CN102148561A - Self-holding type implantable miniature generator using vasomotion - Google Patents
Self-holding type implantable miniature generator using vasomotion Download PDFInfo
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- CN102148561A CN102148561A CN2011100554348A CN201110055434A CN102148561A CN 102148561 A CN102148561 A CN 102148561A CN 2011100554348 A CN2011100554348 A CN 2011100554348A CN 201110055434 A CN201110055434 A CN 201110055434A CN 102148561 A CN102148561 A CN 102148561A
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Abstract
The invention relates to a self-holding type implantable miniature generator using vasomotion, belonging to the technical field of micro electro mechanical systems. The self-holding type implantable miniature generator using vasomotion comprises a flexible shielding layer, a structural shielding layer, a stator and a plurality of rotors, wherein the flexible shielding layer coats the blood vessel; the stator and the rotors are arranged outside the flexible shielding layer; and the structural shielding layer coats the stator and the rotors. The self-holding type implantable miniature generator using vasomotion can acquire an appropriate energy source from a human body per se, the inconvenience caused to a patient by replacing batteries is avoided, and the discomfort of human body and the risk of inflammatory response, caused by acquiring the energy source, are reduced.
Description
Technical field
The present invention relates to a kind of device of micro-electromechanical system field, specifically is a kind of implantable microgenerator of angiokinetic self-sustaining that utilizes.
Background technology
In recent years, along with MEMS (micro electro mechanical system) (MEMS:Micro-Electro-Mechanical Systems) continuous advancement in technology, make micro-system ranges of application such as microelectronic device and microsensor constantly enlarge, be widely used in a plurality of fields, particularly medical domain.Implantable micro-system is meant utilizes the MEMS technology to make, can implant into body and produce interactional microsystem with human body.The energy supply of implantable micro-system generally solves by power supply, and the performance of power supply and quality are present most of MEMS technology key in application places.
For the energy supply problem of implantable micro-system, general solution is outside energy supply and from charged pool.Outside energy supply comprises outside directly line energy supply and based on the methods such as energy acquisition energy supply of vibration, the wherein outside directly line energy supply reaction that causes inflammation easily, and increased patient's immoderation, be not suitable for long-term use.Energy acquisition energy supply method based on vibration generally has three kinds: piezoelectric type, electrostatic and electromagnetic type.Wherein again because piezoelectric energy collector have simple in structure, energy density is high and the life-span is long, can form the focus of attention into people with advantage such as MEMS processing technology compatibility.But the MEMS piezoelectric type vibrational energy collector of present fully-integrated manufacturing also is difficult to satisfy the low energy-consumption electronic device demands of applications: on the one hand, present MEMS energy acquisition technology also can't be effectively under low frequency environments (less than 100Hz) carry out energy acquisition; On the other hand, the electric energy power density that is obtained is also less, and depends on the external environment condition vibration frequency.Also wanting outside vibration source to cooperate when this energy-provision way uses, use for long-term implantation, also is very inconvenient.The traditional electrical chemical cell supply power mode that carries exist the life-span short, need often to change and shortcoming such as storage power is limited, and change the cell process complexity under certain conditions, cost is very high or not may realize changing.
Find through retrieval prior art, C.Eunpyo, people such as S.Q.Lee are at 5th IEEE International Conferenceon Nano/Micro Engineered and Molecular Systems (2010), pp.680-683 writes articles " MEMS powergeneration using activation of cardiomyocytes on a PMN-PT diaphragm " and (utilizes the micromachine generator of the cardiac muscle cell's driving that activates on the PMN-PT single crystal film, " NEMS2010 "), the single crystal film of the PMN-PT that this technology adopts has an interdigital electrode design, and this makes the external pressure that is carried on this film to become possibility by the piezoelectric effect output voltage.Though the device that the document proposes can be as the alternative source of micro-/ nano robot or implantable micro-system, but for implantable micro-system, if each microgenerator all is equipped with a core that drives with the cardiac muscle cell, its range of application can be restricted so.U.S. Patent number: US7,579,757, " Method and micro power generator for generatingelectrical power from low frequency vibrational energy " (obtaining the method and the microgenerator of electric energy from low-frequency vibration), this technology discloses a kind of method that obtains electric energy from low-frequency vibration.This technology can be converted to dither to low-frequency vibration by mechanical means, and the method by electromagnetic coupled obtains electric energy then.The stability of this method and life-span are all very limited, it are applied in also have very big distance on the implantable micro-system.
Summary of the invention
The present invention is directed to the deficiencies in the prior art, a kind of implantable microgenerator of angiokinetic self-sustaining that utilizes is proposed, make it obtain the suitable energy from human body self, avoided changing battery to the inconvenience that the patient causes, reduced owing to obtaining the risk that does not accommodate inflammatory reaction that energy source causes human body.
The present invention is achieved by the following technical solutions, the present invention includes: flexible shielding layer, structual shield layer, stator and several rotors with array distribution, wherein: the flexible shielding layer coats blood vessel, stator and rotor are arranged at flexible shielding layer outside, and the structual shield layer is coated on outside stator and the rotor.
Be equipped with electrode on described flexible shielding layer and the structual shield layer.
Described stator comprises: with the perforate and the conductive helix circle winding of array distribution, wherein: the area of each perforate is less than the internal surface area of respective rotor, conductive helix circle winding is arranged at the both sides of perforate, when blood vessel expands or shrink, when promptly producing relative motion, rotor does not contact with perforate.
Described conductive helix circle winding wire wide region is 10nm-10 μ m.
Described rotor is the movable film that comprises closing coil, and the position of the both sides counter electrode of this rotor is provided with the contact.
The present invention utilizes blood circulation time in blood vessel to cause the phenomenon of vessel cycle pucker ﹠ bloat, drive rotor periodically contacts flexible shielding layer and structual shield layer respectively in the closed space of flexible shielding layer and the encirclement of structual shield layer electrode, finish the conversion of mechanical energy and electric energy by electromagnetic induction, and can adjust density and the number of plies, the quantity of rotor and the density of closing coil of conductive helix circle winding, reach the effect that adapts to different capacity output.
Flexible shielding layer and structual shield layer can completely cut off body fluid.Stator produces magnetic field by conductive helix circle winding, and rotor contacts with the flexible shielding layer by the perforate at stator, and drives rotor motion generation electric energy by this flexible shielding layer.The flexible shielding layer can adapt to the pucker ﹠ bloat of blood vessel, and when vessel retraction, the electrode of the contact of rotor contact flexible shielding layer is in order to output voltage.The structual shield layer can the supporting construction assurance device itself be squeezed and damages, and when blood vessel expanded, the electrode of the contact contact structures screen of rotor was in order to output voltage.
The present invention is simple in structure, makes easily, and volume is suitable, only need give starting resistor of stator when implanting, and can export electric energy under blood vessel drives, and satisfies the power consumption needs of the implantable micro-system of self-sustaining.
Description of drawings
Fig. 1 is the typical implant site of the present invention in human body and the schematic diagram of mode.
Fig. 2 is stator and the view of rotor when vessel retraction in the present embodiment.
Fig. 3 is stator and the view of rotor when blood vessel expands in the present embodiment.
The last figure of Fig. 4 is the schematic diagram that stator and the rotor in the present embodiment contacts with the structual shield layer when blood vessel expands.
Fig. 4 figure below is the schematic diagram that stator and the rotor in the present embodiment contacts with the flexible shielding layer when vessel retraction.
Fig. 5 is the stator in the present embodiment and the schematic diagram of rotor relative position.
Embodiment
Below in conjunction with accompanying drawing embodiments of the invention are elaborated, present embodiment is being to implement under the prerequisite with the technical solution of the present invention, provided detailed execution mode and concrete operating process, but protection scope of the present invention is not limited to following embodiment.
As Fig. 1 and shown in Figure 5, present embodiment comprises: flexible shielding layer 1, rotor 2, stator 3 and structual shield layer 6, wherein: flexible shielding layer 1 coats blood vessel 4, and stator 3 and rotor 2 are arranged at flexible shielding layer 1 outside, and structual shield layer 6 coats outside stator 3 and the rotor 2.
As shown in Figure 4 and Figure 5, be equipped with electrode 5 on described flexible shielding layer 1 and the structual shield layer 6.
Described stator 3 comprises: with the perforate 8 and the conductive helix circle winding 7 of array distribution, wherein: the area of perforate 8 is less than the internal surface area of rotor 2, and conductive helix circle winding 7 is arranged at the both sides of perforate 8.
Described conductive helix circle winding 7 live width scopes are 10nm-10 μ m.
As shown in Figure 4, described rotor 2 comprises the movable film of closing coil, and the position of the both sides counter electrode of rotor 2 is provided with the contact (not shown).Described contact contacts with electrode 5, because the contact is very little, and is the dot structure of closing coil.
When blood vessel 4 expanded or shrinks, when promptly producing relative motion, rotor 2 did not contact with perforate 8.
Described conductive helix circle winding 7 adopts flexible material, in order to adapt to the magnetic field of different occasions, can adjust the loop density of single layer of flexible as required, the coil number of plies.
Described rotor 2 is the movable films that comprise closing coil, and the quantity of this closing coil can be adjusted loop density as required, and also can adjust the quantity of rotor 2 as required, forms rotor 2 arrays.
Described movable film adopts metallic film.
The operation principle of present embodiment is: as shown in Figure 1, this device finds a suitable blood vessel 4 near the implant site of implantable micro-system, and the principle of choosing is that the electric power demand and the surgery that satisfy implantable micro-system are implanted easy.When this device implant into body, because the conductive helix circle winding 7 in the stator 3 does not have electric current to pass through, can not produce induced field, thereby need award 3 one starting resistors of stator, make stator 3 start, after blood vessel 4 began to drive rotor 2 and reaches stable state, this device can independently be exported electric energy.
As Fig. 2 and shown in Figure 5, in blood vessel 4 contraction processes, under the tractive of flexible shielding layer 6, rotor 2 shrinks to blood vessel 4 by the perforate 8 of stator 3, and the magnetic flux of the closing coil of rotor 2 takes place to change fast, induces voltage in the closing coil, when blood vessel 4 is retracted to the limit, rotor 2 closely is centered around around the stator 3 and the single rotor in the rotor 2 does not contact mutually, and the electrode 5 of flexible shielding layer 6 contacts output voltage with the contact of rotor 2.
As Fig. 3 and shown in Figure 5, in blood vessel 4 expansion processes, under the extruding of flexible shielding layer 6, stator 3 expands under the driving of blood vessel 4, and the perforate 8 of rotor 2 by stator 3 blood vessel 4 dorsad is the radial pattern motion, and the magnetic flux of the closing coil of rotor 2 takes place to change fast, induce voltage in the closing coil, when blood vessel 4 expand into the limit, the electrode 5 of structual shield layer 1 contacted output voltage with the contact of rotor 2.
A pucker ﹠ bloat process of blood vessel 4, this device are promptly finished one-period output.Afterwards, along with the periodicity of heart is beated, this device is periodically finished output.And can regulate power output in time according to the needs of human motion.
In order to adapt to the array of rotor 2, the contact of the electrode 5 of rotor 2 and structual shield layer 1, flexible shielding layer 6 can be done into strips, and the voltage of the array of rotor 2 is drawn.Adopt the mode of contact and electrode 5 output voltages, avoided the complexity of connecting line and the complex electromagnetic fields that is coupled out thus.The other parts of rotor 2 except that electrode 5 all do not contact with flexible shielding layer 6 with structual shield layer 1, reduce resistance and energy loss with this.
Conductive helix circle winding 7 gets around the perforate 8 at stator, and when blood vessel 4 expanded or shrinks, when promptly producing relative motion, rotor 2 did not contact with perforate 8, reduces resistance and energy loss with this.Because perforate 8 internal diameters of stator 3 are less than stator 3, conductive helix circle winding 7 interconnects by the space around the perforate 8 of stator 3.
As shown in table 1, it is as shown in the table for the used size of the application request of present embodiment.
Table 1 0.5 * 0.5 * 1cm
3One group of modular design parameter of size microgenerator
| Be suitable for the contracted diameter (mm) of |
3 |
| Whole microgenerator size (long * wide * thick) (cm 3) | 1×1×1 |
| Structual shield layer (length * diameter * thick) (μ m 3) | 10000×10000×500 |
| Flexible shielding layer (length * diameter * thick) (μ m 3) | 10000×3000×100 |
| Rotor (length * diameter * thick) (μ m 3) | 180×3600×2000 |
| Stator (length * diameter * thick) (μ m 3) | 10000×3500×200 |
| Conductive helix circle winding standard live width and interval (μ m) | 1 |
| Closing coil standard live width and interval (μ m) | 1 |
Claims (5)
1. one kind is utilized the implantable microgenerator of angiokinetic self-sustaining, it is characterized in that: comprising: flexible shielding layer, structual shield layer, stator and several rotors with array distribution, wherein: the flexible shielding layer coats blood vessel, stator and rotor are arranged at flexible shielding layer outside, the structual shield layer is coated on outside stator and the rotor, is equipped with electrode on described flexible shielding layer and the structual shield layer.
2. the implantable microgenerator of angiokinetic self-sustaining that utilizes according to claim 1, it is characterized in that, described stator comprises: with the perforate and the conductive helix circle winding of array distribution, wherein: the area of each perforate is less than the internal surface area of respective rotor, and conductive helix circle winding is arranged at the both sides of perforate.
3. the implantable microgenerator of angiokinetic self-sustaining that utilizes according to claim 2 is characterized in that, described conductive helix circle winding wire wide region is 10nm-10 μ m.
4. the implantable microgenerator of angiokinetic self-sustaining that utilizes according to claim 1 is characterized in that described rotor is the movable film that comprises closing coil, and the position of the both sides counter electrode of rotor is provided with the contact.
5. according to claim 1, the 2 or 4 described implantable microgenerators of angiokinetic self-sustaining that utilize, it is characterized in that described rotor does not contact with perforate.
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| Application Number | Priority Date | Filing Date | Title |
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| CN2011100554348A CN102148561A (en) | 2011-03-08 | 2011-03-08 | Self-holding type implantable miniature generator using vasomotion |
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Cited By (2)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| CN104739427A (en) * | 2013-12-26 | 2015-07-01 | 中国人民解放军第二军医大学 | Implantable biological energy blood glucose monitor |
| WO2023236532A1 (en) * | 2022-06-08 | 2023-12-14 | 深圳清华大学研究院 | Micro power generation apparatus based on blood vessel pulsation, and implantable micro device |
Citations (5)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| CN1294772A (en) * | 1999-02-20 | 2001-05-09 | Em百思特株式会社 | Film coil and mfg. method for motors and generators |
| US20040073267A1 (en) * | 2002-10-09 | 2004-04-15 | Asher Holzer | Micro-generator implant |
| US20070167988A1 (en) * | 2006-01-13 | 2007-07-19 | Cernasov Andre N | Apparatus and method for supplying power to subcutaneously implanted devices |
| CN101454963A (en) * | 2006-03-17 | 2009-06-10 | 耐力节奏股份有限公司 | Energy generating systems for implanted medical devices |
| CN101918078A (en) * | 2007-04-17 | 2010-12-15 | 佩尔皮图姆有限公司 | The energy collecting device that is used to the equipment of implanting |
-
2011
- 2011-03-08 CN CN2011100554348A patent/CN102148561A/en active Pending
Patent Citations (5)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| CN1294772A (en) * | 1999-02-20 | 2001-05-09 | Em百思特株式会社 | Film coil and mfg. method for motors and generators |
| US20040073267A1 (en) * | 2002-10-09 | 2004-04-15 | Asher Holzer | Micro-generator implant |
| US20070167988A1 (en) * | 2006-01-13 | 2007-07-19 | Cernasov Andre N | Apparatus and method for supplying power to subcutaneously implanted devices |
| CN101454963A (en) * | 2006-03-17 | 2009-06-10 | 耐力节奏股份有限公司 | Energy generating systems for implanted medical devices |
| CN101918078A (en) * | 2007-04-17 | 2010-12-15 | 佩尔皮图姆有限公司 | The energy collecting device that is used to the equipment of implanting |
Cited By (2)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| CN104739427A (en) * | 2013-12-26 | 2015-07-01 | 中国人民解放军第二军医大学 | Implantable biological energy blood glucose monitor |
| WO2023236532A1 (en) * | 2022-06-08 | 2023-12-14 | 深圳清华大学研究院 | Micro power generation apparatus based on blood vessel pulsation, and implantable micro device |
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Application publication date: 20110810 |