the pump chamber.
As long as the pump system is well ventilated, its reference port is in communication with the air space within the pump system housing, which is at atmospheric pressure. This sensor is also an associated pressure sensor. It may be useful to obtain information about patient pressure by placing additional pressure sensors after the outlet valve.

  This additional pressure sensor is directly related to the patient's pressure. Two pressure sensors, the main pressure sensor that measures the pressure in the pump chamber and the pressure sensor that measures the pressure after the outlet valve, should have the same reference port pressure. Comparing the development of the two signals after the stroke is either a leak in the pump at the valve seat, or a leak between the pump outlet port and the patient (typically due to a poor connection of the patient set). Useful for detection. This is described in further detail herein.

  Furthermore, the pressure difference between the two sensors immediately after the stroke, that is, when there is no flow rate, also shows good airtightness of the outlet valve.

  This additional sensor can also be used to detect abnormal pressures at the outlet port, including blockage of the infusion set.

  This additional sensor can also be calibrated during functional manufacturing tests using the gases described herein above, if desired.

  This additional pressure sensor can be easily integrated into the pump chip by designing a second membrane for pressure measurement. This pressure can be measured by using a strain gauge in a Wheatstone bridge configuration used as another pressure sensor in the pump. Ideally, the injection dose for the strain gauge is equivalent to that of the main detector in the pump. Therefore, the user can adjust the sensitivity as needed by simply modifying the dimensions of the membrane rather than the dose itself.

  The fluid path between the pump outlet valve and the patient set should preferably be made so as not to trap air during the initial pump priming.

Implementation of a temperature sensor for better leakage and monitoring accuracy using an additional pressure sensor In this chapter, the reliability during analysis of the second detection signal is described.

  As described above, the width and height of the apex of pressure can be used to obtain information regarding the tightness of the downstream line between the pump and the patient. The user can also propose qualitative criteria for these different features.

Furthermore, the integral of the pressure versus time curve is theoretically proportional to the flow rate for a given fluid resistance. This change in integration is a good indication of malfunction, including temperature changes as well as bubbles and leakage.
P (t) −P (patient) = Rf × Q (t)
Where Rf is the fluid resistance between the additional pressure sensor and the patient, Q (t) is the instantaneous flow rate, and P (t) is the pressure measured by the additional sensor.
Laminar flow is considered and Rf is given by Poiseuille's law.
P (patient) is the pressure of the patient and is also the pressure measured by a further sensor after the flow has disappeared.

  This sensor also provides good pump accuracy because it directly accesses the change in flow over time. Of course, in a given pumping system with an infusion set, the fluid resistance varies with temperature by solving for fluid viscosity (Poiseuille's law). Ideally, this pressure sensor is also coupled to a temperature sensor.

  If a fluid such as water is used, the change in viscosity with temperature is known and the signal can be corrected so that it is not temperature dependent. Detection of malfunctions becomes more reliable.

  Even if the temperature sensor is not strictly necessary due to the small dimensions of the pump components and good heat conduction, the temperature sensor can be placed in the pump, for example in contact with the fluid.

  The thermal sensor may be a simple thermal resistor (RTD or resistance temperature detector) that exhibits good sensitivity between 5 and 40 ° C. The Wheatstone bridge of the pressure sensor also exhibits a similar temperature dependence and can serve this purpose. The thermocouple can also be integrated into the pumping unit. Finally, a semiconductor temperature sensor based on the basic temperature and current characteristics of a diode or transistor can be used.

  If two identical transistors are operated at different but constant collector current densities, the base-emitter voltage difference is proportional to the absolute temperature of the transistors. This voltage difference is converted into a single-ended voltage or current. An offset may be applied to convert the signal from absolute temperature to Celsius or Fahrenheit temperature.

  FIG. 13 shows the relative change in viscosity for a 1 ° C. temperature change. The fluid resistance varies linearly with viscosity, allowing direct access to the flow rate accuracy that can be expected as a 1 ° C temperature sensor resolution. At 5 ° C., the maximum error induced by the temperature sensor for flow accuracy is 2.8%. The temperature sensor can also be designed to induce an error that is lower than the accuracy target for flow rate.

  The combination of outlet pressure sensor and temperature sensor can be used as a sophisticated and related pulsed flow sensor that is efficient due to the small response time of the pressure sensor.

Absolute flow meter For absolute flow measurement, the fluid resistance between the additional pressure sensor and the patient should be known to have good accuracy. The patient set shows a typically large change in fluid resistance from one batch to another as compared to the fluid resistance of the passage in the micropump. Care should also be taken to keep the patient set's fluid resistance very low compared to the fluid resistance of the outlet passage in the micropump.

  The above-described fluid resistance Rf can be controlled with an accuracy compatible with absolute flow measurement.

  From the above description, fluid measurement is valid as long as the fluid resistance of the patient set is small, i.e., there is no blockage of the fluid line.

  The flow rate at the outlet of the micropump is measured. Any leakage after an additional pressure sensor (such as a connector) induces a change in the signal shape of both detectors, but the fluid measurement remains accurate.

  Fluid monitoring is also a very powerful feature, but information from both detectors is required for accurate interpretation of flow data.

During further pressure sensor calibration it is also possible to calibrate the integral of the pressure signal proportional to the flow rate (typically by using a commercial flow meter placed in series with the pump outlet). is there. Here, care must be taken not to cause a large fluid resistance at the outlet during the test.

  Naturally, the invention is not limited to the examples described and illustrated above, but extends to any embodiment belonging to the claims.

Claims (15)

In a medical pump device having a pump,
The pump is
A pump chamber having a variable volume;
An inlet communicating with the pump chamber and provided with an inlet valve;
An outlet communicating with the pump chamber and provided with a valve;
An actuator suitable for changing the variable volume of the pump chamber;
A fluid passage comprising the inlet, the pump chamber, the outlet, and a downstream line located downstream of the outlet valve;
A pressure sensor (4) for measuring the pressure between the inlet valve and the outlet valve of the fluid passageway;
Processing means for analyzing the pressure signal of the pressure sensor,
The medical pump device wherein the processing means analyzes the pressure signal during an operating cycle comprising two partial movements of the actuator separated by a total movement of the actuator. The medical pump device of claim 1, wherein the pressure sensor is structurally designed to be used to detect a blockage in the downstream line. The medical pump device according to claim 1, wherein the pump is a micropump having the variable volume of the pump chamber, the pump being composed of 10 nl to 10 μl. The medical pump device comprises a pumping membrane, operatively connected to the actuator, suitable for changing the variable volume of the pump chamber,
The medical pump device according to claim 1, wherein at least one of the inlet valve and the outlet valve is a check valve. The medical pump device according to claim 1, wherein at least one valve opens or closes at a predetermined pressure threshold. The medical pump device according to claim 1, wherein the at least one valve can be further controlled from the outside. The medical pump device according to claim 1, wherein the pressure sensor includes a flexible membrane. The medical pump device according to claim 4, wherein the pumping membrane (3) is made of a semiconductor material and a strain gauge is embedded or arranged in the pumping membrane (3). 5. The medical pump device according to claim 4, comprising an optical sensor suitable for monitoring the deflection of the pumping membrane (3). The medical pump device according to claim 9, comprising an astigmatism optical element between the pumping film (3) and the optical sensor. The medical pump device according to claim 1, comprising at least one further pressure sensor. The medical pump device of claim 11, wherein the additional pressure sensor is positioned in the downstream line. The medical pump device according to claim 11, further comprising a flow restrictor in the downstream line. The medical pump device of claim 13, wherein the additional pressure sensor is positioned between the outlet valve and the flow restrictor. The medical pump device according to claim 1, further comprising a temperature sensor.

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