US20070261496A1 - Pressure sensing - Google Patents

Pressure sensing Download PDF

Info

Publication number
US20070261496A1
US20070261496A1 US11/808,287 US80828707A US2007261496A1 US 20070261496 A1 US20070261496 A1 US 20070261496A1 US 80828707 A US80828707 A US 80828707A US 2007261496 A1 US2007261496 A1 US 2007261496A1
Authority
US
United States
Prior art keywords
inductor
capacitor
pressure
sensor
compressible wall
Prior art date
Legal status (The legal status is an assumption and is not a legal conclusion. Google has not performed a legal analysis and makes no representation as to the accuracy of the status listed.)
Abandoned
Application number
US11/808,287
Inventor
Lennart Jonsson
Johan Drott
Thomas Hertz
Current Assignee (The listed assignees may be inaccurate. Google has not performed a legal analysis and makes no representation or warranty as to the accuracy of the list.)
Gambro Lundia AB
Original Assignee
Gambro Lundia AB
Priority date (The priority date is an assumption and is not a legal conclusion. Google has not performed a legal analysis and makes no representation as to the accuracy of the date listed.)
Filing date
Publication date
Priority to US54420504P priority Critical
Priority to SE0400330A priority patent/SE0400330D0/en
Priority to SE0400330-7 priority
Priority to US10/589,353 priority patent/US7771380B2/en
Priority to PCT/SE2005/000184 priority patent/WO2005077262A1/en
Application filed by Gambro Lundia AB filed Critical Gambro Lundia AB
Priority to US11/808,287 priority patent/US20070261496A1/en
Publication of US20070261496A1 publication Critical patent/US20070261496A1/en
Assigned to CITICORP TRUSTEE COMPANY LIMITED reassignment CITICORP TRUSTEE COMPANY LIMITED IP SECURITY AGREEMENT SUPPLEMENT Assignors: GAMBRO LUNDIA AB
Assigned to GAMBRO LUNDIA AB reassignment GAMBRO LUNDIA AB RELEASE OF SECURITY INTEREST IN PATENTS Assignors: CITICORP TRUSTEE COMPANY LIMITED, AS SECURITY AGENT
Application status is Abandoned legal-status Critical

Links

Images

Classifications

    • AHUMAN NECESSITIES
    • A61MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61MDEVICES FOR INTRODUCING MEDIA INTO, OR ONTO, THE BODY; DEVICES FOR TRANSDUCING BODY MEDIA OR FOR TAKING MEDIA FROM THE BODY; DEVICES FOR PRODUCING OR ENDING SLEEP OR STUPOR
    • A61M1/00Suction or pumping devices for medical purposes; Devices for carrying-off, for treatment of, or for carrying-over, body-liquids; Drainage systems
    • A61M1/36Other treatment of blood in a by-pass of the natural circulatory system, e.g. temperature adaptation, irradiation ; Extra-corporeal blood circuits
    • A61M1/3621Extra-corporeal blood circuits
    • A61M1/3639Blood pressure control, pressure transducers specially adapted therefor
    • AHUMAN NECESSITIES
    • A61MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61MDEVICES FOR INTRODUCING MEDIA INTO, OR ONTO, THE BODY; DEVICES FOR TRANSDUCING BODY MEDIA OR FOR TAKING MEDIA FROM THE BODY; DEVICES FOR PRODUCING OR ENDING SLEEP OR STUPOR
    • A61M2205/00General characteristics of the apparatus
    • A61M2205/12General characteristics of the apparatus with interchangeable cassettes forming partially or totally the fluid circuit
    • AHUMAN NECESSITIES
    • A61MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61MDEVICES FOR INTRODUCING MEDIA INTO, OR ONTO, THE BODY; DEVICES FOR TRANSDUCING BODY MEDIA OR FOR TAKING MEDIA FROM THE BODY; DEVICES FOR PRODUCING OR ENDING SLEEP OR STUPOR
    • A61M2205/00General characteristics of the apparatus
    • A61M2205/35Communication
    • A61M2205/3546Range
    • A61M2205/3569Range sublocal, e.g. between console and disposable
    • YGENERAL TAGGING OF NEW TECHNOLOGICAL DEVELOPMENTS; GENERAL TAGGING OF CROSS-SECTIONAL TECHNOLOGIES SPANNING OVER SEVERAL SECTIONS OF THE IPC; TECHNICAL SUBJECTS COVERED BY FORMER USPC CROSS-REFERENCE ART COLLECTIONS [XRACs] AND DIGESTS
    • Y10TECHNICAL SUBJECTS COVERED BY FORMER USPC
    • Y10TTECHNICAL SUBJECTS COVERED BY FORMER US CLASSIFICATION
    • Y10T29/00Metal working
    • Y10T29/49Method of mechanical manufacture
    • Y10T29/49002Electrical device making
    • Y10T29/49117Conductor or circuit manufacturing

Abstract

A biological fluid device comprises a pressure sensor, which is arranged on the device. The pressure sensor comprises a compressible container, the compression of which is indicative of the pressure, and is capable of wireless communication.

Description

    TECHNICAL FIELD
  • The present invention relates to management of fluids used in a medical procedure and more specifically to pressure sensing in a biological fluid.
  • BACKGROUND
  • There are a number of procedures in which biological fluids such as blood, blood components as well as mixtures of blood or blood components with other fluids as well as any other liquid comprising biological cells, are managed. Examples of such procedures include treatments where blood is taken out in an extracorporeal blood circuit. Such treatments involve, for example, hemodialysis, hemofiltration, hemodiafiltration, plasmapheresis, blood component separation, blood oxygenation, etc. Normally, blood is removed from a blood vessel at a blood access and returned to the same blood vessel. During these procedures it is often desirable and also important to monitor the pressure in the biological fluid system.
  • U.S. patent application 20020007137 describes a prior art dialysis pressure sensing system wherein the pressure in an extracorporeal blood circuit is measured with an ordinary pressure transducer.
  • Typically, when performing pressure sensing using arrangements according to prior art, the extracorporeal blood circuit is connected to a patient and a dialysis machine. The pressure sensor is located within the dialysis machine and operably and structurally connected to the extracorporeal blood circuit.
  • Even though the extracorporeal blood circuit typically is in the form of a disposable arrangement there is a risk of cross contamination between patients. Between the pressure sensor in the dialysis machine and the blood in the disposable extracorporeal circuit is arranged an air column in a connector line/column. The air column exerts a backpressure on the blood, thereby preventing blood from getting in contact with the pressure sensor/machine. The dialysis machine normally comprises pumps of roller type creating a pulsating flow of blood in such a way that blood is penetrating into the connector line to some extent. In case the blood flow is blocked there is a potential risk that the backpressure exerted on the blood by the air column in the connector line is overcome and that blood reach a protective filter, protecting the pressure sensor. In such a case, cross contamination could occur if this situation reoccurs with another patient connected to the machine and the machine has not been cleaned properly. Also there is a potential risk that bacteria could grow in blood residuals at the protective filter.
  • Another problem is that of leakage, which may occur due to operator mistakes during set-up of the system. Needless to say, leakage could be of danger to an operator of the system in case contaminated blood is present in the system. Leakage may also lead to erroneous or less accurate pressure measurements.
  • International patent application with publication number WO 02/22187 discloses a blood pump having a disposable blood passage cartridge with integrated pressure sensors. Signal wires convey information from pressure transducers to a controller.
  • Hence, electrical contact problems may occur due to presence of spillage (or contamination) of fluids such as blood as well as contamination of particles such as salt crystals and burrs. Moreover electric connector means imply that there exist edges, indentations, protrusions etc. in the vicinity of means for transporting fluids, which typically enhances the risk of spillage (or contamination) of fluids as well as particles collecting in the area of the connector means. Needless to say, electrical connectors open to touch by operator, may also constitute an added risk of an operator being subject to electric shock.
  • Moreover, electric wiring and connectors that are needed for transmission of pressure information from pressure sensors according to prior art are unnecessarily complicated and adds to the risk of mistakes during use.
  • Thus, there is a general problem of how to provide a disposable fluid arrangement which is electrically safe, avoids risks relating to accumulation of spillage (or contamination) of fluids as well as particles, is easy to set-up, avoid leakage and which reduces the risk of cross contamination between patients and/or operators of the system.
  • SUMMARY OF THE INVENTION
  • An object of the present invention is to provide a system capable of overcoming problems related to prior art systems.
  • The object of the present invention is achieved in different aspects by way of a device, a use of a device, a system, a use of a system and a method according to the appended claims.
  • An inventive device for transporting biological fluid in at least a part of an extracorporeal circuit, where at least part of the extracorporeal circuit is disposable and comprises at least one pressure sensor configured to be in fluid communication with the biological fluid during use, is characterized in that the at least one pressure sensor is configured for sensing a difference between a pressure of the biological fluid and a reference pressure and comprises an electric circuit that is configured to be energized by an applied alternating first electromagnetic field and configured to communicate information indicative of a pressure from the pressure sensor via a second alternating electromagnetic field.
  • In an embodiment, the first and second alternating electromagnetic fields are one and the same electromagnetic field and also in an embodiment, the first and second alternating electromagnetic fields are in the radio frequency range.
  • In an embodiment, the sensor comprises a compressible container, the compression or expansion of which is indicative of the pressure. Preferably, the container is open, i.e. configured with an opening or passage etc., to introduce atmospheric pressure into the container.
  • According to an embodiment of the present invention the pressure sensor may include components in the form of a capacitance and/or an inductance, of which components at least one is a variable component which varies with the relative compression and/or expansion of the container, said capacitance and/or inductance being part of a resonance circuit.
  • By having such a sensor it is possible to measure, in a wireless manner, the magnitude of the variable component by measuring the resonance frequency. This is advantageous in that it avoids the drawbacks related to prior art devices as discussed above. Thus, either the variable capacitance or the variable inductance is measured. From earlier measurements, i.e. calibration measurements, of the variable components dependence of the pressure the pressure may be determined.
  • Although it is preferred that the container is open, it is feasible that in some embodiments the compressible container may include a gas such as air at any known pressure, i.e. a reference pressure in a closed container. Thereby the container may have a known fixed pressure therein, so as to have a reference.
  • The sensor may be tailored to have any predetermined resonance frequency in an unaffected state. This may be used in an identification procedure by way of radio frequency measurements, in order to provide for identifying between different disposables used in different applications, such as dialyser, cassette, bloodline, ultrafilter, tube, connector, container, chamber, fluid bag, blood bag, collection bags, pump segment part of lineset, oxygenator etc.
  • A system for managing biological fluids according to the invention comprises a device with at least one pressure sensor as discussed above, at least one transmitter configured to transmit an alternating electromagnetic field to the at least one sensor in the device, at least one receiver configured to receive radio frequency information from the device, wherein the received information is indicative of at least one pressure sensed by the device, and a control unit configured to control the transmitter and the receiver. In an embodiment, the at least one sensor is located in close proximity, e.g. 5 to 40 mm, to the at least one transmitter and the at least one receiver.
  • An advantage of the invention is that, by disposing with the need for structurally connecting a pressure sensor to an extracorporeal blood circuit, thereby minimizing the air-blood interface, risks of cross contamination between patients and/or operators are avoided.
  • Another advantage is that it is easy to set-up and thereby avoiding risks of leakage, which may be dangerous to an operator of the system.
  • Yet another advantage of the present invention is that it provides an integrated pressure sensor which is sufficiently inexpensive to allow each device to be disposed of after each use.
  • The above aspects may be separate or combined in the same embodiment. Embodiments of the present invention will now be described with reference to the accompanying drawings.
  • BRIEF DESCRIPTION OF THE DRAWINGS
  • FIG. 1 shows schematically an extracorporeal blood circuit connected to a patient.
  • FIG. 2 shows schematically an extracorporeal blood circuit comprising a device according to an embodiment of the present invention.
  • FIG. 3 shows schematically a part of an extracorporeal blood circuit comprising a device with a sensor according to an embodiment of the present invention.
  • FIG. 4 shows part of FIG. 3 in larger scale.
  • FIGS. 5 a-5 e show schematically a device comprising a pressure sensor.
  • FIGS. 6 a and 6 b show a tube mounted pressure sensor according to an embodiment of the present invention.
  • FIG. 6 c shows a tube mounted pressure sensor according to an embodiment of the present invention.
  • FIGS. 7 a and 7 b show a system according to the present invention.
  • FIGS. 8 a-8 c show a respective system according to the present invention.
  • DESCRIPTION OF EMBODIMENTS
  • The invention will be described initially by way of illustration of an extracorporeal blood circuit during the process of dialysis followed by a description of pressure sensors and concluding with a description of a system comprising a blood circuit, pressure sensors, a transmitter and a receiver.
  • FIG. 1 discloses a forearm 1 of a human patient. The forearm comprises an artery 2, in this case the radial artery, and a vein 3, in this case the cephalic vein. Openings are surgically created in the artery 2 and the vein 3 and the openings are connected to form a fistula 4, in which the arterial blood flow is cross-circuited to the vein. Due to the fistula, the blood flow through the artery and vein is increased and the vein forms a thickened area downstream of the connecting openings. When the fistula has matured after a few months the vein is thicker and may be punctured repeatedly. Normally, the thickened vein area is called a fistula. As the skilled person will realize, an artificial vein may also be used.
  • An arterial needle 5 is placed in the fistula, in the enlarged vein close to the connected openings and a venous needle 6 is placed downstream of the arterial needle, normally at least five centimeters downstream thereof.
  • The needles are connected to a tube system 7 shown in FIG. 2, forming an extracorporeal circuit comprising a blood pump 8, such as may be found in a dialysis circuit. The blood pump transfers blood from the blood vessel, through the arterial needle, the extracorporeal circuit, the venous needle and back into the blood vessel.
  • The extracorporeal blood circuit 7 shown in FIG. 2 further comprises an arterial clamp 9 and a venous clamp 10 for isolating the patient should an error occur.
  • Downstream of pump 8 is a dialyzer 11 comprising a blood compartment 12 and a dialysis fluid compartment 13 separated by a semi permeable membrane 14. Further downstream of the dialyzer is a drip chamber 15, separating air from the blood therein.
  • Blood passes from the arterial needle past the arterial clamp 9 to the blood pump 8. The blood pump drives the blood through the dialyzer 11 and further via the drip chamber 15 and past the venous clamp 10 back to the patient via the venous needle. The drip chamber may comprise air or air bubbles.
  • The dialysis compartment 13 of the dialyzer 11 is provided with dialysis fluid via a first pump 16, which obtains dialysis fluid from a source of pure water, normally RO-water, and one or several concentrates of ions, metering pumps 17 and 18 being shown for metering such concentrates.
  • An exchange of substances between the blood and the dialysis fluid takes place in the dialyzer through the semi permeable membrane. Notably, urea is passed from the blood, through the semi permeable membrane and to the dialysis fluid present at the other side of the membrane. The exchange may take place by diffusion under the influence of a concentration gradient, so called hemodialysis, and/or by convection due to a flow of liquid from the blood to the dialysis fluid, so called ultrafiltration, which is an important feature of hemodiafiltration or hemofiltration.
  • FIG. 3 shows schematically a section of a part of a blood circuit 30 with a pressure sensor 323 according to the present invention. The sensor 323 may be attached inside a tubing line such as line 70 in FIG. 2 after the pump 8 leading to the dialyser, as indicated by reference numeral 23″ in FIG. 2. Alternatively the sensor 323 may be arranged in a tubing line 70 before the pump 8, as indicated by reference numeral 23′ in FIG. 2. As further alternatives the sensor 23 may be arranged after the dialyzer at reference numeral 23′″ or in a drip chamber such as drip chamber 15 in FIG. 2.
  • The pressure sensor 323 comprises a container 25 with a compressible wall 24. A hole 35 in the wall 32 of the blood circuit ensures that the pressure within the container 25 is equal to atmospheric pressure. A resonance circuit is enclosed by the compressible container and comprises a variable capacitor 26 and an inductor 27. Such a sensor is shown in even larger scale in FIG. 4. The variable capacitor may have in one embodiment a number of interdigital conductors 28 in the form of fingers arranged on two opposing metal electrodes. A first of the electrodes 29 may be arranged on the compressible wall 24 while a second of the electrodes 31 may be fixed in relation to the wall 32 of the blood circuit, e.g. may be affixed to an interior wall of a tubing line 70 or a drip chamber 15. As the pressure in the extracorporeal circuit varies, the compressible wall of the container will move and accordingly the first electrode 29 and the second electrode 31 will move in relation to each other and thus the capacitance will vary. The resonance frequency of the resonance circuit constituted by the capacitor and the inductor will then vary in accordance with the capacitance of the capacitor.
  • Outside the blood circuit an exciter antenna 33 in FIG. 3 is arranged connected to a tunable oscillator 34 which may be controlled by a control unit 39. The oscillator may drive the antenna to influence the electromagnetic field at one or more different frequencies. In one embodiment the control unit 39 may use the grid-dip oscillator technique according to which technique the oscillator frequency is swept over the resonance frequency of the sensor, or other techniques for analyzing resonance frequencies of LC circuits. The oscillator is inductively coupled to the sensor and at the resonance frequency the sensor will be energized and thereby drain energy from the external circuit. A current-dip in the oscillator circuit may then be detected. The resonance frequency of the oscillator circuit may then be detected and may be transformed into a pressure by an established, e.g. calibrated, relationship between the frequency of the dip frequency and the fluid pressure, i.e. the difference between blood pressure and atmospheric pressure.
  • A device comprising a pressure sensor 500 will now be schematically described with reference to FIGS. 5 a-d. FIG. 5 a shows the sensor 500 in perspective view and FIGS. 5 b-d shows the sensor 500 in cross section and forming part of a wall 530 of an extracorporeal blood circuit having an inside surface 531, being in contact with the blood, and an outside surface 532, being in contact with the outside atmosphere.
  • The sensor 500 comprises a substrate 501 on which a lid 502 is arranged. A cavity 503 is formed between the substrate 501 and the lid 502, whereby the substrate 501 and the lid 502 form walls of the cavity 503, defining a container. The substrate 501 and the lid 502 are made of an electrically isolating material and the cavity 503 has been formed by way of, e.g., micro machining, as is known in the art. The cavity 503 is in pressure communication with the surroundings by means of a hole 535 in the substrate 501 in the sense that exchange of gas, i.e. air, is possible between the cavity 503 and the outside of the cavity 503. The container is also compressible, where the term compressible is used in the meaning that the volume of the container may increase as well as decrease depending on the pressure in the extracorporeal circuit.
  • A first electrode 504 and a second electrode 505 are arranged on two opposing walls of the cavity 503 forming a capacitive arrangement. These electrodes 504,505 form, together with an inductor 506, a resonance circuit similar to the one described above in connection with FIGS. 3 and 4.
  • FIG. 5 c illustrates a situation where the sensor 500 is located in an environment in which the pressure in the extracorporeal circuit is higher than the pressure inside the cavity 503, i.e. higher than atmospheric pressure. This leads to a net pressure force 510 acting on the lid 502 resulting in a decrease of the volume of the cavity 503. Consequently, the two electrodes 504,505 are brought closer to each other, changing the capacitance of the electrode arrangement and thereby changing the resonance frequency of the resonance circuit.
  • FIG. 5 d illustrates a situation where the sensor 500 is located in an environment in which the pressure in the extracorporeal circuit is lower than the pressure inside the cavity 503, i.e. lower than atmospheric pressure. This leads to a net pressure force 520 acting on the lid 502 resulting in an increase of the volume of the cavity 503. Consequently, the two electrodes 504,505 are brought further away from each other, changing the capacitance of the electrode arrangement and thereby changing the resonance frequency of the resonance circuit.
  • FIG. 5 e illustrates schematically an alternative embodiment of a device comprising a sensor configuration. A sensor 551 is mounted, e.g. glued or welded, on the inside wall 550 of a container for a biological fluid, for example a blood container with, e.g., rigid walls. Similar to the embodiment described above, electrodes 554 and 565 and an inductor 566 are located on a sensor lid 554 and a substrate 561, respectively. A cavity 553 is formed by the lid 552 and the substrate 561. As in the previous embodiment, the cavity 553 is in pressure communication with the outside of the container for biological fluid by means of a hole 555. A pressure differences between the cavity and the inside of the container for biological fluid results in flexing of the lid 552 and consequent relative displacement of the electrodes 554 and 565.
  • An alternative embodiment of a device according to the invention is illustrated in a perspective view in FIG. 6 a and in a cross sectional view in FIG. 6 b. A pressure sensor 601, similar to the sensors described above in connection with FIGS. 5 a-e, comprises a cavity 603 and a hole 635 for allowing the cavity 603 to obtain atmospheric pressure. A part of an electrode pattern 605 is formed on the sensor 601. The sensor 601 is attached to a tube 602, of which only a short section is shown, by way of a housing 610. The difference between a pressure of a fluid within the tube 602 and the atmospheric pressure is sensed via a membrane 612 as described above in connection with FIGS. 5 a-e.
  • The device, i.e. housing and sensor described above in FIGS. 6 a and 6 b, is manufactured, for example, by way of techniques that employ insert molding.
  • Yet an alternative embodiment of a device according to the invention is illustrated in a cross sectional view in FIG. 6 c. A pressure sensor 681, similar to the sensors described above in connection with FIGS. 5 a-e, comprises a cavity 683 and a hole 685 for allowing the cavity 683 to obtain atmospheric pressure. A part of an electrode pattern is formed on the sensor 681. The sensor 681 is attached to a tube 682, of which only a short section is shown, at a location where the tube 682 is provided with a hole 690 as described, e.g., in the international patent application published with number WO 00/72747. The difference between a pressure of a fluid within the tube 682 and the atmospheric pressure is sensed as described above in connection with FIGS. 5 a-5 e.
  • Turning now to FIGS. 7 a and 7 b, a system 701 according to one embodiment of the present invention will be briefly described. The system 701 comprises a device 703, such as a cassette, which forms part of an extracorporeal blood circuit 711, 712. Two pressure sensors 702, such as the sensors described above, are arranged in a side wall of the device 703, the arrangement being such that the sensor is mounted flush with both an inside surface and an outside surface of the wall of the device 703. It is to be noted, however, that it is not necessary that the sensor is mounted flush with the surfaces.
  • In operation, the device 703 is arranged at a dialysis apparatus 704, only a part of which is shown in FIGS. 7 a and 7 b, secured by means of mechanical coupling devices 708, 709. Within the dialysis apparatus 704 is an electromagnetic wave transmitter and a receiver located, schematically illustrated by a coil structure 705. The transmitter and receiver is controlled by a control unit (not shown) within the apparatus 704.
  • FIGS. 8 a-c illustrate schematically, by way of a respective block diagram, systems according to the present invention. The systems may for example form part, as described above, of a dialysis machine of which only a respective side wall 806, 826 and 846 is illustrated. Moreover, the systems are controlled by means of a respective controller 801, 821 and 841.
  • In FIG. 8 a, a first tunable oscillator 808 connected to a first transmitting and receiving antenna 810 communicates by way of a first alternating electromagnetic field with a first sensor 802. A second tunable oscillator 812 connected to a second transmitting and receiving antenna 814 communicates by way of a second alternating electromagnetic field with a second sensor 804. The tunable oscillators 808, 812 thereby provide a respective signal to the controller 801 indicative of the conditions sensed by the sensors 802 and 804, respectively.
  • In FIG. 8 b, a transmitter 828 connected to a transmitting antenna 830 generates, i.e. transmits, an alternating electromagnetic field which interacts with a sensor 822. A receiver 832 receives, via a receiving antenna 834, the alternating electromagnetic field, as modified by interaction with the sensor 822, and thereby provides a signal to the controller 821 indicative of the conditions sensed by the sensor 822.
  • In FIG. 8 c, a transmitter 848 connected to an antenna 850 generates, i.e. transmits, an alternating electromagnetic field which interacts with a sensor 842. A receiver 852 receives, via the same antenna 850, the alternating electromagnetic field, as modified by interaction with the sensor 842, and thereby provides a signal to the controller 841 indicative of the conditions sensed by the sensor 842.
  • After manufacture of a device comprising a pressure sensor as described above, there might be a wish to test the sensor so that one may be certain that it functions properly. One way of doing this is to apply a pressure to the sensor and measure the resonance frequency of the sensor. The sensor is made to have a certain resonance frequency without any applied pressure. If the pressure sensor has a different resonance frequency when a pressure is applied to the sensor this may be taken as an indication that the pressure sensor is functioning. However, it may be that the pressure sensor has a different resonance frequency without any applied pressure and still is non-functioning. Thus, in order to be more certain at least two different testing pressures may be applied to the sensor while the resonance frequency is measured.
  • The testing pressure may be applied in a number of different ways, for example as a static pressure in a pressure chamber.
  • By trimming during manufacturing of the pressure sensor it may be given different resonance frequencies which can thus be used to distinguish between different disposable sets. Thus, different tubing sets for use on the same machine may be identified as different tubing sets by discernment of the different resonance frequencies. Moreover, different medical procedures may also make use hereof.
  • As mentioned above the calibration at manufacturing and/or at the beginning of use at startup of a dialysis session can also provide for ensuring that the pressure sensor is working. This can be a function test like process to see if a proper response to the application of varying pressures by the blood pump or other mechanical alteration. The mechanical alteration may be the appliance of a mechanical force to test the electronic response frequency. The force for altering the sensor mechanically may be applied, e.g., by applying an ultrasound wave on the sensor.
  • The described embodiments are intended as examples only and may be modified by the man skilled in the art in a number of different ways without departing from the scope and the spirit of the invention which is defined by the appending claims.
  • For example the resonant sensor described above may be modified in that the inductance is made variable while the capacitance is fixed.
  • Another example is that the device for transporting biological fluid may be used in other extracorporeal management and/or treatments of biological fluids than specified above. Such other extracorporeal management and/or treatments may include: separation of blood into blood components; treatment to reduce pathogens such as viruses in biological fluids; absorption of specific cells or substances in blood; cell sorting and treatment of selected cells.

Claims (28)

1-28. (canceled)
29. A disposable sensor system, comprising:
a substrate;
a capacitor and an inductor fixed to said substrate to form a disposable pressure sensor thereof, wherein said inductor comprises an inductor surface, at least one electrode of a capacitor and a compressible wall, wherein when said compressible wall is exposed to a pressure, said compressible wall moves close to said inductor surface and/or said at least one capacitor electrode, thereby resulting in an increase in an inductance and/or a capacitance and a decrease in a resonant frequency associated with said capacitor and said inductor, wherein said increase and said decrease are detectable by external interrogation; and
interrogation electronics associated with said inductor and said capacitor, wherein said interrogation electronics externally detect said increase in said inductance and/or said capacitance and said decrease in said resonant frequency.
30. The system of claim 1 further comprising a trimming mechanism for trimming said capacitor in order to calibrate data based on said decrease in said resonant frequency.
31. The system of claim 1 further comprising a trimming mechanism for trimming said inductor in order to calibrate data based on said increase in said inductance.
32. A device for transporting biological fluid in at least a part of an extracorporeal circuit, said at least part of the extracorporeal circuit being disposable and comprising:
at least one disposable sensor configured to be in fluid communication with the biological fluid, the at least one disposable sensor comprising:
a substrate,
a capacitor and an inductor fixed to said substrate to form a disposable pressure sensor thereof, wherein said inductor comprises an inductor surface, at least one electrode of a capacitor and a compressible wall, wherein when said compressible wall is exposed to a pressure, said compressible wall moves close to said inductor surface and/or said at least one capacitor electrode, thereby resulting in an increase in an inductance and/or a capacitance and a decrease in a resonant frequency associated with said capacitor and said inductor, wherein said increase and said decrease are detectable by external interrogation, and
interrogation electronics associated with said inductor and said capacitor,
wherein said interrogation electronics externally detect said increase in said inductance and/or said capacitance and said decrease in said resonant frequency.
33. The disposable sensor of claim 1 further comprising a trimming mechanism for trimming said capacitor in order to calibrate data based on said decrease in said resonant frequency.
34. The system of claim 1 further comprising a trimming mechanism for trimming said inductor in order to calibrate data based on said increase in said inductance.
35. A disposable sensor method, comprising the steps of:
providing a substrate;
fixing a capacitor and an inductor fixed to said substrate to form a disposable pressure sensor thereof;
configuring said substrate to include an inductor surface, at least one capacitor electrode and a compressible wall, wherein when said compressible wall is exposed to a pressure, said compressible wall moves close to said inductor and/or a surface of said at least one capacitor electrode, thereby resulting in an increase in an inductance and/or a capacitance and a decrease in a resonant frequency associated with said capacitor and said inductor, wherein said increase and said decrease are detectable by external interrogation; and
associating interrogation electronics with said inductor and said capacitor, wherein said interrogation electronics externally detect said increase in said inductance and/or said capacitance and said decrease in said resonant frequency.
36. The method of claim 35 further comprising the step of calibrating data based on said decrease in said resonant frequency utilizing a trimming mechanism for said capacitor.
37. The method of claim 35 further comprising the step of calibrating data based on said increase in said inductance utilizing a trimming mechanism for said inductor.
38. A disposable flow sensor comprising:
at least one pressure sensing device for detecting fluid pressure in a channel, wherein said at least one pressure sensing device comprises:
a compressible wall, and a capacitor electrically coupled to an inductor to form an LC tank circuit, said capacitor and/or inductor being mechanically coupled to said compressible wall such that a deflection of said diaphragm in response to fluid pressure applied thereto causes a change in the LC tank circuit inductance and/or capacitance and a change in the resonant frequency thereof, and wherein, when said at least one pressure sensing device is operatively coupled to said channel, said fluid pressure and said flow rate can be determined by detecting changes in said resonant frequency using interrogation.
39. The sensor of claim 38, wherein said capacitor comprises a pair of spaced apart conductive plates, one of said plates being carried on or forming said compressible wall.
40. The sensor of claim 39, wherein said inductor comprises a patch or layer of conductive or magnetic material carried on or forming said compressible wall, such that a deflection of said compressible wall causes a change in inductance of said inductor.
41. The sensor of claim 39 further comprising a substrate coupled to said compressible wall, said inductor and/or at one least one of said capacitor plates being carried on said substrate.
42. The sensor of claim 41 further comprising a calibration capacitor and/or calibration inductor carried on said substrate, said calibration capacitor and/or inductor being trimmable or adjustable for calibrating said pressure sensing device.
43. A differential pressure flow sensor system comprising:
a disposable flow sensor comprising upstream and downstream pressure sensing devices for detecting a differential pressure between upstream and downstream locations of a flow channel;
wherein each of said pressure sensing devices comprises a compressible wall, a capacitor and an inductor electrically coupled to said capacitor so as to form an LC tank circuit, said capacitor and/or inductor being mechanically coupled to said compressible wall such that a deflection of said diaphragm in response to fluid pressure applied thereto causes a change in the inductance and/or capacitance of said LC tank circuit and a change in the resonant frequency thereof and, wherein, when said upstream and downstream pressure sensing devices are operatively coupled to said upstream and downstream channel locations, respectively, said differential pressure and said flow rate can be determined by detecting changes in said resonant frequency using interrogation.
44. The system of claim 43 further comprising external interrogation electronics for wirelessly detecting said change in resonant frequency of each of said pressure sensing devices.
45. The system of claim 43, wherein said compressible wall of said pressure sensing devices are molded in a wall of said channel at upstream and downstream locations, respectively.
46. The system of claim 43 further comprising a substrate coupled to said compressible wall and, wherein said inductor and/or or at least one electrode plate of said capacitor is/are carried on said substrate.
47. The system of claim 46 further comprising a calibration capacitor and/or calibration inductor formed on said substrate, said calibration capacitor and/or inductor being trimmable or adjustable for calibrating said pressure sensing device.
48. The system of claim 43, wherein said capacitor comprises a pair of spaced apart conductive plates, one of said plates being carried on or forming said compressible wall.
49. The system of claim 43, wherein said inductor includes a patch or layer of conductive or magnetic material coupled to said compressible wall such that deflection of said diaphragm causes a change in inductance of said inductor.
50. The system of claim 43, wherein said inductor includes a single patch or layer of conductive or magnetic material coupled to both compressible wall of said pressure sensing devices such that deflection of said compressible wall causes a change in inductance of said inductors of said pressure sensing devices.
51. The system of claim 43 further comprising a transceiver for wireless transmitting an electromagnetic interrogation signal to said pressure sensing devices and/or for receiving resulting resonant electromagnetic signals therefrom so as to detect said changes in resonant frequency.
52. A method of manufacturing a flow sensor system for measuring the flow rate of fluid in a channel, said method comprising:
forming a pair of disposable pressure sensing devices for measuring the pressure differential in a flow channel; and
mechanically coupling said pressure sensing devices to said channel at upstream and downstream locations, respectively.
53. The method of claim 52, wherein forming each disposable pressure sensing device comprises: forming a compressible wall; forming a capacitor and inductor; electrically coupling said capacitor to said inductor so as to form an LC circuit; and mechanically coupling said capacitor and/or inductor to said compressible wall such that a deflection of said compressible wall caused by pressure applied thereto causes a change in said capacitance and/or inductance of said LC circuit.
54. The method of claim 52 further comprising configuring external interrogation electronics for wireless detecting the resonant frequencies of said pressure sensing devices.
55. The method of claim 52 further comprising forming a trimmable capacitor and/or trimmable inductor on said pressure sensing devices for calibration thereof.
US11/808,287 2004-02-12 2007-06-08 Pressure sensing Abandoned US20070261496A1 (en)

Priority Applications (6)

Application Number Priority Date Filing Date Title
US54420504P true 2004-02-12 2004-02-12
SE0400330A SE0400330D0 (en) 2004-02-12 2004-02-12 Pressure sensing
SE0400330-7 2004-02-12
US10/589,353 US7771380B2 (en) 2004-02-12 2005-02-11 Pressure sensing
PCT/SE2005/000184 WO2005077262A1 (en) 2004-02-12 2005-02-11 Pressure sensing
US11/808,287 US20070261496A1 (en) 2004-02-12 2007-06-08 Pressure sensing

Applications Claiming Priority (1)

Application Number Priority Date Filing Date Title
US11/808,287 US20070261496A1 (en) 2004-02-12 2007-06-08 Pressure sensing

Related Parent Applications (2)

Application Number Title Priority Date Filing Date
PCT/SE2005/000184 Continuation WO2005077262A1 (en) 2004-02-12 2005-02-11 Pressure sensing
US11/589,353 Continuation US7952553B2 (en) 2006-06-12 2006-10-30 Amplifier circuits in which compensation capacitors can be cross-connected so that the voltage level at an output node can be reset to about one-half a difference between a power voltage level and a common reference voltage level and methods of operating the same

Publications (1)

Publication Number Publication Date
US20070261496A1 true US20070261496A1 (en) 2007-11-15

Family

ID=31974218

Family Applications (2)

Application Number Title Priority Date Filing Date
US10/589,353 Active 2026-08-14 US7771380B2 (en) 2004-02-12 2005-02-11 Pressure sensing
US11/808,287 Abandoned US20070261496A1 (en) 2004-02-12 2007-06-08 Pressure sensing

Family Applications Before (1)

Application Number Title Priority Date Filing Date
US10/589,353 Active 2026-08-14 US7771380B2 (en) 2004-02-12 2005-02-11 Pressure sensing

Country Status (9)

Country Link
US (2) US7771380B2 (en)
EP (1) EP1713383B1 (en)
KR (1) KR101158596B1 (en)
CN (1) CN100431483C (en)
AU (1) AU2005212146B2 (en)
CA (1) CA2549067C (en)
ES (1) ES2525468T3 (en)
SE (1) SE0400330D0 (en)
WO (1) WO2005077262A1 (en)

Cited By (14)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US20060191354A1 (en) * 2005-02-25 2006-08-31 Drager Medical Ag & Co. Kg Device for measuring a volume flow with inductive coupling
US20060275907A1 (en) * 2003-05-09 2006-12-07 Cgs Sensortechnik Gmbh Device for measuring pressure
US20100241077A1 (en) * 2009-03-17 2010-09-23 Roche Diagnostics International Ag Cannula Assemblies And Ambulatory Infusion Systems With Pressure Sensors Made Of Stacked Coplanar Layers
WO2010108714A1 (en) * 2009-03-26 2010-09-30 Robert Bosch Gmbh Blood treatment device
US20100300208A1 (en) * 2009-05-27 2010-12-02 Canon Kabushiki Kaisha Capacitive electro-mechanical transducer
US7845239B1 (en) * 2006-03-24 2010-12-07 Polysensors Inc. Disposable flow chamber electro-magnetic flow sensor
US20110301575A1 (en) * 2010-06-03 2011-12-08 Medtronic, Inc. Implantable medical pump with pressure sensor
US8088091B2 (en) 2009-03-09 2012-01-03 New Jersey Institute Of Technology No clog shunt using a compact fluid drag path
US20120272518A1 (en) * 2009-08-21 2012-11-01 Regents Of The University Of Minnesota Flexible sensors and related systems for determining forces applied to an object, such as a surgical instrument, and methods for manufacturing same
WO2015172891A1 (en) * 2014-05-15 2015-11-19 Novalung Gmbh Medico-technical measuring device and measuring method
US10105103B2 (en) 2013-04-18 2018-10-23 Vectorious Medical Technologies Ltd. Remotely powered sensory implant
US10205488B2 (en) 2013-04-18 2019-02-12 Vectorious Medical Technologies Ltd. Low-power high-accuracy clock harvesting in inductive coupling systems
US10226193B2 (en) 2015-03-31 2019-03-12 Medtronic Ps Medical, Inc. Wireless pressure measurement and monitoring for shunts
US10463306B2 (en) 2014-05-15 2019-11-05 Novalung Gmbh Medical measuring system and method for production of the measuring system

Families Citing this family (30)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US8449487B2 (en) * 2006-12-01 2013-05-28 Gambro Lundia Ab Blood treatment apparatus
US8152751B2 (en) 2007-02-09 2012-04-10 Baxter International Inc. Acoustic access disconnection systems and methods
US10463778B2 (en) 2007-02-09 2019-11-05 Baxter International Inc. Blood treatment machine having electrical heartbeat analysis
DE102008010948B4 (en) 2008-02-25 2013-10-17 Fresenius Medical Care Deutschland Gmbh Method for calibrating a sensor within a chamber; Sensor, disposable and treatment device with such a sensor
AU2009262505B2 (en) 2008-06-26 2014-08-07 Gambro Lundia Ab Method and device for processing a time-dependent measurement signal
US9370324B2 (en) 2008-11-05 2016-06-21 Fresenius Medical Care Holdings, Inc. Hemodialysis patient data acquisition, management and analysis system
IT1392256B1 (en) * 2008-12-05 2012-02-22 Illinois Tool Works A pressure sensor modified to detect operating parameters of an appliance provided with a relatively mobile component
US8591448B2 (en) * 2009-05-13 2013-11-26 Haemonetics Corporation Pressure monitoring within a fluid cassette
US8454822B2 (en) * 2009-05-29 2013-06-04 Emd Millipore Corporation Disposable tangential flow filtration liner with sensor mount
JP5951483B2 (en) 2009-06-26 2016-07-13 ガンブロ・ルンディア・エービーGambro Lundia Ab Extracorporeal fluid system, computer program product, and method for data extraction
US8753515B2 (en) 2009-12-05 2014-06-17 Home Dialysis Plus, Ltd. Dialysis system with ultrafiltration control
WO2011163608A2 (en) * 2010-06-24 2011-12-29 University Of Utah Research Foundation Pressure sensitive microparticles for measuring characteristics of fluid flow
US9194792B2 (en) 2010-09-07 2015-11-24 Fresenius Medical Care Holdings, Inc. Blood chamber for an optical blood monitoring system
US8743354B2 (en) 2010-09-07 2014-06-03 Fresenius Medical Care Holdings, Inc. Shrouded sensor clip assembly and blood chamber for an optical blood monitoring system
US9173988B2 (en) 2010-11-17 2015-11-03 Fresenius Medical Care Holdings, Inc. Sensor clip assembly for an optical monitoring system
CA2817148C (en) 2010-11-17 2017-07-18 Fresenius Medical Care Holdings, Inc. Sensor clip assembly for an optical monitoring system
CN102147308A (en) * 2010-12-23 2011-08-10 大丰市丰泰机电有限公司 Fuel-gas micro pressure gauge
ES2640953T3 (en) 2011-10-07 2017-11-07 Outset Medical, Inc. Purification of heat exchange fluid for a dialysis system
USD725261S1 (en) 2012-02-24 2015-03-24 Fresenius Medical Care Holdings, Inc. Blood flow chamber
US9808567B2 (en) 2012-12-14 2017-11-07 Gambro Lundia Ab Diaphragm repositioning for pressure pod using position sensing
US9220834B2 (en) * 2012-12-20 2015-12-29 Acist Medical Systems, Inc. Pressure sensing in medical injection systems
EP2934618B1 (en) * 2012-12-20 2020-01-15 Gambro Lundia AB Blood set component connection detection
WO2014147028A1 (en) 2013-03-20 2014-09-25 Gambro Lundia Ab Monitoring of cardiac arrest in a patient connected to an extracorporeal blood processing apparatus
DE102013014097A1 (en) * 2013-08-23 2015-02-26 Fresenius Medical Care Deutschland Gmbh Disposable articles for dialysis treatment, dialysis machine and a water treatment system for dialysate
JP2017514653A (en) 2014-04-29 2017-06-08 アウトセット・メディカル・インコーポレイテッドOutset Medical, Inc. Dialysis system and method
FR3025311B1 (en) 2014-08-26 2016-12-30 Commissariat Energie Atomique Pressure sensor of a fluid
US10172989B2 (en) 2014-09-12 2019-01-08 Easydial Inc. Portable hemodialysis machine and disposable cartridge with blood leak sensor
US20160101226A1 (en) * 2014-10-09 2016-04-14 Fresenius Medical Care Holdings, Inc. Sensing Negative Pressure with a Pressure Transducer
USD799031S1 (en) 2015-09-09 2017-10-03 Fresenius Medical Care Holdings, Inc. Blood flow chamber with directional arrow
US10413654B2 (en) 2015-12-22 2019-09-17 Baxter International Inc. Access disconnection system and method using signal metrics

Citations (15)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US4160971A (en) * 1975-05-02 1979-07-10 National Research Development Corporation Transponders
US5756900A (en) * 1993-12-28 1998-05-26 Tasco Japan Co., Ltd. Pressure sensing apparatus
US5807258A (en) * 1997-10-14 1998-09-15 Cimochowski; George E. Ultrasonic sensors for monitoring the condition of a vascular graft
US6015386A (en) * 1998-05-07 2000-01-18 Bpm Devices, Inc. System including an implantable device and methods of use for determining blood pressure and other blood parameters of a living being
US6272930B1 (en) * 1996-05-10 2001-08-14 Corneal Industrie Tube assembly including a pressure measuring device
US20020071137A1 (en) * 2000-12-13 2002-06-13 Haines Robert E. Image forming devices and methods of facilitating ordering of an imaging consumable
US20020115920A1 (en) * 2001-01-22 2002-08-22 Rich Collin A. MEMS capacitive sensor for physiologic parameter measurement
US6532834B1 (en) * 1999-08-06 2003-03-18 Setra Systems, Inc. Capacitive pressure sensor having encapsulated resonating components
US20040073137A1 (en) * 2002-08-27 2004-04-15 Board Of Trustees Of Michigan State University Implantable microscale pressure sensor system for pressure monitoring and management
US20040082867A1 (en) * 2002-10-29 2004-04-29 Pearl Technology Holdings, Llc Vascular graft with integrated sensor
US20050076719A1 (en) * 2003-10-10 2005-04-14 Henrik Jakobsen Capacitive sensor
US6887214B1 (en) * 2000-09-12 2005-05-03 Chf Solutions, Inc. Blood pump having a disposable blood passage cartridge with integrated pressure sensors
US7059195B1 (en) * 2004-12-02 2006-06-13 Honeywell International Inc. Disposable and trimmable wireless pressure sensor for medical applications
US20060144155A1 (en) * 2004-12-02 2006-07-06 Honeywell International Inc. Pressure flow sensor systems and pressure flow sensors for use therein
US7181975B1 (en) * 2005-09-13 2007-02-27 Honeywell International Wireless capacitance pressure sensor

Family Cites Families (8)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US5873840A (en) * 1997-08-21 1999-02-23 Neff; Samuel R. Intracranial pressure monitoring system
EP0947815A1 (en) * 1998-04-01 1999-10-06 HAENNI & CIE. AG Differential pressure transducer
US6383158B1 (en) * 1998-12-01 2002-05-07 Dsu Medical Corporation Dialysis pressure monitoring with clot suppression
SE515627C2 (en) * 1999-05-31 2001-09-10 Gambro Lundia Ab Apparatus for measuring a property of an existing pipeline in a fluid
DE20113789U1 (en) 2001-01-10 2002-05-23 Braun Melsungen Ag Medical device
EP1236479B1 (en) * 2001-02-19 2005-05-04 Nextier Co., Ltd. Dialyzing system
DE20121388U1 (en) * 2001-04-18 2002-09-26 Univ Dresden Tech Device for wireless pressure measurement in liquids
DE20121938U1 (en) * 2001-09-25 2003-09-04 Weiser Roland Sensor device for measurement of pressure values inside epi- or subdural drainage systems within the human body has a leak-tight housing with a sensor arrangement that transmits measurement values to an external evaluation unit

Patent Citations (15)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US4160971A (en) * 1975-05-02 1979-07-10 National Research Development Corporation Transponders
US5756900A (en) * 1993-12-28 1998-05-26 Tasco Japan Co., Ltd. Pressure sensing apparatus
US6272930B1 (en) * 1996-05-10 2001-08-14 Corneal Industrie Tube assembly including a pressure measuring device
US5807258A (en) * 1997-10-14 1998-09-15 Cimochowski; George E. Ultrasonic sensors for monitoring the condition of a vascular graft
US6015386A (en) * 1998-05-07 2000-01-18 Bpm Devices, Inc. System including an implantable device and methods of use for determining blood pressure and other blood parameters of a living being
US6532834B1 (en) * 1999-08-06 2003-03-18 Setra Systems, Inc. Capacitive pressure sensor having encapsulated resonating components
US6887214B1 (en) * 2000-09-12 2005-05-03 Chf Solutions, Inc. Blood pump having a disposable blood passage cartridge with integrated pressure sensors
US20020071137A1 (en) * 2000-12-13 2002-06-13 Haines Robert E. Image forming devices and methods of facilitating ordering of an imaging consumable
US20020115920A1 (en) * 2001-01-22 2002-08-22 Rich Collin A. MEMS capacitive sensor for physiologic parameter measurement
US20040073137A1 (en) * 2002-08-27 2004-04-15 Board Of Trustees Of Michigan State University Implantable microscale pressure sensor system for pressure monitoring and management
US20040082867A1 (en) * 2002-10-29 2004-04-29 Pearl Technology Holdings, Llc Vascular graft with integrated sensor
US20050076719A1 (en) * 2003-10-10 2005-04-14 Henrik Jakobsen Capacitive sensor
US7059195B1 (en) * 2004-12-02 2006-06-13 Honeywell International Inc. Disposable and trimmable wireless pressure sensor for medical applications
US20060144155A1 (en) * 2004-12-02 2006-07-06 Honeywell International Inc. Pressure flow sensor systems and pressure flow sensors for use therein
US7181975B1 (en) * 2005-09-13 2007-02-27 Honeywell International Wireless capacitance pressure sensor

Cited By (27)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US20060275907A1 (en) * 2003-05-09 2006-12-07 Cgs Sensortechnik Gmbh Device for measuring pressure
US7803628B2 (en) * 2003-05-09 2010-09-28 Mhm Harzbecher Medizintechnik Gmbh Device for measuring pressure
US20060191354A1 (en) * 2005-02-25 2006-08-31 Drager Medical Ag & Co. Kg Device for measuring a volume flow with inductive coupling
US7418859B2 (en) * 2005-02-25 2008-09-02 Dräger Medical AG & Co. KG Device for measuring a volume flow with inductive coupling
US7845239B1 (en) * 2006-03-24 2010-12-07 Polysensors Inc. Disposable flow chamber electro-magnetic flow sensor
US8088091B2 (en) 2009-03-09 2012-01-03 New Jersey Institute Of Technology No clog shunt using a compact fluid drag path
US20100241077A1 (en) * 2009-03-17 2010-09-23 Roche Diagnostics International Ag Cannula Assemblies And Ambulatory Infusion Systems With Pressure Sensors Made Of Stacked Coplanar Layers
US9283319B2 (en) 2009-03-17 2016-03-15 Roche Diagnostics International Ag Cannula assemblies and ambulatory infusion systems with pressure sensors made of stacked coplanar layers
US8313468B2 (en) * 2009-03-17 2012-11-20 Roche Diagnostics International Ag Cannula assemblies and ambulatory infusion systems with pressure sensors made of stacked coplanar layers
US20120095351A1 (en) * 2009-03-26 2012-04-19 Robert Bosch Gmbh Blood treatment device
WO2010108714A1 (en) * 2009-03-26 2010-09-30 Robert Bosch Gmbh Blood treatment device
US8256302B2 (en) * 2009-05-27 2012-09-04 Canon Kabushiki Kaisha Capacitive electro-mechanical transducer
US20100300208A1 (en) * 2009-05-27 2010-12-02 Canon Kabushiki Kaisha Capacitive electro-mechanical transducer
US9222845B2 (en) * 2009-08-21 2015-12-29 Regents Of The University Of Minnesota Flexible sensors and related systems for determining forces applied to an object, such as a surgical instrument, and methods for manufacturing same
US20120272518A1 (en) * 2009-08-21 2012-11-01 Regents Of The University Of Minnesota Flexible sensors and related systems for determining forces applied to an object, such as a surgical instrument, and methods for manufacturing same
US20160076953A1 (en) * 2009-08-21 2016-03-17 Regents Of The University Of Minnesota Flexible sensors and related systems for determining forces applied to an object, such as a surgical instrument, and methods for manufacturing same
US10406281B2 (en) * 2010-06-03 2019-09-10 Medtronic, Inc. Implantable medical pump with pressure sensor
US20110301575A1 (en) * 2010-06-03 2011-12-08 Medtronic, Inc. Implantable medical pump with pressure sensor
US9737657B2 (en) * 2010-06-03 2017-08-22 Medtronic, Inc. Implantable medical pump with pressure sensor
US10205488B2 (en) 2013-04-18 2019-02-12 Vectorious Medical Technologies Ltd. Low-power high-accuracy clock harvesting in inductive coupling systems
US10105103B2 (en) 2013-04-18 2018-10-23 Vectorious Medical Technologies Ltd. Remotely powered sensory implant
JP2017520280A (en) * 2014-05-15 2017-07-27 ノヴァラング ゲゼルシャフト ミット ベシュレンクテル ハフツング Medical technical measuring apparatus and measuring method
US10463306B2 (en) 2014-05-15 2019-11-05 Novalung Gmbh Medical measuring system and method for production of the measuring system
US10391227B2 (en) 2014-05-15 2019-08-27 Novalung Gmbh Medico-technical measuring device and measuring method
WO2015172891A1 (en) * 2014-05-15 2015-11-19 Novalung Gmbh Medico-technical measuring device and measuring method
EP3590564A1 (en) * 2014-05-15 2020-01-08 novalung GmbH Medical technical measuring device and measuring method
US10226193B2 (en) 2015-03-31 2019-03-12 Medtronic Ps Medical, Inc. Wireless pressure measurement and monitoring for shunts

Also Published As

Publication number Publication date
CN1913825A (en) 2007-02-14
US20070179433A1 (en) 2007-08-02
EP1713383B1 (en) 2014-11-12
EP1713383A1 (en) 2006-10-25
CA2549067C (en) 2013-07-16
SE0400330D0 (en) 2004-02-12
CA2549067A1 (en) 2005-08-25
AU2005212146B2 (en) 2010-12-02
WO2005077262A1 (en) 2005-08-25
US7771380B2 (en) 2010-08-10
CN100431483C (en) 2008-11-12
KR101158596B1 (en) 2012-06-22
ES2525468T3 (en) 2014-12-23
KR20060129286A (en) 2006-12-15
AU2005212146A1 (en) 2005-08-25

Similar Documents

Publication Publication Date Title
US8114288B2 (en) System and method for conducting hemodialysis and hemofiltration
JP6239501B2 (en) Blood treatment system and method
US8870549B2 (en) Fluid pumping systems, devices and methods
EP2526982B1 (en) Acoustic access disconnection systems
US4436620A (en) Integral hydraulic circuit for hemodialysis apparatus
JP6235447B2 (en) Hemodialysis system using adsorbent and storage tank
CA2682073C (en) Sensor apparatus systems, devices and methods
CN105148344B (en) System and method are charged for dialysis system
EP1896725B1 (en) An apparatus for controlling blood flow in an extracorporeal circuit
US4759371A (en) Implantable, calibrateable measuring instrument for a body substance and a calibrating method
JP5960861B2 (en) Hemodialysis system
US5554113A (en) Flow pressure transducer
EP3222308B1 (en) Pump system and method for acoustically estimating liquid delivery
EP2117624B1 (en) Optical access disconnection systems
JP4118233B2 (en) Method and apparatus for detecting fluid line leaks
JP4077722B2 (en) Apparatus and method for controlling flow of body fluid during treatment of extracorporeal fluid
EP2211935B1 (en) Acoustic access disconnect detection system
US7107837B2 (en) Capacitance fluid volume measurement
EP0591184B1 (en) Apheresis method and device
EP1996269B1 (en) Surgical cassette with multi area fluid chamber
US5230341A (en) Measuring the change of intravascular blood volume during blood filtration
US7938792B2 (en) Adaptive algorithm for access disconnect detection
US8491518B2 (en) Diaphragm pressure pod for medical fluids
US6623443B1 (en) Method and device for the detection of stenosis in extra-corporeal blood treatment
US6346084B1 (en) Measuring vascular access pressure

Legal Events

Date Code Title Description
AS Assignment

Owner name: CITICORP TRUSTEE COMPANY LIMITED, UNITED KINGDOM

Free format text: IP SECURITY AGREEMENT SUPPLEMENT;ASSIGNOR:GAMBRO LUNDIA AB;REEL/FRAME:022714/0702

Effective date: 20090331

Owner name: CITICORP TRUSTEE COMPANY LIMITED,UNITED KINGDOM

Free format text: IP SECURITY AGREEMENT SUPPLEMENT;ASSIGNOR:GAMBRO LUNDIA AB;REEL/FRAME:022714/0702

Effective date: 20090331

STCB Information on status: application discontinuation

Free format text: ABANDONED -- FAILURE TO RESPOND TO AN OFFICE ACTION

AS Assignment

Owner name: GAMBRO LUNDIA AB, COLORADO

Free format text: RELEASE OF SECURITY INTEREST IN PATENTS;ASSIGNOR:CITICORP TRUSTEE COMPANY LIMITED, AS SECURITY AGENT;REEL/FRAME:027456/0050

Effective date: 20111207