CA1276240C - Transcutaneous power and signal transmission system and methods for increased signal transmission efficiency - Google Patents
Transcutaneous power and signal transmission system and methods for increased signal transmission efficiencyInfo
- Publication number
- CA1276240C CA1276240C CA000504471A CA504471A CA1276240C CA 1276240 C CA1276240 C CA 1276240C CA 000504471 A CA000504471 A CA 000504471A CA 504471 A CA504471 A CA 504471A CA 1276240 C CA1276240 C CA 1276240C
- Authority
- CA
- Canada
- Prior art keywords
- frequency
- signal transmission
- coupling
- tuned
- coupling coil
- 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.)
- Expired - Lifetime
Links
Classifications
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61F—FILTERS IMPLANTABLE INTO BLOOD VESSELS; PROSTHESES; DEVICES PROVIDING PATENCY TO, OR PREVENTING COLLAPSING OF, TUBULAR STRUCTURES OF THE BODY, e.g. STENTS; ORTHOPAEDIC, NURSING OR CONTRACEPTIVE DEVICES; FOMENTATION; TREATMENT OR PROTECTION OF EYES OR EARS; BANDAGES, DRESSINGS OR ABSORBENT PADS; FIRST-AID KITS
- A61F11/00—Methods or devices for treatment of the ears or hearing sense; Non-electric hearing aids; Methods or devices for enabling ear patients to achieve auditory perception through physiological senses other than hearing sense; Protective devices for the ears, carried on the body or in the hand
- A61F11/04—Methods or devices for enabling ear patients to achieve auditory perception through physiological senses other than hearing sense, e.g. through the touch sense
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61N—ELECTROTHERAPY; MAGNETOTHERAPY; RADIATION THERAPY; ULTRASOUND THERAPY
- A61N1/00—Electrotherapy; Circuits therefor
- A61N1/18—Applying electric currents by contact electrodes
- A61N1/32—Applying electric currents by contact electrodes alternating or intermittent currents
- A61N1/36—Applying electric currents by contact electrodes alternating or intermittent currents for stimulation
- A61N1/36036—Applying electric currents by contact electrodes alternating or intermittent currents for stimulation of the outer, middle or inner ear
- A61N1/36038—Cochlear stimulation
-
- Y—GENERAL TAGGING OF NEW TECHNOLOGICAL DEVELOPMENTS; GENERAL TAGGING OF CROSS-SECTIONAL TECHNOLOGIES SPANNING OVER SEVERAL SECTIONS OF THE IPC; TECHNICAL SUBJECTS COVERED BY FORMER USPC CROSS-REFERENCE ART COLLECTIONS [XRACs] AND DIGESTS
- Y10—TECHNICAL SUBJECTS COVERED BY FORMER USPC
- Y10S—TECHNICAL SUBJECTS COVERED BY FORMER USPC CROSS-REFERENCE ART COLLECTIONS [XRACs] AND DIGESTS
- Y10S128/00—Surgery
- Y10S128/903—Radio telemetry
Abstract
Abstract of the Disclosure A transcutaneous signal transmission system having coupling coil alignment tolerance and increased coupling efficiency includes an external transmitter and first tuned circuit including a first coupling coil and an implantable receiver and second tuned circuit including a second coupling coil. The first and second tuned circuits are stagger tuned whereby closer spacing of the coupling coils is permitted in achieving optimum coup-ling.
Description
1.'A~7~i240 TRANSCUTANEOUS POWER AND SIGNAL TRANS~ISSION SYSTEM AND
METHODS FOR INCREASED SIGNAL TRANSMISSION EFFICIENCY
This invention relates generally to systems for trans-mitting e]ectrical signals into the body of a patient, and more particularly the invention relates to the transmission of signals to a receiver which is implanted in the body.
Transcutaneous signal transmission systems are known and widely utilized for neural and muscle stimulation. Such systems are generally preferred over other transmission systems such as the use of implanted batteries or the use of direct percutaneous wiring. Typically, a trans-mitter transmits a modulated signal to an imp]anted receiver via two inductively coupled coils. The coils are part of tuned circuits which can cooperatively function as a bandpass filter. Our U. S. Patent No.
4,284,856 and U. S. Patent No. 4,357,497 disclose auditory stimulation apparatus in which inductive coupled coils are utilized in transcutaneous signal transmission.
Heretofore, inductive transmission systems have been designed for optimum efficiency with a consequential dependence of induced voltage in the implanted coil on exact positioning of the transmitter coil. Thus, in applications such as auditory stimulation where a precise output signal is necessary, the inductive transmission system has limitations in effectiveness.
~2 ~;240 Our U. S. Patent No. 4,441,210 discloses a method and apparatus which al]ows a tolerance in coil alignment for optimum signal transmission. The transmitter and receiver coils are tuned to the frequency of the transmission signal, and critical coupling is achieved between the coils. Critical coupling is realized by adjusting the spacing of the coils whereby the output impedance of the transmitter decreases to one-half of the output impedance of the transmitter with no coup-]ing. Spacing between the coils cannot decrease below apredetermined ]imit because the coils would then become overcoupled and result in a drop in signal. Practically speaking, the alignment tolerance realized with critical coupling is offset by a limit in transmission efficiency of about 50%.
An object of the present invention is a method and means of maintaining coil alignment tolerance while increasing the efficiency in signal transmission.
A feature of the invention is the use of transmitter and receiver tuned circuits which are not tuned to the same frequency.
Briefly, the transmission system in accordance with the invention includes a transmitter in which audio signals modulate a carrier signal at an RF frequency. The modulated carrier signal is inductively coupled from a transmitter tuned circuit to a receiver tuned circuit.
The two tuned circuits are stagger tuned whereby closer spacing of the coupling coils is required for optimum signal coupling. Importantly, the closer spacing of the coils for optimum coupling permits an increase in signal transmission efficiency to 90% or more.
In a preferred embodiment, the receiver circuit is tuned to the carrier signal frequency, and the transmitter , i~27624o circuit is detuned to increase coupling of the two tuned circuits at optimum coupling. It has been found that signal transmission efficiency increases substantially (i.e. from 50% ta 90% or more~
with only a small decrease in alignment tolerance.
In accordance with a broad aspect of the invention ~here is provided, in a transcutaneous signal transmission system, a method of transmitting signals comprising the steps of providing an external transmitter and first tuned circuit including a first coupling coil, said first tuned circuit being tuned to a first frequency, providing an implantable receiver and second tuned circuit including a second coupling coil, said second tuned circuit being tuned to a second frequency, and transmitting signals between said coupling coils at a third frequency, said third frequency being different from at least one of said first and second frequencies.
In accordance with another broad aspect of the invention there is provided a transcutaneous signal transmission system comprising an external transmitter and first tuned circuit including a first coupling coil, said first tuned circuit being tuned to a first frequency, and an implantable receiver and second tuned circuit including a second coupling coil, said external transmitter transmitting signals at a third frequency, said third frequency differing from at least one of said first and second frequencies.
In accordance with another broad aspect of the invention there is provided a signal transmission system comprising a transmitter and first tuned circuit including a first coupling _, :~, .4, ,. ~..
-3a- ~1051~ 51 coll, said first tuned circuit bein~ tuned to a first frequency, and a receiver and secon~ tuned circuit including a second coupling coil, said sècond tuned circuit being coupled to said first tuned circuit, said transmitter transmitting siynals at a third frequency, said third frequency differing from at least one of said first and second frequencies.
The invention and objects and features thereof will be more readily apparent from the following detailed description and appended claims when taken with the drawing, in which:
Figure l is a functional block diagram of an auditory stimulation system in accordance with one embodiment of the invention .
Figure 2 is a plot illustrating signal transmission : efficiency as a function of transmitter and receiver dPtuning from the transmission frequency.
Referring now to the drawings, Figure l is a functional block diagram of auditory stimulation apparatus in accordance with one embodiment of the invention. Similar apparatus is disclosed in U.S. Patent No. 4,441,210, supra. A microphone 12 has its output applied to a speech processor electronics shown as being enc}osed by the broken line box 14. Included in the speed processor channel is a gain control amplifier 16 which receives as its input the electrical output from the microphone 12, and the output from the gain control amplifier 16 i5 applied through a bandpass filter 18 to an isoloudness frequency adjustment circuit 20. Circuit 20 is a frequency dependent network which compensates for the fact that the stimulated current for a given loudness is ~'^,' ' , ;. ~
i276240 ~-3~ Sl~
frequency dependent. Tlle speech processor electronics 14 further includes a dynamic ran~e compression circuit 22 which may either precede or follow the isoloudness frequency adjustment circuit 20.
i . " ' .~ ~, ..
i;~7~
The output of the speech processor 14 is arranged to modulate the output of an RF oscillator in the AM
transmitter module 24. The modulated output from the transmitter is applied across a transmitting coil 26 and a capacitor 28, these last mentioned two components being designed to cooperate as a tuned circuit 30.
The implant unit 31 is shown to the right of the skin interface 32 and includes the receiver coil 33 which has a capacitor 34 connected in parallel with it. The parallel combination of the receiving coil 33 and the capacitor 34 forms a tuned receiver circuit 36. The output from the tuned receiver circuit is coupled as an input to a diode demodulator network 38 which functions in a conventional fashion to remove the modulation envelope from the RF carrier. The output of the diode demodulator is applied via the leads 40 to electrodes in or near the cochlea.
As above described, our U. S. Patent No. 4,441,210 describes the tuning of the circuits 30 and 36 to the RF
frequency of transmitter 24 and the achieving of criti-cal coupling between the two tuned circuits whereby alignment tolerance of the coils 30 and 36 is increased.
However, signal transmission efficiency in such an arrangement is limited to 50~.
In accordance with the present invention the tuned circuits 30 and 36 are detuned whereby closer position-ing of the two coils 30, 36 is necessary to achieve optimu~ coupling. The closer positioning of the coils has the attendant benefit of substantially increasing the signal transmission efficiency while only slightly decreasing the alignment tolerance of the two coils.
~HKW
1~76~40 Figure 2 is a plot of transmission efficiency obtained at the relative maximum of the transimpedance over the normalized frequency offset of the transmitter tuned circuit (xl) and the receiver tuned circuit (x2) with respect to the carrier frequency. The plot is actually a three-dimensional surface. From this plot it will be noted that the best efficiency is reali~ed when the receiver tuned circuit is tuned to the carrier frequency (i.e. x2 = 0), while progressive detuning of the trans-mitter tuned circuit necessitates increased couplingwith the ensuing positive effect of increased efficien-cy. Experiments have demonstrated that coupling coeffi-cients, K, of up to three are achievable ana trans-mission efficiency of 85~ are achievable.
The following table shows the usable (relative) ranges K/K of the coupling coefficient, K. K is defined by an allowable drop of the output voltage at the receiver coil of 5% from its maximum value assumed for some value of K within that range. The ensuing relative distance tolerances, dld, for four different coupling coeffi-cients are as follows:
K xl K/K d/d l 0 0.67 0.58 1.5 l 0.58 0.36 2 2 0.57 0.38 2.5 3 0.57 0.45 From this table it is seen that the position tolerance afforded by optimum coupling at K=l is only slightly affected by the detuning to increase efficiency. For example, at K=1 the value of d/d is 0.58; whereas, at K=2,5 d/d is 0.45.
It has been shown that an improved transcutaneous signal transmission system is provided by detuning the transmitter and receiver tuned circuits whereby closer spacing of the coupling coils can be realized for optimum coupling. The closer spacing of the coils permits increased efficiency in signal transmission without significantly affecting alignment tolerance.
While the invention has been described with reference to one embodiment, the description is illustrative of the invention and is not to be construed as limiting the invention. Various modifications and applications may occur to those skilled in the art without departing from the true spirit and scope of the invention as defined by the appended claims.
METHODS FOR INCREASED SIGNAL TRANSMISSION EFFICIENCY
This invention relates generally to systems for trans-mitting e]ectrical signals into the body of a patient, and more particularly the invention relates to the transmission of signals to a receiver which is implanted in the body.
Transcutaneous signal transmission systems are known and widely utilized for neural and muscle stimulation. Such systems are generally preferred over other transmission systems such as the use of implanted batteries or the use of direct percutaneous wiring. Typically, a trans-mitter transmits a modulated signal to an imp]anted receiver via two inductively coupled coils. The coils are part of tuned circuits which can cooperatively function as a bandpass filter. Our U. S. Patent No.
4,284,856 and U. S. Patent No. 4,357,497 disclose auditory stimulation apparatus in which inductive coupled coils are utilized in transcutaneous signal transmission.
Heretofore, inductive transmission systems have been designed for optimum efficiency with a consequential dependence of induced voltage in the implanted coil on exact positioning of the transmitter coil. Thus, in applications such as auditory stimulation where a precise output signal is necessary, the inductive transmission system has limitations in effectiveness.
~2 ~;240 Our U. S. Patent No. 4,441,210 discloses a method and apparatus which al]ows a tolerance in coil alignment for optimum signal transmission. The transmitter and receiver coils are tuned to the frequency of the transmission signal, and critical coupling is achieved between the coils. Critical coupling is realized by adjusting the spacing of the coils whereby the output impedance of the transmitter decreases to one-half of the output impedance of the transmitter with no coup-]ing. Spacing between the coils cannot decrease below apredetermined ]imit because the coils would then become overcoupled and result in a drop in signal. Practically speaking, the alignment tolerance realized with critical coupling is offset by a limit in transmission efficiency of about 50%.
An object of the present invention is a method and means of maintaining coil alignment tolerance while increasing the efficiency in signal transmission.
A feature of the invention is the use of transmitter and receiver tuned circuits which are not tuned to the same frequency.
Briefly, the transmission system in accordance with the invention includes a transmitter in which audio signals modulate a carrier signal at an RF frequency. The modulated carrier signal is inductively coupled from a transmitter tuned circuit to a receiver tuned circuit.
The two tuned circuits are stagger tuned whereby closer spacing of the coupling coils is required for optimum signal coupling. Importantly, the closer spacing of the coils for optimum coupling permits an increase in signal transmission efficiency to 90% or more.
In a preferred embodiment, the receiver circuit is tuned to the carrier signal frequency, and the transmitter , i~27624o circuit is detuned to increase coupling of the two tuned circuits at optimum coupling. It has been found that signal transmission efficiency increases substantially (i.e. from 50% ta 90% or more~
with only a small decrease in alignment tolerance.
In accordance with a broad aspect of the invention ~here is provided, in a transcutaneous signal transmission system, a method of transmitting signals comprising the steps of providing an external transmitter and first tuned circuit including a first coupling coil, said first tuned circuit being tuned to a first frequency, providing an implantable receiver and second tuned circuit including a second coupling coil, said second tuned circuit being tuned to a second frequency, and transmitting signals between said coupling coils at a third frequency, said third frequency being different from at least one of said first and second frequencies.
In accordance with another broad aspect of the invention there is provided a transcutaneous signal transmission system comprising an external transmitter and first tuned circuit including a first coupling coil, said first tuned circuit being tuned to a first frequency, and an implantable receiver and second tuned circuit including a second coupling coil, said external transmitter transmitting signals at a third frequency, said third frequency differing from at least one of said first and second frequencies.
In accordance with another broad aspect of the invention there is provided a signal transmission system comprising a transmitter and first tuned circuit including a first coupling _, :~, .4, ,. ~..
-3a- ~1051~ 51 coll, said first tuned circuit bein~ tuned to a first frequency, and a receiver and secon~ tuned circuit including a second coupling coil, said sècond tuned circuit being coupled to said first tuned circuit, said transmitter transmitting siynals at a third frequency, said third frequency differing from at least one of said first and second frequencies.
The invention and objects and features thereof will be more readily apparent from the following detailed description and appended claims when taken with the drawing, in which:
Figure l is a functional block diagram of an auditory stimulation system in accordance with one embodiment of the invention .
Figure 2 is a plot illustrating signal transmission : efficiency as a function of transmitter and receiver dPtuning from the transmission frequency.
Referring now to the drawings, Figure l is a functional block diagram of auditory stimulation apparatus in accordance with one embodiment of the invention. Similar apparatus is disclosed in U.S. Patent No. 4,441,210, supra. A microphone 12 has its output applied to a speech processor electronics shown as being enc}osed by the broken line box 14. Included in the speed processor channel is a gain control amplifier 16 which receives as its input the electrical output from the microphone 12, and the output from the gain control amplifier 16 i5 applied through a bandpass filter 18 to an isoloudness frequency adjustment circuit 20. Circuit 20 is a frequency dependent network which compensates for the fact that the stimulated current for a given loudness is ~'^,' ' , ;. ~
i276240 ~-3~ Sl~
frequency dependent. Tlle speech processor electronics 14 further includes a dynamic ran~e compression circuit 22 which may either precede or follow the isoloudness frequency adjustment circuit 20.
i . " ' .~ ~, ..
i;~7~
The output of the speech processor 14 is arranged to modulate the output of an RF oscillator in the AM
transmitter module 24. The modulated output from the transmitter is applied across a transmitting coil 26 and a capacitor 28, these last mentioned two components being designed to cooperate as a tuned circuit 30.
The implant unit 31 is shown to the right of the skin interface 32 and includes the receiver coil 33 which has a capacitor 34 connected in parallel with it. The parallel combination of the receiving coil 33 and the capacitor 34 forms a tuned receiver circuit 36. The output from the tuned receiver circuit is coupled as an input to a diode demodulator network 38 which functions in a conventional fashion to remove the modulation envelope from the RF carrier. The output of the diode demodulator is applied via the leads 40 to electrodes in or near the cochlea.
As above described, our U. S. Patent No. 4,441,210 describes the tuning of the circuits 30 and 36 to the RF
frequency of transmitter 24 and the achieving of criti-cal coupling between the two tuned circuits whereby alignment tolerance of the coils 30 and 36 is increased.
However, signal transmission efficiency in such an arrangement is limited to 50~.
In accordance with the present invention the tuned circuits 30 and 36 are detuned whereby closer position-ing of the two coils 30, 36 is necessary to achieve optimu~ coupling. The closer positioning of the coils has the attendant benefit of substantially increasing the signal transmission efficiency while only slightly decreasing the alignment tolerance of the two coils.
~HKW
1~76~40 Figure 2 is a plot of transmission efficiency obtained at the relative maximum of the transimpedance over the normalized frequency offset of the transmitter tuned circuit (xl) and the receiver tuned circuit (x2) with respect to the carrier frequency. The plot is actually a three-dimensional surface. From this plot it will be noted that the best efficiency is reali~ed when the receiver tuned circuit is tuned to the carrier frequency (i.e. x2 = 0), while progressive detuning of the trans-mitter tuned circuit necessitates increased couplingwith the ensuing positive effect of increased efficien-cy. Experiments have demonstrated that coupling coeffi-cients, K, of up to three are achievable ana trans-mission efficiency of 85~ are achievable.
The following table shows the usable (relative) ranges K/K of the coupling coefficient, K. K is defined by an allowable drop of the output voltage at the receiver coil of 5% from its maximum value assumed for some value of K within that range. The ensuing relative distance tolerances, dld, for four different coupling coeffi-cients are as follows:
K xl K/K d/d l 0 0.67 0.58 1.5 l 0.58 0.36 2 2 0.57 0.38 2.5 3 0.57 0.45 From this table it is seen that the position tolerance afforded by optimum coupling at K=l is only slightly affected by the detuning to increase efficiency. For example, at K=1 the value of d/d is 0.58; whereas, at K=2,5 d/d is 0.45.
It has been shown that an improved transcutaneous signal transmission system is provided by detuning the transmitter and receiver tuned circuits whereby closer spacing of the coupling coils can be realized for optimum coupling. The closer spacing of the coils permits increased efficiency in signal transmission without significantly affecting alignment tolerance.
While the invention has been described with reference to one embodiment, the description is illustrative of the invention and is not to be construed as limiting the invention. Various modifications and applications may occur to those skilled in the art without departing from the true spirit and scope of the invention as defined by the appended claims.
Claims (12)
1. In a transcutaneous signal transmission system, a method of transmitting signals comprising the steps of providing an external transmitter and first tuned circuit including a first coupling coil, said first tuned circuit being tuned to a first frequency, providing an implantable receiver and second tuned circuit including a second coupling coil, said second tuned circuit being tuned to a second frequency, and transmitting signals between said coupling coils at a third frequency, said third frequency being different from at least one of said first and second frequencies.
2. The method as defined by Claim 1 wherein said second frequency and said third frequency are the same.
3. The method as defined by Claim 2 and further includ-ing the step of positioning said first coupling coil with respect to said second coupling coil to achieve optimum coupling.
4. The method as defined by Claim 1 and further includ-ing the step of positioning said first coupling coil with respect to said second coupling coil to achieve optimum coupling.
5. A transcutaneous signal transmission system compris-ing an external transmitter and first tuned circuit including a first coupling coil, said first tuned circuit being tuned to a first frequency, and an implantable receiver and second tuned circuit including a second coupling coil, said external transmitter transmitting signals at a third frequency, said third frequency differing from at least one of said first and second frequencies.
6. The transcutaneous signal transmission system as defined by Claim 5 wherein said second frequency and said third frequency are the same.
7, The transcutaneous signal transmission system as defined by Claim 6 wherein said first coupling coil is positioned with respect to said second coupling coil to achieve optimum coupling.
8. The transcutaneous signal transmission system as defined by Claim 5 wherein said first coupling coil is positioned with respect to said second coupling coil to achieve optimum coupling.
9. A signal transmission system comprising a transmitter and first tuned circuit including a first coupling coil, said first tuned circuit being tuned to a first frequency, and a receiver and second tuned circuit including a second coupling coil, said second tuned circuit being coupled to said first tuned circuit, said transmitter transmitting signals at a third frequency, said third frequency differing from at least one of said first and second frequencies.
10. The signal transmission system as defined by Claim 9 wherein said second frequency and said third frequency are the same.
11. The signal transmission system as defined by Claim 10 wherein said first coupling coil is positioned with respect to said second coupling coil to achieve optimum coupling.
12. The signal transmission system as defined by Claim 9 wherein said first coupling coil is positioned with respect to said second coupling coil to achieve optimum coupling.
Applications Claiming Priority (2)
| Application Number | Priority Date | Filing Date | Title |
|---|---|---|---|
| US71402385A | 1985-03-20 | 1985-03-20 | |
| US714,023 | 1985-03-20 |
Publications (1)
| Publication Number | Publication Date |
|---|---|
| CA1276240C true CA1276240C (en) | 1990-11-13 |
Family
ID=24868491
Family Applications (1)
| Application Number | Title | Priority Date | Filing Date |
|---|---|---|---|
| CA000504471A Expired - Lifetime CA1276240C (en) | 1985-03-20 | 1986-03-19 | Transcutaneous power and signal transmission system and methods for increased signal transmission efficiency |
Country Status (5)
| Country | Link |
|---|---|
| US (1) | US5070535A (en) |
| EP (1) | EP0200321A3 (en) |
| JP (1) | JPS61276568A (en) |
| AU (1) | AU5481786A (en) |
| CA (1) | CA1276240C (en) |
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-
1986
- 1986-03-18 EP EP86301983A patent/EP0200321A3/en not_active Ceased
- 1986-03-18 AU AU54817/86A patent/AU5481786A/en not_active Abandoned
- 1986-03-19 JP JP61061951A patent/JPS61276568A/en active Pending
- 1986-03-19 CA CA000504471A patent/CA1276240C/en not_active Expired - Lifetime
-
1987
- 1987-01-30 US US07/009,565 patent/US5070535A/en not_active Expired - Lifetime
Also Published As
| Publication number | Publication date |
|---|---|
| EP0200321A2 (en) | 1986-11-05 |
| AU5481786A (en) | 1986-09-25 |
| JPS61276568A (en) | 1986-12-06 |
| EP0200321A3 (en) | 1987-03-11 |
| US5070535A (en) | 1991-12-03 |
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