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JP2010075394

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This translation is machine-generated. It cannot be guaranteed that it is intelligible, accurate,
complete, reliable or fit for specific purposes. Critical decisions, such as commercially relevant or
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DESCRIPTION JP2010075394
An accurate implantable bone conduction hearing aid is proposed. SOLUTION: An in-vivo unit 3
embedded in a skull 4 is provided with a vibrator 34 composed of a super magnetostrictive
element, and an audible sound modulation transmission signal S1 which is amplitude-modulated
by a sound collection signal generated in the extracorporeal unit 2 By transmitting the
transmission magnetic flux 33 to the in-vivo receiving coil 32 provided in the in-vivo unit 3 from
31 and causing the vibrator 34 to extend and contract by the induced electromotive force of the
in-vivo receiving coil 32, power supply and demodulation in the in-vivo unit 3 are performed. The
audible sound signal can be guided with high accuracy without providing a circuit. [Selected
figure] Figure 4
Implantable bone conduction hearing aid
[0001]
The present invention relates to an implantable bone-conduction hearing aid, and in particular, it
is possible to sensitively conduct audible sound vibration.
[0002]
The bone conduction hearing aids have been described in Patent Documents 1 to 4 as
transmitting the audible sound vibration through the skull to the vestibular and cochlea inner
bones in the skull without passing through the narrow and complex shaped ear canal. Has been
proposed.
04-05-2019
1
Japanese Patent Application No. 9-261797 Japanese Patent No. 3174324 Japanese Patent LaidOpen No. 2004-289219 Japanese Patent Laid-Open No. 2007-184722
[0003]
On the other hand, in the practical use as a bone conduction hearing aid of this kind, first, in
order to transmit vibration to the skull from the outside of the scalp, the audible sound
transducer is transmitted through the scalp with a headband or the like. Although a thing
strongly pressed against the skull has been proposed, there is a problem that the burden on the
wearer is excessive.
[0004]
Second, there is a configuration in which the titanium bone conduction terminal is embedded in
the back of the ear and the external vibrator is attached to the titanium bone conduction
terminal, but the titanium bone conduction terminal is exposed on the back ear skin. There is a
problem that the application is limited because a large bone guiding ability of at least about 45
[dB] is required due to inconvenience and insufficient output of the external vibrator.
[0005]
The present invention has been made in consideration of the above points, and an object of the
present invention is to propose an implantable bone conduction hearing aid in which a wide band
and sufficient output audible sound vibration can be guided by the implantable body unit. .
[0006]
In order to solve such problems, in the present invention, the external magnetic transmission coil
31 generates the transmission magnetic flux 33 based on the audible sound modulation
transmission signal S1 obtained by amplitude-modulating the carrier signal S3 with the sound
collection signal S2 obtained from the microphone 11. An induced electromotive force S11 is
generated by the in-vivo receiving coil 32 embedded in the extracorporeal unit 2 and the skull 5
under the scalp 4 and intersected with the transmission magnetic flux 33 coming from the
extracorporeal unit 2, and the magnetostrictive element is generated by the induced
electromotive force S11. The in-vivo unit 3 for applying a vibration corresponding to the sound
collection signal S2 to the skull 5 as a bone conduction vibration is provided in the skull 5 by
driving the vibrator 34 to extend and contract.
[0007]
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2
According to the present invention, an in-vivo unit embedded in the skull is provided with a
transducer made of a super magnetostrictive element, and an audible sound modulation
transmission signal formed by amplitude modulation with a sound collection signal generated in
the extracorporeal unit is transmitted from the extracorporeal transmission coil to the in-vivo
unit. The transmission sound flux is transmitted to the in-vivo receiving coil provided at the same
time, and the vibrator is extended / contracted driven by the induced electromotive force of the
in-vivo receiving coil, so that the audible sound signal is high without providing a power supply
or a demodulation circuit in the in-vivo unit It can be guided with accuracy.
[0008]
An embodiment of the present invention will now be described in detail with reference to the
drawings.
[0009]
(1) Configuration of Implantable Bone Conduction Hearing Aid In FIG. 1, reference numeral 1
denotes an implantable bone conduction hearing aid, which is constituted by an extracorporeal
unit 2 and an intracorporeal unit 3.
[0010]
The extracorporeal unit 2 is embedded in the skull 5 covered by the scalp 4 and is provided with
an audible sound modulation signal transmission unit 2A provided on the scalp 4 so as to face
the intracorporeal unit 3, and the audible sound modulation signal transmission unit 2A. And a
sound collection processing unit 2B for giving an audible sound modulation transmission signal
S1.
[0011]
As shown in FIG. 2, the sound collection processing unit 2B inputs the sound collection signal S2
obtained from the microphone unit 11 to the AM modulation circuit 12, thereby collecting the
carrier wave signal S3 supplied from the carrier wave oscillation circuit 13 An audible sound
modulation signal S4 is generated by amplitude modulation (AM modulation) according to S2.
[0012]
The audible sound modulation signal S4 is amplified by the output amplification circuit 14 and
sent out to the audible sound modulation signal transmission unit 2A as the audible sound
modulation transmission signal S1.
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[0013]
The sound collection processing unit 2 B is driven by the power supply battery 15.
[0014]
The intracorporeal unit 3 (FIG. 1) is embedded in a portion close to the auricle 21 of the wearer
(for example, the temporal bone under the milk projection), whereby an extracorporeal unit
disposed at a position facing the intracorporeal unit 3 The microphone 11 of the sound collection
processing unit 2B that constitutes 2 can collect audible sound that can be heard by the wearer
of the implantable bone conduction hearing aid 1 when it originally reaches the eardrum 23
through the external ear canal 22.
[0015]
Therefore, when the wearer can hear the audible sound normally, the vibration of the tympanic
membrane 23 is transmitted to the vestibular and cochlea 28 through the ear small bone 27
composed of the tuchi bone 24, the quinuta bone 25 and the stapes bone 26, Sound information
can be sent to the brainstem from the cochlea.
[0016]
The implantable bone conduction hearing aid 1 supplies the audible sound modulation
transmission signal S1 to the audible sound modulation signal receiving unit 3A of the internal
unit 3 embedded in the skull 5 from the extracorporeal unit 2 instead of the sound transmission
through the external ear canal 22. Thus, an audible sound vibration is generated in the in-vivo
unit 3, and the audible sound vibration is transmitted to the earlobe 27 via the skull 5.
[0017]
The audible sound modulation signal transmission unit 2A of the extracorporeal unit 2 crosses
the scalp 4 and transmits the audible sound modulation transmission signal S1 to the audible
sound modulation signal reception unit 3A of the internal unit 3 as shown in FIG. Have.
[0018]
On the other hand, the in-vivo unit 3 is provided with the in-vivo reception coil 32 constituting
the audible sound modulation signal receiving unit 3A so as to face the extracorporeal
transmission coil 31 with the scalp 4 interposed therebetween. The transmission magnetic flux
33 generated when flowing through the extracorporeal transmission coil 31 passes through the
scalp 4 and intersects the in-vivo reception coil 32 to generate an electromotive force signal S11
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4
between both end terminals 32A and 32B of the in-vivo reception coil 32.
[0019]
The electromotive force signal S11 generated in the in-vivo reception coil 32 has the same
modulation signal format as the audible sound modulation signal S4 (FIG. 2) obtained in the AM
modulation circuit 12, and thereby the audible sound from the extracorporeal unit 2 to the invivo unit 3 Transmission of a signal including information is performed, and an electromotive
force signal S11 obtained between both terminals 32A and 32B of the in-vivo reception coil 32 is
applied to the excitation unit 3B which constitutes the in-vivo unit 3.
[0020]
The vibration unit 3B has a rod-shaped vibrator 34 and a vibration drive coil 35 wound around
the rod-like vibrator 34. When the electromotive force signal S11 is given to the vibration drive
coil 35, the magnetic flux generated is a rod-shaped vibrator 34. Transparent in the longitudinal
direction of
[0021]
The vibrator 34 is made of a super magnetostrictive material whose length is changed according
to the amount of magnetic flux when the magnetic flux is transmitted in the length direction,
whereby the bar-shaped vibrator 34 responds to the electromotive force signal S11. The length is
variable.
[0022]
Here, since the electromotive force signal S11 changes in the same signal format as the audible
sound modulation signal S4 obtained from the AM modulation circuit 12 as described above, the
vibrator 34 is eventually collected from the microphone 11 According to the sound signal S2, the
length vibrates in the direction indicated by the arrow a, and this vibration is applied to the skull
5 as an output of the implantable bone conduction hearing aid 1.
[0023]
Thus, the implantable bone conduction hearing aid 1 applies vibration corresponding to the
collected audible sound from the internal unit 3 to the skull 5 with respect to the audible sound
collected by the extracorporeal unit 2, and this vibration is the skull 5. It is transmitted through
the inside to the earlobe 27, and this is transmitted from the vestibule and cochlea 28 to the
brainstem as sound information.
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[0024]
(2) Example FIG. 4 shows an example of the above-mentioned embodiment, and the audible
sound modulation signal transmitter 2A of the extracorporeal unit 2 is shown in FIG. As shown in
(A), it has a magnetic yoke 41 whose longitudinal cross section has an “E” shape and has a
cylindrical external shape as a whole, and the extracorporeal transmission coil 31 is wound
around the cylindrical central yoke portion 41A. There is.
[0025]
Thus, for the transmission magnetic flux 33 generated in the central yoke portion 41A by the
extracorporeal transmission coil 31, there is a magnetic path passing from the central yoke
portion 41A through the cylindrical cylindrical yoke portion 41C via the disc-shaped end plate
yoke portion 41B. It is formed.
[0026]
Thus, when the extracorporeal transmission coil 31 is mounted on the scalp 4, the tip surfaces of
the central yoke portion 41 A and the cylindrical yoke portion 41 C of the magnetic yoke 41 are
disposed on the scalp 4.
[0027]
On the other hand, the in-vivo unit 3 has a magnetic yoke 42 whose longitudinal cross section
has an "E" shape and has a cylindrical external shape so as to face the magnetic yoke 41, and the
cylindrical central yoke portion 42A receives the body. The coil 32 is wound.
[0028]
The central yoke portion 42A of the magnetic yoke 42 receives the transmission magnetic flux
33 generated in the central yoke portion 41A of the magnetic yoke 41 of the extracorporeal unit
2 to form a disk-shaped end plate yoke portion 42B and a cylindrical cylindrical yoke portion
42C. A magnetic path for flowing the transmission magnetic flux 33 to the magnetic yoke 41 of
the extracorporeal unit 2 is formed.
[0029]
Thus, as shown in FIG. 6, the transmission magnetic flux 33 generated in the central yoke portion
41A of the magnetic yoke 41 by the extracorporeal transmission coil 31 of the extracorporeal
unit 2 passes through the scalp 4 and the central yoke portion of the magnetic yoke 42 of the inbody unit 3. 42A-end plate yoke portion 42B-magnetic path of cylindrical yoke portion 42C, and
04-05-2019
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further across the scalp 4 cylindrical yoke portion 41C of magnetic yoke 41 of external unit 2end plate yoke portion 41B-magnetic path of central yoke portion 41A Flow through.
[0030]
Thus, the transmission magnetic flux 33 generated in the magnetic yoke 41 of the extracorporeal
unit 2 crosses the scalp 4 and intersects the in-vivo receiving coil 32 to generate an induced
electromotive force.
[0031]
As shown in FIG. 7, a disk-shaped excitation portion mounting base 47 is formed so as to
protrude outward at the center position of the outer surface of the end plate yoke portion 42B of
the magnetic yoke 42, and this excitation portion attachment The excitation unit 3B is fixed so as
to protrude outward on the table 47.
[0032]
The vibrating portion 3B has a vibrator 34 formed of a bar-shaped giant magnetostrictive
element having a circular cross section, and a pair of operating point setters 48A and 48B
formed of disk-shaped permanent magnets are fixed to both ends thereof.
[0033]
A vibrator drive coil 35 is wound around the vibrator 34, and both ends T1 and T2 of the in-vivo
reception coil 32 are directly connected to both ends T11 and T12 of the vibrator drive coil 35.
[0034]
Thus, an excitation current corresponding to the audible sound modulated transmission signal S1
obtained by the interbody reception coil 32 intersecting the transmission magnetic flux 33 flows
through the vibrator drive coil 35, and as a result, the vibrator 34 is shown in FIG. By performing
the expansion and contraction operation according to the expansion and contraction
characteristics as the magnetostrictive element, the tip end of the vibrator 34 (the other end is
fixed to the magnetic yoke 42 to form a free end) is vibrated.
[0035]
As indicated by the expansion and contraction characteristic curve K1 in FIG. 8, the giant
magnetostrictive element constituting the vibrator 34 changes the amount of expansion and
contraction so that the amount of expansion increases as the excitation field H increases
04-05-2019
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corresponding to the excitation field H. It has a characteristic that exhibits
[0036]
In the case of this embodiment, the operating point setters 48A and 48B consisting of a pair of
permanent magnets are used at both ends of the vibrator 34 consisting of the super
magnetostrictive element, whereby the bias magnetic field H0 is given to the super
magnetostrictive element. Thus, when an electromotive force signal S11 is given around the
excitation operating point HX determined by the bias magnetic field H0, the amount of expansion
D1 of the vibrator 34 is an amount of expansion around the expansion operating point DX
corresponding to the excitation operating point HX. D1 changes.
[0037]
As a result, the tip end position of the vibrator 34 is displaced according to the change of the
expansion / contraction amount D1, so that the tip end of the vibrator 34 is vibrated.
[0038]
In the case of the embodiment of FIG. 4, the magnetic yoke 42 of the in-vivo reception coil 32 is
fixed to the skull 5 by the fixing screw 45 and a contact 50 made of a titanium material having a
dome shape is As the outer surface of the contact 50 is in contact with the skull 5, when the tip
of the vibrator 34 is displaced, it is transmitted as vibration to the skull 5 via the contact 50.
[0039]
Thus, by using the titanium material as the contact 50, the contact 50 adheres well to the skull
due to the characteristics of the titanium material, and the advantage of good transmission of
vibration and easy processing is effectively used. it can.
[0040]
In the case of this embodiment, the contactor 50 is connected to the end plate yoke portion 42B
of the magnetic yoke 42 by the connection ring 51 made of an annular flexible material, and is
thereby supported in a vibratable state.
[0041]
In the case of the embodiment of FIG. 4, as shown in FIG. 9, the sound collection processing unit
housing case fixed on the end plate yoke portion 41B of the magnetic yoke 41 constituting the
audible sound transmission unit 2A. The sound collection processing unit substrate 52 on which
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8
the AM modulation circuit 12 which is a circuit element of the sound collection processing unit
2B, the carrier wave oscillation circuit 13 and the output amplification circuit 14 are mounted is
provided in 51. 11 and a power supply battery 15 stored in the battery storage space 53 are
provided.
[0042]
The power supply battery 15 stored in the battery storage space 53 can be replaced and
replenished directly by the user (without requiring surgery or the like) by opening and closing
the openable and closable battery cover 54 as necessary.
[0043]
In the embodiment of FIG. 4, the intracorporeal unit 3 is implanted into the temporal bone of the
breast 5 in the vicinity of the auricle 21 of the skull 5 by implantation and fixed to the skull 5 by
a fixing screw 45.
[0044]
When the intracorporeal unit 3 is used as the implantable bone conduction hearing aid 1, the
wearer arranges the extracorporeal unit 2 at a position facing the intracorporeal unit 3 in the
scalp 4.
[0045]
At this time, the transmission magnetic flux 33 generated by the extracorporeal transmission coil
31 of the magnetic yoke 41 constituting the audible sound transmission unit 2A of the in-body
unit 2 crosses the scalp 4 and the audible sound information between it and the magnetic yoke
42 of the in-body unit 3 Form a magnetic path for transmitting
[0046]
At the same time, the magnetic flux of the permanent magnet used to set the operating point of
the vibrator 34 flows superimposed on the magnetic path transmitting the audible sound
information, and this magnetic flux causes the extracorporeal unit 2 to be transferred to the
internal unit 3. The extracorporeal unit 2 is stably mounted on the scalp 4 by the generation of
the attracting magnetic force.
[0047]
In this state, the carrier wave oscillation circuit 13 supplies a pulse signal of 40 [kHz] as the
04-05-2019
9
carrier wave signal S3 to the AM modulation circuit 12, thereby modulating the audible sound by
amplitude modulation with the sound collection signal S2 fetched from the microphone 11. A
signal S4 is obtained.
[0048]
The audible sound modulation signal S4 is converted into a transmission magnetic flux 33 by the
extracorporeal transmission coil 31 as an energy source for vibrating the vibrator 34 of the invivo unit 3, and this transmission magnetic flux 33 is different from the in-vivo reception coil 32
of the in-body unit 3. By generating an induced electromotive force in the in-vivo reception coil
32 by crossing, the electromotive force signal S11 is applied to both ends of the vibrator drive
coil 35 constituting the excitation unit 3B, and as a result, the vibrator 34 vibrates. Do.
[0049]
At this time, the vibrator 34 is constituted by the giant magnetostrictive element having the
expansion and contraction characteristic shown in FIG. 8 and has an AM demodulation form of
the pulse carrier by the self demodulation function obtained from the vibration characteristic of
the giant magnetostrictive element itself. From the electromotive force signal S11, a vibration
operation is performed so as to exhibit an expansion / contraction amount D1 according to the
sound collection signal S2 which is the amplitude modulation component.
[0050]
Thus, when the vibrator 34 vibrates in response to the sound collection signal S2 which is an
amplitude modulation component for the carrier pulse signal, the audible sound vibration is
applied to the skull 5 through the contact 50, and the ear 54 passes through the skull 54. It is
transmitted to the small bone 27.
[0051]
As a result, even if there is a failure that the audible sound signal is not transmitted to the
vestibular and cochlea 28 through the ear canal 22, eardrum 23 and earlobe 27, the wearer can
hear the audible sound reaching the ear canal 22 as a skull 5 It can be received in the vestibule
and cochlea 28 by the bone conduction action through which it can send audible sound
information to the brainstem.
[0052]
According to the above configuration, it is possible to realize the implantable bone conduction
hearing aid 1 capable of bone conduction of audible sound vibration via the skull 5 by the
04-05-2019
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external unit 2 and the internal unit 3.
[0053]
By using the super magnetostrictive element exhibiting expansion and contraction characteristics
as shown in FIG. 8 as the vibrator 34 of the in-vivo unit 3 for this purpose, AM can be specially
selected by utilizing the self-demodulation function of the super magnetostrictive element. A
clear audible sound vibration can be guided to the vestibule and cochlea 28 without providing a
demodulation circuit.
[0054]
According to the experiment on the operation of the vibrator 34, as shown in FIG. 10A, the fixed
end side displacement representing the displacement of the joint surface between the operating
point setting element 48A of the vibrator 34 and the vibrator mounting base 47 When the
displacement detection device (LDV) detects the amount detection signal S21 and the free end
side displacement detection signal S22 representing the displacement of the tip end face of the
vibrator 34, both can be detected as signals of the same phase. It could be confirmed that
vibration was generated in the longitudinal direction of the vibrator 34 made of a
magnetostrictive element.
[0055]
Further, as shown in FIG. 10B, the frequency spectrum of the free end side change detection
signal S22 has a peak P1 in the frequency component of 4 kHz and a peak P2 in the frequency
component of 40 kHz. Was confirmed.
[0056]
In this experiment, a pulse signal of 40 kHz was used as the carrier signal, whereas a sine wave
of 4 kHz was used as the audible sound signal, and the peak P2 of the frequency component of
40 kHz was used. As compared to the case where the peak P1 of the 4 [kHz] component which is
the amplitude modulation signal is extremely large as compared with the above, a vibrator
constituted by the vibrator 34 and a pair of operating point designers 48A and 48B provided at
both ends thereof. As shown in FIG. 8, the unit 61 applies an electromotive force signal S11 in
the form of a signal in which the pulse carrier is amplitude-modulated by an audible sound signal
to the vibrator drive coil 35 as a vibration drive source. As an amount of expansion and
contraction D1, an audible sound modulation transmission signal in a signal format amplitudemodulated by a pulse carrier is self-demodulated to output an amount of expansion and
contraction corresponding to the sound collection signal.
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[0057]
Thus, according to the extracorporeal unit 2 and the in-vivo unit 3, it is possible to realize the
implantable bone conduction hearing aid 1 capable of converting the sound collection signal
captured by the microphone 11 into the bone conduction signal component with high accuracy.
[0058]
In this way, the internal unit 3 can be a simple operation for implanting, and there is no need to
provide an operating power source in the internal unit 3, so that the operation for replenishing
the power supply in the body, etc. An unnecessary implantable bone conduction hearing aid can
be obtained.
[0059]
(3) Other Embodiments (3-1) In the above embodiment, a rod-shaped super magnetostrictive
element having a circular cross section is used as the vibrator 34, but the cross sectional shape
may be a quadrangle or an ellipse as needed. Even if it selects to various shapes, such as a shape,
the same effect as the above-mentioned case is acquired.
[0060]
Further, although the pair of operating point setting elements 38A and 38B made of permanent
magnets are provided at both ends of the vibrator 34, the way of inserting the operating point
setting elements 48A and 48B may be changed. It is only necessary to set a bias magnetic field
for determining the excitation operation point HX of 8.
[0061]
(3-2) In the in-vivo unit 3 according to the above-described embodiment, one end of the vibrator
34 is fixed as the fixed end to the magnetic yoke 42 formed by winding the in-vivo receiving coil
32, and the displacement of the free end is determined. The configuration is such that the bone
conduction output is applied to the skull 5, but the method of applying the bone conduction
output of the oscillator 34 to the skull 5 is not limited to this. For example, the oscillator 34 is
different from the magnetic yoke 42 It may be provided on the body.
[0062]
(3-3) In the above-described embodiment, as the method of attaching the extracorporeal unit 2 to
the scalp 4, the case is described in which the attraction magnetic force with the in-vivo unit 3 is
used. In addition to this, a wearing tool for separately wearing the extracorporeal unit 2 on the
04-05-2019
12
scalp 4 may be used.
[0063]
The present invention is applicable to bone conduction hearing aids.
[0064]
1 is a partial cross-sectional view showing an embodiment of an implantable bone conduction
hearing aid according to the present invention.
FIG. 2 is a schematic electrical circuit diagram showing the configuration for generating audible
sound vibration of the implantable bone conduction hearing aid 1 of FIG. 1;
FIG. 6 is a schematic perspective view for describing transmission of an audible sound
transmission signal into the body.
It is a longitudinal cross-sectional view which shows the structure of the Example of an
implantable bone conduction hearing aid.
It is a perspective view which shows the transmission structure and reception structure which
comprise the signal-transmission mechanism of the audible sound modulation | alteration
transmission signal in the body.
FIG. 6 is a schematic diagram for describing a magnetic path formed by a magnetic yoke 41 of
the extracorporeal unit 2 and a magnetic yoke 42 of the in-vivo unit 3.
FIG. 8 is a perspective view showing a detailed configuration of a vibration excitation unit 3B of
the in-vivo unit 3.
FIG. 16 is a characteristic curve diagram showing expansion and contraction characteristics of
the giant magnetostrictive element constituting the vibrator 34.
04-05-2019
13
FIG. 6 is a schematic cross-sectional view showing a configuration of a sound collection
processing unit 2B of the extracorporeal unit 2.
(A) is a signal waveform diagram showing a displacement amount of the vibrator 34, (B) is a
characteristic curve diagram showing a frequency spectrum of the free end side displacement
detection signal S22.
Explanation of sign
[0065]
DESCRIPTION OF SYMBOLS 1 ...... Implantable bone conduction hearing aid, 2 ... ユ ニ ッ ト
extracorporeal unit, 2 A 可 聴 audible sound modulation signal transmission part, 2 B 集 sound
collection processing part, 3 体内 intracorporeal unit, 3 A ...... audible sound modulation signal
reception part, 3 B ...... Excitation part 4 ...... scalp 5 頭 skull 頭 11 マ イ ク ロ ホ ン microphone
12 変 調 AM modulation circuit 13 搬 送 波 carrier oscillation circuit 14 出力 output
amplification circuit 15 電源 power battery 21 ... ...... Auricle 22 22 Outer ear canal 23 23
tympanic bone 25 24 bone 25 ツ 26 stab bone 27 耳 ear small bone 28 骨 vestibule and cochlea
31 体外 extracorporeal transmission Coils 32: body reception coil 33: transmission magnetic flux
34: vibrator 35: vibration drive coil 41, 42: magnetic yoke 41A, 42A: central yoke portion 41B,
42B: End plate yoke portion 41C, 42C: cylindrical yoke portion 47: excitation Mounting base,
48A, 48B ... Operating point setter, 51 ... Sound collection processing unit storage case, 52 ...
Sound collection processing unit board, 53 ... Battery storage space, 54 ... Battery cover, 61 ...
Vibration Child unit.
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