CN104814721A - Triangular wave frequency coding high spectral imaging measurement system applied to mammary gland - Google Patents

Abstract

The invention discloses a triangular wave frequency coding hyperspectral imaging measurement system applied to mammary glands. A group of monochromatic light sources is distributed on one side of breast tissue samples, and a camera is distributed on the other side of breast tissue samples; a group of monochromatic Each monochromatic light source in the light source is densely arranged on a set hemispherical surface, and a lens is used to converge into a beam of light to form a light source; the camera forms a light source receiving device; a triangular wave with different frequencies and a ratio of 2 times is used to drive a group of monochromatic Each monochromatic light source in the light source, each pixel in the image received by the camera is the monochromatic light combination of each monochromatic light source through the mammary gland; the computer separates the monochromatic light combination to obtain each monochromatic light combination in the monochromatic light combination Based on the contribution of the color light source, the transmission hyperspectral image of the breast can be realized. The invention realizes the high-precision measurement of breast transmission hyperspectral imaging with high speed and large information, and the device of the invention has the advantages of low cost, convenient application and the like, and is suitable for regular home self-examination.

Description

Hyperspectral Imaging Measurement System Applied to Triangular Wave Frequency Encoding of Mammary Gland

technical field

The invention relates to the field of imaging measurement systems, in particular to a hyperspectral imaging measurement system applied to mammary glands with triangular wave frequency encoding.

Background technique

In the prior art, imaging the interior of objects, especially the interior of the human body, has the outstanding advantages of being non-destructive, non-invasive, and non-radiative through light, but so far there is no mammary gland transmission imaging optical measurement system that can be used at home for frequent tumors The reason for the self-inspection is that the existing breast imaging measurement system has high cost, complex operation, and limited accuracy, which cannot meet the needs of breast self-inspection in practical applications.

Contents of the invention

The present invention provides a triangular wave frequency coded hyperspectral imaging measurement system applied to mammary glands. The present invention realizes high-speed, large-information high-precision measurement of mammary gland transmitted light imaging and meets the needs of practical applications. For details, see Described below:

A hyperspectral imaging measurement system applied to mammary glands with triangular wave frequency encoding, the imaging measurement system includes: a group of monochromatic light sources, a camera, and a computer connected externally to the camera; a group of monochromatic light sources are distributed on breast tissue samples on one side of the breast tissue sample, and the camera is distributed on the other side of the breast tissue sample;

Among them, each monochromatic light source in a group of monochromatic light sources is densely arranged on a set hemispherical surface, and a lens is used to converge into a beam of light to form a light source; the camera forms a light source receiving device;

Each monochromatic light source in a group of monochromatic light sources is driven separately by triangular waves with different frequencies and a ratio of 2 times. Each pixel in the image received by the camera is the combination of monochromatic light transmitted by each monochromatic light source through the mammary gland;

The computer separates the monochromatic light combination to obtain the contribution of each monochromatic light source in the monochromatic light combination, thereby realizing the transmission hyperspectral imaging of the breast.

Wherein, the monochromatic light source and the camera are arranged symmetrically on both sides of the breast tissue sample.

Wherein, the monochromatic light source is a laser diode.

In another embodiment, the monochromatic light source is a monochromatic diode.

In another embodiment, the camera is a mobile phone camera.

The beneficial effects of the technical solution provided by the present invention are: the present invention uses triangular waves with different frequencies and a 2-fold ratio to drive the monochromatic light source, and separates the photoelectric signals detected by the camera to obtain each monochromatic light source in the monochromatic light combination contribution, and then realize the imaging of breast tissue samples, the invention realizes the high-precision measurement of high-speed, large-information linear array imaging light, and the invention has the advantages of low cost, convenient application, etc., and is suitable for home self-examination.

Description of drawings

Fig. 1 is a structural schematic diagram of a hyperspectral imaging measurement system applied to triangular wave frequency encoding of mammary glands;

Fig. 2 is a schematic diagram of the relative positions of the monochromatic light source, the breast tissue sample and the camera provided by the present invention;

Fig. 3 is a schematic diagram of a triangular wave.

In the accompanying drawings, the list of parts represented by each label is as follows:

1: A group of monochromatic light sources; 2: Lens;

3: Breast tissue sample; 4: Camera.

Detailed ways

In order to make the purpose, technical solution and advantages of the present invention clearer, the implementation manners of the present invention will be further described in detail below.

Example 1

A hyperspectral image imaging measurement system applied to mammary glands with triangular wave frequency encoding, see Figure 1 and Figure 2, the imaging measurement system includes: a group of n monochromatic light sources 1 (denoted by LD, the wavelength of the monochromatic light source is between 600 ~ Between 1200nm, this wave band is " optical window ", and penetration depth is relatively deep) and a camera 4, (wherein, the specific value of n is related to the sensitivity of breast tissue sample 3 to different wavelengths, the embodiment of the present invention is to this No limitation); a group of monochromatic light sources 1 are distributed on one side of the breast tissue sample 3, and a camera 4 is distributed on the other side of the breast tissue sample 3;

Among them, each monochromatic light source LD ₁ ... LD _n in a group of monochromatic light sources 1 is densely arranged on a set hemispherical surface, and the lens 2 is used to converge into a beam of light to form a line array light source; the camera 4 forms a multi-wavelength light source to receive device, the camera 4 is CMOS or CCD, and the existing camera 4 has been able to collect light in the near-infrared band. The imaging measurement system also includes a computer (not shown in the figure) connected externally to the camera 4 .

Referring to Fig. 3, triangular waves with different frequencies and a ratio of 2 times are used to respectively drive each monochromatic light source LD _i in a group of monochromatic light sources 1, and the camera 4 collects them. In the collected images, each pixel is for each The monochromatic light source LD _i passes through the monochromatic light combination I _ij of the breast tissue sample 3; the computer separates the monochromatic light combination I _ij to obtain the contribution of each monochromatic light source LD _i in the monochromatic light combination I _ij , which constitutes each Transmission images at wavelengths. According to the different optical characteristics of normal tissue and tumor tissue in breast tissue at each wavelength, the transmitted light imaging measurement of breast is performed to realize early detection of tumors.

Wherein, the steps for the computer to separate the monochromatic light combination I _ij to obtain the contribution of each monochromatic light source LD _i in the monochromatic light combination I _ij are as follows:

1) Assuming that the photoelectric signal is sampled at a speed 4M times faster than the highest frequency f _max of LD _j driving a monochromatic light source, f _s =4M×f _max , to obtain a sampling signal x(m), where M is a positive integer greater than or equal to 1;

$\mathrm{<span\; class="notranslate">\; x</span>}<span\; class="notranslate">\; (</span>\mathrm{<span\; class="notranslate">\; m</span>}<span\; class="notranslate">\; )</span><span\; class="notranslate">\; =</span>\underset{\mathrm{<span\; class="notranslate">\; i</span>}<span\; class="notranslate">\; =</span>\mathrm{<span\; class="notranslate">\; 0</span>}}{\overset{\mathrm{<span\; class="notranslate">\; m</span>}<span\; class="notranslate">\; -</span>\mathrm{<span\; class="notranslate">\; 1</span>}}{\mathrm{<span\; class="notranslate">\; \&Sigma;</span>}}}\mathrm{<span\; class="notranslate">\; x</span>}<span\; class="notranslate">\; (</span>\mathrm{<span\; class="notranslate">\; 4</span>}\mathrm{<span\; class="notranslate">\; lm</span>}<span\; class="notranslate">\; -</span>\mathrm{<span\; class="notranslate">\; i</span>}<span\; class="notranslate">\; )</span><span\; class="notranslate">\; ,</span>\mathrm{<span\; class="notranslate">\; l</span>}<span\; class="notranslate">\; =</span>\mathrm{<span\; class="notranslate">\; 0,1,2</span>}<span\; class="notranslate">\; ,</span><span\; class="notranslate">\; .</span><span\; class="notranslate">\; .</span><span\; class="notranslate">\; .</span><span\; class="notranslate">\; .</span><span\; class="notranslate">\; .</span><span\; class="notranslate">\; .</span><span\; class="notranslate">\; -</span><span\; class="notranslate">\; -</span><span\; class="notranslate">\; -</span><span\; class="notranslate">\; (</span>\mathrm{<span\; class="notranslate">\; 1</span>}<span\; class="notranslate">\; )</span>$

2) The computer will accumulate the sampling signals in the positive and negative half periods of each triangle wave period corresponding to each wavelength, and perform a difference operation on the accumulated results;

That is, the cumulative sum is obtained by accumulating the sampling values of the positive half period of each triangular wave within a certain period of time (integer number of triangular wave periods), and the cumulative sum is obtained by accumulating the sampling values of the negative half period of each triangular wave. Subtract.

3) The above-mentioned differences of each wavelength are accumulated for k cycles or integer multiples of k cycles, wherein:

$\mathrm{<span\; class="notranslate">\; k</span>}<span\; class="notranslate">\; =</span>\frac{\mathrm{<span\; class="notranslate">\; a</span>}\frac{\mathrm{<span\; class="notranslate">\; 1</span>}}{{\mathrm{<span\; class="notranslate">\; f</span>}}_{\mathrm{<span\; class="notranslate">\; min</span>}}}}{\frac{\mathrm{<span\; class="notranslate">\; 1</span>}}{{\mathrm{<span\; class="notranslate">\; f</span>}}_{\mathrm{<span\; class="notranslate">\; no</span>}}}}<span\; class="notranslate">\; -</span><span\; class="notranslate">\; -</span><span\; class="notranslate">\; -</span><span\; class="notranslate">\; (</span>\mathrm{<span\; class="notranslate">\; 2</span>}<span\; class="notranslate">\; )</span>$

In the formula: f _min is the lowest frequency in the excitation triangular wave; a is a preset constant, the value is a positive integer greater than or equal to 1, a/f _min is the period of down-sampling; f _n is the excitation frequency of the triangular wave of the processed wavelength .

For the sampled value whose amplitude is x, if N(>>1) points are evenly sampled and averaged within a certain period of time, the average value obtained is

$\stackrel{<span\; class="notranslate">\; \&OverBar;</span>}{\mathrm{<span\; class="notranslate">\; x</span>}}<span\; class="notranslate">\; =</span>\frac{\mathrm{<span\; class="notranslate">\; 1</span>}}{\mathrm{<span\; class="notranslate">\; N</span>}}\underset{\mathrm{<span\; class="notranslate">\; i</span>}<span\; class="notranslate">\; =</span>\mathrm{<span\; class="notranslate">\; 1</span>}}{\overset{\mathrm{<span\; class="notranslate">\; N</span>}}{\mathrm{<span\; class="notranslate">\; \&Sigma;</span>}}}<span\; class="notranslate">\; [</span>{\mathrm{<span\; class="notranslate">\; x</span>}}_{\mathrm{<span\; class="notranslate">\; i</span>}}<span\; class="notranslate">\; ]</span><span\; class="notranslate">\; =</span>\frac{\mathrm{<span\; class="notranslate">\; 1</span>}}{\mathrm{<span\; class="notranslate">\; N</span>}}\mathrm{<span\; class="notranslate">\; N</span>}<span\; class="notranslate">\; (</span><span\; class="notranslate">\; [</span>\mathrm{<span\; class="notranslate">\; x</span>}<span\; class="notranslate">\; ]</span><span\; class="notranslate">\; +</span>{\mathrm{<span\; class="notranslate">\; \&Delta;x</span>}}_{\mathrm{<span\; class="notranslate">\; i</span>}}<span\; class="notranslate">\; )</span><span\; class="notranslate">\; =</span><span\; class="notranslate">\; [</span>\mathrm{<span\; class="notranslate">\; x</span>}<span\; class="notranslate">\; ]</span><span\; class="notranslate">\; +</span>{\mathrm{<span\; class="notranslate">\; \&Delta;x</span>}}_{\mathrm{<span\; class="notranslate">\; i</span>}}<span\; class="notranslate">\; -</span><span\; class="notranslate">\; -</span><span\; class="notranslate">\; -</span><span\; class="notranslate">\; (</span>\mathrm{<span\; class="notranslate">\; 3</span>}<span\; class="notranslate">\; )</span>$

Wherein, [x] is the quantization of x by the analog-to-digital converter, that is, a positive integer obtained by rounding off. x _i is the amplitude of point i, and [ _xi ] is the quantization of x _i by the analog-to-digital converter, that is, a positive integer obtained by rounding off.

Equation (3) shows that sampling a relatively "clean" signal multiple times to average does not improve its accuracy, and the error of the obtained average value is the same as that of a single sampling, which is Δx _i .

If the sampled sawtooth wave with an amplitude of x is uniformly sampled at N(>>1) points within a certain period of time and averaged, the average value obtained is

$\stackrel{<span\; class="notranslate">\; \&OverBar;</span>}{\mathrm{<span\; class="notranslate">\; x</span>}}<span\; class="notranslate">\; =</span>\frac{\mathrm{<span\; class="notranslate">\; 1</span>}}{\mathrm{<span\; class="notranslate">\; N</span>}}\underset{\mathrm{<span\; class="notranslate">\; i</span>}<span\; class="notranslate">\; =</span>\mathrm{<span\; class="notranslate">\; 1</span>}}{\overset{\mathrm{<span\; class="notranslate">\; N</span>}}{\mathrm{<span\; class="notranslate">\; \&Sigma;</span>}}}<span\; class="notranslate">\; [</span>{\mathrm{<span\; class="notranslate">\; x</span>}}_{\mathrm{<span\; class="notranslate">\; i</span>}}<span\; class="notranslate">\; ]</span><span\; class="notranslate">\; =</span>\frac{\mathrm{<span\; class="notranslate">\; 1</span>}}{\mathrm{<span\; class="notranslate">\; N</span>}}\underset{\mathrm{<span\; class="notranslate">\; i</span>}<span\; class="notranslate">\; =</span>\mathrm{<span\; class="notranslate">\; 1</span>}}{\overset{\mathrm{<span\; class="notranslate">\; N</span>}}{\mathrm{<span\; class="notranslate">\; \&Sigma;</span>}}}<span\; class="notranslate">\; [</span>{\mathrm{<span\; class="notranslate">\; m</span>}}_{\mathrm{<span\; class="notranslate">\; i</span>}}<span\; class="notranslate">\; +</span>{\mathrm{<span\; class="notranslate">\; \&Delta;x</span>}}_{\mathrm{<span\; class="notranslate">\; i</span>}}<span\; class="notranslate">\; ]</span><span\; class="notranslate">\; -</span><span\; class="notranslate">\; -</span><span\; class="notranslate">\; -</span><span\; class="notranslate">\; (</span>\mathrm{<span\; class="notranslate">\; 4</span>}<span\; class="notranslate">\; )</span>$

Wherein, x _i =m _i + _{Δxi , m i =[xi ] .} That is to say, _{mi is rounded to obtain a positive integer, and Δx i is} a "random" error discarded after being rounded.

Formula (4) can be further obtained by using the arithmetic series summation formula:

$\begin{array}{c}\stackrel{<span\; class="notranslate">\; \&OverBar;</span>}{\mathrm{<span\; class="notranslate">\; x</span>}}<span\; class="notranslate">\; =</span>\frac{\mathrm{<span\; class="notranslate">\; 1</span>}}{\mathrm{<span\; class="notranslate">\; N</span>}}\underset{\mathrm{<span\; class="notranslate">\; i</span>}<span\; class="notranslate">\; =</span>\mathrm{<span\; class="notranslate">\; 1</span>}}{\overset{\mathrm{<span\; class="notranslate">\; N</span>}}{\mathrm{<span\; class="notranslate">\; \&Sigma;</span>}}}{\mathrm{<span\; class="notranslate">\; m</span>}}_{\mathrm{<span\; class="notranslate">\; i</span>}}<span\; class="notranslate">\; +</span>\frac{\mathrm{<span\; class="notranslate">\; 1</span>}}{\mathrm{<span\; class="notranslate">\; N</span>}}\underset{\mathrm{<span\; class="notranslate">\; i</span>}<span\; class="notranslate">\; =</span>\mathrm{<span\; class="notranslate">\; 1</span>}}{\overset{\mathrm{<span\; class="notranslate">\; N</span>}}{\mathrm{<span\; class="notranslate">\; \&Sigma;</span>}}}{\mathrm{<span\; class="notranslate">\; \&Delta;x</span>}}_{\mathrm{<span\; class="notranslate">\; i</span>}}<span\; class="notranslate">\; =</span>\frac{\mathrm{<span\; class="notranslate">\; 1</span>}}{\mathrm{<span\; class="notranslate">\; N</span>}}\frac{\mathrm{<span\; class="notranslate">\; 1</span>}}{\mathrm{<span\; class="notranslate">\; 2</span>}}<span\; class="notranslate">\; (</span>\mathrm{<span\; class="notranslate">\; 0</span>}<span\; class="notranslate">\; +</span><span\; class="notranslate">\; [</span>\mathrm{<span\; class="notranslate">\; x</span>}<span\; class="notranslate">\; ]</span><span\; class="notranslate">\; )</span>\mathrm{<span\; class="notranslate">\; N</span>}<span\; class="notranslate">\; +</span>\frac{\mathrm{<span\; class="notranslate">\; 1</span>}}{\mathrm{<span\; class="notranslate">\; N</span>}}\underset{\mathrm{<span\; class="notranslate">\; i</span>}<span\; class="notranslate">\; =</span>\mathrm{<span\; class="notranslate">\; 1</span>}}{\overset{\mathrm{<span\; class="notranslate">\; N</span>}}{\mathrm{<span\; class="notranslate">\; \&Sigma;</span>}}}{\mathrm{<span\; class="notranslate">\; \&Delta;x</span>}}_{\mathrm{<span\; class="notranslate">\; i</span>}}\\ <span\; class="notranslate">\; =</span>\frac{\mathrm{<span\; class="notranslate">\; 1</span>}}{\mathrm{<span\; class="notranslate">\; 2</span>}}<span\; class="notranslate">\; [</span>\mathrm{<span\; class="notranslate">\; x</span>}<span\; class="notranslate">\; ]</span><span\; class="notranslate">\; +</span>\frac{\mathrm{<span\; class="notranslate">\; 1</span>}}{\mathrm{<span\; class="notranslate">\; N</span>}}\underset{\mathrm{<span\; class="notranslate">\; i</span>}<span\; class="notranslate">\; =</span>\mathrm{<span\; class="notranslate">\; 1</span>}}{\overset{\mathrm{<span\; class="notranslate">\; N</span>}}{\mathrm{<span\; class="notranslate">\; \&Sigma;</span>}}}{\mathrm{<span\; class="notranslate">\; \&Delta;x</span>}}_{\mathrm{<span\; class="notranslate">\; i</span>}}\end{array}<span\; class="notranslate">\; -</span><span\; class="notranslate">\; -</span><span\; class="notranslate">\; -</span><span\; class="notranslate">\; (</span>\mathrm{<span\; class="notranslate">\; 5</span>}<span\; class="notranslate">\; )</span>$

The first term in formula (5) is the quantized value, although it is half smaller than the result of formula (3), but according to the error theory, the accuracy of a data will not be changed by multiplying by a fixed non-zero constant. However, the latter item is a random number with zero mean value, which is lower than that in (3) Therefore, oversampling the sawtooth wave or triangular wave excitation signal can also achieve the effect of improving the accuracy, and there is no need to add high-frequency disturbance signals.

In the embodiments of the present invention, unless otherwise specified, the models of the devices are not limited, as long as they can complete the above functions.

Example 2

A triangular-wave frequency-encoded hyperspectral imaging measurement system applied to mammary glands, see Fig. 1 and Fig. 2 , this embodiment uses laser diodes as monochromatic light sources LD ₁ ... LD _n as an example for illustration.

Each laser diode LD _i in a group of monochromatic light sources 1 is respectively driven by triangular waves with different frequencies and a ratio of 2 times _. The color light combination I _ij ; the computer can separate the monochromatic light combination I _ij to obtain the contribution of each laser diode LD _i in the monochromatic light combination I _ij , based on which the transmission hyperspectral image of the breast tissue sample 3 can be performed.

The computer processing steps in this embodiment are the same as those in Embodiment 1, and will not be repeated here in this embodiment.

In the embodiments of the present invention, unless otherwise specified, the models of the devices are not limited, as long as they can complete the above functions.

Example 3

A triangular-wave frequency-encoded hyperspectral imaging measurement system applied to mammary glands, see Fig. 1 and Fig. 2 , this embodiment uses monochromatic diodes as monochromatic light sources LD ₁ ... LD _n as an example for illustration.

Triangular waves with different frequencies and a ratio of 2 times are used to respectively drive each monochromatic diode LD _i in a group of monochromatic light sources 1 , and each pixel in the camera 4 receives each monochromatic diode LD _i through the breast tissue sample 3 The monochromatic light combination I _ij ; the computer can separate the monochromatic light combination I _ij to obtain the contribution of each monochromatic diode LD _i in the monochromatic light combination I _ij , and accordingly the transmission hyperspectral image of the breast tissue sample 3 can be obtained imaging.

The computer processing steps in this embodiment are the same as those in Embodiment 1, and will not be repeated here in this embodiment.

In the embodiments of the present invention, unless otherwise specified, the models of the devices are not limited, as long as they can complete the above functions.

Example 4

A triangular-wave frequency-encoded hyperspectral image measurement system applied to mammary glands, see Fig. 1 and Fig. 2. In this embodiment, a laser diode is used as a monochromatic light source LD ₁ ... LD _n and a mobile phone camera is used as a camera as an example for illustration.

Each laser diode LD _i in a group of monochromatic light sources 1 is respectively driven by triangular waves with different frequencies and a ratio of 2 times, and each pixel in the mobile phone camera 4 receives the signal transmitted by each laser diode LD _i through the breast tissue sample 3 The monochromatic light combination I _ij ; the computer can separate the monochromatic light combination I _ij to obtain the contribution of each laser diode LD _i in the monochromatic light combination I _ij , based on which the transmission hyperspectral image of the breast tissue sample 3 can be performed.

The computer processing steps in this embodiment are the same as those in Embodiment 1, and will not be repeated here in this embodiment.

In the embodiments of the present invention, unless otherwise specified, the models of the devices are not limited, as long as they can complete the above functions.

Example 5

A triangular-wave frequency-encoded hyperspectral image measurement system applied to mammary glands, see Fig. 1 and Fig. 2 , this embodiment uses a monochromatic diode as a monochromatic light source LD ₁ ... LD _n and a mobile phone camera as a camera as an example for illustration.

Triangular waves with different frequencies and a ratio of 2 times are used to drive each monochrome diode LD _i in a group of monochrome light sources 1 respectively, and each pixel in the mobile phone camera 4 receives each monochrome diode LD _i through the breast tissue sample The monochromatic light combination I _ij of 3; the computer can separate the monochromatic light combination I _ij to obtain the contribution of each laser diode LD _i in the monochromatic light combination I _ij , and accordingly the transmission hyperspectral image of the breast tissue sample 3 can be obtained imaging.

The computer processing steps in this embodiment are the same as those in Embodiment 1, and will not be repeated here in this embodiment.

In the embodiments of the present invention, unless otherwise specified, the models of the devices are not limited, as long as they can complete the above functions.

Those skilled in the art can understand that the accompanying drawing is only a schematic diagram of a preferred embodiment, and the serial numbers of the above-mentioned embodiments of the present invention are for description only, and do not represent the advantages and disadvantages of the embodiments.

The above descriptions are only preferred embodiments of the present invention, and are not intended to limit the present invention. Any modifications, equivalent replacements, improvements, etc. made within the spirit and principles of the present invention shall be included in the protection of the present invention. within range.

Claims (5)

1. be applied to a high-spectrum imaging measurement system for the triangular wave frequency coding of mammary gland, described imaging measurement system comprises: one group of monochromater, photographic head, and the computer external with photographic head; It is characterized in that, one group of monochromater is distributed in the side of mammary gland tissue sample, and photographic head is distributed in the opposite side of mammary gland tissue sample;

Wherein, each monochromater dense arrangement in one group of monochromater, on a set hemisphere face, adopts lens to pool light beam, forms light source; Photographic head forms light source receiver part;

Adopt different frequency and become the triangular wave of 2 times of ratio to drive each monochromater in one group of monochromater respectively, in the image that photographic head receives, to be each monochromater combine through the monochromatic light of mammary gland each pixel;

Computer is separated the contribution of each monochromater obtained in monochromatic light combination to monochromatic light combination, realize the transmission high-spectrum imaging to mammary gland accordingly.

2. a kind of high-spectrum imaging measurement system being applied to the triangular wave frequency coding of mammary gland according to claim 1, it is characterized in that, described monochromater, described photographic head are symmetrical arranged on described mammary gland tissue sample two sides.

3. a kind of high-spectrum imaging measurement system being applied to the triangular wave frequency coding of mammary gland according to claim 1 and 2, it is characterized in that, described monochromater is laser diode.

4. a kind of high-spectrum imaging measurement system being applied to the triangular wave frequency coding of mammary gland according to claim 1 and 2, it is characterized in that, described monochromater is monochrome photodiode.

5. a kind of high-spectrum imaging measurement system being applied to the triangular wave frequency coding of mammary gland according to claim 1 and 2, it is characterized in that, described photographic head is mobile phone camera.