WO2009100981A1 - Charging device having homogeneous magnetic field - Google Patents
Charging device having homogeneous magnetic field Download PDFInfo
- Publication number
- WO2009100981A1 WO2009100981A1 PCT/EP2009/050884 EP2009050884W WO2009100981A1 WO 2009100981 A1 WO2009100981 A1 WO 2009100981A1 EP 2009050884 W EP2009050884 W EP 2009050884W WO 2009100981 A1 WO2009100981 A1 WO 2009100981A1
- Authority
- WO
- WIPO (PCT)
- Prior art keywords
- magnetic
- coil
- magnetic element
- air gap
- hearing
- Prior art date
- Legal status (The legal status is an assumption and is not a legal conclusion. Google has not performed a legal analysis and makes no representation as to the accuracy of the status listed.)
- Ceased
Links
Classifications
-
- H—ELECTRICITY
- H04—ELECTRIC COMMUNICATION TECHNIQUE
- H04R—LOUDSPEAKERS, MICROPHONES, GRAMOPHONE PICK-UPS OR LIKE ACOUSTIC ELECTROMECHANICAL TRANSDUCERS; DEAF-AID SETS; PUBLIC ADDRESS SYSTEMS
- H04R25/00—Deaf-aid sets, i.e. electro-acoustic or electro-mechanical hearing aids; Electric tinnitus maskers providing an auditory perception
- H04R25/55—Deaf-aid sets, i.e. electro-acoustic or electro-mechanical hearing aids; Electric tinnitus maskers providing an auditory perception using an external connection, either wireless or wired
-
- H—ELECTRICITY
- H02—GENERATION; CONVERSION OR DISTRIBUTION OF ELECTRIC POWER
- H02J—CIRCUIT ARRANGEMENTS OR SYSTEMS FOR SUPPLYING OR DISTRIBUTING ELECTRIC POWER; SYSTEMS FOR STORING ELECTRIC ENERGY
- H02J50/00—Circuit arrangements or systems for wireless supply or distribution of electric power
- H02J50/10—Circuit arrangements or systems for wireless supply or distribution of electric power using inductive coupling
-
- H—ELECTRICITY
- H04—ELECTRIC COMMUNICATION TECHNIQUE
- H04R—LOUDSPEAKERS, MICROPHONES, GRAMOPHONE PICK-UPS OR LIKE ACOUSTIC ELECTROMECHANICAL TRANSDUCERS; DEAF-AID SETS; PUBLIC ADDRESS SYSTEMS
- H04R2225/00—Details of deaf aids covered by H04R25/00, not provided for in any of its subgroups
- H04R2225/31—Aspects of the use of accumulators in hearing aids, e.g. rechargeable batteries or fuel cells
-
- H—ELECTRICITY
- H04—ELECTRIC COMMUNICATION TECHNIQUE
- H04R—LOUDSPEAKERS, MICROPHONES, GRAMOPHONE PICK-UPS OR LIKE ACOUSTIC ELECTROMECHANICAL TRANSDUCERS; DEAF-AID SETS; PUBLIC ADDRESS SYSTEMS
- H04R2460/00—Details of hearing devices, i.e. of ear- or headphones covered by H04R1/10 or H04R5/033 but not provided for in any of their subgroups, or of hearing aids covered by H04R25/00 but not provided for in any of its subgroups
- H04R2460/17—Hearing device specific tools used for storing or handling hearing devices or parts thereof, e.g. placement in the ear, replacement of cerumen barriers, repair, cleaning hearing devices
Definitions
- the present invention relates to a charger for a
- Hearing device for inductive charging with a magnetic element having a specific passage area for magnetic flux is understood here to mean any sound-emitting device which can be worn in or on the ear, in particular a hearing device, a headset, headphones and the like.
- Hearing aids are portable hearing aids that are used to care for the hearing impaired.
- different types of hearing aids such as behind-the-ear hearing aids (BTE), hearing aid with external receiver (RIC: receiver in the canal) and in-the-ear hearing aids (ITE), e.g. Concha hearing aids or canal hearing aids (ITE, CIC).
- BTE behind-the-ear hearing aids
- RIC hearing aid with external receiver
- ITE in-the-ear hearing aids
- ITE in-the-ear hearing aids
- ITE in-the-ear hearing aids
- ITE concha hearing aids or canal hearing aids
- the hearing aids listed by way of example are worn on the outer ear or in the ear canal.
- bone conduction hearing aids, implantable or vibrotactile hearing aids are also available on the market. The stimulation of the damaged hearing takes place either mechanically or electrically.
- Hearing aids have in principle as essential components an input transducer, an amplifier and an output transducer.
- the input transducer is usually a sound receiver, z. As a microphone, and / or an electromagnetic receiver, for. B. an induction coil.
- the output transducer is usually used as an electroacoustic transducer, z. As miniature speaker, or as an electromechanical transducer, z. B. bone conduction, realized.
- the amplifier is usually integrated in a signal processing unit. This basic structure is shown in FIG. 1 using the example of a behind-the-ear hearing device. In a hearing aid housing 1 for carrying behind the ear, one or more microphones 2 for receiving the sound from the environment are installed.
- a signal Processing unit 3 which is also integrated into the hearing aid housing 1, processes the microphone signals and amplifies them.
- the output signal of the signal processing unit 3 is transmitted to a loudspeaker or earpiece 4, which outputs an acoustic signal.
- the sound is optionally transmitted via a sound tube, which is fixed with an earmold in the ear canal, to the eardrum of the device carrier.
- the power supply of the hearing device and in particular the signal processing unit 3 is effected by a likewise integrated into the hearing aid housing 1 battery. 5
- hearing aids are equipped with rechargeable batteries, electrical energy must be supplied to them at regular intervals.
- the supply of electrical energy via galvani- see contacts is often considered negative, as the
- the inductive charging methods are disadvantaged in terms of effectiveness of the wired charging systems in principle. This results from the magnetic coupling between primary and secondary coil, which is not equal to one, that is not ideal. The reason for this is the so-called stray field, namely the field lines that are generated by the primary coil, but do not penetrate the surface of the secondary coil. In addition to reduced efficiency, stray fields also lead to increased electromagnetic radiation from the charger.
- it has hitherto been proposed to maximize the coupling between the primary and the secondary coil by means of a suitable geometric arrangement. So z. For example, in most electric toothbrushes, the primary coil is placed within the secondary coil in the same plane. This ensures that all field lines cross the secondary coil.
- Other chargers with planar coils use ferrite cores that guide magnetic lines and minimize stray fields.
- the object of the present invention is therefore to provide a charger for hearing devices, which ensures an increased charging efficiency.
- a charger for a hearing device having a first magnetic element having a first passage surface for magnetic flux, and comprising a second magnetic element having a second passage surface for the magnetic flux, and an air gap between the two passage surfaces of the magnetic flux is penetrated, and in which a secondary coil of the hearing device is insertable.
- the magnetic flux in the air gap and thus in the secondary coil or charging coil of a hearing device can be concentrated by the two magnetic elements, so that the degree of coupling of the inductive coupling between the charger and the hearing device increases.
- the first magnetic element and the second magnetic element may each be an electrical coil.
- both coils can be arranged to form a heat recovery coil.
- a homogeneous magnetic field can be generated in a relatively large volume.
- the first magnetic element and the second magnetic element may each be one end of a ferromagnetic core of a magnetic circuit with an air gap. If then the faces of two core sections spaced by the air gap are close to each other, results in the air gap, a magnetic field of high strength.
- an excitation with a primary coil, through which the ferromagnetic core passes, is sufficient.
- Such an arrangement has the advantage that hardly stray fields arise and thus the electromagnetic radiation from the charger is minimal.
- the two passage surfaces are the same size and arranged so that they are parallel and their distance is smaller than the square root of the size of one of the two passage surfaces. This results in an intense, almost homogeneous magnetic field between the two magnetic elements or coils.
- FIG. 1 is a schematic diagram of the essential components of a hearing aid
- FIG 3 shows the coil arrangement of a charger according to a first embodiment of the present invention
- FIG. 4 shows the generation of a homogeneous magnetic field in a charger according to a second embodiment of the present invention.
- FIG 2 a primary coil 10 is shown, which generates a magnetic field in a known manner.
- the magnetic field at the selected time has the structure and direction indicated by the field lines.
- a corresponding alternating magnetic field In order to induce a current in a secondary coil 11, a corresponding alternating magnetic field must be generated.
- the magnetic field then alternately has the drawn direction and the corresponding opposite direction. The strength of the magnetic field and thus the density of the magnetic field lines does not change during this change of direction.
- the secondary coil 11 For charging an accumulator connected to the secondary coil 11, the secondary coil 11 is brought as close as possible and coaxially to the primary coil 10.
- the magnetic field has already decreased significantly compared to the center of the primary coil 10.
- a stray field arises in the area 12 a stray field that provides no contribution to the charging process.
- the degree of coupling between primary coil 10 and secondary coil 11 and thus the charging efficiency of a charger with a corresponding coil arrangement is correspondingly low.
- a coil arrangement according to FIG. 3 is proposed for a charging device of a hearing device.
- the primary coil is here replaced by an arrangement of two or more coils 13, 14, which are arranged coaxially to each other. They can each be designed as planar coils and have in their interior a passage area through which the generated magnetic field passes.
- the passage areas of the two coils 13 and 14 are the same size.
- the two coils 13 and 14 are arranged here as a Helmholtz coil. Ie. the width of the air gap between the coils 13 and 14, ie their distance corresponds to their radius. If necessary, their distance is also smaller than the square root of the passage area of a coil.
- FIG. 4 shows an alternative embodiment of the magnetic components of a charger according to the invention.
- the magnetic components essentially consist of a ferromagnetic core 16 and a primary coil 17 applied thereto.
- the annular core has an air gap 18.
- the secondary coil 11 of the hearing device or of the hearing device can be inserted in it.
- the one end face of the toroidal core in the air gap 18 or the end portion 19 of the core 16 the first magnetic element with the first passage area and the other end face of the annular core in the air gap 18 and the local end portion 20 of the core 16, the second magnetic element with the second passage area.
- the two passage areas are chosen to be the same size here.
- the width of the air gap 18 should be smaller than the square root of the passage area of the ferromagnetic core 16.
Landscapes
- Engineering & Computer Science (AREA)
- Computer Networks & Wireless Communication (AREA)
- Health & Medical Sciences (AREA)
- General Health & Medical Sciences (AREA)
- Neurosurgery (AREA)
- Otolaryngology (AREA)
- Physics & Mathematics (AREA)
- Acoustics & Sound (AREA)
- Signal Processing (AREA)
- Power Engineering (AREA)
- Charge And Discharge Circuits For Batteries Or The Like (AREA)
Abstract
Description
Beschreibungdescription
Ladegerät mit homogenem MagnetfeldCharger with homogeneous magnetic field
Die vorliegende Erfindung betrifft ein Ladegerät für eineThe present invention relates to a charger for a
Hörvorrichtung zum induktiven Laden mit einem Magnetelement, das eine bestimmte Durchtrittsfläche für magnetischen Fluss aufweist. Unter dem Begriff Hörvorrichtung wird hier jedes im oder am Ohr tragbare, schallausgebende Gerät, insbesondere ein Hörgerät, ein Headset, Kopfhörer und dergleichen verstanden .Hearing device for inductive charging with a magnetic element having a specific passage area for magnetic flux. The term hearing device is understood here to mean any sound-emitting device which can be worn in or on the ear, in particular a hearing device, a headset, headphones and the like.
Hörgeräte sind tragbare Hörvorrichtungen, die zur Versorgung von Schwerhörenden dienen. Um den zahlreichen individuellen Bedürfnissen entgegenzukommen, werden unterschiedliche Bauformen von Hörgeräten wie Hinter-dem-Ohr-Hörgeräte (HdO) , Hörgerät mit externem Hörer (RIC: receiver in the canal) und In-dem-Ohr-Hörgeräte (IdO), z.B. auch Concha-Hörgeräte oder Kanal-Hörgeräte (ITE, CIC), bereitgestellt. Die beispielhaft aufgeführten Hörgeräte werden am Außenohr oder im Gehörgang getragen. Darüber hinaus stehen auf dem Markt aber auch Knochenleitungshörhilfen, implantierbare oder vibrotaktile Hörhilfen zur Verfügung. Dabei erfolgt die Stimulation des geschädigten Gehörs entweder mechanisch oder elektrisch.Hearing aids are portable hearing aids that are used to care for the hearing impaired. In order to meet the numerous individual needs, different types of hearing aids such as behind-the-ear hearing aids (BTE), hearing aid with external receiver (RIC: receiver in the canal) and in-the-ear hearing aids (ITE), e.g. Concha hearing aids or canal hearing aids (ITE, CIC). The hearing aids listed by way of example are worn on the outer ear or in the ear canal. In addition, bone conduction hearing aids, implantable or vibrotactile hearing aids are also available on the market. The stimulation of the damaged hearing takes place either mechanically or electrically.
Hörgeräte besitzen prinzipiell als wesentliche Komponenten einen Eingangswandler, einen Verstärker und einen Ausgangswandler. Der Eingangswandler ist in der Regel ein Schallempfänger, z. B. ein Mikrofon, und/oder ein elektromagnetischer Empfänger, z. B. eine Induktionsspule. Der Ausgangswandler ist meist als elektroakustischer Wandler, z. B. Miniaturlautsprecher, oder als elektromechanischer Wandler, z. B. Knochenleitungshörer, realisiert. Der Verstärker ist üblicherweise in eine Signalverarbeitungseinheit integriert. Dieser prinzipielle Aufbau ist in FIG 1 am Beispiel eines Hinter- dem-Ohr-Hörgeräts dargestellt. In ein Hörgerätegehäuse 1 zum Tragen hinter dem Ohr sind ein oder mehrere Mikrofone 2 zur Aufnahme des Schalls aus der Umgebung eingebaut. Eine Signal- Verarbeitungseinheit 3, die ebenfalls in das Hörgerätegehäuse 1 integriert ist, verarbeitet die Mikrofonsignale und verstärkt sie. Das Ausgangssignal der Signalverarbeitungseinheit 3 wird an einen Lautsprecher bzw. Hörer 4 übertragen, der ein akustisches Signal ausgibt. Der Schall wird gegebenenfalls über einen Schallschlauch, der mit einer Otoplastik im Gehörgang fixiert ist, zum Trommelfell des Geräteträgers übertragen. Die Energieversorgung des Hörgeräts und insbesondere die der Signalverarbeitungseinheit 3 erfolgt durch eine ebenfalls ins Hörgerätegehäuse 1 integrierte Batterie 5.Hearing aids have in principle as essential components an input transducer, an amplifier and an output transducer. The input transducer is usually a sound receiver, z. As a microphone, and / or an electromagnetic receiver, for. B. an induction coil. The output transducer is usually used as an electroacoustic transducer, z. As miniature speaker, or as an electromechanical transducer, z. B. bone conduction, realized. The amplifier is usually integrated in a signal processing unit. This basic structure is shown in FIG. 1 using the example of a behind-the-ear hearing device. In a hearing aid housing 1 for carrying behind the ear, one or more microphones 2 for receiving the sound from the environment are installed. A signal Processing unit 3, which is also integrated into the hearing aid housing 1, processes the microphone signals and amplifies them. The output signal of the signal processing unit 3 is transmitted to a loudspeaker or earpiece 4, which outputs an acoustic signal. The sound is optionally transmitted via a sound tube, which is fixed with an earmold in the ear canal, to the eardrum of the device carrier. The power supply of the hearing device and in particular the signal processing unit 3 is effected by a likewise integrated into the hearing aid housing 1 battery. 5
Werden Hörgeräte mit wiederaufladbaren Akkumulatoren versehen, so ist ihnen in regelmäßigen Abständen elektrische Energie zuzuführen. Die Zufuhr elektrischer Energie über galvani- sehe Kontakte wird vielfach als negativ angesehen, da dieIf hearing aids are equipped with rechargeable batteries, electrical energy must be supplied to them at regular intervals. The supply of electrical energy via galvani- see contacts is often considered negative, as the
Kontakte am Hörgerät entweder von außen leicht zugänglich und meist nicht potentialfrei sind oder aufwändig geschützt werden müssen. Daher werden als Alternative vielfach induktive Ladeverfahren angeboten.Contacts on the hearing aid either from the outside easily accessible and usually not floating or expensive to protect. Therefore, inductive charging methods are often offered as an alternative.
Die induktiven Ladeverfahren sind bezüglich Effektivität den drahtgebundenen Ladesystemen gegenüber prinzipbedingt benachteiligt. Dies ergibt sich aus der magnetischen Kopplung zwischen Primär- und Sekundärspule, die ungleich eins, d. h. nicht ideal ist. Der Grund hierfür ist das so genannte Streufeld, nämlich die Feldlinien, die von der Primärspule erzeugt werden, die Fläche der Sekundärspule aber nicht durchdringen. Neben verringerter Effektivität führen Streufelder auch zu einer erhöhten elektromagnetischen Abstrahlung aus dem Lade- gerät. Um den Wirkungsgrad induktiver Ladeverfahren zu erhöhen, wurde bislang vorgeschlagen, die Kopplung zwischen der Primär- und der Sekundärspule durch geeignete geometrische Anordnung zu maximieren. So ist z. B. bei den meisten elektrischen Zahnbürsten die Primärspule innerhalb der Sekundär- spule in der gleichen Ebene platziert. Damit ist gewährleistet, dass alle Feldlinien die Sekundärspule kreuzen. Bei anderen Ladegeräten mit Planarspulen werden Ferritkerne verwendet, die Magnetlinien führen und Streufelder minimieren. Die Aufgabe der vorliegenden Erfindung besteht somit darin, ein Ladegerät für Hörvorrichtungen bereitzustellen, das einen erhöhten Ladewirkungsgrad gewährleistet.The inductive charging methods are disadvantaged in terms of effectiveness of the wired charging systems in principle. This results from the magnetic coupling between primary and secondary coil, which is not equal to one, that is not ideal. The reason for this is the so-called stray field, namely the field lines that are generated by the primary coil, but do not penetrate the surface of the secondary coil. In addition to reduced efficiency, stray fields also lead to increased electromagnetic radiation from the charger. In order to increase the efficiency of inductive charging methods, it has hitherto been proposed to maximize the coupling between the primary and the secondary coil by means of a suitable geometric arrangement. So z. For example, in most electric toothbrushes, the primary coil is placed within the secondary coil in the same plane. This ensures that all field lines cross the secondary coil. Other chargers with planar coils use ferrite cores that guide magnetic lines and minimize stray fields. The object of the present invention is therefore to provide a charger for hearing devices, which ensures an increased charging efficiency.
Erfindungsgemäß wird diese Aufgabe gelöst durch ein Ladegerät für eine Hörvorrichtung mit einem ersten Magnetelement, das eine erste Durchtrittsfläche für magnetischen Fluss aufweist, sowie umfassend ein zweites Magnetelement das eine zweite Durchtrittsfläche für den magnetischen Fluss aufweist, und einen Luftspalt zwischen den beiden Durchtrittsflächen, der von dem magnetischen Fluss durchdrungen wird, und in den eine Sekundärspule der Hörvorrichtung einführbar ist.According to the invention, this object is achieved by a charger for a hearing device having a first magnetic element having a first passage surface for magnetic flux, and comprising a second magnetic element having a second passage surface for the magnetic flux, and an air gap between the two passage surfaces of the magnetic flux is penetrated, and in which a secondary coil of the hearing device is insertable.
Günstigerweise kann durch die beiden Magnetelemente der magnetische Fluss im Luftspalt und damit in der Sekundärspule bzw. Ladespule einer Hörvorrichtung konzentriert werden, so dass der Kopplungsgrad der induktiven Kopplung zwischen Ladegerät und Hörvorrichtung steigt.Conveniently, the magnetic flux in the air gap and thus in the secondary coil or charging coil of a hearing device can be concentrated by the two magnetic elements, so that the degree of coupling of the inductive coupling between the charger and the hearing device increases.
In einer speziellen Ausführungsform können das erste Magnetelement und das zweite Magnetelement jeweils eine elektrische Spule sein. Insbesondere können beide Spulen zu einer HeIm- holtz-Spule angeordnet sein. Hierdurch lässt sich in einem verhältnismäßig großen Volumen ein homogenes Magnetfeld erzeugen .In a specific embodiment, the first magnetic element and the second magnetic element may each be an electrical coil. In particular, both coils can be arranged to form a heat recovery coil. As a result, a homogeneous magnetic field can be generated in a relatively large volume.
Unter Umständen ist es günstig, die beiden Spulen mit mindestens noch einer weiteren Spule zu koppeln, so dass die Stärke des Felds und damit auch der Ladewirkungsgrad verbessert wird.Under certain circumstances, it is advantageous to couple the two coils with at least one further coil, so that the strength of the field and thus also the charging efficiency is improved.
Entsprechend einer alternativen Ausführungsform kann das erste Magnetelement und das zweite Magnetelement jeweils ein En- de eines ferromagnetischen Kerns eines magnetischen Kreises mit Luftspalt sein. Wenn sich dann die Stirnflächen zweier Kernabschnitte beabstandet durch den Luftspalt nahe gegenüber stehen, ergibt sich im Luftspalt ein Magnetfeld hoher Stärke. Bei Verwendung eines ringförmigen Kerns, der lediglich durch den Luftspalt unterbrochen ist, genügt eine Erregung mit einer Primärspule, durch die der ferromagnetische Kern hin- durchläuft. Eine derartige Anordnung hat den Vorteil, dass kaum Streufelder entstehen und somit die elektromagnetische Abstrahlung aus dem Ladegerät minimal ist.According to an alternative embodiment, the first magnetic element and the second magnetic element may each be one end of a ferromagnetic core of a magnetic circuit with an air gap. If then the faces of two core sections spaced by the air gap are close to each other, results in the air gap, a magnetic field of high strength. When using an annular core which is interrupted only by the air gap, an excitation with a primary coil, through which the ferromagnetic core passes, is sufficient. Such an arrangement has the advantage that hardly stray fields arise and thus the electromagnetic radiation from the charger is minimal.
Vorzugsweise sind die beiden Durchtrittsflächen gleich groß und so angeordnet, dass sie parallel sind und ihr Abstand kleiner als die Quadratwurzel der Größe eines der beiden Durchtrittsflächen ist. Hierdurch ergibt sich zwischen beiden Magnetelementen bzw. Spulen ein intensives annähernd homogenes Magnetfeld.Preferably, the two passage surfaces are the same size and arranged so that they are parallel and their distance is smaller than the square root of the size of one of the two passage surfaces. This results in an intense, almost homogeneous magnetic field between the two magnetic elements or coils.
Die vorliegende Erfindung wird nun anhand der beigefügten Zeichnungen näher erläutert, in denn zeigen:The present invention will now be explained in more detail with reference to the accompanying drawings, in which:
FIG 1 eine Prinzipskizze der wesentlichen Komponenten ei- nes Hörgeräts;1 is a schematic diagram of the essential components of a hearing aid;
FIG 2 eine Spulenanordnung zum induktiven Laden gemäß dem Stand der Technik;2 shows a coil arrangement for inductive charging according to the prior art;
FIG 3 die Spulenanordnung eines Ladegeräts gemäß einer ersten Ausführungsform der vorliegenden Erfindung und3 shows the coil arrangement of a charger according to a first embodiment of the present invention and
FIG 4 die Erzeugung eines homogenen Magnetfelds in einem Ladegerät gemäß einer zweiten Ausführungsform der vorliegenden Erfindung.4 shows the generation of a homogeneous magnetic field in a charger according to a second embodiment of the present invention.
Die nachfolgend näher geschilderten Ausführungsbeispiele stellen bevorzugte Ausführungsformen der vorliegenden Erfin- düng dar. Zunächst sei jedoch anhand von FIG 2 zum besserenThe exemplary embodiments described in more detail below represent preferred embodiments of the present invention. First, however, with reference to FIG. 2 for the better
Verständnis der Erfindung erläutert, wie ein übliches Ladegerät zum induktiven Laden eines Hörgeräts aufgebaut ist. In FIG 2 ist eine Primärspule 10 wiedergegeben, die in bekannter Weise ein Magnetfeld erzeugt. In dem vorliegenden Beispiel hat das Magnetfeld zu dem gewählten Zeitpunkt die mit den Feldlinien angedeutete Struktur und Richtung. Um in einer Sekundärspule 11 einen Strom zu induzieren, muss ein entsprechendes Wechselmagnetfeld erzeugt werden. Das Magnetfeld hat dann abwechselnd die eingezeichnete Richtung und die entsprechende Gegenrichtung. Die Stärke des Magnetfelds und damit die Dichte der Magnetfeldlinien ändert sich bei diesem Richtungswechsel jedoch nicht.Understanding the invention explains how a conventional charger for inductive charging a hearing aid is constructed. In FIG 2, a primary coil 10 is shown, which generates a magnetic field in a known manner. In the present example, the magnetic field at the selected time has the structure and direction indicated by the field lines. In order to induce a current in a secondary coil 11, a corresponding alternating magnetic field must be generated. The magnetic field then alternately has the drawn direction and the corresponding opposite direction. The strength of the magnetic field and thus the density of the magnetic field lines does not change during this change of direction.
Für das Laden eines an die Sekundärspule 11 angeschlossenen Akkumulators wird die Sekundärspule 11 möglichst nahe und koaxial an die Primärspule 10 gebracht. In FIG 2 ist jedoch zu erkennen, dass am Ort der Sekundärspule 11 das Magnetfeld bereits deutlich abgenommen hat gegenüber dem Zentrum der Primärspule 10. Außerdem entsteht im Bereich 12 ein Streufeld, das keinen Beitrag zum Ladevorgang liefert. Der Kopplungsgrad zwischen Primärspule 10 und Sekundärspule 11 und damit der Ladewirkungsgrad eines Ladegeräts mit entsprechender Spulenanordnung ist entsprechend gering.For charging an accumulator connected to the secondary coil 11, the secondary coil 11 is brought as close as possible and coaxially to the primary coil 10. In Figure 2, however, it can be seen that at the location of the secondary coil 11, the magnetic field has already decreased significantly compared to the center of the primary coil 10. In addition, arises in the area 12 a stray field that provides no contribution to the charging process. The degree of coupling between primary coil 10 and secondary coil 11 and thus the charging efficiency of a charger with a corresponding coil arrangement is correspondingly low.
Aus diesem Grund wird gemäß der vorliegenden Erfindung eine Spulenanordnung entsprechend FIG 3 für ein Ladegerät einer Hörvorrichtung vorgeschlagen. Die Primärspule ist hier durch eine Anordnung aus zwei oder mehr Spulen 13, 14 ersetzt, die zueinander koaxial angeordnet sind. Sie können jeweils als Planarspulen ausgebildet sein und besitzen in ihrem Inneren eine Durchtrittsfläche, durch die das erzeugte Magnetfeld hindurchtritt. Im vorliegenden Fall sind die Durchtrittsflächen der beiden Spulen 13 und 14 gleich groß. Außerdem sind die beiden Spulen 13 und 14 hier als Helmholtz-Spule angeordnet. D. h. die Breite des Luftspalts zwischen den Spulen 13 und 14, d. h. ihr Abstand, entspricht ihrem Radius. Gegebe- nenfalls ist ihr Abstand auch kleiner als die Quadratwurzel der Durchtrittsfläche einer Spule. Folglich ergibt sich zwischen beiden Spulen 13 und 14 ein näherungsweise homogenes magnetisches Feld. Wird die Sekundärspule 11 des Hörgeräts in den Luftspalt 15 zwischen den beiden Helmholtz-Spulen 13, 14 platziert, gehen mehr Feldlinien durch die Sekundärspule 11 als im Fall von nur einer einzigen Primärspule 10 (vergleiche FIG 2) . Der magnetische Fluss durch die Sekundärspule 11 ist somit erhöht, weshalb in der Sekundärspule auch ein höherer elektrischer Strom induziert wird.For this reason, according to the present invention, a coil arrangement according to FIG. 3 is proposed for a charging device of a hearing device. The primary coil is here replaced by an arrangement of two or more coils 13, 14, which are arranged coaxially to each other. They can each be designed as planar coils and have in their interior a passage area through which the generated magnetic field passes. In the present case, the passage areas of the two coils 13 and 14 are the same size. In addition, the two coils 13 and 14 are arranged here as a Helmholtz coil. Ie. the width of the air gap between the coils 13 and 14, ie their distance corresponds to their radius. If necessary, their distance is also smaller than the square root of the passage area of a coil. Consequently, an approximately homogeneous magnetic field results between the two coils 13 and 14. If the secondary coil 11 of the hearing aid in Placed the air gap 15 between the two Helmholtz coils 13, 14, go more field lines through the secondary coil 11 than in the case of only a single primary coil 10 (see FIG 2). The magnetic flux through the secondary coil 11 is thus increased, which is why a higher electric current is induced in the secondary coil.
In FIG 4 ist eine alternative Ausführungsform der magnetischen Komponenten eines erfindungsgemäßen Ladegeräts darge- stellt. Die magnetischen Komponenten bestehen im Wesentlichen aus einem ferromagnetischen Kern 16 und einer darauf aufgebrachten Primärspule 17. Außerdem weist der ringförmige Kern einen Luftspalt 18 auf. In ihn lässt sich die Sekundärspule 11 der Hörvorrichtung bzw. des Hörgeräts einführen. In diesem Fall stellt die eine Stirnseite des Ringkerns im Luftspalt 18 bzw. der dortige Endabschnitt 19 des Kerns 16 das erste Magnetelement mit der ersten Durchtrittsfläche und die andere Stirnseite des ringförmigen Kerns im Luftspalt 18 bzw. der dortige Endabschnitt 20 des Kerns 16 das zweite Magnetelement mit der zweiten Durchtrittsfläche dar. Die beiden Durchtrittsflächen sind hier gleich groß gewählt. Die Breite des Luftspalts 18 sollte kleiner sein als die Quadratwurzel aus der Durchtrittsfläche des ferromagnetischen Kerns 16. In diesem Luftspalt 18 würden dann sehr konzentrierte, näherungs- weise homogene Magnetfelder herrschen. Wird nun wiederum die Sekundärspule 11 in dem Spalt 18 platziert, wird der Streufeldanteil viel geringer sein als im Falle einer Primärspule ohne einen derartigen Kern 16. Diese Anordnung ist besonders für sehr kleine Geräte, wie Hörgeräte, vorteilhaft, weil für das Einführen der Sekundärspule nur ein relativ enger Spalt 18 zur Verfügung steht.FIG. 4 shows an alternative embodiment of the magnetic components of a charger according to the invention. The magnetic components essentially consist of a ferromagnetic core 16 and a primary coil 17 applied thereto. In addition, the annular core has an air gap 18. The secondary coil 11 of the hearing device or of the hearing device can be inserted in it. In this case, the one end face of the toroidal core in the air gap 18 or the end portion 19 of the core 16, the first magnetic element with the first passage area and the other end face of the annular core in the air gap 18 and the local end portion 20 of the core 16, the second magnetic element with the second passage area. The two passage areas are chosen to be the same size here. The width of the air gap 18 should be smaller than the square root of the passage area of the ferromagnetic core 16. In this air gap 18 would then very concentrated, approximately homogeneous magnetic fields prevail. If, in turn, the secondary coil 11 is placed in the gap 18, the stray field component will be much lower than in the case of a primary coil without such a core 16. This arrangement is particularly advantageous for very small devices, such as hearing aids, because only for the insertion of the secondary coil a relatively narrow gap 18 is available.
Mit den oben dargestellten magnetischen Anordnungen können deutlich effizientere Energieübertragungssysteme aufgebaut werden. Insbesondere durch die Anordnung gemäß FIG 4 kann auch die elektromagnetische Abstrahlung minimiert werden. With the above-described magnetic arrangements, significantly more efficient power transmission systems can be constructed. In particular, by the arrangement of FIG 4, the electromagnetic radiation can be minimized.
Claims
Applications Claiming Priority (4)
| Application Number | Priority Date | Filing Date | Title |
|---|---|---|---|
| US2821408P | 2008-02-13 | 2008-02-13 | |
| DE102008008899A DE102008008899A1 (en) | 2008-02-13 | 2008-02-13 | Charger with homogeneous magnetic field |
| US61/028,214 | 2008-02-13 | ||
| DE102008008899.4 | 2008-02-13 |
Publications (1)
| Publication Number | Publication Date |
|---|---|
| WO2009100981A1 true WO2009100981A1 (en) | 2009-08-20 |
Family
ID=40896450
Family Applications (1)
| Application Number | Title | Priority Date | Filing Date |
|---|---|---|---|
| PCT/EP2009/050884 Ceased WO2009100981A1 (en) | 2008-02-13 | 2009-01-27 | Charging device having homogeneous magnetic field |
Country Status (2)
| Country | Link |
|---|---|
| DE (1) | DE102008008899A1 (en) |
| WO (1) | WO2009100981A1 (en) |
Cited By (6)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| EP2375534A1 (en) * | 2010-04-09 | 2011-10-12 | Nxp B.V. | Apparatus for transferring energy to an accumulator and system for charging an electric accumulator |
| WO2014008317A1 (en) * | 2012-07-02 | 2014-01-09 | Resonate Industries, Inc. | Miniature low-power remote battery charging systems and methods |
| CN104009511A (en) * | 2013-02-22 | 2014-08-27 | 西门子公司 | Wireless charging system for hearing instruments |
| US9132276B2 (en) | 2010-12-10 | 2015-09-15 | Cochlear Limited | Portable power charging of implantable medical devices |
| CN110474383A (en) * | 2018-05-09 | 2019-11-19 | 奥迪康有限公司 | Charger antenna unit, charger device and device to be charged |
| EP3796441A1 (en) | 2019-09-18 | 2021-03-24 | Sivantos Pte. Ltd. | Battery charger for charging a wearable audio device |
Families Citing this family (2)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| DE102009056719A1 (en) * | 2009-12-02 | 2011-06-09 | Siemens Medical Instruments Pte. Ltd. | Hearing aid battery charging arrangement, has battery charging unit with transmitting coil inductively radiating magnetic energy, where coil is arranged at ear of bearer such that radiated energy is received by receiving coil of hearing aid |
| DE102014201118A1 (en) * | 2014-01-22 | 2015-07-23 | Siemens Aktiengesellschaft | Dual antenna system for charging one or more hearing aids |
Citations (3)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| WO1989005530A1 (en) * | 1987-12-10 | 1989-06-15 | Uniscan Ltd. | Antenna structure for providing a uniform field |
| US6661197B2 (en) * | 2001-02-22 | 2003-12-09 | Uwe Zink | Wireless battery charging system for existing hearing aids using a dynamic battery and a charging processor unit |
| US7211986B1 (en) * | 2004-07-01 | 2007-05-01 | Plantronics, Inc. | Inductive charging system |
Family Cites Families (2)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| DE1116305B (en) * | 1959-07-29 | 1961-11-02 | Schmidt Geb Metallwarenfab | Charger and rechargeable small electrical device with inductive coupling |
| WO2008095530A1 (en) | 2007-02-05 | 2008-08-14 | Continental Automotive Gmbh | Control module and method for operating a motor vehicle |
-
2008
- 2008-02-13 DE DE102008008899A patent/DE102008008899A1/en not_active Withdrawn
-
2009
- 2009-01-27 WO PCT/EP2009/050884 patent/WO2009100981A1/en not_active Ceased
Patent Citations (3)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| WO1989005530A1 (en) * | 1987-12-10 | 1989-06-15 | Uniscan Ltd. | Antenna structure for providing a uniform field |
| US6661197B2 (en) * | 2001-02-22 | 2003-12-09 | Uwe Zink | Wireless battery charging system for existing hearing aids using a dynamic battery and a charging processor unit |
| US7211986B1 (en) * | 2004-07-01 | 2007-05-01 | Plantronics, Inc. | Inductive charging system |
Cited By (16)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| US9590445B2 (en) | 2010-04-09 | 2017-03-07 | Nxp B.V. | Apparatus for transferring energy to an accumulator and system for charging an electric accumulator |
| EP2375535A1 (en) * | 2010-04-09 | 2011-10-12 | Nxp B.V. | Apparatus for transferring energy to an accumulator and system for charging an electric accumulator |
| US20110248673A1 (en) * | 2010-04-09 | 2011-10-13 | Nxp B.V. | Apparatus for transferring energy to an accumulator and system for charging an electric accumulator |
| EP2375534A1 (en) * | 2010-04-09 | 2011-10-12 | Nxp B.V. | Apparatus for transferring energy to an accumulator and system for charging an electric accumulator |
| US9597522B2 (en) | 2010-12-10 | 2017-03-21 | Cochlear Limited | Portable power charging of implantable medical devices |
| US9132276B2 (en) | 2010-12-10 | 2015-09-15 | Cochlear Limited | Portable power charging of implantable medical devices |
| WO2014008317A1 (en) * | 2012-07-02 | 2014-01-09 | Resonate Industries, Inc. | Miniature low-power remote battery charging systems and methods |
| CN104009511A (en) * | 2013-02-22 | 2014-08-27 | 西门子公司 | Wireless charging system for hearing instruments |
| US9161141B2 (en) | 2013-02-22 | 2015-10-13 | Siemens Aktiengesellschaft | Wireless charging system for hearing instruments |
| EP2770753A1 (en) * | 2013-02-22 | 2014-08-27 | Siemens Aktiengesellschaft | Wireless charging system for hearing instruments |
| US9788129B2 (en) | 2013-02-22 | 2017-10-10 | Siemens Aktiengesellschaft | Wireless charging system for hearing instruments |
| CN110474383A (en) * | 2018-05-09 | 2019-11-19 | 奥迪康有限公司 | Charger antenna unit, charger device and device to be charged |
| EP3573079A1 (en) * | 2018-05-09 | 2019-11-27 | Oticon A/s | Charger antenna unit, charger device, and device to be charged |
| US11451089B2 (en) | 2018-05-09 | 2022-09-20 | Oticon A/S | Charger antenna unit, charger device, and device to be charged |
| EP3796441A1 (en) | 2019-09-18 | 2021-03-24 | Sivantos Pte. Ltd. | Battery charger for charging a wearable audio device |
| US11637343B2 (en) | 2019-09-18 | 2023-04-25 | Sivantos Pte. Ltd. | Charger operable in different charging modes for charging an accumulator of the charger and an accumulator of an audio device |
Also Published As
| Publication number | Publication date |
|---|---|
| DE102008008899A1 (en) | 2009-08-27 |
Similar Documents
| Publication | Publication Date | Title |
|---|---|---|
| EP1962557B1 (en) | Hearing device with a special energy reception system and corresponding method | |
| DE102009007233B4 (en) | Hearing device with noise compensation and design method | |
| WO2009100981A1 (en) | Charging device having homogeneous magnetic field | |
| DE102013210689B3 (en) | Antenna device for hearing instruments | |
| DE102008015263B4 (en) | Hearing system with subband signal exchange and corresponding method | |
| DE102010021173A1 (en) | Hearing device with passive, deeply seated in the auditory canal unit | |
| EP3579336B1 (en) | Antenna and device incorporating the same | |
| EP2053876A1 (en) | Hearing device with single connection for shielding and identification of an earpiece | |
| EP2180724A1 (en) | Earpiece with bridges | |
| EP1903835A2 (en) | Hearing device with supplementary screening device | |
| DE102007007800B3 (en) | Hearing device with receiver compensation coil | |
| EP2375784B1 (en) | Hearing aid with amorphous speaker shielding | |
| EP1651006A2 (en) | Hearing aid with line loop to compensate the inductive disturbance fields | |
| EP2437258A2 (en) | Method and device for frequency compression with selective frequency shifting | |
| EP1944850A2 (en) | Charging device for a hearing aid, hearing aid and hearing aid remote control | |
| EP2091124A2 (en) | Charger for a hearing aid with a mobile charging contact and accompanying hearing aid system | |
| EP2053878B1 (en) | Hearing aid using an inductive switching regulator as a radio transmitter | |
| DE102019215843A1 (en) | Hearing instrument | |
| DE102017012195B4 (en) | Hearing aid, in particular behind-the-ear hearing aid | |
| EP3739906B1 (en) | Hearing instrument | |
| DE102007001642A1 (en) | Method for reducing interference power and corresponding acoustic system | |
| EP2552129B1 (en) | Hearing aid with special sound channel | |
| DE102006049469B4 (en) | Hearing aid with live metal strap | |
| DE102010012946B4 (en) | Hearing aid with amorphous speaker shield | |
| DE102018222016A1 (en) | Hearing aid and method for operating a hearing aid |
Legal Events
| Date | Code | Title | Description |
|---|---|---|---|
| 121 | Ep: the epo has been informed by wipo that ep was designated in this application |
Ref document number: 09709519 Country of ref document: EP Kind code of ref document: A1 |
|
| NENP | Non-entry into the national phase |
Ref country code: DE |
|
| 122 | Ep: pct application non-entry in european phase |
Ref document number: 09709519 Country of ref document: EP Kind code of ref document: A1 |