CN101980412A - A Percutaneous Closed-Loop Controlled Charging Device for Implantable Medical Instruments - Google Patents
A Percutaneous Closed-Loop Controlled Charging Device for Implantable Medical Instruments Download PDFInfo
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Abstract
The invention discloses a percutaneous closed-loop control charging device for implantation type medical treatment instrument and belongs to the technical field of implantation medical instrument. The percutaneous closed-loop control charging device for implantation type medical treatment instrument comprises an external charger and an internal implantation type medical instrument. An external energy transmitting coil is a large-size flat magnetic core coil, and an internal energy receiving coil is a hollow coil; the external energy transmitting coil transmits electromagnetic energy by adopting a resonance electromagnetic coupling manner with parallel central shafts; and the electrical energy obtained by the internal energy receiving coil charges an internal rechargeable battery through an internal charge control circuit. The closed-loop control charging device communicates in a pulse position modulation manner for closed-loop control to ensure the energy received by the implantation medical instrument in different charging phases to be within the normal range, effectively control the heating and increase the safety; the closed-loop control charging device calculates the efficiency by the internal feedback parameter to realize counterpoint prompt and increase the charging efficiency. The percutaneous wireless charging method can charge the implantation type medical instrument by a titanium casing, is safe and reliable in charging, and can be applied to all types of implantation type medical instruments equivalent to a deep brain stimulator in power level.
Description
Technical field
The present invention relates to be used for implantation medical equipment through skin closed-loop control charging device, belong to the implantation medical equipment technical field.
Background technology
The implantation medical equipment kind is a lot, and range of application is also very wide, as heart pacemaker, brain pacemaker, muscle stimulator, artificial cochlea etc.All kinds of implantation medical equipment prevailing prices are high, but the life-span is shorter mostly.The principal element in restriction implantation medical equipment life-span is the capacity of battery, and existing implantation medical equipment product adopts the lithium primary cell of high-energy-density to power more.General implantation medical equipment has only the life-span about 3 to 5 years.In case the energy content of battery exhausts, the patient just has to undergo surgery again, changes implantation medical equipment, and not only for the patient causes wound on the health, expensive price is also brought huge economic pressures for the patient.For implantation medical equipment, the energy supply has become a bottleneck problem that limits its development.
For prolonging the useful life of implantation medical equipment, rechargeable lithium battary begins to be applied to the implantable medical field as the substitute of lithium primary cell.With respect to lithium primary cell, lithium rechargeable batteries is the electric energy support that implantation medical equipment provides the longer time with littler volume, lighter weight.Implantation medical equipment is implanted in patient's body, and has tissue such as skin to isolate between external charging device, need generally based on the electromagnetic coupled principle, utilize the penetration by electromagnetic fields human body skin to transmit electric energy to implantation medical equipment through skin wireless charging mode.
Implantation medical equipment generally uses the Titanium sealing of biocompatibility, has formed stronger electromagnetic shielding on the one hand, makes on the other hand external being difficult to the coil and the circuit of the titanium enclosure that implants accurately to be located.The wireless charging scheme that Chinese invention patent " chargeable brain depth stimulator " (application number 200410019937.X) provides is based on traditional transformer mode, transmitting coil and receiving coil are wound in respectively on same size " U " the type magnetic core, requirement realizes electromagnetic coupled with the magnetic core aligned position of two coils, but, receiving coil is encapsulated in implantation medical equipment inside, accurately the location is very difficult for it, the magnetic core of transmitting coil and receiving coil is easy to produce deviation, thereby cause the reduction greatly of energy transmission efficiency, the stability of charging can't be guaranteed; In addition, U type structured core requires magnetic core to have bigger height, is difficult to be applied to pursue implantation medical equipment frivolous, miniaturization.U.S.'s application for a patent for invention " implantation medical equipment power transfer and remote measurement drive circuit switched design " (publication number US20050075693A1) provides a kind of design of implantation medical equipment energy transmission system, but and the closely-related heating problem of fail safe does not solve from design point of view at all, but, increased the complexity and the cost of corresponding Machine Design by using special material to reduce heating.PCT application for a patent for invention " the long distance charging of closed loop " (publication number WO2009/055579A1) has provided a kind of closed loop design method; be intended to solve the interruption of charging to patient's daily routines; but to achieve these goals; this patent has been used a plurality of external energy transmitting coils, carries out energy delivery by in closed-loop control selection and the immediate external coil groups of energy i (in vivo) receiving coil (can for a plurality of) and the body.This method has the problem of two maximums: the one, and heating problem can guarantee that heating is in prescribed limit by fan etc. or the inner special material that adopts.The secondth, the governing response speed issue, select suitable external energy transmitting coil because need not stop to carry out closed-loop control, the meeting consuming time of this process is long, may bring the problem of body internal heat generation, and along with patient's action, this process also needs to repeat.
Summary of the invention
At the deficiencies in the prior art, the purpose of this invention is to provide and a kind ofly can satisfy the safe and reliable of implantation medical equipment such as brain depth stimulator requirement through skin wireless closed-loop control charging device, external employing flat magnetic core coil, adopt air core coil in the body, realization is charged to the Medical Instruments that implants from external, by the effective size of received energy in the control volume of closed-loop control, prevent the too high influence to human body of Medical Instruments temperature in the body, external charger can guarantee not exist heating to surpass the problem of body temperature by circuit design simultaneously.In addition, can calculate by charge efficiency and realize inside and outside coil contraposition prompting, improve charge efficiency, improve reliability and fail safe.Closed-loop control realize the different charging stages external in body initial transmissions energy difference, further emitted energy is finely tuned on this basis by closed loop feedback, realize quick adjustment, avoid the body internal heat generation to surpass prescribed limit.In the charge initiation incipient stage, during the promptly initial contraposition, above-mentioned charging with body in the frequency of communicating by letter can increase.The application can be fixed on charger energy transmitting coil body and be implanted near the Medical Instruments, and patient can be movable.In addition, the present invention can be in the charging incipient stage, the signal that external communication coil is coupled to is sampled (this moment telecommunication circuit it goes without doing communication function), charged state in the quick antimer, improve initial charge to bit rate, avoid the initial body internal heat generation problem that bit rate is brought slowly, improve reliability and fail safe.
In order to realize the foregoing invention purpose, the present invention adopts following technical scheme: be used for the charging device through the skin closed-loop control of implantation medical equipment, it is characterized in that, comprise external charger and vivo implantation type Medical Instruments, wherein:
External charger comprises live part and antenna part, wherein
Antenna part has a shell, is built-in with at this shell: energy transmitting coil temperature sensor outside external communication coil, external energy transmitting coil and the individuality, wherein
External energy transmitting coil is a kind of flat magnetic core coil, forms by the magnetic core of a transmitting coil and coaxial arrangement,
External energy transmitting coil temperature sensor is measured the temperature of this external energy transmitting coil;
External communication coil is a kind of flat magnetic core coil, is made up of the magnetic core of a communication coil and coaxial arrangement, and this magnetic core and the used magnetic core of external energy transmitting coil are the magnetic core of same type;
Live part; comprise: power supply circuits, the current sampling circuit, power converting circuit, communication/charging diverter switch, voltage sampling circuit, the charge protection switch that drive amplifying circuit, power amplification/receiving circuit, constitute with resistance; and first microprocessor, wherein:
Power supply circuits; be provided with: Chuan Jie fuse and diode successively; also has an individual outer battery charging charger; external rechargeable battery is successively through described fuse; diode and described voltage sampling circuit are powered to described first microprocessor; the voltage detecting end of described voltage sampling circuit first output and charge protection switch links to each other simultaneously; second output of described voltage sampling circuit and the voltage sample input of described first microprocessor link to each other; outside AC power is received described voltage sampling circuit input by described external battery charge charger; simultaneously; described external battery charge charger is through the rechargeable battery charging of described fuse to described outside
Drive amplifying circuit, be made up of a chip for driving, the drive control signal input of this chip for driving links to each other with the drive control signal output of described first microprocessor,
Power amplification/receiving circuit is connected in series mutually in full-bridge topology mode by four power field effect pipes and forms, and the input that transmits of this power amplification/receiving circuit links to each other with the output that drives amplifying circuit,
Power converting circuit, adopt any in Buck or Boost or the Sepic circuit, the input of this power converting circuit links to each other with the output of described current sampling circuit, respectively to described first microprocessor output voltage signal, to chip for driving and power amplification/receiving circuit power supply
The charge protection switch; be a CMOS electronic switch, this charge protection switch control end links to each other with described first microprocessor input, and the charge protection switch input terminal links to each other with the voltage sampling circuit output; the charge protection output switching terminal links to each other with the current sampling circuit input
Diverter switch is switched in communication/charging, has two, wherein
First communication/charging the diverter switch, it is a CMOS electronic switch, input links to each other with the output of described power amplification/receiving circuit, the output of this first communication/charging diverter switch then links to each other with the input of the PPM communicates decoded unit of first microprocessor, the control end of the described first communication/charging diverter switch then links to each other with the communication/charging switch-over control signal output of described first microprocessor
Second communication/charging diverter switch, it is a MUX, be provided with: the communications reception signal input part, link to each other with the output of described external communication coil, a power amplification/receiving circuit energy output that transmits is arranged, be connected to the input of described external energy transmitting coil, a power amplification/receiving circuit energy output that transmits is arranged in addition, be connected to the input of described external communication coil, control by described second communication/charging diverter switch, the control end of described second communication/charging diverter switch links to each other with the output of the described communication/charging switch-over control signal of described first microprocessor, and described these two communication/charging diverter switches realize the switching between external communication and the charging under described first microprocessor control;
The vivo implantation type Medical Instruments comprises: be placed in following each part in the titanium shell: second microprocessor, communication coil, charging control section part, rechargeable battery, communication processing circuit and treatment module in energy receiving coil, titanium shell and two temperature sensors energy receiving coil, the body, wherein:
The energy receiving coil is flat, and size and weight are all less than described external energy transmitting coil, but both are the central axes placement, are used to receive the electromagnetic energy of described energy transmitting coil output,
The charging control section part is followed in series to form by current rectifying and wave filtering circuit, charging control circuit, rechargeable battery and second microprocessor, wherein:
Current rectifying and wave filtering circuit, input links to each other with the output of described energy receiving coil, and electromagnetic energy is converted to direct current signal by AC signal,
Charging control circuit, adopt chip MCP73841, input links to each other with the output of described current rectifying and wave filtering circuit, and the charging voltage sampled signal is imported/go out end, battery temperature sampled signal to import/go out end and the charging current output links to each other with the corresponding end of described rechargeable battery
Rechargeable battery, output links to each other with the voltage signal input of described second microprocessor,
Telecommunication circuit, the input interconnection of the PPM codec unit of output and described second microprocessor, communication coil interconnection in this telecommunication circuit and the described body receives the signal that described external communication coil is launched, and perhaps transmits to external communication coil;
The treatment module, input links to each other with the treatment signal output part of described second microprocessor;
Second microprocessor, be provided with: titanium shell temperature signal input, energy receiving coil temperature input, and from the input of the temperature signal of the input of the charge capacity sampled signal of described charging control circuit output and rechargeable battery, in addition, also has a input from the output voltage signal of described current rectifying and wave filtering circuit
Described charging control circuit divides following three phases to the control of charging of described rechargeable battery: by charged battery voltage less than the precharge below the set point; constant current charge and reach desired charging voltage after charging; after being full of, stop charging; and the temperature of charging voltage after being full of and described rechargeable battery by described second microprocessor by the described telecommunication circuit in the body; mail to external in the body behind the communication coil; simultaneously also described titanium shell temperature; energy receiving coil temperature mails to external; described first microprocessor has been received through external communication coil in stage of communication; behind each signal that sends by described implantation medical equipment that described power amplification/receiving circuit and PPM communicates decoded circuit are sent; how to adjust the position and the angle of described external energy transmitting coil with display mode prompting user; to realize that better electromagnetic coupled state is to improve charge efficiency; in case it is full to charge; or the temperature of external energy transmitting coil; during the temperature overrun of energy receiving coil, then described first microprocessor cuts off power supply to stop the energy emission by the charge protection switch.
Further, described energy i (in vivo) receiving coil adopts air core coil, places titanium shell inside.Described external energy transmitting coil adopts the flat magnetic core coil, and external energy transmitting coil and energy i (in vivo) receiving coil adopt the central axes mode to place, and by efficiency calculation prompting coil contraposition situation, has improved the stability and the reliability of charging.Especially,, can realize coil coupling contraposition fast, prevent that the energy i (in vivo) receiving coil temperature short time from sharply raising, effectively guarantee fail safe by prompting in the charging starting stage.In the different charging stages, do closed-loop control according to communications feedback information, adjust the emissive porwer of external energy transmitting coil automatically, effectively the received energy of control volume interior loop is installed heating in normal range (NR) thereby the assurance body is interior.
Compared with prior art, the present invention has following beneficial effect: (1) wireless charging device through skin of the present invention can pass skin and the titanium shell charges to the Medical Instruments of implant into body, prolong the useful life of implantation medical equipment, alleviated misery and financial burden that the patient performs the operation once more; (2) reduced the size and the weight of implantation medical equipment, thereby reduced implantation medical equipment, improved patient's quality of life as the harmful effect of the foreign matter in the human body to patient body; (3) can effectively control in the charging process size of received energy in the body by closed-loop control, prevent the too high influence of unit temp in the body, improve fail safe human body; (4) can feed back by charge efficiency, realization body, inner-outer coil contraposition are pointed out automatically, improve charge efficiency, improve reliability and fail safe; (5) can be in the initial contraposition process of charging, external telecommunication circuit it goes without doing communication function, but the signal that is coupled on it in the charging process is sampled, charged state in the antimer fast, improve initial charge to bit rate, avoid the initial body internal heat generation problem that bit rate is brought slowly, improve reliability and fail safe; (6) there are the up to ten million patients that use implantation medical equipment in the whole nation, and the present invention has high economic benefit and social benefit.
Description of drawings
Fig. 1 is an overall schematic of the present invention.
Fig. 2 is a receiving coil electromagnetic coupled schematic diagram in external transmitting coil of the present invention and the body.
Fig. 3 is a charging master-plan principle schematic.
Fig. 4 is a part theory diagram in the body of the present invention.
Fig. 5 is the closed-loop control schematic diagram.
Fig. 6 is each stage energy emission schematic diagram of charging.
Fig. 7 is the charging and the sequential distribution diagram of communicating by letter in the charging process.
Embodiment
Below in conjunction with accompanying drawing the execution mode that is used for the wireless charging device through skin of implantation medical equipment of the present invention is made a detailed description.
As shown in Figure 1, of the present invention be used for implantation medical equipment through skin closed-loop control charging device, form by external charger and vivo implantation type Medical Instruments 14; Wherein external charger is made up of live part 10 and antenna part 39.Antenna part 39 comprises external communication coil 11, external energy transmitting coil 13 and external communication coil and the shared magnetic core 12 of external energy transmitting coil etc.; Implantation medical equipment titanium shell 14 inside comprise communication coil 15, energy receiving coil 16, charging control circuit 17, rechargeable battery 18 etc. in the body.
The external energy transmitting coil 13 of internal magnetic core 12 and energy i (in vivo) receiving coil 16 are by the electromagnetic energy transfer of electromagnetic coupled realization through skin and titanium shell 14.The energy receiving coil 16 that implants takes up space less, to alleviate the volume and weight of implantation medical equipment.Less-restrictive for external energy transmitting coil 13 and magnetic core 12, can be by changing coil turn and core shapes, size, adjust the driving voltage of external energy transmitting coil and frequency etc., improve the coupling efficiency between transmitting power and energy transmitting coil and the energy receiving coil, thereby improve the obtainable energy of energy i (in vivo) receiving coil.Communication coil 15 carries out inside and outside signal transmission by coupled modes in external communication coil 11 and the body, is used for body, inside and outside information bidirectional transmission.
As shown in Figure 2, the external energy transmitting coil 13 through skin closed-loop control charging device that is used for implantation medical equipment is magnetic core coil, 12 is described magnetic core, and the use of magnetic core can be regulated inductance value, the number of turn etc. and the closely-related parameter of energy transmission efficiency, to improve coupling efficiency.The magnetic core 12 of the described device of the application and external energy transmitting coil 13 do not exist heating to exceed the problem of the normal range (NR) that people's physical efficiency bears, and need not to adopt the special material heat radiation, and be safe and simple.Energy i (in vivo) receiving coil 16 is an air core coil, and receiving coil and transmitting coil adopt the central axes mode to place.The energy transmitting coil 13 that the described energy receiving coil that implants 16 requires to put into the titanium shell and take up room less, external is a flat, and its area is slightly larger than energy i (in vivo) receiving coil 16, and its inside is the cylinder magnetic core 12 of 1 flat.Described external energy transmitting coil and core shapes are designed to flat and weight is mainly located for convenience in the charging process.When external energy transmitting coil 13 time with respect to the 16 generative center axle offsets of energy i (in vivo) receiving coil, this device can guarantee that all coupling effect is better in PT positional tolerance is the scope of 1cm, body is implanted into the heating of Medical Instruments in normal range (NR), simultaneously, external energy transmitting coil 13, magnetic core 12 and energy i (in vivo) receiving coil 16 temperature are in normal range (NR).The tolerance of coil coupling and the stability of charging are guaranteed.When the position of coil changed, charging system showed that by efficient providing contraposition points out, and guarantees high charge efficiency in the charging process.Compare prior art, in the different charging stages, adjust the transmitting power of external energy transmitting coil by closed-loop control, guarantee the heating of vivo implantation type Medical Instruments in normal range (NR), charging operations is more simple, and charging process is more stable, safety.
As shown in Figure 3, the external charger through skin closed-loop control charging device that is used for implantation medical equipment partly comprises live part 10 and antenna part 39.
Wherein, energy transmitting coil 13 places in the antenna casing 39, also comprises external communication coil 11 in the antenna casing, magnetic core 12, external energy transmitting coil temperature sensor 31.The implantation medical equipment that antenna casing 39 is pressed close to implant in the charging process charges, about charging distance 1.5cm.External communication coil 11 is used for the inside and outside two-way communication of body, and communication distance is greater than charging distance.The temperature sampling signal of energy transmitting coil temperature sensor 31 is sent into first microprocessor 32 and is done overheat protector and judge, when temperature exceeds normal range (NR), microprocessor can cut off charging processes by charge protection switch 38.
Power amplification receiving circuit 33 mainly is made up of four power field effect pipes that constitute the full-bridge topology, the different drive pulse signal that first microprocessor 32 sends, behind the amplifying circuit 37 of overdriving (chip for driving is TC4424), realize power amplification circuit or communications reception circuit.
PPM communicates decoded circuit 35 is expanded circuit by filter circuit, shaping circuit and pulsewidth and is formed.
As shown in Figure 4, the body through skin closed-loop control charging device that is used for implantation medical equipment comprises second microprocessor 41, communication coil 15, charging control section part (comprising current rectifying and wave filtering circuit 40, charging control circuit 17, rechargeable battery 18 and second microprocessor 41), rechargeable battery, communication processing circuit and treatment module in energy i (in vivo) receiving coil 16, titanium shell and energy receiving coil temperature sensor 44, the body inner the branch.
Figure 5 shows that the closed-loop control schematic diagram.Whole charging device is by power section 50, and control section 51 is formed.Charger circuit 10 is by external energy transmitting coil 13 emitted energies, energy i (in vivo) receiving coil 16 received energies.Energy i (in vivo) receiving coil 16 received signals are through rectification, filter circuit obtains d. c. voltage signal, this direct current signal, cell voltage, electric current and temperature etc. are in body after microprocessor 41 sampling, at the charging stopping period, communication coil 15 is transmitted into external in body, external microprocessor 32 is done the closed loop computing, be used for doing the control of closed loop energy, adjust the emissive porwer of external energy transmitting coil 13 in real time, to guarantee that received energy is in normal range (NR) in the body, guarantee the fail safe of charging, simultaneously the efficient situation is calculated, to body, the alignment situation of inner-outer coil is pointed out, to guarantee charging process high efficiency and stability.
Fig. 6 is the outer energy emission of each stage body of a charging schematic diagram.External microprocessor 32 is judged the residing different phase of charging according to charged state feedback information in the body, difference according to the charging stage, the emissive porwer of the outer energy transmitting coil 13 of external microprocessor 32 control volumes, and then adjusted received energy on the energy i (in vivo) receiving coil 16, thereby guarantee that received energy is in normal range (NR) in the body.In preliminary filling, constant current and constant-voltage phase, external emissive porwer is shown in 61,62 and 63, and closed-loop control system can guarantee that body is implanted into the Medical Instruments temperature in the reasonable scope according to actual charged state feedback information in each stage fine-tuned emission intensity.
Fig. 7 is charging in the charging process, communication sequential distribution diagram.High amplitude, low frequency are adopted in charging, and low amplitude value, high-frequency are adopted in communication.Charging process can be carried out inside and outside communication exchange information at interval.
In the charge initiation incipient stage, during the promptly initial contraposition, above-mentioned charging with body in the frequency of communicating by letter can increase.Simultaneously, external communication coil it goes without doing 11 this moments communication function in the charging process, the voltage signal that is coupled on it is sampled by microprocessor 32 in charging process, comes charge condition in the antimer according to the voltage magnitude size that is coupled to.Utilize the voltage signal that is coupled in the charging process on communication coil charged state in the antimer fast, improve initial charge, avoid the body internal heat generation problem initially bit rate brought slowly, improve reliability and fail safe bit rate.
Aforesaid way is the preferred embodiment of the present invention, for those skilled in the art, on the basis that is used for the wireless charging device through skin of implantation medical equipment disclosed by the invention, be easy to expect being applied to various instrument systems, and be not limited only to the described system configuration of the specific embodiment of the invention, therefore previously described mode is just preferred, and does not have restrictive meaning.
Claims (4)
1. be used for the charging device through the skin closed-loop control of implantation medical equipment, it is characterized in that, comprise external charger and vivo implantation type Medical Instruments, wherein:
External charger comprises live part and antenna part, wherein
Antenna part has a shell, is built-in with at this shell: energy transmitting coil temperature sensor outside external communication coil, external energy transmitting coil and the individuality, wherein
External energy transmitting coil is a kind of flat magnetic core coil, forms by the magnetic core of a transmitting coil and coaxial arrangement,
External energy transmitting coil temperature sensor is measured the temperature of this external energy transmitting coil;
External communication coil is a kind of flat magnetic core coil, is made up of the magnetic core of a communication coil and coaxial arrangement, and this magnetic core and the used magnetic core of external energy transmitting coil are the magnetic core of same type;
Live part; comprise: power supply circuits, the current sampling circuit, power converting circuit, communication/charging diverter switch, voltage sampling circuit, the charge protection switch that drive amplifying circuit, power amplification/receiving circuit, constitute with resistance; and first microprocessor, wherein:
Power supply circuits; be provided with: Chuan Jie fuse and diode successively; also has an individual outer battery charging charger; external rechargeable battery is successively through described fuse; diode and described voltage sampling circuit are powered to described first microprocessor; the voltage detecting end of described voltage sampling circuit first output and charge protection switch links to each other simultaneously; second output of described voltage sampling circuit and the voltage sample input of described first microprocessor link to each other; outside AC power is received described voltage sampling circuit input by described external battery charge charger; simultaneously; described external battery charge charger is through the rechargeable battery charging of described fuse to described outside
Drive amplifying circuit, be made up of a chip for driving, the drive control signal input of this chip for driving links to each other with the drive control signal output of described first microprocessor,
Power amplification/receiving circuit is connected in series mutually in full-bridge topology mode by four power field effect pipes and forms, and the input that transmits of this power amplification/receiving circuit links to each other with the output that drives amplifying circuit,
Power converting circuit, adopt any in Buck or Boost or the Sepic circuit, the input of this power converting circuit links to each other with the output of described current sampling circuit, respectively to described first microprocessor output voltage signal, to chip for driving and power amplification/receiving circuit power supply
The charge protection switch; be a CMOS electronic switch, this charge protection switch control end links to each other with described first microprocessor input, and the charge protection switch input terminal links to each other with the voltage sampling circuit output; the charge protection output switching terminal links to each other with the current sampling circuit input
Diverter switch is switched in communication/charging, has two, wherein
First communication/charging the diverter switch, it is a CMOS electronic switch, input links to each other with the output of described power amplification/receiving circuit, the output of this first communication/charging diverter switch then links to each other with the input of the PPM communicates decoded unit of first microprocessor, the control end of the described first communication/charging diverter switch then links to each other with the communication/charging switch-over control signal output of described first microprocessor
Second communication/charging diverter switch, it is a MUX, be provided with: the communications reception signal input part, link to each other with the output of described external communication coil, a power amplification/receiving circuit energy output that transmits is arranged, be connected to the input of described external energy transmitting coil, a power amplification/receiving circuit energy output that transmits is arranged in addition, be connected to the input of described external communication coil, control by described second communication/charging diverter switch, the control end of described second communication/charging diverter switch links to each other with the output of the described communication/charging switch-over control signal of described first microprocessor, and described these two communication/charging diverter switches realize the switching between external communication and the charging under described first microprocessor control;
The vivo implantation type Medical Instruments comprises: be placed in following each part in the titanium shell: second microprocessor, communication coil, charging control section part, rechargeable battery, communication processing circuit and treatment module in energy receiving coil, titanium shell and two temperature sensors energy receiving coil, the body, wherein:
The energy receiving coil is flat, and size and weight are all less than described external energy transmitting coil, but both are the central axes placement, are used to receive the electromagnetic energy of described energy transmitting coil output,
The charging control section part is followed in series to form by current rectifying and wave filtering circuit, charging control circuit, rechargeable battery and second microprocessor, wherein:
Current rectifying and wave filtering circuit, input links to each other with the output of described energy receiving coil, and electromagnetic energy is converted to direct current signal by AC signal,
Charging control circuit, adopt chip MCP73841, input links to each other with the output of described current rectifying and wave filtering circuit, and the charging voltage sampled signal is imported/go out end, battery temperature sampled signal to import/go out end and the charging current output links to each other with the corresponding end of described rechargeable battery
Rechargeable battery, output links to each other with the voltage signal input of described second microprocessor,
Telecommunication circuit, the input interconnection of the PPM codec unit of output and described second microprocessor, communication coil interconnection in this telecommunication circuit and the described body receives the signal that described external communication coil is launched, and perhaps transmits to external communication coil;
The treatment module, input links to each other with the treatment signal output part of described second microprocessor;
Second microprocessor, be provided with: titanium shell temperature signal input, energy receiving coil temperature input, and from the input of the temperature signal of the input of the charge capacity sampled signal of described charging control circuit output and rechargeable battery, in addition, also has a input from the output voltage signal of described current rectifying and wave filtering circuit
Described charging control circuit divides following three phases to the control of charging of described rechargeable battery: by charged battery voltage less than the precharge below the set point; constant current charge and reach desired charging voltage after charging; after being full of, stop charging; and the temperature of charging voltage after being full of and described rechargeable battery by described second microprocessor by the described telecommunication circuit in the body; mail to external in the body behind the communication coil; simultaneously also described titanium shell temperature; energy receiving coil temperature mails to external; described first microprocessor has been received through external communication coil in stage of communication; behind each signal that sends by described implantation medical equipment that described power amplification/receiving circuit and PPM communicates decoded circuit are sent; how to adjust the position and the angle of described external energy transmitting coil with display mode prompting user; to realize that better electromagnetic coupled state is to improve charge efficiency; in case it is full to charge; or the temperature of external energy transmitting coil; during the temperature overrun of energy receiving coil, then described first microprocessor cuts off power supply to stop the energy emission by the charge protection switch.
2. according to claim 1 be used for implantation medical equipment through skin closed-loop control charging device, it is characterized in that described power amplification receiving circuit adopts the full-bridge topology of band dead band control.
3. according to claim 1 be used for implantation medical equipment through skin closed-loop control charging device, it is characterized in that, described charging control circuit is controlled each stage of charging, monitoring simultaneously comprises the charging current of described rechargeable battery, cell voltage and battery temperature are at interior charging status information, and regularly pass to above-mentioned charging status information external, and can described battery temperature overrun or charging do not finish but situation that the timing that charge has arrived take place in the described charging current signal of cut-out automatically, circuit in the body is protected, and pass to externally by described second microprocessor, make the emission of external energy stop; After electric quantity of rechargeable battery was full of, described charging control circuit can cut off described charging current automatically, and was positioned at external energy radiating circuit by telecommunication circuit notice in the body and stops the electromagnetic energy emission, finished charging.
4. according to claim 1 be used for implantation medical equipment through skin closed-loop control charging device, it is characterized in that described PPM communicates decoded circuit is expanded each circuit by filtering, shaping, pulsewidth and is composed in series successively.
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Citations (2)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| US6088619A (en) * | 1999-02-26 | 2000-07-11 | Implex Aktiengesellschaft Hearing Technology | Device and method for aiding the positioning of an external part relative to an implantable part of a charging system for an implantable medical device |
| CN101352596A (en) * | 2008-09-19 | 2009-01-28 | 清华大学 | Externally powered implantable medical devices |
-
2010
- 2010-09-27 CN CN2010102938668A patent/CN101980412B/en active Active
Patent Citations (2)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| US6088619A (en) * | 1999-02-26 | 2000-07-11 | Implex Aktiengesellschaft Hearing Technology | Device and method for aiding the positioning of an external part relative to an implantable part of a charging system for an implantable medical device |
| CN101352596A (en) * | 2008-09-19 | 2009-01-28 | 清华大学 | Externally powered implantable medical devices |
Non-Patent Citations (1)
| Title |
|---|
| 《中国生物医学工程学报》 20090630 王伟明,马伯志,郝红伟,刘方军,胡春华,李路明 用于植入式医疗仪器的无线通信系统研究 第408-414页 1-4 第28卷, 第3期 * |
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Address after: 100084 mailbox 100084-82, Beijing City Patentee after: TSINGHUA University Country or region after: China Patentee after: Beijing Pinchi Medical Equipment Co.,Ltd. Address before: 100084 mailbox 100084-82, Beijing City Patentee before: TSINGHUA University Country or region before: China Patentee before: BEIJING PINS MEDICAL Co.,Ltd. |
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| CP03 | Change of name, title or address |