JP6914812B2 - Probe and relay coil for nuclear magnetic resonance measurement - Google Patents

Description

The present invention relates to a probe for nuclear magnetic resonance measurement, and more particularly to a relay coil that is inductively coupled to a detection coil.

Nuclear Magnetic Resonance (NMR) is a phenomenon in which atomic nuclei placed in a static magnetic field interact with electromagnetic waves having their own frequencies. The device for measuring the phenomenon is a nuclear magnetic resonance measuring device. An MRI (Magnetic Resonance Imaging) device is also a type of nuclear magnetic resonance measuring device.

A typical nuclear magnetic resonance measuring device has a spectrometer and a probe for nuclear magnetic resonance measurement (NMR probe). The NMR probe is provided with a detection coil that irradiates the sample to be measured with an electromagnetic wave and detects the nuclear magnetic resonance generated in the sample. Recently, research is underway to construct the detection coil with a superconducting material (usually a high-temperature superconducting material). If the detection coil is constructed of a superconducting material, its electrical resistance becomes zero in the cooled state, so that a very high Q value can be realized, that is, high-sensitivity measurement can be realized. However, when the detection coil is made of a superconducting material, it is very difficult to connect the detection coil. This is because if wiring is made to it, the characteristics of the superconducting material will change. Superconducting materials are usually constructed as oxides, to which wiring is technically difficult.

Patent Document 1 discloses a detection coil (main coil) made of a superconducting material and a pickup coil (relay coil as a sub coil) arranged in the vicinity thereof. The detection coil and the pickup coil are inductively coupled, that is, they are connected wirelessly. The relay coil has a simple loop or ring shape, that is, it does not have a significant width or depth in the direction of the coil center axis. The relay coil is also disclosed in Patent Document 2.

U.S. Pat. No. 9,274,199 (Fig. 1B) Japanese Unexamined Patent Publication No. 2016-151494 (Fig. 2)

When the relay coil is configured as a linear and loop-shaped coil, magnetic fluxes from various directions can easily enter the relay coil, and can be easily coupled to an object other than the main coil in an inductive manner. That is, parasitic binding is likely to occur. When a parasitic bond occurs, a loss in transmitting electromagnetic energy occurs, and an electromagnetic wave (that is, noise) other than the electromagnetic wave to be observed is detected, resulting in a decrease in the S / N ratio. By strengthening the inductive coupling between the main coil and the relay coil, the parasitic coupling can be reduced, but in that case, a significant high frequency current flows in the circuit after the relay coil and the energy efficiency decreases. Problems such as a decrease in the Q value of the coil are likely to occur.

An object of the present invention is to prevent or reduce parasitic coupling when a relay coil that inductively couples to the main coil is used. Alternatively, it is an object of realizing a relay coil having coupling destination selectivity or directivity. Alternatively, the relay coil is arranged so as not to affect the characteristics of the main coil as much as possible.

The probe for nuclear magnetic resonance measurement according to the embodiment is a main coil that performs at least one of transmission and reception in order to detect a nuclear magnetic resonance signal from a measurement target, and a sub coil that is inductively coupled to the main coil. The relay coil includes a coil body, and the coil body extends in the direction of its central axis and surrounds the central axis.

According to the above configuration, the relay coil is arranged so as to be inductively coupled to the main coil. That is, the main coil and the relay coil are electrically connected wirelessly via the electromagnetic induction phenomenon. The coil body in the relay coil has a virtual central axis, and has a form of extending (spreading) in the direction of the central axis while surrounding the central axis. With such a form, the coil body has a coupling destination selectivity or directivity. This can prevent or reduce parasitic binding. From a different point of view, according to the above configuration, it is less likely to be affected by electromagnetic noise coming from various directions. Further, it is not necessary to bring the relay coil closer to the main coil to strengthen the inductive coupling degree. For example, if a relay coil made of a normal metal is brought close to a main coil made of an oxide high-temperature superconducting material, there arises a problem that the Q value of the detection coil decreases. However, according to the above configuration, Such problems are less likely to occur. According to the experiment, by adopting the above configuration on the premise of the main coil composed of the high-temperature superconducting material, the S / N can be significantly improved while maintaining the high Q value inherent in the main coil. Has been confirmed.

The main coil is a transmitting coil that irradiates an object with an electromagnetic wave that causes nuclear magnetic resonance, a receiving coil that detects a signal that represents nuclear magnetic resonance generated by the object, or a transmission / reception that exerts both functions. It is a coil for. The function of the relay coil may change depending on the function of the main coil. Desirably, as the main coil, a pair of detection coils made of a high-temperature superconducting material are provided on both sides of the object.

In the embodiment, the coil body is composed of a sheet-shaped conductive member surrounding the central axis. Here, the sheet shape means a thinly spread form. Desirably, the relay coil body is made of metal leaf. When the area of the relay coil facing the main coil (area of the opening edge) becomes large, the magnetic field formed by the main coil is likely to be disturbed, and the Q value of the main coil is likely to be deteriorated. On the other hand, if the thickness of the coil body is reduced, the area of the portion of the coil body facing the detection coil becomes smaller, so that problems such as magnetic field disturbance and Q value decrease can be prevented or reduced.

In the embodiment, the coil body has a tubular shape. The cross section of the coil body orthogonal to the central axis is, for example, circular, elliptical, or polygonal. It is also conceivable that the cross section has a C-shape, a D-shape, or a spiral shape. In an embodiment, the relay coil includes a pair of terminals connected to the coil body. Desirably, the coil body and the terminal pair are composed of a single member. According to this, it becomes possible to easily manufacture a relay coil by deforming a single sheet-shaped member. A non-conductive member that supports or assists the relay coil body may be provided on the outside or inside of the relay coil body.

In the embodiment, the coil body has a first end and a second end facing each other through a slit parallel to the central axis, and the terminal pair includes a first terminal extending from the first end and the terminal. It is composed of a second terminal extending from the second end alongside the first terminal. This configuration facilitates wiring to the coupling coil. In an embodiment, the relay coil has a first opening and a second opening, the first opening facing the main coil. In the embodiment, the main coil is made of a superconducting material.

The relay coil according to the embodiment is a relay coil body that inductively couples to a main coil made of a superconducting material that transmits and receives at least one of the nuclear magnetic resonance signals from the measurement target. Including, the relay coil body is made of a tubular metal foil. It is also conceivable to provide a plurality of relay coils. This relay coil can be used in an NMR measuring device that detects nuclear magnetic resonance generated in a sample, as well as in an MRI device that detects nuclear magnetic resonance generated in a living body.

According to the present invention, when a relay coil that is inductively coupled to the main coil is used, parasitic coupling can be prevented or reduced. Alternatively, according to the present invention, a relay coil having coupling destination selectivity or directivity can be realized. Alternatively, according to the present invention, the relay coil can be arranged so as not to affect the characteristics of the main coil as much as possible.

It is a block diagram which shows the structural example of the NMR measurement system which concerns on embodiment. It is sectional drawing which shows the structure in the probe head. It is a circuit diagram which shows the electric circuit including a detection coil and a relay coil. It is a perspective view which shows the structure in the probe head. It is a figure which shows the coil body in the relay coil. It is a perspective view which shows the comparative example. It is a figure which shows the 1st arrangement example of a relay coil. It is a figure which shows the 2nd arrangement example of a relay coil. It is a figure which shows the 3rd arrangement example of a relay coil. It is a figure which shows the 2nd example of a relay coil. It is a figure which shows the 3rd example of a relay coil. It is a figure which shows the 4th example of a relay coil. It is a figure which shows the 5th example of a relay coil. It is a figure which shows the 6th example of a relay coil.

Hereinafter, embodiments will be described with reference to the drawings.

FIG. 1 shows a configuration example of the NMR measurement system according to the embodiment. The NMR measurement system according to the embodiment causes nuclear magnetic resonance in a specific atomic nucleus in a sample by irradiating the sample to be measured with an electromagnetic wave, and observes a signal (FID signal) generated thereafter. be. Examples of the sample include a gas sample, a liquid sample and a solid sample. The illustrated NMR measurement system is composed of a control device 10, a measurement device 12, and a cooler 14. The z direction is the vertical direction, the x direction is the first horizontal direction, and the y direction is the second horizontal direction.

The measuring device 12 includes a static magnetic field generator 18 and an NMR probe 16. The static magnetic field generator 18 generates a uniform static magnetic field parallel to the z direction in the sample space where the sample exists. The static magnetic field generator 18 has a bore 12A as a through hole formed along the z direction. The NMR probe 16 is roughly classified into an insertion portion 16A and a base portion 16B. The insertion portion 16A is inserted into the bore 12A. A sample tube, a detection coil (main coil), a relay coil (sub coil), and the like are provided in the probe head 28, which is the upper part of the insertion portion 16A. The details of the inside of the probe head 28 will be described later with reference to each figure after FIG. The inside of the NMR probe 16 is in a vacuum state. A cooler 14 is provided to cool each element (particularly the detection coil, the relay coil and the electric circuit) in the probe head 28, particularly to cool the detection coil to a predetermined temperature or lower to form a superconducting state. Has been done. In the embodiment, the cooler 14 feeds liquid helium or low temperature helium gas into the NMR probe 16 through the pipe 26. A shimming unit is also arranged in the bore 12A, but this is not shown.

The control device 10 functions as a spectrometer. Specifically, the control device 10 has a transmission unit 20, a reception unit 22, and an arithmetic control unit 24. In FIG. 1, only the main configuration of the control device 10 is shown, and the details thereof are not shown. The transmission unit 20 generates a transmission signal (RF signal) according to the transmission pulse sequence and sends it to the NMR probe 16. As a result, the detection coil irradiates the sample with electromagnetic waves. A signal representing nuclear magnetic resonance generated in the sample is detected in the detection coil, whereby the received signal is sent from the NMR probe 16 to the receiving unit 22. In the receiving unit, a spectrum is generated by processing the received signal. The data is sent to the arithmetic control unit 24. The spectrum may be generated in the arithmetic control unit 24. The arithmetic control unit 24 has a function of controlling the operation of each configuration shown in FIG. 1 and analyzing the acquired data.

FIG. 2 illustrates the structure of the probe head 28 according to the embodiment. The shield 29 has, for example, a cylindrical shape. Electromagnetic waves coming from the outside world are blocked by the shield 29. A probe container is provided on the outside of the shield 29. The inside 28A of the probe container is an airtight chamber and is in a vacuum state.

The pedestal 34 has a disk-shaped shape extending in the horizontal direction, and it is made of, for example, a metal having good thermal conductivity, for example, copper. The heat exchanger to which the refrigerant is supplied from the cooling device and the heat conductive member provided between the heat exchanger and the pedestal 34 are not shown. A tube 30 as an inner partition wall is provided so as to penetrate the probe head 28 in the z direction. Atmosphere exists inside the tube 30, and the temperature inside the tube 30 is room temperature. A sample tube 32 is arranged inside the tube 30. The sample to be measured is housed in the sample tube 32. A gas having a predetermined temperature may be poured into the tube 30 to adjust the temperature of the sample.

A pair of detection coil units 36A and 36B are arranged on the pedestal 34 on both sides of the pipe 30 in an upright posture. Each detection coil unit 36A, 36B has a substrate 38A, 38B and a detection coil 40A, 40B. The detection coils 40A and 40B cooperate with each other or exert the same action with each other, and from a functional point of view, all of them correspond to a single detection coil.

The substrates 38A and 38B are made of sapphire glass or the like as an insulating material. The detection coils 40A and 40B are configured as a film or layer made of a high-temperature superconducting material as an oxide. The detection coils 40A and 40B can also be made of ordinary metal. In the embodiment, the temperature of the pair of detection coils 40A and 40B is maintained below a certain temperature at which the superconducting effect occurs. Each of the detection coils 40A and 40B is configured as a one-turn planar coil as specifically shown in FIG. Each of the detection coils 40A and 40B may be configured as a coil having a plurality of turns. The Q value of the detection coils 40A and 40B is, for example, 10,000 or more.

In the embodiment, the pair of detection coils 40A and 40B function as transmission / reception coils, respectively. However, the pair of detection coils 40A and 40B may be used as reception-only coils, respectively. The resonance frequency of the pair of detection coils 40A and 40B can be adjusted by moving an object closer to or further away from any of the detection coils 40A and 40B. For example, when the dielectric is brought close to any of the detection coils 40A and 40B, the resonance frequency is lowered. Increasing the area of the metal leaf facing the high-frequency magnetic field increases the resonance frequency. When an alternating current flows through the pair of detection coils 40A and 40B due to the nuclear magnetic resonance generated in the sample, an alternating magnetic field penetrating the pair of detection coils 40A and 40B is generated. It is shown by B in FIG.

A relay coil 42 is provided in the vicinity of the detection coil unit 36B (on the side opposite to the tube 30). The relay coil 42 is a sub coil or a pickup coil, and as described above, the relay coil 42 is inductively coupled to the pair of detection coils 40A and 40B. That is, the relay coil 42 and the pair of detection coils 40A and 40B are electrically connected wirelessly by electromagnetic induction. In the embodiment, the relay coil 42 functions at the time of transmission and at the time of reception. At the time of transmission, the transmission signal from the control device side is transmitted to the pair of detection coils 40A and 40B via the relay coil 42, and at the time of reception, the reception signal generated by the pair of detection coils 40A and 40B is the relay coil. It is sent to the control device side via 42.

The relay coil 42 is composed of a coil body 46 and a pair of terminals 48. In the embodiment, the coil body 46 and the terminal pair 48 are manufactured by rolling one metal foil (metal sheet) as a single member and bending it. It is also possible to configure the coil body 46 and the terminal pair 48 with different materials. The relay coil 42, particularly the coil body 46, is made of a metal having low electrical resistance and good thermal conductivity, for example, copper, gold, silver, aluminum, etc., and in the embodiment, it is made of copper. .. It is desirable that the relay coil 42 is made of a magnetic susceptibility correction material so as not to disturb the magnetic field. That is, it is desirable that the relay coil 42 as a whole is configured so that magnetization does not occur or magnetization becomes small. The magnetic susceptibility correction material consists of, for example, a plurality of layers that cancel each other's magnetization.

The coil body 46 has a virtual central axis. The coil body 46 has a form that surrounds the central axis and extends in the direction of the central axis (has a significant length), and specifically, the coil body 46 has a tubular shape. The central axis is parallel to the central axis penetrating the pair of detection coils 40A and 40B in the illustrated example. The specific form of the relay coil 42 will be described in more detail later.

A support column 44 is provided on the pedestal 34, and a relay coil 42 is attached to the tip of the support column 44. The strut 44 has a coaxial structure, that is, the strut 44 has a function of wiring to a pair of terminals. The support column 44 is made of a material having good thermal conductivity, for example, copper. The strut 44 may also be made of a magnetic susceptibility correction material.

Since the coil body 46 of the relay coil 42 has a tubular shape, a certain magnetic flux guide effect works, and the coupling destination selectivity or directivity is generated as a function of the relay coil 42. That is, it is possible to exclude or reduce unnecessary parasitic coupling without bringing the relay coil 42 close to the detection coils 40A and 40B. It is also possible to provide a plurality of relay coils. A transmission coil for decoupling, a transmission coil for deuterium lock, and the like are provided in the probe head 28, but these are not shown.

FIG. 3 shows an equivalent circuit for the electrical configuration within the probe head. The detection coil 40 and the relay coil 42 (coil body 46) are inductively coupled. Reference numeral 52 indicates the mutual inductance between the coils 40 and 42. Reference numeral 50 indicates a capacitance component, and the capacitance component corresponds to a capacitance component or the like possessed by the detection coil itself. An electric circuit 54 for tuning matching is connected to the relay coil 42, and the electric circuit 54 has, for example, a variable capacitor 56.

FIG. 4 shows the inside of the probe head as a perspective view. As described above, a pair of detection coil units 36A and 36B are provided on the pedestal 34 in parallel with each other. Specifically, they are held by a pair of holders 60A, 60B arranged on the pedestal 34. Each detection coil unit 36A and 36B has the same configuration. Here, focusing on the detection coil unit 36B, it is composed of a substrate 38B and a detection coil 40B. A relay coil 42 held by a support column 44 is provided in the vicinity of the detection coil 40B. Specifically, the relay coil 42 is provided so as to face the center of the detection coil 40B in the y direction and the lower portion in the z direction.

The detection coil 40B is a one-turn type planar coil. Specifically, the detection coil 40B is composed of a horizontal side 62a, a vertical side 62b, a horizontal side 62c, a vertical side 62d, and a horizontal side 62e. The horizontal side 62a and the horizontal side 62e are separated from each other through a certain gap, and the capacitance component is composed of them. The detection coil included in the detection coil unit 36A has a coil pattern symmetrical to that of the detection coil 40B.

FIG. 5 schematically shows the coil body 46 of the relay coil according to the first example. As described above, the coil main body 46 is configured as a conductive sheet that extends in the direction of the central axis C and surrounds the central axis C, and specifically, is made of a tubular copper foil. The coil body 46 has a first opening edge 66 and a second opening edge 72. The inside of the first opening edge 66 is the first opening 70, and the inside of the second opening edge 72 is the second opening 74. In the illustrated example, the first opening faces the detection coil 40B, especially its interior 64. The lowest level H1 of the coil body 46 is above the lowest level H2 of the inner 64, which is an example. The lowest level H1 may be lower than the lowest level H2 as long as sufficient sensitivity can be obtained. The coil body 46 has two sides facing each other at its lower portion, and two terminals extend downward from the two sides. However, the two terminals are not shown in FIG.

The length L of the coil body 46 is, for example, in the range of several mm to several cm, preferably in the range of several mm to 10 mm. For example, the length L may be about 0.5 to 1 times the distance between the pair of detection coils. It may be more than that. When the distance between the pair of detection coils is about 9 mm, L may be 5 mm. It is considered that the directivity can be sharpened by increasing the length L. The diameter D of the coil body is, for example, in the range of a few mm to 10 mm, preferably in the range of 1 mm to 5 mm. It is desirable to match the impedance of the electric circuit with the impedance of the relay coil. For example, the length L and the diameter D may be adjusted so that the impedance of the relay coil becomes 50Ω. The coil body 46 is configured to be very thin, and its thickness t may be in the range of several μm to several hundred μm, or may be 1 mm or more. For example, where the skin effect is determined by the electrical resistance of the material constituting the coil body, the thickness t of the coil body may be about 30 times the thickness δ based on the thickness δ at which the skin effect occurs. For example, the thickness t may be 10 μm. Each numerical value given above is an example.

As the thickness t becomes smaller, the area of the coil body 46 facing the detection coil 40B (the area of the first opening edge 66) becomes smaller, and the magnetic field created by the pair of detection coils is less likely to be disturbed. When magnetic flux enters the metal material and an eddy current is generated there, the Q value of the superconducting coil deteriorates, but if the thickness t is very small, the eddy current is reduced to prevent or reduce the deterioration of the Q value. can. If it is difficult to maintain the shape of the coil body, a mandrel as an endoskeleton or a frame as an exoskeleton may be used. The thin metal layer formed on those skeletons can also be called a metal foil in terms of its morphology and its function.

As indicated by reference numeral 78, a vertical slide mechanism may be provided so that the position of the relay coil in the z direction can be changed. Further, as indicated by reference numeral 79, a horizontal slide mechanism may be provided so that the position of the relay coil in the x direction can be changed. As indicated by reference numeral 82, a tilt mechanism may be provided so that the relay coil can be rotated around the virtual axis 80 parallel to the y direction. Further, as indicated by reference numeral 86, a swivel mechanism (swing mechanism) may be provided so that the relay coil can be rotated around the virtual axis 84 parallel to the z direction. By changing the position and orientation of the relay coil, the mutual inductance between the relay coil and the detection coil can be adjusted.

FIG. 6 shows a comparative example. A pair of detection coil units 36A and 36B are provided on the pedestal 34. A relay coil 100 is provided in the vicinity of the detection coil unit 36B. The relay coil 100 is supported by a support column 104. The relay coil 100 has a coil body 102. The coil body 102 corresponds to a one-turn type linear coil. When such a configuration is adopted, the coupling destination selectivity or directivity in the coil body 102 can hardly be expected. Magnetic flux coming from various directions passes through the coil space. Further, in the relay coil 100, the area facing the detection coil is relatively large, and there is a concern that the Q value of the detection coil may decrease.

On the other hand, according to the embodiment shown in FIGS. 2 to 5, since the coil body of the relay coil has a tubular shape, the coil body can be provided with coupling destination selectivity or directivity. That is, it becomes possible to eliminate or reduce parasitic bonds. Further, since the coil body is in the form of a thin sheet, the area of the relay coil facing the detection coil is very small, and a decrease in the Q value of the detection coil can be prevented or reduced.

According to the experiment, in the configurations shown in FIGS. 2 to 5, when the relay coil is formed of copper foil, its length L is 5 mm, its diameter D is 3 mm, and its thickness t is 10 μm. , 16000 is obtained as the Q value of the detection coil. The detection coil was composed of an oxide high-temperature superconducting member, and its self-resonant frequency was 800 MHz. The temperature was 2K. On the other hand, in the comparative example shown in FIG. 6, when a relay coil having a number of turns of 1 and a diameter of 3 mm was formed by a silver wire having a diameter of 0.6 mm, the Q value of the detection coil was about 6000. In the comparative example, the same conditions as those in the embodiment were adopted except for the detection coil.

As described above, according to the configuration of the embodiment, a very high Q value can be obtained as the Q value of the detection coil made of the superconducting material. Further, according to the configuration of the embodiment, noise is very suppressed and a very good S / N ratio can be obtained. In particular, according to the configuration of the embodiment, even if the coupling between the detection coil and the relay coil is weakened, it is not easily affected by the parasitic coupling, and the energy efficiency can be improved in the signal transmission in both tubes.

7 to 9 show some examples of relay coil arrangements. In the first example shown in FIG. 7, the space between the pair of detection coils 40A and 40B is the internal space 90, and the other space is the external space 92. Reference numeral 30A indicates the internal space of the tube 30 (the space in which the sample tube is housed). In the first example shown in FIG. 7, the relay coil 94A is provided in the external space 92 at a position deviated below the central axis of the pair of detection coils 40A and 40B. This configuration is basically the same as the configuration shown in FIGS. 2 to 5.

In FIGS. 8 and 9, the same reference numerals are given to the same configurations as those shown in FIG. 7. In the second example shown in FIG. 8, the relay coil 94B is arranged inside 30A of the pipe 30 in the internal space 90. In the third example shown in FIG. 9, the relay coil 94C is arranged outside the pipe 30 in the internal space 90.

FIG. 10 shows a second example of the relay coil. The relay coil does not have a pair of terminals protruding from the coil body 110, and wiring is provided to both ends (both sides of the coil body 110 via a gap) of the coil body 110. FIG. 11 shows a third example of the relay coil. The cross section of the coil body 112 is elliptical. FIG. 12 shows a fourth example of the relay coil. The cross section of the coil body 114 is rectangular. The coil body 114 is provided with a pair of terminals 116. FIG. 12 shows a fifth example of the relay coil. The cross section of the coil body 118 is triangular. The coil body 118 is provided with a pair of terminals 120. FIG. 14 shows a sixth example of the relay coil. The cross section of the coil body 122 is hexagonal. The coil body 122 is provided with a pair of terminals 124. Both forms are examples. The cross section of the coil body may be C-shaped, D-shaped, or spiral. It is also conceivable to adopt a coil body having a plurality of turns. In any case, it is desirable to adopt a form of the coil body that surrounds the central axis and spreads in the direction of the central axis. Further, it is desirable that the coil body is made of a thin and wide shape, that is, a sheet-like material.

According to the above embodiment, when a relay coil that inductively couples to the detection coil is used, parasitic coupling can be prevented or reduced. In other words, a relay coil having coupling destination selectivity or directivity can be realized. Further, according to the above embodiment, the relay coil can be arranged while maintaining the good characteristics of the detection coil made of the superconducting material.

10 Control device, 12 Measuring device, 16 NMR probe, 18 Static magnetic field generator, 36A, 36B detection coil unit, 38A, 38B substrate, 40A, 40B detection coil, 42 relay coil, 44 columns, 46 coil body, 48 terminal pairs ..

Claims (9)

A main coil that performs at least one of transmission and reception to detect a nuclear magnetic resonance signal from the measurement target,
A relay coil as a sub coil that is inductively coupled to the main coil,
Including
The relay coil includes a coil body and includes a coil body.
The coil body extends in the direction of its central axis and has a form surrounding the central axis.
A probe for measuring nuclear magnetic resonance. In the probe according to claim 1,
The coil body is composed of a sheet-shaped conductive member that surrounds the central axis.
A probe for measuring nuclear magnetic resonance. In the probe according to claim 1,
The coil body has a tubular shape.
A probe for measuring nuclear magnetic resonance. In the probe according to claim 3,
The cross section of the coil body orthogonal to the central axis is circular, elliptical, or polygonal.
A probe for measuring nuclear magnetic resonance. In the probe according to claim 1,
The relay coil includes a terminal pair connected to the coil body.
A probe for measuring nuclear magnetic resonance. In the probe according to claim 5,
The coil body and the terminal pair are composed of a single member.
The coil body has a first end and a second end facing each other through a slit parallel to the central axis.
The terminal pair comprises a first terminal extending from the first end and a second terminal extending alongside the first terminal from the second end.
A probe for measuring nuclear magnetic resonance. In the probe according to claim 1,
The relay coil has a first opening and a second opening.
The first opening faces the main coil,
A probe for measuring nuclear magnetic resonance. In the probe according to claim 1,
The main coil is made of a superconducting material.
A probe for measuring nuclear magnetic resonance. It includes a relay coil body that inductively couples to a main coil made of a superconducting material that performs at least one of transmission and reception to detect a nuclear magnetic resonance signal from a measurement target.
The relay coil body is made of a tubular metal foil.
A relay coil for nuclear magnetic resonance measurement.

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