Optical Sensor System for 3D Jones Matrix Reconstruction of Optical Anisotropy Maps of Self-Assembled Polycrystalline Soft Matter Films

Figure 1 shows a diagram of the polarization interferometry of Jones layer-by-layer distributions of dehydrated films JMI [ 46 , 47 , 49 ].

1. Two states of linear polarisation are sequentially formed in the “irradiating” ( I r ) and “reference” ( R e ) parallel laser beams– I r ( 0 ° ) − Re ⁡ ( 0 ° ) ≡ p i I r ( 90 ° ) − Re ⁡ ( 90 ° ) ≡ r . 2. For each of the polarization states ( p and r ), two partial interference patterns are recorded through the polarizer-analyzer 14 with the orientation of the transmission plane at angles Ω = 0 ° ; Ω = 90 ° . 3. Analytical processing of microscopic interference images of dehydrated film samples was carried out using the digital Fourier transform F υ , ν [ 49 ]: (26) F 0 ; 90 υ , ν = 1 M × N ∑ m = 0 M − 1 ∑ n = 0 N − 1 I x , y Ω = 0 ° ; 90 ° exp ⁡ − i 2 π m × υ M + n × ν N . where I x 0 Ω = 0 ° m , n = U x 0 Ω = 0 ° m , n U x 0 * Ω = 0 ° m , n ; I x 90 Ω = 90 ° m , n = U x 90 Ω = 90 ° m , n U x 90 * Ω = 90 ° m , n I y 0 Ω = 0 ° m , n = U y 0 Ω = 0 ° m , n U y 0 * Ω = 0 ° m , n I y 90 Ω = 90 ° m , n = U y 90 Ω = 90 ° m , n U y 90 * Ω = 90 ° m , n U x , y 0,90 , orthogonal components of complex amplitude for different orientations, Ω = 0 ° ; Ω = 90 ° ; * denotes the complex conjugation operation; υ , ν are the spatial frequencies and m = 1120 , n = 960 are the number of pixels of the CCD camera 4. The results of the digital Fourier transform (Relations (25), (26)) are used to obtain distributions of complex amplitudes according to the following algorithms: (27) Ω 0 0 → U x 0 Ω = 0 ° ; Ω 9 0 0 → U x 90 Ω = 90 ° exp ⁡ i φ x 90 − φ x 0 ; (28) Ω 0 0 → U y 0 Ω = 0 ° ; Ω 9 0 0 → U y 90 Ω = 90 ° exp ⁡ i φ y 90 − φ y 0 5. By means of stepwise ( Δ θ ) phase ( θ k ) scanning of the reconstructed field of complex amplitudes (Relations (27), (28)) using Algorithms (20)–(25), we obtain coordinate distributions of the optical birefringence parameters J T θ k , m × n .

The resulting set of optical anisotropy maps f ≡ L B θ k , m , n ; C B θ , m , n was analyzed in a statistical approach using the following algorithms to calculate mean ( Z 1 ), variance ( Z 2 ), skewness ( Z 3 ) and kurtosis ( Z 4 ) [ 43 , 44 , 45 , 46 , 47 , 48 , 49 , 50 , 51 ] (29) Z 1 = 1 K ∑ j = 1 K f j ; Z 2 = 1 K ∑ j = 1 K f 2 j ; Z 3 = 1 Z 2 3 1 K ∑ j = 1 K f 3 j ; Z 4 = 1 Z 2 4 1 K ∑ j = 1 K f 4 j , where K = M × N —CCD pixels quantity.

The search for the most sensitive phase plane was carried out as follows. 1. At the first stage: Discrete phase scanning was carried out in “maximum” increments Δ θ k m a x = 0.25   rad . Using Relations (20)–(25), birefringence maps were calculated f ≡ L B θ k , m , n ; C B θ , m , n . Central statistical moments Z i = 1 ; 2 ; 3 ; 4 were calculated for the optical anisotropy distributions f ≡ L B θ k , m , n ; C B θ , m , n . The differences between the obtained values of the statistical parameters were assessed Δ Z i k = Z i θ j + 1 m a x − Z i θ j m a x . The phase interval Δ θ * = θ j + 1 m a x ÷ θ j m a x was determined, within which the monotonic increase in the value ends Δ Z i = ( Z i θ j + 1 m a x − Z i θ j m a x ) ≤ 0 . The macrointerval phase found Δ θ * was analyzed again in finer increments Δ θ q m i n = 0.05   rad − Δ Z i = Z i θ j + 1 m i n − Z i θ j m i n . The new (most sensitive) phase section θ * was determined, in which Δ Z i θ * = m a x . Discrete phase scanning was carried out in “maximum” increments Δ θ k m a x = 0.25   rad . Using Relations (20)–(25), birefringence maps were calculated f ≡ L B θ k , m , n ; C B θ , m , n . Central statistical moments Z i = 1 ; 2 ; 3 ; 4 were calculated for the optical anisotropy distributions f ≡ L B θ k , m , n ; C B θ , m , n . The differences between the obtained values of the statistical parameters were assessed Δ Z i k = Z i θ j + 1 m a x − Z i θ j m a x . The phase interval Δ θ * = θ j + 1 m a x ÷ θ j m a x was determined, within which the monotonic increase in the value ends Δ Z i = ( Z i θ j + 1 m a x − Z i θ j m a x ) ≤ 0 . The macrointerval phase found Δ θ * was analyzed again in finer increments Δ θ q m i n = 0.05   rad − Δ Z i = Z i θ j + 1 m i n − Z i θ j m i n . The new (most sensitive) phase section θ * was determined, in which Δ Z i θ * = m a x . 2. In this plane θ * , the mean Δ Z ¯ i = 1 ; 2 ; 3 ; 4 * and standard deviations σ Δ Z i * are determined Therefore, prostate tumor diagnosis, for each of the statistical moments Z i = 1 ; 2 ; 3 ; 4 the sensitivity (30) ( S e 12 f = a 12 a 12 + b 12 100 % ;   S e 34 f = a 34 a 34 + b 34 100 ) , specificity (31) ( S p 12 f = c 12 c 12 + d 12 100 % ;   S p 34 f = c 34 c 34 + d 34 100 % ) and balanced accuracy (32) ( A c 12 f = 0.5 S e 12 + S p 12 ;   A c 34 f = 0.5 S e 34 + S p 34 ) were calculated [ 56 , 57 , 58 , 59 ]. Here, a 12 a 34 and b 12 b 34 are the number of correct and incorrect diagnoses within investigation group 2 (group 4); and c 12 c 34 and d 12 d 34 are the same within control group 1 (group 3).

Blood and saliva samples were taken for the purpose of determination of the prostate tumor [ 60 , 61 , 62 , 63 ]. Experimental blood plasma samples were obtained by centrifugation. Liquid drops with a volume of 10 μL were applied onto optically homogeneous glass heated to the temperature of the human body (36.6 °C). The process of complete drying (dehydration) lasted 45–50 min. Experimental saliva samples were obtained by taking 2–3 mL of liquid into a test tube and settling it until the mucin proteins precipitated. Then, by centrifugation, the liquid and sedimentary components were separated. A drop of liquid with a volume of 10 μL was applied to optically homogeneous glass heated to the temperature of the human body (36.6 °C). The process of complete drying (dehydration) lasted 40–45 min. The main biochemical components of blood plasma are water (90%), proteins (7%), organic nonprotein compounds (2%), salts (1%). Protein composition—60% albumin, 40% globulin. It is known [ 62 ] that in the process of blood plasma dehydration, a dry (polycrystalline) drop is formed, which contains three zones: “outer”—an annular ridge, which almost entirely consists of linearly birefringent needlelike albumin crystals ( h ~ 12   μ m − 15   μ m ); “transitional”—circularly birefringent structure of globulin crystals with a small content of albumin crystals and optically isotropic crystals of NaCl salt ( h ~ 10   μ m − 12   μ m ); “Central”—solid crystals of NaCl salt ( h ~ 7   μ m − 10   μ m ). “outer”—an annular ridge, which almost entirely consists of linearly birefringent needlelike albumin crystals ( h ~ 12   μ m − 15   μ m ); “transitional”—circularly birefringent structure of globulin crystals with a small content of albumin crystals and optically isotropic crystals of NaCl salt ( h ~ 10   μ m − 12   μ m ); “Central”—solid crystals of NaCl salt ( h ~ 7   μ m − 10   μ m ). The composition of saliva and blood plasma is correlated with each other. Saliva contains the same protein fractions as blood plasma—albumin and globulins. At the same time, among them, there are significantly fewer albumins and four times more globulins. When a saliva drop is dehydrated, the crystallization results differ significantly from the polycrystalline structure of a blood plasma drop. This is due to the lower concentration of albumin and globulin proteins in saliva. Therefore, the marginal protein roll is not formed. A dry drop of saliva has the form of a film quasi-uniform in thickness ( h ~ 10   μ m ÷ 15   μ m ), where optically isotropic dendritic networks of cubic crystals of NaCl salt are localized. Such a film contains, in the form of domains, large (linearly birefringent needlelike albumin crystals) and small (circularly birefringent globulin crystals) optically anisotropic aggregates with a range of sizes h = 10   μ m ÷ 500   μ m . Four representative groups of blood plasma and saliva polycrystalline films were formed: Group 1 consisted of n = 36 samples of BPF from healthy donors; Group 2 consisted of n = 36 samples of BPF films of patients with moderately differentiated adenocarcinoma (3 + 4; 4 + 3 on Gleason’s Pattern scale-ISUP grade 2–3); Group 3 consisted of n = 36 SF samples from healthy donors. Group 4 consisted of n = 36 SF samples from patients with moderately differentiated adenocarcinoma (3 + 4; 4 + 3 on Gleason’s Pattern scale-ISUP grade 2–3). Group 1 consisted of n = 36 samples of BPF from healthy donors; Group 2 consisted of n = 36 samples of BPF films of patients with moderately differentiated adenocarcinoma (3 + 4; 4 + 3 on Gleason’s Pattern scale-ISUP grade 2–3); Group 3 consisted of n = 36 SF samples from healthy donors. Group 4 consisted of n = 36 SF samples from patients with moderately differentiated adenocarcinoma (3 + 4; 4 + 3 on Gleason’s Pattern scale-ISUP grade 2–3).

The results of 3D Jones scanning of the BPF and SF from the control (group 1 and group 3) and experimental (group 2 and group 4) for the experimentally optimal phase planes ( θ b l o o d * δ = 0.35   r a d ; θ s a l i v a * δ = 0.35   r a d and θ b l o o d * ω = 0.25   r a d ; θ s a l i v a * ω = 0.25   r a d ; ) are shown in a series of fragments in Figure 2 and Figure 3 . On a series of fragments of Figure 2 and Figure 3 represent, reconstructed by Jones matrix tomography, coordinate distributions (optical anisotropy maps) of linear L B θ * , m , n (Fragments (1),(2)) and circular C B θ * , m , n (Fragments (3),(4)) birefringence of supramolecular networks of dehydrated plasma films ( Figure 2 ) and saliva ( Figure 3 ) of healthy donors (Fragments (1), (3)) and prostate cancer patients (Fragments (2), (4)). Comparison of the obtained data revealed a correlation between the model analysis (Ratios (1)–(25)) and the experimental results ( Figure 2 and Figure 3 ). Namely: The presence of mechanisms of linear L B θ * , m , n and circular C B θ * , m , n birefringence of supramolecular networks of dehydrated films of biological fluids with different morphological architectonics ( Figure 2 and Figure 3 ). Individual topographic structure of maps of various birefringence mechanisms L B and C B , which are formed dendritic (Fragments (1), (2)) and spherulitic (Fragments (1), (2)) components of optically anisotropic supramolecular networks of biological crystals of dehydrated blood plasma films ( Figure 2 ) and saliva ( Figure 3 ). Insignificant differences (the magnitude of the average and the amplitude of fluctuations) between topographic maps of linear birefringence of L B θ * , m , n dendritic components of optically anisotropic architectonics of dehydrated plasma films ( Figure 2 ) and saliva ( Figure 3 ) of healthy donors (Fragments (1)) and prostate cancer patients (Fragments (2)). A significant increase in the circular birefringence of C B θ * , m , n spherulite components of the optically anisotropic architectonics of dehydrated plasma films ( Figure 2 ) and saliva ( Figure 3 ) of healthy donors (Fragments (3)) and prostate cancer patients (Fragments (4)). The presence of mechanisms of linear L B θ * , m , n and circular C B θ * , m , n birefringence of supramolecular networks of dehydrated films of biological fluids with different morphological architectonics ( Figure 2 and Figure 3 ). Individual topographic structure of maps of various birefringence mechanisms L B and C B , which are formed dendritic (Fragments (1), (2)) and spherulitic (Fragments (1), (2)) components of optically anisotropic supramolecular networks of biological crystals of dehydrated blood plasma films ( Figure 2 ) and saliva ( Figure 3 ). Insignificant differences (the magnitude of the average and the amplitude of fluctuations) between topographic maps of linear birefringence of L B θ * , m , n dendritic components of optically anisotropic architectonics of dehydrated plasma films ( Figure 2 ) and saliva ( Figure 3 ) of healthy donors (Fragments (1)) and prostate cancer patients (Fragments (2)). A significant increase in the circular birefringence of C B θ * , m , n spherulite components of the optically anisotropic architectonics of dehydrated plasma films ( Figure 2 ) and saliva ( Figure 3 ) of healthy donors (Fragments (3)) and prostate cancer patients (Fragments (4)). Quantitative and objective scenarios of changes in various types of birefringence L B θ * , m , n and C B θ * , m , n . The optically anisotropic architectonics of dehydrated films of biological fluids of both types are illustrated by statistical analysis data (ratios (29)), which are presented in Table 2 . The maximum intergroup differences were established: BPF- Δ Z 3 C B = 1.62 ; Δ Z 4 C B = 1.63 ; SF- Δ Z 3 C B = 1.69 ; Δ Z 4 C B = 1.65 . BPF- Δ Z 3 C B = 1.62 ; Δ Z 4 C B = 1.63 ; SF- Δ Z 3 C B = 1.69 ; Δ Z 4 C B = 1.65 . For these statistical parameters, Table 3 shows the values of the sensitivity S e , specificity S p and balanced accuracy A c of the method of layer-by-layer Jones matrix mapping with reproduction of maps of linear and circular birefringence of polycrystalline films of blood plasma and saliva. The results shown in Table 3 indicate a different efficiency in diagnosing prostate cancer by Jones matrix layered reproduction of maps of linear L B θ * , m , n and circular C B θ * , m , n birefringence of BPF and SF. It was found that the layer-by-layer mapping of the linear birefringence distributions L B θ * , m , n of the dendritic component of the optically anisotropic architectonics of dehydrated plasma films is quite sensitive and accurate (87.5%) to the pathological change in the structure of supramolecular networks of needlelike albumin crystals. The accuracy of a similar diagnosis for the dendritic component of the supramolecular network of the dehydrated saliva film appears to be significantly lower (76.4%) due to a lower level of linear birefringence of needle-shaped albumin crystals and a high concentration of optically isotropic cubic NaCl crystals. The most optimal and practically independent of the type of biological fluid was the statistical analysis of the coordinate distributions of the circular birefringence value C B θ * , m , n associated with the concentration of globulins. In this situation, an excellent level of balanced accuracy was achieved: A c Z 3 ; 4 = 93.05 % ÷ 95.8 % .

The relevance of diagnosis and treatment of prostate cancer is undeniable because of the high prevalence and hidden nature of the disease in the global male population [ 1 , 2 , 3 ]. The most important diagnostic task is the differentiation of prostate cancer stages, which determines the prognosis and treatment [ 4 ]. A variety of optical analysis techniques could be a promising avenue for addressing these pressing biomedical challenges [ 5 , 6 , 7 , 8 , 9 , 10 ]. The most sensitive to polarization manifestations of changes in the optical anisotropy of biological objects [ 11 , 12 , 13 , 14 , 15 ] are the multiparameter techniques of Mueller matrix [ 5 , 16 , 17 ], polarimetry [ 10 , 18 , 19 , 20 , 21 , 22 , 23 ], matrix decomposition [ 24 , 25 ] and coordinate mapping [ 26 , 27 , 28 , 29 ] using various analytical approximations [ 6 , 7 , 8 , 9 ], computer proceedings [ 30 , 31 , 32 , 33 , 34 ] and optically devises [ 35 , 36 , 37 , 38 , 39 , 40 ]. The most accurate (gold standard) and mandatory stage of diagnosis is histological and immunohistochemical examination of tumor biopsy, which allows us to make a final conclusion, determine the histological picture of the pathological condition with an accuracy that is close to the maximum (~100%) [ 41 ]. At the same time, these studies are not rapid, require the use of expensive reagents, are also largely subjective, and do not provide the possibility of quantitative analysis of the parameters of microscopic images of internal organ preparations. Currently, instrumental high-precision (~95%) polarization interference methods for differential diagnosis of histological sections of prostate tumor biopsy have been developed, which are devoid of the above disadvantages of traditional histological examination [ 42 ]. At the same time, obtaining a biopsy is a traumatic and sometimes dangerous operation for patients’ health. Therefore, it is relevant to develop new rapid instrumental biophysical methods for differential diagnosis of prostate tumors using a minimally invasive procedure, an optical study of the polycrystalline structure of dehydrated films of biological fluids of human organs. Polarimetric studies of the polarization manifestations of BF anisotropy make it possible to detect pathological changes in the quaternary and tertiary polycrystalline structure of basic proteins (albumin and globulin) in blood plasma and other biological fluids, which are inaccessible in the most common biochemical methods. In a series of works [ 43 , 44 , 45 , 46 , 47 , 48 , 49 , 50 , 51 ], the sensitivity of polarimetric methods to inflammatory, pathological and necrotic changes in the polycrystalline structure of films of blood plasma, urine, synovial fluid, and cerebrospinal fluid was demonstrated. Despite such promising results in diagnosing the structure of biofluid films, there are still a number of unresolved problems. Among them are the following: There is no unified (unified) analytical description of polarization manifestations of optical properties of complex phase and amplitude anisotropic structure of networks of biological crystals in the volume of dehydrated BF films. Algorithms for polarization reconstruction of histograms of polycrystalline networks of biological crystal maps of various optical anisotropy mechanisms, birefringence and dichroism, have not been developed. Dehydrated BF films exhibit a complex spatially inhomogeneous volumetric structure of networks of biological crystals. On the other hand, polarization methods provide integrally averaged information over the whole volume of the biological layer in the form of 2D matrix element distributions. As a consequence, the sensitivity of existing methods of matrix polarimetry does not provide the capability to detect spatially localized changes of optical anisotropy of networks of biological crystals. There is no unified (unified) analytical description of polarization manifestations of optical properties of complex phase and amplitude anisotropic structure of networks of biological crystals in the volume of dehydrated BF films. Algorithms for polarization reconstruction of histograms of polycrystalline networks of biological crystal maps of various optical anisotropy mechanisms, birefringence and dichroism, have not been developed. Dehydrated BF films exhibit a complex spatially inhomogeneous volumetric structure of networks of biological crystals. On the other hand, polarization methods provide integrally averaged information over the whole volume of the biological layer in the form of 2D matrix element distributions. As a consequence, the sensitivity of existing methods of matrix polarimetry does not provide the capability to detect spatially localized changes of optical anisotropy of networks of biological crystals. There is no unified medical-physical approach to the objective evaluation of diagnostic efficiency of matrix polarimetry methods. Thus, a new and urgent issue of matrix polarimetry is the development of the Jones matrix model of analytical description of optical anisotropy of various types of dehydrated films of biological fluids followed by determination of algorithmic relationships between parameters of optical anisotropy of dehydrated BF films and values of partial matrix elements. This polarimetric approach can be developed and generalized into a synthesis of polarization interference mapping and digital holographic reconstruction of object fields of complex amplitudes for layer-by-layer reconstruction of optical anisotropy maps of dehydrated BF films. Therefore, to improve the sensitivity and accuracy of polarimetric matrix diagnostics, it is urgent to create a new method for the layer-by-layer study of polycrystalline films of biological fluids by synthesizing polarization (Jones matrix) and interference methods [ 43 , 44 , 45 , 46 , 47 , 48 , 49 , 50 ]. In addition, the potential of the Jones matrix tomography technique can be expanded to other equally relevant areas, such as instrumental medical diagnostics COVID-19 [ 51 , 52 , 53 ] Our work aims to create and validate a new experimental method of polarization interference multilayer Jones matrix scanning of the polycrystalline structure of blood plasma (BPF) and saliva (SF) for diagnosis and differentiation of prostate cancer stages.

According to traditional concepts [ 54 , 55 ], a polycrystalline film of any biological fluid can be represented as a sequence of partial layers with six different types of phase (optical birefringence–LB (0,90);(45,135) , CB ⊗,⊕ ) and amplitude (LD (0,90);(45,135) , CD ⊗,⊕ ) anisotropy. These LD 0,90 , LD 45,135 and LB 0,90 , LB 45,135 –“linear dichroism–birefringence”; CD ⊗;⊕ and CB ⊗;⊕ –“circular dichroism–birefringence” of biological layer optically anisotropic component for linearly (0° ÷ 90° and 45° ÷ 135°) and circularly right-(⊗) and left-(⊕) polarised others. (1) L B 0 ; 90 = 2 π λ n 0 − n 90 h ; (2) L B 45 ; 135 = 2 π λ n 45 − n 135 h ; (3) C B ⊗ ; ⊕ = 2 π λ n ⊗ − n ⊕ h ; (4) L D 0 ; 90 = 2 π λ χ 0 − χ 90 h ; (5) L D 45 ; 135 = 2 π λ χ 45 − χ 135 h ; (6) C D ⊗ ; ⊕ = 2 π λ χ ⊗ − χ ⊕ h ; where n 0 , n 90 , n 45 , n 135 and χ 0 , χ 90 , χ 45 , χ 135 are refractive indices–absorption for orthogonal amplitude components 0°–90° and 45°–135°; λ —laser wavelength; h —geometrical layer thickness. Given the insignificant absorption of dehydrated BPF and SF in our work, we limit ourselves to taking into account the effects of birefringence. We describe the polarization manifestations of each optical anisotropy mechanism by the Jones partial matrix operators of the formula below [ 48 ]: (7) J L B 0 ; 90 = exp ⁡ − 0.5 i L B 0 ; 90 0 0 exp ⁡ 0.5 i L B 0 ; 90 ; (8) J L B 45 ; 135 = cos ⁡ 0 . 5 L B 45 ; 135 − i sin ⁡ 0 . 5 L B 45 ; 135 − i sin ⁡ 0 . 5 L B 45 ; 135 cos ⁡ 0 . 5 L B 45 ; 135 ; (9) J C B ⊗ ; ⊕ = cos ⁡ C B ⊗ ; ⊕ sin ⁡ C B ⊗ ; ⊕ − sin ⁡ C B ⊗ ; ⊕ cos ⁡ C B ⊗ ; ⊕ ; An analytical form of the generalized Jones matrix of a polycrystalline medium with complex anisotropy was found in [ 48 ] (10) J = j 11 j 12 j 21 j 22 = cos ⁡ 0 . 5 V − i L V sin ⁡ 0 . 5 V C   −   i L ′ V sin ⁡ 0 . 5 V − C   +   i L ′ V sin ⁡ 0 . 5 V cos ⁡ 0 . 5 V + i L V sin ⁡ 0 . 5 V Here V —generalized anisotropy vector (11) V = V L 0 ; 90 , L 45 ; 135 ; − C ⊗ ; ⊕ , where (12) L 0 ; 90 = L B 0 ; 90 ; L 45 ; 135 = L B 45 ; 135 ; C ⊗ ; ⊕ = C B ⊗ ; ⊕ . . From (11) and (12) we obtain an explicit form of the vector modulus V (13) V = L 0 ; 90 + L 45 ; 135 + C ⊗ ; ⊕ 0.5 = L B 2 0 ; 90 + ( L B 2 45 ; 135 ) + C B 2 ⊗ ; ⊕ 0.5 , On the basis of (7)–(13), we obtain theoretical interrelations between the parameters of linear and circular birefringence dichroism and elements of the Jones matrix J of an optically anisotropic layer (14) V = 2 arccos ⁡ 0.5 Re ⁡ j 11 + Re ⁡ j 22 ; (15) L B 0 ; 90 = V 2 sin ⁡ 0 . 5 V Im ⁡ j 22 − Im ⁡ j 11 ; (16) L B 45,135 = V 2 sin ⁡ 0 . 5 V Im ⁡ j 12 + Im ⁡ j 21 ; (17) C B ⊗ ; ⊕ = V 2 sin ⁡ 0 . 5 V Im ⁡ j 12 − Im ⁡ j 21 The algorithm for calculating the elements of the Jones matrix J (Expression (1)) includes the irradiation of a polycrystalline film sample by linearly polarised beams with azimuths 0° (Jones vector 1 0 ) and 90° (Jones vector 0 1 ) (18) U 0 = U x 0 U y o = j 11 j 12 j 21 j 22 1 0 ⇒ j 11 j 21 ⇒ U x 0 = 1 0 0 0 j 11 j 12 ⇒ j 11 ; U y 0 = 0 0 0 1 j 11 j 12 ⇒ j 21 ; (19) U 90 = U x 90 U y 90 = j 11 j 12 j 21 j 22 0 1 ⇒ j 12 j 22 ⇒ U x 90 = 1 0 0 0 j 12 j 22 ⇒ j 21 ; U y 90 = 0 0 0 1 j 12 j 22 ⇒ j 22 . As a result, we obtain the following expressions for the Jones matrix tomography of the polycrystalline structure of a biological fluid film (20) V = 2 arccos ⁡ 0.5 U x 0 exp ⁡ i φ x 0 + U y 90 exp ⁡ i φ y 90 ; (21) L B 0 ; 90 = V 2 sin ⁡ 0 . 5 V U y 90 sin ⁡ φ y 90 − U x 0 sin ⁡ φ x 0 ; (22) L B 45,135 = V 2 sin ⁡ 0 . 5 V U y 0 sin ⁡ φ y 0 − U x 90 sin ⁡ φ x 90 ; (23) C B ⊗ ; ⊕ = V 2 sin ⁡ 0 . 5 V U y 0 sin ⁡ φ y 0 − U x 90 sin ⁡ φ x 90 ; In further experimental studies, we will use the generally accepted parameters for the different types of birefringence (24) L B = L B 0 ; 90 2 + L B 45 ; 135 2 ; (25) C B ≡ C B ⊗ ; ⊕ .

At the first stage, layer-by-layer maps f ≡ L B θ k , m , n ; C B θ , m , n of BPF and SF of healthy donors were studied. The results of 3D Jones matrix layer-by-layer tomography for phase planes θ k = 0.1   rad ; 0.25   rad ; 0.5   rad are presented in the framework of statistical analysis of changes in coordinate distributions of the magnitude of optical birefringence parameters of supramolecular networks of biological crystals. Such processes are quantitatively characterized by a set of mean values Z ¯ i and standard deviations ± 2 σ (within group 1 and group 3) of the values of statistical moments Z i (Relation (29)) characterizing the maps of optical anisotropy f ≡ L B θ k , m , n ; C B θ , m , n of polycrystalline films of blood plasma and saliva ( Table 1 ). The data obtained revealed the individual means of all parameters Z i , characterizing the statistical structure of BPF and SF maps f ≡ L B θ k , m , n ; C B θ , m , n , in all phase planes, θ k = 0.1   rad ; 0.25   rad ; 0.5   rad . The largest phase ( θ k ) differences were found for the statistical moments of the 3rd and 4th orders, which characterize the skewness and kurtosis of the distributions of the optical anisotropy parameters f ≡ L B θ k , m , n ; C B θ , m , n of polycrystalline films of biological fluids: BPF- Δ Z 3 L B = 2.48 ; Δ Z 4 L B = 2.02 and Δ Z 3 C B = 2.86 ; Δ Z 4 C B = 1.99 ; SF- Δ Z 3 L B = 2.52 ; Δ Z 4 L B = 2.03 and Δ Z 3 C B = 2.84 ; Δ Z 4 C B = 2.02 BPF- Δ Z 3 L B = 2.48 ; Δ Z 4 L B = 2.02 and Δ Z 3 C B = 2.86 ; Δ Z 4 C B = 1.99 ; SF- Δ Z 3 L B = 2.52 ; Δ Z 4 L B = 2.03 and Δ Z 3 C B = 2.84 ; Δ Z 4 C B = 2.02

For the first time, the Jones matrix analytical model for the optical anisotropy description of different types of dehydrated films of biological fluids, such as blood plasma and saliva, is proposed. New algorithmic relationships between phase anisotropy parameters (birefringence and optical activity) of dehydrated films and values of partial elements of the Jones matrix were found. Based on the synthesis of polarization interference mapping and digital holographic reconstruction of object fields of complex amplitudes, a new technique of phase Jones matrix scanning with the subsequent layer-by-layer reconstruction of optically mapped optically anisotropic structure of dehydrated biological liquid films was developed and tested experimentally for the first time. An original algorithm for determining the cross section in the volume of dehydrated films of biological fluids is proposed, which is most effective for differential diagnosis of pathological changes in optical birefringence. New objective criteria (markers) for high accuracy (93.05% to 95.8%) diagnosis and differentiation (91.7% to 94.4%) of prostate cancer stages have been defined in the statistical Jones matrix analysis of the reconstructed optical anisotropy maps of dehydrated blood plasma and saliva samples. The present study is one of the first steps in the fundamental development and experimental testing of the diagnostic potential of the Jones express technique matrix tomography of polycrystalline architectonics of dehydrated human fluid films. The next steps in the development of this method will be experimental studies planned on the scale of clinical institutions of the countries represented by the members of the author’s team for the purpose of expert evaluation and determination of the validity of Jones matrix tomography of pathological conditions of human organs.