CN107261328B - Special external charging coupling device for spinal cord electrical stimulation - Google Patents
Special external charging coupling device for spinal cord electrical stimulation Download PDFInfo
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- CN107261328B CN107261328B CN201710296324.8A CN201710296324A CN107261328B CN 107261328 B CN107261328 B CN 107261328B CN 201710296324 A CN201710296324 A CN 201710296324A CN 107261328 B CN107261328 B CN 107261328B
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- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61N—ELECTROTHERAPY; MAGNETOTHERAPY; RADIATION THERAPY; ULTRASOUND THERAPY
- A61N1/00—Electrotherapy; Circuits therefor
- A61N1/18—Applying electric currents by contact electrodes
- A61N1/32—Applying electric currents by contact electrodes alternating or intermittent currents
- A61N1/36—Applying electric currents by contact electrodes alternating or intermittent currents for stimulation
- A61N1/372—Arrangements in connection with the implantation of stimulators
- A61N1/378—Electrical supply
- A61N1/3787—Electrical supply from an external energy source
Abstract
The application discloses a special external charging coupling device for spinal cord electrical stimulation, which comprises an external magnetic field generating side, an internal magnetic field induction side and an internal magnetic field generating side; the in-vivo magnetic field induction side comprises a first induction coil used for receiving the variable magnetic field generated by the in-vivo magnetic field generation side and a variable capacitance battery connected with the first induction coil; the variable-capacitance battery is connected with the pulse generator and the electrode plate; the in-vivo magnetic field generation side includes a stent installed in an arterial blood vessel; the vascular stent is connected with a rotating wheel which can rotate along with the blood flow; a second induction coil connected with the variable-capacitance battery is wound on the rotating wheel; two magnets with opposite magnetism are arranged on the vascular stent at the positions on two sides of the rotating wheel.
Description
Technical Field
The invention relates to the field of spinal cord electrical stimulation, in particular to an external charging coupling device special for spinal cord electrical stimulation.
Background
Neuropathic pain is a difficult and problematic condition that is difficult to treat and can cause significant pain to the patient. To relieve the pain of patients, a power source implanted Spinal Cord Stimulation (SCS) neuromodulation technique is commonly used. The technology for regulating and controlling the spinal cord electrical stimulation nerves by power supply implantation is to implant a spinal cord electrical stimulation device into a human body, and relieve neuropathic pain of a patient by stimulating target positions of pain generated on spinal nerves by electrical stimulation.
Existing spinal cord electrical stimulation devices include an electrical stimulation pulse generator and a fixed capacitance battery that powers the electrical stimulation pulse generator. Because the fixed capacitor battery has a limited amount of power, the patient must replace the fixed capacitor battery after a period of use. This not only makes SCS neuromodulation technology expensive, common people hardly bear the burden, but also makes patients increase the pain of operation. In order to solve the problem that the fixed capacitor battery needs to be replaced at regular time, an external charging coupling device for spinal cord electrical stimulation has been developed. The spinal cord electrical stimulation in-vitro coupling device comprises an in-vitro magnetic field generating side capable of generating a variable magnetic field and an in-vivo magnetic field induction side for performing in-vitro charging according to the variable magnetic field generated by the in-vitro magnetic field generating side. The in-vivo magnetic field induction side comprises an induction coil used for receiving the current generated by the variable magnetic field and a variable capacitance battery connected with the induction coil to form a loop. The variable-capacitance battery is connected with a pulse generator for generating electrical stimulation, and the pulse generator is connected with an electrode plate for directly electrically stimulating spinal nerves.
Although the problem that a battery needs to be replaced in an operation is solved by the conventional spinal cord electrical stimulation in-vitro charging coupling device, the in-vitro magnetic field generation side for generating a variable magnetic field to charge the in-vivo electromagnetic induction side is expensive, and only a special medical institution exists, so that a patient needs to go to a hospital regularly to be charged, which brings inconvenience to the daily life of the patient.
Disclosure of Invention
The invention aims to provide an external charging coupling device special for spinal cord electrical stimulation, which solves the problem that the existing external charging coupling device for spinal cord electrical stimulation can only be charged through an external magnetic field generation side.
In order to solve the above problems, the following scheme is provided:
the first scheme is as follows: the special external charging coupling device for spinal cord electrical stimulation comprises an external magnetic field generating side and an internal magnetic field induction side; the in-vivo magnetic field induction side comprises a first induction coil used for receiving the variable magnetic field generated by the in-vivo magnetic field generation side and a variable capacitance battery connected with the first induction coil; the variable-capacitance battery is connected with a pulse generator and an electrode plate; further comprising an in-vivo magnetic field generation side; the in-vivo magnetic field generation side includes a stent installed in a blood vessel; the blood vessel support is connected with a rotating wheel which can rotate along with the flow of blood; a second induction coil connected with the variable-capacitance battery is wound on the rotating wheel; two magnets with opposite magnetism are arranged on the vascular stent at the positions on two sides of the rotating wheel.
The working principle is as follows:
when the variable-capacitance battery works, the variable magnetic field can be generated through the external magnetic field generating side, so that the first induction coil in the internal magnetic field induction side generates electromagnetic induction to form current, and the variable-capacitance battery is charged. The variable capacitance battery powers the pulse generator, enabling the pulse generator to generate pulsed electrical stimulation and deliver such electrical stimulation to the implanted neural target site via the electrode pads. And when there is no external magnetic field generating side, the variable capacitance battery can be charged through the internal magnetic field generating side. A magnetic field is formed on the intravascular stent on the internal magnetic field induction side through two magnets with opposite magnetism. And the rotating wheel connected with the blood vessel support rotates along with the blood flow. In the rotating process of the rotating wheel, a second induction coil on the rotating wheel and the variable-capacitance battery form a loop cuts the magnetic induction line to generate induction current, and the variable-capacitance battery is charged through the induction current. The variable-capacitance battery supplies power to the pulse generator, and the pulse generator generates pulse electrical stimulation and transmits the pulse electrical stimulation to the target position of the spinal nerves through the electrode plate.
Has the advantages that:
1. the characteristic that human blood flows all the time is utilized, the rotating wheel arranged in the blood vessel is enabled to rotate continuously, the second induction coil is enabled to cut the magnetic induction line continuously to generate induction current, the variable capacitance battery is charged, and the problem that the variable capacitance battery can only be charged through the side where the external magnetic field is generated at present is effectively solved.
2. A first induction coil in the in-vivo magnetic field induction side can receive a variable magnetic field generated by the in-vitro magnetic field generation side to form induction current, and the first induction coil transmits the current to a variable capacitance battery connected with the first induction coil; the second induction coil cuts the magnetic induction line to generate induction current and transmits the current to the variable-capacitance battery connected with the second induction coil; the variable capacitance battery can be charged by the external magnetic field generation side, and can also be charged by the internal magnetic field generation side.
3. The rotating wheel is installed through the blood vessel support, so that the rotating wheel can be placed in flowing blood, and the blood vessel support can also play a role in supporting the blood vessel and preventing the blood vessel from being blocked.
4. The invention effectively solves the problem that the existing spinal cord electrical stimulation in-vitro charging coupling device can only charge through the side where the in-vitro magnetic field is generated.
Scheme II: further, the external magnetic field generating side includes an electromagnetic conversion coil for generating a varying electromagnetic field and coaxial with the first induction coil.
The electromagnetic conversion coil generates a variable magnetic field, and the first induction coil coaxial with the electromagnetic conversion coil receives the variable magnetic field to form induction current.
The third scheme is as follows: furthermore, a communicating pipe for a lead to pass through is connected between the internal magnetic field induction side and the internal magnetic field generation side.
The in-vivo magnetic field induction side and the in-vivo magnetic field generation side are connected by a communication pipe.
And the scheme is as follows: furthermore, a one-way plug for preventing blood from flowing into the communicating pipe is arranged in the communicating pipe.
Because of the one-way plug, blood in the blood vessel can not enter the communicating pipe, but heat generated in the body sensing side can be transferred into the blood vessel through the one-way plug, and along with the flow of the blood, gas is formed in the lung and is taken out of the body.
And a fifth scheme: further, the in-vivo magnetic field induction side comprises an annular shell sleeved on the spine; the pulse generator and the variable capacitance battery are disposed within an annular housing; the electrode plate is arranged on the contact surface of the annular shell and the vertebra.
The annular shell plays a role in protecting electronic components such as variable capacitance batteries, pulse generators and the like. The electrode plate is arranged on the contact surface of the annular shell and the vertebra, and can directly stimulate spinal nerves in the vertebra.
Scheme six: further, the electrode plates are a plurality of electrode plates which are uniformly distributed on the annular shell.
Through the stimulation to spinal nerves in all directions, the excessive injury caused by the long-term stimulation to the same direction is avoided.
Drawings
Fig. 1 is a schematic structural diagram of an embodiment of the present invention.
Detailed Description
The present invention will be described in further detail below by way of specific embodiments:
reference numerals in the drawings of the specification include: the device comprises an electrical stimulation pulse generator 1, an electromagnetic conversion coil 2, a pulse generator 3, a main induction coil 4, a telescopic pipe 5, an electromagnet 6, an electrode plate 7, an annular shell 8, a heat dissipation layer 9, a heat absorption layer 10, a first induction coil 11, a second induction coil 12, a blood vessel support 13, a rotating wheel 14, a communicating pipe 15, a magnet 16 and a variable capacitance battery 17.
The embodiment is basically as shown in the attached figure 1: the special external charging coupling device for spinal cord electrical stimulation comprises an external magnetic field generating side, an internal magnetic field induction side and an internal magnetic field generating side.
The external magnetic field generating side comprises an electric stimulation pulse generator 1 and an electromagnetic conversion coil 2 which form a loop; the internal magnetic field induction side comprises an annular shell 8 fixed under the skin of the lateral abdomen of the human body in a minimally invasive surgery and an internal magnetic field induction circuit arranged in the annular shell 8.
The annular shell 8 is an edible glue shell; the inner wall of the edible glue shell is coated with a heat dissipation layer 9, and the outer wall of the edible glue shell is coated with a heat absorption layer 10.
The edible gum shell has certain hardness and flexibility, can exist in a human body for a long time, and does not damage internal organs of the human body. Can go out the heat dissipation that the internal magnetic field induction circuit in the annular shell 8 produced through heat dissipation layer 9, make the internal magnetic field induction circuit in the annular shell 8 can distribute away the heat that work produced. The heat is transmitted to the heat absorption layer 10 through the edible glue shell, and the heat absorption layer 10 absorbs and dissipates the heat, so that the damage of the excessive heat to the human body is avoided.
The heat dissipation layer 9 is an aluminum nitride layer.
The aluminum nitride has good heat dissipation performance, can dissipate heat quickly, and avoids damage to the circuit and human bodies caused by heat collection.
The heat absorbing layer 10 is an edible plastic layer doped with graphene.
The graphene has good electric and thermal conductivity, and the graphene is doped into the edible plastic layer, so that the heat absorption and heat resistance of the plastic layer can be improved. Through the edible level plastic layer that is mixed with graphite alkene, not only can absorb the heat that the edible gum shell transmitted out and dissipate, can also play the guard action to the edible gum shell.
The in-vivo magnetic field induction circuit comprises four pulse generators 3 which generate pulses through electromagnetic induction with the electrical stimulation pulse generator 1, electrode plates 7 which are correspondingly connected with each pulse generator 3 to form a loop, and variable capacitance batteries 17 which are respectively communicated with the loops formed by the pulse generators 3 and the electrode plates 7; a telescopic pipe 5 which can extend downwards along the axial direction of the annular shell 8 is arranged in the annular shell 8; the telescopic pipes 5 are uniformly distributed on the inner wall of the annular shell 8; the electrode plate 7 is arranged at the telescopic end of the telescopic pipe 5 and can perform telescopic motion along with the telescopic pipe 5; the pulse generator 3 is arranged in the annular shell 8, and an electromagnet 16 which is just opposite to the electrode plate 7 is connected in parallel on the pulse generator 3; first induction coils 11 which can be used for charging the variable-capacitance batteries 17 are respectively connected between the variable-capacitance batteries 17 and loops formed by the pulse generators 3 and the electrode plates 7.
A total induction coil 4 connected only with the variable capacitance battery 17 is arranged in the annular housing 8 along the communication direction of the annular housing 8; the axis of the total induction coil 4 is perpendicular to the axis of each first induction coil 11.
When only the variable-capacitance battery 17 needs to be charged, only the electromagnetic conversion coil 2 in the external magnetic field generation side needs to be coaxially corresponding to the total induction coil 4, that is, magnetic flux transformation is vertically performed from the sole or head direction of a person, so that the total induction coil 4 generates current to charge the variable-capacitance battery 17.
The variable-capacitance cell 17 is three variable-capacitance cells 17 connected in parallel with each other.
When one variable-capacitance battery 17 is damaged, other variable-capacitance batteries 17 are replaced for use, so that the removal and replacement in an operation are avoided.
Firstly, the direction of spinal cord electrical stimulation is found, namely the position of a target point is found. The electromagnetic conversion coil 2 at the side where the external magnetic field is generated is aligned to the position direction of the target point. The external magnetic field generating side is started to enable the electric stimulation pulse generator 1 and the electromagnetic conversion coil 2 to start working. The electrical stimulation pulse generator 1 is close to the skin of a person, so that the pulse generator 3 generates current in a loop formed by the pulse generator 3 and the electrode plate 7 under the action of electromagnetic induction. The pulse generator 3 starts to work, and the generated pulse electric stimulation is transmitted to the electrode plate 7. At the same time, the electromagnet 16 connected in parallel with the pulse generator 3 generates magnetism, and the electrode sheet 7 having the same magnetism as that of the magnetic field generated by the electromagnetic induction is pushed inward in the radial direction of the ring-shaped casing 8. The electrode plate 7 pushes the telescopic shell to push towards the target position and carries out pulse electrical stimulation on spinal nerves in the target position. When the first induction coil 11 receives the changing magnetic field generated by the electromagnetic conversion coil 2 while electrically stimulating the target position, the current is generated to charge the variable capacitance battery 17.
The external electrical stimulation pulse generator 1 comprises a power management module for realizing the stabilization of circuit voltage, an E-class amplifier module for realizing energy amplification, a wireless transmitting circuit module for transmitting energy inside and outside a body, a modulation module for modulating a transmission signal and a microcontroller respectively connected with the modules; the stimulation parameters sent by the microcontroller change the resonance of the capacitor and the inductor through the modulation module to perform signal modulation, obtain pulse signals and transmit the pulse signals to the class-E amplifier module.
The external electrical stimulation pulse generator 1 transmits stimulation parameters to the modulation module through the microcontroller, changes resonance of the capacitor and the inductor, adjusts the resonance to a proper pulse signal, and transmits the pulse signal to the class E amplification module for amplification so as to reduce energy loss during transmission. The class-E amplification module transmits the amplified pulse current to the wireless transmitting circuit module, and the wireless transmitting circuit module transmits the pulse signal to the electromagnetic conversion coil 2 for electromagnetic conversion. The power management module accesses the mains current after voltage stabilization into the circuit to provide energy for the external electromagnetic pulse generator 3.
The internal magnetic field induction side comprises an annular shell 8 fixed under the flank part, and the internal electromagnetic conversion pulse generator 3 is arranged in the annular shell 8; the annular shell 8 is provided with a telescopic pipe 5 for the electrode plate 7 to extend out of the annular shell 8.
The annular shell 8 plays a role of protecting the electromagnetic conversion pulse generator 3 in the body, and the electrode plate 7 is arranged in the extension tube 5, so that the extension tube 5 which extends out can be selected to extend out according to the actual condition of a patient, different patients can be installed according to the actual condition when using the same device, the universality of the invention is increased, and the invention is beneficial to large-scale production during manufacturing.
A main induction coil 4 connected with a variable capacitance battery 17 is arranged in the annular shell 8 along the communication direction of the annular shell 8; a first induction coil 11 is arranged at the communication part of the extension tube 5 and the annular shell 8; the axis of the total induction coil 4 is perpendicular to the axis of each first induction coil 11.
The total induction coil 4 generates electromagnetic induction reaction through magnetic induction lines generated outside the cutting body to form current and stores the current in a variable capacitance battery 17 connected with the current. Compared with a fixed capacitor battery, the variable capacitor battery 17 can be charged and discharged for multiple times, is favorable for recycling, and avoids the need of taking out and replacing the battery as before. The first induction coil 11 on the telescopic pipe 5 is perpendicular to the axis of the main induction coil 4, when the changing magnetic flux is supplied to the corresponding first induction coil 11, the first induction coil 11 is enabled to cut the magnetic induction line, and the first induction coil 11 generates magnetism. And because the axis of the total induction coil 4 and the magnetic field induction coil are vertical, the directions of the magnetic induction lines which need to be cut by the total induction coil 4 are different, namely, only the first induction coil 11 in each direction is specially used for generating magnetism. The total induction coil 4 and the magnetic field induction coil do not interfere with each other.
The in-vivo electromagnetic conversion pulse generator 3 includes a parallel resonance circuit, a voltage-doubling rectifying circuit, a demodulating circuit, and a stimulus pulse waveform generating circuit, which are connected in sequence.
The in-vivo electromagnetic pulse generator 3 minimizes the voltage loss of the received pulse signal through the parallel resonant circuit, transmits the pulse signal to the demodulation circuit through the voltage doubling rectification circuit for demodulation, and finally converts the demodulated pulse signal into a stimulation pulse wave again through the stimulation pulse wave forming circuit and transmits the stimulation pulse wave to the electrode plate 7 for stimulating spinal nerves.
The internal electromagnetic conversion pulse generators 3 include four which are uniformly arranged in the annular housing 8, and each internal electromagnetic conversion pulse generator 3 is connected with the main induction coil 4 respectively.
The number of the in-vivo electromagnetic conversion pulse generators 3 is four, so that the power of each electromagnetic conversion pulse generator 3 can be reduced, and the heat dissipation of all the electromagnetic conversion pulse generators 3 is reduced. Each internal electromagnetic conversion pulse generator 3 is respectively connected with the main induction coil 4, the internal electromagnetic conversion pulse generators 3 are independent from each other and do not influence each other, and if one internal electromagnetic conversion pulse generator 3 is damaged, the normal operation of the other three internal electromagnetic conversion pulse generators 3 is not influenced. And four evenly distributed, the stress on the whole annular shell 8 is more stable.
The internal magnetic field induction side comprises an annular shell 8 sleeved on the spine; the annular housing 8 may also be a titanium alloy housing, the inner wall of which is connected to an aluminum nitride layer for heat dissipation. Four extension tubes 5 which can extend inwards along the radial direction of the annular shell 8 are arranged in the annular shell 8; the telescopic pipes 5 are uniformly distributed on the inner wall of the annular shell 8; the electrode plate 7 is arranged at the telescopic end of the telescopic pipe 5 and can perform telescopic motion along with the telescopic pipe 5; the pulse generator 3 is arranged in the annular shell 8 and is positioned behind the telescopic pipe 5; the pulse generator 3 is connected in parallel with an electromagnet 16 which is just opposite to the electrode plate 7; the variable-capacitance battery 17 forms an independent circuit with each pulse generator 3 and the electrode sheet 7. The first induction coil 11 is sleeved on the pulse generator 3, and the pulse generator 3 plays a role in guiding the first induction coil 11. The axial direction of the first magnetic induction coil 1 can be fixed, and the first magnetic induction coil can be conveniently aligned with the electromagnetic conversion coil 2.
The electrode plate 7 is arranged on the contact surface of the annular shell 8 and the vertebra. The electrode plate 7 is arranged on the contact surface of the annular shell 8 and the vertebra, so that spinal nerves in the vertebra can be directly stimulated.
The variable-capacitance battery 17 is three batteries connected in parallel, and the first induction coil 11 is connected with each variable-capacitance battery 17 respectively to charge the variable-capacitance battery 17. The situation that the whole device cannot be used after one variable-capacitance battery 17 is damaged is avoided.
The annular housing 8 plays a role in protecting and radiating electronic components such as the variable-capacitance battery 17, the pulse generator 3 and the like. The titanium alloy shell has good metallicity and non-metallicity, has certain hardness and certain flexibility, can exist in a human body for a long time, and does not damage internal organs of the human body. The aluminum nitride layer coated on the outer wall of the shell can dissipate heat generated by various electronic components in the annular shell 8, so that the annular shell 8 is kept in a temperature environment suitable for the operation of various electronic components.
The pulse generators 3 and the electrode plates 7 are uniformly distributed in four groups on the circumferential direction of the annular shell 8, and the pulse generators 3 and the electrode plates 7 of each group are connected with the variable-capacitance battery 17 in parallel. Each group of pulse generators 3 and the electrode plates 7 are mutually independent and mutually complementary to influence, not only can send out electrical stimulation simultaneously, but also can be continuously used when other groups are damaged, and the service time of the device is prolonged.
The external magnetic field generating side includes an electromagnetic conversion coil 2 for generating a varying electromagnetic field and coaxial with the first induction coil 11. The electromagnetic conversion coil 2 generates a changing magnetic field, and the first induction coil 11 coaxial with the electromagnetic conversion coil receives the changing magnetic field to form induction current. By aligning the electromagnetic conversion coil 2 with any one of the first induction coils 11 in four different directions, the variable-capacitance battery 17 can be charged by the induced current formed on this first induction coil 11. Because the first induction coils 11 are evenly distributed on the housing and the two oppositely arranged first induction coils are parallel to each other in cross section. Therefore, when the electromagnetic conversion coil 2 is aligned with one of the first induction coils 11 and the magnetic flux change in the electromagnetic conversion coil 2 is transmitted to the first induction coil 11, the first induction coil 11 generates an induced current and transmits the induced current to the variable-capacitance battery 17 for charging. Meanwhile, the electromagnet 16 opposite to the first induction coil 11 generates magnetism due to electrification, and the electrode plate 7 at the top of the extension tube 5 is pushed out to the spinal cord for electrical stimulation. At this time, the other group of the first induction coil 11 and the electrode plate 7 far away from the electromagnetic conversion coil 2 are subjected to a reaction force, so that the electrode plate 7 is adsorbed by the electromagnet 16 behind the electrode plate 7, the electrode plate 7 drives the extension tube 5 to contract back to the inner wall of the annular housing 8, and at this time, the electrode plate 7 does not stimulate the spinal cord any more. In short, when the electromagnetic conversion coil 2 is aligned with a first induction coil 11, the electrode plate 7 close to the first induction coil 11 extends out to stimulate the spinal cord; and the electrode sheet 7 corresponding to the other induction coil opposite to the first induction coil 11 is retracted and separated from the spinal cord.
The in-vivo magnetic field generation side includes a ring-shaped blood vessel stent 13 installed in an arterial blood vessel; the blood vessel bracket 13 is connected with a rotating wheel 14 which can rotate along with the blood flow; a second induction coil 12 which is connected with a variable capacitance battery 17 and forms a loop is wound on the rotating wheel 14; two magnets 16 with opposite magnetism are arranged on the blood vessel support 13 at the two sides of the rotating wheel 14.
A communicating pipe 15 for passing a lead is connected between the in-vivo magnetic field induction side and the in-vivo magnetic field generation side. The in-vivo magnetic field induction side and the in-vivo magnetic field generation side are connected by a communication pipe 15.
A one-way stopper for preventing inflow of blood is provided in the communicating tube 15. Because of the one-way plug, blood in the blood vessel cannot enter the communicating tube 15, but heat generated in the in-vivo sensing side can enter the blood vessel through the one-way plug and be carried out of the body along with the flow of the blood.
The electrode plates 7 are four electrode plates 7 which are uniformly distributed on the annular shell 8. Through the stimulation to the spinal cord nerve in four directions, avoid long-term the same direction of stimulating and cause excessive loss.
When the variable-capacitance battery charging device works, the variable magnetic field can be generated by the external magnetic field generating side, so that the first induction coil 11 in the internal magnetic field induction side generates electromagnetic induction to form current, and the variable-capacitance battery 17 is charged. The variable capacitance battery 17 powers the pulse generator 3, enabling the pulse generator 3 to generate pulsed electrical stimulation and deliver such electrical stimulation to the implanted neural target site via the electrode pad 7. When there is no external magnetic field generation side, the variable capacitance battery 17 can be charged by the internal magnetic field generation side. A magnetic field is formed on the loop-shaped stent 13 on the in-vivo magnetic field induction side by two magnets 16 of opposite magnetic polarity. And the rotating wheel 14 connected to the circular stent 13 rotates with the blood flow. During the rotation of the rotating wheel 14, the second induction coil 12 of the rotating wheel 14 around the variable-capacitance battery 17 forms a loop to cut the magnetic induction line to generate induction current, and the variable-capacitance battery 17 is charged through the induction current. The variable-capacitance battery 17 supplies power to the pulse generator 3, and the pulse generator 3 generates pulse electric stimulation and transmits the pulse electric stimulation to a target position of spinal nerves through the electrode plate 7.
The foregoing is merely an example of the present invention, and common general knowledge in the field of known specific structures and characteristics is not described herein in any greater extent than that known in the art at the filing date or prior to the priority date of the application, so that those skilled in the art can now appreciate that all of the above-described techniques in this field and have the ability to apply routine experimentation before this date can be combined with one or more of the present teachings to complete and implement the present invention, and that certain typical known structures or known methods do not pose any impediments to the implementation of the present invention by those skilled in the art. It should be noted that, for those skilled in the art, without departing from the structure of the present invention, several changes and modifications can be made, which should also be regarded as the protection scope of the present invention, and these will not affect the effect of the implementation of the present invention and the practicability of the patent. The scope of the claims of the present application shall be determined by the contents of the claims, and the description of the embodiments and the like in the specification shall be used to explain the contents of the claims.
Claims (5)
1. The special external charging coupling device for spinal cord electrical stimulation comprises an external magnetic field generating side and an internal magnetic field induction side; the in-vivo magnetic field induction side comprises a first induction coil used for receiving the variable magnetic field generated by the in-vivo magnetic field generation side and a variable capacitance battery connected with the first induction coil; the variable-capacitance battery is connected with a pulse generator and an electrode plate; the method is characterized in that: further comprising an in-vivo magnetic field generation side; the in-vivo magnetic field generation side includes a stent installed in a blood vessel; the blood vessel support is connected with a rotating wheel which can rotate along with the flow of blood; a second induction coil connected with the variable-capacitance battery is wound on the rotating wheel; two magnets with opposite magnetism are arranged at the positions on the two sides of the rotating wheel on the blood vessel bracket;
the magnetic field induction side in the body comprises an annular shell sleeved on the spine; the pulse generator and the variable capacitance battery are disposed within an annular housing; the electrode plate is arranged on the contact surface of the annular shell and the vertebra;
a main induction coil connected with the variable capacitance battery only is arranged in the annular shell along the communication direction of the annular shell; the axis of the total induction coil is perpendicular to the axis of each first induction coil.
2. The special external charging coupling device for spinal cord electrical stimulation according to claim 1, wherein: the external magnetic field generating side comprises an electromagnetic conversion coil which is used for generating a variable electromagnetic field and is coaxial with the first induction coil.
3. The special external charging coupling device for spinal cord electrical stimulation according to claim 1, wherein: and a communicating pipe for a lead to pass through is connected between the internal magnetic field induction side and the internal magnetic field generation side.
4. The special external charging coupling device for spinal cord electrical stimulation according to claim 3, wherein: the communicating pipe is internally provided with a one-way plug for preventing blood from flowing in.
5. The special external charging coupling device for spinal cord electrical stimulation according to claim 1, wherein: the electrode plates are uniformly distributed on the annular shell.
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| Publication number | Priority date | Publication date | Assignee | Title |
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| WO2013070875A1 (en) * | 2011-11-08 | 2013-05-16 | Nevro Corporation | Medical device contact assemblies for use with implantable leads, and associated systems and methods |
| CN105769169A (en) * | 2016-04-01 | 2016-07-20 | 中国科学院电工研究所 | Spinal cord intra-operative monitoring device |
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| US20040073267A1 (en) * | 2002-10-09 | 2004-04-15 | Asher Holzer | Micro-generator implant |
| CN100386916C (en) * | 2006-04-28 | 2008-05-07 | 清华大学 | Wireless charging device through skin in use for implantation type medical treatment instrument |
| US20090171448A1 (en) * | 2007-04-27 | 2009-07-02 | Uri Eli | Implantable device with miniature rotating portion for energy harvesting |
| CN106512214A (en) * | 2016-12-20 | 2017-03-22 | 北京品驰医疗设备有限公司 | Implantable sacral nerve stimulator adopting wireless percutaneous charging mode |
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| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| WO2013070875A1 (en) * | 2011-11-08 | 2013-05-16 | Nevro Corporation | Medical device contact assemblies for use with implantable leads, and associated systems and methods |
| CN105769169A (en) * | 2016-04-01 | 2016-07-20 | 中国科学院电工研究所 | Spinal cord intra-operative monitoring device |
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