Patent Application
20250072805
One aspect of the embodiment relates to a brain measurement apparatus.
A photoexcitation magnetic sensor capable of measuring a weak external magnetic field is known (see, for example, U.S. Patent Publication No. 2022/0091200 and U.S. Pat. No. 10,782,368). In the photoexcitation magnetic sensor, alkali metal atoms in a cell are excited by pump light, probe light irradiated toward the cell so as to intersect the pump light is measured by an optical sensor, and an intensity of the external magnetic field is detected based on an output of the optical sensor.
The inventors of the present application have studied an apparatus capable of measuring a brain magnetic field and acquiring a brain morphological image by fusing a conventional photoexcitation magnetic sensor as described above and a magnetic resonance imaging (MRI) apparatus. In order to realize an apparatus in which the photoexcitation magnetic sensor and the MRI apparatus are fused, it is desirable that the accuracy of two types of measurement be maintained without the measurement by the MRI apparatus affecting the accuracy of the measurement by the photoexcitation magnetic sensor.
Therefore, one aspect of the embodiment has been made in view of such a problem, and an object thereof is to provide a brain measurement apparatus that realizes measurement of a brain magnetic field and acquisition of a brain morphological image with high accuracy.
A brain measurement apparatus according to a first aspect of the embodiment includes: a magnetoencephalograph having: a cell in which alkali metal vapor is filled, a pump laser configured to emit pump light for exciting alkali metal atoms constituting the alkali metal vapor, a probe laser configured to emit probe light for detecting a change in electron spin in an excited state of the alkali metal atoms to a sensitivity region intersecting the pump light in the cell, an optical sensor configured to detect a polarization plane angle of the probe light having passed through the sensitivity region, and a bias magnetic field coil configured to apply a bias magnetic field in a same direction as the pump light and determine a resonance frequency of the electron spin; and an MRI apparatus having: a static magnetic field coil for applying a static magnetic field, a gradient magnetic field coil for applying a gradient magnetic field, a transmission coil for transmitting a transmission pulse of a predetermined frequency, and a receiver coil configured to detect a nuclear magnetic resonance signal generated by transmission of the transmission pulse, and the magnetoencephalograph and the MRI apparatus are surrounded by a magnetic shield including a soft magnetic material.
According to the first aspect, the pump light is emitted in a state where the bias magnetic field is applied to the cell filled with an alkali metal, whereby the electron spins of the alkali metal atoms are generated (excited). Further, the probe light is emitted to the sensitivity region intersecting the pump light in the cell, the polarization plane angle of the probe light having passed through the sensitivity region is detected by the optical sensor, and an intensity of the brain magnetic field in the sensitivity region can be measured based on the detected polarization plane angle. In addition, according to the first aspect, the static magnetic field and the gradient magnetic field are applied by the static magnetic field coil and the gradient magnetic field coil, and the nuclear magnetic resonance signal generated by transmission of the transmission pulse is detected by the receiver coil, whereby a brain morphological image (MR image) can be measured. Here, in the brain measurement apparatus according to the first aspect, the magnetoencephalograph and the MRI apparatus are surrounded by the magnetic shield. This magnetic shield has properties of relatively high magnetic permeability and relatively low coercive force. Therefore, the influence of the environmental magnetic field at the time of measurement can be reduced, and the magnetic shield can be prevented from being magnetized at the time of measuring the brain magnetic field by the static magnetic field applied at the time of measuring the MR image. As a result, both the measurement of the brain magnetic field and the acquisition of the brain morphological image can be realized with high accuracy.
In the first aspect, it is preferable that the soft magnetic material is a material having a relative magnetic permeability of 1 or more and a coercive force smaller than that of a ferromagnetic material. In this case, both the measurement of the brain magnetic field and the acquisition of the brain morphological image can be realized more accurately.
Further, in the first aspect, it is also preferable that the soft magnetic material is an amorphous magnetic material. In this case, both the measurement of the brain magnetic field and the acquisition of the brain morphological image can be realized more accurately.
Furthermore, in the first aspect, it is also preferable that the soft magnetic material is a nanocrystalline magnetic material. In this case, both the measurement of the brain magnetic field and the acquisition of the brain morphological image can be realized more accurately.
Furthermore, in the first aspect, it is also preferable that the magnetoencephalograph further has tilting device for tilting a direction of the electron spin in a direction perpendicular to the pump light. In this case, by measuring the intensity of the brain magnetic field based on the frequency of the change in the polarization plane angle of the detected probe light, the measurement sensitivity of the brain magnetic field can be maintained without being affected by an environmental magnetic field.
In addition, in the first aspect, it is preferable that the magnetoencephalograph has two or more sensitivity regions where the pump light and the probe light intersect with each other, and measures the brain magnetic field based on a difference between outputs of the optical sensors corresponding to two adjacent sensitivity regions. In this case, by using the difference between the outputs of the optical sensors corresponding to the two adjacent sensitivity regions, common mode noise common to the two sensitivity regions is removed, and the measurement of the weak brain magnetic field can be realized.
Furthermore, in the first aspect, it is also preferable that the tilting device irradiates an RF pulse having a same frequency as the resonance frequency. In this case, the measurement of the brain magnetic field based on the frequency of the change in the polarization plane angle of the probe light can be realized by simple means.
Furthermore, in the first aspect, it is also preferable that the tilting device irradiates pulsed light. In this way, the measurement of the brain magnetic field based on the frequency of the change in the polarization plane angle of the probe light can be realized by simple means.
In the first aspect, it is preferable that the static magnetic field coil is configured by the same coil as the bias magnetic field coil. In this case, the bias magnetic field and the static magnetic field can be stably applied by the commonly used coil, and stable measurement can be realized by a miniaturized apparatus.
Furthermore, in the first aspect, it is also preferable that the gradient magnetic field coil corrects the gradient of the bias magnetic field at the time of measuring the brain magnetic field. As a result, the gradient of the bias magnetic field can be corrected at the time of measuring the brain magnetic field by the gradient magnetic field coil, and stable measurement of the brain magnetic field can be realized.
A brain measurement apparatus according to an embodiment is [1] “a brain measurement apparatus including:
The brain measurement apparatus according to the embodiment may be [2] “the the brain measurement apparatus described in [1] above, in which
The brain measurement apparatus according to the embodiment may be [3] “the brain measurement apparatus described in [2] above, in which
The brain measurement apparatus according to the embodiment may be [4] “the brain measurement apparatus described in [3] above, in which
The brain measurement apparatus according to the embodiment may be [5] “the brain measurement apparatus described in any of [1] to [4] above, in which
The brain measurement apparatus according to the embodiment may be [6] “the brain measurement apparatus described in any of [1] to [5] above, in which
The brain measurement apparatus according to the embodiment may be [7] “the brain measurement apparatus described in [5] above, in which
The brain measurement apparatus according to the embodiment may be [8] “the brain measurement apparatus described in [5] above, in which
The brain measurement apparatus according to the embodiment may be [9] “the brain measurement apparatus described in any of [1] to [8] above, in which
The brain measurement apparatus according to the embodiment may be [10] “the brain measurement apparatus described in any of [1] to [9] above, in which
Hereinafter, an embodiment of the present invention will be described in detail with reference to the accompanying drawings. In the description, the same reference numeral is used for the same component or a component having the same function, and redundant description is omitted.
In the following description, a direction approximately parallel to a central axis of a head of the subject is defined as a y-axis direction, and directions perpendicular to the y-axis and perpendicular to each other are defined as a z-axis direction and an x-axis direction. In the following description, a positive direction and a negative direction along the x-axis are referred to as a +x-axis direction and a −x-axis direction, respectively, a positive direction and a negative direction along the y-axis are referred to as a +y-axis direction and a −y-axis direction, respectively, and a positive direction and a negative direction along the z-axis are referred to as a +z-axis direction and a −z-axis direction, respectively.
The nonmagnetic frame 104 is a frame covering the entire region of a scalp of the subject to be measured for the brain magnetic field, and is made of a nonmagnetic material such as graphite having a relative magnetic permeability close to 1 and not disturbing magnetic field distribution. The nonmagnetic frame 104 can be, for example, a helmet-type frame that surrounds the entire scalp of the subject and is attached on the head of the subject. A plurality of photoexcitation magnetic sensors 1 and 1A are fixed to the nonmagnetic frame 104 so as to be close to the scalp of the subject. Furthermore, the receiver coils 122 for detecting a nuclear magnetic resonance signal for MR image measurement are fixed on the opposite side of the plurality of photoexcitation magnetic sensors 1 and 1A to the scalp of the subject in the nonmagnetic frame 104. The receiver coil 122 detects a nuclear magnetic resonance signal of a proton to be described later and converts it into a current.
The plurality of photoexcitation magnetic sensors 1A are disposed at predetermined intervals around the y-axis so as to surround the head near the top of the head of the subject, for example. The plurality of photoexcitation magnetic sensors 1 are disposed at predetermined intervals around the y-axis so as to surround the head away from the photoexcitation magnetic sensors 1A in the −y-axis direction.
As illustrated in
The cell 2 is a container that is filled with alkali metal vapor. The cell 2 is disposed along the direction along the x-axis. The cell 2 has a substantially rectangular parallelepiped shape having a plane substantially parallel to an xy plane and a bottomed cylindrical shape. The cross section of the cell 2 in a direction perpendicular to a longitudinal direction of the cell 2 (direction along a yz plane) is, for example, a square. The cell 2 may be made of a material such as quartz, sapphire, silicon, Kovar glass, or borosilicate glass, for example. The cell 2 has optical transparency with respect to pump light and probe light to be described later. The heater 3 and the like are attached to a side surface of the cell 2 in the −z-axis direction. A magnetic field Bm to be measured generated from a measurement target is incident on the side surface of the cell 2 in the −z-axis direction along the +z-axis direction.
The alkali metal constituting the alkali metal vapor filled in the cell 2 may be, for example, at least one or more type of lithium (Li), sodium (Na), potassium (K), rubidium (Rb), and cesium (Cs). For example, the alkali metal may be potassium and rubidium, or may be only potassium. Potassium has a relatively low spin-destruction collision relaxation rate among alkali metals used in photoexcitation magnetic sensors. The spin-destruction collision relaxation rate of potassium is smaller than, for example, cesium and rubidium. Therefore, when a single alkali metal is adopted, the photoexcitation magnetic sensor using only potassium has higher sensitivity than the photoexcitation magnetic sensor using only cesium or only rubidium.
In addition, the cell 2 contains filling gas. The filling gas suppresses relaxation of the spin polarization of the alkali metal vapor. The filling gas also protects alkali metal vapor and suppresses noise emission. The filling gas may be, for example, an inert gas such as helium (He), neon (Ne), argon (Ar), krypton (Kr), xenon (Xe), or nitrogen (N2). The filling gas may be, for example, helium and nitrogen.
As described above, the heater 3 is attached to the cell 2. The heater 3 generates heat according to a current supplied from a heater power supply (not illustrated). The heater 3 controls a vapor density of the alkali metal by controlling an internal temperature of the cell 2. For example, when potassium is contained as the alkali metal in the cell 2, the heater 3 heats the cell 2 so that the internal temperature of the cell 2 becomes 100° C.
The pump laser 4 emits pump light for exciting alkali metal atoms in the −z-axis direction. That is, the pump laser 4 emits linearly polarized pump light, and the pump light is converted into circularly polarized light by the ¼ wavelength plates 27a to 27d. The alkali metal atoms contained in the cell 2 are excited by pump light in a circularly polarized state, and spin polarization is generated. A wavelength of the pump light is set according to the type of atoms constituting the alkali metal vapor (more specifically, a wavelength of an absorption line). For example, when the atom constituting the alkali metal vapor is potassium, the wavelength of the pump light is set to 770.11 nm according to a resonance line of potassium. When the alkali metal atoms contained in the cell 2 are potassium and rubidium, the pump laser 4 may emit pump light for exciting the atoms of rubidium and transferring the spin polarization of the atom of rubidium to the atom of potassium. In this case, the atom of rubidium is excited by the pump light. Then, due to a spin exchange interaction between potassium and rubidium, the spin polarization of the atom of rubidium is transferred to the atom of potassium, and the atom of potassium is in an excited state.
The pump light from the pump laser 4 enters the cell 2 via the first optical system 6.
The lens 21 is provided adjacent to the pump laser 4 in the −z-axis direction, and condenses the pump light emitted from the pump laser 4. The ½ wavelength plate 22 is provided adjacent to the lens 21 in the −z-axis direction, and rotates a polarization plane such that the power of the pump laser is distributed 1:3 by the polarization beam splitter 23a.
The polarization beam splitter 23a is provided adjacent to the ½ wavelength plate 22 in the −z-axis direction, separates two linearly polarized light components perpendicular to each other from the polarized light component of the pump light transmitted through the ½ wavelength plate 22, transmits one linearly polarized light component in the −z-axis direction, and reflects the other linearly polarized light component in the −x-axis direction. The polarization beam splitters 23b and 23c and the total reflection mirror 25 are provided side by side in order in the −x-axis direction with respect to the polarization beam splitter 23a. The polarization beam splitters 23b and 23c separate two linearly polarized light components perpendicular to each other from the pump light transmitted through the polarization beam splitters 23a and 23b, respectively, transmit one linearly polarized light component in the −x-axis direction, and reflect the other linearly polarized light component in the −z-axis direction. The total reflection mirror 25 reflects the linearly polarized pump light transmitted through the polarization beam splitter 23c in the −z-axis direction.
The ½ wavelength plate 24a is provided between the polarization beam splitter 23a and the polarization beam splitter 23b, and rotates the polarization plane of the linearly polarized pump light reflected by the polarization beam splitter 23a. Thus, the pump light can be separated into two linearly polarized light components by the polarization beam splitter 23b. The ½ wavelength plate 24b is provided between the polarization beam splitter 23b and the polarization beam splitter 23c, and rotates the polarization plane of the linearly polarized pump light transmitted through the polarization beam splitter 23b. Thus, the pump light can be separated into two linearly polarized light components by the polarization beam splitter 23c.
The polarizer 26a and the ¼ wavelength plate 27a are provided adjacent to the polarization beam splitter 23a in order in the −z-axis direction. The polarizer 26a transmits a specific linearly polarized light component of the pump light transmitted through the polarization beam splitter 23a, and the ¼ wavelength plate 27a changes the polarization state of the pump light transmitted through the polarizer 26a to circularly polarized light and transmits the circularly polarized light as pump light PLa in the −z-axis direction.
The polarizers 26b, 26c, and 26d and the ¼ wavelength plates 27b, 27c, and 27d are provided adjacent to the polarization beam splitters 23b and 23c and the total reflection mirror 25 in order in the −z-axis direction, respectively. The functions of the polarizers 26b, 26c, and 26d and the ¼ wavelength plates 27b, 27c, and 27d are the same as those of the polarizer 26a and the 1/4 wavelength plate 27a, respectively, and transmit pump lights PLb, PLc, and PLd in the −z-axis direction.
The first optical system 6 having the above configuration is configured such that four systems of pump lights PLa to PLd transmitting through the four ¼ wavelength plates 27a, 27b, 27c, and 27d can be incident on regions separated in a longitudinal direction (direction along the x-axis) in the cell 2.
The probe laser 5 emits, in the −y-axis direction, probe light for detecting precession motion of spin when the electron spin in the excited state of the alkali metal atom is tilted by 90 degrees. That is, the probe laser 5 emits linearly polarized probe light. When the probe light passes through the alkali metal vapor, a magneto-optical rotation angle changes under the influence of the state of spin polarization of the alkali metal atom. By detecting the change in the magneto-optical rotation angle, the state of the precession motion of the spin can be derived. The wavelength of the probe light is set according to the type of atoms constituting the alkali metal vapor (more specifically, the wavelength of the absorption line). For example, when only potassium is contained as the alkali metal in the cell 2, the wavelength of the probe light is detuned from the wavelength of the pump light (for example, 770.11 nm), and is set to, for example, about 770.05 nm. Since the wavelength of the probe light is detuned from the wavelength of the pump light, absorption of the probe light by potassium is suppressed.
When potassium and rubidium are contained in the cell 2 as the alkali metals, the probe laser 5 may emit probe light for detecting the change in the magneto-optical rotation angle caused by the spin polarization in the excited state of the atom of potassium. A density of rubidium used for excitation is set to be smaller than a density of potassium used for the probe. When the density of rubidium is smaller than the density of potassium, attenuation of pump light due to excitation is suppressed. Thus, the photoexcitation magnetic sensor 1 can obtain uniform sensitivity in the cell 2.
Probe light from the probe laser 5 enters the cell 2 via the second optical system 7.
The ½ wavelength plate 31a is provided adjacent to the probe laser 5 in the −x-axis direction, and rotates the polarization plane such that the power of the probe laser is distributed 1:3 by the polarization beam splitter 32a. The polarization beam splitters 32a, 32b, and 32c are provided side by side in order in the −x-axis direction with respect to the ½ wavelength plate 31a, separate two linearly polarized light components perpendicular to each other from the polarized light component of the probe light transmitted through the ½ wavelength plate 31a, transmit one linearly polarized light component in the −x-axis direction, and reflect the other linearly polarized light component in the −y-axis direction. The ½ wavelength plate 31b is provided between the polarization beam splitter 32a and the polarization beam splitter 32b, and rotates the polarization plane of the linearly polarized probe light transmitted through the polarization beam splitter 32a. Thus, the probe light can be separated into two linearly polarized light components by the polarization beam splitter 32b. The ½ wavelength plate 31c is provided between the polarization beam splitter 32b and the polarization beam splitter 32c, and rotates the polarization plane of the linearly polarized probe light transmitted through the polarization beam splitter 32b. Thus, the probe light can be separated into two linearly polarized light components by the polarization beam splitter 32c. The total reflection mirror 33 reflects the linearly polarized probe light transmitted through the polarization beam splitter 32c in the −y-axis direction.
The polarizers 34a, 34b, 34c, and 34d transmit specific linearly polarized light components of the probe light reflected by the polarization beam splitters 32a, 32b, and 32c and the total reflection mirror 33, respectively.
The second optical system 7 having the above configuration is configured such that four systems of probe lights QLa to QLd transmitting through the four polarizers 34a, 34b, 34c, and 34d can be incident on the sensitivity regions ARa to ARd intersecting the pump lights PLa to PLd arranged in the longitudinal direction (direction along the x-axis) in the cell 2, respectively.
Referring to
The bias magnetic field gradient correction coils 12 and 13 are a coil group for correcting a gradient of the bias magnetic field Bz in a direction along the y-axis, a direction along the z-axis, or a direction along the x-axis. The bias magnetic field gradient correction coils 12 and 13 may be configured to include a coil group that corrects gradients in one or two directions of the direction along the y-axis, the direction along the z-axis, and the direction along the x-axis in the bias magnetic field Bz, or may be configured to include a coil group that corrects gradients in three directions. Due to the presence of the bias magnetic field gradient correction coils 12 and 13, even when the bias magnetic field Bz is not uniform due to the influence of an environmental magnetic field or the like, it is possible to perform correction so as to be uniform, and it is possible to enhance the detection sensitivity of the photoexcitation magnetic sensor 1 with respect to the brain magnetic field. As will be described later, the bias magnetic field gradient correction coils 12 and 13 are also shared as the gradient magnetic field coil used at the time of measuring the MR image by the MRI module.
Here, the bias magnetic field gradient correction coils 12 and 13 will be specifically described.
As illustrated in
As illustrated in
The first to third coils 13A, 12A, and 13B are coils that correct a first-order gradient magnetic field. Note that the first to third coils 13A, 12A, and 13B may be coils that further correct a second-order gradient magnetic field, and in this case, the uniformity of the bias magnetic field Bz can be further improved. Arrows illustrated in the first to third coils 13A, 12A, and 13B in
The tilting coil 14 (see
Referring back to
The third optical system 9 includes ½ wavelength plates 41a, 41b, 41c, and 41d and polarization beam splitters 42a, 42b, 42c, and 42d. The ½ wavelength plates 41a, 41b, 41c, and 41d are provided adjacent to the cell 2 in the −y-axis direction on optical paths of the probe lights QLa, QLb, QLc, and QLd having passed through the sensitivity regions ARa to ARd of the cell 2, respectively, and rotate the polarization planes of the linearly polarized light of the probe lights QLa, QLb, QLc, and QLd having passed through the cell 2. These ½ wavelength plates 41a, 41b, 41c, and 41d are rotatably supported about the axis along the y-axis so that the rotation angle of the polarization plane of the probe light can be adjusted. The polarization beam splitters 42a, 42b, 42c, and 42d separate two linearly polarized light components perpendicular to each other from the polarized light components of the probe lights QLa, QLb, QLc, and QLd transmitted through the ½ wavelength plates 41a, 41b, 41c, and 41d, respectively, transmit one linearly polarized light component in the −y-axis direction, and reflect the other linearly polarized light component in the z-axis direction.
The optical sensor group 8 is an element group that detects polarization plane angles of the probe lights QLa, QLb, QLc, and QLd having passed through the sensitivity regions ARa to ARd, and includes four optical sensor pairs 43a, 43b, 43c, and 43d. The optical sensor pair 43a includes two photodiodes 44a and 45a, the photodiode 44a outputs a detection signal obtained by detecting the intensity of the other linearly polarized light component of the probe light QLa, and the photodiode 45a outputs a detection signal obtained by detecting the intensity of one linearly polarized light component of the probe light QLa. Similarly, the optical sensor pair 43b, 43c, and 43d have two photodiodes 44b and 45b, two photodiodes 44c and 45c, and two photodiodes 44d and 45d, respectively. The two photodiodes 44b and 45b respectively output detection signals obtained by detecting intensities of two linearly polarized light components of the probe light QLb, the two photodiodes 44c and 45c respectively output detection signals obtained by detecting intensities of two linearly polarized light components of the probe light QLc, and the two photodiodes 44d and 45d respectively output detection signals obtained by detecting two linearly polarized light components of the probe light QLd.
Referring again to
The readout circuit 10 physically includes a memory such as a RAM and a ROM, a processor (arithmetic circuit) such as a CPU, a communication interface, and an auxiliary storage device such as a hard disk and a semiconductor memory. The readout circuit 10 can be realized by, for example, a personal computer, a cloud server, a smartphone, a tablet terminal, or the like. The function of the readout circuit 10 is realized by executing a program stored in the memory by the CPU of the computer system.
The function of the measurement processing of the brain magnetic field by the measurement unit of the readout circuit 10 will be described with reference to
At the time of the measurement processing of the brain magnetic field by the readout circuit 10, control is performed by a control circuit (not illustrated) such that irradiation is performed such that the pump light is repeatedly turned on/off in a pulse shape (
The FID indicates how the electron spin of the alkali metal atom is relaxed, and the frequency of the precession motion of the electron spin changes according to the variation in the brain magnetic field in the sensitivity region ARa, so that the frequency of the vibration changes according to the variation in the brain magnetic field. For example, when the resonance frequency of the electron spin is 100 kHz and the brain magnetic field changes from 0 pT to 1 pT, the frequency of the precession motion changes about 0.007 Hz. By using such a property, the readout circuit 10 derives, with respect to the waveform of the FID at the initial stage of the relaxation time, a frequency a1 of vibration of the FID, by performing fitting using a function V as shown in the following formula;
V=a
0 sin (2πa1 (t−a2))e−a
(in the above formula, t indicates a time, and a0, a1, and a2 indicate predetermined parameters), and the frequency a1 is acquired as a measurement value of the brain magnetic field in the sensitivity region ARa. Similarly, the readout circuit 10 acquires measurement values of the brain magnetic field in the sensitivity regions ARb, ARc, and ARd based on the detection signals output from the optical sensor pairs 43b, 43c, and 43d. Furthermore, the readout circuit 10 can acquire time-series data of the measurement values by repeating this operation at a frequency of 100 to 1000 Hz.
Next, a configuration of the photoexcitation magnetic sensor 1A will be described with reference to
The first optical system 6 includes a lens 21, a ½ wavelength plate 22, a polarization beam splitter 23a, and a ¼ wavelength plate 27a. The polarization beam splitter 23a is provided adjacent to the ½ wavelength plate 22 in the −y-axis direction, and reflects the linearly polarized light component in the pump light transmitted through the ½ wavelength plate in the −z-axis direction. The ¼ wavelength plate 27a is provided adjacent to the polarization beam splitter 23a in the −z-direction, changes the linearly polarized pump light reflected by the polarization beam splitter 23a into circularly polarized light, and transmits the pump light in the −z-axis direction. The first optical system 6 having the above configuration is configured such that one system of pump light can be incident in the longitudinal direction (direction along the z-axis) in the cell 2.
The second optical system 7 includes a lens 35, a ½ wavelength plate 36, and a total reflection mirror 37 in addition to the ½ wavelength plates 31a, 31b, and 31c, the polarization beam splitters 32a, 32b, and 32c, the total reflection mirror 33, and the polarizers 34a, 34b, 34c, and 34d. The lens 35 is provided adjacent to the probe laser 5 in the −y-axis direction, and condenses the probe light emitted from the probe laser 5 in the −y-axis direction. The total reflection mirror 37 is provided adjacent to the lens 35 in the −y-axis direction, and reflects the probe light transmitted through the lens 35 toward the ½ wavelength plate 31a in the −z-axis direction. The second optical system 7 having such a configuration is configured such that each of the four systems of the probe lights QLa to QLd transmitted through the four polarizers 34a, 34b, 34c, and 34d can be incident on the four sensitivity regions intersecting the pump light PL arranged in the longitudinal direction (direction along the x-axis) in the cell 2.
Returning back to
The static magnetic field coil configuring the MRI module is configured by the same coil as the bias magnetic field coil 11 described above. The bias magnetic field coil 11 applies a static magnetic field in the z-axis direction at the time of measuring the MR image. The bias magnetic field coil 11 is switchably connected to either the MRI power supply 106 or the bias magnetic field power supply 107 via the switch 105. At the time of measuring the MR image, the bias magnetic field coil 11 is connected to the MRI power supply 106 under the control of the control device 109, thereby generating a static magnetic field having a predetermined intensity according to the current supplied from the MRI power supply 106. The bias magnetic field coil 11 is connected to the bias magnetic field power supply 107 under the control of the control device 109 at the time of measuring the brain magnetic field, thereby generating a bias magnetic field having a predetermined intensity according to the current supplied from the bias magnetic field power supply 107. As a result, even in a case where the intensity of the bias magnetic field (for example, 14 μT) and the intensity of the static magnetic field (for example, 7 mT) are greatly different, it is possible to stably perform the MR image measurement and the brain magnetic field measurement by sharing the coils having the same number of turns.
The gradient magnetic field coil configuring the MRI module is configured by the same coil as the bias magnetic field gradient correction coils 12 and 13 described above. The bias magnetic field gradient correction coils 12 and 13 apply a gradient magnetic field at the time of measuring the MR image. The bias magnetic field gradient correction coils 12 and 13 generate a gradient magnetic field having a gradient selective to the x-axis direction, the y-axis direction, and the z-axis direction according to the current supplied from the gradient correction power supply 108. The gradient correction power supply 108 supplies a current for gradient correction of the bias magnetic field Bz to the bias magnetic field gradient correction coils 12 and 13 at the time of measuring the brain magnetic field.
The transmission coil 121 is a coil that irradiates (transmits) the head of the subject with an RF pulse (transmission pulse) of a predetermined frequency (for example, about 300 kHz) at the time of measuring the MR image. The transmission coil 121 is disposed, for example, above the head of the subject outside the nonmagnetic frame 104.
The reception amplifier 124 is electrically connected to both ends of the receiver coil 122 via a cable, detects the current output from the receiver coil 122, amplifies the detection result, and outputs the amplified detection result to the control device 109.
The control device 109 controls power supplied to various types of coils at the time of measuring the brain magnetic field and at the time of measuring the MR image, and executes measurement processing of the MR image. The control device 109 is electrically connected to the switch 105, the MRI power supply 106, the bias magnetic field power supply 107, the gradient correction power supply 108, a power supply (not illustrated) for the transmission coil 121, the reception amplifier 124, and the like. The control device 109 physically includes a memory such as a RAM and a ROM, a processor (arithmetic circuit) such as a CPU, a communication interface, and an auxiliary storage device such as a hard disk and a semiconductor memory. The control device 109 can be realized by, for example, a personal computer, a cloud server, a smartphone, a tablet terminal, or the like. The function of the control device 109 is realized by executing a program stored in the memory by the CPU of the computer system.
Specifically, the control device 109 controls switching of the switch 105 between the time of measuring the brain magnetic field and the time of measuring the MR image, connects the bias magnetic field coil 11 and the bias magnetic field power supply 107 at the time of measuring the brain magnetic field, and connects the bias magnetic field coil 11 and the MRI power supply 106 at the time of measuring the MR image. Furthermore, at the time of measuring the MR image, the control device 109 determines currents to be supplied to the bias magnetic field coil 11 and the bias magnetic field gradient correction coils 12 and 13 that operate as coils for applying a static magnetic field and a gradient magnetic field, respectively, and outputs a control signal for outputting the currents to the MRI power supply 106 and the gradient correction power supply 108. That is, the control device 109 determines a current flowing through the bias magnetic field coil 11 so as to apply a magnetic field, as a static magnetic field, in the z-axis direction having a predetermined intensity (for example, 7 mT) to the head of the subject. In addition, the control device 109 selectively determines an x-axis direction magnetic field gradient, a y-axis direction magnetic field gradient, and a z-axis direction magnetic field gradient as the gradient magnetic field, and determines a current flowing through the bias magnetic field gradient correction coils 12 and 13. As a result, it is possible to determine a position to be sliced in the MR image and encode the position in the slice plane by phase encoding and frequency encoding.
In addition, the control device 109 determines the currents to be supplied to the bias magnetic field coil 11 and the bias magnetic field gradient correction coils 12 and 13, and outputs a control signal for outputting the currents to the bias magnetic field power supply 107 and the gradient correction power supply 108 at the time of measuring the brain magnetic field. That is, the control device 109 determines the current flowing through the bias magnetic field coil 11 so as to apply a magnetic field, as the bias magnetic field Bz, in the z-axis direction having a predetermined intensity (for example, 14 μT). In addition, the control device 109 determines a current to be supplied to the bias magnetic field gradient correction coils 12 and 13 in order to correct the gradient of the bias magnetic field Bz in the direction along the x-axis, the direction along the y-axis, or the direction along the z-axis.
Furthermore, at the time of measuring the MR image, the control device 109 performs control to irradiate the head of the subject with an RF pulse of a predetermined frequency (for example, about 300 kHz when the intensity of the static magnetic field is 7 mT) by controlling power supplied to the transmission coil 121. As a result, protons of the slice plane (the plane selected by the static magnetic field and the gradient magnetic field) resonate and the spin tilts. Thereafter, the control device 109 controls the power of the transmission coil 121 to be turned off. As a result, the MR image can be acquired by measuring the state in which the spin returns based on the output of the reception amplifier 124. More specifically, the control device 109 measures a nuclear magnetic resonance signal from the protons by encoding a position by a frequency and a phase using a known spin echo sequence, a gradient echo sequence, or the like, and converts the measurement result into an MR image using FFT.
The electromagnetic shield 114 is a shield member that shields high frequency (for example, 10 kHz or more) electromagnetic noise, and is made of, for example, a mesh interwoven with metallic threads, a non-magnetic metal plate such as aluminum, or the like. The electromagnetic shield 114 is disposed so as to surround the photoexcitation magnetic sensors 1 and 1A, the transmission coil 121, the receiver coil 122, the reception amplifier 124, the nonmagnetic frame 104, the bias magnetic field coil 11, the bias magnetic field gradient correction coils 12 and 13, and the tilting coil 14. The electromagnetic shield 114 can prevent noise in the 300 kHz band, which is a measurement frequency, from entering the receiver coil 122 and increasing at the time of measuring the MR image. In addition, it is possible to prevent the high-frequency noise from entering the photoexcitation magnetic sensors 1 and 1A at the time of measuring the brain magnetic field and the operation from becoming unstable.
The magnetic shield 115 is a shield member for reducing mixing of magnetic noise of a low frequency of 100 Hz or less corresponding to brain magnetism, and includes, for example, a high-permeability magnetic material formed of a soft magnetic material. The high-permeability magnetic material constituting the magnetic shield 115 is preferably a material having a relative magnetic permeability of 1 or more and a coercive force smaller than that of the ferromagnetic material. For example, the high-permeability magnetic material is preferably an amorphous magnetic material, and more preferably a nanocrystalline magnetic material. For example, the magnetic shield 115 has a laminated structure including a plurality of layers of the sheet of the high-permeability magnetic material and a conductive film made of aluminum. The magnetic shield 115 is disposed so as to surround, from the outside of the electromagnetic shield 114, the magnetoencephalograph module including the photoexcitation magnetic sensors 1 and 1A, the nonmagnetic frame 104, the bias magnetic field coil 11, the bias magnetic field gradient correction coils 12 and 13, and the tilting coil 14, and the MRI module including the transmission coil 121, the receiver coil 122, and the reception amplifier 124. With the magnetic shield 115, it is possible to improve the S/N at the time of measuring the brain magnetic field. Furthermore, the geomagnetism generated by direct current can be reduced to about ⅕ of the intensity, the current supplied to the bias magnetic field gradient correction coils 12 and 13 can be reduced to about ⅕, the current consumption of the entire apparatus can be reduced, and the gradient magnetic field noise intensity caused by the noise generated by the gradient correction power supply 108 can be reduced to ⅕.
Next, a brain measurement method using the brain measurement apparatus M1 according to the embodiment will be described with reference to
First, when the measurement of the brain magnetic field is started with the nonmagnetic frame 104 attached to the subject, the control device 109 connects the bias magnetic field coil 11 and the bias magnetic field power supply 107 (step S1). Next, the control device 109 determines a current to be supplied to the bias magnetic field coil 11 for applying a bias magnetic field, and outputs a control signal to the bias magnetic field power supply 107 to control generation of the bias magnetic field by the bias magnetic field coil 11 (step S2). In addition, the control device 109 determines a current to be supplied to the bias magnetic field gradient correction coils 12 and 13 for gradient correction of the bias magnetic field, and outputs a control signal to the gradient correction power supply 108 to control correction of the gradient of the bias magnetic field by the bias magnetic field gradient correction coils 12 and 13 (step S3). In this state, the readout circuit 10 acquires measurement values of the brain magnetic field in a plurality of sensitivity regions of each of the photoexcitation magnetic sensors 1 and 1A in time series (step S4). The readout circuit 10 outputs the acquired time-series measurement values to a predetermined output destination. The predetermined output destination may be an external device such as a terminal device connected via a communication interface in addition to the memory of the readout circuit 10, a storage device such as a hard disk, and an output device such as a display.
Referring to
Furthermore, the control device 109 determines a current to be supplied to the bias magnetic field gradient correction coils 12 and 13 for generating the gradient magnetic field, and outputs a control signal to the gradient correction power supply 108, thereby controlling generation of an x-axis direction magnetic field gradient on the slice plane (step S9). As a result, phase encoding is performed. Then, the control device 109 determines a current to be supplied to the bias magnetic field gradient correction coils 12 and 13 for generating the gradient magnetic field, and outputs a control signal to the gradient correction power supply 108 to control generation of a y-axis direction magnetic field gradient on the slice plane (step S10). As a result, frequency encoding is performed.
At the same time, a detection signal of a nuclear magnetic resonance signal from protons is output via the receiver coil 122 and the reception amplifier 124, and accordingly, the control device 109 acquires data of the nuclear magnetic resonance signal (step S11). Thereafter, the control device 109 determines whether to acquire the nuclear magnetic resonance signal data related to another slice plane (step S12). As a result of the determination, when the nuclear magnetic resonance signal data related to another slice plane is acquired (“YES” in step S12), the processing returns to step S7. On the other hand, when the nuclear magnetic resonance signal data related to another slice plane is not acquired (“NO” in step S12), an MR image is acquired by performing Fourier transform on the nuclear magnetic resonance signal data acquired so far (step S13). The control device 109 outputs the acquired MR image to a predetermined output destination. The predetermined output destination may be an external device such as a terminal device connected via a communication interface in addition to a memory of the control device 109, a storage device such as a hard disk, and an output device such as a display.
According to the brain measurement apparatus M1 described above, the electron spin of the alkali metal atom is generated (excited) by emitting the pump light in a state where the bias magnetic field in which the gradient is corrected is applied to the cell 2 in which the alkali metal is filled. Further, the probe light is emitted to a sensitivity region intersecting the pump light in the cell 2, a polarization plane angle of the probe light having passed through the sensitivity region is detected by the optical sensor group 8, and the intensity of the brain magnetic field in the sensitivity region can be measured based on the detected polarization plane angle. In addition, according to the brain measurement apparatus M1, a static magnetic field and a gradient magnetic field are applied by the bias magnetic field coil 11 and the bias magnetic field gradient correction coils 12 and 13, and a nuclear magnetic resonance signal generated by transmission of the RF pulse is detected by the receiver coil 122, whereby a brain morphological image (MR image) can be measured.
Here, in the brain measurement apparatus M1, the magnetoencephalograph module and the MRI module are surrounded by the magnetic shield 115. This magnetic shield 115 has properties of relatively high magnetic permeability and relatively low coercive force. Therefore, the influence of the environmental magnetic field at the time of measuring the brain magnetic field can be reduced, and the magnetic shield 115 can be prevented from being magnetized at the time of measuring the brain magnetic field by the static magnetic field applied at the time of measuring the MR image. As a result, both the measurement of the brain magnetic field and the acquisition of the MR image can be realized with high accuracy.
In the brain measurement apparatus M1, the soft magnetic material included in the magnetic shield 115 has a relative magnetic permeability of 1 or more and a coercive force smaller than that of the ferromagnetic material. In this case, both measurement of the brain magnetic field and acquisition of the MR image can be realized more accurately. In a case where a shield material containing iron that is generally used is used as a magnetic shield, when a brain magnetic field is measured after MR image measurement, the magnetic shield is magnetized, and the photoexcitation magnetic sensors 1 and 1A do not operate normally. On the other hand, in the present embodiment, the magnetization of the magnetic shield by the measurement of the MR image can be avoided, and the influence of the geomagnetism or the environmental magnetic field can be reduced.
In addition, in the present embodiment, the magnetoencephalograph module is provided with the tilting coil 14 which is the tilting device for tilting the direction of the electron spin in the direction perpendicular to the pump light. In this case, by measuring the intensity of the brain magnetic field based on the frequency of the change in the polarization plane angle of the detected probe light, the measurement sensitivity of the brain magnetic field can be maintained without being affected by an environmental magnetic field.
In addition, the photoexcitation magnetic sensors 1 and 1A according to the present embodiment have sensitivity regions divided into four in a direction along the longitudinal direction of the cell 2. Therefore, the common mode noise can be removed by acquiring the difference value between the measurement values of the brain magnetic field acquired for two adjacent sensitivity regions among the four divided sensitivity regions.
Furthermore, in the present embodiment, the tilting coil 14 that irradiates an RF pulse having the same frequency as the resonance frequency is provided as the tilting device. In this case, the measurement of the brain magnetic field based on the frequency of the change in the polarization plane angle of the probe light can be realized by simple means. Note that the tilting device may be a light source that irradiates pulsed light. Also in this case, the measurement of the brain magnetic field based on the frequency of the change in the polarization plane angle of the probe light can be realized by simple means.
In the present embodiment, the static magnetic field coil is configured by the same coil as the bias magnetic field coil 11. As a result, the bias magnetic field and the static magnetic field can be stably applied by the commonly used coil, and stable measurement of the brain magnetic field and the MR image can be realized.
Further, in the present embodiment, the gradient magnetic field coil is preferably configured by the same coil as the bias magnetic field gradient correction coils 12 and 13. As a result, correction of the gradient of the bias magnetic field and application of the gradient magnetic field can be stably performed by the commonly used coil, and stable measurement of the brain magnetic field and the MR image can be realized.
Although various embodiments of the present invention have been described above, the present invention is not limited to the above embodiments, and may be modified or applied to other objects without changing the gist described in each claim.
For example, the photoexcitation magnetic sensors 1 and 1A of the above embodiment have the sensitivity regions ARa to ARd divided into four, but may have any number of sensitivity regions as long as the sensitivity regions are two or more.
In addition, the photoexcitation magnetic sensor 1 of the above embodiment can also adopt a configuration of the following modification.
The photoexcitation magnetic sensor 1B includes a pump laser 4 and a first optical system 6 for causing pump light of four systems to enter regions separated in the longitudinal direction (direction along the x-axis) in the cell 2 corresponding to each of the two cells 2.
In addition, the photoexcitation magnetic sensor 1B includes the second optical system 7 as an optical system for splitting the probe light into two and causing the split probe light to enter the two cells 2. The second optical system 7 includes a lens 35, a ½ wavelength plate 36, a polarization beam splitter 38, and total reflection mirrors 37a to 37c. The polarization beam splitter 38 is provided adjacent to the ½ wavelength plate 36 in the −z-axis direction, separates two linearly polarized light components perpendicular to each other from the polarized light component of the probe light transmitted through the ½ wavelength plate 36, transmits one linearly polarized light component in the −z-axis direction, and reflects the other linearly polarized light component in the +y-axis direction. The total reflection mirror 37a reflects the linearly polarized light component of the probe light transmitted through the polarization beam splitter 38 in the −x-axis direction, and causes the linearly polarized light component to be incident on one of the cells 2 in the longitudinal direction thereof. The total reflection mirrors 37b and 37c continuously reflect the linearly polarized light component of the probe light reflected by the polarization beam splitter 38 in the −z-axis direction and the −x-axis direction and cause the component to be incident on the other cell 2 in the longitudinal direction thereof. The second optical system 7 having such a configuration is configured such that each of the two systems of probe light can be incident on four sensitivity regions intersecting the pump light arranged in the longitudinal direction (direction along the x-axis) in the cell 2.
In addition, four pairs of bias magnetic field coils 11a to 11d are provided in each of the two cells 2 included in the photoexcitation magnetic sensor 1B. These bias magnetic field coils 11a to 11d generate bias magnetic fields having different magnetic field intensities in a stepwise manner in the four sensitivity regions in the cell 2 together with the bias magnetic field coil 11. As a result, the resonance frequencies of the electron spins in the four sensitivity regions in the cell 2 can be set to different values such as 98.5 kHz, 99.5 kHz, 100.5 kHz, and 101.5 kHz. The photoexcitation magnetic sensor 1B includes two third optical
systems 9 and two optical sensor pairs 43a and 43b corresponding to the two cells 2. The third optical system 9 includes a total reflection mirror 46, a ½ wavelength plate 47, a polarization beam splitter 48, and a total reflection mirror 49. The total reflection mirror 46 reflects the probe light having passed through the cell 2 in the −x-axis direction in the +z-axis direction. The ½ wavelength plate 47 rotates the polarization plane of the probe light reflected by the total reflection mirror 46. The ½ wavelength plate 47 is supported so as to be rotatable about an axis along the z-axis so that the rotation angle of the polarization plane of the probe light can be adjusted. The polarization beam splitter 48 separates the probe light transmitted through the ½ wavelength plate 47 into two linearly polarized light components perpendicular to each other, transmits one linearly polarized light component in the +z-axis direction to be incident on the optical sensor pair 43a or the optical sensor pair 43b, and reflects the other linearly polarized light component in the +x-direction. The total reflection mirror 49 reflects the other linearly polarized light component reflected by the polarization beam splitter 48 in the +z-axis direction to be incident on the optical sensor pair 43a or the optical sensor pair 43b.
Also in the photoexcitation magnetic sensor 1B having the above configuration, by including the readout circuit 10, it is possible to execute the measurement processing of the brain magnetic field regarding eight sensitivity regions of 4×2. That is, the readout circuit 10 extracts a specific frequency band corresponding to the resonance frequency of the electron spin in the sensitivity region from the voltage signal generated based on the detection signal of each of the optical sensor pairs 43a and 43b, and acquires a measurement value of the brain magnetic field based on the voltage signal of the extracted frequency band. The readout circuit 10 can acquire measurement values corresponding to the eight sensitivity regions by repeating extraction of frequency bands and acquisition of measurement values for the eight sensitivity regions.
Also in the above modification, by acquiring the difference between the measurement values regarding the two adjacent sensitivity regions, it is possible to remove the common mode noise and enhance the detection accuracy of the brain magnetic field.
In the above embodiment and the above modification, the linearly polarized pump light is converted into the circularly polarized light, but the circularly polarized pump light may be emitted from the pump laser.
In addition, the arrangement of the photoexcitation magnetic sensors 1 and 1A in the brain measurement apparatus M1 can be variously changed.
According to the brain measurement apparatus M2 having the above configuration, it is possible to acquire a measurement value obtained by measuring a weak magnetic field from the head S. Specifically, according to the arrangement example of
Note that, in the brain measurement apparatus M2, a configuration in which the photoexcitation magnetic sensor 1 and the photoexcitation magnetic sensor 1A are arranged only at positions close to the head S and are not arranged in parallel is also applicable. In this case, by acquiring a difference between measurement values of two adjacent sensitivity regions of one of the photoexcitation magnetic sensors 1 and 1A, it is possible to measure the weak magneto-encephalogram from which the common mode noise has been removed.
| Number | Date | Country | Kind |
|---|---|---|---|
| 2023-143517 | Sep 2023 | JP | national |
