US20180161487A1 - Pump, system with a blood pump and method for producing a blood pump - Google Patents
Pump, system with a blood pump and method for producing a blood pump Download PDFInfo
- Publication number
- US20180161487A1 US20180161487A1 US15/411,091 US201715411091A US2018161487A1 US 20180161487 A1 US20180161487 A1 US 20180161487A1 US 201715411091 A US201715411091 A US 201715411091A US 2018161487 A1 US2018161487 A1 US 2018161487A1
- Authority
- US
- United States
- Prior art keywords
- pump
- fact
- blood pump
- per
- pressure sensor
- 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
Links
Images
Classifications
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61M—DEVICES 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
- A61M60/00—Blood pumps; Devices for mechanical circulatory actuation; Balloon pumps for circulatory assistance
- A61M60/10—Location thereof with respect to the patient's body
- A61M60/122—Implantable pumps or pumping devices, i.e. the blood being pumped inside the patient's body
- A61M60/165—Implantable pumps or pumping devices, i.e. the blood being pumped inside the patient's body implantable in, on, or around the heart
- A61M60/17—Implantable pumps or pumping devices, i.e. the blood being pumped inside the patient's body implantable in, on, or around the heart inside a ventricle, e.g. intraventricular balloon pumps
-
- A61M1/1086—
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61M—DEVICES 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
- A61M60/00—Blood pumps; Devices for mechanical circulatory actuation; Balloon pumps for circulatory assistance
- A61M60/40—Details relating to driving
- A61M60/403—Details relating to driving for non-positive displacement blood pumps
- A61M60/422—Details relating to driving for non-positive displacement blood pumps the force acting on the blood contacting member being electromagnetic, e.g. using canned motor pumps
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61M—DEVICES 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
- A61M60/00—Blood pumps; Devices for mechanical circulatory actuation; Balloon pumps for circulatory assistance
- A61M60/10—Location thereof with respect to the patient's body
- A61M60/122—Implantable pumps or pumping devices, i.e. the blood being pumped inside the patient's body
- A61M60/196—Implantable pumps or pumping devices, i.e. the blood being pumped inside the patient's body replacing the entire heart, e.g. total artificial hearts [TAH]
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61M—DEVICES 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
- A61M60/00—Blood pumps; Devices for mechanical circulatory actuation; Balloon pumps for circulatory assistance
- A61M60/20—Type thereof
- A61M60/205—Non-positive displacement blood pumps
- A61M60/216—Non-positive displacement blood pumps including a rotating member acting on the blood, e.g. impeller
-
- A61M1/101—
-
- A61M1/12—
-
- A61M1/122—
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61M—DEVICES 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
- A61M2205/00—General characteristics of the apparatus
- A61M2205/33—Controlling, regulating or measuring
- A61M2205/3331—Pressure; Flow
- A61M2205/3334—Measuring or controlling the flow rate
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61M—DEVICES 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
- A61M2205/00—General characteristics of the apparatus
- A61M2205/33—Controlling, regulating or measuring
- A61M2205/3368—Temperature
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61M—DEVICES 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
- A61M2205/00—General characteristics of the apparatus
- A61M2205/33—Controlling, regulating or measuring
- A61M2205/3375—Acoustical, e.g. ultrasonic, measuring means
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61M—DEVICES 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
- A61M2230/00—Measuring parameters of the user
- A61M2230/04—Heartbeat characteristics, e.g. ECG, blood pressure modulation
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61M—DEVICES 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
- A61M60/00—Blood pumps; Devices for mechanical circulatory actuation; Balloon pumps for circulatory assistance
- A61M60/10—Location thereof with respect to the patient's body
- A61M60/122—Implantable pumps or pumping devices, i.e. the blood being pumped inside the patient's body
- A61M60/126—Implantable pumps or pumping devices, i.e. the blood being pumped inside the patient's body implantable via, into, inside, in line, branching on, or around a blood vessel
- A61M60/148—Implantable pumps or pumping devices, i.e. the blood being pumped inside the patient's body implantable via, into, inside, in line, branching on, or around a blood vessel in line with a blood vessel using resection or like techniques, e.g. permanent endovascular heart assist devices
Definitions
- the invention relates to a blood pump made of titanium with a measuring device for to determine the flow based on acoustic flow measurement processes as well as a blood pump with a temperature sensor and/or a pressure sensor as well as a system with a blood pump and an inlet cannula and/or an outlet cannula with an outlet connector as well as a procedure to produce a blood pump with a measurement device.
- the task of this invention is to improve current state-of-the-art blood pumps.
- a titanium blood pump with a measurement device to determine flow, based on acoustic flow measurement processes, whereby the measurement device has a measurement path with two coupling wedges with two transducers arranged with them, and the measurement device on a blood pump is arranged in such a way that an installation functions as a reflector.
- An installation is any component that is arranged inside the pump. Any installation can be used as a reflector, so that the measurement device can be freely located on the blood pump. In particular, no space free of installations must be found for the measurement. This allows a more compact design.
- Acoustic flow measurement techniques permit the determination of the flow of fluids through analysis of the flow of modulated acoustic waves.
- a paired sensor unit consisting transducers acting as alternating transmitters and receivers, it can principally assess the relative transit time differences (in and against the flow direction), beam deflection (shunting) and changes in phase, amplitude and frequency of the acoustic waves. Also, scattering effects can be evaluated. So effects, such as Doppler effects or entrainment effects can be determined.
- a preferred embodiment is to assess the relative transit time.
- the transducers In order to achieve a measurement effect and to receive the transmitted sound waves, the transducers must be installed in a specific angle range to the flow. This is done by mounting on so-called coupling wedges.
- the coupling wedges are firmly connected to the blood pump. This is preferably carried out by appropriate cut-outs on the pump housing.
- a variant is the gluing or welding of coupling wedges to the desired measurement points.
- a blood pump it is desirable for a blood pump to be able to determine the flow or volume, without invasively accessing the flow stream. Thus it is especially preferable not to have the transducers in contact with the bloodstream.
- the fluid being measured is blood.
- the blood pump is used to support or to replace the human heart.
- the blood pump satisfies the requirements for fully implantable medical devices.
- titanium Due to its corrosion resistance compared to other metals, titanium is used as the biomaterial for blood pumps.
- Other biocompatible materials can be used in pump construction, such as ceramics like zirconium oxide.
- the installation is a motor and flow is measured in an annular gap. It is thus possible to integrate flow measurement in the main blood pump section. This makes it possible to have a compact structure, especially integrated wire management.
- the measurement paths can be arranged on opposite sites. A maximum distance between the measuring points can be achieved.
- an arrangement on the pump the housing is easily possible.
- the measurement device is hermetically sealed in a space via the pump environment. If the measurement device is insulated from the environment in such a manner, a design as an implantable blood pump is particularly possible.
- a grommet is arranged between the space and the interior of the pump. In this way, all wires can be led in the interior of the pump.
- the grommet can be arranged along a longitudinal axis. Thus the path can also show a radial skew.
- a second independent aspect of the invention relates to a blood pump which has a temperature sensor.
- the temperature sensor can determine the temperature of the blood while the blood pump is operating. High temperatures lead to blood damage and should therefore be avoided.
- a third independent aspect of the invention relates to a blood pump whereby it has an integrated pressure sensor.
- the pressure sensor can either be an absolute pressure sensor or a differential pressure sensor.
- This pressure sensor can be integrated into a pump inlet and/or pump outlet. It can gather data on pressure conditions at both these sites on the pump. Through measurement at both locations, flow can determined using a stored characteristic map.
- a pressure sensor can be integrated in the pump inlet when the pump inlet is placed directly into the ventricle without the interposition of a cannula. Thus an arrangement of the sensor on the outside of the pump inlet makes sense in order to measure the chamber pressure.
- a fourth independent aspect of the invention relates to a blood pump which has a first pressure sensor and a second pressure sensor, whereby the first pressure sensor is arranged in such a way that it measures pressure in one heart chamber and the second pressure sensor is arranged that it measures pressure in a downstream vascular system.
- the heart chamber can be, for example, an atrium or a ventricle, while the downstream vascular system can be, for example, an arterial system.
- a fifth independent aspect of the invention is a system consisting of a blood pump and an inlet cannula, whereby the inlet cannula has a pressure sensor and the pressure sensor is arranged particularly at the tip of the inlet cannula. This allows for separated exchange of the components of the inlet cannula and the blood pump.
- the pressure sensor on the tip of the inlet cannula is arranged on the inside and/or the outside of the tip. It is thereby possible to measure the pressure directly in the chamber if it is mounted on the outside of the cannula, whereby a sensor placed on the inside of the tip of the inlet cannula measures the pressure within the pump system. This is possible when placing the pump in the ventricle as well as in the atrium.
- a further advantage is when an additional flow sensor is arranged in the system.
- this sensor can be placed on the inlet cannula.
- Flow measurement is also possible in a decoupled fashion.
- placement of a flow sensor on the outlet cannula or outlet connector is possible. This flow measurement is usually easier possible, since the flow channel is relatively large.
- This flow sensor technology may be provided additionally to the flow sensor technology integrated into the pump, or alternatively to it.
- outlet cannula is equipped with an outlet connector in which a pressure sensor is placed. This allows for pressure measurement at the pump outlet.
- the integration of the sensor in the periphery creates a separation of the complex technical entities of pump and sensor units. This results in risk minimisation during production. A change of the pump during treatment is not excluded. By a separating the components, one need not change the sensors.
- Pressure measurement of chamber pressure as well as systemic blood pressure in the downstream vascular system provide not only monitoring of the technical system, but also makes therapeutic monitoring possible.
- a final aspect of the invention relates to a procedure to produce a blood pump with a measuring device, wherein the coupling wedges are milled from the pump housing. This means that further attachment of the coupling wedges is not needed because they are automatically integrated into the pump housing.
- the coupling wedges are thereby positioned so that that a measurement occurs in the annular gap.
- a further advantage is that if a coupling wedge has an enclosing wall milled from the pump housing. This has the advantage that the coupling wedges from the three spatial directions are surrounded by a wall. They are therefore protected in these three spatial directions, and the wall need not be connected with the pump housing. Thus concomitant mounting electronic components of the measurement path can be done from above.
- the drill hole can be drilled in an axial direction.
- the wires s can be guided sidewards or in the direction of flow.
- a cover can be installed on the wall, so that the coupling wedges are hermetically sealed off from the pump environment.
- the measurement device is sealed off from influences from the outside, and is in particular water-sealed.
- the cover can be welded. This would produce a lasting, sealed connection.
- FIGS. 1 a and 1 b a schematic presentation of a longitudinal section through a blood pump with a measurement device and a cross-section through the blood pump with the measuring device.
- FIGS. 2 a and b a schematic representation of a transverse and longitudinal section through a blood pump with a measuring device with two measuring paths
- FIGS. 3 a, b and c a schematic presentation of a longitudinal section through a blood pump with a measuring device, a topview of the blood pump with the measurement device and a three-dimensional side view of the blood pump with the measuring device,
- FIGS. 4 a, b and c a schematic representation of a longitudinal section through a blood pump with a measuring device with two measuring paths, of which one has a sound barrier, a topview of the blood pump with the measuring device with two with two measuring paths of which one has a sound barrier and a three-dimensional side view of the blood pump with the measuring apparatus with two measuring paths of which one has a sound barrier,
- FIG. 5 a schematic representation of a cannula system with a blood pump with an inlet and an outlet cannula with an outlet connector with integrated pressure measurement at the pump inlet and outlet,
- FIG. 6 a schematic representation of a cannula system with a blood pump with an inlet and an outlet cannula with an outlet connector with integrated pressure measurement in the inlet cannula and an outlet connector,
- FIG. 7 a schematic representation of a system with a blood pump having an inlet cannula and an outlet cannula with pressure measurement integrated into the pump at the pump inlet and outlet with pressure measurement integrated in the inlet cannula and the outlet connector.
- FIG. 8 a schematic representation of a blood pump in its operation location in the blood system between the atrium and arterial system
- FIG. 9 a schematic representation of a system with a blood pump with an inlet and an outlet cannula with an outlet connector r with pressure measurement integrated into the pump inlet and outlet, here with integrated pressure measurement in the inlet cannula and an outlet connector as well as an integrated flow and temperature sensor technology,
- FIG. 10 a schematic representation of a blood pump in its operation location in the blood system between the ventricle and the arterial system
- FIG. 11 a schematic representation of a blood pump at its operation location in the blood system between the ventricle and arterial system, whereby the pump inlet is placed directly without use of an intermediate cannula in the heart chamber,
- FIG. 12 a schematic representation of a blood pump on location in the blood system between the atrium and arterial system, whereby the pump inlet is directly placed without use of an intermediate cannula in the heart chamber,
- FIG. 13 a schematic view of a section of the tip of an inlet cannula
- FIG. 14 a schematic representation of a cross-section of an outlet cannula with an outlet connector.
- a measurement device can be provided, as shown in FIGS. 1 a and 1 b, which allows for integrated flow measurement in the annular gap 3 .
- the measuring device consists of a measuring path 4 with two coupling wedges 5 , 6 and transducers 7 , 8 arranged on these.
- the measuring apparatus 2 is arranged in a hermetically sealed box 9 , consisting of a wall 10 and a cover 11 .
- a side wall of the wall 10 has a drill hole 12 , through which for operation and control of the measuring device 2 wires (not pictured) are guided sideways and to the inside of the pump.
- the coupling wedges 5 and 6 and the wall 10 of the box 9 are milled from the pump housing 13 .
- the transducers 7 , 8 are first welded and assembled and the appropriate wires (not pictured) for the operation and control of the transducers 7 , 8 are led through the drill hole 12 .
- the flow measuring unit 2 hermetically sealed.
- the blood flows through the pump 1 , shown schematically by the arrow 14 at the pump inlet 15 into the blood pump 1 and flows over the rotor 16 and through the annular gap 3 between the motor 17 and the pump housing 13 .
- the measuring device 2 is placed for integrated flow measurement over the annular gap 3 .
- the transducer 7 or the transducer 8 sends sound waves which move through the blood flow in the annular gap 3 and are reflected on the motor 17 , so that the other transducer 8 or 7 receives them. From the data obtained, the flow rate or the volume flow rate can then be determined in the annular gap 3 . In order to keep a direct transfer between the coupling wedges 5 and 6 as low as possible, the piece of the wall 18 of the pump housing 13 located between the coupling wedges is kept as thin as thin as possible.
- a blood pump 21 can have a measuring device with several measuring paths.
- two flow sensors 22 , 23 are arranged opposite of one another to allow simultaneous flow measurement over the annular gap 24 , one above the motor 25 and one below the motor 25 .
- the blood flows through the pump inlet 26 over the rotor 27 through the annular gap 24 between the motor 25 and the pump housing 28 , to then leave the blood pump 21 through the pump outlet 29 .
- the flow measurement is done by the flow sensors 22 and 23 each at annular gap 24 in which the flow is determined.
- a measurement path 32 on the blood pump 31 in FIG. 3 a - c consists of two coupling wedges 33 , 34 which are not surrounded by a box milled from the pump housing.
- the measuring path 32 is positioned in axial direction.
- the coupling wedges 33 , 34 are however again milled from the pump housing 35 .
- the coupling wedges 33 , 34 each show a coupling angle ⁇ , ⁇ of 30° perpendicular to the pump housing 35 .
- the outside diameter of the pump housing 35 in the area of the motor 36 is about 14 mm, the inner diameter is about 11 mm, whereas the diameter of the motor itself is approximately 8.5 mm.
- the annular gap 37 thus has a width of about 1.25 mm.
- the coupling wedges 33 and 34 are arranged at a distance of about 1.8 mm and each shows in flow direction a length of 4 mm, as well as a width of 4 mm perpendicular to the flow direction.
- the distance between the two tips 38 and 39 of the two coupling wedges 33 , 34 is approximately 7.8 mm.
- a second measuring path 40 is positioned with respective components.
- the measuring path 42 consisting of two coupling wedges 43 and 44 is placed in a radial orientation.
- This transducer has three sound walls 45 , 46 and 47 , which prevent transfer of sound from one coupling wedge directly to the next coupling wedge. The number of sound walls is however variable.
- a second radial measurement path 48 without acoustic breaker is provided.
- the coupling wedges 49 and 50 each on the outside show a coupling angle ⁇ , ⁇ of 30° to the perpendicular.
- a blood pump 61 When installed a blood pump 61 is integrated into a pump system 60 , see FIG. 5 .
- the pump is connected with an inlet cannula 62 and an outlet cannula with an outlet connector 63 .
- the inlet cannula 62 is connected by a tip 65 to the heart wall 66 .
- the blood flows over a tip 65 through the inlet cannula 62 into the pump inlet 67 , where it is pumped through the motor 68 operated with the rotor 69 through the blood pump 61 to exit again at the pump outlet 70 .
- an outlet connector 64 with the outlet cannula 63 is attached.
- the pressure is determined at the pressure sensor 71 at the pump inlet 67 and the pressure sensor 72 at the pump outlet 70 at both these locations in the system.
- the pressure can be measured at the tip 83 of the inlet cannula 82 , and the outlet connector 89 of the outlet cannula 90 by the relevant sensors 91 , 92 and 93 .
- sensor 91 measures the pressure distal to the heart wall 84 directly in the atrium
- the sensor 92 measures the pressure within the pump system 80 at the pump inlet 85
- the sensor 93 measures the pressure within the pump system 80 at the pump outlet 88 .
- the blood pump 81 also includes a rotor 86 and a motor 87 , through which the blood is transported.
- the blood pump 101 with rotor 102 and motor 103 has a flow sensor 104 and pressure sensors 105 , 106 at the pump inlet 107 and the pump outlet 108 .
- pressure sensors 109 , 111 are provided at the tip 110 of the inlet cannula 112 .
- the pressure sensor 111 is placed on the inside of the tip 110 and thus measures the pressure at that point, whereas the pressure sensor 109 is distal to the heart wall 113 on the outside of the tip 110 , and thus measures pressure in the atrium.
- the outlet cannula 114 at the outlet connector 115 includes a further pressure sensor 116 , which determines the pressure at this point.
- such a system 121 measures the pressure at four places on the pump system 121 consisting of the blood pump 122 , inlet cannula 123 and outlet cannula 124 , as presented in the operating condition in the blood system in FIG. 8 .
- the pressure directly in the atrium 125 the pressure at the pump inlet 126 , the pressure at the pump outlet 127 and the pressure at entry to the aorta at the location 128 .
- the pressure at pump inlet 126 can be measured by in the blood pump 122 integrated sensors, as well as by a sensor integrated in the inside of the inlet cannula 123 .
- the pressure at pump outlet 127 can be measured by a sensor integrated in the blood pump 122 , as well as through a sensor integrated into the outlet sensor. Furthermore, the arrangement of a sensor at the tip of the outlet connector is also possible on the outside in order to measure aortal pressure.
- the blood pump 132 includes a flow sensor 133 as well as a temperature sensor 134 .
- pressure sensors 137 , 138 are integrated in the pump inlet 135 as well as in the pump outlet 136 .
- the inlet cannula 139 also has a flow sensor 140 .
- a pressure sensor 142 is integrated into a cannula tip 141 on the inside of the tip 141 and a pressure sensor 143 is provided on the outside of the tip 141 distal to the heart wall 144 .
- the outlet cannula 145 in the outlet connector 146 has a pressure sensor 147 .
- the blood pump system 151 consisting of blood pump 154 with inflow cannula 155 and outlet cannula 156 may then make the measurements by the appropriate sensors at the points indicated.
- a pump system 161 or 171 as shown in FIGS. 11 and 12 , so that the pump inlet 162 , 172 of the blood pump 163 , 173 can be placed directly into a heart chamber without interposition of a cannula, namely in the ventricle 164 or in the atrium 174 .
- the outlet cannula 165 , 175 is introduced into the aorta 166 , 176 .
- One of the sensors placed on the outside of the blood inlet 162 , 172 can thus measure the chamber pressure. Also further flow and pressure sensors (not pictured) provide relevant data, such as pressure in the arterial system.
- the inlet cannula 181 on the heart-facing side of the inlet cannula 181 , has a tip 182 to which the cannula 183 is attached.
- the tip 182 is connected to the cannula 183 and engages at its tip with the heart wall 184 .
- a pressure sensor 185 is integrated into the tip 182 .
- An outlet cannula 191 as shown in FIG. 14 , has an outlet connector 192 , over which the graft or the outlet 193 is connected to the blood pump 194 .
- a pressure sensor 195 is integrated into the outlet connector 192 .
Abstract
The invention relates to a blood pump made of titanium with a measuring device for determining flow based on acoustic flow measurement methods, and a blood pump with a temperature sensor and/or a pressure sensor, and a system with a blood pump and an inlet cannula and/or an outlet connector and a method for producing a blood pump with a measuring device.
Description
- This application is a continuation of patent application Ser. No. 14/431,370, filed May 22, 2015, entitled PUMP, SYSTEM WITH A BLOOD PUMP AND METHOD FOR PRODUCING A BLOOD PUMP, which is a 371 of International Application No. PCT/DE2013/000540, filed Sep. 25, 2013 and claimed priority to U.S. Provisional Application Ser. No. 61/744,693, filed Oct. 2, 2012 and claimed priority to German Application Nos. DE 10 2013 012 391.7, filed Jul. 26, 2013 and DE 10 2012 018 893.2, filed Sep. 26, 2012, the entirety of all of which are incorporated herein by reference.
- n/a
- The invention relates to a blood pump made of titanium with a measuring device for to determine the flow based on acoustic flow measurement processes as well as a blood pump with a temperature sensor and/or a pressure sensor as well as a system with a blood pump and an inlet cannula and/or an outlet cannula with an outlet connector as well as a procedure to produce a blood pump with a measurement device.
- The task of this invention is to improve current state-of-the-art blood pumps.
- This is, in accordance with the first aspect of the invention, a titanium blood pump with a measurement device to determine flow, based on acoustic flow measurement processes, whereby the measurement device has a measurement path with two coupling wedges with two transducers arranged with them, and the measurement device on a blood pump is arranged in such a way that an installation functions as a reflector.
- An installation is any component that is arranged inside the pump. Any installation can be used as a reflector, so that the measurement device can be freely located on the blood pump. In particular, no space free of installations must be found for the measurement. This allows a more compact design.
- Acoustic flow measurement techniques permit the determination of the flow of fluids through analysis of the flow of modulated acoustic waves. In a paired sensor unit consisting transducers acting as alternating transmitters and receivers, it can principally assess the relative transit time differences (in and against the flow direction), beam deflection (shunting) and changes in phase, amplitude and frequency of the acoustic waves. Also, scattering effects can be evaluated. So effects, such as Doppler effects or entrainment effects can be determined. A preferred embodiment is to assess the relative transit time.
- In order to achieve a measurement effect and to receive the transmitted sound waves, the transducers must be installed in a specific angle range to the flow. This is done by mounting on so-called coupling wedges. The coupling wedges are firmly connected to the blood pump. This is preferably carried out by appropriate cut-outs on the pump housing. A variant is the gluing or welding of coupling wedges to the desired measurement points.
- It is desirable for a blood pump to be able to determine the flow or volume, without invasively accessing the flow stream. Thus it is especially preferable not to have the transducers in contact with the bloodstream.
- In a blood pump, the fluid being measured is blood. The blood pump is used to support or to replace the human heart. The blood pump satisfies the requirements for fully implantable medical devices.
- Due to its corrosion resistance compared to other metals, titanium is used as the biomaterial for blood pumps. Other biocompatible materials can be used in pump construction, such as ceramics like zirconium oxide.
- Advantageously, the installation is a motor and flow is measured in an annular gap. It is thus possible to integrate flow measurement in the main blood pump section. This makes it possible to have a compact structure, especially integrated wire management.
- It is advantageous to have several measurement paths along the circumference. This thus increases measurement accuracy. Thus various spatial arrangements for the measurement paths, such as in the direction of the main axis or crossing the main axis or in the diagonal direction are possible. Thus even complex flow patterns can be detected.
- In particular, the measurement paths can be arranged on opposite sites. A maximum distance between the measuring points can be achieved. In addition, an arrangement on the pump the housing is easily possible.
- It is advantageous to place a sound barrier between the coupling wedges. This can minimise the transmission directly from one coupling wedge to another. The sound is thus ideally mainly transmitted through the fluid. Also other measures can prevent direct transmission of the sound from one coupling wedge to another coupling wedge, such as through filling with a damping medium, reducing the wall thickness of the pump housing between the coupling wedges or a milling of grooving in the wall between the two coupling wedges. In particular, a combination of these measures is advantageous.
- It is advantageous if the measurement device is hermetically sealed in a space via the pump environment. If the measurement device is insulated from the environment in such a manner, a design as an implantable blood pump is particularly possible.
- It is advantageous if a grommet is arranged between the space and the interior of the pump. In this way, all wires can be led in the interior of the pump.
- The grommet can be arranged along a longitudinal axis. Thus the path can also show a radial skew.
- A second independent aspect of the invention relates to a blood pump which has a temperature sensor. The temperature sensor can determine the temperature of the blood while the blood pump is operating. High temperatures lead to blood damage and should therefore be avoided.
- A third independent aspect of the invention relates to a blood pump whereby it has an integrated pressure sensor. The pressure sensor can either be an absolute pressure sensor or a differential pressure sensor. This pressure sensor can be integrated into a pump inlet and/or pump outlet. It can gather data on pressure conditions at both these sites on the pump. Through measurement at both locations, flow can determined using a stored characteristic map. In particular, a pressure sensor can be integrated in the pump inlet when the pump inlet is placed directly into the ventricle without the interposition of a cannula. Thus an arrangement of the sensor on the outside of the pump inlet makes sense in order to measure the chamber pressure.
- It is particularly advantageous here to have a combination of pressure and flow sensor technology on the pump in order to derive information on thrombi, suction or recovery. Due to the connection between the pump and the sensor/cannula there is no installation at the cannula.
- A fourth independent aspect of the invention relates to a blood pump which has a first pressure sensor and a second pressure sensor, whereby the first pressure sensor is arranged in such a way that it measures pressure in one heart chamber and the second pressure sensor is arranged that it measures pressure in a downstream vascular system. The heart chamber can be, for example, an atrium or a ventricle, while the downstream vascular system can be, for example, an arterial system.
- A fifth independent aspect of the invention is a system consisting of a blood pump and an inlet cannula, whereby the inlet cannula has a pressure sensor and the pressure sensor is arranged particularly at the tip of the inlet cannula. This allows for separated exchange of the components of the inlet cannula and the blood pump.
- It is advantageous if the pressure sensor on the tip of the inlet cannula is arranged on the inside and/or the outside of the tip. It is thereby possible to measure the pressure directly in the chamber if it is mounted on the outside of the cannula, whereby a sensor placed on the inside of the tip of the inlet cannula measures the pressure within the pump system. This is possible when placing the pump in the ventricle as well as in the atrium.
- A further advantage is when an additional flow sensor is arranged in the system. For example, this sensor can be placed on the inlet cannula. Flow measurement is also possible in a decoupled fashion. Also placement of a flow sensor on the outlet cannula or outlet connector is possible. This flow measurement is usually easier possible, since the flow channel is relatively large. This flow sensor technology may be provided additionally to the flow sensor technology integrated into the pump, or alternatively to it.
- A further independent aspect of the invention is that the outlet cannula is equipped with an outlet connector in which a pressure sensor is placed. This allows for pressure measurement at the pump outlet. The integration of the sensor in the periphery (inlet cannula, outlet cannula with an outlet connector) creates a separation of the complex technical entities of pump and sensor units. This results in risk minimisation during production. A change of the pump during treatment is not excluded. By a separating the components, one need not change the sensors.
- Pressure measurement of chamber pressure as well as systemic blood pressure in the downstream vascular system provide not only monitoring of the technical system, but also makes therapeutic monitoring possible.
- A final aspect of the invention relates to a procedure to produce a blood pump with a measuring device, wherein the coupling wedges are milled from the pump housing. This means that further attachment of the coupling wedges is not needed because they are automatically integrated into the pump housing. Advantageously, the coupling wedges are thereby positioned so that that a measurement occurs in the annular gap.
- A further advantage is that if a coupling wedge has an enclosing wall milled from the pump housing. This has the advantage that the coupling wedges from the three spatial directions are surrounded by a wall. They are therefore protected in these three spatial directions, and the wall need not be connected with the pump housing. Thus concomitant mounting electronic components of the measurement path can be done from above.
- Further, one can drill from within the walls to the inside of the pump. Later, wires can be guided in this drill hole which lead from the inside of the wall to the inside of the pump.
- The drill hole can be drilled in an axial direction. Thus, the wires s can be guided sidewards or in the direction of flow.
- Finally, a cover can be installed on the wall, so that the coupling wedges are hermetically sealed off from the pump environment. Thus the measurement device is sealed off from influences from the outside, and is in particular water-sealed.
- Thus the cover can be welded. This would produce a lasting, sealed connection.
- The invention will be explained in more detail with reference to drawings and implementation examples below. These show:
-
FIGS. 1a and 1b a schematic presentation of a longitudinal section through a blood pump with a measurement device and a cross-section through the blood pump with the measuring device. -
FIGS. 2a and b a schematic representation of a transverse and longitudinal section through a blood pump with a measuring device with two measuring paths, -
FIGS. 3a, b and c a schematic presentation of a longitudinal section through a blood pump with a measuring device, a topview of the blood pump with the measurement device and a three-dimensional side view of the blood pump with the measuring device, -
FIGS. 4a, b and c a schematic representation of a longitudinal section through a blood pump with a measuring device with two measuring paths, of which one has a sound barrier, a topview of the blood pump with the measuring device with two with two measuring paths of which one has a sound barrier and a three-dimensional side view of the blood pump with the measuring apparatus with two measuring paths of which one has a sound barrier, -
FIG. 5 a schematic representation of a cannula system with a blood pump with an inlet and an outlet cannula with an outlet connector with integrated pressure measurement at the pump inlet and outlet, -
FIG. 6 a schematic representation of a cannula system with a blood pump with an inlet and an outlet cannula with an outlet connector with integrated pressure measurement in the inlet cannula and an outlet connector, -
FIG. 7 a schematic representation of a system with a blood pump having an inlet cannula and an outlet cannula with pressure measurement integrated into the pump at the pump inlet and outlet with pressure measurement integrated in the inlet cannula and the outlet connector. -
FIG. 8 a schematic representation of a blood pump in its operation location in the blood system between the atrium and arterial system, -
FIG. 9 a schematic representation of a system with a blood pump with an inlet and an outlet cannula with an outlet connector r with pressure measurement integrated into the pump inlet and outlet, here with integrated pressure measurement in the inlet cannula and an outlet connector as well as an integrated flow and temperature sensor technology, -
FIG. 10 a schematic representation of a blood pump in its operation location in the blood system between the ventricle and the arterial system, -
FIG. 11 a schematic representation of a blood pump at its operation location in the blood system between the ventricle and arterial system, whereby the pump inlet is placed directly without use of an intermediate cannula in the heart chamber, -
FIG. 12 a schematic representation of a blood pump on location in the blood system between the atrium and arterial system, whereby the pump inlet is directly placed without use of an intermediate cannula in the heart chamber, -
FIG. 13 a schematic view of a section of the tip of an inlet cannula and -
FIG. 14 a schematic representation of a cross-section of an outlet cannula with an outlet connector. - In a blood pump 1, a measurement device can be provided, as shown in
FIGS. 1a and 1 b, which allows for integrated flow measurement in the annular gap 3. The measuring device consists of a measuring path 4 with two coupling wedges 5, 6 and transducers 7, 8 arranged on these. The measuring apparatus 2 is arranged in a hermetically sealed box 9, consisting of awall 10 and acover 11. A side wall of thewall 10 has adrill hole 12, through which for operation and control of the measuring device 2 wires (not pictured) are guided sideways and to the inside of the pump. In production, the coupling wedges 5 and 6 and thewall 10 of the box 9 are milled from thepump housing 13. Before thecover 11 is applied and sealed, the transducers 7, 8 are first welded and assembled and the appropriate wires (not pictured) for the operation and control of the transducers 7, 8 are led through thedrill hole 12. Thus installation from the top is possible. Only after application and welding of thecover 11 is the flow measuring unit 2 hermetically sealed. In operation, the blood flows through the pump 1, shown schematically by thearrow 14 at thepump inlet 15 into the blood pump 1 and flows over therotor 16 and through the annular gap 3 between themotor 17 and thepump housing 13. In order to measure the flow rate or the volume flow rate of thisblood flow 14 in the annular gap, the measuring device 2 is placed for integrated flow measurement over the annular gap 3. In operation alternately the transducer 7 or the transducer 8 sends sound waves which move through the blood flow in the annular gap 3 and are reflected on themotor 17, so that the other transducer 8 or 7 receives them. From the data obtained, the flow rate or the volume flow rate can then be determined in the annular gap 3. In order to keep a direct transfer between the coupling wedges 5 and 6 as low as possible, the piece of thewall 18 of thepump housing 13 located between the coupling wedges is kept as thin as thin as possible. - As shown in
FIG. 2 , ablood pump 21 can have a measuring device with several measuring paths. Thus twoflow sensors annular gap 24, one above themotor 25 and one below themotor 25. Also here, when operating, the blood flows through thepump inlet 26 over therotor 27 through theannular gap 24 between themotor 25 and thepump housing 28, to then leave theblood pump 21 through thepump outlet 29. Thus the flow measurement is done by theflow sensors annular gap 24 in which the flow is determined. - A
measurement path 32 on theblood pump 31 inFIG. 3a -c, consists of twocoupling wedges path 32 is positioned in axial direction. Thecoupling wedges pump housing 35. Thecoupling wedges pump housing 35. The outside diameter of thepump housing 35 in the area of themotor 36 is about 14 mm, the inner diameter is about 11 mm, whereas the diameter of the motor itself is approximately 8.5 mm. Theannular gap 37 thus has a width of about 1.25 mm. Thecoupling wedges tips coupling wedges second measuring path 40 is positioned with respective components. - Also, on the
blood pump 41 inFIG. 4a-c the measuringpath 42, consisting of twocoupling wedges sound walls radial measurement path 48 without acoustic breaker is provided. Thecoupling wedges - When installed a
blood pump 61 is integrated into apump system 60, seeFIG. 5 . Thus the pump is connected with aninlet cannula 62 and an outlet cannula with anoutlet connector 63. Theinlet cannula 62 is connected by atip 65 to theheart wall 66. The blood flows over atip 65 through theinlet cannula 62 into thepump inlet 67, where it is pumped through themotor 68 operated with therotor 69 through theblood pump 61 to exit again at thepump outlet 70. To this, anoutlet connector 64 with theoutlet cannula 63 is attached. The pressure is determined at thepressure sensor 71 at thepump inlet 67 and thepressure sensor 72 at thepump outlet 70 at both these locations in the system. Thus, not only monitoring of the technical system, but also therapeutic monitoring is possible. - Alternatively, as shown in the
blood pump system 80 inFIG. 6 , the pressure can be measured at thetip 83 of theinlet cannula 82, and theoutlet connector 89 of theoutlet cannula 90 by therelevant sensors sensor 91 measures the pressure distal to theheart wall 84 directly in the atrium, thesensor 92 measures the pressure within thepump system 80 at thepump inlet 85, and thesensor 93 measures the pressure within thepump system 80 at thepump outlet 88. Theblood pump 81 also includes arotor 86 and amotor 87, through which the blood is transported. - Also, combined flow and pressure measurement is possible, as is shown in the
blood pump system 100 with theblood pump 101, shown inFIG. 7 . Here theblood pump 101 withrotor 102 andmotor 103 has aflow sensor 104 andpressure sensors 105, 106 at thepump inlet 107 and thepump outlet 108. In addition, alsopressure sensors tip 110 of theinlet cannula 112. Here, thepressure sensor 111 is placed on the inside of thetip 110 and thus measures the pressure at that point, whereas thepressure sensor 109 is distal to theheart wall 113 on the outside of thetip 110, and thus measures pressure in the atrium. In addition, theoutlet cannula 114 at theoutlet connector 115 includes afurther pressure sensor 116, which determines the pressure at this point. There are sensors integrated in this system in theblood pump 101 at itsinlet 107 andoutlet 108, as well as in thetip 110 of theinlet cannula 112 and theoutlet connector 115 of theoutlet cannula 114. Thus there is at least one partial separation of the complex technical units of thepump 101 and the sensors. This minimises risk during production and during treatment switching of thepump 101 is not excluded. A change of the sensor technology is then only partially necessary. - Altogether, such a
system 121 measures the pressure at four places on thepump system 121 consisting of theblood pump 122,inlet cannula 123 andoutlet cannula 124, as presented in the operating condition in the blood system inFIG. 8 . Namely, the pressure directly in theatrium 125, the pressure at thepump inlet 126, the pressure at thepump outlet 127 and the pressure at entry to the aorta at thelocation 128. Thus the pressure atpump inlet 126 can be measured by in theblood pump 122 integrated sensors, as well as by a sensor integrated in the inside of theinlet cannula 123. Also the pressure atpump outlet 127 can be measured by a sensor integrated in theblood pump 122, as well as through a sensor integrated into the outlet sensor. Furthermore, the arrangement of a sensor at the tip of the outlet connector is also possible on the outside in order to measure aortal pressure. - As shown in
FIG. 9 , one could also imagine ablood pump system 131 which unites all sensor types. Thus theblood pump 132 includes aflow sensor 133 as well as atemperature sensor 134. Furthermore,pressure sensors pump inlet 135 as well as in thepump outlet 136. Theinlet cannula 139 also has aflow sensor 140. In addition, apressure sensor 142 is integrated into a cannula tip 141 on the inside of the tip 141 and apressure sensor 143 is provided on the outside of the tip 141 distal to theheart wall 144. In addition, theoutlet cannula 145 in theoutlet connector 146 has apressure sensor 147. Thus, combined flow and pressure measurement is possible, which are both incorporated into theblood pump 132, and decoupled from the blood pump in theinlet cannula 139 andoutlet cannula 145 at different locations. - As an alternative to the location presented in
FIG. 8 in theatrium 152, one can also implant directly into theventricle 153. Theblood pump system 151 consisting ofblood pump 154 withinflow cannula 155 andoutlet cannula 156 may then make the measurements by the appropriate sensors at the points indicated. - In addition, it is possible that one can place a
pump system FIGS. 11 and 12 , so that thepump inlet blood pump 163, 173 can be placed directly into a heart chamber without interposition of a cannula, namely in theventricle 164 or in theatrium 174. Theoutlet cannula aorta blood inlet 162, 172 (not pictured) can thus measure the chamber pressure. Also further flow and pressure sensors (not pictured) provide relevant data, such as pressure in the arterial system. - In detail, the
inlet cannula 181, as is shown inFIG. 13 , on the heart-facing side of theinlet cannula 181, has atip 182 to which thecannula 183 is attached. Thetip 182 is connected to thecannula 183 and engages at its tip with theheart wall 184. In addition, a pressure sensor 185 is integrated into thetip 182. - An
outlet cannula 191, as shown inFIG. 14 , has anoutlet connector 192, over which the graft or theoutlet 193 is connected to theblood pump 194. Apressure sensor 195 is integrated into theoutlet connector 192.
Claims (23)
1. Blood pump made of titanium with a measuring device to determine flow based on acoustic flow measurement processes, whereby the measuring device has a measuring path with two coupling wedges with two transducers placed on these,
characterised by the fact that the measuring device is attached to the blood pump in such a way that an installation functions as a reflector.
2. Blood pump as per claim 1 , characterised by the fact that the installation is a motor and that the flow is measured in an annular gap.
3. Blood pump as per claim 1 or claim 2 , characterised by the fact that along the circumference, several measuring paths are arranged.
4. Blood pump as per claim 3 , characterised by the, fact that the measurement paths are placed on opposite sides.
5. Blood pump according to one of the preceding claims, characterised by the fact that that a sound wall is arranged between the coupling wedges.
6. Blood pump according to one of the preceding claims, characterised by the fact that the measuring device is sealed hermetically in a space via the pump environment.
7. Blood pump as per claim 6 , characterised by the fact that a grommet is arranged between the space and the inside of the pump.
8. Blood pump as per claim 6 or claim 7 , characterised by the fact that the grommet is arranged along the longitudinal axis.
9. Blood pump, in particular according to one of claims 1 to 8 , characterised by the fact that it comprises a temperature sensor.
10. Blood pump, in particular according to one of claims 1 to 9 , characterised by the fact that
it comprises an integrated pressure sensor.
11. Blood pump as per claim 10 , characterised by the fact that the pressure sensor is placed at a pump inlet and/or a pump outlet.
12. Blood pump in particular according to claim 10 or claim 11 , characterised by the fact that it comprises a first pressure sensor and a second pressure sensor, wherein
the first pressure sensor is arranged in such a way that it measures pressure in one heart chamber,
and the second pressure sensor is arranged in such a way that it measures pressure in the downstream vascular system.
13. System comprising a blood pump, especially a blood pump as per one of the claims 1 to 12 , and an inlet cannula, characterised by the fact that it has a pressure sensor in the inlet cannula, whereby the pressure sensor is arranged in particular at the tip of the inlet cannula.
14. System as per claim 13 , characterised by the fact that the pressure sensor placed on the tip of the inlet cannula is placed on the inside and/or the outside of the tip.
15. System according to one of claim 13 or 14 , characterised by the fact that a flow sensor is arranged at the inlet cannula.
16. System according to one of claims 13 to 15 , characterised by the fact that a flow sensor is arranged at the outlet connector.
17. System with a blood pump in particular according to one of claims 12 to 16 characterised by the fact that the system comprises an outlet cannula with an outlet connector and the outlet connector has a pressure sensor.
18. Process for the preparation of a blood pump with a measuring device, in particular according to one of claims 1 to 12 , characterised by the fact that the coupling wedges are cut from the pump housing.
19. Process as per claim 18 , characterised by the fact that the wall which encloses one of the coupling wedges is milled from the pump housing.
20. Process as per claim 19 , characterised by the fact that a drill hole is drilled from inside the wall to the interior of the pump.
21. Process as per claim 20 , characterised by the fact that a drill hole is drilled in an axial direction.
22. Procedure as per one of claims 19 to 21 , characterised by the fact that a cover is put on the wall, so that coupling wedges are hermetically sealed from the pump environment.
23. Process as per claim 22 , characterised by the fact that the cover is welded.
Priority Applications (1)
Application Number | Priority Date | Filing Date | Title |
---|---|---|---|
US15/411,091 US20180161487A1 (en) | 2012-09-26 | 2017-01-20 | Pump, system with a blood pump and method for producing a blood pump |
Applications Claiming Priority (8)
Application Number | Priority Date | Filing Date | Title |
---|---|---|---|
DE102012018893.2 | 2012-09-26 | ||
DE102012018893 | 2012-09-26 | ||
US201261744693P | 2012-10-02 | 2012-10-02 | |
DE102013012391.7 | 2013-07-26 | ||
DE102013012391.7A DE102013012391A1 (en) | 2012-09-26 | 2013-07-26 | Pump, system with a blood pump and method of making a blood pump |
PCT/DE2013/000540 WO2014048411A2 (en) | 2012-09-26 | 2013-09-25 | Pump, system with a blood pump and method for producing a blood pump |
US201514431370A | 2015-05-22 | 2015-05-22 | |
US15/411,091 US20180161487A1 (en) | 2012-09-26 | 2017-01-20 | Pump, system with a blood pump and method for producing a blood pump |
Related Parent Applications (2)
Application Number | Title | Priority Date | Filing Date |
---|---|---|---|
US14/431,370 Continuation US9572916B2 (en) | 2012-09-26 | 2013-09-25 | Pump, system with a blood pump and method for producing a blood pump |
PCT/DE2013/000540 Continuation WO2014048411A2 (en) | 2012-09-26 | 2013-09-25 | Pump, system with a blood pump and method for producing a blood pump |
Publications (1)
Publication Number | Publication Date |
---|---|
US20180161487A1 true US20180161487A1 (en) | 2018-06-14 |
Family
ID=50235422
Family Applications (2)
Application Number | Title | Priority Date | Filing Date |
---|---|---|---|
US14/431,370 Expired - Fee Related US9572916B2 (en) | 2012-09-26 | 2013-09-25 | Pump, system with a blood pump and method for producing a blood pump |
US15/411,091 Abandoned US20180161487A1 (en) | 2012-09-26 | 2017-01-20 | Pump, system with a blood pump and method for producing a blood pump |
Family Applications Before (1)
Application Number | Title | Priority Date | Filing Date |
---|---|---|---|
US14/431,370 Expired - Fee Related US9572916B2 (en) | 2012-09-26 | 2013-09-25 | Pump, system with a blood pump and method for producing a blood pump |
Country Status (4)
Country | Link |
---|---|
US (2) | US9572916B2 (en) |
EP (1) | EP2900294A2 (en) |
DE (2) | DE102013012391A1 (en) |
WO (1) | WO2014048411A2 (en) |
Families Citing this family (9)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
US10449274B2 (en) | 2013-06-26 | 2019-10-22 | Circulite, Inc. | System and method of facilitating connection between cannulae and a blood pump |
EP3108809A1 (en) * | 2015-06-22 | 2016-12-28 | Berlin Heart GmbH | Method and device for measuring pressure on a patient's heart |
US9717830B2 (en) | 2015-10-28 | 2017-08-01 | Circulite, Inc. | Inflow cannula and blood flow assist system |
EP3205359B1 (en) * | 2016-02-11 | 2018-08-29 | Abiomed Europe GmbH | Blood pump system |
EP3509662B1 (en) * | 2016-09-06 | 2020-12-30 | Heartware, Inc. | Integrated sensors for intraventricular vad |
CN110997032A (en) * | 2017-08-18 | 2020-04-10 | 心脏器械股份有限公司 | Thrombus detection and removal using flexible electronic sensors and emitters |
EP3706819A1 (en) * | 2017-11-06 | 2020-09-16 | Heartware, Inc. | Vad with intra-housing fluid access ports |
WO2019210365A1 (en) * | 2018-05-03 | 2019-11-07 | Northern Development AS | Implantable device and delivery method |
CN116672596A (en) * | 2022-02-23 | 2023-09-01 | 上海微创心力医疗科技有限公司 | Temperature control method, device, control equipment and storage medium of catheter pump |
Family Cites Families (11)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
US3425064A (en) | 1966-05-09 | 1969-02-04 | Parametrics Inc | Transducer for artificial heart |
US4227407A (en) * | 1978-11-30 | 1980-10-14 | Cornell Research Foundation, Inc. | Volume flow measurement system |
CA1327838C (en) * | 1988-06-13 | 1994-03-15 | Fred Zacouto | Implantable device to prevent blood clotting disorders |
US5453576A (en) * | 1994-10-24 | 1995-09-26 | Transonic Systems Inc. | Cardiovascular measurements by sound velocity dilution |
EP2058017A3 (en) * | 1996-10-04 | 2011-02-23 | Tyco Healthcare Group LP | Circulatory support system |
US5865749A (en) * | 1996-11-07 | 1999-02-02 | Data Sciences International, Inc. | Blood flow meter apparatus and method of use |
US6183412B1 (en) * | 1997-10-02 | 2001-02-06 | Micromed Technology, Inc. | Implantable pump system |
US6293901B1 (en) * | 1997-11-26 | 2001-09-25 | Vascor, Inc. | Magnetically suspended fluid pump and control system |
US8402974B2 (en) * | 2006-05-30 | 2013-03-26 | Coherex Medical, Inc. | Methods, systems, and devices for sensing, measuring, and controlling closure of a patent foramen ovale |
US20080133006A1 (en) * | 2006-10-27 | 2008-06-05 | Ventrassist Pty Ltd | Blood Pump With An Ultrasonic Transducer |
EP2037236A3 (en) * | 2007-09-11 | 2011-01-19 | Levitronix LLC | Calibration method of a flow measurement in a flow system and a flow system for carrying out the method |
-
2013
- 2013-07-26 DE DE102013012391.7A patent/DE102013012391A1/en not_active Withdrawn
- 2013-09-25 WO PCT/DE2013/000540 patent/WO2014048411A2/en active Application Filing
- 2013-09-25 US US14/431,370 patent/US9572916B2/en not_active Expired - Fee Related
- 2013-09-25 EP EP13789154.5A patent/EP2900294A2/en not_active Withdrawn
- 2013-09-25 DE DE112013004741.1T patent/DE112013004741A5/en not_active Withdrawn
-
2017
- 2017-01-20 US US15/411,091 patent/US20180161487A1/en not_active Abandoned
Also Published As
Publication number | Publication date |
---|---|
US20150335804A1 (en) | 2015-11-26 |
DE102013012391A1 (en) | 2014-03-27 |
WO2014048411A2 (en) | 2014-04-03 |
EP2900294A2 (en) | 2015-08-05 |
DE112013004741A5 (en) | 2016-06-30 |
US9572916B2 (en) | 2017-02-21 |
WO2014048411A3 (en) | 2014-08-28 |
Similar Documents
Publication | Publication Date | Title |
---|---|---|
US20180161487A1 (en) | Pump, system with a blood pump and method for producing a blood pump | |
CN109641092B (en) | Integrated sensor for intraventricular VAD | |
US8876685B2 (en) | Blood pump with an ultrasound transducer | |
JP7382648B2 (en) | Analyzer and method for analyzing fluid viscosity | |
US10307070B2 (en) | Intravascular pressure and flow data diagnostic systems, devices, and methods | |
US6704590B2 (en) | Doppler guiding catheter using sensed blood turbulence levels | |
US10213537B2 (en) | Ventricular assist devices and integrated sensors thereof | |
US20080167566A1 (en) | Systems and methods for determining systolic time intervals | |
US20160000403A1 (en) | Method and Apparatus for Monitoring Cardiac Output | |
US20070208293A1 (en) | Methods and devices for noninvasive pressure measurment in ventricular shunts | |
US20210379360A1 (en) | Implantable device for determining a fluid volume flow through a blood vessel | |
TW201507694A (en) | An improved blood pressure monitoring method | |
CN110573089A (en) | Intravascular flow and pressure measurements | |
US20210346676A1 (en) | Method for determining a flow rate of a fluid flowing through an implanted vascular support system, and implantable vascular support system | |
EP2314214B1 (en) | Cerebral compliance monitoring | |
US20220032032A1 (en) | Implantable vascular support system | |
JP6721707B2 (en) | Method and apparatus for improving blood flow velocity measurement | |
JP2009240348A (en) | Blood pump system | |
CN111885962A (en) | Medical device comprising a sensor array and system for measuring | |
JP3565982B2 (en) | Catheter with sensor function | |
WO2020240214A3 (en) | System and method for measuring pressure waves in dialysis lines | |
WO2023196600A9 (en) | System and method for monitoring physiological parameters based on cerebrospinal fluid pressures taken at two or more locations |
Legal Events
Date | Code | Title | Description |
---|---|---|---|
AS | Assignment |
Owner name: CIRCULITE GMBH, FLORIDA Free format text: ASSIGNMENT OF ASSIGNORS INTEREST;ASSIGNOR:MARSEILLE, OLIVER;REEL/FRAME:042548/0611 Effective date: 20161010 |
|
STPP | Information on status: patent application and granting procedure in general |
Free format text: FINAL REJECTION MAILED |
|
STCB | Information on status: application discontinuation |
Free format text: ABANDONED -- FAILURE TO RESPOND TO AN OFFICE ACTION |