JP2009261782A - Energy supply coil, energy supply device, and wireless type subject's interior information acquisition system - Google Patents

Abstract

<P>PROBLEM TO BE SOLVED: To provide an energy supply coil uniforming (or a value close thereto) a magnetic field strength in a coil irrelevant to locations. <P>SOLUTION: This energy supply coil Ba, or an example of the energy supply coil includes a coil group having three or more coils in series and a voltage larger than a voltage impressed on the coil at the center whose magnetic field intensity becomes the strongest, is impressed on the coils at both ends whose magnetic field strength is weakest in the coil group. <P>COPYRIGHT: (C)2010,JPO&INPIT

Description

  The present invention relates to an energy supply coil that is used in a state of being introduced into a subject and supplies energy from outside the subject to a subject internal introduction device that performs a predetermined function inside the subject. The present invention relates to an energy supply coil that makes a magnetic field intensity constant in a coil regardless of location (a value close to that), an energy supply device using the coil, and a wireless subject internal information acquisition system.

  In recent years, in the field of endoscopes, swallowable capsule endoscopes have been proposed and put into practical use. This capsule endoscope is provided with an imaging mechanism and a wireless communication mechanism. Capsule endoscopes are swallowed from the subject's mouth for observation (examination) and then move in the body cavity, such as the stomach and small intestine, according to their peristaltic movement until they are naturally discharged. In addition, it has a function of performing imaging.

  Image data captured by the capsule endoscope is sequentially transmitted to the outside by wireless communication and stored in the memory. When the patient carries the receiver having the wireless communication function and the memory function, the patient can freely act during the period from swallowing the capsule endoscope to being discharged. Thereafter, the doctor or nurse can make a diagnosis by displaying an organ image on the display based on the image data stored in the memory.

  Such a capsule endoscope may have a configuration in which driving power is obtained from a built-in power supply source. However, in recent years, a configuration in which driving power is supplied from the outside to the capsule endoscope via wireless transmission has attracted attention. ing. By adopting a configuration in which power is supplied from the outside in this way, it is possible to avoid that the capsule endoscope is unintentionally consumed and stops driving while moving inside the body cavity. It is.

When power is supplied from the outside as described above, it is preferable that the power supply source be carried by the subject, so that it is preferable to have as high energy efficiency as possible when supplying power. In view of this, for example, a method using an energy supply coil wound around a subject at a substantially constant pitch as disclosed in Patent Document 1 has been devised.
Japanese Patent Laying-Open No. 2005-87552 (published on April 7, 2005)

  However, when such an energy supply coil having a constant pitch is used, the strength of the internal magnetic field varies depending on the location, and in particular, the magnetic field strength at the center of the coil is the strongest and the magnetic field strength at the coil end is the weakest. For example, when it is assumed that the coil for supplying energy is formed on a general adult body (radius = 0.15 m, length = 0.4 m), the center of the coil is 1.7 times the end of the coil. Field strength.

  The power supply to the capsule endoscope must supply the power necessary for driving the capsule endoscope at any position in the body, so the coil end with the weakest magnetic field strength is the worst case. As a result, the central portion of the coil has a magnetic field strength as strong as 1.7 times the required magnetic field strength. Therefore, the above-mentioned coil for supplying energy with a constant pitch generates extra magnetic field strength, which causes a problem that energy efficiency is lowered.

  In addition, since a strong magnetic field has an effect on human health and may cause malfunction of a device such as a cardiac pacemaker, the magnetic field strength cannot be increased without limit.

  The present invention has been made in view of the above problems, and an energy supply coil that makes the magnetic field strength in the coil constant (a value close to that) regardless of the location, and an energy supply device using the same, It is another object of the present invention to provide a wireless subject internal information acquisition system.

  In order to solve the above problems, an energy supply coil according to the present invention (hereinafter referred to as a “first energy supply coil”) includes a coil group in which three or more coils are provided in series. A voltage larger than the voltage applied to the coil at the center is applied to the coils at both ends of the group.

  According to the above configuration, the first energy supply coil includes the coil group in which three or more coils are provided in series, and the coil at both ends where the magnetic field strength is weakest in this coil group has the most magnetic field strength. A voltage larger than the voltage applied to the coil in the central portion where the voltage becomes strong is applied. As a result, it is possible to make up only the portion where the magnetic field strength is insufficient and to make the magnetic field strength in the coil constant (a value close to that) regardless of the location. As described above, the first energy supply coil has an effect of providing an energy supply coil in which the magnetic field intensity in the coil is constant (a value close to that) regardless of the location.

  As described above, the magnetic field strength in the coil can be made constant (a value close to that) regardless of the location, so that the first energy supply coil can be used, for example, the capsule endoscope described above. When supplying energy to the subject internal introduction device, the necessary energy can be obtained without generating extra magnetic field strength and as long as the subject internal introduction device is in the internal space. Therefore, efficient energy supply without waste can be realized. As a result, it is possible to reduce the power consumption of the power source that supplies the voltage to the energy supply coil. When a battery is assumed as the power source, the size and weight of the battery can be reduced.

  In the first energy supply coil, since the magnetic field intensity can be kept low, safety for the subject can be ensured.

  In the energy supply coil according to the present invention, it is preferable that the voltage applied to each coil in the coil group is changed stepwise in two or more steps from the central coil to the both end coils.

  In the energy supply coil according to the present invention, it is preferable that the voltage applied to each coil in the coil group increases from the coil at the center to the coils at both ends.

  According to said structure, the voltage applied to each said coil can be optimized, and the magnetic field intensity in a coil can be made constant with high precision irrespective of a place.

  In the coil for energy supply according to the present invention, in the coil group, a current ratio between the coil at each end and the coil at the center is preferably 1.1 to 1.8.

  In order to solve the above problems, an energy supply coil according to the present invention (hereinafter referred to as a “second energy supply coil”) includes a coil group in which three or more coils are provided in series. The number of turns per unit length of the coil at both ends of the group is larger than the number of turns per unit length of the coil at the center, and an equal voltage is applied to each coil in the coil group.

  The second energy supply coil has the same effect as the effect of the first energy supply coil by changing the number of turns per unit length of the coil instead of changing the voltage applied to the coil. .

  That is, the second energy supply coil includes a coil group in which three or more coils are provided in series, and the number of turns per unit length of the coil at both ends where the magnetic field strength is the weakest in this coil group is the most magnetic field. More than the number of turns per unit length of the coil in the central portion where the strength is increased. Thereby, only the portion where the magnetic field strength is insufficient can be compensated, and the magnetic field strength in the coil can be made constant (a value close to that) regardless of the location, as in the case of the first energy supply coil. As described above, the second energy supply coil has an effect of providing an energy supply coil in which the magnetic field strength in the coil is constant regardless of the location (a value close to that). As a result, as in the first energy supply coil, it is possible to efficiently supply energy without waste and to ensure the safety of the subject.

  In the energy supply coil according to the present invention, the number of turns per unit length of each coil in the coil group is preferably changed stepwise in two or more steps from the center coil to the both end coils. .

  In the energy supply coil according to the present invention, it is preferable that the number of turns per unit length of each coil in the coil group increases continuously from the coil at the center to the coils at both ends.

  According to said structure, the number of turns per unit length of each said coil can be optimized, and the magnetic field intensity in a coil can be made constant with a high precision irrespective of a place.

  In the coil for energy supply according to the present invention, in the coil group, a winding ratio per unit length between the coil at each end and the coil at the center is preferably 1.1 to 1.8.

  In order to solve the above problems, an energy supply coil according to the present invention (hereinafter referred to as a “third energy supply coil”) includes a coil group in which three or more coils are provided in series as main coils. The coil group further includes an auxiliary coil provided to overlap the main coils at both ends of the coil group, and an equal voltage is applied to each main coil in the coil group, and the auxiliary coil in the coil group Is characterized in that a voltage smaller than the voltage applied to the main coil is applied.

  The third energy supply coil is not a change in the voltage applied to the coil, nor does it change the number of turns per unit length of the coil, and by adding a coil, the first energy supply coil and the coil The same effect as the effect of the second energy supply coil is achieved.

  That is, the third energy supply coil includes a coil group in which three or more coils are provided in series as a main coil, and the auxiliary coil is superimposed on the main coil at both ends where the magnetic field strength is weakest in this coil group. A voltage smaller than the voltage applied to the main coil is applied to the auxiliary coil. As a result, only the portion where the magnetic field strength is insufficient is compensated, and the magnetic field strength in the coil is made constant regardless of the location as in the case of the first energy supply coil and the second energy supply coil. )be able to. As described above, the third energy supply coil has an effect of providing an energy supply coil in which the magnetic field strength in the coil is constant (a value close to that) regardless of the location. As a result, it is possible to efficiently supply energy without waste and to ensure the safety of the subject. The first energy supply coil and the second energy supply It is the same as the coil.

  In the energy supply coil according to the present invention, it is preferable that the auxiliary coil has the same axis and radius as the main coil, and the length is equal to or less than the radius of the main coil.

  In order to solve the above-described problems, an energy supply apparatus according to the present invention includes the energy supply coil and voltage supply means for supplying a desired voltage to the energy supply coil.

  Further, in order to solve the above-described problem, the wireless subject internal information acquisition system according to the present invention is arranged inside the subject and the subject internal introduction device introduced inside the subject, and the subject internal introduction described above. A wireless subject internal information acquisition system comprising: a transmitter / receiver that acquires information obtained by the device via radio and supplies energy to the subject internal introduction device, wherein the transmitter / receiver includes: In order to supply energy to the subject internal introduction device, the energy supply device is provided.

  According to said structure, since the said coil for energy supply is used, as mentioned above, while being able to implement | achieve efficient energy supply without waste with respect to the subject internal introduction apparatus, in that case, it is subject Can be secured.

  The energy supply coil according to the present invention includes a coil group in which three or more coils are provided in series. The coil at both ends where the magnetic field strength is weakest in the coil group is the center where the magnetic field strength is strongest. Apply a voltage greater than the voltage applied to the coil in the section.

  In addition, another energy supply coil according to the present invention includes a coil group in which three or more coils are provided in series, and the number of turns per unit length of the coil at both ends where the magnetic field strength is weakest in this coil group. Is greater than the number of turns per unit length of the coil at the center where the magnetic field strength is strongest.

  Further, another energy supply coil according to the present invention includes a coil group in which three or more coils are provided in series as a main coil, and the main coil at both ends where the magnetic field strength is weakest in this coil group. An auxiliary coil is provided in an overlapping manner, and a voltage smaller than the voltage applied to the main coil is applied to the auxiliary coil.

  As described above, each of the energy supply coils according to the present invention supplements only the portion where the magnetic field strength is insufficient, and the magnetic field strength in the coil is the same as the first energy supply coil and the second energy supply coil. Regardless of this, there is an effect that it can be made constant (a value close to that).

  As a result, when energy is supplied to a subject internal introduction device such as a capsule endoscope using each of the energy supply coils, an extra magnetic field strength is not particularly generated. Efficient energy supply can be realized. Moreover, in each said coil for energy supply, since the magnetic field intensity | strength can be restrained low, the safety | security with respect to a subject can be ensured.

  The embodiment of the present invention will be described below with reference to FIGS.

(Configuration of wireless subject internal information acquisition system)
FIG. 1 shows the configuration of a wireless subject internal information acquisition system 10 according to this embodiment.

  As shown in FIG. 1, the wireless subject internal information acquisition system 10 is introduced into the body of the subject 1 and the transmission / reception device 2 having a wireless transmission / reception function, and executes a predetermined function in the body of the subject 1. And a subject internal introduction device. In this embodiment, a capsule endoscope will be described as an example of the subject internal introduction device. The capsule endoscope 3 as the capsule endoscope is introduced into the body of the subject 1 and operates by driving power obtained from a radio signal transmitted from the transmission / reception device 2 to capture an image of the body cavity. Data is transmitted to the transmission / reception device 2.

  Further, the wireless subject internal information acquisition system 10 performs a data transfer between the display device 4 that displays an intra-body cavity image based on data received by the transmission / reception device 2 and the transmission / reception device 2 and the display device 4. The portable recording medium 5 is provided. The transmission / reception device 2 includes a transmission / reception jacket 2a worn by the subject 1 and an external device 2b that performs processing of a radio signal transmitted / received via the transmission / reception jacket 2a.

  The display device 4 is for displaying an in-vivo image captured by the capsule endoscope 3, and has a configuration such as a workstation that displays an image based on data obtained by the portable recording medium 5. Have Specifically, the display device 4 may be configured to directly display an image using a CRT display, a liquid crystal display, or the like, or may be configured to output an image to another medium such as a printer.

  The portable recording medium 5 can be attached to and detached from the external device 2b and the display device 4, and has a structure capable of outputting or recording information when being inserted into both. Specifically, the portable recording medium 5 is inserted into the external device 2 b and transmitted from the capsule endoscope 3 while the capsule endoscope 3 is moving in the body cavity of the subject 1. Record the data. Then, after the capsule endoscope 3 is ejected from the subject 1, that is, after imaging of the inside of the subject 1 is finished, the capsule endoscope 3 is taken out from the external device 2b and inserted into the display device 4 to be attached to the display device. The data recorded by 4 is read out. When data is transferred between the external device 2b and the display device 4 by a portable recording medium 5 such as a compact flash (registered trademark) memory, and the external device 2b and the display device 4 are connected by wire. Unlike the above, the subject 1 can freely move during imaging in the body cavity.

(Configuration of transceiver)
The transmission / reception device (energy supply device) 2 has a function as a power feeding device that transmits power to the capsule endoscope 3 and receives in-vivo image data transmitted from the capsule endoscope 3. It also has a function as a device.

  FIG. 2 shows the configuration of the transmission / reception device 2. As shown in the figure, the transmission / reception device 2 has a shape that can be worn by the subject 1, and includes a transmission / reception jacket 2a including reception antennas A1 to An and a power feeding antenna (energy supply coil) B, and transmission / reception. And an external device 2b for processing the received radio signal.

  The external device 2b has a function of processing a radio signal transmitted from the capsule endoscope 3. Specifically, as shown in FIG. 2, the external device 2b performs predetermined processing on the radio signals received by the receiving antennas A1 to An, and the capsule endoscope 3 out of the radio signals. An RF receiving unit 11 that extracts and outputs the acquired image data, an image processing unit 12 that performs necessary processing on the output image data, and a storage unit 13 that records the image data subjected to image processing. With. Note that image data is recorded on the portable recording medium 5 via the storage unit 13.

  The external device (voltage supply means) 2 b has a function of generating a radio signal to be transmitted to the capsule endoscope 3. Specifically, the external device 2 b includes an oscillator 14 that generates a power feeding signal and defines an oscillation frequency, and a control information input unit that generates a control information signal for controlling the driving state of the capsule endoscope 3. 15, a superimposing circuit 16 that combines the power feeding signal and the control information signal, and an amplifier circuit 17 that amplifies the intensity of the combined signal. The signal amplified by the amplifier circuit 17 is sent to the power feeding antenna B and transmitted to the capsule endoscope 3. The external device 2b includes a power supply unit 18 including a predetermined power storage device or an AC power adapter, and the constituent elements of the external device 2b use the power supplied from the power supply unit 18 as driving energy.

(Configuration of capsule endoscope)
Next, the capsule endoscope 3 will be described. FIG. 3 shows the configuration of the capsule endoscope 3. As shown in the figure, the capsule endoscope 3 includes an LED 19 for irradiating an imaging region when photographing the inside of the subject 1, an LED drive circuit 20 for controlling the drive state of the LED 19, and the LED 19. A CCD 21 that captures an image of the irradiated region and a signal processing circuit 22 that processes an image signal output from the CCD 21 into imaging information in a desired format are provided. The capsule endoscope 3 includes a CCD drive circuit 26 that controls the drive state of the CCD 21 and an RF transmission unit that generates an RF signal by modulating image data captured by the CCD 21 and processed by the signal processing circuit 22. 23, a transmission antenna unit 24 that transmits the RF signal output from the RF transmission unit 23, an LED drive circuit 20, a CCD drive circuit 26, and a system control circuit 32 that controls the operation of the RF transmission unit 23. The CCD 21, the signal processing circuit 22, and the CCD driving circuit 26 are collectively referred to as an imaging circuit 40.

  By providing these mechanisms, the capsule endoscope 3 acquires the image information of the subject region illuminated by the LED 19 by the CCD 21 while being introduced into the subject 1. The acquired image information is subjected to signal processing by the signal processing circuit 22, converted into an RF signal by the RF transmission unit 23, and then transmitted to the outside via the transmission antenna unit 24.

  The capsule endoscope 3 includes a receiving antenna unit 25 that receives a radio signal transmitted from the transmission / reception device 2 and a separation circuit 27 that separates a power feeding signal from a signal received by the receiving antenna unit 25. . Furthermore, the capsule endoscope 3 includes a power regeneration circuit 28 that regenerates power from the separated power supply signal, a booster circuit 29 that boosts the regenerated power, and a capacitor 30 that stores the boosted power. Prepare. Further, the capsule endoscope 3 detects the content of the control information signal from the component separated from the power feeding signal by the separation circuit 27, and if necessary, the LED drive circuit 20, the CCD drive circuit 26, and the system control circuit 32. Is provided with a control information detection circuit 31 for outputting a control signal. The control information detection circuit 31 and the system control circuit 32 also have a function of distributing drive power supplied from the battery 30 to other components.

  By providing these mechanisms, the capsule endoscope 3 first receives a radio signal transmitted from the transmission / reception device 2 at the reception antenna unit 25, and then receives a power feeding signal and a control information signal from the received radio signal. To separate. The control information signal is output to the LED drive circuit 20, the CCD drive circuit 26, and the system control circuit 32 through the control information detection circuit 31, and is used for controlling the drive state of the LED 19, the CCD 21, and the RF transmission unit 23. On the other hand, the power feeding signal is regenerated as power by the power regeneration circuit 28, and the regenerated power is boosted to the potential of the capacitor 30 by the booster circuit 29 and then stored in the capacitor 30. The battery 30 has a configuration capable of supplying power to the system control circuit 32 and other components. Thus, the capsule endoscope 3 has a configuration in which power is supplied by wireless transmission from the transmission / reception device 2.

(Configuration of feeding antenna)
Next, the power feeding antenna B will be described. In the present embodiment, three types of power feeding antennas will be described as examples of the power feeding antenna B.

  FIG. 4 shows a schematic configuration of a feeding antenna Ba which is an example of the feeding antenna B. The feeding antenna Ba includes a coil group in which three or more coils are provided in series. In this embodiment, the case where the coil group is composed of six coils 50 to 55 as shown in FIG. 4 will be described as an example.

  As shown in FIG. 4, the power feeding antenna Ba has a conductive wire wound in a coil shape around the internal space 58 so as to form a cylindrical internal space 58 in which the subject 1 is disposed (coil). 50 to 55), the capsule endoscope 3 is fed by magnetic coupling feeding. Here, the coils 50 to 55 are cylindrical solenoid coils that are sparsely wound so that the self-inductance is low. These coils 50 to 55 are embedded in or attached to the transmission / reception jacket 2a. The internal space 58 formed by the coils 50 to 55 is formed corresponding to the position where the capsule endoscope 3 passes through the subject 1.

  When the power feeding antenna Ba is used as the power feeding antenna B, the amplifiers 60 to 65 are provided in the amplifier circuit 17 in the external device 2b. The amplifiers 60 and 61 are connected to the coils 50 and 55, the amplifiers 62 and 63 are connected to the coils 51 and 54, respectively, and the amplifiers 64 and 65 are connected to the coils 52 and 53, respectively. The amplifiers 60 to 65 amplify the intensity of the signal output from the superimposing circuit 16 and supply the amplified signal to the coils 50 to 55, respectively.

  When the voltage supplied to the coil 50 is “V50”, the voltage supplied to the coil 51 is “V51”, and the other voltages are also “V52” to “V55”, these voltages V50 to V55 are in phase. These voltage values have a relationship of V50 = V55> V51 = V54> V52 = V53. This can be realized by appropriately setting the amplification degree of the amplifiers 60 to 65.

  Here, when a constant current is passed through each coil of the coil group, the magnetic field strength generated in the internal space 58 is strongest at the central portion of the coil group and becomes weaker toward the end portion, and at each end portion. It becomes the weakest. That is, the intensity of the magnetic field generated varies depending on the location. If the magnetic field strength varies depending on the location as described above, there arises a problem that an unnecessary magnetic field strength is inevitably generated when power is supplied to the capsule endoscope 3, and efficient and efficient energy supply cannot be achieved.

  Therefore, as shown in the relationship of the voltage values of the above voltages V50 to V55, a voltage larger than the voltage applied to the coils 52 and 53 at the center is applied to the coils 50 and 55 at both ends in the coil group. In general, since the magnetic field strength created by a circular current is proportional to the flowing current, applying a voltage as described above compensates only for the portion where the magnetic field strength is insufficient, and the magnetic field strength in the coil is independent of the location. It can be constant (a value close to that).

  Here, the current ratio between the coils 50 and 55 at both ends and the coils 52 and 53 at the center is preferably 1.1 to 1.8. When the current ratio is 1.1, each coil in the coil group is a coil having a radius of about 30 cm and a length of about 20 cm. On the other hand, when the current ratio is 1.8, each coil in the coil group is a coil having a radius of about 10 cm and a length of about 40 cm. These coils can also be used in Examples 2 and 3 described later.

  Note that the radius is a portion indicated by “r” in FIG. 4 and indicates a radius in the circular internal space 58 formed by the coil. Moreover, the said length is a part which attached | subjected the code | symbol "l" in FIG. 4, and is the length of the longitudinal direction (The direction in which the coils 50-55 were provided in series) of the said coil group. Furthermore, specific numerical values such as the radius are calculated on the assumption that the coil is wound around the body of the person who is the subject 1.

  FIG. 5 shows the relationship between the magnetic field strength (vertical axis) and the distance from the coil end (horizontal axis) of the coil group in which the voltage to be applied is changed according to the location of the coil as described above. As shown in the figure, the distance from the coil end is equal to or less than the coil length L, that is, the magnetic field strength is constant inside the coil, and the magnetic field strength is attenuated as the distance from the coil increases beyond the coil length L, that is, outside the coil. Yes.

  Further, as described above, when a constant current is passed through each coil of the coil group, the magnetic field strength generated in the internal space 58 is strongest in the central portion of the coil group and becomes weaker toward the end portion. Therefore, as shown in the relationship between the voltage values of the voltages V50 to V55 described above, the voltage applied to the coil is increased as it goes from the center to the end in the coil group. That is, in the coil group, not only the central portion and the end portion, but also the voltage applied to the coils at other locations is optimized. Thereby, the magnetic field strength in the coil can be made constant regardless of the location with higher accuracy.

  As described above, the feeding antenna Ba according to the present embodiment is formed by a coil group in which three or more coils are provided in series, and a higher voltage is supplied to the coil at the end of the coil group. Therefore, the magnetic field intensity generated in the internal space formed by the coil group can be made constant (a value close to that) regardless of the location.

  Since the magnetic field strength in the coil can be made constant (a value close to that) regardless of the location as described above, the feeding endoscope Ba can be used as the feeding antenna B with respect to the capsule endoscope 3. When energy is supplied, unnecessary energy is not generated, and as long as the capsule endoscope 3 is in the internal space, necessary energy can be obtained regardless of the location. Efficient energy supply can be realized. As a result, it is possible to reduce the power consumption of the power source that supplies the voltage to the power feeding antenna B. When a battery is assumed as the power source, the size and weight can be reduced.

  Further, in the power feeding antenna Ba, the magnetic field intensity can be kept low, and thus safety for the subject can be ensured.

  FIG. 6 shows a schematic configuration of a feeding antenna Bb which is another example of the feeding antenna B. In the power feeding antenna Ba described in the first embodiment, by adjusting the amount of current flowing through the coil, the magnetic field intensity generated in the internal space formed by the coil is constant (or a value close thereto) regardless of the location. However, the power feeding antenna Bb in the present embodiment has the same effect as the power feeding antenna Ba by adjusting the number of turns per unit length of the coil.

  The power feeding antenna Bb includes a coil group in which three or more coils are provided in series. In this embodiment, the case where the coil group is composed of six coils 70 to 75 as shown in FIG. 6 will be described as an example.

  As shown in FIG. 6, the power feeding antenna Bb has a conductive wire wound in a coil shape around the internal space 78 so as to form a cylindrical internal space 78 in which the subject 1 is disposed (coil). 70 to 75), and power is supplied to the capsule endoscope 3 by magnetic coupling power supply. Here, the coils 70 to 75 are cylindrical solenoid coils that are sparsely wound so that the self-inductance is low. These coils 70 to 75 are embedded in or attached to the transmission / reception jacket 2a. The internal space 58 formed by the coils 70 to 75 is formed corresponding to the position where the capsule endoscope 3 passes through the subject 1.

  Here, if the number of turns per unit length of the coil 70 is “n70”, the number of turns per unit length of the coil 71 is “n71”, and the number of turns per unit length of other coils is also “n72” to “n75”. The number of turns has a relationship of n70 = n75> n71 = n74> n72 = n73. In the coil group, the turns ratio per unit length between the coils 70 and 75 at both ends and the coils 72 and 73 at the center is preferably 1.1 to 1.8. When the power feeding antenna B is used as the power feeding antenna B, the amplifier circuit 17 in the external device 2b includes amplifiers 80 and 81 and supplies equal voltages to the coils 70 to 75, respectively. Hereinafter, the amplifier circuit 17 corresponding to the second embodiment is referred to as an “amplifier circuit 17a”.

  That is, in the power feeding antenna Bb, the number of turns per unit length of the coils 70 and 75 at both ends in the coil group is larger than the number of turns per unit length of the coils 72 and 73 at the center. In general, since the magnetic field strength generated by the circular current is proportional to the number of turns, setting the number of turns per unit length of the coil as described above compensates only for the portion where the magnetic field strength is insufficient, thereby increasing the magnetic field strength in the coil. Can be made constant regardless of location (a value close to that).

  In the coil group, the number of turns per unit length of the coil is increased from the center to the end. Thereby, the magnetic field strength in the coil can be made constant regardless of the location with higher accuracy.

  As described above, the power feeding antenna Bb according to the present embodiment is formed by a coil group in which three or more coils are provided in series, and the number of turns per unit length is increased as the coil is at the end of the coil group. ing. Therefore, the magnetic field intensity generated in the internal space formed by the coil group can be made constant (a value close to that) regardless of the location. As a result, when energy is supplied to the capsule endoscope 3 using the power supply antenna Bb as the power supply antenna B, an efficient energy supply without waste is achieved as in the case of the power supply antenna Ba. It is possible and the safety for the subject 1 can be ensured.

  FIG. 7 shows a schematic configuration of a feeding antenna Bc, which is still another example of the feeding antenna B. In the power feeding antenna Ba described in the first embodiment, by adjusting the amount of current flowing through the coil, the magnetic field intensity generated in the internal space formed by the coil is constant (or a value close thereto) regardless of the location. did. Further, the power feeding antenna Bb described in the second embodiment has the same effect as the power feeding antenna Ba by adjusting the number of turns per unit length of the coil. The power feeding antenna Bc in the present embodiment has the same effect as the power feeding antennas Ba and Bb by adding a coil.

  The feeding antenna Bc includes a coil group in which three or more coils are provided in series as main coils. In this embodiment, the case where the coil group is composed of six main coils 90 to 95 as shown in FIG. 7 will be described as an example.

  As shown in FIG. 7, in the power feeding antenna Bc, a conductive wire is wound around the inner space 98 in a coil shape so as to form a cylindrical inner space 98 in which the subject 1 is arranged (mainly). Coils 90 to 95) are fed to the capsule endoscope 3 by magnetic coupling feeding. Here, the main coils 90 to 95 are cylindrical solenoid coils that are sparsely wound so that the self-inductance is low. These main coils 90 to 95 are embedded in or attached to the transmission / reception jacket 2a. The internal space 98 formed by the main coils 90 to 95 is formed corresponding to the position where the capsule endoscope 3 passes through the subject 1.

  Here, in addition to the main coils 90 to 95, the power feeding antenna Bc includes auxiliary coils 96 and 97 provided to overlap the main coils 90 and 95. The auxiliary coils 96 and 97 have the same axis and radius as the main coils 90 to 95, and the length is preferably equal to or less than the radius of the main coils 90 to 95.

  When the feeding antenna Bc is used as the feeding antenna B, the amplification circuit 17 in the external device 2b (hereinafter, the amplification circuit 17 corresponding to this embodiment is referred to as “amplification circuit 17b”) is described in the second embodiment. The function of the amplifier circuit 17a in FIG. That is, the amplifier circuit 17b includes amplifiers 80 and 81 (not shown), and supplies equal voltages to the main coils 90 to 95, respectively. The amplifier circuit 17b further includes amplifiers 83 and 84, and supplies the auxiliary coils 96 and 97 with a voltage smaller than the voltage supplied to the main coils 90 to 95 (the phase is the same for both voltages).

  That is, the power feeding antenna Bc includes auxiliary coils 96 and 97 in addition to the coils 90 and 95 at both ends where the magnetic field strength generated in the internal space 98 is the weakest when a constant current is passed through each main coil of the coil group. Is added. A voltage smaller than the voltage supplied to the main coils 90 to 95 is supplied to the auxiliary coils 96 and 97. Thereby, the power feeding antenna Bc can make up only the portion where the magnetic field strength is insufficient, and can make the magnetic field strength in the coil constant (a value close to that) regardless of the location.

  As a result, when energy is supplied to the capsule endoscope 3 using the power supply antenna Bc as the power supply antenna B, as in the case of the power supply antennas Ba and Bb, efficient energy without waste. While supply is possible, the safety | security with respect to the subject 1 can be ensured.

  The present invention is not limited to the above-described embodiments, and various modifications are possible within the scope shown in the claims, and embodiments obtained by appropriately combining technical means disclosed in different embodiments. Is also included in the technical scope of the present invention.

  The energy supply coil according to the present invention can make the magnetic field strength in the coil constant (a value close to that) regardless of location, and is used by being introduced into a subject such as a capsule endoscope, for example. It can be used suitably for the use which supplies energy with respect to the to-be-tested object internal introduction apparatus. At that time, efficient energy supply without waste can be realized and safety for the subject can be ensured.

  In addition, an energy supply apparatus according to the present invention includes the above-described energy supply coil and is used for supplying energy to the subject internal introduction apparatus. Further, a wireless subject internal information acquisition system according to the present invention includes: Suitable for use with the above-mentioned various configurations, performing energy supply to the subject internal introduction device and controlling its operation, and acquiring information obtained by the subject internal introduction device and performing appropriate processing Can be used.

It is a figure which shows the structure of the wireless type | mold subject internal information acquisition system which concerns on embodiment of this invention. It is a block diagram which shows the structure of the transmission / reception apparatus which comprises the said wireless type | mold subject internal information acquisition system. It is a block diagram which shows the structure of the capsule endoscope which comprises the said wireless type | mold subject internal information acquisition system. It is a figure which shows the structural example of the antenna for electric power feeding. 5 is a graph showing the relationship between the magnetic field strength and the distance from the coil end in the power feeding antenna shown in FIG. 4. It is a figure which shows the other structural example of the antenna for electric power feeding. It is a figure which shows the further another structural example of the antenna for electric power feeding.

Explanation of symbols

2 Transmission / reception device (energy supply device)
2b External device (voltage supply means)
3 Capsule endoscope (subject internal introduction device)
10. Wireless subject internal information acquisition system 50-55, 70-75, 90-95 coil, main coil 96, 97 Auxiliary coil Ba, Bb, Bc Energy supply coil

Claims (12)

Comprising a coil group in which three or more coils are provided in series;
The energy supply coil, wherein a voltage larger than a voltage applied to a central coil is applied to the coils at both ends of the coil group.   2. The energy supply according to claim 1, wherein the voltage applied to each coil in the coil group is changed stepwise in two or more steps from the coil at the center to the coils at both ends. coil.   3. The energy supply coil according to claim 2, wherein a voltage applied to each coil in the coil group increases from the coil at the center to the coils at both ends.   In the said coil group, the current ratio of the coil of each said edge part and the coil of the said center part is 1.1-1.8, The energy as described in any one of Claims 1-3 characterized by the above-mentioned. Coil for supply. Comprising a coil group in which three or more coils are provided in series;
The number of turns per unit length of the coil at both ends of the coil group is greater than the number of turns per unit length of the coil at the center,
An equal voltage is applied to each coil in the coil group.   6. The energy supply according to claim 5, wherein the number of turns per unit length of each coil in the coil group is changed stepwise in two or more steps from the coil at the center to the coils at both ends. Coil.   The coil for energy supply according to claim 6, wherein the number of turns per unit length of each coil in the coil group increases from the coil at the center to the coils at both ends.   In the said coil group, the turns ratio per unit length of the coil of each said end part and the coil of the said center part is 1.1-1.8, It is any one of Claims 5-7 characterized by the above-mentioned. The coil for energy supply described in 1. A coil group in which three or more coils are provided in series as a main coil,
The coil group further includes an auxiliary coil provided to overlap the main coil at both ends of the coil group,
An equal voltage is applied to each main coil in the coil group, and a voltage smaller than the voltage applied to the main coil is applied to the auxiliary coil in the coil group. .   The said auxiliary coil has the same axis | shaft and radius as the said main coil, The length is below the radius of the said main coil, The coil for energy supply of Claim 9 characterized by the above-mentioned. The energy supply coil according to any one of claims 1 to 10,
An energy supply device comprising: a voltage supply means for supplying a desired voltage to the energy supply coil. A subject internal introduction device that is introduced into the subject, and an information that is arranged outside the subject and obtained by the subject internal introduction device is acquired wirelessly and energy is provided to the subject internal introduction device. A wireless subject internal information acquisition system comprising a transmission / reception device for supplying
12. The wireless subject internal information acquisition system according to claim 11, wherein the transmission / reception device includes the energy supply device according to claim 11 to supply energy to the subject internal introduction device.

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