WO2013008417A1

WO2013008417A1 - Photoacoustic imaging method and device

Info

Publication number: WO2013008417A1
Application number: PCT/JP2012/004328
Authority: WO
Inventors: 和弘広田
Original assignee: 富士フイルム株式会社
Priority date: 2011-07-14
Filing date: 2012-07-04
Publication date: 2013-01-17
Also published as: JP2013034852A; JP5694991B2

Abstract

[Problem] To prevent a part of a lumen or the like from being absent in a display of a photoacoustic image. [Solution] A photoacoustic imaging device (10) for irradiating a subject with pulse light of a wavelength that is absorbed by the interior thereof, from a laser light source (13), detecting the acoustic waves generated from the subject thereby and obtaining photoacoustic data, and imaging the subject on the basis of the photoacoustic data and displaying the same on an image displaying means, wherein the device is provided with: ultrasonic image acquiring means (11, 40, 41) for transmitting ultrasonic waves toward the subject, detecting the reflected ultrasonic waves thereby reflected from the subject, and obtaining ultrasonic data; and correcting means (27, 28, 42) for correcting a specific portion within the subject shown by the photoacoustic data, on the basis of the ultrasonic data showing the specific portion.

Description

Photoacoustic imaging method and apparatus

The present invention relates to a photoacoustic imaging method, that is, a method of irradiating a subject such as a living tissue with light and imaging the subject based on an acoustic wave generated by the light irradiation.

The present invention also relates to an apparatus for performing a photoacoustic imaging method.

Conventionally, as shown in Patent Document 1 and Non-Patent Document 1, for example, a photoacoustic imaging apparatus that images the inside of a living body using a photoacoustic effect is known. In this photoacoustic imaging apparatus, a living body is irradiated with pulsed light such as pulsed laser light. Inside the living body that has been irradiated with the pulsed light, the living tissue that has absorbed the energy of the pulsed light undergoes volume expansion due to heat and generates acoustic waves. Therefore, it is possible to detect the acoustic wave with an ultrasonic probe or the like and visualize the inside of the living body based on the electrical signal (photoacoustic signal) obtained thereby. The photoacoustic imaging method is suitable for imaging a specific tissue in a living body, such as a blood vessel, since an image is constructed based only on an acoustic wave emitted from a specific light absorber.

The photoacoustic image has an advantage that blood vessels and the like in the living body that are light absorbers can be extracted and displayed. For example, Patent Document 2 discloses a technique for displaying such extracted blood vessels.

JP 2005-21380 A Special table 2010-512929

However, in the conventional photoacoustic imaging apparatus, a problem has been recognized that the blood vessel may be displayed in a partially missing state.

Hereinafter, this problem will be described in detail with reference to FIGS. Here, as shown in both figures, an ultrasonic probe P in which a plurality of ultrasonic transducers are arranged one-dimensionally (in the horizontal direction in the figures) is used for acoustic wave detection, and a plurality of ultrasonic transducers are used. For example, a light transmitting portion L in which tips of a plurality of optical fibers are arranged in parallel in the same direction as the arrangement direction of the acoustic wave vibrators is disposed, and from there, a pulse laser beam is directed toward the blood vessel H to be imaged. Shall be irradiated. Note that such an ultrasonic probe P is generally used as a means for transmitting an ultrasonic wave toward a subject and a means for receiving an ultrasonic wave reflected by the subject in order to acquire an ultrasonic echo image. .

FIG. 2 shows a case where the blood vessel H is relatively thin and the above-described problem does not occur. That is, in this case, as schematically shown on the right side of the blood vessel H, an acoustic wave is generated on the blood vessel wall on the side close to the ultrasonic probe P and on the blood vessel wall on the side far from the ultrasonic probe P. This is because the pulsed laser light emitted from the light transmitting part L is not completely absorbed inside the blood vessel H and reaches the blood vessel wall far from the ultrasonic probe P.

On the other hand, when the blood vessel H is relatively thick, as shown in FIG. 3, the acoustic wave is generated only on the blood vessel wall on the side close to the ultrasonic probe P and not on the blood vessel wall on the side far from the ultrasonic probe P. Sometimes. This is because the pulse laser beam emitted from the light transmitting part L is completely absorbed inside the blood vessel H and does not reach the blood vessel wall far from the ultrasonic probe P. In such a situation, the blood vessel wall far from the ultrasonic probe P is lost in the photoacoustic image.

The case where a part of a blood vessel is missing has been described above. However, a portion that is in the shape of a lumen like a blood vessel may be displayed missing due to the same cause.

The present invention has been made in view of the above circumstances, and an object thereof is to provide a photoacoustic imaging method capable of preventing a part of a lumen or the like from being displayed missing.

It is another object of the present invention to provide a photoacoustic imaging apparatus that can implement such a photoacoustic imaging method.

The photoacoustic imaging method according to the present invention comprises:
The object is irradiated with pulsed light having a wavelength that is absorbed inside the object, thereby detecting an acoustic wave emitted from the object, obtaining photoacoustic data, and imaging the object based on the photoacoustic data. In the photoacoustic imaging method for displaying on the image display means,
Transmitting ultrasonic waves toward the subject, thereby detecting reflected ultrasonic waves reflected by the subject to obtain ultrasonic data;
Correcting a specific portion in the subject indicated by the photoacoustic data based on the ultrasonic data indicating the specific portion;
The subject is imaged by the photoacoustic data after correction.

In the photoacoustic imaging method according to the present invention, the specific portion is, for example, a lumen portion in a subject. Such a lumen portion is, for example, a blood vessel portion.

Moreover, as said correction | amendment, the correction | amendment which connects the pipe wall part missing in a photoacoustic image for the perimeter along the tube wall part in an ultrasonic image is applicable, for example.

And such a correction | amendment produces | generates so that the tube wall part missing in a photoacoustic image may be displayed in the aspect distinguishable from the tube wall part which exists in a photoacoustic image, for example, the color-coded aspect. It is desirable to be a thing.

Alternatively, as the above-described correction, it is possible to apply a correction in which a portion inside the tube wall portion in the ultrasonic image is filled with a predetermined color in the photoacoustic image.

When applying such correction, the predetermined color is different from the tube wall portion that is normally imaged at a position different from the tube wall portion to be corrected for filling. It is desirable to do.

In the photoacoustic imaging method according to the present invention,
As the pulsed light, irradiating pulsed light having a plurality of different wavelengths,
It is desirable to identify a plurality of portions of the subject having different absorption characteristics with respect to the pulsed light of each wavelength and display them in a distinguishable manner.

As described above, in order to display a plurality of parts in an identifiable manner, for example, the display colors of these parts may be changed from each other.

The plurality of wavelengths are preferably two wavelengths having different absorption characteristics in the artery and vein of the living body.

On the other hand, the photoacoustic imager according to the present invention is:
The object is irradiated with pulsed light having a wavelength that is absorbed inside the object, thereby detecting an acoustic wave emitted from the object to obtain photoacoustic data, and imaging the object based on the photoacoustic data. In the photoacoustic imaging device for displaying on the image display means,
Ultrasonic image acquisition means for transmitting ultrasonic waves toward the subject, thereby detecting reflected ultrasonic waves reflected by the subject and obtaining ultrasonic data;
And a correction unit configured to correct a specific portion in the subject indicated by the photoacoustic data based on the ultrasonic data indicating the specific portion.

As the correction means, for example, means for correcting a lumen portion in a subject as the specific portion can be applied.

In addition, as the correction means, means for correcting a blood vessel portion in the subject as the lumen portion can be applied.

Further, as the correcting means, it is possible to apply means for correcting the tube wall portion missing in the photoacoustic image along the entire tube wall portion in the ultrasonic image.

And such a correction | amendment means is produced | generated so that the tube wall part missing in a photoacoustic image may be displayed in the aspect distinguishable from the tube wall part which exists in a photoacoustic image, for example, the color-coded aspect. It is desirable to do.

Alternatively, as the correction means, it is also possible to apply means for performing correction to fill a portion inside the tube wall portion in the ultrasonic image with a predetermined color in the photoacoustic image.

In addition, the correction means for performing such filling is to change the predetermined color to a color different from the tube wall portion that is normally imaged at a position different from the tube wall portion to be corrected for the filling. It is desirable to set it.

In the photoacoustic imaging apparatus according to the present invention,
Means for irradiating pulsed light having a plurality of different wavelengths as the pulsed light;
It is desirable to provide means for discriminating a plurality of portions of the subject having different absorption characteristics with respect to pulsed light of each wavelength and displaying them in a mutually distinguishable manner.

It is desirable that the means for identifying the plurality of parts and displaying them in a mutually distinguishable manner is to display these parts in different colors.

Conventionally known ultrasonic images are unsuitable for clearly extracting and displaying blood vessels and the like as in photoacoustic images, but parts that are desired to be imaged are lost due to light absorption. It is unrelated to the problem. In view of this point, the photoacoustic imaging method according to the present invention transmits ultrasonic waves toward the subject, thereby detecting reflected ultrasonic waves reflected by the subject to obtain ultrasonic data, and the photoacoustic data is Since the specific part in the object shown is corrected based on the ultrasonic data indicating the specific part, and the object is imaged by the photoacoustic data after the correction, this photoacoustic imaging method According to the above, even if there is a missing portion in the original photoacoustic image, the missing portion can be displayed by correction.

In the photoacoustic imaging method according to the present invention, in particular, the pulsed light is irradiated with pulsed light having a plurality of different wavelengths, and a plurality of portions of the subject having different absorption characteristics for the pulsed light of each wavelength are identified. In the case where the images are displayed so as to be distinguishable from each other, for example, the arteries and veins of a living body can be clearly identified and observed, which is advantageous in assisting surgery and detecting abnormalities.

On the other hand, the photoacoustic imaging apparatus of the present invention transmits an ultrasonic wave toward a subject, thereby detecting an ultrasonic wave reflected by the subject and obtaining ultrasonic data, and an optical image acquisition unit. Since the correction part which correct | amends the specific part in the subject which acoustic data shows based on the said ultrasonic data which shows this specific part is provided, according to this photoacoustic imaging device, this invention mentioned above The photoacoustic imaging method can be implemented.

1 is a block diagram showing a schematic configuration of a photoacoustic imaging apparatus according to a first embodiment of the present invention. Schematic explaining the generation of photoacoustic signals in the blood vessel The figure explaining the problem in the conventional device The figure which shows the example of the ultrasonic image in the apparatus of FIG. The figure which shows the example of the photoacoustic image in the apparatus of FIG. The figure which shows the example of the photoacoustic image and ultrasonic image in the apparatus of FIG. The figure which shows the example of the photoacoustic image and ultrasonic image in the apparatus of FIG. The figure which shows the correction example of a photoacoustic image The block diagram which shows schematic structure of the photoacoustic imaging device by the 2nd Embodiment of this invention. The figure which shows the example of the ultrasonic image in the apparatus of FIG. The figure which shows the example of the photoacoustic image in the apparatus of FIG. The figure which shows the example of the photoacoustic image and ultrasonic image in the apparatus of FIG. The figure which shows the example of the photoacoustic image and ultrasonic image in the apparatus of FIG. The figure which shows the correction example of a photoacoustic image Graph showing the molecular absorption coefficient for each light wavelength of oxygenated hemoglobin (oxy-Hb) and deoxygenated hemoglobin (deoxy-Hb)

Hereinafter, embodiments of the present invention will be described in detail with reference to the drawings. FIG. 1 is a block diagram showing a basic configuration of a photoacoustic imaging apparatus 10 according to the first embodiment of the present invention. The photoacoustic imaging apparatus 10 can acquire both a photoacoustic image and an ultrasonic image, and includes an ultrasonic probe (probe) 11, an ultrasonic unit 12, a laser light source unit 13, and an image display. Means 14 are provided.

The laser light source unit 13 emits pulse laser light having a predetermined wavelength, and the pulse laser light emitted from the laser light source unit 13 is irradiated on the subject. The pulse laser beam is schematically shown in FIG. 1 with respect to the emission direction. For example, the pulse laser beam is guided to the probe 11 using light guide means such as a plurality of optical fibers, and directed from the probe 11 portion toward the subject. It is desirable to be irradiated.

The probe 11 performs output (transmission) of ultrasonic waves to the subject and detection (reception) of reflected ultrasonic waves reflected back from the subject. For this purpose, the probe 11 has, for example, a plurality of ultrasonic transducers arranged one-dimensionally. The probe 11 detects ultrasonic waves (acoustic waves) generated by the observation target in the subject absorbing the laser light from the laser light source unit 13 by using a plurality of ultrasonic transducers. The probe 11 detects the acoustic wave and outputs an acoustic wave detection signal, and also detects the reflected ultrasonic wave and outputs an ultrasonic detection signal.

When the above-described light guide means is coupled to the probe 11, the end portion of the light guide means, that is, the tip portions of the plurality of optical fibers are arranged in the direction in which the plurality of ultrasonic transducers are arranged (left and right in FIG. 1). The laser beam is emitted toward the subject from there. Hereinafter, the case where the light guide means is coupled to the probe 11 as described above will be described as an example.

When acquiring a photoacoustic image or an ultrasonic image of a subject, the probe 11 is moved in a direction substantially perpendicular to a one-dimensional direction in which a plurality of ultrasonic transducers are arranged, whereby the subject is subjected to laser light and ultrasonic waves. Is two-dimensionally scanned. This scanning may be performed by an inspector moving the probe 11 manually, or a more precise two-dimensional scanning may be realized using a scanning mechanism.

The ultrasonic unit 12 includes a reception circuit 21, an AD conversion unit 22, a reception memory 23, a data separation unit 24, a photoacoustic image reconstruction unit 25, a detection / logarithmic conversion unit 26, a blood vessel determination unit 27, a blood vessel correction unit 28, and Photoacoustic image construction means 29 is provided.

The receiving circuit 21 receives the acoustic wave detection signal and the ultrasonic wave detection signal output from the probe 11. The AD conversion means 22 is a sampling means, which samples the acoustic wave detection signal and the ultrasonic detection signal received by the receiving circuit 21 and converts them into photoacoustic data and ultrasonic data, which are digital signals, respectively. This sampling is performed at a predetermined sampling period in synchronization with, for example, an externally input AD clock signal.

In addition to the ultrasound image reconstruction means 40 that receives the output of the data separation means 24, the ultrasound unit 12 includes a detection / logarithm conversion means 41, a lumen detection means 42, an ultrasound image construction means 43, and this ultrasound. The image construction means 43 and the image composition means 44 for receiving the output of the photoacoustic image construction means 29 are provided. The output of the image synthesizing unit 44 is input to the image display unit 14 including, for example, a CRT or a liquid crystal display device. Further, the ultrasonic unit 12 includes a transmission control circuit 30 and a control unit 31 that controls the operation of each unit in the ultrasonic unit 12.

The photoacoustic data or ultrasonic data output from the AD converter 22 is temporarily stored in the reception memory and then input to the data separator 24. The data separation unit 24 separates the input photoacoustic data and the ultrasonic data from each other, the photoacoustic data is input to the photoacoustic image reconstruction unit 25, and the ultrasonic data is input to the ultrasonic image reconstruction unit 40. .

The laser light source unit 13 is a solid-state laser unit including a Q-switch pulse laser 32 made of a Ti: Sapphire laser or the like and a flash lamp 33 as an excitation light source. In the following description, a case where a photoacoustic image showing a blood vessel is acquired will be described as an example. In this case, a laser light source unit 13 that emits pulsed laser light having a wavelength that is well absorbed in the blood vessel is selected. Used.

When the laser light source unit 13 receives an optical trigger signal instructing light emission from the control means 31, the laser light source unit 13 turns on the flash lamp 33 to excite the Q switch pulse laser 32. For example, when the flash lamp 33 sufficiently excites the Q switch pulse laser 32, the control means 31 outputs a Q switch trigger signal. When the Q switch pulse laser 32 receives the Q switch trigger signal, the Q switch pulse laser 32 turns on the Q switch to emit pulsed laser light.

Here, the time required from when the flash lamp 33 is turned on until the Q-switch pulse laser 32 is sufficiently excited can be estimated from the characteristics of the Q-switch pulse laser 32 and the like. In place of controlling the Q switch from the control means 31 as described above, the Q switch may be turned on after the Q switch pulse laser 32 is sufficiently excited in the laser light source unit 13. In that case, a signal indicating that the Q switch is turned on may be notified to the ultrasonic unit 12 side.

The control unit 31 inputs an ultrasonic trigger signal for instructing ultrasonic transmission to the transmission control circuit 30. When receiving the ultrasonic trigger signal, the transmission control circuit 30 transmits an ultrasonic wave from the probe 11. The control means 31 outputs the optical trigger signal first, and then outputs an ultrasonic trigger signal. The light trigger signal is output to irradiate the subject with laser light and the acoustic wave is detected, and then the ultrasonic trigger signal is output to transmit the ultrasonic wave to the subject and the reflected ultrasonic wave. Is detected.

The control means 31 further outputs a sampling trigger signal that instructs the AD conversion means 22 to start sampling. The sampling trigger signal is output after the optical trigger signal is output and before the ultrasonic trigger signal is output, more preferably at the timing when the subject is actually irradiated with the laser light. Therefore, the sampling trigger signal is output in synchronization with the timing at which the control means 31 outputs the Q switch trigger signal, for example. When receiving the sampling trigger signal, the AD conversion means 22 starts sampling the acoustic wave detection signal output from the probe 11 and received by the receiving circuit 21.

After outputting the optical trigger signal, the control means 31 outputs the ultrasonic trigger signal at the timing when the detection of the acoustic wave is finished. At this time, the AD conversion means 22 continues the sampling without interrupting the sampling of the acoustic wave detection signal. In other words, the control unit 31 outputs the ultrasonic trigger signal in a state where the AD conversion unit 22 continues sampling the acoustic wave detection signal. When the probe 11 transmits ultrasonic waves in response to the ultrasonic trigger signal, the detection target of the probe 11 changes from acoustic waves to reflected ultrasonic waves. The AD conversion means 22 continuously samples the acoustic wave detection signal and the ultrasonic wave detection signal by continuously sampling the detected ultrasonic wave detection signal.

The AD conversion unit 22 stores photoacoustic data and ultrasonic data obtained by sampling in a common reception memory 23. The sampling data stored in the reception memory 23 is photoacoustic data up to a certain point, and becomes ultrasonic data from a certain point. The data separation unit 24 separates the photoacoustic data and the ultrasonic data stored in the reception memory 23, inputs the photoacoustic data to the photoacoustic image reconstruction unit 25, and converts the ultrasonic data into the ultrasonic image reconstruction unit. 40.

Hereinafter, generation and display of an ultrasonic image and a photoacoustic image will be described with reference to FIGS. 4A to 4D. The ultrasound image reconstruction means 40 adds the ultrasound data that is data for each of the plurality of ultrasound transducers included in the probe 11 to generate ultrasound tomographic image data for one line. The detection / logarithm conversion means 41 generates an envelope of the ultrasonic tomographic image data, and then logarithmically converts the envelope to widen the dynamic range, and then inputs this data to the lumen detection means 42. From this data, the lumen detection means 42 detects an annular portion that is considered to be a lumen by a method such as pattern matching.

Here, FIG. 4A schematically shows an example of an ultrasonic tomographic image, in which one tissue E and lumens F, G, and H are shown. In FIG. 4A and FIGS. 4B, 4C, and 4D, which will be described later, it is assumed that ultrasonic waves and pulsed laser light are emitted from the upper side to the lower side in the drawing. In each figure, the portion of the lumen H is separately enlarged for easy understanding. When the ultrasonic tomographic image is like this, the lumen detecting means 42 detects the annular portion, that is, the portions of the lumens F, G, and H, and stores the data indicating the shape and position of the blood vessel. Input to the judging means 27.

The output of the detection / logarithm conversion means 41 is also input to the ultrasonic image construction means 43 as it is. The ultrasonic image construction unit 43 generates an ultrasonic tomographic image (ultrasonic echo image) based on the data of each line output from the detection / logarithmic conversion unit 41. That is, the ultrasonic image constructing unit 43 generates the ultrasonic tomographic image so that, for example, the position in the time axis direction of the peak portion of the ultrasonic detection signal described above is converted into the position in the depth direction in the tomographic image. .

The above processing is sequentially performed with the scanning movement of the probe 11, thereby generating ultrasonic tomographic images regarding a plurality of locations in the scanning direction of the subject. Then, the image data carrying these ultrasonic tomographic images is input to the image composition means 44. If it is desired to display only the ultrasonic tomographic image alone, the image data carrying the ultrasonic tomographic image passes through the image synthesizing unit 44 and is sent to the image display unit 14. A tomographic image is displayed.

Next, generation and display of a photoacoustic image will be described. In the photoacoustic image reconstruction means 25, photoacoustic data obtained by irradiating the subject with photoacoustic data separated from the ultrasonic data by the data separation means 24, that is, pulse laser light having a wavelength absorbed by the blood vessel. Data is entered. The photoacoustic image reconstruction means 25 adds the photoacoustic data, which is data for each of the plurality of ultrasonic transducers included in the probe 11, to generate photoacoustic image data for one line. The detection / logarithm conversion means 26 generates an envelope of the photoacoustic image data, and then logarithmically converts the envelope to widen the dynamic range, and then inputs this data to the blood vessel determination means 27.

FIG. 4B schematically shows a photoacoustic image of the same cross section as that shown in FIG. 4A as the photoacoustic image carried by the above-described photoacoustic image data. In this photoacoustic image, blood vessel portions Fa and Ha exist as an example. Among them, a relatively thick blood vessel portion Ha is a pulse laser beam for the reason described above with reference to FIGS. Since the blood vessel wall on the side farther from the irradiation side (the side where the probe 11 exists, here the upper side in the figure) is missing, it is unclear whether it can be regarded as a blood vessel.

Therefore, the blood vessel judging means 27 originally has the above-mentioned blood vessel portion Ha having a half annular shape based on the data indicating the shape and position of the lumen H input from the lumen detecting means 42 as described above. It is determined that it is a lumen, that is, it clearly shows a blood vessel. Receiving the determination result of the lumen detecting means 42, the blood vessel correcting means 28 connects the photoacoustic image data input from the detection / logarithm converting means 26 with the half annular portion along the lumen H all around the circumference. Correct so that it is a circular ring.

4C and 4D illustrate the above correction. If the ultrasonic tomographic image data and the photoacoustic image data are synthesized without performing the above correction, the lumen H and the blood vessel portion Ha in the image displayed based on the synthesized data are enlarged in FIG. 4C. The image is formed in the state shown in the figure. On the other hand, if the ultrasonic tomographic image data and the photoacoustic image data are synthesized after performing the above correction, the lumen H and the corrected blood vessel portion Ha ′ are imaged in an enlarged state in FIG. 4D. It becomes. Thus, by performing the above correction, the blood vessel portion is displayed in the original shape in the photoacoustic image.

The corrected blood vessel portion H ′ is generated so that a portion originally present in the photoacoustic image and a portion added by the correction are displayed in a manner that can be distinguished from each other, for example, in a color-coded manner. It is desirable. By doing so, the device operator can grasp that the original photoacoustic image was missing.

The corrected photoacoustic image data is input to the photoacoustic image construction unit 29. The photoacoustic image construction means 29 generates a photoacoustic image based on the photoacoustic image data for each line. That is, the photoacoustic image construction unit 29 generates a photoacoustic image such that, for example, the position in the time axis direction of the peak portion of the photoacoustic image data is converted into a position in the depth direction in the tomographic image.

The above processing is sequentially performed with the scanning movement of the probe 11, thereby generating photoacoustic images regarding a plurality of locations in the scanning direction of the subject. The image data carrying these photoacoustic images is input to the image synthesizing means 44, where it is synthesized with the image data carrying the above-mentioned ultrasonic tomographic image, and the image carried by the synthesized data is input to the image display means 14. Is displayed. As described above, an image displayed based on the synthesized data is as shown in FIG. 4D.

In the present embodiment, the blood vessel portion Ha having a half annular shape is corrected so as to become an annular blood vessel portion Ha ′ connected all around, but instead, as shown in FIG. The inside of the lumen H may be corrected to fill with a predetermined color as indicated by J in the figure to indicate that it is a blood vessel.

When such filling is performed, a blood vessel part that is normally imaged at a position different from the blood vessel part Ha to be corrected for filling the predetermined color (for example, the blood vessel part Fa in FIG. 5). It is desirable to set it to a different color. By doing so, it becomes possible to easily determine whether the blood vessel portion Ha is normally displayed normally or whether it is normally displayed by the correction.

In the above embodiment, the ultrasonic image acquisition means for transmitting the ultrasonic wave toward the subject and detecting the reflected ultrasonic wave reflected by the subject to obtain the ultrasonic data is the probe 11, the ultrasonic image re-transmission unit. Compensation means comprising a construction means 40 and a detection / logarithm conversion means 41, and a correction means for correcting a specific part in the subject indicated by the photoacoustic data based on ultrasonic data indicating the specific part It comprises means 42, blood vessel determination means 27 and blood vessel correction means 28.

Next, another embodiment of the present invention in which an artery and a vein can be identified and displayed will be described with reference to FIGS. FIG. 6 is a block diagram showing a basic configuration of the photoacoustic imaging apparatus 110 according to the second embodiment of the present invention. In FIG. 6, the same elements as those in FIG. 1 are denoted by the same reference numerals, and description thereof will be omitted unless necessary (the same applies hereinafter). Compared with the photoacoustic imaging apparatus 10 of FIG. 1, the photoacoustic imaging apparatus 110 basically includes a two-wavelength data complexization means 115, an intensity information extraction means 116, and a two-wavelength data calculation means 117. In addition, a laser light source unit 113 that can selectively emit two-wavelength pulsed laser light is used instead of the laser light source unit 13.

More specifically, the laser light source unit 113 is obtained by applying a Q switch pulse laser 132 in place of the Q switch pulse laser 32 of FIG. The Q-switch pulse laser 132 includes a solid-state laser rod 133 that is a laser medium excited by the flash lamp 33, a partial transmission mirror 134 disposed on the front side (use light extraction side) of the laser rod 133, and a laser rod. A mirror 135 which is arranged on the rear side of 133 and constitutes a laser resonator together with the partial transmission mirror 134, a Q switch element 136 which is arranged between the laser rod 133 and the partial transmission mirror 134, and a rotary filter element ( A band pass filter 137 provided between the laser rod 133 and the mirror 135, a servo motor 138 for rotating the rotary filter element, and a rotational position of the rotary filter element. Encoder 139 and the output from encoder 139 Those formed by a band-pass filter control unit 140 for controlling the driving of the motor 138.

As the laser rod 133, a laser rod that emits light having center wavelengths of 750 nm and 800 nm, respectively, by excitation of the flash lamp 33 is used. Correspondingly, as the rotary filter element, an element in which two filter parts that transmit light in the vicinity of 750 nm and light in the vicinity of 800 nm are held by a rotating body is applied. The servo motor 138 selectively inserts one of the two filter portions into the optical path of the backward emission light between the laser rod 133 and the mirror 135 by rotating the rotating body (filter rotating body).

When the above-described filter portion that transmits light in the vicinity of 750 nm satisfactorily is inserted in the optical path of the backward emission light, only light in the vicinity of 750 nm is fed back to the laser rod 133 via the mirror 135. Therefore, in this case, since the gain of light having a center wavelength of 750 nm is particularly high, pulse laser light having a center wavelength of 750 nm is emitted from the Q switch pulse laser 132. Similarly, when a filter portion that transmits light in the vicinity of 800 nm satisfactorily is inserted into the optical path of the backward emission light, pulse laser light having a center wavelength of 800 nm is emitted from the Q switch pulse laser 132.

For the laser rod 133, for example, alexandrite crystal, Cr: LiSAF (Cr: LiSrAlF6), Cr: LiCAF (Cr: LiCaAlF6) crystal, Ti: Sapphire crystal, or the like can be used.

In addition, in the filter rotating body of the bandpass filter 137, a filter portion that favorably transmits light in the vicinity of a wavelength of 750 nm is carried on one half (for example, a region from 0 ° to 180 ° of the rotational displacement position), and the other half (for example, rotating) A filter portion that satisfactorily transmits light in the vicinity of a wavelength of 800 nm is carried in a region of a displacement position of 180 ° to 360 °. Therefore, when the filter rotator is rotated by the servo motor 138, the two filter portions are alternately inserted into the optical path of the outgoing light in the laser resonator at a switching speed corresponding to the rotation speed of the filter rotator. Will be.

The encoder 139 is a rotary encoder composed of, for example, a rotary plate with slits attached to the output shaft of the servo motor 138 and a transmissive photo interrupter. The encoder 139 detects the rotational displacement position of the filter rotating body, and the rotational displacement thereof. A BPF (band pass filter) state signal indicating the position is generated. Based on the BPF state signal, the bandpass filter control unit 140, for example, controls the servo motor so that the amount of rotational displacement detected by the encoder 139 during a predetermined time becomes an amount corresponding to the predetermined rotational speed of the filter rotating body. The voltage supplied to 138 is controlled.

On the other hand, the control means 31 controls each part in the ultrasonic unit 12 as described above, and the two filter parts inserted in the backward emission light path in the laser resonator are switched at a predetermined switching speed. The band pass filter control unit 140 is controlled. Note that the rotation speed of the filter rotator is based on, for example, the number of wavelengths of pulsed laser light to be emitted from the laser light source unit 113 (number of transmission wavelength regions of the bandpass filter) and the number of pulsed laser lights per unit time. May be determined as appropriate.

The trigger control unit 31a of the control unit 31 outputs an optical trigger signal that instructs the laser light source unit 113 to drive the flash lamp 33, for example, periodically at predetermined time intervals. The flash lamp 33 emits light in response to the light trigger signal and irradiates the laser rod 133 with excitation light. At this time, the trigger control unit 31a outputs an optical trigger signal based on the BPF state signal. That is, for example, the trigger control unit 31a has a filter portion corresponding to the wavelength of the pulsed laser beam to be emitted in the BPF state information of the band pass filter 137 (that is, the bandpass filter 137 in which the backward emission light path in the laser resonator is inserted). When the information indicates the position obtained by subtracting the amount of displacement of the filter rotator during the time required for excitation of the laser rod 133 from the rotational displacement position of the filter rotator, an optical trigger signal is output.

After outputting the optical trigger signal, the trigger control unit 31a outputs the Q switch trigger signal to the Q switch element 136 of the laser light source unit 113. At this time, the trigger control unit 31a outputs a Q switch trigger signal at the timing when the filter portion corresponding to the wavelength of the pulsed laser beam to be emitted is inserted into the backward emission optical path in the laser resonator. Thus, since the pulse laser beam is output only when the Q switch trigger signal is input and the Q switch element 136 is opened, the pulse laser beam can be extremely intense. In FIG. 1, this type of Q switch element is not particularly illustrated, but the Q switch pulse laser 32 also includes the same Q switch element as described above.

Next, blood vessel images displayed in the photoacoustic imaging apparatus 110 of FIG. 6 will be described with reference to FIGS. 7A to 7D and 8. FIG. In this apparatus 110, a blood vessel part, which is one of the lumens, is displayed in the original shape basically in the same manner as in the photoacoustic imaging apparatus 10 in FIG. In particular, arteries and veins of blood vessels can be distinguished from each other and displayed. Hereinafter, this point will be described in detail.

As an example, the molecular absorption coefficient at a wavelength of 750 nm of oxygenated hemoglobin (oxy-Hb combined with oxygen) contained in a large amount of human arteries is lower than the molecular absorption coefficient at a wavelength of 800 nm. On the other hand, the molecular absorption coefficient at a wavelength of 750 nm of deoxygenated hemoglobin (hemoglobin deoxy-Hb not bound to oxygen) contained in a large amount in the vein is higher than the molecular absorption coefficient at a wavelength of 800 nm. FIG. 9 shows molecular absorption coefficients for each light wavelength of oxygenated hemoglobin (oxy-Hb) and deoxygenated hemoglobin (deoxy-Hb). In this embodiment, using this property, is the photoacoustic signal obtained by irradiating light with a central wavelength of 750 nm relatively larger than the photoacoustic signal obtained by irradiating light with a central wavelength of 800 nm? By examining whether it is small, the photoacoustic signal from the artery and the photoacoustic signal from the vein are discriminated.

In the present embodiment, sampling of the acoustic wave detection signal by the AD conversion means 22 is repeatedly performed by the number of wavelengths of light emitted from the laser light source unit 113. For example, the acoustic wave detection signal obtained when the subject is irradiated with pulse laser light having a center wavelength of 750 nm from the laser unit 113 is first sampled, and then the subject is irradiated with pulse laser light having a center wavelength of 800 nm. The acoustic wave detection signal obtained at the time of sampling is sampled. In addition, sampling of the ultrasonic detection signal is performed in the same manner as in the first embodiment.

The photoacoustic data and ultrasonic data obtained by the above sampling are stored in the common reception memory 23. The sampling data stored in the reception memory 23 is photoacoustic data up to a certain point, and becomes ultrasonic data from a certain point. In particular, the photoacoustic data is photoacoustic data (hereinafter referred to as first photoacoustic data) when the subject is irradiated with a pulse laser beam having a center wavelength of 750 nm until a certain point in time. This is ultrasonic data (hereinafter referred to as second photoacoustic data) when the specimen is irradiated with pulsed laser light having a central wavelength of 800 nm. The data separation unit 24 separates the photoacoustic data and the ultrasonic data stored in the reception memory 23, inputs the photoacoustic data to the two-wavelength data complexization unit 115, and converts the ultrasonic data into the ultrasonic image reconstruction unit. 40.

The two-wavelength data complexization unit 115 generates complex number data in which one of the first photoacoustic data and the second photoacoustic data is a real part and the other is an imaginary part. In the following description, it is assumed that complex data is generated in which the first photoacoustic data is a real part and the second photoacoustic data is an imaginary part.

The photoacoustic image reconstruction unit 25 reconstructs a photoacoustic image from the complex number data input from the two-wavelength data complex number conversion unit 115 by a Fourier transform method (FTA method). For image reconstruction using the Fourier transform method, for example, a conventionally known method described in the literature “Photoacoustic Image Reconstruction-A Quantitative Analysis” Jonathan I. Sperl et al., SPIE-OSA, Vol. can do. The photoacoustic image reconstruction unit 25 inputs data after Fourier transform indicating the reconstructed image to the intensity information extraction unit 116 and the two-wavelength data calculation unit 117.

The intensity information extraction unit 116 generates intensity information indicating the signal intensity based on the photoacoustic data corresponding to each wavelength. In the present embodiment, the intensity information extraction unit 116 generates intensity information from complex number data indicating the reconstructed image input from the photoacoustic image reconstruction unit 25. That is, the intensity information extraction unit 116 extracts (X ² + Y ² ) ^1/2 as intensity information, for example, when complex number data is represented by X + iY.

Subsequent processing by the detection / logarithmic conversion means 26, the blood vessel determination means 27, and the blood vessel correction means 28 is performed in the same manner as in the apparatus of FIG. Therefore, in this case as well, in the photoacoustic image constructed by the photoacoustic image construction means 29, the blood vessel portion is shown as an annular shape connected around the entire circumference, or a circular shape whose interior is filled with a predetermined color. Become. The image data carrying the photoacoustic image is input to the image synthesizing unit 44, where it is synthesized with the image data carrying the ultrasonic tomographic image, and the image carried by the synthesized data is displayed on the image display unit 14. .

An example of the image displayed on the image display means 14 will be described with reference to FIGS. 7A to 7D and 8. FIG. 7A, 7B, 7C, and 7D show examples of images of the same type as the previously described FIGS. 4A, 4B, 4C, and 4D, respectively. In this example, in the ultrasonic tomographic image of FIG. 7A, one tissue E and lumens F, G, and H are shown as in FIG. 4A, and both the lumens F and G are blood vessel portions. However, in this example, unlike the case of FIG. 4B, in the photoacoustic image of FIG. 7B, both the blood vessel part Fa and the blood vessel part Ha are in a state where the blood vessel wall on the side far from the pulse laser light irradiation side is missing. .
Therefore, if the ultrasonic tomographic image data and the photoacoustic image data are synthesized without performing the above-described correction by the blood vessel correction means 28, the lumen H and the blood vessel portion in the image displayed based on the synthesized data. Ha and the lumen F and the blood vessel portion Fa are imaged in the state shown in an enlarged view in FIG. 7C. On the other hand, if the ultrasonic tomographic image data and the photoacoustic image data are synthesized after the correction by the blood vessel correction means 28, the lumen H and the corrected blood vessel portion Ha ′, and the lumen F and The corrected blood vessel portion Fa ′ is imaged in the state shown in an enlarged view in FIG. 7D. Thus, by performing the above correction, the blood vessel portion is displayed in the original shape in the photoacoustic image.

In this case as well, the blood vessel portions Ha and Fa having a half annular shape are corrected so as to become annular blood vessel portions Ha ′ and Fa ′ connected all around, but instead, FIG. As shown, the inside of the lumens H and F may be corrected to be filled with a predetermined color as indicated by J and K in the figure, respectively, so as to indicate the blood vessel.

Here, for example, when the blood vessel portion Ha ′ is an artery and the blood vessel portion Fa ′ is a vein, the points are displayed so as to be distinguishable from each other. The two-wavelength data calculation means 117 in FIG. 6 shows the relative signal intensity relationship between the photoacoustic data (first photoacoustic data and second photoacoustic data) corresponding to each wavelength (750 nm and 800 nm). Extract. In the present embodiment, the two-wavelength data calculation unit 117 uses the data indicating the reconstructed image reconstructed by the photoacoustic image reconstruction unit 115 as input data, and from this input data that is complex data, the real part and the imaginary part Phase information indicating which is relatively larger is extracted. That is, the two-wavelength data calculation unit 117 generates θ = tan ⁻¹ (Y / X) as phase information when, for example, complex number data is represented by X + iY. When X = 0, θ = 90 °. When the first photoacoustic data (X) constituting the real part and the second photoacoustic data (Y) constituting the imaginary part are equal, the phase information is θ = 45 °. The phase information approaches θ = 0 ° as the first photoacoustic data is relatively large, and approaches θ = 90 ° as the second photoacoustic data is relatively large.

The photoacoustic image construction means 29 receives the intensity information that has been subjected to the blood vessel correction after the detection / logarithmic conversion process is performed by the detection / logarithmic conversion means 26, and also receives the phase information from the two-wavelength data calculation means 117. The The photoacoustic image construction unit 29 generates a photoacoustic image based on the input phase information and intensity information. That is, the photoacoustic image construction unit 29 determines the luminance (gradation value) of each pixel in the distribution image of the light absorber based on, for example, input intensity information. Moreover, the photoacoustic image construction means 29 determines the color (display color) of each pixel in the light absorber distribution image based on, for example, phase information. The photoacoustic image construction unit 29 determines the color of each pixel based on the input phase information using, for example, a color map in which a phase range of 0 ° to 90 ° is associated with a predetermined color.

Here, since the range of the phase 0 ° to 45 ° is a range in which the first photoacoustic data is larger than the second photoacoustic data, the source of the photoacoustic signal is more than the absorption with respect to light having a wavelength of 800 nm. It is considered that this is a vein through which blood mainly containing deoxygenated hemoglobin has a larger absorption with respect to light having a wavelength of 750 nm. On the other hand, since the range of 45 ° to 90 ° of the phase is a range in which the second photoacoustic data is smaller than the first photoacoustic data, the source of the photoacoustic signal has a wavelength larger than the absorption with respect to light having a wavelength of 800 nm. It is considered that this is an artery through which blood mainly containing oxygenated hemoglobin flows, which absorbs less light at 750 nm.

Therefore, as a color map, for example, the phase gradually changes so that the phase is 0 ° in blue and the phase becomes colorless (white) as the phase approaches 45 °, and the phase 90 ° is red and the phase is 45. Use a color map that gradually changes its color to become white as it approaches °. By doing so, the portion corresponding to the artery, that is, the corrected blood vessel portion Ha ′ in FIG. 7D and the corrected blood vessel portion J in FIG. 8 are represented in red on the photoacoustic image, and the portion corresponding to the vein, that is, the corrected blood vessel portion in FIG. Fa ′ and the corrected blood vessel K in FIG. 8 can be represented in blue. Instead of using the intensity information, the gradation value may be constant, and the color corresponding to the portion corresponding to the artery and the portion corresponding to the vein may be performed according to the phase information.

In the present embodiment, one of the first photoacoustic data and the second photoacoustic data obtained by irradiating the subject with light of two wavelengths, respectively, is the real part, and the other is the imaginary part. Complex number data is generated, and a reconstructed image is generated from the complex number data by Fourier transform. In such a case, since the reconstruction process only needs to be performed once, the reconstruction can be performed more efficiently than when the first photoacoustic data and the second photoacoustic data are separately reconstructed. it can.

As is apparent from the above description, in the present embodiment, the two-wavelength data calculation unit 117 and the photoacoustic image construction unit 29 identify a plurality of portions of the subject having different absorption characteristics with respect to pulsed light having a plurality of wavelengths. Thus, a means for displaying each other in a distinguishable manner is configured.

Further, in this embodiment, the pulse laser beam of two wavelengths is alternately switched at high speed to irradiate the subject to generate one image, but the pulse laser beam of one wavelength is generated by the subject. It is also possible to generate another image by irradiating the subject with pulsed laser light of another wavelength by performing wavelength switching after generating one image by irradiating the object.

The two wavelengths can be selected in any combination of two wavelengths as long as the absorption coefficients are theoretically different from each other. However, from the viewpoint of clearly distinguishing and imaging arteries / veins, one is 793 to 802 nm (more preferably), which is close to the isosbestic point of oxygenated hemoglobin (oxy-Hb) and deoxygenated hemoglobin (deoxy-Hb). It is desirable that the isoabsorption point is 798 nm), and the other is 748 to 770 nm (more preferably 757 nm having an absorption peak of deoxygenated hemoglobin) in which absorption of both hemoglobins is greatly different.

Although two embodiments of the present invention have been described above, the photoacoustic imaging apparatus and method of the present invention are not limited to the above embodiments, and various modifications and changes are made to the configuration of the above embodiments. What has been done is also included in the scope of the present invention.

For example, in a photoacoustic image, a lumen portion other than a blood vessel may be partially lost for the same reason as in the case of the blood vessel described above. However, such a lumen portion other than the blood vessel is included in the ultrasound image. It is also possible to configure the photoacoustic imaging apparatus of the present invention to correct based on this.

Claims

The object is irradiated with pulsed light having a wavelength that is absorbed inside the object, thereby detecting an acoustic wave emitted from the object to obtain photoacoustic data, and imaging the object based on the photoacoustic data. In the photoacoustic imaging method for displaying on the image display means,
Transmitting ultrasonic waves toward the subject, thereby detecting reflected ultrasonic waves reflected by the subject to obtain ultrasonic data;
Correcting a specific portion in the subject indicated by the photoacoustic data based on the ultrasonic data indicating the specific portion;
A photoacoustic imaging method, wherein the subject is imaged by the photoacoustic data after correction.
The photoacoustic imaging method according to claim 1, wherein the specific portion is a lumen portion in a subject.
3. The photoacoustic imaging method according to claim 2, wherein the lumen portion is a blood vessel portion.
4. The photoacoustic imaging method according to claim 2, wherein the correction is correction that connects a missing tube wall portion in the photoacoustic image along the entire circumference of the tube wall portion in the ultrasonic image. 5. .
The correction is generated so that a tube wall portion missing in the photoacoustic image is displayed in a manner distinguishable from a tube wall portion existing in the photoacoustic image. Item 5. The photoacoustic imaging method according to Item 4.
4. The photoacoustic imaging method according to claim 2, wherein the correction is correction for filling a portion inside the tube wall portion in the ultrasonic image with a predetermined color in the photoacoustic image.
7. The light according to claim 6, wherein the predetermined color is a color different from a tube wall portion that is normally imaged at a position different from the tube wall portion subjected to the correction for filling. Acoustic imaging method.
As the pulsed light, irradiating pulsed light having a plurality of different wavelengths,
8. The photoacoustic imaging method according to claim 1, wherein a plurality of portions of the subject having different absorption characteristics with respect to pulsed light of each wavelength are identified and displayed so as to be distinguishable from each other.
9. The photoacoustic imaging method according to claim 8, wherein the plurality of parts are displayed in different colors.
The photoacoustic imaging method according to claim 8 or 9, wherein the plurality of wavelengths are two wavelengths having different absorption characteristics in an artery and a vein of a living body.
The object is irradiated with pulsed light having a wavelength that is absorbed inside the object, thereby detecting an acoustic wave emitted from the object, obtaining photoacoustic data, and imaging the object based on the photoacoustic data. In the photoacoustic imaging device for displaying on the image display means,
Ultrasonic image acquisition means for transmitting ultrasonic waves toward the subject, thereby detecting reflected ultrasonic waves reflected by the subject and obtaining ultrasonic data;
A photoacoustic imaging apparatus, comprising: a correcting unit that corrects a specific portion in the subject indicated by the photoacoustic data based on the ultrasound data indicating the specific portion.
12. The photoacoustic imaging apparatus according to claim 11, wherein the correction means corrects a lumen portion in a subject as the specific portion.
13. The photoacoustic imaging apparatus according to claim 12, wherein the correction means corrects a blood vessel portion in the subject as the lumen portion.
The light according to claim 12 or 13, wherein the correction means corrects the tube wall portion missing in the photoacoustic image by connecting all the circumferences along the tube wall portion in the ultrasonic image. Acoustic imaging device.
The correction means generates the tube wall portion missing in the photoacoustic image so as to be displayed in a manner distinguishable from the tube wall portion existing in the photoacoustic image. The photoacoustic imaging apparatus according to claim 14.
The photoacoustic imaging apparatus according to claim 12 or 13, wherein the correction means performs correction for filling a portion inside the tube wall portion in the ultrasonic image with a predetermined color in the photoacoustic image. .
The correction means sets the predetermined color to a color different from a tube wall portion that is normally imaged at a position different from the tube wall portion to be corrected for filling. The photoacoustic imager according to claim 16, wherein
Means for irradiating pulsed light having a plurality of different wavelengths as the pulsed light;
The light according to any one of claims 11 to 17, further comprising means for identifying a plurality of portions of the subject having different absorption characteristics with respect to pulsed light of each wavelength and displaying them in a distinguishable manner from each other. Acoustic imaging device.
19. The photoacoustic imaging apparatus according to claim 18, wherein the means for identifying the plurality of parts and displaying them in such a manner that they can be distinguished from each other displays the parts in different colors.
20. The photoacoustic imaging apparatus according to claim 18, wherein the plurality of wavelengths are two wavelengths having different absorption characteristics in an artery and a vein of a living body.