CN219539245U - Ventricular assist device - Google Patents

Abstract

The utility model provides a ventricular assist device, comprising an inner assembly, an outer assembly and a blood pump; the internal component comprises a secondary winding and a winding bracket, the secondary winding is connected with the blood pump, the secondary winding, the winding bracket and the blood pump are all used for being implanted into a body, and the secondary winding is used for being wound on the winding bracket; the external component comprises a primary winding arranged outside the body, and the primary winding is used for being wound on the winding bracket; the primary winding is configured to provide self energy to the secondary winding, which is configured to provide received energy to the blood pump. The device can safely and reliably complete the charging process with high efficiency, is not easy to cause wound infection, and can greatly improve the survival rate of the operation of patients and the life quality after the operation.

Description

Ventricular assist device

Technical Field

The utility model relates to the technical field of medical equipment, in particular to a ventricular assist device.

Background

At present, the power supply of the ventricular assist device is mostly transmitted by using a percutaneous cable, and the percutaneous cable needs to pass through the skin of a human body (for example, pass through the skin of an abdomen), so that infection is often caused at a skin wound. Patients often need to be hospitalized for multiple times after operation due to percutaneous cable wound infection, and severe wound infection has high mortality rate and seriously affects further popularization of percutaneous cable transmission power supply. In addition, the wounds of the percutaneous cables need to be frequently disinfected and cleaned, which also causes inconvenience to the implanted patient.

Yet another power supply mode of the ventricular assist device is a wireless charging technology, and application of the wireless charging technology to the ventricular assist device is a hot spot of research in recent years. Wireless charging can solve the problem of infection caused by power transmission through a percutaneous cable, but an internal coil and an external coil which need to transmit power in the wireless charging technology are always opposite. During actual use, the patient is unconscious during sleep, and because the external coil is positioned in the wearing equipment, the movement or turning over of the patient easily causes dislocation of the external coil and the internal coil in the wearing equipment, thereby influencing the energy transmission efficiency of wireless charging.

Disclosure of Invention

The utility model aims to provide a ventricular assist device which can always keep the relative positions of a secondary winding and a primary winding fixed in the charging process, so that the charging process can be safely, reliably and efficiently completed, and the survival rate and the life quality of patients after operation are greatly improved.

To achieve the above object, the present utility model provides a ventricular assist device including an inner member, an outer member, and a blood pump; the internal component comprises a secondary winding and a winding bracket, the secondary winding is connected with the blood pump, the secondary winding, the winding bracket and the blood pump are all used for being implanted into a body, and the secondary winding is used for being wound on the winding bracket; the external component comprises a primary winding arranged outside the body, and the primary winding is used for being wound on the winding bracket; the primary winding is configured to provide self energy to the secondary winding, which is configured to provide received energy to the blood pump.

Optionally, the wire winding support is sleeve structure, the secondary winding with the primary winding is all followed wire winding support's circumference coiling is in on the wire winding support.

Optionally, a groove penetrating along the circumferential direction is formed in the side wall of the winding support, and the secondary winding and the primary winding are wound in the groove.

Optionally, the winding support is perpendicular to the skin surface, the winding support is close to the opening of one end for skin along the axial direction, and the winding support is sealed away from one end for skin along the axial direction.

Optionally, the winding position of the primary winding on the winding bracket corresponds to the winding position of the secondary winding on the winding bracket.

Optionally, the material of the winding bracket is one of soft magnetic material, ferrite and nonmetallic material.

Optionally, the outer wall of the winding bracket and the outer surface wall of the secondary winding are coated with medical polymer coatings.

Optionally, the internal assembly further comprises a built-in controller, wherein a distal end of the built-in controller is connected with the blood pump, a proximal end of the built-in controller is connected with the secondary winding, and the built-in controller is used for receiving energy transferred by the secondary winding and transferring the energy to the blood pump.

Optionally, the internal assembly further comprises an internal battery for connection with the internal controller, the internal battery for providing energy to the blood pump through the internal controller.

Optionally, the external component further comprises a system controller and an external battery, wherein one end of the system controller is connected with the primary winding, and the other end of the system controller is connected with the external battery; the system controller is used for receiving energy transmitted by the external battery and transmitting the energy to the primary winding.

Optionally, the internal assembly further comprises a backup cable, a distal end of the backup cable is connected with the blood pump, a proximal end of the backup cable is implanted under the skin, and the backup cable is used for connecting an external device to supply energy to the blood pump.

The ventricular assist device provided by the utility model comprises an internal component, an external component and a blood pump; the internal component comprises a secondary winding and a winding bracket, the secondary winding is connected with the blood pump, the secondary winding, the winding bracket and the blood pump are all used for being implanted into a body, and the secondary winding is used for being wound on the winding bracket; the external component comprises a primary winding arranged outside the body, and the primary winding is used for being wound on the winding bracket; the primary winding is configured to provide self energy to the secondary winding, which is configured to provide received energy to the blood pump.

So configured, the ventricular assist device adopts the wire winding support to couple energy, and can realize the power supply to the blood pump by carrying out energy transmission between the primary winding and the secondary winding, and because the secondary winding and the primary winding are firmly coupled together through the wire winding support, the relative positions of the secondary winding and the primary winding can be fixed in the whole charging process, thereby the power supply process can be safely, reliably, efficiently and stably completed, wound infection is not easy to be caused, the problem that an internal coil and an external coil cannot be always opposite in wireless charging is avoided, and the survival rate and the life quality of patients after operation are greatly improved.

In addition, the utility model can implant the built-in battery and the standby cable in the patient, so that the built-in battery can supply short-term energy to the blood pump when the power supply system cannot work, and can continuously supply power to the blood pump through the standby cable after seeking help, so that the utility model can be used as a standby power supply scheme of the blood pump to further ensure the life safety of the patient.

Drawings

FIG. 1 is a schematic view of an application scenario of a central room auxiliary device according to a preferred embodiment of the present utility model;

FIG. 2 is an enlarged schematic view of a portion of the structure of FIG. 1;

FIG. 3 is a schematic diagram of a magnetic circuit in accordance with a preferred embodiment of the present utility model;

FIG. 4a is a schematic left-hand view of a wire-wound support according to a preferred embodiment of the present utility model;

FIG. 4b is a schematic cross-sectional view of the line A-A of FIG. 4 a;

fig. 4c is a schematic perspective view of a winding bracket according to a preferred embodiment of the utility model.

Reference numerals are described as follows:

an inner assembly 1; a secondary winding 11; a wire winding bracket 12; a groove 121; a built-in controller 13; a built-in battery 14; a spare cable 15; an outer assembly 2; a primary winding 2121; a system controller 22; an external battery 23; a blood pump 3; a transformer 5; skin 4.

Detailed Description

The utility model is described in further detail below with reference to the drawings and the specific examples. The advantages and features of the present utility model will become more apparent from the following description. It should be noted that the drawings are in a very simplified form and are all to a non-precise scale, merely for convenience and clarity in aiding in the description of embodiments of the utility model.

The terms "center," "longitudinal," "transverse," "length," "width," "thickness," "upper," "lower," "front," "rear," "left," "right," "vertical," "horizontal," "top," "bottom," "inner," "outer," "clockwise," "counter-clockwise," "axial," "radial," "circumferential," etc. refer to an orientation or positional relationship based on that shown in the drawings, merely for convenience of description and to simplify the description, and do not indicate or imply that the devices or elements referred to must have a particular orientation, be constructed and operated in a particular orientation, and therefore should not be construed as limiting the utility model.

In the present utility model, unless explicitly specified and limited otherwise, the terms "mounted," "connected," "secured," and the like are to be construed broadly and include, for example, either fixedly attached, detachably attached, or integrally formed; may be mechanically connected, may be electrically connected or may be in communication with each other; either directly, or through an intermediary, may be internal to the two elements or in an interactive relationship with the two elements, unless explicitly defined otherwise. The specific meaning of the above terms in the present utility model can be understood by those of ordinary skill in the art according to the specific circumstances. In the description of the present utility model, "plurality" means at least two, for example, two or three or more, etc.

As used in this specification, the term "proximal" generally refers to the end that is proximal to a doctor or operator; the term "distal" is opposite "proximal" and generally refers to an end that is distal from a medical or operator.

The utility model will now be described in detail with reference to the drawings and a preferred embodiment. The following embodiments and features of the embodiments may be complemented or combined with each other without conflict.

As shown in fig. 1, a preferred embodiment of the present utility model provides a ventricular assist device comprising an inner member 1, an outer member 2, and a blood pump 3, the outer member 2 being adapted to be placed outside a patient's body, the inner member 1 and the blood pump 3 being adapted to be implanted in the patient's body. The outer assembly 2 is adapted to be connected to an alternating current and to transmit the alternating current through the inner assembly 1 to the blood pump 3 in order to provide electrical energy for the normal operation of the blood pump 3.

It should be understood that the blood pump 3 is a mechanical pump capable of applying work to blood to assist the flow of blood, and may be, for example, a pulsatile blood pump or a rotary blood pump. In the following description, a fully magnetic suspension centrifugal pump is illustrated, but it will be appreciated by a person skilled in the art that the inner and outer assemblies 1, 2 may also be applied to other types of blood pumps 3.

As shown in fig. 1-2, the inner assembly 1 includes a secondary winding 11 and a winding support 12, the secondary winding 11 being connected to the blood pump 3, the secondary winding 11 and the winding support 12 being adapted for implantation in a patient. The outer assembly 2 comprises a primary winding 21 for placement in the body, i.e. the primary winding 21 is placed outside the patient's body, the primary winding 21 being intended to be wound on the winding support 12. Since the wound support 12 is implanted in the patient and is wrapped by the skin 4, the primary winding 21 is wound around the wound support 12 wrapped by the skin 4. In use of the ventricular assist device, the primary winding 21 is connected to an alternating current and is used to supply its own energy to the secondary winding 11, the secondary winding 11 being used to supply the received energy to the blood pump 3 to effect the supply of power to the blood pump 3. It should be understood that the components of the present utility model may be connected by wires.

In this embodiment, the wound support 12 around which the secondary winding 11 is wound is entirely implanted under the patient's skin 4 or within the fat layer. Specifically, a part of the winding support 12 around which the secondary winding 11 is wound protrudes from the body surface, and the other part is covered with the skin 4 or the fat layer without protruding from the body surface, and the primary winding 21 is wound around a part of the surface of the winding support 12 protruding from the skin 4 of the human body. So configured, since the secondary winding 11 and the winding support 12 are implanted entirely within the skin 4 or fat layer of the patient, and no percutaneous cable is provided through the skin 4 in the solution, i.e. no component is provided to form a wound through the skin 4, skin infection can be avoided from the root, and the safety of the patient during charging can be improved. It should be understood that the wire-wound stand 12 protruding from the body surface means that the wire-wound stand 12 protrudes outward from the outer surface of the human skin to form a protruding portion on the outer surface of the normal human skin.

So set up, ventricular assist device adopts wire winding support 12 coupling energy, the accessible carries out the energy transmission in order to realize the power supply to blood pump 3 between primary winding 21 and secondary winding 11, because secondary winding 11 and primary winding 21 are in the same place through wire winding support 12 firm coupling, so can make secondary winding 11 and primary winding 21's relative position fixed in whole charging process, thereby can safe and reliable, high-efficient and stable completion power supply process, and be difficult for causing the wound infection, can avoid in the wireless charging internal coil and external coil can not be relative problem all the time, improve survival rate and quality of life after the patient's the art by a wide margin.

In more detail, referring to fig. 1 and 2, the primary winding 21, the winding bracket 12 and the secondary winding 11 constitute an air-core transformer 5, the primary winding 21 being a primary winding of the transformer 5, and the secondary winding 11 being a secondary winding of the transformer 5. The primary winding 21 is for connection to an external alternating current and is capable of generating an alternating magnetic flux outside the primary winding 21. The alternating magnetic flux can be introduced into the interior of the winding bracket 12, namely passes through the interior of the secondary winding 11 to drive the secondary winding 11 to generate induced electromotive force and induced current so as to realize power supply to the blood pump 3.

Referring to fig. 3, i1 and i2 in the drawing indicate the current direction of the coil in the primary winding 21, where i1 indicates the current direction of the coil inward, and arrow a indicates the direction of magnetic flux induced around the coil when the current direction of the coil is inward; i2 indicates the outward direction of the current of the coil, and arrow a indicates the direction of the magnetic flux induced around the coil when the outward direction of the current of the coil. It is understood that when the primary winding 21 is connected to the alternating current, the alternating magnetic flux generated from the primary winding 21 may enter the inside of the winding bracket 12 in the directions indicated by the arrows a and b in fig. 3, i.e., enter the secondary winding 11, and then an induced electromotive force and an induced current may be generated in the secondary winding 11.

Preferably, the material of the winding bracket 12 is one of soft magnetic material, ferrite and nonmetallic material, wherein the nonmetallic material is preferably laminated by adopting a sheet structure with low electric conductivity and high magnetic conductivity. Preferably, the magnetic flux is made of a soft magnetic material, and since the magnetic permeability of the soft magnetic material is far higher than that of air, the alternating magnetic flux is easier to enter the interior of the winding bracket 12 along the directions of arrow a and arrow b, that is, the winding bracket 12 made of the soft magnetic material can guide most of the alternating magnetic flux to enter the interior of the winding bracket 12, so that the magnetic flux leakage of the primary winding 21 can be reduced, and the energy transmission efficiency of the transformer 5 can be improved. In addition, compared with a transformer with an iron core, the iron loss and the eddy current loss of the winding bracket 12 made of the soft magnetic material are smaller, so that the energy transmission efficiency of the transformer 5 can be further improved. It should be appreciated that soft magnetic materials, ferrites, and nonmetallic materials are all conventional materials and will not be described in detail herein.

Further, the outer surface of the winding bracket 12 and the outer surface of the secondary winding 11 are coated with a medical polymer coating to ensure the safety of the contact of the winding bracket 12 and the secondary winding 11 with human tissues.

The shape of the winding support 12 is not limited in the present utility model, and the winding support 12 may be provided in a cylindrical shape (refer to fig. 4 c), an elliptic cylindrical shape, a square shape, or other suitable shape, preferably a cylindrical shape, so as to facilitate the winding of the primary winding 21 and the secondary winding 11.

As shown in fig. 4a to 4c, as a preferred embodiment, the winding support 12 has a sleeve structure, and the secondary winding 11 and the primary winding 21 are wound on the winding support 12 along the circumferential direction of the winding support 12. It should be understood that both the circumferential and axial directions in the present utility model refer to the circumferential and axial directions of the wire-wound bracket 12.

With continued reference to fig. 4a to 4c, the side wall of the winding support 12 is provided with a groove 121 penetrating in the circumferential direction, and the secondary winding 11 and the primary winding 21 are both wound in the groove 121 in the circumferential direction, so that the outer surface of the winding support 12 after the secondary winding 11 is wound is ensured to be flat, i.e. the secondary winding 11 is ensured not to protrude from a plane parallel to the axis formed at the maximum outer diameter of the winding support 12, so as to avoid damage to the surface of the skin 4.

Preferably, the outer wall of the winding bracket 12 for winding the secondary winding 11 is of a sheet structure, that is, the groove wall of the groove 121 for winding the secondary winding 11 is of a sheet structure, so that iron loss and turbine loss of the winding bracket 12 can be reduced, and energy transmission efficiency is improved.

To reduce the effect of the secondary winding 11 and the wire-wound support 12 on human tissue, the wire-wound support 12 is arranged perpendicular to the surface of the skin 4, i.e. the axis of the wire-wound support 12 is substantially perpendicular to the surface of the skin 4. The end of the winding support 12 axially adjacent to the skin 4 is open, and the end of the winding support 12 axially remote from the skin 4 is sealed, i.e. the distal end of the winding support 12 is sealed.

In a preferred embodiment, the winding position of the secondary winding 11 on the winding support 12 corresponds to the winding position of the primary winding 21 on the winding support 12, so that after the secondary winding 11 is wound, the primary winding 21 is wound on the outer surface of the secondary winding 11 wrapped by the skin 4, and at this time, the secondary winding 11 and the primary winding 21 are respectively located on two sides of the skin 4 and are indirectly contacted through the skin 4, so that the secondary winding 11 can obtain more alternating magnetic flux generated by the primary winding 21, so as to improve energy transmission efficiency.

In another embodiment, the primary winding 21 may also be wound directly onto the wound support 12 wrapped by the skin 4, in which case the secondary winding 11 and the primary winding 21 are wound onto the wound support 12, respectively, without indirect contact with each other with the skin. In yet another embodiment, a portion of the primary winding 21 may be wound directly onto the wound support 12 wrapped by the skin 4 and another portion may be wound onto the outer surface of the secondary winding 11 wrapped by the skin 4, with the secondary winding 11 and the primary winding 21 each having a portion that makes indirect contact through the skin.

In order to obtain a predetermined voltage for the blood pump 3, the secondary winding 11 and the primary winding 211 each preferably include a plurality of turns around which the bobbin 12 is wound, and the number of turns of the secondary winding 11 is preferably the same as the number of turns of the primary winding 21. Of course, in other embodiments, the number of turns of the secondary winding 11 may be different from the number of turns of the primary winding 21. The operator can set the specific turns ratio of the secondary winding 11 and the primary winding 21 according to the predetermined voltage required by the blood pump 3.

Referring back to fig. 1, the external assembly 2 further includes a system controller 22 and an external battery 23, one end of the system controller 22 is connected to the primary winding 21, and the other end is connected to the external battery 23. The system controller 22 is configured to receive energy transferred from the external battery 23 and to transfer the energy to the primary winding 21 after converting the energy. In another embodiment, the system controller 22 may also be connected to an external ac power source to receive energy delivered by the external ac power source.

Specifically, the system controller 22 is configured to receive energy released from the external battery 23, and is configured to convert the energy into an external ac power (e.g., a high-frequency ac power) of a desired operating frequency and amplitude of the primary winding 21, and the external ac power is transformed by the transformer 5 to a received ac power of a desired operating frequency and amplitude of the secondary winding 11. When the number of turns of the secondary winding 11 and the primary winding 21 is the same, the external ac power can be transformed by the transformer 5 to the received ac power of the same operating frequency and amplitude.

As shown in fig. 1, the internal assembly 1 further comprises a built-in controller 13, wherein a distal end of the built-in controller 13 is connected with the blood pump 3, a proximal end of the built-in controller 13 is connected with the secondary winding 11, and the built-in controller 13 is used for receiving energy transmitted by the secondary winding 11 and transmitting the energy to the blood pump 3 after converting the energy so as to realize power supply to the blood pump 3. Specifically, the ac power received by the secondary winding 11 may be rectified, filtered and stabilized by the built-in controller 13 to form a working power supply required by the blood pump 3, and the powered blood pump 3 is used for running at a set rotational speed under the drive of the built-in driver.

With continued reference to fig. 1, the internal assembly 1 further comprises an internal battery 14, the internal battery 14 being for connection to the internal controller 13, the internal battery 14 being for providing energy to the blood pump 3 via the internal controller 13. When the patient needs to shower or swim, the primary winding 21 can be removed to separate the primary winding 21 from the wound support 12, at which point the built-in battery 14 can continue to power the blood pump 3 for a period of time (e.g., 1-2 hours) without external power. In addition, the built-in battery 14 can also be used as an emergency standby power supply device of the blood pump 3, and when any one of the system controller 22, the transformer 5 and the built-in controller 13 fails, the built-in battery 14 can continuously supply power to the blood pump 3, so that time is provided for a patient to seek support and troubleshooting.

When the built-in battery 14 discharges to a maximum depth of discharge, the built-in controller 13 will give an alarm to remind the patient to install the primary winding 21 in time so as to enable the blood pump 3 to continue to work under the power supply of the transformer 5.

Further, a battery management module (i.e., BMS system) for controlling charge and discharge of the built-in battery 14 is provided in the built-in controller 13. Specifically, the battery management module of the built-in controller 13 is used to detect the voltage and current in the built-in battery 14; after the patient removes the primary winding 21, the battery management module can switch the built-in battery 14 to a discharge mode to power the blood pump 3 via the built-in battery 14; after the patient reinstalls the primary winding 21, the battery management module can switch the built-in battery 14 to a charging mode, where the energy obtained by the secondary winding 11 can simultaneously power the blood pump 3 and charge the built-in battery 14.

Preferably, the inner assembly 1 further comprises a spare cable 15, the distal end of the spare cable 15 being connected to the blood pump 3, the proximal end being implanted under the skin 4, the spare cable 15 being adapted to connect to an external device for providing energy to the blood pump 3. Specifically, when the power supply system of the transformer 5 of the ventricular assist device cannot work, the built-in battery 13 can supply short-term energy to the blood pump 3, at this time, the built-in driver of the blood pump 3 switches the working mode of the blood pump 3 to the minimum safe mode according to the safe control strategy, the minimum safe mode can ensure the minimum pumping requirement of the heart of the patient, at this time, the patient needs to go to the nearest hospital, and the standby cable 15 is started under the assistance of the doctor to continuously supply power to the blood pump 3 through the standby cable 15.

In one example, a backup connector of the external battery 23 may be connected to the backup cable 15 to power the blood pump 3 via the external battery 23, so as to be a backup power supply scheme of the blood pump 3 to further ensure life safety of the patient.

In summary, the ventricular assist device provided by the utility model can form the transformer 5 through the primary winding 21, the winding bracket 12 and the secondary winding 11 to perform energy transmission on the blood pump 3, and since the secondary winding 11 and the primary winding 21 are firmly coupled together through the winding bracket 12, the relative positions of the secondary winding 11 and the primary winding 21 can be fixed all the time in the charging process, so that the power supply process can be completed safely, reliably, efficiently and stably, and the survival rate and the life quality of patients after operation can be improved.

The above description is only illustrative of the preferred embodiments of the present utility model and is not intended to limit the scope of the present utility model, and any alterations and modifications made by those skilled in the art based on the above disclosure shall fall within the scope of the present utility model.

Claims (10)

1. A ventricular assist device comprising an inner assembly, an outer assembly, and a blood pump; the internal component comprises a secondary winding and a winding bracket, the secondary winding is connected with the blood pump, the secondary winding, the winding bracket and the blood pump are all used for being implanted into a body, and the secondary winding is used for being wound on the winding bracket; the external component comprises a primary winding arranged outside the body, and the primary winding is used for being wound on the winding bracket; the primary winding is configured to provide self energy to the secondary winding, which is configured to provide received energy to the blood pump.

2. The ventricular assist device of claim 1 wherein the winding support is of a sleeve configuration, the secondary winding and the primary winding each being wound on the winding support in a circumferential direction of the winding support.

3. A ventricular assist device as claimed in claim 2 wherein the wire-wound support is disposed perpendicular to the skin surface, the wire-wound support opening axially adjacent one end for the skin, the wire-wound support sealing axially away from the end for the skin.

4. The ventricular assist device of claim 1, wherein a winding position of the primary winding on the winding support corresponds to a winding position of the secondary winding on the winding support.

5. The ventricular assist device of claim 1, wherein the material of the wire-wound support is one of a soft magnetic material, ferrite, and a non-metallic material.

6. The ventricular assist device of claim 1 wherein an outer wall of the wire-wound stent and an outer wall of the secondary winding are both coated with a medical polymer coating.

7. The ventricular assist device of any one of claims 1-6, wherein the internal assembly further comprises an internal controller having a distal end coupled to the blood pump and a proximal end coupled to the secondary winding, the internal controller configured to receive energy delivered by the secondary winding and configured to deliver energy to the blood pump.

8. The ventricular assist device of claim 7, wherein the internal assembly further comprises an internal battery for connection with the internal controller, the internal battery for providing energy to the blood pump through the internal controller.

9. The ventricular assist device of any one of claims 1-6, wherein the external assembly further comprises a system controller and an external battery, one end of the system controller being connected to the primary winding and the other end being connected to the external battery; the system controller is used for receiving energy transmitted by the external battery and transmitting the energy to the primary winding.

10. The ventricular assist device of any one of claims 1-6, wherein the internal assembly further comprises a backup cable having a distal end connected to the blood pump and a proximal end implanted under the skin, the backup cable for connecting an external device to energize the blood pump.