WO2011036792A1

WO2011036792A1 - Imaging device, imaging device control method, and imaging device control program

Info

Publication number: WO2011036792A1
Application number: PCT/JP2009/066770
Authority: WO
Inventors: 佐藤　隆幸; 数明小嶋; 勝己野口
Original assignee: 国立大学法人高知大学; 三洋電機株式会社; 三洋半導体株式会社; 瑞穂医科工業株式会社
Priority date: 2009-09-28
Filing date: 2009-09-28
Publication date: 2011-03-31
Also published as: JPWO2011036792A1

Abstract

Provided is a fluorescent endoscopic device or the like that does not require an optical filter and does not require special image signal processing for the purpose of color correction. In the structure of the device equipped with an excitation light radiation means (1), a radiation means drive means (3), a photoelectric conversion means (8) that converts fluorescent light generated by living tissue into an electrical signal, a photoelectric conversion element drive means (6) that determines the drive timing for the photoelectric conversion means (8), and a stored charge reset means (6) that resets a charge stored in the photoelectric conversion means (8), the excitation light radiation means (1) is driven intermittently, and when the excitation light radiation means (1) is not being driven, the photoelectric conversion element drive means (6) drives the photoelectric conversion means (6) to perform photoelectric conversion.

Description

IMAGING DEVICE, IMAGING DEVICE CONTROL METHOD, AND IMAGING DEVICE CONTROL PROGRAM

The present invention relates to an imaging apparatus that irradiates a living body with excitation light and captures fluorescence emitted from the living body to obtain a fluorescent image, a control method for the imaging apparatus, and a control program for the imaging apparatus.

There has been proposed a fluorescence observation endoscope apparatus that captures fluorescence of a living body through an endoscope and displays a fluorescence image for diagnosis of whether the living body is normal or abnormal. Such a fluorescence observation endoscope apparatus includes a conventional endoscope (electronic endoscope) and a light source processor apparatus (a processor that processes a video signal output from the electronic endoscope and outputs it as a video signal). Light source device). Specifically, an electronic endoscope used in a fluorescence observation endoscope apparatus is a light guide fiber bundle (hereinafter, simply referred to as “light guide”) that guides irradiation light toward a living tissue, with respect to light in a specific band. A material made of quartz glass fiber with good transparency is used, and an excitation light cut filter for cutting light of a specific wavelength used as excitation light is inserted in the optical path from the objective window to the image sensor. Yes.

The light source processor device is configured so that white light or excitation light can be introduced into the light guide of the endoscope as irradiation light for the living tissue, and when white light is introduced into the light guide (hereinafter, “ It is configured to change the image processing content for the image signal output from the electronic endoscope when the excitation light is introduced into the light guide (hereinafter referred to as “fluorescence observation mode”). ing.

In this fluorescence observation endoscope apparatus, there is an apparatus that simultaneously captures visible light color and near-infrared fluorescence. In this technique, a reagent that emits near-infrared fluorescence (indocyanine green or the like (hereinafter also referred to as ICG)). It is essential to dispose an optical filter that specifically blocks the irradiation light (near infrared light) for exciting the image pickup device at the input.

JP 2002-89109 A

However, in the conventional fluorescence observation endoscope apparatus, when the wavelength band of the excitation light and the wavelength band of the fluorescence are close to each other or at least a part of each wavelength band overlaps, the wavelength band of the excitation light and the fluorescence It was difficult or impossible to separate the wavelength band from the wavelength band using an optical filter. In addition, when the wavelength band of fluorescence and the wavelength band of visible light are close or at least partially overlap each other, the wavelength band of fluorescence and the wavelength band of visible light can be combined using an optical filter. It was difficult or impossible to separate.

For this reason, even when a reagent that emits medically favorable fluorescence is developed, if the relationship between the wavelength bands is as described above, the fluorescence observation endoscope used in the conventional medical field Using the apparatus, it was not possible to simultaneously provide an image of the peripheral region of the patient's operation with reflected illumination light and an image of the affected area with fluorescence.

In medical settings, it is safe and reliable for a doctor to perform an operation while observing the peripheral part of the patient (the part observed by illumination light with visible light) including the affected part that emits fluorescence during the operation. Is very important to carry out.

However, since the illuminance ratio between the reflected illumination light and the fluorescence in the light receiving unit is essentially very large, increasing the intensity of the emitted illumination light increases the illuminance of the reflected illumination light. In a fluorescence observation endoscope apparatus using an optical filter, it is very difficult to reliably detect fluorescence. That is, in the conventional fluorescence observation endoscope apparatus using the optical filter, a special optical filter for illumination light is required. However, even if this special optical filter is used, a sufficiently clear image of the affected area due to fluorescence cannot be provided. It was. For this reason, the doctor could not visually recognize a clear image of the peripheral region of the patient's operation due to the reflected illumination light required during the operation and a clear image of the affected area due to the fluorescence.

Also, by making the optical filter that specifically blocks a certain wavelength band into an essential configuration, the configuration of the imaging device and the configuration including the optical filter become complicated, and the cost of the entire device has been increased. Furthermore, when the wavelength band of the optical filter for blocking the excitation light and the wavelength band of the visible light are close to each other or overlapped, the control of the wavelength band of the transmitted light by the optical filter becomes insufficient, and can be obtained. There arises a problem that the color balance of the image is lost or broken, or the noise of the obtained image cannot be sufficiently removed and the image is not clear.

The present invention has been made in view of such problems, and the problem is that, in the medical field, at least one optical filter used in a conventional fluorescence observation endoscope apparatus is unnecessary. An imaging device that can eliminate the need for special image signal processing for color correction and can simultaneously display a real-time moving image of a normal color image and a real-time moving image of a fluorescent image on a display device, a control method for the imaging device, and imaging It is an object to provide a control program for an apparatus.

In order to solve the above problems, the present invention adopts the following configuration.

That is, the invention according to claim 1 is an imaging apparatus (20) that irradiates a living tissue with at least one of excitation light and illumination light. Excitation light irradiation means (1) for irradiating the excitation light; Irradiation means driving means (3) for driving the excitation light irradiation means (1), and photoelectric conversion means for converting the fluorescence generated from the living tissue to which the fluorescent compound is administered, which has been irradiated with the excitation light, into electrical signals ( 8), a photoelectric conversion element driving means (6) for determining the operation timing of the photoelectric conversion means, and an accumulated charge reset means (6) for resetting the charge accumulated in the photoelectric conversion means, The irradiation means driving means (3) drives the excitation light irradiation means (1) intermittently, and the photoelectric conversion element driving means (6) is driven by the irradiation means driving means (3). Driven) The non time the photoelectric conversion means (8) is driven by, characterized in that to perform the photoelectric conversion.

The invention according to claim 2 is the imaging device (20) according to claim 1, further comprising illumination light irradiating means (2) for irradiating the illumination light, wherein the illuminating means driving means (3) The excitation light irradiating means (1) and the illumination light irradiating means (2) are driven, and the photoelectric conversion means (8) emits fluorescence emitted from the biological tissue to which the fluorescent compound is administered, which has been irradiated with the excitation light. Is converted into an electrical signal, and the reflected illumination light reflected by the biological tissue irradiated with the illumination light is converted into an electrical signal.

According to a third aspect of the present invention, in the imaging device (20) according to the first or second aspect, the photoelectric conversion means (8) is driven by the photoelectric conversion element driving means (6) immediately before the photoelectric conversion means (8) is driven. The accumulated charge reset means (6) resets the charges accumulated in the photoelectric conversion means (8).

According to a fourth aspect of the present invention, in the imaging apparatus (20) according to the second or third aspect, the irradiation means driving means (3) includes the excitation light irradiation means (1) and the illumination light irradiation means ( 2) are driven intermittently so as not to be driven simultaneously, and the photoelectric conversion element driving means (6) is in the period when the excitation light irradiation means (1) is not driven by the irradiation means driving means (3). The photoelectric conversion means (8) is driven to perform photoelectric conversion.

The invention according to claim 5 is the imaging device (20) according to any one of claims 2 to 4, wherein the irradiation means driving means (3) includes the excitation light irradiation means (1) and the excitation light irradiation means (1). The illumination light irradiation means (2) is alternately and intermittently driven so as not to be driven simultaneously, and the excitation light irradiation means (1) is driven by the irradiation means driving means (3). The photoelectric conversion means (8) is driven to perform photoelectric conversion during a non-driven period.

The invention according to claim 6 is the imaging apparatus (20) according to any one of claims 2 to 5, wherein the irradiation means driving means (3) is irradiated from the illumination light irradiation means (2). It is characterized in that at least one of the pulse width of the illumination light and the luminance of the pulsed illumination light can be arbitrarily changed.

According to a seventh aspect of the present invention, in the imaging apparatus (20) according to any one of the second to sixth aspects, the irradiation unit driving unit (3) is at least the excitation with a substantially sinusoidal signal. The excitation light irradiation means (1) is intermittently driven by driving the light irradiation means (1).

According to an eighth aspect of the present invention, in the imaging device (20) according to the seventh aspect, the photoelectric conversion element driving means (6) for determining an operation timing of the photoelectric conversion element (8) includes the excitation light. The photoelectric conversion element (8) is delayed by a phase difference corresponding to a delay time from irradiation of the excitation light to generation of the fluorescence with respect to the substantially sinusoidal signal for driving the irradiation means (1). It is characterized by being driven.

Further, the invention according to claim 9 is an excitation light irradiation step (1) for irradiating the excitation light in the control method of the imaging device (20) for irradiating the living tissue with at least one of excitation light and illumination light. Irradiating means driving step (3) for driving and irradiating the excitation light in the excitation light irradiation step (1), and fluorescence generated from the living tissue to which the fluorescent compound is administered, irradiated with the excitation light. A photoelectric conversion step (8) for converting into an electric signal, a photoelectric conversion element driving step (6) for determining an operation timing in the photoelectric conversion step (8), and a charge accumulated in the photoelectric conversion step (6) are reset. An accumulated charge resetting step (6), wherein the excitation light is intermittently driven in the irradiation means driving step (3), and the irradiation means driving step (3) in the photoelectric conversion element driving step (6). In There the excitation light is characterized in that to perform the photoelectric conversion in the photoelectric conversion process to a period of non-irradiated (8).

Furthermore, the invention according to claim 10 is the control method according to claim 9, further comprising an illumination light irradiation step (2) for irradiating the illumination light, wherein the excitation light irradiation in the irradiation means driving step (3). The excitation light in the step (1) and the illumination light in the illumination light irradiation step (2) are driven and irradiated, and the fluorescent compound that has been irradiated with the excitation light in the photoelectric conversion step (8) is administered. The fluorescent light generated from the living tissue is converted into an electrical signal, and the reflected illumination light reflected by the living tissue irradiated with the illumination light is converted into an electrical signal.

Further, the invention according to claim 11 is directed to an excitation light irradiating means (1) for irradiating a computer included in an imaging device (20) for irradiating a living tissue with at least one of excitation light and illumination light. ), Irradiation means driving means (3) for driving the excitation light irradiation means (1), and photoelectric conversion for converting fluorescence generated from the living tissue to which the fluorescent compound is administered, which has been irradiated with the excitation light, into electrical signals. Means (8), photoelectric conversion element driving means (6) for determining the operation timing of the photoelectric conversion means (8), and accumulated charge reset means (6) for resetting the charge accumulated in the photoelectric conversion means (8). The irradiation means driving means (3) intermittently drives the excitation light irradiation means (1), and the photoelectric conversion element driving means (8) is driven by the irradiation means driving means (3). Serial excitation light irradiation means (1) by driving said photoelectric conversion means (8) during a period that is not driven and having a function of executing photoelectric conversion.

Furthermore, the invention according to claim 12 is to cause a computer included in the imaging apparatus (20) according to claim 11 to function as illumination light irradiation means (2) for irradiating the illumination light, and to irradiate the drive means ( 3) Drives the excitation light irradiation means (1) and the illumination light irradiation means (2), and the photoelectric conversion means (8) is irradiated with the excitation light and is irradiated with the fluorescent compound. The fluorescent light generated from the tissue is converted into an electrical signal, and the reflected illumination light reflected by the living tissue irradiated with the illumination light is converted into an electrical signal.

Furthermore, the invention according to claim 12 is characterized in that, in the imaging apparatus (20) according to any one of claims 1 to 7, the photoelectric conversion means (8) is a color imaging device.

When the type of fluorescent compound injected into a living body and the substance such as an additive change, the wavelength of excitation light and the wavelength of fluorescence for generating fluorescence may change. As a result, the wavelength band of excitation light and the wavelength band of fluorescence are close to each other, or at least a part of each wavelength band overlaps, and the wavelength band of fluorescence and the wavelength band of visible light are close or respectively According to the present invention, it is possible to simultaneously provide an image of a peripheral part of a patient's operation by reflected illumination light and an image of an affected part by fluorescence. .

In addition, when the type of fluorescent compound injected into the living body and substances such as additives have changed, the wavelength of the excitation light and the wavelength of the fluorescence for generating fluorescence may each change, Conventionally, it has been necessary to produce an optical filter such as a bandpass filter, a low wavelength band filter, and a high wavelength band filter according to the wavelength changed each time. By converting the axial optical filter into an electrical time axis filter, it is not necessary to use an optical filter, which simplifies the mechanical and electrical configuration of the imaging device of the endoscopic device, The cost of the imaging device of the mirror device can be reduced.

Further, the excitation light irradiation means is intermittently driven, and the photoelectric conversion means is driven and photoelectric conversion is performed during a period when the excitation light irradiation means is not driven, so that the high-intensity reflected excitation light is blocked. Eliminates the need to use optical filters.

Furthermore, since there is no possibility of receiving high-intensity reflected excitation light, a clear image of the patient's peripheral region of the patient and a clear image of the affected area due to fluorescence are simultaneously obtained by the reflected illumination light required during the operation. Doctors can now see.

Furthermore, since there is no possibility of receiving high-intensity reflected excitation light, it is possible to prevent the color balance of the subject from being broken.

Furthermore, the possibility of receiving high-intensity reflected excitation light is eliminated, and it is not necessary to widen the dynamic range of an electronic circuit including photoelectric conversion, so that the circuit configuration is simplified.

In addition, the charge accumulated in the photoelectric conversion means can be reset at each measurement even when the intensity of the fluorescence generated from the living tissue to which the fluorescent compound has been administered that has been irradiated with the excitation light is very small. Thus, accurate photoelectric conversion is possible even when the fluorescence is weak.

Furthermore, even when the reflected illumination light reflected by the living tissue irradiated with the illumination light is converted into an electrical signal, the charge accumulated in the photoelectric conversion means is reset at each measurement, so that the reflected light is reflected by the photoelectric conversion means. It becomes possible to accurately perform photoelectric conversion of the intensity of illumination light.

Further, the excitation light irradiating means and the illumination light irradiating means are intermittently driven so as not to be driven simultaneously, and the photoelectric conversion means is driven and photoelectric conversion is performed during a period in which the excitation light irradiating means and the illumination light irradiating means are not driven. As a result, it is not necessary to use optical filters such as optical filters that block high-intensity reflected excitation light, visible light transmission optical filters, and fluorescence transmission optical filters.

Furthermore, when receiving reflected illumination light, there is no possibility of receiving high-intensity reflected excitation light, so that it is possible to prevent the color balance of the subject from being broken.

Further, since the excitation light irradiation means and the illumination light irradiation means are driven alternately and intermittently without being driven at the same time, based on the fluorescence reflected from the affected area and the illumination light reflected from around the affected area including the affected area The affected part and the image including the affected part can be viewed in real time, and the patient can be quickly examined and / or operated using the endoscope apparatus.

Furthermore, the need for optical filters such as an optical filter and / or a visible light transmission optical filter and a fluorescence transmission optical filter that block high-intensity reflected excitation light is eliminated, and thus the endoscope apparatus can be reduced in size and cost. Become.

Further, the brightness of the illumination light is obtained by intermittently driving the excitation light source as the excitation light irradiation means and driving the image sensor as the photoelectric conversion means during a period when the excitation light source is not driven to perform photoelectric conversion. If the illumination light image by the illumination light reflected by the living tissue irradiated with the illumination light is brightened or darkened so that the doctor is most suitable for surgery or the like, the excitation light The fluorescence image and the illumination light image by the fluorescence generated from the irradiated biological tissue can be simultaneously clearly and visually recognized.

In addition, when the delay from excitation light irradiation to fluorescence generation is very short, theoretically, it is possible to separate in time by shortening the emission pulse of the excitation light. It is difficult to control. Even in such a case, according to the present invention, the excitation light and the fluorescence can be separated by driving the irradiation means driving means such as an LED with a substantially sinusoidal signal.

Further, according to the present invention, even when the delay from the irradiation of the excitation light to the generation of the fluorescence is very short, the fluorescence generated by the irradiation of the excitation light is reliably photoelectrically converted by using the fluorescence lifetime. It becomes possible to measure with an element.

1 is a block diagram illustrating an entire endoscope system including an imaging device of an endoscope apparatus according to an embodiment of the present invention. It is a figure which shows the function outline | summary of the imaging device of the endoscope apparatus which concerns on embodiment of this invention. It is a figure which shows an example of the relationship between the illumination light of the embodiment concerning this invention, excitation light, and the wavelength range of fluorescence. It is a figure which shows an example of the operation | movement which concerns on embodiment of this invention. It is a figure which shows an example of the flowchart which shows the operation | movement which concerns on embodiment of this invention. It is a figure which shows an example of the operation | movement which concerns on embodiment of this invention. It is a figure which shows an example of the flowchart which shows the operation | movement which concerns on embodiment of this invention. It is a figure which shows an example of the operation | movement which concerns on embodiment of this invention.

Hereinafter, the best mode for carrying out the present invention will be described with reference to the drawings.

However, the present invention can be implemented in many different modes, and those skilled in the art can easily understand that the modes and details can be variously changed without departing from the spirit and scope of the present invention. Is done. Therefore, the present invention is not construed as being limited to the description of this embodiment mode. Note that in all the drawings for describing the embodiments, the same portions or portions having similar functions are denoted by the same reference numerals, and repetitive description thereof is omitted.
(Embodiment)
In this embodiment, the living tissue is irradiated with at least one of excitation light and illumination light, and the fluorescence image generated by the fluorescence generated from the living tissue that has been irradiated with the excitation light and the illumination light are received. An imaging device that receives an illumination light image reflected by the living tissue reflected by the living tissue by photoelectric conversion, acquires signals representing the fluorescent image and the illumination light image, and outputs the signals as image signals. A control method and a control program for the imaging apparatus will be described.

That is, as a more specific example, an excitation light source as an excitation light irradiation unit is intermittently driven, and an image sensor as a photoelectric conversion unit is driven to perform photoelectric conversion during a period when the excitation light source is not driven. Therefore, it is not necessary to use an optical filter including an optical filter that blocks high-intensity reflected excitation light, and no special image signal processing for color correction is required. An apparatus configuration and a flowchart of an imaging apparatus control method for an apparatus, an imaging apparatus control program for an endoscope apparatus will be described.

Here, a configuration for exerting the function will be described with reference to functional block diagrams shown in FIGS.

FIG. 1 is an external view of an endoscope system including an imaging device of an endoscope apparatus that is an embodiment of a fluorescence observation endoscope apparatus according to the present invention. As shown in FIG. 1, the endoscope system includes a fluorescence observation endoscope 10, an imaging device 20 of the endoscope apparatus, and a monitor 60.

The fluorescence observation endoscope 10 is obtained by adding a modification for fluorescence observation to a normal electronic endoscope, and is inserted into a body cavity. An operation unit 10b having an angle knob or the like for bending the tip of the unit 10a, a light guide flexible tube 10e for connecting the operation unit 10b and the light source processor device 20, and the light guide flexible tube 10e. The connector 10d provided at the base end of is provided.

FIG. 2 is a functional block diagram of the imaging apparatus 20 of the endoscope apparatus in FIG. An imaging device 20 of an endoscope apparatus operates an excitation light source 1 serving as excitation light irradiation means for irradiating a living body with excitation light and a fluorescence observation endoscope 10 in the living body and looks around the affected area of the living body. Illumination light source 2 as illumination light irradiating means for irradiating illumination light, and a light source as illuminating means driving means for driving excitation light source 1 and illumination light source 2 by determining timing of irradiating light from excitation light source 1 and illumination light source 2 The driving circuit 3, the timing generation circuit 4 that outputs a signal for determining timing to the light source driving circuit 3, the transmitter 5 that generates the reference clock in the imaging device 20 of the endoscope apparatus, and the photoelectric of the image sensor 8 Image sensor driving circuit 6 as photoelectric conversion element driving means and stored charge resetting means for determining conversion timing, fluorescence from the affected area of the living body, reflected illumination light, and The lens 7 that receives the radiation excitation light, the image sensor 8 as a photoelectric conversion unit that receives the fluorescence and reflected illumination light from the affected part of the living body and executes photoelectric conversion, and the analog signal output from the image sensor 8 are processed. An image for causing the monitor 60 to operate the fluorescence observation endoscope 10 in the living body from a signal output from the analog front end circuit 9 and the analog front end circuit 9, and a video for displaying a surrounding image including the affected part of the living body And a digital signal processing circuit 10 for generating a signal.

The excitation light source 1 has a function of irradiating excitation light for exciting a fluorescent reagent such as indocyanine injected into a living body (living tissue).

The wavelength of light from the excitation light source 1 is determined by the type of reagent. As an example, in the case of indocyanine, a wavelength in the range of about 750 nm to 780 nm is selected as the excitation light.

Note that a fluorescent reagent such as indocyanine absorbs the energy of excitation light to excite electrons and release excess energy as electromagnetic waves when it returns to the ground state. Therefore, in the case of indocyanine, which generally emits electromagnetic waves (fluorescence) having a wavelength longer than the wavelength of absorbed light and a wavelength in the range of about 750 nm to 780 nm is selected as the excitation light, the wavelength of the fluorescence is about 850 nm. Nearby.

In addition, a transient response is observed in the fluorescence response to the excitation light, and this transient response period is also referred to as a fluorescence lifetime. In the present invention, fluorescence in the fluorescence lifetime that is the transient response period is used. The fluorescence lifetime is a period that starts after the end of irradiation with excitation light (or immediately after the end of irradiation).

As the type of the excitation light source 1, an arbitrary light source including an LED (Light Emitting Diode) and a semiconductor laser can be selected.

The illumination light source 2 is for obtaining an illumination light image (normal observation image) for operating the fluorescence observation endoscope 10 in the living body, and for obtaining an illumination light image for viewing the affected area and the surroundings of the affected area. It has a function of irradiating illumination light.

In the imaging device 20 of the endoscope apparatus according to the present embodiment, a fluorescent image generated by fluorescence generated from the living tissue of the affected area that has been irradiated with the excitation light, and a living body in the living body that has been irradiated with the illumination light and the surrounding living tissue including the affected area. In order to receive the illumination light image by the illumination light reflected by the illumination light source, the illumination light source 2 emits illumination light.

The illumination light image (ordinary observation image) is required because the affected part is identified by observing the periphery of the affected part, and the intra-body-cavity insertion part 10a inserted into the body is manipulated by the operation part 10b having an angle knob or the like. This is because an image inside the body (including the affected part) is necessary.

As the type of illumination light source 2, any light source including an LED and a semiconductor laser can be selected. Further, the wavelength of the light from the illumination light source 2 includes at least a part of the visible light in order for the operator to observe the body including the affected part.

The light source driving circuit 3 has a function of driving the excitation light source 1 and the illumination light source 2, and at least a function of driving the excitation light source 1 intermittently.

The light source drive circuit 3 can drive the illumination light source 2 continuously or drive the illumination light source 2 intermittently while driving the excitation light source 1 intermittently (see FIG. 4).

When the light source driving circuit 3 continuously drives the illumination light source 2 while driving the excitation light source 1 intermittently, the image sensor 8 has a timing when the excitation light source 1 is not driven intermittently (fluorescence lifetime). (Corresponding to t1 in FIG. 4): Fluorescence image due to fluorescence generated from the living tissue of the affected area that has been irradiated with excitation light at the end of irradiation with excitation light).

And the excitation light source 1 drives intermittently the illumination light image by the illumination light reflected when the illumination light irradiated from the illumination light source 2 was irradiated to the affected part and the living tissue of the human body which does not include the affected part. The image sensor 8 receives light at a timing when the fluorescent image is not received and when the fluorescent image is not received.

Specifically, the illumination light image is received by the image sensor 8 after the fluorescence lifetime and during the time until the excitation light source 1 is intermittently driven (corresponding to t2 in FIG. 4).

Alternatively, a plurality of image sensors 8 may be provided. In this case, an illumination light image is received by one of the plurality of image sensors 8 at an arbitrary time when the excitation light source 1 is not intermittently driven. It is also possible to configure such that.

Further, the light source driving circuit 3 has a function of intermittently driving the excitation light source 1 and the illumination light source 2 so as not to be driven simultaneously.

The light source driving circuit 3 has a function of alternately and intermittently driving the excitation light source 1 and the illumination light source 2 so as not to be driven simultaneously (see FIG. 6B).

In this case, the light source driving circuit 3 drives the excitation light source 1 for a predetermined time, and then stops driving the excitation light source 1. The timing at which the illumination light source 2 is intermittently driven in the image sensor 8 (corresponding to the exposure 2 period in FIG. 6): the duration of the fluorescence generated after the irradiation of the excitation light of the exposure 1 in FIG. The illumination light image generated by the illumination light reflected by the living body is received at a predetermined time after completion). (See FIG. 6 (b)).

That is, the light source drive circuit 3 drives the illumination light source 2 for a predetermined time, and the illumination light source 2 performs illumination during the period during which the illumination light source 2 is driven (corresponding to the exposure 2 period in FIG. 6). The image sensor 8 receives an illumination light image generated by the light reflected from the living body.

The excitation light source 1 that is intermittently driven can be driven by an arbitrary signal that is driven intermittently, such as a pulse signal or a substantially sinusoidal signal.

The light source driving circuit 3 has a function of driving at least one of the pulse width of the illumination light emitted from the illumination light source 2 or the luminance of the pulsed illumination light to be arbitrarily changeable (not shown). ). Further, the light source driving circuit 3 has a function of driving at least one of the pulse width of the excitation light emitted from the excitation light source 1 and the luminance of the pulsed excitation light so as to be arbitrarily changed (not shown). ).

The light source driving circuit 3 has a function of driving the excitation light source 1 intermittently by driving at least the excitation light source 1 with a substantially sinusoidal signal (see FIG. 8).

When the fluorescence delay is very short, theoretically, temporal separation is possible by shortening the emission pulse of the excitation light. However, it is actually difficult to control the excitation light source 1 using a rectangular wave at a high frequency. In such a case, the LED is driven by a sine wave as shown in FIG.

Further, the image sensor drive circuit 6 delays the image sensor 8 by a phase difference corresponding to a delay time from irradiation of excitation light to generation of fluorescence with respect to a substantially sinusoidal signal for driving the excitation light source 1. It has a function of driving (see FIG. 8).

For example, as an example, the illumination is modulated at a frequency that is, for example, four times the fluorescence delay time, and the sensor exposure is performed at the portion shown in FIG.

The timing generation circuit 4 generates a timing signal for determining the timing at which the light source driving circuit 3 drives the excitation light source 1 and the illumination light source 2 and the timing at which the image sensor driving circuit 6 drives the image sensor 8.

The image sensor driving circuit 6 has a function of driving the image sensor 8 and performing photoelectric conversion during a period when the excitation light source 1 is not driven by the light source driving circuit 3 (see FIGS. 4 and 6).

The image sensor driving circuit 6 has a function of resetting the charge accumulated in the image sensor 8 immediately before the image sensor 8 is driven by the photoelectric conversion element driving means.

By resetting the charge accumulated in the image sensor 8 immediately before the image sensor 8 is driven, the amount of light received by the image sensor 8 after the reset can be accurately measured. The image sensor 8 may be a monochrome imaging device or a color imaging device.

As is apparent from the above description, the image sensor driving circuit 6 drives the image sensor 8 during a period in which the excitation light source 1 is not driven by the light source driving circuit 3, and receives irradiation of excitation light during the fluorescence lifetime. It has a function of receiving a fluorescent image by fluorescence generated from the living tissue of the affected area and executing photoelectric conversion.

The lens 7 has a function of receiving fluorescence, reflected illumination light, and reflected excitation light from the affected part of the living body.

Since the image sensor drive circuit 6 does not operate the image sensor 8 at the timing when the reflected excitation light passes through the lens 7, the reflected excitation light has no effect on the resulting video signal. In addition, since the photoelectric conversion is not performed by the image sensor 8 at the timing when the reflected excitation light passes through the lens 7, an optical filter that blocks the reflected excitation light is not necessary.

Therefore, the image sensor 8 performs photoelectric conversion of fluorescence and reflected illumination light among the light transmitted through the lens 7.

The analog front end circuit 9 has a function of processing an analog signal output from the image sensor 8.

The digital signal processing circuit 10 displays an image for causing the monitor 60 to operate the fluorescence observation endoscope 10 in the living body and a surrounding image including the affected part of the living body from the signal output from the analog front end circuit 9. A function of generating a video signal;
(Relationship between illumination light, excitation light and fluorescence wavelength bands)
Next, the relationship between the wavelength bands of illumination light, excitation light, and fluorescence will be described with reference to FIG.

FIG. 3A is a diagram showing the relationship between the illumination light, the reagent excitation light, and the fluorescence wavelength band of the reagent when a reagent such as ICG that emits general near-infrared fluorescence is used.

The illumination light is emitted from the illumination light source 1 in a visible light (about 400 nm to about 800 nm) region that can be visually recognized by a human, and the illumination light in the wavelength band is received by the image sensor 8 as an illumination light image.

The excitation light emitted from the excitation light source 1 that is intermittently driven is in the near infrared region, but the fluorescence emitted from the affected area irradiated with the excitation light has a wavelength in the near infrared region that is longer than the excitation light. This is shown in FIG. 3 (a).

The conventional method blocks (attenuates) excitation light with high light intensity so that it is not received by a light-receiving element such as an image sensor. This bandpass is used to receive fluorescence in the near-infrared wavelength band and illumination light in the visible light region. An optical filter was required. For this purpose, it is necessary to make a band pass optical filter having a good cut-off characteristic part of the configuration. Moreover, such an optical filter is expensive, and when the wavelength bands of excitation light and fluorescence change depending on the type of reagent, it is necessary to prepare bandpass optical filters having different wavelength characteristics.

If excitation light with high light intensity cannot be sufficiently attenuated by an optical filter, a part of the excitation light is received by a light receiving element such as an image sensor. For this reason, there has been a problem that the color balance of the obtained video signal is broken and the image observed on the monitor is difficult to see.

FIG. 3B shows the relationship between the wavelength bands of illumination light, excitation light, and fluorescence when using the reagent such as ICG that emits the general near-infrared fluorescence shown in FIG. 3A. In the figure, is the wavelength band of the near-infrared region excitation light emitted from the excitation light source 1 driven intermittently and the near-infrared region fluorescence emitted from the affected area irradiated with the excitation light very close? It is a figure which shows the case where at least one part overlaps.

In this case, even if a conventional optical filter is used, it may be impossible to separate excitation light and fluorescence.

In FIG. 3C, the excitation light emitted from the excitation light source 1 driven intermittently is in the ultraviolet region, and the fluorescence emitted from the affected area irradiated with the excitation light is in the visible light region. It is shown.

In this case, it becomes impossible to separate the illumination light image by the illumination light continuously irradiated and the fluorescence image by using the optical filter, and the conventional method obtains the fluorescence image of the affected area by the reagent. It is not possible.

However, by converting a wavelength axis optical filter using a conventional lens or the like into an electrical time axis filter according to the present invention, the relationship between the wavelength bands of illumination light, excitation light, and fluorescence is shown in FIG. ) And FIG. 3C, it is possible to accurately obtain an illumination light image and a fluorescence image by illumination light as video signals.
(Embodiment 1)
Next, Embodiment 1 of this application is demonstrated using FIG.

FIG. 4 shows a case where the excitation light emitted from the excitation light source 1 is intermittently driven in a pulse shape.

Fluorescence emitted from the affected part of the living body continues to emit a fluorescence image as a fluorescence lifetime only for t1 time after the irradiation of the excitation light emitted from the excitation light source 1 is finished in a pulse shape.

Further, since fluorescence is generated immediately after the excitation light irradiation, the fluorescence is generated even during the period when the excitation light is irradiated.

At the time when the irradiation of the excitation light emitted from the excitation light source 1 ends in a pulse shape, the image sensor drive circuit 6 resets the charge accumulated in the image sensor 8 and is excited after the charge of the image sensor 8 is reset. A fluorescent image corresponding to the light is received.

Thereafter, the fluorescence image received by the image sensor 8 is converted into an image signal as an image that allows the observer to observe the affected area on the monitor 60 via the analog front end circuit 9 and the digital signal processing circuit 10. Is done.

In FIG. 4, the illumination light emitted from the illumination light source 2 is reflected by the living body during the time from the elapse of t1 time, which is the fluorescence lifetime, to the start of the next excitation light irradiation (corresponding to t2 in FIG. 4). The illumination light image formed in this manner may be configured to be received by the image sensor 8.

Thereafter, similarly, the illumination light image received by the image sensor 8 passes through the analog front end circuit 9 and the digital signal processing circuit 10 as an image that reflects the inside of the living body or the periphery of the affected part. Is converted into a video signal as an observable video.

A plurality of image sensors 8 may be provided. In this case, it is possible to configure the illumination light image to be received by one of the plurality of image sensors 8 at an arbitrary time when the excitation light source 1 is not intermittently driven.

In the above case, the light receiving surfaces of the plurality of image sensors 8 may be configured to include an optical filter for receiving an illumination light image and / or an optical filter for receiving a fluorescent image.

When the imaging device of the endoscope apparatus according to the present invention has the above-described configuration, if the substance such as the type of fluorescent compound and the additive to be injected into the living body changes conventionally, The wavelength of the excitation light and the wavelength of the fluorescence for generating the fluorescence may change. Optical such as a bandpass filter, a low wavelength band filter, a high wavelength band filter, etc., adapted to the changed wavelength each time. According to the present invention, it is not necessary to use an optical filter by converting a wavelength axis optical filter such as a lens into an electrical time axis filter. In addition, the mechanical configuration and the electrical configuration of the imaging apparatus of the endoscope apparatus can be simplified, and the cost of the imaging apparatus of the endoscope apparatus can be reduced.

Next, by implementing these functions in the imaging device 20 of the endoscope apparatus of FIG. 2 and utilizing the fluorescence lifetime, a special image signal for color correction using reflected excitation light or the like without using an optical filter is used. A part of the processing operation for realizing a function that makes processing unnecessary will be described with reference to FIG.

FIG. 5 is a processing flowchart showing the timing at which the functions of this embodiment are executed.

In step S10, the light source drive circuit 3 turns on the excitation light source 1.

In step S11, the excitation light from the excitation light source 1 turned on is irradiated toward the affected part (containing the reagent) in the living body.

In step S12, the light source drive circuit 3 turns off the excitation light source 1 and stops the irradiation of the excitation light into the living body.

In step S13, the image sensor drive circuit 6 resets the charge accumulated in the image sensor 8, and drives the image sensor 8 to receive a fluorescent image corresponding to the excitation light after the charge of the image sensor 8 is reset. To do.

In step S14, the image sensor driving circuit 6 photoelectrically converts the fluorescent image received by the image sensor 8 in step S14.

In step S15, the fluorescent image received by the image sensor 8 is converted into an image of the affected area through the analog front end circuit 9 and the digital signal processing circuit 10, and an image signal as an image that allows the observer to observe the affected area on the monitor 60. Is converted to

In step S16, it is determined whether or not the imaging by the imaging device 20 of the endoscope apparatus has been completed. When imaging by the imaging device 20 of the endoscope apparatus is completed (step S16: YES), imaging by the imaging apparatus 20 of the endoscope apparatus is terminated, and imaging by the imaging apparatus 20 of the endoscope apparatus is completed. If not (step S16: NO), the process returns to step S10 to capture the next fluorescent image of the affected area.

In the flowchart showing the above operation, the operation of the illumination light is not described. However, the illumination light source 1 may be continuously turned on to continuously irradiate the illumination light, or intermittently the illumination light. May be driven by the light source driving circuit 3 so as to irradiate.
(Embodiment 2)
Next, a case where the excitation light source 1 and the illumination light source 2 are alternately and intermittently driven so as not to be simultaneously driven by the light source driving circuit 3 will be described with reference to FIG.

In this case, the light source drive circuit 3 drives the excitation light source 1 for a predetermined time and irradiates the excitation light near the affected part of the human body, and then stops driving the excitation light source 1 (FIG. 6C). Corresponds to t3).

Thereafter, the image sensor 8 has a timing at which the excitation light source 1 does not intermittently emit the excitation light and has a fluorescence lifetime (corresponding to the exposure 1 in FIG. 6 and the duration of the fluorescence generated after the end of the excitation light irradiation). ) To receive a fluorescent image due to fluorescence generated from the living tissue of the affected area that has been irradiated with the excitation light.

Thereafter, the light source drive circuit 3 drives the illumination light source 2 for a predetermined time to irradiate the illumination light around the tip of the endoscope of the human body, and stops driving the illumination light source 2 (FIG. 6C). This corresponds to the exposure 2 of the above).

The image sensor 8 is a timing at which the illumination light source 2 is intermittently driven (corresponding to the exposure 2 period in FIG. 6C): fluorescence generated after the irradiation of the excitation light in the exposure 1 in FIG. The illumination light image generated when the illumination light from the illumination light source 2 is reflected by the living body is received at a predetermined time after the end of the duration.

That is, the light source drive circuit 3 drives the illumination light source 2 for a predetermined time, and during the period in which the illumination light source 2 is driven (corresponding to the exposure 2 period in FIG. 5), the image sensor 8 An illumination light image generated when the illumination light from the illumination light source 2 is reflected by the living body is received.

The image sensor driving circuit 6 resets the charge accumulated in the image sensor 8 at the timing when the exposure 2 and exposure 3 periods start (see FIG. 6C).

Next, a flowchart showing a part of this embodiment will be described with reference to FIG.

In the flowchart of FIG. 7, the case where the excitation light source 1 and the illumination light source 2 are alternately and intermittently driven so as not to be simultaneously driven by the light source driving circuit 3 will be described.

In step S20, the light source driving circuit 3 turns on the excitation light source 1.

In step S21, the excitation light is irradiated from the excitation light source 1 that is turned on toward the affected part (containing the reagent) in the living body.

In step S22, the light source drive circuit 3 turns off the excitation light source 1 and stops the irradiation of the excitation light into the living body.

In step S23, the image sensor driving circuit 6 turns on the image sensor 8.

In step S24, the image sensor drive circuit 6 resets the charge accumulated in the image sensor 8, and drives the image sensor 8 so as to receive a fluorescent image corresponding to the excitation light after the charge of the image sensor 8 is reset. To do.

In step S25, the image sensor driving circuit 6 photoelectrically converts the fluorescent image received by the image sensor 8 in step S14. The fluorescent image received by the image sensor 8 is converted as an image of the affected area through the analog front end circuit 9 and the digital signal processing circuit 10 into an image signal as an image that allows the observer to observe the affected area on the monitor 60. Is done.

In step S26, the image sensor drive circuit 6 resets the charge accumulated in the image sensor 8, and after the charge of the image sensor 8 is reset, the image sensor 8 is received so as to receive an illumination light image corresponding to the illumination light. To drive.

In step S27, the light source driving circuit 3 turns on the illumination light source 2.

In step S28, the image sensor driving circuit 6 photoelectrically converts the illumination light image received by the image sensor 8. Then, the illumination light image received by the image sensor 8 is imaged as an image inside the human body via the analog front end circuit 9 and the digital signal processing circuit 10, and an image signal as an image that allows the observer to observe the affected area on the monitor 60 Is converted to

In step S29, the image sensor drive circuit 6 turns off the image sensor 8.

In step S30, the light source drive circuit 3 turns off the illumination light source 2 and stops the illumination light irradiation.

In step S31, it is determined whether or not the imaging by the imaging device 20 of the endoscope apparatus is completed. When imaging by the imaging device 20 of the endoscope apparatus is completed (step S31: YES), imaging by the imaging apparatus 20 of the endoscope apparatus is terminated, and imaging by the imaging apparatus 20 of the endoscope apparatus is completed. If not (step S31: NO), the process returns to step S20, and the next fluorescent image of the affected area is taken.

As described above, according to the operation related to FIG. 7, it is not necessary to use an optical filter by converting an optical filter of a wavelength axis such as a lens into an electric time axis filter. The mechanical configuration and electrical configuration of the apparatus are simplified, and the cost of the imaging apparatus of the endoscope apparatus can be reduced.

Also, since there is no possibility of receiving high intensity reflected excitation light, it is possible to prevent the color balance of the subject from being broken.

Also, there is no possibility of receiving high-intensity reflected excitation light, and it is not necessary to take a wide dynamic range of an electronic circuit including photoelectric conversion, so that the circuit configuration is simplified.

Next, FIG. 8 shows an example in which the excitation light source 1 driven intermittently is driven by a substantially sinusoidal signal.

In this case, the light source driving circuit 3 has a function of driving the excitation light source 1 intermittently by driving at least the excitation light source 1 with a substantially sinusoidal signal.

When the delay of fluorescence (fluorescence lifetime) generated in the affected part of a living body is very short, theoretically, the fluorescence pulse of excitation light and fluorescence is reduced by shortening the emission pulse of excitation light emitted from the excitation light source 1. Can be separated in time. However, in practice, it is difficult to control the excitation light source 1 using a high-frequency rectangular wave. In such a case, the excitation light source 1 such as an LED is driven in a substantially sine wave shape as shown in FIG.

In FIG. 8, the fluorescence generated in the affected area of the living body is received by the image sensor 8 through the lens 7 after a predetermined time (t4 in FIG. 8) from the substantially sinusoidal excitation light.

In this case, in order for the image sensor 8 to efficiently receive the fluorescence generated in the affected part of the living body, the light source driving circuit 3 applies excitation light to the substantially sinusoidal signal that drives the excitation light source 1. It is desirable to drive the image sensor 8 with a delay of a phase difference corresponding to a delay time (t4 in FIG. 8) from irradiation of the light to generation of fluorescence (see FIG. 8).

That is, it is not necessary to have a phase difference exactly by the delay time from the excitation light irradiation to the generation of the fluorescence, and it is possible to receive a fluorescence having a sufficient intensity to form a fluorescence image by the fluorescence received by the image sensor 8 Any difference may be used.

In the case of FIG. 8, the illumination is modulated at a frequency that is, for example, four times the delay time of fluorescence, and the sensor is exposed at the portion shown in FIG. become.
(Embodiment 3)
In the present embodiment, the excitation light source as the excitation light irradiating means is intermittently driven, and the image sensor as the photoelectric conversion means is driven to perform the photoelectric conversion during the period in which the excitation light source is not driven. Even if the brightness of the illumination light is arbitrarily changed and the illumination light image by the illumination light reflected by the living tissue irradiated with the illumination light is brightened or darkened so that doctors and the like are most suitable for surgery, A fluorescence image by fluorescence generated from the biological tissue irradiated with the excitation light; and
An embodiment in which the illumination light image can be clearly visually recognized will be described.

In order to change the illuminance of reflected illumination light (reflected illumination light) that is visible light, two methods can be considered to increase the luminance of the illumination light on the radiation side (in the form of pulses in FIG. 6A). It is conceivable to increase the amplitude of the emitted visible light or to increase the pulse width of the visible light emitted in a pulse form in FIG.

First, as a first case, when the amplitude of the visible light emitted in a pulse shape in FIG. 6A is increased, the illumination luminance of the illumination light source 2 is increased via the light source drive circuit 3 of FIG. become. As shown in FIG. 2, the illumination light source 2 is an independent circuit unit that is separate from the excitation light source 1. Therefore, the luminance can be freely adjusted without correlation with the luminance of the excitation light source 1.

Further, as shown in FIG. 6, the excitation light source as the excitation light irradiating means is intermittently driven, and the image sensor as the photoelectric conversion means is driven to perform the photoelectric conversion during the period when the excitation light source is not driven. Therefore, even if the illuminance of the illumination light image is changed (it can be made very bright) regardless of the fluorescence image with very low illuminance, a clear fluorescence image and a clear illumination light image can be obtained independently. It can be visually recognized by a user such as a doctor.

Next, as a second case, when the pulse width of the visible light emitted in a pulse shape in FIG. 6A is increased, the pulse driving time of the illumination light source 2 via the light source driving circuit 3 in FIG. Will be lengthened. Further, as shown in FIG. 2, the illumination light source 2 is an independent circuit unit that is separate from the excitation light source 1, and therefore is freely irradiated from the illumination light source 2 without correlation with the luminance or pulse width of the excitation light source 1. The pulse width of the illumination light can be adjusted (time t3 and time exposure 2 in FIG. 6A can be set independently and separately. In this case, time t3 + time exposure) 1 + time exposure 2 may be changed, and time t3, time exposure 1 and time exposure 2 may be adjusted to arbitrary times so that time t3 + time exposure 1 + time exposure 2 is constant. .)
Even if the illuminance by the reflected illumination light is changed in this way, as shown in FIG. 6, the excitation light source as the excitation light irradiation means is intermittently driven, and photoelectric conversion is performed during the period when the excitation light source is not driven. Since the image sensor is driven to perform photoelectric conversion as a means, even if the illuminance of the illumination light image is changed (it can be very bright) regardless of the fluorescence image with very small illuminance, A user such as a doctor can visually recognize a clear fluorescent image and a clear illumination light image independently.

As described above, the imaging device of the endoscope apparatus of the present invention may be provided and used in any endoscope apparatus, and can be applied to other reagents having different fluorescence wavelengths.

Further, the above processing can improve the convenience of the imaging apparatus of the endoscope apparatus.

5 and 7 are recorded in advance on a recording medium such as a hard disk or recorded in advance via a network such as the Internet, and are read out and executed by a general-purpose microcomputer or the like. Accordingly, it is possible to cause the general-purpose microcomputer or the like to function as the CPU according to the embodiment.

Furthermore, the present invention is not limited to the above-described embodiments, and various modifications can be made within the scope of the gist of the present invention.

Further, it is to be understood that the embodiments described and illustrated herein are exemplary only and should not be considered as limiting the scope of the present invention. Other changes and modifications may be made in accordance with the spirit and scope of the invention.

DESCRIPTION OF SYMBOLS 1 Excitation light source 2 Illumination light source 3 Light source drive circuit 4 Timing generation circuit 5 Transmitter 6 Image sensor drive circuit 7 Lens 8 Image sensor

Claims

In an imaging apparatus that irradiates at least one of excitation light and illumination light on a biological tissue,
Excitation light irradiation means for irradiating the excitation light;
Irradiation means driving means for driving the excitation light irradiation means;
Photoelectric conversion means for converting the fluorescence generated from the living tissue to which the fluorescent compound has been administered, which has been irradiated with the excitation light, into an electrical signal;
Photoelectric conversion element driving means for determining operation timing of the photoelectric conversion means;
Accumulated charge resetting means for resetting charges accumulated in the photoelectric conversion means;
Comprising
The irradiation means driving means drives the excitation light irradiation means intermittently, and the photoelectric conversion element driving means drives the photoelectric conversion means during a period when the excitation light irradiation means is not driven by the irradiation means driving means. An imaging apparatus characterized by causing photoelectric conversion to be executed.
The imaging device according to claim 1,
Comprising illumination light irradiating means for irradiating the illumination light;
The irradiation means driving means drives the excitation light irradiation means and the illumination light irradiation means,
The photoelectric conversion means converts the fluorescence generated from the biological tissue to which the fluorescent compound is administered, irradiated with the excitation light into an electrical signal, and is reflected by the biological tissue irradiated with the illumination light. An imaging apparatus that converts illumination light into an electrical signal.
The imaging device according to claim 1 or 2,
Immediately before the photoelectric conversion means is driven by the photoelectric conversion element driving means, the accumulated charge reset means resets the charge accumulated in the photoelectric conversion means.
In the imaging device according to claim 2 or 3,
The irradiation means driving means is intermittently driven so as not to drive the excitation light irradiation means and the illumination light irradiation means simultaneously, and the photoelectric conversion element driving means is driven by the irradiation means driving means. An image pickup apparatus that performs photoelectric conversion by driving the photoelectric conversion means during a period in which it is not driven.
The imaging apparatus according to any one of claims 2 to 4,
The irradiation unit driving unit alternately and intermittently drives the excitation light irradiation unit and the illumination light irradiation unit so as not to drive simultaneously, and the photoelectric conversion element driving unit is irradiated with the excitation light by the irradiation unit driving unit. An image pickup apparatus that performs photoelectric conversion by driving the photoelectric conversion means during a period in which the means is not driven.
In the imaging device according to any one of claims 2 to 5,
The imaging device characterized in that the irradiation means driving means can arbitrarily change at least one of a pulse width of illumination light irradiated from the illumination light irradiation means or a luminance of pulsed illumination light. .
In the imaging device according to any one of claims 1 to 6,
The imaging apparatus characterized in that the irradiation means driving means drives the excitation light irradiation means intermittently by driving at least the excitation light irradiation means with a substantially sinusoidal signal.
The imaging apparatus according to claim 7,
The photoelectric conversion element driving means for determining the operation timing of the photoelectric conversion element is from the excitation light irradiation to the generation of the fluorescence with respect to the substantially sinusoidal signal for driving the excitation light irradiation means. An imaging apparatus, wherein the photoelectric conversion element is driven with a delay by a phase difference corresponding to a delay time.
In a control method of an imaging apparatus that irradiates a living tissue with at least one of excitation light and illumination light,
An excitation light irradiation step of irradiating the excitation light;
An irradiation means driving step for driving and irradiating the excitation light in the excitation light irradiation step;
A photoelectric conversion step of converting the fluorescence generated from the living tissue to which the fluorescent compound has been administered, which has been irradiated with the excitation light, into an electrical signal;
A photoelectric conversion element driving step for determining operation timing in the photoelectric conversion step;
An accumulated charge resetting step for resetting charges accumulated in the photoelectric conversion step;
Comprising
In the irradiation means driving step, the excitation light is intermittently driven, and in the photoelectric conversion element driving step, photoelectric conversion in the photoelectric conversion step is executed during a period in which the excitation light is not irradiated in the irradiation means driving step. And a method of controlling the imaging apparatus.
The control method according to claim 9, wherein
An illumination light irradiation step of irradiating the illumination light;
In the irradiation means driving step, the excitation light in the excitation light irradiation step and the illumination light in the illumination light irradiation step are driven and irradiated,
In the photoelectric conversion step, the fluorescence generated from the biological tissue to which the fluorescent compound has been administered, which has been irradiated with the excitation light, is converted into an electrical signal, and the reflection reflected by the biological tissue that has been irradiated with the illumination light A method for controlling an imaging apparatus, comprising converting illumination light into an electrical signal.
A computer included in an imaging apparatus that irradiates biological tissue with at least one of excitation light and illumination light;
Excitation light irradiation means for irradiating the excitation light;
Irradiation means driving means for driving the excitation light irradiation means,
Photoelectric conversion means for converting the fluorescence generated from the living tissue to which the fluorescent compound has been administered, which has been irradiated with the excitation light, into an electrical signal;
Photoelectric conversion element driving means for determining operation timing of the photoelectric conversion means;
Accumulated charge resetting means for resetting charges accumulated in the photoelectric conversion means;
Function as
The irradiation means driving means drives the excitation light irradiation means intermittently, and the photoelectric conversion element driving means drives the photoelectric conversion means during a period when the excitation light irradiation means is not driven by the irradiation means driving means. And a control program for the imaging apparatus, which has a function of executing photoelectric conversion.
A computer included in the imaging apparatus according to claim 11,
Function as illumination light irradiation means for irradiating the illumination light;
The irradiation means driving means drives the excitation light irradiation means and the illumination light irradiation means,
The photoelectric conversion means converts the fluorescence generated from the biological tissue to which the fluorescent compound is administered, irradiated with the excitation light into an electrical signal, and is reflected by the biological tissue irradiated with the illumination light. A control program for an imaging apparatus, which has a function of converting illumination light into an electrical signal.
In the imaging device according to any one of claims 1 to 8,
The image pickup apparatus, wherein the photoelectric conversion element is a color image pickup device.